US20060216209A1

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Publication number: US20060216209A1
Application number: US11/316,205
Authority: US
Inventors: James Braig; Peter Rule
Original assignee: Individual
Current assignee: Optiscan Biomedical Corp
Priority date: 2005-02-14
Filing date: 2005-12-21
Publication date: 2006-09-28
Also published as: WO2006088772A1; US7860543B2; US20070081626A1; US20070082342A1; WO2006088785A1; WO2007044492A2; US20060195046A1; WO2007044492A3; US20070083091A1; WO2007044055A1; US7860542B2

Abstract

In certain embodiments, a sampling assembly is for use with a main analyzer. The main analyzer is configured to sense an analyte in a body fluid obtained from a patient through a first fluid passageway extending from the main analyzer. The sampling assembly includes an instrument portion separate from the main analyzer and including at least one sensor. The instrument portion is removably engaged with the first fluid passageway. The at least one sensor is in sensing engagement with the first fluid passageway such that the at least one sensor can sense a property of a fluid within the first fluid passageway.

Description

RELATED APPLICATIONS

This application claims the benefit under 35 U.S.C. § 119(e) of U.S. Provisional Application No. 60/652,660, filed Feb. 14, 2005, titled ANALYTE DETECTION SYSTEM; U.S. Provisional Application No. 60/724,199, filed Oct. 6, 2005, titled INTENSIVE CARE UNIT BLOOD ANALYSIS SYSTEM AND METHOD; U.S. Provisional Application No. 60/658,001, filed Mar. 2, 2005, titled SEPARATING BLOOD SAMPLE FOR ANALYTE DETECTION SYSTEM; and of U.S. Provisional Application No. 60/673,551, filed Apr. 21, 2005, titled APPARATUS AND METHODS FOR SEPARATING SAMPLE FOR ANALYTE DETECTION SYSTEM. The entire contents of each of the above-listed provisional applications are hereby incorporated by reference herein and made part of this specification.

BACKGROUND

1. Field

Certain embodiments disclosed herein relate to methods and apparatus for determining the concentration of an analyte in a sample, such as an analyte in a sample of bodily fluid, as well as methods and apparatus which can be used to support the making of such determinations.

2. Description of the Related Art

It is a common practice to measure the levels of certain analytes, such as glucose, in a bodily fluid, such as blood. Often this is done in a hospital or clinical setting when there is a risk that the levels of certain analytes may move outside a desired range, which in turn can jeopardize the health of a patient. Certain currently known systems for analyte monitoring in a hospital or clinical setting suffer from various drawbacks.

SUMMARY

In certain embodiments, a sampling assembly is configured for use with a main analyzer. The main analyzer is configured to sense an analyte in a body fluid obtained from a patient through a first fluid passageway extending from the main analyzer. The sampling assembly comprises an instrument portion separate from the main analyzer and comprising at least one sensor. The instrument portion is removably engaged with the first fluid passageway. The at least one sensor is in sensing engagement with the first fluid passageway such that the at least one sensor can sense a property of a fluid within the first fluid passageway. In certain other embodiments, the at least one sensor is configured to detect the arrival of the body fluid in the first fluid passageway.

In certain embodiments, a sampling assembly is configured for use with a main analyzer. The main analyzer is configured to sense an analyte in a body fluid obtained from a patient through a first fluid passageway. The passageway has a patient end spaced from the main analyzer and an interface region where the first fluid passageway meets the main analyzer. The sampling assembly comprises an instrument portion comprising at least one sensor. The instrument portion is removably engaged with the first fluid passageway between the patient end and the interface region. The at least one sensor is in sensing engagement with the first fluid passageway such that the at least one sensor can sense a property of a fluid contained in the first fluid passageway. In certain other embodiments, the at least one sensor is configured to detect the arrival of the body fluid in the first fluid passageway.

In certain embodiments, a body fluid analysis system comprises a main analyzer configured to measure an analyte in a sample of body fluid obtained from a patient. The body fluid analysis system further comprises a sampling assembly in communication with the main analyzer. The sampling assembly comprises a first fluid passageway extending from the main analyzer and having a patient end spaced from the main analyzer. The sampling assembly further comprises an instrument portion removably engaged with the first fluid passageway and located on the first fluid passageway spaced from the main analyzer. The instrument portion has at least one sensor in sensing engagement with the first fluid passageway. In certain other embodiments, at least one of the at least one sensor is configured to detect the arrival of the body fluid in the first fluid passageway.

In certain embodiments, a method of handles body fluid within a first fluid passageway which extends from and is in fluid communication with a main analyzer. The method comprises removably engaging the first fluid passageway with a sensing module separate from the main analyzer. The method further comprises, with at least one sensor of the sensing module, sensing a property of a fluid within the first fluid passageway. In certain other embodiments, the sensing comprises sensing the arrival of the fluid in the first fluid passageway.

Certain objects and advantages of the invention(s) are described herein. Of course, it is to be understood that not necessarily all such objects or advantages may be achieved in accordance with any particular embodiment. Thus, for example, those skilled in the art will recognize that the invention(s) may be embodied or carried out in a manner that achieves or optimizes one advantage or group of advantages as taught herein without necessarily achieving other objects or advantages as may be taught or suggested herein.

Certain embodiments are summarized above. However, despite the foregoing discussion of certain embodiments, only the appended claims (and not the present summary) are intended to define the invention(s). The summarized embodiments, and other embodiments, will become readily apparent to those skilled in the art from the following detailed description of the preferred embodiments having reference to the attached figures, the invention(s) not being limited to any particular embodiment(s) disclosed.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic of a fluid handling system in accordance with one embodiment;

FIG. 1A is a schematic of a fluid handling system, wherein a fluid handling and analysis apparatus of the fluid handling system is shown in a cutaway view;

FIG. 1B is a cross-sectional view of a bundle of the fluid handling system ofFIG. 1A taken along theline1B-1B;

FIG. 2 is a schematic of an embodiment of a sampling apparatus of the present invention;

FIG. 3 is a schematic showing details of an embodiment of a sampling apparatus of the present invention;

FIG. 4 is a schematic of an embodiment of a sampling unit of the present invention;

FIG. 5 is a schematic of an embodiment of a sampling apparatus of the present invention;

FIG. 6A is a schematic of an embodiment of gas injector manifold of the present invention;

FIG. 6B is a schematic of an embodiment of gas injector manifold of the present invention;

FIGS. 7A-7J are schematics illustrating methods of using the infusion and blood analysis system of the present invention, whereFIG. 7A shows one embodiment of a method of infusing a patient, andFIGS. 7B-7J illustrate steps in a method of sampling from a patient, whereFIG. 7B shows fluid being cleared from a portion of the first and second passageways;FIG. 7C shows a sample being drawn into the first passageway;FIG. 7D shows a sample being drawn into second passageway;FIG. 7E shows air being injected into the sample;FIG. 7F shows bubbles being cleared from the second passageway;FIGS. 7H and 7I show the sample being pushed part way into the second passageway followed by fluid and more bubbles; andFIG. 7J shows the sample being pushed to analyzer;

FIG. 8 is a perspective front view of an embodiment of a sampling apparatus of the present invention;

FIG. 9 is a schematic front view of one embodiment of a sampling apparatus cassette of the present invention;

FIG. 10 is a schematic front view of one embodiment of a sampling apparatus instrument of the present invention;

FIG. 11 is an illustration of one embodiment of an arterial patient connection of the present invention;

FIG. 12 is an illustration of one embodiment of a venous patient connection of the present invention;

FIGS. 13A, 13B, and13C are various views of one embodiment of a pinch valve of the present invention, whereFIG. 13A is a front view,FIG. 13B is a sectional view, andFIG. 13C is a sectional view showing one valve in a closed position;

FIGS. 14A and 14B are various views of one embodiment of a pinch valve of the present invention, whereFIG. 14A is a front view andFIG. 14B is a sectional view showing one valve in a closed position;

FIG. 15 is a side view of one embodiment of a separator;

FIG. 16 is an exploded perspective view of the separator ofFIG. 15;

FIG. 17 is one embodiment of a fluid analysis apparatus of the present invention;

FIG. 18 is a top view of a cuvette for use in the apparatus ofFIG. 17;

FIG. 19 is a side view of the cuvette ofFIG. 18;

FIG. 20 is an exploded perspective view of the cuvette ofFIG. 18;

FIG. 21 is a schematic of an embodiment of a sample preparation unit;

FIG. 22A is a perspective view of another embodiment of a fluid handling and analysis apparatus having a main instrument and removable cassette;

FIG. 22B is a partial cutaway, side elevational view of the fluid handling and analysis apparatus with the cassette spaced from the main instrument;

FIG. 22C is a cross-sectional view of the fluid handling and analysis apparatus ofFIG. 22A wherein the cassette is installed onto the main instrument;

FIG. 23A is a cross-sectional view of the cassette of the fluid handling and analysis apparatus ofFIG. 22A taken along theline23A-23A;

FIG. 23B is a cross-sectional view of the cassette ofFIG. 23A taken along theline23B-23B ofFIG. 23A;

FIG. 23C is a cross-sectional view of the fluid handling and analysis apparatus having a fluid handling network, wherein a rotor of the cassette is in a generally vertical orientation;

FIG. 23D is a cross-sectional view of the fluid handling and analysis apparatus, wherein the rotor of the cassette is in a generally horizontal orientation;

FIG. 23E is a front elevational view of the main instrument of the fluid handling and analysis apparatus ofFIG. 23C;

FIG. 24A is a cross-sectional view of the fluid handling and analysis apparatus having a fluid handling network in accordance with another embodiment;

FIG. 24B is a front elevational view of the main instrument of the fluid handling and analysis apparatus ofFIG. 24A;

FIG. 25A is a front elevational view of a rotor having a sample element for holding sample fluid;

FIG. 25B is a rear elevational view of the rotor ofFIG. 25A;

FIG. 25C is a front elevational view of the rotor ofFIG. 25A with the sample element filled with a sample fluid;

FIG. 25D is a front elevational view of the rotor ofFIG. 25C after the sample fluid has been separated;

FIG. 25E is a cross-sectional view of the rotor taken along theline25E-25E ofFIG. 25A;

FIG. 25F is an enlarged sectional view of the rotor ofFIG. 25E;

FIG. 26A is an exploded perspective view of a sample element for use with a rotor of a fluid handling and analysis apparatus;

FIG. 26B is a perspective view of an assembled sample element;

FIG. 27A is a front elevational view of a fluid interface for use with a cassette;

FIG. 27B is a top elevational view of the fluid interface ofFIG. 27A;

FIG. 27C is an enlarged side view of a fluid interface engaging a rotor;

FIG. 28 is a cross-sectional view of the main instrument of the fluid handling and analysis apparatus ofFIG. 22A taken along the line28-28;

FIG. 29 is a graph illustrating the absorption spectra of various components that may be present in a blood sample;

FIG. 30 is a graph illustrating the change in the absorption spectra of blood having the indicated additional components ofFIG. 29 relative to a Sample Population blood and glucose concentration, where the contribution due to water has been numerically subtracted from the spectra;

FIG. 31 is an embodiment of an analysis method for determining the concentration of an analyte in the presence of possible interferents;

FIG. 32 is one embodiment of a method for identifying interferents in a sample for use with the embodiment ofFIG. 31;

FIG. 33A is a graph illustrating one embodiment of the method ofFIG. 32, andFIG. 33B is a graph further illustrating the method ofFIG. 32;

FIG. 34 is a one embodiment of a method for generating a model for identifying possible interferents in a sample for use with an embodiment ofFIG. 31;

FIG. 35 is a schematic of one embodiment of a method for generating randomly-scaled interferent spectra;

FIG. 36 is one embodiment of a distribution of interferent concentrations for use with the embodiment ofFIG. 35;

FIG. 37 is a schematic of one embodiment of a method for generating combination interferent spectra;

FIG. 38 is a schematic of one embodiment of a method for generating an interferent-enhanced spectral database;

FIG. 39 is a graph illustrating the effect of interferents on the error of glucose estimation;

FIGS. 40A, 40B,40C, and40D each have a graph showing a comparison of the absorption spectrum of glucose with different interferents taken using two different techniques: a Fourier Transform Infrared (FTIR) spectrometer having an interpolated resolution of 1 cm⁻¹(solid lines with triangles); and by 25 finite-bandwidth IR filters having a Gaussian profile and full-width half-maximum (FWHM) bandwidth of 28 cm⁻¹corresponding to a bandwidth that varies from 140 nm at 7.08 μm, up to 279 nm at 10 μm (dashed lines with circles). The Figures show a comparison of glucose with mannitol (FIG. 40A), dextran (FIG. 40B), n-acetyl L cysteine (FIG. 40C), and procainamide (FIG. 40D), at a concentration level of 1 mg/dL and path length of 1 μm;

FIG. 41 shows a graph of the blood plasma spectra for 6 blood sample taken from three donors in arbitrary units for a wavelength range from 7 μm to 10 μm, where the symbols on the curves indicate the central wavelengths of the 25 filters;

FIGS. 42A, 42B,42C, and42D contain spectra of the Sample Population of 6 samples having random amounts of mannitol (FIG. 42A), dextran (FIG. 42B), n-acetyl L cysteine (FIG. 42C), and procainamide (FIG. 42D), at a concentration levels of 1 mg/dL and path lengths of 1 μm;

FIGS. 43A-43D are graphs comparing calibration vectors obtained by training in the presence of an interferent, to the calibration vector obtained by training on clean plasma spectra for mannitol (FIG. 43A), dextran (FIG. 43B), n-acetyl L cysteine (FIG. 43C), and procainamide (FIG. 43D) for water-free spectra;

FIG. 44 is a schematic illustration of another embodiment of the analyte detection system;

FIG. 45 is a plan view of one embodiment of a filter wheel suitable for use in the analyte detection system depicted inFIG. 44;

FIG. 46 is a partial sectional view of another embodiment of an analyte detection system; *

FIG. 47 is a detailed sectional view of a sample detector of the analyte detection system illustrated inFIG. 46; and

FIG. 48 is a detailed sectional view of a reference detector of the analyte detection system illustrated inFIG. 46.

Reference symbols are used in the Figures to indicate certain components, aspects or features shown therein, with reference symbols common to more than one Figure indicating like components, aspects or features shown therein.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Although certain preferred embodiments and examples are disclosed below, it will be understood by those skilled in the art that the inventive subject matter extends beyond the specifically disclosed embodiments to other alternative embodiments and/or uses of the invention, and to obvious modifications and equivalents thereof. Thus it is intended that the scope of the inventions herein disclosed should not be limited by the particular disclosed embodiments described below. Thus, for example, in any method or process disclosed herein, the acts or operations making up the method/process may be performed in any suitable sequence, and are not necessarily limited to any particular disclosed sequence. For purposes of contrasting various embodiments with the prior art, certain aspects and advantages of these embodiments are described where appropriate herein. Of course, it is to be understood that not necessarily all such aspects or advantages may be achieved in accordance with any particular embodiment. Thus, for example, it should be recognized that the various embodiments may be carried out in a manner that achieves or optimizes one advantage or group of advantages as taught herein without necessarily achieving other aspects or advantages as may be taught or suggested herein. While the systems and methods discussed herein can be used for invasive techniques, the systems and methods can also be used for non-invasive techniques or other suitable techniques, and can be used in hospitals, healthcare facilities, ICUs, or residences.

Overview of Embodiments of Fluid Handling Systems

Disclosed herein are fluid handling systems and various methods of analyzing sample fluids.FIG. 1 illustrates an embodiment of afluid handling system10 which can determine the concentration of one or more substances in a sample fluid, such as a whole blood sample from a patient P. Thefluid handling system10 can also deliver aninfusion fluid14 to the patient P.

Thefluid handling system10 is located bedside and generally comprises acontainer15 holding theinfusion fluid14 and asampling system100 which is in communication with both thecontainer15 and the patient P. Atube13 extends from thecontainer15 to thesampling system100. Atube12 extends from thesampling system100 to the patient P. In some embodiments, one or more components of thefluid handling system10 can be located at another facility, room, or other suitable remote location. One or more components of thefluid handling system10 can communicate with one or more other components of the fluid handling system10 (or with other devices) by any suitable communication means, such as communication interfaces including, but not limited to, optical interfaces, electrical interfaces, and wireless interfaces. These interfaces can be part of a local network, internet, wireless network, or other suitable networks.

TheInfusion fluid14 can comprise water, saline, dextrose, lactated Ringer's solution, drugs, insulin, mixtures thereof, or other suitable substances. The illustratedsampling system100 allows the infusion fluid to pass to the patient P and/or uses the infusion fluid in the analysis. In some embodiments, thefluid handling system10 may not employ infusion fluid. Thefluid handling system10 may thus draw samples without delivering any fluid to the patient P.

Thesampling system100 can be removably or permanently coupled to thetube13 andtube12 via

connectors

110,120. Thepatient connector110 can selectively control the flow of fluid through abundle130, which includes apatient connection passageway112 and asampling passageway113, as shown inFIG. 1B. Thesampling system100 can also draw one or more samples from the patient P by any suitable means. Thesampling system100 can perform one or more analyses on the sample, and then returns the sample to the patient or a waste container. In some embodiments, thesampling system100 is a modular unit that can be removed and replaced as desired. Thesampling system100 can include, but is not limited to, fluid handling and analysis apparatuses, connectors, passageways, catheters, tubing, fluid control elements, valves, pumps, fluid sensors, pressure sensors, temperature sensors, hematocrit sensors, hemoglobin sensors, calorimetric sensors, and gas (or “bubble”) sensors, fluid conditioning elements, gas injectors, gas filters, blood plasma separators, and/or communication devices (e.g., wireless devices) to permit the transfer of information within the sampling system or betweensampling system100 and a network. The illustratedsampling system100 has apatient connector110 and a fluid handling andanalysis apparatus140, which analyzes a sample drawn from the patient P. The fluid handling andanalysis apparatus140 andpatient connector110 cooperate to control the flow of infusion fluid into, and/or samples withdrawn from, the patient P. Samples can also be withdrawn and transferred in other suitable manners.

FIG. 1A is a close up view of the fluid handling andanalysis apparatus140 which is partially cutaway to reveal some of its internal components. The fluid handling andanalysis apparatus140 preferably includes apump203 that controls the flow of fluid from thecontainer15 to the patient P and/or the flow of fluid drawn from the patient P. Thepump203 can selectively control fluid flow rates, direction(s) of fluid flow(s), and other fluid flow parameters as desired. As used herein, the term “pump” is a broad term and means, without limitation, a pressurization/pressure device, vacuum device, or any other suitable means for causing fluid flow. Thepump203 can include, but is not limited to, a reversible peristaltic pump, two unidirectional pumps that work in concert with valves to provide flow in two directions, a unidirectional pump, a displacement pump, a syringe, a diaphragm pump, roller pump, or other suitable pressurization device.

The illustrated fluid handling andanalysis apparatus140 has adisplay141 andinput devices143. The illustrated fluid handling andanalysis apparatus140 can also have asampling unit200 configured to analyze the drawn fluid sample. Thesampling unit200 can thus receive a sample, prepare the sample, and/or subject the sample (prepared or unprepared) to one or more tests. Thesampling unit200 can then analyze results from the tests. Thesampling unit200 can include, but is not limited to, separators, filters, centrifuges, sample elements, and/or detection systems, as described in detail below. The sampling unit200 (seeFIG. 3) can include an analyte detection system for detecting the concentration of one or more analytes in the body fluid sample. In some embodiments, thesampling unit200 can prepare a sample for analysis. If the fluid handling andanalysis apparatus140 performs an analysis on plasma contained in whole blood taken from the patient P, filters, separators, centrifuges, or other types of sample preparation devices can be used to separate plasma from other components of the blood. After the separation process, thesampling unit200 can analyze the plasma to determine, for example, the patient P's glucose level. Thesampling unit200 can employ spectroscopic methods, calorimetric methods, electrochemical methods, or other suitable methods for analyzing samples.

With continued reference toFIGS. 1 and 1A, the fluid14 in thecontainer15 can flow through thetube13 and into afluid source passageway111. The fluid can further flow through thepassageway111 to thepump203, which can pressurize the fluid. The fluid14 can then flow from thepump203 through thepatient connection passageway112 andcatheter11 into the patient P. To analyze the patient's P body fluid (e.g., whole blood, blood plasma, interstitial fluid, bile, sweat, excretions, etc.), the fluid handling andanalysis apparatus140 can draw a sample from the patient P through thecatheter11 to apatient connector110. Thepatient connector110 directs the fluid sample into thesampling passageway113 which leads to thesampling unit200. Thesampling unit200 can perform one or more analyses on the sample. The fluid handling andanalysis apparatus140 can then output the results obtained by thesampling unit200 on thedisplay141.

In some embodiments, thefluid handling system10 can draw and analyze body fluid sample(s) from the patient P to provide real-time or near-real-time measurement of glucose levels. Body fluid samples can be drawn from the patient P continuously, at regular intervals (e.g., every 5, 10, 15, 20, 30 or 60 minutes), at irregular intervals, or at any time or sequence for desired measurements. These measurements can be displayed bedside with thedisplay141 for convenient monitoring of the patient P.

In some embodiments, thefluid handling system10 is a disposable fluid handling system and/or has one or more disposable components. As used herein, the term “disposable” when applied to a system or component (or combination of components), such as a cassette or sample element, is a broad term and means, without limitation, that the component in question is used a finite number of times and then discarded. Some disposable components are used only once and then discarded. Other disposable components are used more than once and then discarded. For example, the fluid handling andanalysis apparatus140 can have a main instrument and a disposable cassette that can be installed onto the main instrument, as discussed below. The disposable cassette can be used for predetermined length of time, to prepare a predetermined amount of sample fluid for analysis, etc. In some embodiments, the cassette can be used to prepare a plurality of samples for subsequent analyses by the main instrument. The reusable main instrument can be used with any number of cassettes as desired. Additionally or alternatively, the cassette can be a portable, handheld cassette for convenient transport. In these embodiments, the cassette can be manually mounted to or removed from the main instrument. In some embodiments, the cassette may be a non disposable cassette which can be permanently coupled to the main instrument, as discussed below.

Disclosed herein are a number of embodiments of fluid handling systems, sampling systems, fluid handling and analysis apparatuses, analyte detection systems, and methods of using the same. Section I below discloses various embodiments of the fluid handling system that may be used to transport fluid from a patient for analysis. Section II below discloses several embodiments of fluid handling methods that may be used with the apparatus discussed in Section I. Section III below discloses several embodiments of a sampling system that may be used with the apparatus of Section I or the methods of Section II. Section IV below discloses various embodiments of a sample analysis system that may be used to detect the concentration of one or more analytes in a material sample. Section V below discloses methods for determining analyte concentrations from sample spectra.

Section I—Fluid Handling System

FIG. 1 is a schematic of thefluid handling system10 which includes thecontainer15 supported by thestand16 and having an interior that is fillable with the fluid14, thecatheter11, and thesampling system100.Fluid handling system10 includes one ormore passageways20 that form conduits between the container, the sampling system, and the catheter. Generally,sampling system100 is adapted to accept a fluid supply, such asfluid14, and to be connected to a patient, including, but not limited tocatheter11 which is used to catheterize apatient P. Fluid14 includes, but is not limited to, fluids for infusing a patient such as saline, lactated Ringer's solution, or water.Sampling system100, when so connected, is then capable of providing fluid to the patient. In addition,sampling system100 is also capable of drawing samples, such as blood, from the patient throughcatheter11 andpassageways20, and analyzing at least a portion of the drawn sample.Sampling system100 measures characteristics of the drawn sample including, but not limited to, one or more of the blood plasma glucose, blood urea nitrogen (BUN), hematocrit, hemoglobin, or lactate levels. Optionally,sampling system100 includes other devices or sensors to measure other patient or apparatus related information including, but not limited to, patient blood pressure, pressure changes within the sampling system, or sample draw rate.

More specifically,FIG. 1 showssampling system100 as including thepatient connector110, the fluid handling andanalysis apparatus140, and theconnector120.Sampling system100 may include combinations of passageways, fluid control and measurement devices, and analysis devices to direct, sample, and analyze fluid.Passageways20 ofsampling system100 include thefluid source passageway111 fromconnector120 to fluid handling andanalysis apparatus140, thepatient connection passageway112 from the fluid handling and analysis apparatus topatient connector110, and thesampling passageway113 from the patient connector to the fluid handling and analysis apparatus. The reference ofpassageways20 as including one or more passageway, for

example passageways

111,112, and113 are provided to facilitate discussion of the system. It is understood that passageways may include one or more separate components and may include other intervening components including, but not limited to, pumps, valves, manifolds, and analytic equipment.

As used herein, the term “passageway” is a broad term and is used in its ordinary sense and includes, without limitation except as explicitly stated, as any opening through a material through which a fluid, such as a liquid or a gas, may pass so as to act as a conduit. Passageways include, but are not limited to, flexible, inflexible or partially flexible tubes, laminated structures having openings, bores through materials, or any other structure that can act as a conduit and any combination or connections thereof. The internal surfaces of passageways that provide fluid to a patient or that are used to transport blood are preferably biocompatible materials, including but not limited to silicone, polyetheretherketone (PEEK), or polyethylene (PE). One type of preferred passageway is a flexible tube having a fluid contacting surface formed from a biocompatible material. A passageway, as used herein, also includes separable portions that, when connected, form a passageway.

The inner passageway surfaces may include coatings of various sorts to enhance certain properties of the conduit, such as coatings that affect the ability of blood to clot or to reduce friction resulting from fluid flow. Coatings include, but are not limited to, molecular or ionic treatments.

As used herein, the term “connected” is a broad term and is used in its ordinary sense and includes, without limitation except as explicitly stated, with respect to two or more things (e.g., elements, devices, patients, etc.): a condition of physical contact or attachment, whether direct, indirect (via, e.g., intervening member(s)), continuous, selective, or intermittent; and/or a condition of being in fluid, electrical, or optical-signal communication, whether direct, indirect, continuous, selective (e.g., where there exist one or more intervening valves, fluid handling components, switches, loads, or the like), or intermittent. A condition of fluid communication is considered to exist whether or not there exists a continuous or contiguous liquid or fluid column extending between or among the two or more things in question. Various types of connectors can connect components of the fluid handling system described herein. As used herein, the term “connector” is a broad term and is used in its ordinary sense and includes, without limitation except as explicitly stated, as a device that connects passageways or electrical wires to provide communication (whether direct, indirect, continuous, selective, or intermittent) on either side of the connector. Connectors contemplated herein include a device for connecting any opening through which a fluid may pass. These connectors may have intervening valves, switches, fluid handling devices, and the like for affecting fluid flow. In some embodiments, a connector may also house devices for the measurement, control, and preparation of fluid, as described in several of the embodiments.

Fluid handling andanalysis apparatus140 may control the flow of fluids throughpassageways20 and the analysis of samples drawn from a patient P, as described subsequently. Fluid handling andanalysis apparatus140 includes thedisplay141 and input devices, such asbuttons143.Display141 provides information on the operation or results of an analysis performed by fluid handling andanalysis apparatus140. In one embodiment,display141 indicates the function ofbuttons143, which are used to input information into fluid handling andanalysis apparatus140. Information that may be input into or obtained by fluid handling andanalysis apparatus140 includes, but is not limited to, a required infusion or dosage rate, sampling rate, or patient specific information which may include, but is not limited to, a patient identification number or medical information. In an other alternative embodiment, fluid handling andanalysis apparatus140 obtains information on patient P over a communications network, for example an hospital communication network having patient specific information which may include, but is not limited to, medical conditions, medications being administered, laboratory blood reports, gender, and weight. As one example of the use offluid handling system10, which is not meant to limit the scope of the present invention,FIG. 1 showscatheter11 connected to patient P.

As discussed subsequently,fluid handling system10 may catheterize a patient's vein or artery.Sampling system100 is releasably connectable tocontainer15 andcatheter11. Thus, for example,FIG. 1 showscontainer15 as including thetube13 to provide for the passage of fluid to, or from, the container, andcatheter11 as including thetube12 external to the patient.Connector120 is adapted to jointube13 andpassageway111.Patient connector110 is adapted to jointube12 and to provide for a connection between

passageways

112 and113.

Patient connector

110 may also include one or more devices that control, direct, process, or otherwise affect the flow through

passageways

112 and113. In some embodiments, one ormore lines114 are provided to exchange signals betweenpatient connector110 and fluid handling andanalysis apparatus140. Thelines114 can be electrical lines, optical communicators, wireless communication channels, or other means for communication. As shown inFIG. 1,sampling system100 may also include

passageways

112 and113, and lines114. The passageways and electrical lines betweenapparatus140 andpatient connector110 are referred to, with out limitation, as thebundle130.

In various embodiments, fluid handling andanalysis apparatus140 and/orpatient connector110, includes other elements (not shown inFIG. 1) that include, but are not limited to: fluid control elements, including but not limited to valves and pumps; fluid sensors, including but not limited to pressure sensors, temperature sensors, hematocrit sensors, hemoglobin sensors, colorimetric sensors, and gas (or “bubble”) sensors; fluid conditioning elements, including but not limited to gas injectors, gas filters, and blood plasma separators; and wireless communication devices to permit the transfer of information within the sampling system or betweensampling system100 and a wireless network.

In one embodiment,patient connector110 includes devices to determine when blood has displacedfluid14 at the connector end, and thus provides an indication of when a sample is available for being drawn throughpassageway113 for sampling. The presence of such a device atpatient connector110 allows for the operation offluid handling system10 for analyzing samples without regard to the actual length oftube12. Accordingly, bundle130 may include elements to provide fluids, including air, or information communication betweenpatient connector110 and fluid handling andanalysis apparatus140 including, but not limited to, one or more other passageways and/or wires.

In one embodiment ofsampling system100, the passageways and lines ofbundle130 are sufficiently long to permit locatingpatient connector110 near patient P, for example withtube12 having a length of less than 0.1 to 0.5 meters, or preferably approximately 0.15 meters and with fluid handling andanalysis apparatus140 located at a convenient distance, for example on anearby stand16. Thus, for example, bundle130 is from 0.3 to 3 meters, or more preferably from 1.5 to 2.0 meters in length. It is preferred, though not required, thatpatient connector110 andconnector120 include removable connectors adapted for fitting to

tubes

12 and13, respectively. Thus, in one embodiment,container15/tube13 andcatheter11/tube12 are both standard medical components, andsampling system100 allows for the easy connection and disconnection of one or both of the container and catheter fromfluid handling system10.

In another embodiment ofsampling system100,

tubes

12 and13 and a substantial portion of

passageways

111 and112 have approximately the same internal cross-sectional area. It is preferred, though not required, that the internal cross-sectional area ofpassageway113 is less than that ofpassageways111 and112 (seeFIG. 1B). As described subsequently, the difference in areas permitsfluid handling system10 to transfer a small sample volume of blood frompatient connector110 into fluid handling andanalysis apparatus140.

Thus, for example, in one embodiment passageways111 and112 are formed from a tube having an inner diameter from 0.3 millimeter to 1.50 millimeter, or more preferably having a diameter from 0.60 millimeter to 1.2 millimeter.Passageway113 is formed from a tube having an inner diameter from 0.3 millimeter to 1.5 millimeter, or more preferably having an inner diameter of from 0.6 millimeter to 1.2 millimeter.

WhileFIG. 1 showssampling system100 connecting a patient to a fluid source, the scope of the present disclosure is not meant to be limited to this embodiment. Alternative embodiments include, but are not limited to, a greater or fewer number of connectors or passageways, or the connectors may be located at different locations withinfluid handling system10, and alternate fluid paths. Thus, for example,

passageways

111 and112 may be formed from one tube, or may be formed from two or more coupled tubes including, for example, branches to other tubes withinsampling system100, and/or there may be additional branches for infusing or obtaining samples from a patient. In addition,patient connector110 andconnector120 andsampling system100 alternatively include additional pumps and/or valves to control the flow of fluid as described below.

FIGS. 1A and 2 illustrate asampling system100 configured to analyze blood from patient P which may be generally similar to the embodiment of the sampling system illustrated inFIG. 1, except as further detailed below. Where possible, similar elements are identified with identical reference numerals in the depiction of the embodiments of FIGS.1 to2.FIGS. 1A and 2

show patient connector

110 as including asampling assembly220 and aconnector230, portions of

passageways

111 and113, andlines114, and fluid handling andanalysis apparatus140 as including thepump203, thesampling unit200, and acontroller210. Thepump203,sampling unit200, andcontroller210 are contained within ahousing209 of the fluid handling andanalysis apparatus140. Thepassageway111 extends from theconnector120 through thehousing209 to thepump203. Thebundle130 extends from thepump203,sampling unit200, andcontroller210 to thepatient connector110.

InFIGS. 1A and 2, thepassageway111 provides fluid communication betweenconnector120 and pump203 andpassageway113 provides fluid communication betweenpump203 andconnector110.Controller210 is in communication withpump203,sampling unit200, andsampling assembly220 throughlines114.Controller210 has access tomemory212, and optionally has access to amedia reader214, including but not limited to a DVD or CD-ROM reader, and communications link216, which can comprise a wired or wireless communications network, including but not limited to a dedicated line, an intranet, or an Internet connection.

As described subsequently in several embodiments, samplingunit200 may include one or more passageways, pumps and/or valves, andsampling assembly220 may include passageways, sensors, valves, and/or sample detection devices.Controller210 collects information from sensors and devices withinsampling assembly220, from sensors and analytical equipment withinsampling unit200, and provides coordinated signals to controlpump203 and pumps and valves, if present, insampling assembly220.

Fluid handling andanalysis apparatus140 includes the ability to pump in a forward direction (towards the patient) and in a reverse direction (away from the patient). Thus, for example, pump203 may direct fluid14 into patient P or draw a sample, such as a blood sample from patient P, fromcatheter11 tosampling assembly220, where it is further directed throughpassageway113 tosampling unit200 for analysis. Preferably, pump203 provides a forward flow rate at least sufficient to keep the patient vascular line open. In one embodiment, the forward flow rate is from 1 to 5 ml/hr. In some embodiments, the flow rate of fluid is about 0.05 ml/hr, 0.1 ml/hr, 0.2 ml/hr, 0.4 ml/hr, 0.6 ml/hr, 0.8 ml/hr, 1.0 ml/hr, and ranges encompassing such flow rates. In some embodiments, for example, the flow rate of fluid is less than about 1.0 ml/hr. In certain embodiments, the flow rate of fluid may be about 0.1 ml/hr or less. When operated in a reverse direction, fluid handling andanalysis apparatus140 includes the ability to draw a sample from the patient tosampling assembly220 and throughpassageway113. In one embodiment, pump203 provides a reverse flow to draw blood tosampling assembly220, preferably by a sufficient distance past the sampling assembly to ensure that the sampling assembly contains an undiluted blood sample. In one embodiment,passageway113 has an inside diameter of from 25 to 200 microns, or more preferably from 50 to 100 microns.Sampling unit200 extracts a small sample, for example from 10 to 100 microliters of blood, or more preferably approximately 40 microliters volume of blood, from samplingassembly220.

In one embodiment, pump203 is a directionally controllable pump that acts on a flexible portion ofpassageway111. Examples of a single, directionally controllable pump include, but are not limited to a reversible peristaltic pump or two unidirectional pumps that work in concert with valves to provide flow in two directions. In an alternative embodiment, pump203 includes a combination of pumps, including but not limited to displacement pumps, such as a syringe, and/or valve to provide bi-directional flow control throughpassageway111.

Controller

210 includes one or more processors for controlling the operation offluid handling system10 and for analyzing sample measurements from fluid handling andanalysis apparatus140.Controller210 also accepts input frombuttons143 and provides information ondisplay141. Optionally,controller210 is in bi-directional communication with a wired or wireless communication system, for example a hospital network for patient information. The one or moreprocessors comprising controller210 may include one or more processors that are located either within fluid handling andanalysis apparatus140 or that are networked to the unit.

The control offluid handling system10 bycontroller210 may include, but is not limited to, controlling fluid flow to infuse a patient and to sample, prepare, and analyze samples. The analysis of measurements obtained by fluid handling andanalysis apparatus140 of may include, but is not limited to, analyzing samples based on inputted patient specific information, from information obtained from a database regarding patient specific information, or from information provided over a network tocontroller210 used in the analysis of measurements byapparatus140.

Fluid handling system

10 provides for the infusion and sampling of a patient blood as follows. Withfluid handling system10 connected to bag15 havingfluid14 and to a patient P,controller210 infuses a patient by operatingpump203 to direct the fluid into the patient. Thus, for example, in one embodiment, the controller directs that samples be obtained from a patient by operatingpump203 to draw a sample. In one embodiment, pump203 draws a predetermined sample volume, sufficient to provide a sample tosampling assembly220. In another embodiment, pump203 draws a sample until a device withinsampling assembly220 indicates that the sample has reached thepatient connector110. As an example which is not meant to limit the scope of the present invention, one such indication is provided by a sensor that detects changes in the color of the sample. Another example is the use of a device that indicates changes in the material withinpassageway111 including, but not limited to, a decrease in the amount offluid14, a change with time in the amount of fluid, a measure of the amount of hemoglobin, or an indication of a change from fluid to blood in the passageway.

When the sample reachessampling assembly220,controller210 provides an operating signal to valves and/or pumps in sampling system100 (not shown) to draw the sample from samplingassembly220 intosampling unit200. After a sample is drawn towardssampling unit200,controller210 then provides signals to pump203 to resume infusing the patient. In one embodiment,controller210 provides signals to pump203 to resume infusing the patient while the sample is being drawn from samplingassembly220. In an alternative embodiment,controller210 provides signals to pump203 to stop infusing the patient while the sample is being drawn from samplingassembly220. In another alternative embodiment,controller210 provides signals to pump203 to slow the drawing of blood from the patient while the sample is being drawn from samplingassembly220.

In another alternative embodiment,controller210 monitors indications of obstructions in passageways or catheterized blood vessels during reverse pumping and moderates the pumping rate and/or direction ofpump203 accordingly. Thus, for example, obstructed flow from an obstructed or kinked passageway or of a collapsing or collapsed catheterized blood vessel that is being pumped will result in a lower pressure than an unobstructed flow. In one embodiment, obstructions are monitored using a pressure sensor insampling assembly220 or alongpassageways20. If the pressure begins to decrease during pumping, or reaches a value that is lower than a predetermined value thencontroller210 directspump203 to decrease the reverse pumping rate, stop pumping, or pump in the forward direction in an effort to reestablish unobstructed pumping.

FIG. 3 is a schematic showing details of asampling system300 which may be generally similar to the embodiments ofsampling system100 as illustrated inFIGS. 1 and 2, except as further detailed below.Sampling system300 includessampling assembly220 having, along passageway112:connector230 for connecting totube12, apressure sensor317, acolorimetric sensor311, afirst bubble sensor314a, afirst valve312, asecond valve313, and asecond bubble sensor314b.Passageway113 forms a “T” withpassageway111 at ajunction318 that is positioned between thefirst valve312 andsecond valve313, and includes agas injector manifold315 and athird valve316. Thelines114 comprise control and/or signal lines extending fromcolorimetric sensor311, first, second, and third valves (312,313,316), first and second bubble sensors (314a,314b),gas injector manifold315, andpressure sensor317.Sampling system300 also includessampling unit200 which has abubble sensor321, asample analysis device330, afirst valve323a, awaste receptacle325, asecond valve323b, and apump328.Passageway113 forms a “T” to form awaste line324 and apump line327.

It is preferred, though not necessary, that the sensors ofsampling system100 are adapted to accept a passageway through which a sample may flow and that sense through the walls of the passageway. As described subsequently, this arrangement allows for the sensors to be reusable and for the passageways to be disposable. It is also preferred, though not necessary, that the passageway is smooth and without abrupt dimensional changes which may damage blood or prevent smooth flow of blood. In addition, is also preferred that the passageways that deliver blood from the patient to the analyzer not contain gaps or size changes that permit fluid to stagnate and not be transported through the passageway.

In one embodiment, the respective passageways on which

valves

312,313,316, and323 are situated along passageways that are flexible tubes, and

valves

312,313,316, and323 are “pinch valves,” in which one or more movable surfaces compress the tube to restrict or stop flow therethrough. In one embodiment, the pinch valves include one or more moving surfaces that are actuated to move together and “pinch” a flexible passageway to stop flow therethrough. Examples of a pinch valve include, for example, Model PV256 Low Power Pinch Valve (Instech Laboratories, Inc., Plymouth Meeting, Pa.). Alternatively, one or more of

valves

312,313,316, and323 may be other valves for controlling the flow through their respective passageways.

Colorimetric sensor

311 accepts or forms a portion ofpassageway111 and provides an indication of the presence or absence of blood within the passageway. In one embodiment,calorimetric sensor311

permits controller

210 to differentiate betweenfluid14 and blood. Preferably,calorimetric sensor311 is adapted to receive a tube or other passageway for detecting blood. This permits, for example, a disposable tube to be placed into or through a reusable calorimetric sensor. In an alternative embodiment,calorimetric sensor311 is located adjacent tobubble sensor314b. Examples of a colorimetric sensor include, for example, an Optical Blood Leak/Blood vs. Saline Detector available from Introtek International (Edgewood, N.J.).

As described subsequently,sampling system300 injects a gas—referred to herein and without limitation as a “bubble”—intopassageway113.Sampling system300 includesgas injector manifold315 at or nearjunction318 to inject one or more bubbles, each separated by liquid, intopassageway113. The use of bubbles is useful in preventing longitudinal mixing of liquids as they flow through passageways both in the delivery of a sample for analysis with dilution and for cleaning passageways between samples. Thus, for example the fluid inpassageway113 includes, in one embodiment of the invention, two volumes of liquids, such as sample S or fluid14 separated by a bubble, or multiple volumes of liquid each separated by a bubble therebetween.

Bubble sensors

314a,314band321 each accept or form a portion of

passageway

112 or113 and provide an indication of the presence of air, or the change between the flow of a fluid and the flow of air, through the passageway. Examples of bubble sensors include, but are not limited to ultrasonic or optical sensors, that can detect the difference between small bubbles or foam from liquid in the passageway. Once such bubble detector is an MEC Series Air Bubble/Liquid Detection Sensor (Introtek International, Edgewood, N.Y.). Preferably,

bubble sensor

314a,314b, and321 are each adapted to receive a tube or other passageway for detecting bubbles. This permits, for example, a disposable tube to be placed through a reusable bubble sensor.

Pressure sensor

317 accepts or forms a portion ofpassageway111 and provides an indication or measurement of a fluid within the passageway. When all valves betweenpressure sensor317 andcatheter11 are open,pressure sensor317 provides an indication or measurement of the pressure within the patient's catheterized blood vessel. In one embodiment, the output ofpressure sensor317 is provided tocontroller210 to regulate the operation ofpump203. Thus, for example, a pressure measured bypressure sensor317 above a predetermined value is taken as indicative of a properly working system, and a pressure below the predetermined value is taken as indicative of excessive pumping due to, for example, a blocked passageway or blood vessel. Thus, for example, withpump203 operating to draw blood from patient P, if the pressure as measured bypressure sensor317 is within a range of normal blood pressures, it may be assumed that blood is being drawn from the patient and pumping continues. However, if the pressure as measured bypressure sensor317 falls below some level, thencontroller210 instructspump203 to slow or to be operated in a forward direction to reopen the blood vessel. One such pressure sensor is a Deltran IV part number DPT-412 (Utah Medical Products, Midvale, Utah).

Sample analysis device

330 receives a sample and performs an analysis. In several embodiments,device330 is configured to prepare of the sample for analysis. Thus, for example,device330 may include asample preparation unit332 and ananalyte detection system334, where the sample preparation unit is located between the patient and the analyte detection system. In general, sample preparation occurs between sampling and analysis. Thus, for example,sample preparation unit332 may take place removed from analyte detection, for example withinsampling assembly220, or may take place adjacent or withinanalyte detection system334.

As used herein, the term “analyte” is a broad term and is used in its ordinary sense and includes, without limitation, any chemical species the presence or concentration of which is sought in the material sample by an analyte detection system. For example, the analyte(s) include, but not are limited to, glucose, ethanol, insulin, water, carbon dioxide, blood oxygen, cholesterol, bilirubin, ketones, fatty acids, lipoproteins, albumin, urea, creatinine, white blood cells, red blood cells, hemoglobin, oxygenated hemoglobin, carboxyhemoglobin, organic molecules, inorganic molecules, pharmaceuticals, cytochrome, various proteins and chromophores, microcalcifications, electrolytes, sodium, potassium, chloride, bicarbonate, and hormones. As used herein, the term “material sample” (or, alternatively, “sample”) is a broad term and is used in its ordinary sense and includes, without limitation, any collection of material which is suitable for analysis. For example, a material sample may comprise whole blood, blood components (e.g., plasma or serum), interstitial fluid, intercellular fluid, saliva, urine, sweat and/or other organic or inorganic materials, or derivatives of any of these materials. In one embodiment, whole blood or blood components may be drawn from a patient's capillaries.101221 In one embodiment,sample preparation unit332 separates blood plasma from a whole blood sample or removes contaminants from a blood sample and thus comprises one or more devices including, but not limited to, a filter, membrane, centrifuge, or some combination thereof. In alternative embodiments,analyte detection system334 is adapted to analyze the sample directly andsample preparation unit332 is not required.

Generally,sampling assembly220 andsampling unit200 direct the fluid drawn from samplingassembly220 intopassageway113 intosample analysis device330.FIG. 4 is a schematic of an embodiment of asampling unit400 that permits some of the sample to bypasssample analysis device330.Sampling unit400 may be generally similar tosampling unit200, except as further detailed below.Sampling unit400 includesbubble sensor321,valve323,sample analysis device330,waste line324,waste receptacle325,valve326,pump line327, pump328, avalve322, and awaste line329.Waste line329 includesvalve322 and forms a “T” at pump line337 andwaste line329.

Valves

316,322,323, and326 permit a flow throughpassageway113 to be routed throughsample analysis device330, to be routed towaste receptacle325, or to be routed throughwaste line324 to wastereceptacle325.

FIG. 5 is a schematic of one embodiment of asampling system500 which may be generally similar to the embodiments of

sampling system

100 or300 as illustrated inFIGS. 1 through 4, except as further detailed below.Sampling system500 includes an embodiment of asampling unit510 and differs fromsampling system300 in part, in that liquid drawn frompassageway111 may be returned topassageway111 at ajunction502 betweenpump203 andconnector120.

With reference toFIG. 5,sampling unit510 includes areturn line503 that intersectspassageway111 on the opposite side ofpump203 frompassageway113, abubble sensor505 and apressure sensor507, both of which are controlled bycontroller210.Bubble sensor505 is generally similar to

bubble sensors

314a,314band321 andpressure sensor507 is generally similar topressure sensor317.Pressure sensor507 is useful in determining the correct operation ofsampling system500 by monitoring pressure inpassageway111. Thus, for example, the pressure inpassageway111 is related to the pressure atcatheter11 whenpressure sensor507 is in fluid communication with catheter11 (that is, when any intervening valve(s) are open). The output ofpressure sensor507 is used in a manner similar to that ofpressure sensor317 described previously in controlling pumps ofsampling system500.

Sampling unit

510 includes

valves

501,326a, and326bunder the control ofcontroller210.Valve501 provides additional liquid flow control betweensampling unit200 andsampling unit510.Pump328 is preferably a bi-directional pump that can draw fluid from and intopassageway113. Fluid may either be drawn from and returned topassageway501, or may be routed towaste receptacle325.

Valves

326aand326bare situated on either side ofpump328. Fluid can be drawn throughpassageway113 and intoreturn line503 by the coordinated control ofpump328 and

valves

326aand326b. Directing flow fromreturn line503 can be used toprime sampling system500 with fluid. Thus, for example, liquid may be pulled intosampling unit510 by operatingpump328 to pull liquid frompassageway113 whilevalve326ais open andvalve326bis closed. Liquid may then be pumped back intopassageway113 by operatingpump328 to push liquid intopassageway113 whilevalve326ais closed andvalve326bis open.

FIG. 6A is a schematic of an embodiment ofgas injector manifold315 which may be generally similar or included within the embodiments illustrated inFIGS. 1 through 5, except as further detailed below.Gas injector manifold315 is a device that injects one or more bubbles in a liquid withinpassageway113 by opening valves to the atmosphere and lowering the liquid pressure within the manifold to draw in air. As described subsequently,gas injector manifold315 facilitates the injection of air or other gas bubbles into a liquid withinpassageway113.Gas injector manifold315 has threegas injectors610 including afirst injector610a, asecond injector610b, and athird injector610c. Eachinjector610 includes a corresponding passageway611 that begins at one of several laterally spaced locations alongpassageway113 and extends through acorresponding valve613 and terminates at acorresponding end615 that is open to the atmosphere. In an alternative embodiment, a filter is placed inend615 to filter out dust or particles in the atmosphere. As described subsequently, eachinjector610 is capable of injecting a bubble into a liquid withinpassageway113 by opening thecorresponding valve613, closing a valve on one end ofpassageway113 and operating a pump on the opposite side of the passageway to lower the pressure and pull atmospheric air into the fluid. In one embodiment ofgas injector manifold315,passageways113 and611 are formed within a single piece of material (e.g., as bores formed in or through a plastic or metal housing (not shown)). In an alternative embodiment,gas injector manifold315 includes fewer than three injectors, for example one or two injectors, or includes more than three injectors. In another alternative embodiment,gas injector manifold315 includes a controllable high pressure source of gas for injection into a liquid inpassageway113. It is preferred thatvalves613 are located close topassageway113 to minimize trapping of fluid in passageways611.

Importantly, gas injected intopassageways20 should be prevented from reachingcatheter11. As a safety precaution, one embodiment prevents gas from flowing towardscatheter11 by the use ofbubble sensor314aas shown, for example, inFIG. 3. Ifbubble sensor314adetects gas withinpassageway111, then one of several alternative embodiments prevents unwanted gas flow. In one embodiment, flow in the vicinity ofsampling assembly220 is directed intoline113 or throughline113 intowaste receptacle325. With further reference toFIG. 3, upon the detection of gas bybubble sensor314a,

valves

316 and323aare opened,valve313 and the

valves

613a,613band613cofgas injector manifold315 are closed, and pump328 is turned on to direct flow away from the portion ofpassageway111 betweensampling assembly220 and patient P intopassageway113.Bubble sensor321 is monitored to provide an indication of whenpassageway113 clears out.Valve313 is then opened,valve312 is closed, and the remaining portion ofpassageway111 is then cleared. Alternatively, all flow is immediately halted in the direction ofcatheter11, for example by closing all valves and stopping all pumps. In an alternative embodiment ofsampling assembly220, a gas-permeable membrane is located withinpassageway113 or withingas injector manifold315 to remove unwanted gas fromfluid handling system10, e.g., by venting such gas through the membrane to the atmosphere or a waste receptacle.

FIG. 6B is a schematic of an embodiment ofgas injector manifold315′ which may be generally similar to, or included within, the embodiments illustrated inFIGS. 1 through 6A, except as further detailed below. Ingas injector manifold315′,air line615 andpassageway113 intersect atjunction318. Bubbles are injected by opening

valve

316 and613 while drawing fluid intopassageway113.Gas injector manifold315′ is thus more compact thatgas injector manifold315, resulting in a more controllable and reliable gas generator.

Section II—Fluid Handling Methods

One embodiment of a method of usingfluid handling system10, includingsampling assembly220 andsampling unit200 ofFIGS. 2, 3 and6A, is illustrated in Table 1 and in the schematic fluidic diagrams ofFIGS. 7A-7J. In general, the pumps and valves are controlled to infuse a patient, to extract a sample from the patient uppassageway111 topassageway113, and to direct the sample alongpassageway113 todevice330. In addition, the pumps and valves are controlled to inject bubbles into the fluid to isolate the fluid from the diluting effect of previous fluid and to clean the lines between sampling. The valves inFIGS. 7A-7J are labeled with suffices to indicate whether the valve is open or closed. Thus a valve “x,” for example, is shown as valve “x-o” if the valve is open and “x-c” if the valve is closed.

TABLE 1


Methods ofoperating system 10 as illustrated in FIGS. 7A-7J

Sample	(FIG. 7B)	R	Off	C	O	one or more	C	C	C
patient	Clear fluid from					are open

	passageways					O	O	O
	(FIG. 7C)	R	Off	O	O	C	C	C	C	C	C
	Draw sample until
	aftercolorimetric
	sensor
311 senses
	blood
	(FIG. 7D)	Off	On	O	C	C	C	C	O	C	O
	Inject sample into
	bubble manifold
	Alternative to	R	On	O	O	C	C	C	O	C	O

Inject bubbles					O	O	O
(FIG. 7F)	F	Off	C	O	C	C	C	O	O	C
Clear bubbles
from patient line
(FIG. 7G)	F	Off	O	O	C	C	C	C	C	C
Clear blood from
patient line
(FIG. 7H)	F	Off	C	O	C	C	C	O	O	C
Move bubbles out
of bubbler

	cleaning bubbles					O	O	O
	(FIG. 7J) Push	F	Off	C	O	C	C	C	O	O	C
	sample to analyzer
	untilbubble sensor
	321 detects bubble

F = Forward (fluid into patient),
R = Reverse (fluid from patient),
O = Open,
C = Closed

FIG. 7A illustrates one embodiment of a method of infusing a patient. In the step ofFIG. 7A, pump203 is operated forward (pumping towards the patient)pump328 is off, or stopped,

valves

313 and312 are open, and

valves

613a,613b,613c,316,323a, and323bare closed. With these operating conditions, fluid14 is provided to patient P. In a preferred embodiment, all of the other passageways at the time of the step ofFIG. 7A substantially containfluid14.

The next nine figures (FIGS. 7B-7J) illustrate steps in a method of sampling from a patient. The following steps are not meant to be inclusive of all of the steps of sampling from a patient, and it is understood that alternative embodiments may include more steps, fewer steps, or a different ordering of steps.FIG. 7B illustrates a first sampling step, where liquid is cleared from a portion of patient connection passageway and

sampling passageways

112 and113. In the step ofFIG. 7B, pump203 is operated in reverse (pumping away from the patient), pump328 is off,valve313 is open, one or more of

valves

613a,613b, and613care open, and

valves

312,316,323a, and326bare closed. With these operating conditions,air701 is drawn intosampling passageway113 and back intopatient connection passageway112 untilbubble sensor314bdetects the presence of the air.

FIG. 7C illustrates a second sampling step, where a sample is drawn from patient P intopatient connection passageway112. In the step ofFIG. 7C, pump203 is operated in reverse, pump328 is off,

valves

312 and313 are open, and

valves

316,613a,613b,613c,323a, and323bare closed. Under these operating conditions, a sample S is drawn intopassageway112, dividingair701 intoair701awithinsampling passageway113 andair701bwithin thepatient connection passageway112. Preferably this step proceeds until sample S extends just past the junction of

passageways

112 and113. In one embodiment, the step ofFIG. 7C proceeds until variations in the output ofcolorimetric sensor311 indicate the presence of a blood (for example by leveling off to a constant value), and then proceeds for an additional set amount of time to ensure the presence of a sufficient volume of sample S.

FIG. 7D illustrates a third sampling step, where a sample is drawn intosampling passageway113. In the step ofFIG. 7D, pump203 is off, or stopped, pump328 is on,

valves

312,316, and326bare open, and

valves

313,613a,613b,613cand323aare closed. Under these operating conditions, blood is drawn intopassageway113. Preferably, pump328 is operated to pull a sufficient amount of sample S intopassageway113. In one embodiment, pump328 draws a sample S having a volume from 30 to 50 microliters. In an alternative embodiment, the sample is drawn into both

passageways

112 and113.Pump203 is operated in reverse, pump328 is on,

valves

312,313,316, and323bare open, and

valves

613a,613b,613cand323aare closed to ensure fresh blood in sample S.

FIG. 7E illustrates a fourth sampling step, where air is injected into the sample. Bubbles which span the cross-sectional area ofsampling passageway113 are useful in preventing contamination of the sample as it is pumped alongpassageway113. In the step ofFIG. 7E, pump203 is off, or stopped, pump328 is on,

valves

316, and323bare open ,

valves

312,313 and323aare closed, and

valves

613a,613b,613care each opened and closed sequentially to draw in three separated bubbles. With these operating conditions, the pressure inpassageway113 falls below atmospheric pressure and air is drawn intopassageway113. Alternatively,

valves

613a,613b,613cmay be opened simultaneously for a short period of time, generating three spaced bubbles. As shown inFIG. 7E,

injectors

610a,610b, and610cinject

bubbles

704,703, and702, respectively, dividing sample S into a forward sample Si, a middle sample S2, and a rear sample S3.

FIG. 7F illustrates a fifth sampling step, where bubbles are cleared frompatient connection passageway112. In the step ofFIG. 7F, pump203 is operated in a forward direction, pump328 is off,

valves

313,316, and323aare open, and

valves

312,613a,613b,613c, and323bare closed. With these operating conditions, the previously injectedair701bis drawn out offirst passageway111 and intosecond passageway113. This step proceeds untilair701bis inpassageway113.

FIG. 7G illustrates a sixth sampling step, where blood inpassageway112 is returned to the patient. In the step ofFIG. 7G, pump203 is operated in a forward direction, pump328 is off,

valves

312 and313 are open, and

valves

316,323a,613a,613b,613cand323bare closed. With these operating conditions, the previously injected air remains inpassageway113 andpassageway111 is filled withfluid14.

FIGS. 7H and 7I illustrates a seventh and eighth sampling steps, where the sample is pushed part way intopassageway113 followed byfluid14 and more bubbles. In the step ofFIG. 7H, pump203 is operated in a forward direction, pump328 is off,

valves

313,316, and323aare open, and

valves

312,613a,613b,613c, and323bare closed. With these operating conditions, sample S is moved partway intopassageway113 with bubbles injected, either sequentially or simultaneously, intofluid14 from

injectors

610a,610b, and610c. In the step ofFIG. 7I, the pumps and valves are operated as in the step ofFIG. 7E, andfluid14 is divided into a forward solution C1, a middle solution C2, and a rear solution C3 separated by

bubbles

705,706, and707.

The last step shown inFIG. 7 isFIG. 7J, where middle sample S2 is pushed to sampleanalysis device330. In the step ofFIG. 7J, pump203 is operated in a forward direction, pump328 is off,

valves

313,316, and323aare open, and

valves

312,613a,613b,613c, and323bare closed. In this configuration, the sample is pushed intopassageway113. Whenbubble sensor321 detectsbubble702, pump203 continues pumping until sample S2 is taken intodevice sample analysis330. Additional pumping using the settings of the step ofFIG. 7J permits the sample S2 to be analyzed and for additional bubbles and solutions to be pushed intowaste receptacle325, cleansingpassageway113 prior to accepting a next sample.

Section III—Sampling System

FIG. 8 is a perspective front view of a third embodiment of asampling system800 of the present invention which may be generally similar to

sampling system

100,300 or500 and the embodiments illustrated inFIGS. 1 through 7, except as further detailed below. The fluid handling andanalysis apparatus140 ofsampling system800 includes the combination of aninstrument810 and asampling system cassette820.FIG. 8 illustratesinstrument810 andcassette820 partially removed from each other.Instrument810 includes controller210 (not shown),display141 andinput devices143, acassette interface811, and lines114.Cassette820 includespassageway111 which extends fromconnector120 toconnector230, and further includespassageway113, ajunction829 of

passageways

111 and113, aninstrument interface821, afront surface823, aninlet825 forpassageway111, and aninlet827 for

passageways

111 and113. In addition,sampling assembly220 is formed from a samplingassembly instrument portion813 having anopening815 for acceptingjunction829. The

interfaces

811 and821 engage the components ofinstrument810 andcassette820 to facilitate pumping fluid and analyzing samples from a patient, and samplingassembly instrument portion813 acceptsjunction829 in opening815 to provide for sampling frompassageway111.

FIGS. 9 and 10 are front views of asampling system cassette820 andinstrument810, respectively, of asampling system800.Cassette820 andinstrument810, when assembled, form various components ofFIGS. 9 and 10 that cooperate to form an apparatus consisting ofsampling unit510 ofFIG. 5,sampling assembly220 ofFIG. 3, andgas injection manifold315′ ofFIG. 6B.

More specifically, as shown inFIG. 9,cassette820 includespassageways20 including:passageway111 having

portions

111a,112a,112b,112c,112d,112e, and112f;passageway113 having

portions

113a,113b,113c,113d,113e, and113f;passageway615;waste receptacle325; disposable components ofsample analysis device330 including, for example, asample preparation unit332 adapted to allow only blood plasma to pass therethrough and asample chamber903 for placement withinanalyte detection system334 for measuring properties of the blood plasma; and adisplacement pump905 having apiston control907.

As shown inFIG. 10,instrument810 includes

bubble sensor units

1001a,1001b, and1001c, calorimetric sensor, which is ahemoglobin sensor unit1003, aperistaltic pump roller1005aand aroller support1005b, pincher pairs1007a,1007b,1007c,1007d,1007e,1007f,1007g, and1007h, anactuator1009, and apressure sensor unit1011. In addition,instrument810 includes portions ofsample analysis device330 which are adapted to measure a sample contained withinsample chamber903 when located near or within aprobe region1002 of an opticalanalyte detection system334.

Passageway portions ofcassette820 contact various components ofinstrument810 to formsampling system800. With reference toFIG. 5 for example, pump203 is formed fromportion111aplaced betweenperistaltic pump roller1005aandroller support1005bto move fluid throughpassageway111 when the roller is actuated;

valves

501,323,326a, and326bare formed with

pincher pairs

1007a,1007b,1007c, and1007d

surrounding portions

113a,113c,113d, and113e, respectively, to permit or block fluid flow therethrough.Pump328 is formed from actuator1009 positioned to movepiston control907. It is preferred that the interconnections between the components ofcassette820 andinstrument810 described in this paragraph are made with one motion. Thus for example the placement of

interfaces

811 and821 places the passageways against and/or between the sensors, actuators, and other components.

In addition to placement ofinterface811 againstinterface821, the assembly ofapparatus800 includes assemblingsampling assembly220. More specifically, an opening815aand815bare adapted to receive

passageways

111 and113, respectively, withjunction829 within samplingassembly instrument portion813. Thus, for example, with reference toFIG. 3,

valves

313 and312 are formed whenportions112band112care placed within pinchers of

pinch valves

1007eand1007f, respectively,

bubble sensors

314band314aare formed when

bubble sensor units

1001b, and1001care in sufficient contact withportions112aand112d, respectively, to determine the presence of bubbles therein; hemoglobin detector is formed whenhemoglobin sensor1003 is in sufficient contact withportion112e, andpressure sensor317 is formed whenportion112fis in sufficient contact withpressure sensor unit1011 to measure the pressure of a fluid therein. With reference toFIG. 6B,

valves

316 and613 are formed when

portions

113fand615 are placed within pinchers of

pinch valves

1007hand1007g,respectively.

In operation, the assembledmain instrument810 andcassette820 ofFIGS. 9-10 can function as follows. The system can be considered to begin in an idle state or infusion mode in which the roller pump1005 operates in a forward direction (with theimpeller1005aturning counterclockwise as shown inFIG. 10) to pump infusion fluid from thecontainer15 through thepassageway111 and thepassageway112, toward and into the patient P. In this infusion mode the pump1005 delivers infusion fluid to the patient at a suitable infusion rate as discussed elsewhere herein.

When it is time to conduct a measurement, air is first drawn into the system to clear liquid from a portion of the

passageways

112,113, in a manner similar to that shown inFIG. 7B. Here, the single air injector ofFIG. 9 (extending from thejunction829 to end615, opposite the passageway813) functions in place of the manifold shown inFIGS. 7A-7J. Next, to draw a sample, the pump1005 operates in a sample draw mode, by operating in a reverse direction and pulling a sample of bodily fluid (e.g. blood) from the patient into thepassageway112 through theconnector230. The sample is drawn up to thehemoglobin sensor1003, and is preferably drawn until the output of thesensor1003 reaches a desired plateau level indicating the presence of an undiluted blood sample in thepassageway112 adjacent thesensor1003.

From this point thepumps905,1005,

valves

1007e,1007f,1007g,1007h,

bubble sensors

1001b,1001cand/orhemoglobin sensor1003 can be operated to move a series of air bubbles and sample-fluid columns into thepassageway113, in a manner similar to that shown inFIGS. 7D-7F. Thepump905, in place of thepump328, is operable by moving thepiston control907 of thepump905 in the appropriate direction (to the left or right as shown inFIGS. 9-10) with theactuator1009.

Once a portion of the bodily fluid sample and any desired bubbles have moved into thepassageway113, thevalve1007hcan be closed, and the remainder of the initial drawn sample or volume of bodily fluid in thepassageway112 can be returned to the patient, by operating the pump1005 in the forward or infusion direction until thepassageway112 is again filled with infusion fluid.

With appropriate operation of the valves1007a-1007h, and the pump(s)905 and/or1005, at least a portion of the bodily fluid sample in the passageway113 (which is 10-100 microliters in volume, or 20, 30, 40, 50 or 60 microliters, in various embodiments) is moved through the sample preparation unit332 (in the depicted embodiment a filter or membrane; alternatively a centrifuge as discussed in greater detail below). Thus, only one or more components of the bodily fluid (e.g., only the plasma of a blood sample) passes through theunit332 or filter/membrane and enters the sample chamber orcell903. Alternatively, where theunit332 is omitted, the “whole” fluid moves into thesample chamber903 for analysis.

Once the component(s) or whole fluid is in thesample chamber903, the analysis is conducted to determine a level or concentration of one or more analytes, such as glucose, lactate, carbon dioxide, blood urea nitrogen, hemoglobin, and/or any other suitable analytes as discussed elsewhere herein. Where theanalyte detection system1700 is spectroscopic (e.g. thesystem1700 of FIGS.17 or44-46), a spectroscopic analysis of the component(s) or whole fluid is conducted.101521 After the analysis, the body fluid sample within thepassageway113 is moved into thewaste receptacle325. Preferably, thepump905 is operated via theactuator1009 to push the body fluid, behind a column of saline or infusion fluid obtained via thepassageway909, back through thesample chamber903 andsample preparation unit332, and into thereceptacle325. Thus, thechamber903 andunit332 are back-flushed and filled with saline or infusion fluid while the bodily fluid is delivered to the waste receptacle. Following this flush a second analysis can be made on the saline or infusion fluid now in thechamber903, to provide a “zero” or background reading. At this point, the fluid handling network ofFIG. 9, other than thewaste receptacle325, is empty of bodily fluid, and the system is ready to draw another bodily fluid sample for analysis.

In some embodiments of theapparatus140, a pair of pinch valve pinchers acts to switch flow between one of two branches of a passageway.FIGS. 13A and 13B are front view and sectional view, respectively, of a firstembodiment pinch valve1300 in an open configuration that can direct flow either one or both of two branches, or legs, of a passageway.Pinch valve1300 includes two separately controllable pinch valves acting on a “Y” shapedpassageway1310 to allow switch of fluid between various legs. In particular, the internal surface ofpassageway1310 forms afirst leg1311 having aflexible pinch region1312, asecond leg1313 having aflexible pinch region1314, and athird leg1315 that joins the first and second legs at anintersection1317. A first pair ofpinch valve pinchers1320 is positioned aboutpinch region1312 and a second pair ofpinch valve pinchers1330 is positioned aboutpinch region1314. Each pair of

pinch valve pinchers

1320 and1330 is positioned on opposite sides of their

corresponding pinch regions

1312,1314 and perpendicular topassageway1310, and are individually controllable bycontroller210 to open and close, that is allow or prohibit fluid communication across the pinch regions. Thus, for example, when pinch valve pinchers1320 (or1330) are brought sufficiently close, each part of pinch region1312 (or1314) touches another part of the pinch region and fluid may not flow across the pinch region.

As an example of the use ofpinch valve1300,FIG. 13B shows the first and second pair of

pinch valve pinchers

1320,1330 in an open configuration.FIG. 13C is a sectional view showing the pair ofpinch valve pinchers1320 brought together, thus closing off a portion offirst leg1311 from the second and

third legs

1313,1315. In part as a result of the distance betweenpinchers1320 andintersection1317 there is avolume1321 associated withfirst leg1311 that is not isolated (“dead space”). It is preferred that dead space is minimized so that fluids of different types can be switched between the various legs of the pinch valve. In one embodiment, the dead space is reduced by placing the placing the pinch valves close to the intersection of the legs. In another embodiment, the dead space is reduced by having passageway walls of varying thickness. Thus, for example, excess material between the pinch valves and the intersection will more effectively isolate a valved leg by displacing a portion ofvolume1321.

As an example of the use ofpinch valve1300 insampling system300,

pinchers

1320 and1330 are positioned to act as

valve

323 and326, respectively.

FIGS. 14A and 14B are various views of a secondembodiment pinch valve1400, whereFIG. 14A is a front view andFIG. 14B is a sectional view showing one valve in a closed position.Pinch valve1400 differs frompinch valve1300 in that the pairs of

pinch valve pinchers

1320 and1330 are replaced by

pinchers

1420 and1430, respectively, that are aligned withpassageway1310.

Alternative embodiment of pinch valves includes 2, 3, 4, or more passageway segments that meet at a common junction, with pinchers located at one or more passageways near the junction.

FIGS. 11 and 12 illustrate various embodiment ofconnector230 which may also form or be attached to disposable portions ofcassette820 as one embodiment of anarterial patient connector1100 and one embodiment avenous patient connector1200.

Connectors

1100 and1200 may be generally similar to the embodiment illustrated inFIGS. 1-10, except as further detailed below.

As shown inFIG. 11,arterial patient connector1100 includes astopcock1101, afirst tube portion1103 having a length X, ablood sampling port1105 to acquire blood samples for laboratory analysis, and fluid handling andanalysis apparatus140, asecond tube1107 having a length Y, and atube connector1109.Arterial patient connector1100 also includes apressure sensor unit1102 that is generally similar topressure sensor unit1011, on the opposite side ofsampling assembly220. Length X is preferably from to6 inches (0.15 meters) to 50 inches (1.27 meters) or approximately 48 inches (1.2 meters) in length. Length Y is preferably from 1 inch (25 millimeters) to 20 inches (0.5 meters), or approximately 12 inches (0.3 meters) in length. As shown inFIG. 12,venous patient connector1200 includes aclamp1201,injection port1105, andtube connector1109.

Section IV—Sample Analysis System

In several embodiments, analysis is performed on blood plasma. For such embodiments, the blood plasma must be separated from the whole blood obtained from the patient. In general, blood plasma may be obtained from whole blood at any point influid handling system10 between when the blood is drawn, for example atpatient connector110 or alongpassageway113, and when it is analyzed. For systems where measurements are preformed on whole blood, it may not be necessary to separate the blood at the point of or before the measurements is performed.

For illustrative purposes, this section describes several embodiments of separators and analyte detection systems which may form part ofsystem10. The separators discussed in the present specification can, in certain embodiments, comprise fluid component separators. As used herein, the term “fluid component separator” is a broad term and is used in its ordinary sense and includes, without limitation, any device that is operable to separate one or more components of a fluid to generate two or more unlike substances. For example, a fluid component separator can be operable to separate a sample of whole blood into plasma and non-plasma components, and/or to separate a solid-liquid mix (e.g. a solids-contaminated liquid) into solid and liquid components. A fluid component separator need not achieve complete separation between or among the generated unlike substances. Examples of fluid component separators include filters, membranes, centrifuges, electrolytic devices, or components of any of the foregoing. Fluid component separators can be “active” in that they are operable to separate a fluid more quickly than is possible through the action of gravity on a static, “standing” fluid. Section IV.A below discloses a filter which can be used as a blood separator in certain embodiments of the apparatus disclosed herein. Section IV.B below discloses an analyte detection system which can be used in certain embodiments of the apparatus disclosed herein. Section IV.C below discloses a sample element which can be used in certain embodiments of the apparatus disclosed herein. Section IV.D below discloses a centrifuge and sample chamber which can be used in certain embodiments of the apparatus disclosed herein.

Section IV.A—Blood Filter

Without limitation as to the scope of the present invention, one embodiment ofsample preparation unit332 is shown as ablood filter1500, as illustrated inFIGS. 15 and 16, whereFIG. 15 is a side view of one embodiment of a filter, andFIG. 16 is an exploded perspective view of the filter.

As shown in the embodiment ofFIG. 15,filter1500 that includes ahousing1501 with aninlet1503, afirst outlet1505 and asecond outlet1507.Housing1501 contains amembrane1509 that divides the internal volume ofhousing1501 into afirst volume1502 that includeinlet1503 andfirst outlet1505 and asecond volume1504.FIG. 16 shows one embodiment offilter1500 as including afirst plate1511 havinginlet1503 andoutlet1505, afirst spacer1513 having an opening formingfirst volume1502, asecond spacer1515 having an opening formingsecond volume1504, and asecond plate1517 havingoutlet1507.

Filter

1500 provides for a continuous filtering of blood plasma from whole blood. Thus, for example, when a flow of whole blood is provided atinlet1503 and a slight vacuum is applied to thesecond volume1504 side ofmembrane1509, the membrane filters blood cells and blood plasma passes throughsecond outlet1507. Preferably, there is transverse blood flow across the surface ofmembrane1509 to prevent blood cells from cloggingfilter1500. Accordingly, in one embodiment of theinlet1503 andfirst outlet1505 may be configured to provide the transverse flow acrossmembrane1509.

In one embodiment,membrane1509 is a thin and strong polymer film. For example, the membrane filter may be a 10 micron thick polyester or polycarbonate film. Preferably, the membrane filter has a smooth glass-like surface, and the holes are uniform, precisely sized, and clearly defined. The material of the film may be chemically inert and have low protein binding characteristics.

One way to manufacturemembrane1509 is with a Track Etching process. Preferably, the “raw” film is exposed to charged particles in a nuclear reactor, which leaves “tracks” in the film. The tracks may then be etched through the film, which results in holes that are precisely sized and uniformly cylindrical. For example, GE Osmonics, Inc. (4636 Somerton Rd. Trevose, Pa. 19053-6783) utilizes a similar process to manufacture a material that adequately serves as the membrane filter. The surface the membrane filter depicted above is a GE Osmonics Polycarbonate TE film.

As one example of the use offilter1500, the plasma from 3 cc of blood may be extracted using a polycarbonate track etch film (“PCTE”) as the membrane filter. The PCTE may have a pore size of 2 μm and an effective area of 170 millimeter². Preferably, the tubing connected to the supply, exhaust and plasma ports has an internal diameter of 1 millimeter. In one embodiment of a method employed with this configuration, 100 μl of plasma can be initially extracted from the blood. After saline is used to rinse the supply side of the cell, another 100 μl of clear plasma can be extracted. The rate of plasma extraction in this method and configuration can be about 15-25 μl/min.

Using a continuous flow mechanism to extract plasma may provide several benefits. In one preferred embodiment, the continuous flow mechanism is reusable with multiple samples, and there is negligible sample carryover to contaminate subsequent samples. One embodiment may also eliminate most situations in which plugging may occur. Additionally, a preferred configuration provides for a low internal volume.

Additional information on filters, methods of use thereof, and related technologies may be found in U.S. Patent Application Publication No. 2005/0038357, published on Feb. 17, 2005, titled SAMPLE ELEMENT WITH BARRIER MATERIAL; and U.S. patent application Ser. No. 11/122,794, filed on May 5, 2005, titled SAMPLE ELEMENT WITH SEPARATOR. The entire contents of the above noted publication and patent application are hereby incorporated by reference herein and made a part of this specification.

Section IV.B—Analyte Detection System

One embodiment ofanalyte detection system334, which is not meant to limit the scope of the present invention, is shown inFIG. 17 as an opticalanalyte detection system1700.Analyte detection system1700 is adapted to measure spectra of blood plasma. The blood plasma provided toanalyte detection system334 may be provided bysample preparation unit332, including but not limited to afilter1500.

Analyte detection system

1700 comprises anenergy source1720 disposed along a major axis X ofsystem1700. When activated, theenergy source1720 generates an energy beam E which advances from theenergy source1720 along the major axis X. In one embodiment, theenergy source1720 comprises an infrared source and the energy beam E comprises an infrared energy beam.

The energy beam E passes through anoptical filter1725 also situated on the major axis X, before reaching aprobe region1710. Proberegion1710 is portion ofapparatus322 in the path of an energized beam E that is adapted to accept a material sample S. In one embodiment, as shown inFIG. 17,probe region1710 is adapted to accept a sample element orcuvette1730, which supports or contains the material sample S. In one embodiment of the present invention,sample element1730 is a portion ofpassageway113, such as a tube or an optical cell. After passing through thesample element1730 and the sample S, the energy beam E reaches adetector1745.

As used herein, “sample element” is a broad term and is used in its ordinary sense and includes, without limitation, structures that have a sample chamber and at least one sample chamber wall, but more generally includes any of a number of structures that can hold, support or contain a material sample and that allow electromagnetic radiation to pass through a sample held, supported or contained thereby; e.g., a cuvette, test strip, etc.

In one embodiment of the present invention,sample element1730 forms a disposable portion ofcassette820, and the remaining portions ofsystem1700 form portions ofinstrument810, and proberegion1710 isprobe region1002.

With further reference toFIG. 17, thedetector1745 responds to radiation incident thereon by generating an electrical signal and passing the signal toprocessor210 for analysis. Based on the signal(s) passed to it by thedetector1745, the processor computes the concentration of the analyte(s) of interest in the sample S, and/or the absorbance/transmittance characteristics of the sample S at one or more wavelengths or wavelength bands employed to analyze the sample. Theprocessor210 computes the concentration(s), absorbance(s), transmittance(s), etc. by executing a data processing algorithm or program instructions residing withinmemory212 accessible by theprocessor210.

In the embodiment shown inFIG. 17, thefilter1725 may comprise a varying-passband filter, to facilitate changing, over time and/or during a measurement taken withapparatus322, the wavelength or wavelength band of the energy beam E that may pass thefilter1725 for use in analyzing the sample S. (In various other embodiments, thefilter1725 may be omitted altogether.) Some examples of a varying-passband filter usable withapparatus322 include, but are not limited to, a filter wheel (discussed in further detail below), an electronically tunable filter, such as those manufactured by Aegis Semiconductor (Woburn, Mass.), a custom filter using an “Active Thin Films platform,” a Fabry-Perot interferometer, such as those manufactured by Scientific Solutions, Inc. (North Chelmsford, Mass.), a custom liquid crystal Fabry-Perot (LCFP) Tunable Filter, or a tunable monochrometer, such as a HORIBA (Jobin Yvon, Inc. (Edison, N.J.) H1034 type with 7-10 μm grating, or a custom designed system.

In oneembodiment detection system1700,filter1725 comprises a varying-passband filter, to facilitate changing, over time and/or during a measurement taken with thedetection system1700, the wavelength or wavelength band of the energy beam E that may pass the filter25 for use in analyzing the sample S. When the energy beam E is filtered with a varying-passband filter, the absorption/transmittance characteristics of the sample S can be analyzed at a number of wavelengths or wavelength bands in a separate, sequential manner. As an example, assume that it is desired to analyze the sample S at N separate wavelengths (Wavelength1 through Wavelength N). The varying-passband filter is first operated or tuned to permit the energy beam E to pass atWavelength1, while substantially blocking the beam E at most or all other wavelengths to which thedetector1745 is sensitive (including Wavelengths2-N). The absorption/transmittance properties of the sample S are then measured atWavelength1, based on the beam E that passes through the sample S and reaches thedetector1745. The varying-passband filter is then operated or tuned to permit the energy beam E to pass atWavelength2, while substantially blocking other wavelengths as discussed above; the sample S is then analyzed atWavelength2 as was done atWavelength1. This process is repeated until all of the wavelengths of interest have been employed to analyze the sample S. The collected absorption/transmittance data can then be analyzed by theprocessor210 to determine the concentration of the analyte(s) of interest in the material sample S. The measured spectra of sample S is referred to herein in general as C_s(λ_i), that is, a wavelength dependent spectra in which C_sis, for example, a transmittance, an absorbance, an optical density, or some other measure of the optical properties of sample S having values at or about a number of wavelengths λ_i, where i ranges over the number of measurements taken. The measurement C_s(λ_i) is a linear array of measurements that is alternatively written as Cs_i.

The spectral region ofsystem1700 depends on the analysis technique and the analyte and mixtures of interest. For example, one useful spectral region for the measurement of glucose in blood using absorption spectroscopy is the mid-IR (for example, about 4 microns to about 11 microns). In oneembodiment system1700,energy source1720 produces a beam E having an output in the range of about 4 microns to about 11 microns. Although water is the main contributor to the total absorption across this spectral region, the peaks and other structures present in the blood spectrum from about 6.8 microns to 10.5 microns are due to the absorption spectra of other blood components. The 4 to 11 micron region has been found advantageous because glucose has a strong absorption peak structure from about 8.5 to 10 microns, whereas most other blood constituents have a low and flat absorption spectrum in the 8.5 to 10 micron range. The main exceptions are water and hemoglobin, both of which are interferents in this region.

The amount of spectral detail provided bysystem1700 depends on the analysis technique and the analyte and mixture of interest. For example, the measurement of glucose in blood by mid-IR absorption spectroscopy is accomplished with from 11 to 25 filters within a spectral region. In oneembodiment system1700,energy source1720 produces a beam E having an output in the range of about 4 microns to about 11 microns, andfilter1725 include a number of narrow band filters within this range, each allowing only energy of a certain wavelength or wavelength band to pass therethrough. Thus, for example, oneembodiment filter1725 includes a filter wheel having 11 filters with a nominal wavelength approximately equal to one of the following: 3 μm, 4.06 μm, 4.6 μm, 4.9 μm, 5.25 μm, 6.12 μm, 6.47 μm, 7.98 μm, 8.35 μm, 9.65 μm, and 12.2 μm.

In one embodiment, individual infrared filters of the filter wheel are multi-cavity, narrow band dielectric stacks on germanium or sapphire substrates, manufactured by either OCLI (JDS Uniphase, San Jose, Calif.) or Spectrogon US, Inc. (Parsippany, N.J.). Thus, for example, each filter may nominally be 1 millimeter thick and 10 millimeter square. The peak transmission of the filter stack is typically between 50% and 70%, and the bandwidths are typically between 150 nm and 350 nm with center wavelengths between 4 and 10 μm. Alternatively, a second blocking IR filter is also provided in front of the individual filters. The temperature sensitivity is preferably <0.01% per degree C. to assist in maintaining nearly constant measurements over environmental conditions.

In one embodiment, thedetection system1700 computes an analyte concentration reading by first measuring the electromagnetic radiation detected by thedetector1745 at each center wavelength, or wavelength band, without thesample element1730 present on the major axis X (this is known as an “air” reading). Second, thesystem1700 measures the electromagnetic radiation detected by thedetector1745 for each center wavelength, or wavelength band, with the material sample S present in thesample element1730, and the sample element and sample S in position on the major axis X (i.e., a “wet” reading). Finally, theprocessor210 computes the concentration(s), absorbance(s) and/or transmittances relating to the sample S based on these compiled readings.

In one embodiment, the plurality of air and wet readings are used to generate a pathlength corrected spectrum as follows. First, the measurements are normalized to give the transmission of the sample at each wavelength. Using both a signal and reference measurement at each wavelength, and letting S_irepresent the signal ofdetector1745 at wavelength i and R_irepresent the signal of the detector at wavelength i, the transmittance, T_iat wavelength i may computed as T_i=S_i(wet)/S_i(air). Optionally, the spectra may be calculated as the optical density, OD_i, as −Log(T_i). Next, the transmission over the wavelength range of approximately 4.5 μm to approximately 5.5 μm is analyzed to determine the pathlength. Specifically, since water is the primary absorbing species of blood over this wavelength region, and since the optical density is the product of the optical pathlength and the known absorption coefficient of water (OD=L σ, where L is the optical pathlength and σ is the absorption coefficient), any one of a number of standard curve fitting procedures may be used to determine the optical pathlength, L from the measured OD. The pathlength may then be used to determine the absorption coefficient of the sample at each wavelength. Alternatively, the optical pathlength may be used in further calculations to convert absorption coefficients to optical density.

Blood samples may be prepared and analyzed bysystem1700 in a variety of configurations. In one embodiment, sample S is obtained by drawing blood, either using a syringe or as part of a blood flow system, and transferring the blood intosample chamber903. In another embodiment, sample S is drawn into a sample container that is asample chamber903 adapted for insertion intosystem1700.

FIG. 44 depicts another embodiment of theanalyte detection system1700, which may be generally similar to the embodiment illustrated inFIG. 17, except as further detailed below. Where possible, similar elements are identified with identical reference numerals in the depiction of the embodiments ofFIGS. 17 and 44.

Thedetection system1700 shown inFIG. 44 includes acollimator30 located betweensource1720 andfilter1725 and a beam sampling optics90 between the filter andsample element1730.Filter1725 includes aprimary filter40 and a filter wheel assembly4420 which can insert one of a plurality of optical filters into energybeam E. System1700 also includes asample detector150 may be generally similar tosample detector1725, except as further detailed below.

As shown inFIG. 44, energy beam E fromsource1720 passes throughcollimator30 through which the before reaching a primaryoptical filter40 which is disposed downstream of awide end36 of thecollimator30.Filter1725 is aligned with thesource1720 andcollimator30 on the major axis X and is preferably configured to operate as a broadband filter, allowing only a selected band, e.g. between about 2.5 μm and about 12.5 μm, of wavelengths emitted by thesource1720 to pass therethrough, as discussed below. In one embodiment, theenergy source1720 comprises an infrared source and the energy beam E comprises an infrared energy beam. Onesuitable energy source1720 is the TOMA TECH™IR-50 available from HawkEye Technologies of Milford, Conn.

With further reference toFIG. 44,primary filter40 is mounted in a mask44 so that only those portions of the energy beam E which are incident on theprimary filter40 can pass the plane of the mask-primary filter assembly. Theprimary filter40 is generally centered on and oriented orthogonal to the major axis X and is preferably circular (in a plane orthogonal to the major axis X) with a diameter of about8 mm. Of course, any other suitable size or shape may be employed. As discussed above, theprimary filter40 preferably operates as a broadband filter. In the illustrated embodiment, theprimary filter40 preferably allows only energy wavelengths between about 4 μm and about 11 μm to pass therethrough. However, other ranges of wavelengths can be selected. Theprimary filter40 advantageously reduces the filtering burden of secondary optical filter(s)60 disposed downstream of theprimary filter40 and improves the rejection of electromagnetic radiation having a wavelength outside of the desired wavelength band. Additionally, theprimary filter40 can help minimize the heating of the secondary filter(s)60 by the energy beam E passing therethrough. Despite these advantages, theprimary filter40 and/or mask44 may be omitted in alternative embodiments of thesystem1700 shown inFIG. 44.

Theprimary filter40 is preferably configured to substantially maintain its operating characteristics (center wavelength, passband width) where some or all of the energy beam E deviates from normal incidence by a cone angle of up to about twelve degrees relative to the major axis X. In further embodiments, this cone angle may be up to about 15 to 35 degrees, or from about 15 degrees or 20 degrees. Theprimary filter40 may be said to “substantially maintain” its operating characteristics where any changes therein are insufficient to affect the performance or operation of thedetection system1700 in a manner that would raise significant concerns for the user(s) of the system in the context in which thesystem1700 is employed.

In the embodiment illustrated inFIG. 44, filter wheel assembly4420 includes anoptical filter wheel50 and astepper motor70 connected to the filter wheel and configured to generate a force to rotate thefilter wheel50. Additionally, aposition sensor80 is disposed over a portion of the circumference of thefilter wheel50 and may be configured to detect the angular position of thefilter wheel50 and to generate a corresponding filter wheel position signal, thereby indicating which filter is in position on the major axis X. Alternatively, thestepper motor70 may be configured to track or count its own rotation(s), thereby tracking the angular position of the filter wheel, and pass a corresponding position signal to theprocessor210. Two suitable position sensors are models EE-SPX302-W2A and EE-SPX402-W2A available from Omron Corporation of Kyoto, Japan.

Optical filter wheel

50 is employed as a varying-passband filter, to selectively position the secondary filter(s)60 on the major axis X and/or in the energy beam E. Thefilter wheel50 can therefore selectively tune the wavelength(s) of the energy beam E downstream of thewheel50. These wavelength(s) vary according to the characteristics of the secondary filter(s)60 mounted in thefilter wheel50. Thefilter wheel50 positions the secondary filter(s)60 in the energy beam E in a “one-at-a-time” fashion to sequentially vary, as discussed above, the wavelengths or wavelength bands employed to analyze the material sample S. An alternative to filterwheel50 is a linear filter translated by a motor (not shown). The linear filter may be, for example, a linear array of separate filters or a single filter with filter properties that change in a linear dimension.

In alternative arrangements, the singleprimary filter40 depicted inFIG. 44 may be replaced or supplemented with additional primary filters mounted on thefilter wheel50 upstream of each of the secondary filters60. As yet another alternative, theprimary filter40 could be implemented as a primary filter wheel (not shown) to position different primary filters on the major axis X at different times during operation of thedetection system1700, or as a tunable filter.

Thefilter wheel50, in the embodiment depicted inFIG. 45, can comprise awheel body52 and a plurality ofsecondary filters60 disposed on thebody52, the center of each filter being equidistant from a rotational center RC of the wheel body. Thefilter wheel50 is configured to rotate about an axis which is (i) parallel to the major axis X and (ii) spaced from the major axis X by an orthogonal distance approximately equal to the distance between the rotational center RC and any of the center(s) of the secondary filter(s)60. Under this arrangement, rotation of thewheel body52 advances each of the filters sequentially through the major axis X, so as to act upon the energy beam E. However, depending on the analyte(s) of interest or desired measurement speed, only a subset of the filters on thewheel50 may be employed in a given measurement run. Ahome position notch54 may be provided to indicate the home position of thewheel50 to aposition sensor80.

In one embodiment, thewheel body52 can be formed from molded plastic, with each of thesecondary filters60 having, for example a thickness of 1 mm and a 10 mm×10 mm or a 5 mm×5 mm square configuration. Each of thefilters60, in this embodiment of the wheel body, is axially aligned with a circular aperture of 4 mm diameter, and the aperture centers define a circle of about 1.70 inches diameter, which circle is concentric with thewheel body52. Thebody52 itself is circular, with an outside diameter of 2.00 inches.

Each of the secondary filter(s)60 is preferably configured to operate as a narrow band filter, allowing only a selected energy wavelength or wavelength band (i.e., a filtered energy beam (Ef) to pass therethrough. As thefilter wheel50 rotates about its rotational center RC, each of the secondary filter(s)60 is, in turn, disposed along the major axis X for a selected dwell time corresponding to each of the secondary filter(s)60.

The “dwell time” for a givensecondary filter60 is the time interval, in an individual measurement run of thesystem1700, during which both of the following conditions are true: (i) the filter is disposed on the major axis X; and (ii) thesource1720 is energized. The dwell time for a given filter may be greater than or equal to the time during which the filter is disposed on the major axis X during an individual measurement run. In one embodiment of theanalyte detection system1700, the dwell time corresponding to each of the secondary filter(s)60 is less than about 1 second. However, the secondary filter(s)60 can have other dwell times, and each of the filter(s)60 may have a different dwell time during a given measurement run.

From thesecondary filter60, the filtered energy beam (Ef) passes through a beam sampling optics90, which includes abeam splitter4400 disposed along the major axis X and having a face4400adisposed at an includedangle0 relative to the major axis X. Thesplitter4400 preferably separates the filtered energy beam (Ef) into a sample beam (Es) and a reference beam (Er).

With further reference toFIG. 44, the sample beam (Es) passes next through afirst lens4410 aligned with thesplitter4400 along the major axis X. Thefirst lens4410 is configured to focus the sample beam (Es) generally along the axis X onto the material sample S. The sample S is preferably disposed in asample element1730 between afirst window122 and asecond window124 of thesample element1730. Thesample element1730 is further preferably removably disposed in aholder4430, and theholder4430 has afirst opening132 and asecond opening134 configured for alignment with thefirst window122 andsecond window124, respectively. Alternatively, thesample element1730 and sample S may be disposed on the major axis X without use of theholder4430.

At least a fraction of the sample beam (Es) is transmitted through the sample S and continues onto asecond lens4440 disposed along the major axis X. Thesecond lens4440 is configured to focus the sample beam (Es) onto asample detector150, thus increasing the flux density of the sample beam (Es) incident upon thesample detector150. Thesample detector150 is configured to generate a signal corresponding to the detected sample beam (Es) and to pass the signal to aprocessor210, as discussed in more detail below.

Beam sampling optics90 further includes athird lens160 and areference detector170. The reference beam (Er) is directed by beam sampling optics90 from thebeam splitter4400 to athird lens160 disposed along a minor axis Y generally orthogonal to the major axis X. Thethird lens160 is configured to focus the reference beam (Er) ontoreference detector170, thus increasing the flux density of the reference beam (Er) incident upon thereference detector170. In one embodiment, the

lenses

4410,4440,160 may be formed from a material which is highly transmissive of infrared radiation, for example germanium or silicon. In addition, any of the

lenses

4410,4440 and160 may be implemented as a system of lenses, depending on the desired optical performance. Thereference detector170 is also configured to generate a signal corresponding to the detected reference beam (Er) and to pass the signal to theprocessor210, as discussed in more detail below. Except as noted below, the sample and

reference detectors

150,170 may be generally similar to thedetector1745 illustrated inFIG. 17. Based on signals received from the sample and

reference detectors

150,170, theprocessor210 computes the concentration(s), absorbance(s), transmittance(s), etc. relating to the sample S by executing a data processing algorithm or program instructions residing within thememory212 accessible by theprocessor210.

In further variations of thedetection system1700 depicted inFIG. 44, beam sampling optics90, including thebeam splitter4400,reference detector170 and other structures on the minor axis Y may be omitted, especially where the output intensity of thesource1720 is sufficiently stable to obviate any need to reference the source intensity in operation of thedetection system1700. Thus, for example, sufficient signals may be generated by

detectors

170 and150 with one or more of

lenses

4410,4440,160 omitted. Furthermore, in any of the embodiments of theanalyte detection system1700 disclosed herein, theprocessor210 and/ormemory212 may reside partially or wholly in a standard personal computer (“PC”) coupled to thedetection system1700.

FIG. 46 depicts a partial cross-sectional view of another embodiment of ananalyte detection system1700, which may be generally similar to any of the embodiments illustrated inFIGS. 17, 44, and45, except as further detailed below. Where possible, similar elements are identified with identical reference numerals in the depiction of the embodiments ofFIGS. 17, 44, and45.

Theenergy source1720 of the embodiment ofFIG. 46 preferably comprises anemitter area22 which is substantially centered on the major axis X. In one embodiment, theemitter area22 may be square in shape. However theemitter area22 can have other suitable shapes, such as rectangular, circular, elliptical, etc. Onesuitable emitter area22 is a square of about 1.5 mm on a side; of course, any other suitable shape or dimensions may be employed.

Theenergy source1720 is preferably configured to selectably operate at a modulation frequency between about 1 Hz and 30 Hz and have a peak operating temperature of between about 1070 degrees Kelvin and 1170 degrees Kelvin. Additionally, thesource1720 preferably operates with a modulation depth greater than about 80% at all modulation frequencies. Theenergy source1720 preferably emits electromagnetic radiation in any of a number of spectral ranges, e.g., within infrared wavelengths; in the mid-infrared wavelengths; above about 0.8 μm; between about 5.0 μm and about 20.0 μm; and/or between about 5.25 μm and about 12.0 μm. However, in other embodiments, thedetection system1700 may employ anenergy source1720 which is unmodulated and/or which emits in wavelengths found anywhere from the visible spectrum through the microwave spectrum, for example anywhere from about 0.4 μm to greater than about 100 μm. In still other embodiments, theenergy source1720 can emit electromagnetic radiation in wavelengths between about 3.5 μm and about 14 μm, or between about 0.8 μm and about 2.5 μm, or between about 2.5 μm and 20 μm, or between about 20 μm and about 100 μm, or between about 6.85 μm and about 10.10 μm. In yet other embodiments, theenergy source1720 can emit electromagnetic radiation within the radio frequency (RF) range or the terahertz range. All of the above-recited operating characteristics are merely exemplary, and thesource1720 may have any operating characteristics suitable for use with theanalyte detection system1700.

A power supply (not shown) for theenergy source1720 is preferably configured to selectably operate with a duty cycle of between about 30% and about 70%. Additionally, the power supply is preferably configured to selectably operate at a modulation frequency of about 10 Hz, or between about 1 Hz and about 30 Hz. The operation of the power supply can be in the form of a square wave, a sine wave, or any other waveform defined by a user.

With further reference toFIG. 46, thecollimator30 comprises atube30awith one or more highly-reflectiveinner surfaces32 which diverge from a relatively narrowupstream end34 to a relatively widedownstream end36 as they extend downstream, away from theenergy source1720. Thenarrow end34 defines anupstream aperture34awhich is situated adjacent theemitter area22 and permits radiation generated by the emitter area to propagate downstream into the collimator. Thewide end36 defines adownstream aperture36a. Like theemitter area22, each of the inner surface(s)32,upstream aperture34aanddownstream aperture36ais preferably substantially centered on the major axis X.

As illustrated inFIG. 46, the inner surface(s)32 of the collimator may have a generally curved shape, such as a parabolic, hyperbolic, elliptical or spherical shape. Onesuitable collimator30 is a compound parabolic concentrator (CPC). In one embodiment, thecollimator30 can be up to about20 mm in length. In another embodiment, thecollimator30 can be up to about30 mm in length. However, thecollimator30 can have any length, and the inner surface(s)32 may have any shape, suitable for use with theanalyte detection system1700.

Theinner surfaces32 of thecollimator30 cause the rays making up the energy beam E to straighten (i.e., propagate at angles increasingly parallel to the major axis X) as the beam E advances downstream, so that the energy beam E becomes increasingly or substantially cylindrical and oriented substantially parallel to the major axis X. Accordingly, theinner surfaces32 are highly reflective and minimally absorptive in the wavelengths of interest, such as infrared wavelengths.

Thetube30aitself may be fabricated from a rigid material such as aluminum, steel, or any other suitable material, as long as theinner surfaces32 are coated or otherwise treated to be highly reflective in the wavelengths of interest. For example, a polished gold coating may be employed. Preferably, the inner surface(s)32 of thecollimator30 define a circular cross-section when viewed orthogonal to the major axis X; however, other cross-sectional shapes, such as a square or other polygonal shapes, parabolic or elliptical shapes may be employed in alternative embodiments.

As noted above, thefilter wheel50 shown inFIG. 46 comprises a plurality ofsecondary filters60 which preferably operate as narrow band filters, each filter allowing only energy of a certain wavelength or wavelength band to pass therethrough. In one configuration suitable for detection of glucose in a sample S, thefilter wheel50 comprises twenty or twenty-twosecondary filters60, each of which is configured to allow a filtered energy beam (Ef) to travel therethrough with a nominal wavelength approximately equal to one of the following: 3 μm, 4.06 μm, 4.6 μm, 4.9 μm, 5.25 μm, 6.12 μm, 6.47 μm, 7.98 μm, 8.35 μm, 9.65 μm, and 12.2 μm. (Moreover, this set of wavelengths may be employed with or in any of the embodiments of theanalyte detection system1700 disclosed herein.) Each secondary filter's60 center wavelength is preferably equal to the desired nominal wavelength plus or minus about 2%. Additionally, thesecondary filters60 are preferably configured to have a bandwidth of about 0.2 μm, or alternatively equal to the nominal wavelength plus or minus about 2%-10%.

In another embodiment, thefilter wheel50 comprises twentysecondary filters60, each of which is configured to allow a filtered energy beam (Ef) to travel therethrough with a nominal center wavelengths of: 4.275 μm, 4.5 μm, 4.7 μm, 5.0 μm, 5.3 μm, 6.056 μm, 7.15 μm, 7.3 μm, 7.55 μm, 7.67 μm, 8.06 μm, 8.482 m, 8.56 μm, 8.87 μm, 9.15 μm, 9.27 μm, 9.48 μm, 9.68 μm, 9.82 μm, and 10.06 μm. (This set of wavelengths may also be employed with or in any of the embodiments of theanalyte detection system1700 disclosed herein.) In still another embodiment, thesecondary filters60 may conform to any one or combination of the following specifications: center wavelength tolerance of ±0.01 μm; half-power bandwidth tolerance of ±0.01 μm; peak transmission greater than or equal to 75%; cut-on/cut-off slope less than 2%; center-wavelength temperature coefficient less than 0.01% per degree Celsius; out of band attenuation greater thanOD 5 from 3 μm to 12 μm; flatness less than 1.0 waves at 0.6328 μm; surface quality of E-E per Mil-F-48616; and overall thickness of about 1 mm.

In still another embodiment, the secondary filters mentioned above may conform to any one or combination of the following half-power bandwidth (“HPBW”) specifications:



	Center Wavelength	HPBW
	(μm)	(μm)

	4.275	0.05
	4.5	0.18
	4.7	0.13
	5.0	0.1
	5.3	0.13
	6.056	0.135
	7.15	0.19
	7.3	0.19
	7.55	0.18
	7.67	0.197
	8.06	0.3
	8.4	0.2
	8.56	0.18
	8.87	0.2
	9.15	0.15
	9.27	0.14
	9.48	0.23
	9.68	0.3
	9.82	0.34
	10.06	0.2

In still further embodiments, the secondary filters may have a center wavelength tolerance of ±0.5% and a half-power bandwidth tolerance of ±0.02 μm.

Of course, the number of secondary filters employed, and the center wavelengths and other characteristics thereof, may vary in further embodiments of thesystem1700, whether such further embodiments are employed to detect glucose, or other analytes instead of or in addition to glucose. For example, in another embodiment, thefilter wheel50 can have fewer than fiftysecondary filters60. In still another embodiment, thefilter wheel50 can have fewer than twentysecondary filters60. In yet another embodiment, thefilter wheel50 can have fewer than tensecondary filters60.

In one embodiment, thesecondary filters60 each measure about 10 mm long by 10 mm wide in a plane orthogonal to the major axis X, with a thickness of about 1 mm. However, thesecondary filters60 can have any other (e.g., smaller) dimensions suitable for operation of theanalyte detection system1700. Additionally, thesecondary filters60 are preferably configured to operate at a temperature of between about 5° C. and about 35° C. and to allow transmission of more than about 75% of the energy beam E therethrough in the wavelength(s) which the filter is configured to pass.

According to the embodiment illustrated inFIG. 46, theprimary filter40 operates as a broadband filter and thesecondary filters60 disposed on thefilter wheel50 operate as narrow band filters. However, one of ordinary skill in the art will realize that other structures can be used to filter energy wavelengths according to the embodiments described herein. For example, theprimary filter40 may be omitted and/or an electronically tunable filter or Fabry-Perot interferometer (not shown) can be used in place of thefilter wheel50 andsecondary filters60. Such a tunable filter or interferometer can be configured to permit, in a sequential, “one-at-a-time” fashion, each of a set of wavelengths or wavelength bands of electromagnetic radiation to pass therethrough for use in analyzing the material sample S.

Areflector tube98 is preferably positioned to receive the filtered energy beam (Ef) as it advances from the secondary filter(s)60. Thereflector tube98 is preferably secured with respect to the secondary filter(s)60 to substantially prevent introduction of stray electromagnetic radiation, such as stray light, into thereflector tube98 from outside of thedetection system1700. The inner surfaces of thereflector tube98 are highly reflective in the relevant wavelengths and preferably have a cylindrical shape with a generally circular cross-section orthogonal to the major and/or minor axis X, Y. However, the inner surface of thetube98 can have a cross-section of any suitable shape, such as oval, square, rectangular, etc. Like thecollimator30, thereflector tube98 may be formed from a rigid material such as aluminum, steel, etc., as long as the inner surfaces are coated or otherwise treated to be highly reflective in the wavelengths of interest. For example, a polished gold coating may be employed.

According to the embodiment illustrated inFIG. 46, thereflector tube98 preferably comprises a major section98aand a minor section98b. As depicted, thereflector tube98 can be T-shaped with the major section98ahaving a greater length than the minor section98b. In another example, the major section98aand the minor section98bcan have the same length. The major section98aextends between afirst end98cand asecond end98dalong the major axis X. The minor section98bextends between the major section98aand athird end98ealong the minor axis Y.

The major section98aconducts the filtered energy beam (Ef) from thefirst end98cto thebeam splitter4400, which is housed in the major section98aat the intersection of the major and minor axes X, Y. The major section98aalso conducts the sample beam (Es) from thebeam splitter4400, through thefirst lens4410 and to thesecond end98d. From thesecond end98dthe sample beam (Es) proceeds through thesample element1730,holder4430 andsecond lens4440, and to thesample detector150. Similarly, the minor section98bconducts the reference beam (Er) through beam sampling optics90 from thebeam splitter4400, through thethird lens160 and to thethird end98e. From thethird end98ethe reference beam (Er) proceeds to thereference detector170.

The sample beam (Es) preferably comprises from about 75% to about 85% of the energy of the filtered energy beam (Ef). More preferably, the sample beam (Es) comprises about 80% of the energy of the filtered energy beam (Es). The reference beam (Er) preferably comprises from about 10% and about 50% of the energy of the filtered energy beam (Es). More preferably, the reference beam (Er) comprises about 20% of the energy of the filtered energy beam (Ef). Of course, the sample and reference beams may take on any suitable proportions of the energy beam E.

Thereflector tube98 also houses thefirst lens4410 and thethird lens160. As illustrated inFIG. 46, thereflector tube98 houses thefirst lens4410 between thebeam splitter4400 and thesecond end98d. Thefirst lens4410 is preferably disposed so that aplane4612 of thelens4410 is generally orthogonal to the major axis X. Similarly, thetube98 houses thethird lens160 between thebeam splitter4400 and thethird end98e. Thethird lens160 is preferably disposed so that aplane162 of thethird lens160 is generally orthogonal to the minor axis Y. Thefirst lens4410 and thethird lens160 each has a focal length configured to substantially focus the sample beam (Es) and reference beam (Er), respectively, as the beams (Es, Er) pass through the

lenses

4410,160. In particular, thefirst lens4410 is configured, and disposed relative to theholder4430, to focus the sample beam (Es) so that substantially the entire sample beam (Es) passes through the material sample S, residing in thesample element1730. Likewise, thethird lens160 is configured to focus the reference beam (Er) so that substantially the entire reference beam (Er) impinges onto thereference detector170.

Thesample element1730 is retained within theholder4430, which is preferably oriented along a plane generally orthogonal to the major axis X. Theholder4430 is configured to be slidably displaced between a loading position and a measurement position within theanalyte detection system1700. In the measurement position, theholder4430 contacts a stop edge136 which is located to orient thesample element1730 and the sample S contained therein on the major axis X.

The structural details of theholder4430 depicted inFIG. 46 are unimportant, so long as the holder positions thesample element1730 and sample S on and substantially orthogonal to the major axis X, while permitting the energy beam E to pass through the sample element and sample. As with the embodiment depicted inFIG. 44, theholder4430 may be omitted and thesample element1730 positioned alone in the depicted location on the major axis X. However, theholder4430 is useful where the sample element1730 (discussed in further detail below) is constructed from a highly brittle or fragile material, such as barium fluoride, or is manufactured to be extremely thin.

As with the embodiment depicted inFIG. 44, the sample and

reference detectors

150,170 shown inFIG. 46 respond to radiation incident thereon by generating signals and passing them to theprocessor210. Based these signals received from the sample and

reference detectors

150,170, theprocessor210 computes the concentration(s), absorbance(s), transmittance(s), etc. relating to the sample S by executing a data processing algorithm or program instructions residing within thememory212 accessible by theprocessor210. In further variations of thedetection system1700 depicted inFIG. 46, thebeam splitter4400,reference detector170 and other structures on the minor axis Y may be omitted, especially where the output intensity of thesource1720 is sufficiently stable to obviate any need to reference the source intensity in operation of thedetection system1700.

FIG. 47 depicts a sectional view of thesample detector150 in accordance with one embodiment.Sample detector150 is mounted in adetector housing152 having a receivingportion152aand acover152b. However, any suitable structure may be used as thesample detector150 andhousing152. The receivingportion152apreferably defines anaperture152cand alens chamber152d, which are generally aligned with the major axis X when thehousing152 is mounted in theanalyte detection system1700. Theaperture152cis configured to allow at least a fraction of the sample beam (Es) passing through the sample S and thesample element1730 to advance through theaperture152cand into thelens chamber152d.

The receivingportion152ahouses thesecond lens4440 in thelens chamber152dproximal to theaperture152c. Thesample detector150 is also disposed in thelens chamber152ddownstream of thesecond lens4440 such that adetection plane154 of thedetector150 is substantially orthogonal to the major axis X. Thesecond lens4440 is positioned such that aplane142 of thelens4440 is substantially orthogonal to the major axis X. Thesecond lens4440 is configured, and is preferably disposed relative to theholder4430 and thesample detector150, to focus substantially all of the sample beam (Es) onto thedetection plane154, thereby increasing the flux density of the sample beam (Es) incident upon thedetection plane154.

With further reference toFIG. 47, asupport member156 preferably holds thesample detector150 in place in the receivingportion152a. In the illustrated embodiment, thesupport member156 is aspring156 disposed between thesample detector150 and thecover152b. Thespring156 is configured to maintain thedetection plane154 of thesample detector150 substantially orthogonal to the major axis X. Agasket157 is preferably disposed between thecover152band the receivingportion152aand surrounds thesupport member156.

The receivingportion152apreferably also houses a printedcircuit board158 disposed between thegasket157 and thesample detector150. Theboard158 connects to thesample detector150 through at least one connectingmember150a. Thesample detector150 is configured to generate a detection signal corresponding to the sample beam (Es) incident on thedetection plane154. Thesample detector150 communicates the detection signal to thecircuit board158 through the connectingmember150a, and theboard158 transmits the detection signal to theprocessor210.

In one embodiment, thesample detector150 comprises a generallycylindrical housing150a, e.g. a type TO-39 “metal can” package, which defines a generallycircular housing aperture150bat its “upstream” end. In one embodiment, thehousing150ahas a diameter of about 0.323 inches and a depth of about 0.248 inches, and theaperture150bmay have a diameter of about 0.197 inches.

Adetector window150cis disposed adjacent theaperture150b, with its upstream surface preferably about 0.078 inches (±0.004 inches) from thedetection plane154. (Thedetection plane154 is located about 0.088 inches (±0.004 inches) from the upstream edge of thehousing150a, where the housing has a thickness of about 0.010 inches.) Thedetector window150cis preferably transmissive of infrared energy in at least a 3-12 micron passband; accordingly, one suitable material for thewindow150cis germanium. The endpoints of the passband may be “spread” further to less than 2.5 microns, and/or greater than 12.5 microns, to avoid unnecessary absorbance in the wavelengths of interest. Preferably, the transmittance of thedetector window150cdoes not vary by more than 2% across its passband. Thewindow150cis preferably about 0.020 inches in thickness. Thesample detector150 preferably substantially retains its operating characteristics across a temperature range of −20 to +60 degrees Celsius.

FIG. 48 depicts a sectional view of thereference detector170 in accordance with one embodiment. Thereference detector170 is mounted in adetector housing172 having a receivingportion172aand acover172b. However, any suitable structure may be used as thesample detector150 andhousing152. The receivingportion172apreferably defines anaperture172cand achamber172dwhich are generally aligned with the minor axis Y, when thehousing172 is mounted in theanalyte detection system1700. Theaperture172cis configured to allow the reference beam (Er) to advance through theaperture172cand into thechamber172d.

The receivingportion172ahouses thereference detector170 in thechamber172dproximal to theaperture172c. Thereference detector170 is disposed in thechamber172dsuch that adetection plane174 of thereference detector170 is substantially orthogonal to the minor axis Y. Thethird lens160 is configured to substantially focus the reference beam (Er) so that substantially the entire reference beam (Er) impinges onto thedetection plane174, thus increasing the flux density of the reference beam (Er) incident upon thedetection plane174.

With further reference toFIG. 48, asupport member176 preferably holds thereference detector170 in place in the receivingportion172a. In the illustrated embodiment, thesupport member176 is aspring176 disposed between thereference detector170 and thecover172b. Thespring176 is configured to maintain thedetection plane174 of thereference detector170 substantially orthogonal to the minor axis Y. Agasket177 is preferably disposed between thecover172band the receivingportion172aand surrounds thesupport member176.

The receivingportion172apreferably also houses a printedcircuit board178 disposed between thegasket177 and thereference detector170. Theboard178 connects to thereference detector170 through at least one connectingmember170a. Thereference detector170 is configured to generate a detection signal corresponding to the reference beam (Er) incident on thedetection plane174. Thereference detector170 communicates the detection signal to thecircuit board178 through the connectingmember170a, and theboard178 transmits the detection signal to theprocessor210.

In one embodiment, the construction of thereference detector170 is generally similar to that described above with regard to thesample detector150.

In one embodiment, the sample and

reference detectors

150,170 are both configured to detect electromagnetic radiation in a spectral wavelength range of between about 0.8 μm and about 25 μm. However, any suitable subset of the foregoing set of wavelengths can be selected. In another embodiment, the

detectors

150,170 are configured to detect electromagnetic radiation in the wavelength range of between about 4 μm and about 12 μm. The detection planes154,174 of the

detectors

150,170 may each define an active area about 2 mm by 2 mm or from about 1 mm by 1 mm to about 5 mm by 5 mm; of course, any other suitable dimensions and proportions may be employed. Additionally, the

detectors

150,170 may be configured to detect electromagnetic radiation directed thereto within a cone angle of about 45 degrees from the major axis X.10236] In one embodiment, the sample and

reference detector subsystems

150,170 may further comprise a system (not shown) for regulating the temperature of the detectors. Such a temperature-regulation system may comprise a suitable electrical heat source, thermistor, and a proportional-plus-integral-plus-derivative (PID) control. These components may be used to regulate the temperature of the

detectors

150,170 at about 35° C. The

detectors

150,170 can also optionally be operated at other desired temperatures. Additionally, the PID control preferably has a control rate of about 60 Hz and, along with the heat source and thermistor, maintains the temperature of the

detectors

150,170 within about 0.1° C. of the desired temperature.

The

detectors

150,170 can operate in either a voltage mode or a current mode, wherein either mode of operation preferably includes the use of a pre-amp module. Suitable voltage mode detectors for use with theanalyte detection system1700 disclosed herein include: models LIE 302 and 312 by InfraTec of Dresden, Germany; model L2002 by BAE Systems of Rockville, Md.; and model LTS-1 by Dias of Dresden, Germany. Suitable current mode detectors include: InfraTec models LIE 301, 315, 345 and 355; and 2×2 current-mode detectors available from Dias.

In one embodiment, one or both of the

detectors

150,170 may meet the following specifications, when assuming an incident radiation intensity of about 9.26×10⁻⁴watts (rms) per cm², at 10 Hz modulation and within a cone angle of about 15 degrees: detector area of 0.040 cm²(2 mm×2 mm square); detector input of 3.70×10⁻⁵watts (rms) at 10 Hz; detector sensitivity of 360 volts per watt at 10 Hz; detector output of 1.333×10⁻²volts (rms) at 10 Hz; noise of 8.00×10⁻⁸volts/sqrtHz at 10 Hz; and signal-to-noise ratios of 1.67×10⁵rms/sqrtHz and 104.4 dB/sqrtHz; and detectivity of 1.00×10⁹cm sqrtHz/watt.

In alternative embodiments, the

detectors

150,170 may comprise microphones and/or other sensors suitable for operation of thedetection system1700 in a photoacoustic mode.

The components of any of the embodiments of theanalyte detection system1700 may be partially or completely contained in an enclosure or casing (not shown) to prevent stray electromagnetic radiation, such as stray light, from contaminating the energy beam E. Any suitable casing may be used. Similarly, the components of thedetection system1700 may be mounted on any suitable frame or chassis (not shown) to maintain their operative alignment as depicted inFIGS. 17, 44, and46. The frame and the casing may be formed together as a single unit, member or collection of members.

In one method of operation, theanalyte detection system1700 shown in FIGS.44 or46 measures the concentration of one or more analytes in the material sample S, in part, by comparing the electromagnetic radiation detected by the sample and

reference detectors

150,170. During operation of thedetection system1700, each of the secondary filter(s)60 is sequentially aligned with the major axis X for a dwell time corresponding to thesecondary filter60. (Of course, where an electronically tunable filter or Fabry-Perot interferometer is used in place of thefilter wheel50, the tunable filter or interferometer is sequentially tuned to each of a set of desired wavelengths or wavelength bands in lieu of the sequential alignment of each of the secondary filters with the major axis X.) Theenergy source1720 is then operated at (any) modulation frequency, as discussed above, during the dwell time period. The dwell time may be different for each secondary filter60 (or each wavelength or band to which the tunable filter or interferometer is tuned). In one embodiment of thedetection system1700, the dwell time for eachsecondary filter60 is less than about 1 second. Use of a dwell time specific to eachsecondary filter60 advantageously allows thedetection system1700 to operate for a longer period of time at wavelengths where errors can have a greater effect on the computation of the analyte concentration in the material sample S. Correspondingly, thedetection system1700 can operate for a shorter period of time at wavelengths where errors have less effect on the computed analyte concentration. The dwell times may otherwise be nonuniform among the filters/wavelengths/bands employed in the detection system.

For eachsecondary filter60 selectively aligned with the major axis X, thesample detector150 detects the portion of the sample beam (Es), at the wavelength or wavelength band corresponding to thesecondary filter60, that is transmitted through the material sample S. Thesample detector150 generates a detection signal corresponding to the detected electromagnetic radiation and passes the signal to theprocessor210. Simultaneously, thereference detector170 detects the reference beam (Er) transmitted at the wavelength or wavelength band corresponding to thesecondary filter60. Thereference detector170 generates a detection signal corresponding to the detected electromagnetic radiation and passes the signal to theprocessor210. Based on the signals passed to it by the

detectors

150,170, theprocessor210 computes the concentration of the analyte(s) of interest in the sample S, and/or the absorbance/transmittance characteristics of the sample S at one or more wavelengths or wavelength bands employed to analyze the sample. Theprocessor210 computes the concentration(s), absorbance(s), transmittance(s), etc. by executing a data processing algorithm or program instructions residing within thememory212 accessible by theprocessor210.

The signal generated by the reference detector may be used to monitor fluctuations in the intensity of the energy beam emitted by thesource1720, which fluctuations often arise due to drift effects, aging, wear or other imperfections in the source itself. This enables theprocessor210 to identify changes in intensity of the sample beam (Es) that are attributable to changes in the emission intensity of thesource1720, and not to the composition of the sample S. By so doing, a potential source of error in computations of concentration, absorbance, etc. is minimized or eliminated.

In one embodiment, thedetection system1700 computes an analyte concentration reading by first measuring the electromagnetic radiation detected by the

detectors

150,170 at each center wavelength, or wavelength band, without thesample element1730 present on the major axis X (this is known as an “air” reading). Second, thesystem1700 measures the electromagnetic radiation detected by the

detectors

150,170 for each center wavelength, or wavelength band, with the material sample S present in thesample element1730, and thesample element1730 and sample S in position on the major axis X (i.e., a “wet” reading). Finally, theprocessor180 computes the concentration(s), absorbance(s) and/or transmittances relating to the sample S based on these compiled readings.

In one embodiment, the plurality of air and wet readings are used to generate a pathlength corrected spectrum as follows. First, the measurements are normalized to give the transmission of the sample at each wavelength. Using both a signal and reference measurement at each wavelength, and letting S_irepresent the signal ofdetector150 at wavelength i and R_irepresent the signal ofdetector170 at wavelength i, the transmission, τ_iis computed as τ_i=S_i(wet)/R_i(wet)/S_i(air)/R_i(air). Optionally, the spectra may be calculated as the optical density, OD_i, as −Log(T_i).

Next, the transmission over the wavelength range of approximately 4.5 μm to approximately 5.5 μm is analyzed to determine the pathlength. Specifically, since water is the primary absorbing species of blood over this wavelength region, and since the optical density is the product of the optical pathlength and the known absorption coefficient of water (OD=L σ, where L is the optical pathlength and σ is the absorption coefficient), any one of a number of standard curve fitting procedures may be used to determine the optical pathlength, L from the measured OD. The pathlength may then be used to determine the absorption coefficient of the sample at each wavelength. Alternatively, the optical pathlength may be used in further calculations to convert absorption coefficients to optical density.

Additional information on analyte detection systems, methods of use thereof, and related technologies may be found in the above-mentioned and incorporated U.S. Patent Application Publication No. 2005/0038357, published on Feb. 17, 2005, titled SAMPLE ELEMENT WITH BARRIER MATERIAL.

Section IV.C—Sample Element

FIG. 18 is a top view of asample element1730,FIG. 19 is a side view of the sample element, andFIG. 20 is an exploded perspective view of the sample element. In one embodiment of the present invention,sample element1730 includessample chamber903 that is in fluid communication with and accepts filtered blood fromsample preparation unit332. Thesample element1730 comprises asample chamber903 defined by sample chamber walls1802. Thesample chamber903 is configured to hold a material sample which may be drawn from a patient, for analysis by the detection system with which thesample element1730 is employed.

In the embodiment illustrated inFIGS. 18-19, thesample chamber903 is defined by first and second

lateral chamber walls

1802a,1802band upper and

lower chamber walls

1802c,1802d; however, any suitable number and configuration of chamber walls may be employed. At least one of the upper and

lower chamber walls

1802c,1802dis formed from a material which is sufficiently transmissive of the wavelength(s) of electromagnetic radiation that are employed by the sample analysis apparatus322 (or any other system with which the sample element is to be used). A chamber wall which is so transmissive may thus be termed a “window;” in one embodiment, the upper and

lower chamber walls

1802c,1802dcomprise first and second windows so as to permit the relevant wavelength(s) of electromagnetic radiation to pass through thesample chamber903. In another embodiment, only one of the upper and

lower chamber walls

1802c,1802dcomprises a window; in such an embodiment, the other of the upper and lower chamber walls may comprise a reflective surface configured to back-reflect any electromagnetic energy emitted into thesample chamber903 by the analyte detection system with which thesample element1730 is employed. Accordingly, this embodiment is well suited for use with an analyte detection system in which a source and a detector of electromagnetic energy are located on the same side as the sample element.

In various embodiments, the material that makes up the window(s) of thesample element1730 is completely transmissive, i.e., it does not absorb any of the electromagnetic radiation from thesource1720 andfilters1725 that is incident upon it. In another embodiment, the material of the window(s) has some absorption in the electromagnetic range of interest, but its absorption is negligible. In yet another embodiment, the absorption of the material of the window(s) is not negligible, but it is stable for a relatively long period of time. In another embodiment, the absorption of the window(s) is stable for only a relatively short period of time, butsample analysis apparatus322 is configured to observe the absorption of the material and eliminate it from the analyte measurement before the material properties can change measurably. Materials suitable for forming the window(s) of thesample element1730 include, but are not limited to, calcium fluoride, barium fluoride, germanium, silicon, polypropylene, polyethylene, or any polymer with suitable transmissivity (i.e., transmittance per unit thickness) in the relevant wavelength(s). Where the window(s) are formed from a polymer, the selected polymer can be isotactic, atactic or syndiotactic in structure, so as to enhance the flow of the sample between the window(s). One type of polyethylene suitable for constructing thesample element1730 istype220, extruded or blow molded, available from KUBE Ltd. of Staefa, Switzerland.

In one embodiment, thesample element1730 is configured to allow sufficient transmission of electromagnetic energy having a wavelength of between about 4 μm and about 10.5 μm through the window(s) thereof. However, thesample element1730 can be configured to allow transmission of wavelengths in any spectral range emitted by theenergy source1720. In another embodiment, thesample element1730 is configured to receive an optical power of more than about 1.0 MW/cm²from the sample beam (Es) incident thereon for any electromagnetic radiation wavelength transmitted through thefilter1725. Preferably, thesample chamber903 of thesample element1730 is configured to allow a sample beam (Es) advancing toward the material sample S within a cone angle of 45 degrees from the major axis X (seeFIG. 17) to pass therethrough.

J In the embodiment illustrated inFIGS. 18-19, the sample element further comprises asupply passage1804 extending from thesample chamber903 to asupply opening1806 and avent passage1808 extending from thesample chamber903 to avent opening1810. While the vent and

supply openings

1806,1810 are shown at one end of thesample element1730, in other embodiments the openings may be positioned on other sides of thesample element1730, so long as it is in fluid communication with the

passages

1804 and1808, respectively.

In operation, thesupply opening1806 of thesample element1730 is placed in contact with the material sample S, such as a fluid flowing from a patient. The fluid is then transported through thesample supply passage1804 and into thesample chamber903 via an external pump or by capillary action.

Where the upper and

lower chamber walls

1802c,1802dcomprise windows, the distance T (measured along an axis substantially orthogonal to thesample chamber903 and/or

windows

1802a,1802b, or, alternatively, measured along an axis of an energy beam (such as but not limited to the energy beam E discussed above) passed through the sample chamber903) between them comprises an optical pathlength. In various embodiments, the pathlength is between about 1 μm and about 300 μm, between about 1 μm and about 100 μm, between about 25 μm and about 40 μm, between about 10 μm and about 40 μm, between about 25 μm and about 60 μm, or between about 30 μm and about 50 μm. In still other embodiments, the optical pathlength is about 50 μm, or about 25 μm. In some instances, it is desirable to hold the pathlength T to within about plus or minus 1 μm from any pathlength specified by the analyte detection system with which thesample element1730 is to be employed. Likewise, it may be desirable to orient the

walls

1802c,1802dwith respect to each other within plus or minus 1 μm of parallel, and/or to maintain each of the

walls

1802c,1802dto within plus or minus 1 μm of planar (flat), depending on the analyte detection system with which thesample element1730 is to be used. In alternative embodiments,

walls

1802c,1802dare flat, textured, angled, or some combination thereof.

In one embodiment, the transverse size of the sample chamber903 (i.e., the size defined by the

lateral chamber walls

1802a,1802b) is about equal to the size of the active surface of thesample detector1745. Accordingly, in a further embodiment thesample chamber903 is round with a diameter of about 4 millimeter to about 12 millimeter, and more preferably from about 6 millimeter to about 8 millimeter.

Thesample element1730 shown inFIGS. 18-19 has, in one embodiment, sizes and dimensions specified as follows. Thesupply passage1804 preferably has a length of about 15 millimeter, a width of about 1.0 millimeter, and a height equal to the pathlength T. Additionally, thesupply opening1806 is preferably about 1.5 millimeter wide and smoothly transitions to the width of thesample supply passage1804. Thesample element1730 is about 0.5 inches (12 millimeters) wide and about one inch (25 millimeters) long with an overall thickness of between about 1.0 millimeter and about 4.0 millimeter. Thevent passage1808 preferably has a length of about 1.0 millimeter to 5.0 millimeter and a width of about 1.0 millimeter, with a thickness substantially equal to the pathlength between the

walls

1802c,1802d. Thevent aperture1810 is of substantially the same height and width as thevent passage1808. Of course, other dimensions may be employed in other embodiments while still achieving the advantages of thesample element1730.

Thesample element1730 is preferably sized to receive a material sample S having a volume less than or equal to about 15 μL (or less than or equal to about 10 μL, or less than or equal to about 5 μL) and more preferably a material sample S having a volume less than or equal to about 2 μL. Of course, the volume of thesample element1730, the volume of thesample chamber903, etc. can vary, depending on many variables, such as the size and sensitivity of thesample detector1745, the intensity of the radiation emitted by theenergy source1720, the expected flow properties of the sample, and whether flow enhancers are incorporated into thesample element1730. The transport of fluid to thesample chamber903 is achieved preferably through capillary action, but may also be achieved through wicking or vacuum action, or a combination of wicking, capillary action, peristaltic, pumping, and/or vacuum action.

FIG. 20 depicts one approach to constructing thesample element1730. In this approach, thesample element1730 comprises afirst layer1820, asecond layer1830, and athird layer1840. Thesecond layer1830 is preferably positioned between thefirst layer1820 and thethird layer1840. Thefirst layer1820 forms theupper chamber wall1802c, and thethird layer1840 forms thelower chamber wall1802d. Where either of the

chamber walls

1802c,1802dcomprises a window, the window(s)/wall(s)1802c/1802din question may be formed from a different material as is employed to form the balance of the layer(s)1820/1840 in which the wall(s) are located. Alternatively, the entirety of the layer(s)1820/1840 may be formed of the material selected to form the window(s)/wall(s)1802c,1802d. In this case, the window(s)/wall(s)1802c,1802dare integrally formed with the layer(s)1820,1840 and simply comprise the regions of the respective layer(s)1820,1840 which overlie thesample chamber903.

With further reference toFIG. 20,second layer1830 may be formed entirely of an adhesive that joins the first and

third layers

1820,1840. In other embodiments, thesecond layer1830 may be formed from similar materials as the first and third layers, or any other suitable material. Thesecond layer1830 may also be formed as a carrier with an adhesive deposited on both sides thereof. Thesecond layer1830 includes voids which at least partially form thesample chamber903,sample supply passage1804,supply opening1806,vent passage1808, and ventopening1810. The thickness of thesecond layer1830 can be the same as any of the pathlengths disclosed above as suitable for thesample element1730. The first and third layers can be formed from any of the materials disclosed above as suitable for forming the window(s) of thesample element1730. In one embodiment, layers1820,1840 are formed from material having sufficient structural integrity to maintain its shape when filled with a sample S. Layers1820,1830 may be, for example, calcium fluoride having a thickness of 0.5 millimeter. In another embodiment, thesecond layer1830 comprises the adhesive portion of Adhesive Transfer Tape no. 9471LE available from 3M Corporation. In another embodiment, thesecond layer1830 comprises an epoxy, available, for example, from TechFilm (31 Dunham Road, Billerica, Mass. 01821), that is bound to

layers

1820,1840 as a result of the application of pressure and heat to the layers.

Thesample chamber903 preferably comprises a reagentless chamber. In other words, the internal volume of thesample chamber903 and/or the wall(s)1802 defining thechamber903 are preferably inert with respect to the sample to be drawn into the chamber for analysis. As used herein, “inert” is a broad term and is used in its ordinary sense and includes, without limitation, substances which will not react with the sample in a manner which will significantly affect any measurement made of the concentration of analyte(s) in the sample withsample analysis apparatus322 or any other suitable system, for a sufficient time (e.g., about 1-30 minutes) following entry of the sample into thechamber903, to permit measurement of the concentration of such analyte(s). Alternatively, thesample chamber903 may contain one or more reagents to facilitate use of the sample element in sample assay techniques which involve reaction of the sample with a reagent.

In one embodiment of the present invention,sample element1730 is used for a limited number of measurements and is disposable. Thus, for example, with reference toFIGS. 8-10,sample element1730 forms a disposable portion ofcassette820 adapted to placesample chamber903 withinprobe region1002.

Additional information on sample elements, methods of use thereof, and related technologies may be found in the above-mentioned and incorporated U.S. Patent Application Publication No. 2005/0038357, published on Feb. 17, 2005, titled SAMPLE ELEMENT WITH BARRIER MATERIAL; and in the above-mentioned and incorporated U.S. patent application Ser. No. 11/122,794, filed on May 5, 2005, titled SAMPLE ELEMENT WITH SEPARATOR.

Section IV.D—Centrifuge

FIG. 21 is a schematic of one embodiment of asample preparation unit2100 utilizing a centrifuge and which may be generally similar to thesample preparation unit332, except as further detailed below. In general, thesample preparation unit332 includes a centrifuge in place of, or in addition to a filter, such as thefilter1500.Sample preparation unit2100 includes a fluid handling element in the form of acentrifuge2110 having asample element2112 and afluid interface2120.Sample element2112 is illustrated inFIG. 21 as a somewhat cylindrical element. This embodiment is illustrative, and the sample element may be cylindrical, planar, or any other shape or configuration that is compatible with the function of holding a material (preferably a liquid) in thecentrifuge2110. Thecentrifuge2110 can be used to rotate thesample element2112 such that the material held in thesample element2112 is separated.

In some embodiments, thefluid interface2120 selectively controls the transfer of a sample from thepassageway113 and into thesample element2112 to permit centrifuging of the sample. In another embodiment, thefluid interface2120 also permits a fluid to flow though thesample element2112 to cleanse or otherwise prepare the sample element for obtaining an analyte measurement. Thus, thefluid interface2120 can be used to flush and fill thesample element2112.

As shown inFIG. 21, thecentrifuge2110 comprises arotor2111 that includes thesample element2112 and anaxle2113 attached to a motor, not shown, which is controlled by thecontroller210. Thesample element2112 is preferably generally similar to thesample element1730 except as described subsequently.

As is further shown inFIG. 21,fluid interface2120 includes afluid injection probe2121 having afirst needle2122 and afluid removal probe2123. Thefluid removal probe2123 has asecond needle2124. Whensample element2112 is properly oriented relative tofluid interface2120, a sample, fluid, or other liquid is dispensed into or passes through thesample element2112. More specifically,fluid injection probe2121 includes a passageway to receive a sample, such as a bodily fluid from thepatient connector110. The bodily fluid can be passed through thefluid injection probe2121 and thefirst needle2122 into thesample element2112. To remove material from thesample element2112, thesample2112 can be aligned with thesecond needle2124, as illustrated. Material can be passed through thesecond needle2124 into thefluid removal probe2123. The material can then pass through a passageway of theremoval probe2123 away from thesample element2112.

One position that thesample element2112 may be rotated through or to is asample measurement location2140. Thelocation2140 may coincide with a region of an analysis system, such as an optical analyte detection system. For example, thelocation2140 may coincide with aprobe region1002, or with a measurement location of another apparatus.

Therotor2111 may be driven in a direction indicated by arrow R, resulting in a centrifugal force on sample(s) withinsample element2112. The rotation of a sample(s) located a distance from the center of rotation creates centrifugal force. In some embodiments, thesample element2112 holds whole blood. The centrifugal force may cause the denser parts of the whole blood sample to move further out from the center of rotation than lighter parts of the blood sample. As such, one or more components of the whole blood can be separated from each other. Other fluids or samples can also be removed by centrifugal forces. In one embodiment, thesample element2112 is a disposable container that is mounted on to adisposable rotor2111. Preferably, the container is plastic, reusable and flushable. In other embodiments, thesample element2112 is a non-disposable container that is permanently attached to therotor2111.

The illustratedrotor2111 is a generally circular plate that is fixedly coupled to theaxle2113. Therotor2111 can alternatively have other shapes. Therotor2111 preferably comprises a material that has a low density to keep the rotational inertia low and that is sufficiently strong and stable to maintain shape under operating loads to maintain close optical alignment. For example, therotor2111 can be comprised of GE brand ULTEM (trademark) polyetherimide (PEI). This material is available in a plate form that is stable but can be readily machined. Other materials having similar properties can also be used.

The size of therotor2111 can be selected to achieve the desired centrifugal force. In some embodiments, the diameter ofrotor2111 is from about 75 millimeters to about 125 millimeters, or more preferably from about 100 millimeters to about 125 millimeters. The thickness ofrotor2111 is preferably just thick enough to support the centrifugal forces and can be, for example, from about 1.0 to 2.0 millimeter thick.

In an alternative embodiment, thefluid interface2120 selectively removes blood plasma from thesample element2112 after centrifuging. The blood plasma is then delivered to an analyte detection system for analysis. In one embodiment, the separated fluids are removed from thesample element2112 through the bottom connector. Preferably, the location and orientation of the bottom connector and the container allow the red blood cells to be removed first. One embodiment may be configured with a red blood cell detector. The red blood cell detector may detect when most of the red blood cells have exited the container by determining the haemostatic level. The plasma remaining in the container may then be diverted into the analysis chamber. After the fluids have been removed from the container, the top connector may inject fluid (e.g., saline) into the container to flush the system and prepare it for the next sample.

FIGS. 22A to23C illustrate another embodiment of a fluid handling andanalysis apparatus140, which employs a removable, disposablefluid handling cassette820. Thecassette820 is equipped with acentrifuge rotor assembly2016 to facilitate preparation and analysis of a sample. Except as further described below, theapparatus140 ofFIGS. 22A-22C can in certain embodiments be similar to any of the other embodiments of theapparatus140 discussed herein, and thecassette820 can in certain embodiments b,e similar to any of the embodiments of thecassettes820 disclosed herein.

The removablefluid handling cassette820 can be removably engaged with amain analysis instrument810. When thefluid handling cassette820 is coupled to themain instrument810, adrive system2030 of themain instrument810 mates with therotor assembly2016 of the cassette820 (FIG. 22B). Once thecassette820 is coupled to themain instrument810, thedrive system2030 engages and can rotate therotor assembly2016 to apply a centrifugal force to a body fluid sample carried by therotor assembly2016.

In some embodiments, therotor assembly2016 includes arotor2020 sample element2448 (FIG. 22C) for holding a sample for centrifuging. When therotor2020 is rotated, a centrifugal force is applied to the sample contained within thesample element2448. The centrifugal force causes separation of one or more components of the sample (e.g., separation of plasma from whole blood). The separated component(s) can then be analyzed by theapparatus140, as will be discussed in further detail below.

Themain instrument810 includes both thecentrifuge drive system2030 and ananalyte detection system1700, a portion of which protrudes from ahousing2049 of themain instrument810. Thedrive system2030 is configured to releasably couple with therotor assembly2016, and can impart rotary motion to therotor assembly2016 to rotate therotor2020 at a desired speed. After the centrifuging process, theanalyte detection system1700 can analyze one or more components separated from the sample carried by therotor2020. The projecting portion of the illustrateddetection system1700 forms aslot2074 for receiving a portion of therotor2020 carrying thesample element2448 so that thedetection system1700 can analyze the sample or component(s) carried in thesample element2448.

To assemble the fluid handling andanalysis apparatus140 as shown inFIG. 22C, thecassette820 is placed on themain instrument810, as indicated by thearrow2007 ofFIGS. 22A and 22B. Therotor assembly2016 is accessible to thedrive system2030, so that once thecassette820 is properly mounted on themain instrument810, thedrive system2030 is in operative engagement with therotor assembly2016. Thedrive system2030 is then energized to spin therotor2020 at a desired speed. Thespinning rotor2020 can pass repeatedly through theslot2074 of thedetection system1700.

After the centrifuging process, therotor2020 is rotated to an analysis position (seeFIGS. 22B and 23C) wherein thesample element2448 is positioned within theslot2074. With therotor2020 andsample element2448 in the analysis position, theanalyte detection system1700 can analyze one or more of the components of the sample carried in thesample element2448. For example, thedetection system1700 can analyze at least one of the components that is separated out during the centrifuging process. After using thecassette820, thecassette820 can be removed from themain instrument810 and discarded. Anothercassette820 can then be mounted to themain instrument810.

With reference toFIG. 23A, the illustratedcassette820 includes thehousing2400 that surrounds therotor assembly2016, and therotor2020 is pivotally connected to thehousing2400 by therotor assembly2016. Therotor2020 includes arotor interface2051 for driving engagement with thedrive system2030 upon placement of thecassette820 on themain instrument810.

In some embodiments, thecassette820 is a disposable fluid handling cassette. The reusablemain instrument810 can be used with any number ofcassettes820 as desired. Additionally or alternatively, thecassette820 can be a portable, handheld cassette for convenient transport. In these embodiments, thecassette820 can be manually mounted to or removed from themain instrument810. In some embodiments, thecassette820 may be a non disposable cassette which can be permanently coupled to themain instrument810.

FIGS. 25A and 25B illustrate thecentrifugal rotor2020, which is capable of carrying a sample, such as bodily fluid. Thus, the illustratedcentrifugal rotor2020 can be considered a fluid handling element that can prepare a sample for analysis, as well as hold the sample during a spectroscopic analysis. Therotor2020 preferably comprises anelongate body2446, at least onesample element2448, and at least onebypass element2452. Thesample element2448 andbypass element2452 can be located at opposing ends of therotor2020. Thebypass element2452 provides a bypass flow path that can be used to clean or flush fluid passageways of the fluid handling andanalysis apparatus140 without passing fluid through thesample element2448.

The illustratedrotor body2446 can be a generally planar member that defines a mountingaperture2447 for coupling to thedrive system2030. The illustratedrotor2020 has a somewhat rectangular shape. In alternative embodiments, therotor2020 is generally circular, polygonal, elliptical, or can have any other shape as desired. The illustrated shape can facilitate loading when positioned horizontally to accommodate theanalyte detection system1700.

With reference toFIG. 25B, a pair of opposing first and second

fluid connectors

2027,2029 extends outwardly from a front face of therotor2020, to facilitate fluid flow through therotor body2446 to thesample element2448 andbypass element2452, respectively. Thefirst fluid connector2027 defines anoutlet port2472 and aninlet port2474 that are in fluid communication with thesample element2448. In the illustrated embodiment,

fluid channels

2510,2512 extend from theoutlet port2472 andinlet port2474, respectively, to thesample element2448. (SeeFIGS. 25E and 25F.) As such, the

ports

2472,2474 and

channels

2510,2512 define input and return flow paths through therotor2020 to thesample element2448 and back.

With continued reference toFIG. 25B, therotor2020 includes thebypass element2452 which permits fluid flow therethrough from anoutlet port2572 to theinlet port2574. Achannel2570 extends between theoutlet port2572 and theinlet port2574 to facilitate this fluid flow. Thechannel2570 thus defines a closed flow path through therotor2020 from oneport2572 to theother port2574. In the illustrated embodiment, theoutlet port2572 andinlet port2574 of thebypass element2452 have generally the same spacing therebetween on therotor2020 as theoutlet port2472 and theinlet port2474.

One or

more windows

2460a,2460bcan be provided for optical access through therotor2020. Awindow2460aproximate thebypass element2452 can be a through-hole (seeFIG. 25E) that permits the passage of electromagnetic radiation through therotor2020. Awindow2460bproximate thesample element2448 can also be a similar through-hole which permits the passage of electromagnetic radiation. Alternatively, one or both of the

windows

2460a,2460bcan be a sheet constructed of calcium fluoride, barium fluoride, germanium, silicon, polypropylene, polyethylene, combinations thereof, or any material with suitable transmissivity (i.e., transmittance per unit thickness) in the relevant wavelength(s). The

windows

2460a,2460bare positioned so that one of the

windows

2460a,2460bis positioned in theslot2074 when therotor2020 is in a vertically orientated position.

Various fabrication techniques can be used to form therotor2020. In some embodiments, therotor2020 can be formed by molding (e.g., compression or injection molding), machining, or a similar production process or combination of production processes. In some embodiments, therotor2020 is comprised of plastic. The compliance of the plastic material can be selected to create the seal with the ends of

pins

2542,2544 of a fluid interface2028 (discussed in further detail below). Non-limiting exemplary plastics for forming the ports (e.g.,

ports

2572,2574,2472,2474) can be relatively chemically inert and can be injection molded or machined. These plastics include, but are not limited to, PEEK and polyphenylenesulfide (PPS). Although both of these plastics have high modulus, a fluidic seal can be made if sealing surfaces are produced with smooth finish and the sealing zone is a small area where high contact pressure is created in a very small zone. Accordingly, the materials used to form therotor2020 and pins2542,2544 can be selected to achieve the desired interaction between therotor2020 and the

pins

2542,2544, as described in detail below.

The illustratedrotor assembly2016 ofFIG. 23A rotatably connects therotor2020 to thecassette housing2400 via arotor axle boss2426 which is fixed with respect to the cassette housing and pivotally holds arotor axle2430 and therotor2020 attached thereto. Therotor axle2430 extends outwardly from therotor axle boss2426 and is fixedly attached to arotor bracket2436, which is preferably securely coupled to a rear face of therotor2020. Accordingly, therotor assembly2016 and thedrive system2030 cooperate to ensure that therotor2020 rotates about theaxis2024, even at high speeds. The illustratedcassette820 has asingle rotor assembly2016. In other embodiments, thecassette820 can have more than onerotor assembly2016.Multiple rotor assemblies2016 can be used to prepare (preferably simultaneously) and test multiple samples.

With reference again toFIGS. 25A, 25B,25E and25F, thesample element2448 is coupled to therotor2020 and can hold a sample of body fluid for processing with the centrifuge. Thesample element2448 can, in certain embodiments, be generally similar to other sample elements or cuvettes disclosed herein (e.g.,sample elements1730,2112) except as further detailed below.

Thesample element2448 comprises asample chamber2464 that holds a sample for centrifuging, and

fluid channels

2466,2468, which provide fluid communication between thechamber2464 and the

channels

2512,2510, respectively, of therotor2020. Thus, the

fluid channels

2512,2466 define a first flow path between theport2474 and thechamber2464, and the

channels

2510,2468 define a second flow path between theport2472 and thechamber2464. Depending on the direction of fluid flow into thesample element2448, either of the first or second flow paths can serve as an input flow path, and the other can serve as a return flow path.

A portion of thesample chamber2464 can be considered aninterrogation region2091, which is the portion of the sample chamber through which electromagnetic radiation passes during analysis by thedetection system1700 of fluid contained in thechamber2464. Accordingly, theinterrogation region2091 is aligned with thewindow2460bwhen thesample element2448 is coupled to therotor2020. The illustratedinterrogation region2091 comprises a radially inward portion (i.e., relatively close to the axis ofrotation2024 of the rotor2020) of thechamber2464, to facilitate spectroscopic analysis of the lower density portion(s) of the body fluid sample (e.g., the plasma of a whole blood sample) after centrifuging, as will be discussed in greater detail below. Where the higher-density portions of the body fluid sample are of interest for spectroscopic analysis, theinterrogation region2091 can be located in a radially outward (i.e., further from the axis ofrotation2024 of the rotor2020) portion of thechamber2464.

Therotor2020 can temporarily or permanently hold thesample element2448. As shown inFIG. 25F, therotor2020 forms arecess2502 which receives thesample element2448. Thesample element2448 can be held in therecess2502 by frictional interaction, adhesives, or any other suitable coupling means. The illustratedsample element2448 is recessed in therotor2020. However, thesample element2448 can alternatively overlie or protrude from therotor2020.

Thesample element2448 can be used for a predetermined length of time, to prepare a predetermined amount of sample fluid, to perform a number of analyses, etc. If desired, thesample element2448 can be removed from therotor2020 and then discarded. Anothersample element2448 can then be placed into therecess2502. Thus, even if thecassette820 is disposable, a plurality ofdisposable sample elements2448 can be used with asingle cassette820. Accordingly, asingle cassette820 can be used with any number of sample elements as desired. Alternatively, thecassette820 can have asample element2448 that is permanently coupled to therotor2020. In some embodiments, at least a portion of thesample element2448 is integrally or monolithically formed with therotor body2446. Additionally or alternatively, therotor2020 can comprise a plurality of sample elements (e.g., with a record sample element in place of the bypass2452). In this embodiment, a plurality of samples (e.g., bodily fluid) can be prepared simultaneously to reduce sample preparation time.

FIGS. 26A and 26B illustrate a layered construction technique which can be employed when forming certain embodiments of thesample element2448. The depictedlayered sample element2448 comprises afirst layer2473, asecond layer2475, and athird layer2478. Thesecond layer2475 is preferably positioned between thefirst layer2473 and thethird layer2478. Thefirst layer2473 forms anupper chamber wall2482, and thethird layer2478 forms alower chamber wall2484. Alateral wall2490 of thesecond layer2475 defines the sides of thechamber2464 and the

fluid channels

2466,2468.

Thesecond layer2475 can be formed by die-cutting a substantially uniform-thickness sheet of a material to form the lateral wall pattern shown inFIG. 26A. Thesecond layer2475 can comprise a layer of lightweight flexible material, such as a polymer material, with adhesive disposed on either side thereof to adhere the first and

third layers

2473,2478 to thesecond layer2475 in “sandwich” fashion as shown inFIG. 26B. Alternatively, thesecond layer2475 can comprise an “adhesive-only” layer formed from a uniform-thickness sheet of adhesive which has been die-cut to form the depicted lateral wall pattern.

However constructed, thesecond layer2475 is preferably of uniform thickness to define a substantially uniform thickness or path length of thesample chamber2464 and/orinterrogation region2091. This path length (and therefore the thickness of thesecond layer2475 as well) is preferably between 10 microns and 100 microns, or is 20, 40, 50, 60, or 80 microns, in various embodiments.

Theupper chamber wall2482,lower chamber wall2484, andlateral wall2490 cooperate to form thechamber2464. Theupper chamber wall2482 and/or thelower chamber wall2484 can permit the passage of electromagnetic energy therethrough. Accordingly, one or both of the first and

third layers

2473,2478 comprises a sheet or layer of material which is relatively or highly transmissive of electromagnetic radiation (preferably infrared radiation or mid-infrared radiation) such as barium fluoride, silicon, polyethylene or polypropylene. If only one of the

layers

2473,2478 is so transmissive, the other of the layers is preferably reflective, to back-reflect the incoming radiation beam for detection on the same side of thesample element2448 as it was emitted. Thus theupper chamber wall2482 and/orlower chamber wall2484 can be considered optical window(s). These window(s) are disposed on one or both sides of theinterrogation region2091 of thesample element2448.

In one embodiment,sample element2448 has opposing sides that are transmissive of infrared radiation and suitable for making optical measurements as described, for example, in U.S. Patent Application Publication No. 2005/0036146, published Feb. 17, 2005, titled SAMPLE ELEMENT QUALIFICATION, and hereby incorporated by reference and made a part of this specification. Except as further described herein, the embodiments, features, systems, devices, materials, methods and techniques described herein may, in some embodiments, be similar to any one or more of the embodiments, features, systems, devices, materials, methods and techniques described in U.S. Patent Application Publication No. 2003/0090649, published on May 15, 2003, titled REAGENT-LESS WHOLE-BLOOD GLUCOSE METER; or in U.S. Patent Application Publication No. 2003/0086075, published on May 8, 2003, titled DEVICE AND METHOD FOR IN VITRO DETERMINATION OF ANALYTE CONCENTRATIONS WITHIN BODY FLUIDS; or in U.S. Patent Application Publication No. 2004/0019431, published on Jan. 29, 2004, titled METHOD OF DETERMINING AN ANALYTE CONCENTRATION IN A SAMPLE FROM AN ABSORPTION SPECTRUM, or in U.S. Pat. No. 6,652,136, issued on Nov. 25, 2003 to Marziali, titled METHOD OF SIMULTANEOUS MIXING OF SAMPLES. In addition, the embodiments, features, systems, devices, materials, methods and techniques described herein may, in certain embodiments, be applied to or used in connection with any one or more of the embodiments, features, systems, devices, materials, methods and techniques disclosed in the above-mentioned U.S. Patent Applications Publications Nos. 2003/0090649; 2003/0086075; 2004/0019431; or U.S. Pat. No. 6,652,136. All of the above-mentioned publications and patent are hereby incorporated by reference herein and made a part of this specification.

With reference toFIGS. 23B and 23C, thecassette820 can further comprise themovable fluid interface2028 for filling and/or removing sample liquid from thesample element2448. In the depicted embodiment, thefluid interface2028 is rotatably mounted to thehousing2400 of thecassette820. Thefluid interface2028 can be actuated between a lowered position (FIG. 22C) and a raised or filling position (FIG. 27C). When theinterface2028 is in the lowered position, therotor2020 can freely rotate. To transfer sample fluid to thesample element2448, therotor2020 can be held stationary and in a sample element loading position (seeFIG. 22C) thefluid interface2028 can be actuated, as indicated by thearrow2590, upwardly to the filling position. When thefluid interface2028 is in the filling position, thefluid interface2028 can deliver sample fluid into thesample element2448 and/or remove sample fluid from thesample element2448.

With continued reference toFIGS. 27A and 27B, thefluid interface2028 has amain body2580 that is rotatably mounted to thehousing2400 of thecassette820. Opposing

brackets

2581,2584 can be employed to rotatably couple themain body2580 to thehousing2400 of thecassette820, and permit rotation of themain body2580 and the

pins

2542,2544 about an axis ofrotation2590 between the lowered position and the filling position. Themain instrument810 can include a horizontally moveable actuator (not shown) in the form of a solenoid, pneumatic actuator, etc. which is extendible through anopening2404 in the cassette housing2400 (seeFIG. 23B). Upon extension, the actuator strikes themain body2580 of thefluid interface2028, causing thebody2580 to rotate to the filling position shown inFIG. 27C. Themain body2580 is preferably spring-biased towards the retracted position (shown inFIG. 23A) so that retraction of the actuator allows the main body to return to the retracted position. Thefluid interface2028 can thus be actuated for periodically placing fluid passageways of the

pins

2542,2544 in fluid communication with asample element2448 located on therotor2020.

Thefluid interface2028 ofFIGS. 27A and 23B includes

fluid connectors

2530,2532 that can provide fluid communication between theinterface2028 and one or more of the fluid passageways of theapparatus140 and/orsampling system100/800, as will be discussed in further detail below. The illustrated

connectors

2530,2532 are in an upwardly extending orientation and positioned at opposing ends of themain body2580. The

connectors

2530,2532 can be situated in other orientations and/or positioned at other locations along themain body2580. Themain body2580 includes a first inner passageway (not shown) which provides fluid communication between theconnector2530 and thepin2542, and a second inner passageway (not shown) which provides fluid communication between theconnector2532 and thepin2544.

The fluid pins2542,2544 extend outwardly from themain body2580 and can engage therotor2020 to deliver and/or remove sample fluid to or from therotor2020. The fluid pins2542,2544 have

respective pin bodies

2561,2563 and pin ends2571,2573. The pin ends2571,2573 are sized to fit within corresponding

ports

2472,2474 of thefluid connector2027 and/or the

ports

2572,2574 of thefluid connector2029, of therotor2020. The pin ends2571,2573 can be slightly chamfered at their tips to enhance the sealing between the pin ends2571,2573 and rotor ports. In some embodiments, the outer diameters of the pin ends2573,2571 are slightly larger than the inner diameters of the ports of therotor2020 to ensure a tight seal, and the inner diameters of the

pins

2542,2544 are preferably identical or very close to the inner diameters of the

channels

2510,2512 leading from the ports. In other embodiments, the outer diameter of the pin ends2571,2573 are equal to or less than the inner diameters of the ports of therotor2020.

J The connections between the

pins

2542,2544 and the corresponding portions of therotor2020, either the

ports

2472,2474 leading to thesample element2448 or the

ports

2572,2574 leading to thebypass element2452, can be relatively simple and inexpensive. At least a portion of therotor2020 can be somewhat compliant to help ensure a seal is formed with the

pins

2542,2544. Alternatively or additionally, sealing members (e.g., gaskets, O-rings, and the like) can be used to inhibit leaking between the pin ends2571,2573 and corresponding

ports

2472,2474,2572,2574.

FIGS. 23A and 23B illustrate thecassette housing2400 enclosing therotor assembly2016 and thefluid interface2028. Thehousing2400 can be a modular body that defines an aperture oropening2404 dimensioned to receive adrive system housing2050 when thecassette820 is operatively coupled to themain instrument810. Thehousing2400 can protect therotor2020 from external forces and can also limit contamination of samples delivered to a sample element in therotor2020, when thecassette820 is mounted to themain instrument810.

The illustratedcassette820 has a pair of opposing

side walls

2041,2043, top2053, and anotch2408 for mating with thedetection system1700. Afront wall2045 andrear wall2047 extend between the

side walls

2041,2043. Therotor assembly2016 is mounted to the inner surface of therear wall2047. Thefront wall2045 is configured to mate with themain instrument810 while providing thedrive system2030 with access to therotor assembly2016.

Theillustrated front wall2045 has theopening2404 that provides access to therotor assembly2016. Thedrive system2030 can be passed through theopening2404 into the interior of thecassette820 until it operatively engages therotor assembly2016. Theopening2404 ofFIG. 23B is configured to mate and tightly surround thedrive system2030. The illustratedopening2404 is generally circular and includes anupper notch2405 to permit the fluid interface actuator of themain instrument810 to access thefluid interface2028, as discussed above. Theopening2404 can have other configurations suitable for admitting thedrive system2030 and actuator into thecassette820.

Thenotch2408 of thehousing2400 can at least partially surround the projecting portion of theanalyte detection system1700 when thecassette820 is loaded onto themain instrument810. The illustratednotch2408 defines a cassette slot2410 (FIG. 23A) that is aligned withelongate slot2074 shown inFIG. 22C, upon loading of thecassette820. Therotating rotor2020 can thus pass through the aligned

slots

2410,2074. In some embodiments, thenotch2408 has a generally U-shaped axial cross section as shown. More generally, the configuration of thenotch2408 can be selected based on the design of the projecting portion of thedetection system1700.

Although not illustrated, fasteners, clips, mechanical fastening assemblies, snaps, or other coupling means can be used to ensure that thecassette820 remains coupled to themain instrument810 during operation. Alternatively, the interaction between thehousing2400 and the components of themain instrument810 can secure thecassette820 to themain instrument810.

FIG. 28 is a cross-sectional view of themain instrument810. The illustratedcentrifuge drive system2030 extends outwardly from afront face2046 of themain instrument810 so that it can be easily mated with therotor assembly2016 of thecassette820. When thecentrifuge drive system2030 is energized, thedrive system2030 can rotate therotor2020 at a desired rotational speed.

The illustratedcentrifuge drive system2030 ofFIGS. 23E and 28 includes acentrifuge drive motor2038 and adrive spindle2034 that is drivingly connected to thedrive motor2038. Thedrive spindle2034 extends outwardly from thedrive motor2038 and forms acentrifuge interface2042. Thecentrifuge interface2042 extends outwardly from thedrive system housing2050, which houses thedrive motor2038. To impart rotary motion to therotor2020, thecentrifuge interface2042 can have keying members, protrusions, notches, detents, recesses, pins, or other types of structures that can engage therotor2020 such that thedrive spindle2034 androtor2020 are coupled together.

Thecentrifuge drive motor2038 ofFIG. 28 can be any suitable motor that can impart rotary motion to therotor2020. When thedrive motor2038 is energized, thedrive motor2038 can rotate thedrive spindle2034 at constant or varying speeds. Various types of motors, including, but not limited to, centrifuge motors, stepper motors, spindle motors, electric motors, or any other type of motor for outputting a torque can be utilized. Thecentrifuge drive motor2038 is preferably fixedly secured to thedrive system housing2050 of themain instrument810.

Thedrive motor2038 can be the type of motor typically used in personal computer hard drives that is capable of rotating at about 7,200 RPM on precision bearings, such as a motor of a Seagate Model ST380011A hard drive (Seagate Technology, Scotts Valley, Calif.) or similar motor. In one embodiment, thedrive spindle2034 may be rotated at 6,000 rpm, which yields approximately 2,000 G's for a rotor having a 2.5 inch (64 millimeter) radius. In another embodiment, thedrive spindle2034 may be rotated at speeds of approximately 7,200 rpm. The rotational speed of thedrive spindle2034 can be selected to achieve the desired centrifugal force applied to a sample carried by therotor2020.

Themain instrument810 includes amain housing2049 that defines a chamber sized to accommodate afilter wheel assembly2300 including afilter drive motor2320 andfilter wheel2310 of theanalyte detection system1700. Themain housing2049 defines a detection system opening3001 configured to receive an analytedetection system housing2070. The illustrated analytedetection system housing2070 extends or projects outwardly from thehousing2049.

Themain instrument810 ofFIGS. 23C and 23E includes abubble sensor unit321, apump2619 in the form of aperistaltic pump roller2620aand aroller support2620b, and

valves

323a,323b. The illustrated

valves

323a,323bare pincher pairs, although other types of valves can be used. When thecassette820 is installed, these components can engage components of afluid handling network2600 of thecassette820, as will be discussed in greater detail below.

With continued reference toFIG. 28, the analytedetection system housing2070 surrounds and houses some of the internal components of theanalyte detection system1700. Theelongate slot2074 extends downwardly from anupper face2072 of thehousing2070. Theelongated slot2074 is sized and dimensioned so as to receive a portion of therotor2020. When therotor2020 rotates, therotor2020 passes periodically through theelongated slot2074. When a sample element of therotor2020 is in thedetection region2080 defined by theslot2074, theanalyte detection system1700 can analyze material in the sample element.

Theanalyte detection system1700 can be a spectroscopic bodily fluid analyzer that preferably comprises anenergy source1720. Theenergy source1720 can generate an energy beam directed along a major optical axis X that passes through theslot2074 towards asample detector1745. Theslot2074 thus permits at least a portion of the rotor (e.g., theinterrogation region2091 orsample chamber2464 of the sample element2448) to be positioned on the optical axis X. To analyze a sample carried by thesample element2448, the sample element and sample can be positioned in thedetection region2080 on the optical axis X such that light emitted from thesource1720 passes through theslot2074 and the sample disposed within thesample element2448.

Theanalyte detection system1700 can also comprise one or more lenses positioned to transmit energy outputted from theenergy source1720. The illustratedanalyte detection system1700 ofFIG. 28 comprises afirst lens2084 and asecond lens2086. Thefirst lens2084 is configured to focus the energy from thesource1720 generally onto the sample element and material sample. Thesecond lens2086 is positioned between the sample element and thesample detector1745. Energy fromenergy source1720 passing through the sample element can subsequently pass through thesecond lens2086. Athird lens2090 is preferably positioned between abeam splitter2093 and areference detector2094. Thereference detector2094 is positioned to receive energy from thebeam splitter2093.

Theanalyte detection system1700 can be used to determine the analyte concentration in the sample carried by therotor2020. Other types of detection or analysis systems can be used with the illustrated centrifuge apparatus or sample preparation unit. The fluid handling andanalysis apparatus140 is shown for illustrative purposes as being used in conjunction with theanalyte detection system1700, but neither the sample preparation unit nor analyte detection system are intended to be limited to the illustrated configuration, or to be limited to being used together.

To assemble the fluid handling andanalysis apparatus140, thecassette820 can be moved towards and installed onto themain instrument810, as indicated by thearrow2007 inFIG. 22A. As thecassette820 is installed, thedrive system2030 passes through the aperture2040 so that thespindle2034 mates with therotor2020. Simultaneously, the projecting portion of thedetection system1700 is received in thenotch2408 of thecassette820. When thecassette820 is installed on themain instrument810, theslot2410 of the notch2048 and theslot2074 of thedetection system1700 are aligned as shown inFIG. 22C. Accordingly, when thecassette820 andmain instrument810 are assembled, therotor2020 can rotate about theaxis2024 and pass through the

slots

2410,2074.

After thecassette820 is assembled with themain instrument810, a sample can be added to thesample element2448. Thecassette820 can be connected to an infusion source and a patient to place the system in fluid communication with a bodily fluid to be analyzed. Once thecassette820 is connected to a patient, a bodily fluid may be drawn from the patient into thecassette820. Therotor2020 is rotated to a vertical loading position wherein thesample element2448 is near thefluid interface2028 and thebypass element2452 is positioned within theslot2074 of thedetection system1700. Once therotor2020 is in the vertical loading position, the

pins

2542,2544 of thefluid interface2028 are positioned to mate with the

ports

2472,2474 of therotor2020. Thefluid interface2028 is then rotated upwardly until the

ends

2571,2573 of the

pins

2542,2544 are inserted into the

ports

2472,2474.

When thefluid interface2028 and thesample element2448 are thus engaged, sample fluid (e.g., whole blood) is pumped into thesample element2448. The sample can flow through thepin2544 into and through therotor channel2512 and thesample element channel2466, and into thesample chamber2464. As shown inFIG. 25C, thesample chamber2464 can be partially or completely filled with sample fluid. In some embodiments, the sample fills at least thesample chamber2464 and theinterrogation region2091 of thesample element2448. The sample can optionally fill at least a portion of the

sample element channels

2466,2468. The illustratedsample chamber2464 is filled with whole blood, although thesample chamber2464 can be filled with other substances. After thesample element2448 is filled with a desired amount of fluid, thefluid interface2028 can be moved to a lowered position to permit rotation of therotor2020.

Thecentrifuge drive system2030 can then spin therotor2020 and associatedsample element2448 as needed to separate one or more components of the sample. The separated component(s) of the sample may collect or be segregated in a section of the sample element for analysis. In the illustrated embodiment, thesample element2448 ofFIG. 25C is filled with whole blood prior to centrifuging. The centrifugal forces can be applied to the whole blood untilplasma2594 is separated from theblood cells2592. After centrifuging, theplasma2594 is preferably located in a radially inward portion of thesample element2448, including theinterrogation region2091. Theblood cells2592 collect in a portion of thesample chamber2464 which is radially outward of theplasma2594 andinterrogation region2091.

Therotor2020 can then be moved to a vertical analysis position wherein thesample element2448 is disposed within theslot2074 and aligned with thesource1720 and thesample detector1745 on the major optical axis X. When therotor2020 is in the analysis position, theinterrogation portion2091 is preferably aligned with the major optical axis X of thedetection system1700. Theanalyte detection system1700 can analyze the sample in thesample element2448 using spectroscopic analysis techniques as discussed elsewhere herein.

After the sample has been analyzed, the sample can be removed from thesample element2448. The sample may be transported to a waste receptacle so that thesample element2448 can be reused for successive sample draws and analyses. Therotor2020 is rotated from the analysis position back to the vertical loading position. To empty thesample element2448, thefluid interface2028 can again engage thesample element2448 to flush thesample element2448 with fresh fluid (either a new sample of body fluid, or infusion fluid). Thefluid interface2028 can be rotated to mate the

pins

2542,2544 with the

ports

2472,2474 of therotor2020. Thefluid interface2028 can pump a fluid through one of the

pins

2542,2544 until the sample is flushed from thesample element2448. Various types of fluids, such as infusion liquid, air, water, and the like, can be used to flush thesample element2448. After thesample element2448 has been flushed, thesample element2448 can once again be filled with another sample.

In an alternative embodiment, thesample element2448 may be removed from therotor2020 and replaced after each separate analysis, or after a certain number of analyses. Once the patient care has terminated, the fluid passageways or conduits may be disconnected from the patient and thesample cassette820 which has come into fluid contact with the patient's bodily fluid may be disposed of or sterilized for reuse. Themain instrument810, however, has not come into contact with the patient's bodily fluid at any point during the analysis and therefore can readily be connected to a newfluid handling cassette820 and used for the analysis of a subsequent patient.

Therotor2020 can be used to provide a fluid flow bypass. To facilitate a bypass flow, therotor2020 is first rotated to the vertical analysis/bypass position wherein thebypass element2452 is near thefluid interface2028 and thesample element2448 is in theslot2074 of theanalyte detection system1700. Once therotor2020 is in the vertical analysis/bypass position, the

pins

2542,2544 can mate with the

ports

2572,2574 of therotor2020. In the illustrated embodiment, thefluid interface2028 is rotated upwardly until the

ends

2571,2573 of the

pins

2542,2544 are inserted into the

ports

2572,2574. Thebypass element2452 can then provide a completed fluid circuit so that fluid can flow through one of the

pins

2542,2544 into thebypass element2452, through thebypass element2452, and then through the

other pin

2542,2544. Thebypass element2452 can be utilized in this manner to facilitate the flushing or sterilizing of a fluid system connected to thecassette820.

As shown inFIG. 23B, thecassette820 preferably includes thefluid handling network2600 which can be employed to deliver fluid to thesample element2448 in therotor2020 for analysis. Themain instrument810 has a number of components that can, upon installation of thecassette820 on themain instrument810, extend through openings in thefront face2045 ofcassette820 to engage and interact with components of thefluid handling network2600, as detailed below.

Thefluid handling network2600 of the fluid handling andanalysis apparatus140 includes thepassageway111 which extends from theconnector120 toward and through thecassette820 until it becomes thepassageway112, which extends from thecassette820 to thepatient connector110. Aportion111aof thepassageway111 extends across anopening2613 in thefront face2045 of thecassette820. When thecassette820 is installed on themain instrument810, theroller pump2619 engages theportion111a, which becomes situated between theimpeller2620aand theimpeller support2620b(seeFIG. 23C).

Thefluid handling network2600 also includespassageway113 which extends from thepatient connector110 towards and into thecassette820. After entering thecassette820, thepassageway113 extends across anopening2615 in thefront face2045 to allow engagement of thepassageway113 with abubble sensor321 of themain instrument810, when thecassette820 is installed on themain instrument810. Thepassageway113 then proceeds to theconnector2532 of thefluid interface2028, which extends thepassageway113 to thepin2544. Fluid drawn from the patient into thepassageway113 can thus flow into and through thefluid interface2028, to thepin2544. The drawn body fluid can further flow from thepin2544 and into thesample element2448, as detailed above.

Apassageway2609 extends from theconnector2530 of thefluid interface2028 and is thus in fluid communication with thepin2542. Thepassageway2609 branches to form thewaste line324 and thepump line327. Thewaste line324 passes across anopening2617 in thefront face2045 and extends to thewaste receptacle325. Thepump line327 passes across anopening2619 in thefront face2045 and extends to thepump328. When thecassette820 is installed on themain instrument810, the

pinch valves

323a,323bextend through the

openings

2617,2619 to engage the

lines

324,327, respectively.

Thewaste receptacle325 is mounted to thefront face2045. Waste fluid passing from thefluid interface2028 can flow through the

passageways

2609,324 and into thewaste receptacle325. Once thewaste receptacle325 is filled, thecassette820 can be removed from themain instrument810 and discarded. Alternatively, the filledwaste receptacle325 can be replaced with anempty waste receptacle325.

Thepump328 can be a displacement pump (e.g., a syringe pump). Apiston control2645 can extend over at least a portion of anopening2621 in thecassette face2045 to allow engagement with anactuator2652 when thecassette820 is installed on themain instrument810. When thecassette820 is installed, the actuator2652 (FIG. 23E) of themain instrument810 engages thepiston control2645 of thepump328 and can displace thepiston control2645 for a desired fluid flow.

It will be appreciated that, upon installing thecassette820 ofFIG. 23A on themain instrument810 ofFIG. 23E, there is formed (as shown inFIG. 23E) a fluid circuit similar to that shown in thesampling unit200 inFIG. 3. This fluid circuit can be operated in a manner similar to that described above in connection with the apparatus ofFIG. 3 (e.g., in accordance with the methodology illustrated inFIGS. 7A-7J and Table 1).

FIG. 24A depicts another embodiment of afluid handling network2700 that can be employed in thecassette820. Thefluid handling network2700 can be generally similar in structure and function to thenetwork2600 ofFIG. 23B, except as detailed below. Thenetwork2700 includes thepassageway111 which extends from theconnector120 toward and through thecassette820 until it becomes thepassageway112, which extends from thecassette820 to thepatient connector110. Aportion111aof thepassageway111 extends across anopening2713 in thefront face2745 of thecassette820. When thecassette820 is installed on themain instrument810, aroller pump2619 of themain instrument810 ofFIG. 24B can engage theportion111ain a manner similar to that described above with respect toFIGS. 23B-23C. Thepassageway113 extends from thepatient connector110 towards and into thecassette820. After entering thecassette820, thepassageway113 extends across anopening2763 in thefront face2745 to allow engagement with avalve2733 of themain instrument810. Awaste line2704 extends from thepassageway113 to thewaste receptacle325 and across anopening2741 in thefront face2745. Thepassageway113 proceeds to theconnector2532 of thefluid interface2028, which extends thepassageway113 to thepin2544. Thepassageway113 crosses anopening2743 in thefront face2745 to allow engagement of thepassageway113 with abubble sensor2741 of themain instrument810 ofFIG. 24B. When thecassette820 is installed on themain instrument810, thepinch valves2732,2733 extend through the

openings

2731,2743 to engage the

passageways

113,2704, respectively.

The illustratedfluid handling network2700 also includes apassageway2723 which extends between thepassageway111 and apassageway2727, which in turn extends between thepassageway2723 and thefluid interface2028. Thepassageway2727 extends across anopening2733 in thefront face2745. Apump line2139 extends from apump328 to the

passageways

2723,2727. When thecassette820 is installed on themain instrument810, the

pinch valves

2716,2718 extend through the

openings

2725,2733 in thefront face2745 to engage the

passageways

2723,2727, respectively.

It will be appreciated that, upon installing thecassette820 on the main instrument810 (as shown inFIG. 24A), there is formed a fluid circuit that can be operated in a manner similar to that described above, in connection with the apparatus ofFIGS. 9-10.

In view of the foregoing, it will be further appreciated that the various embodiments of the fluid handling and analysis apparatus140 (comprising amain instrument810 and cassette820) depicted inFIGS. 22A-28 can serve as the fluid handling andanalysis apparatus140 of any of thesampling systems100/300/500, or thefluid handling system10, depicted inFIGS. 1-5 herein. In addition, the fluid handling andanalysis apparatus140 ofFIGS. 22A-28 can, in certain embodiments, be similar to theapparatus140 ofFIGS. 1-2 or8-10, except as further described above.

Section V—Methods for Determining Analyte Concentrations from Sample Spectra

This section discusses a number of computational methods or algorithms which may be used to calculate the concentration of the analyte(s) of interest in the sample S, and/or to compute other measures that may be used in support of calculations of analyte concentrations. Any one or combination of the algorithms disclosed in this section may reside as program instructions stored in thememory212 so as to be accessible for execution by theprocessor210 of the fluid handling andanalysis apparatus140 oranalyte detection system334 to compute the concentration of the analyte(s) of interest in the sample, or other relevant measures.

Several disclosed embodiments are devices and methods for analyzing material sample measurements and for quantifying one or more analytes in the presence of interferents. Interferents can comprise components of a material sample being analyzed for an analyte, where the presence of the interferent affects the quantification of the analyte. Thus, for example, in the spectroscopic analysis of a sample to determine an analyte concentration, an interferent could be a compound having spectroscopic features that overlap with those of the analyte. The presence of such an interferent can introduce errors in the quantification of the analyte. More specifically, the presence of interferents can affect the sensitivity of a measurement technique to the concentration of analytes of interest in a material sample, especially when the system is calibrated in the absence of, or with an unknown amount of, the interferent.

Independently of or in combination with the attributes of interferents described above, interferents can be classified as being endogenous (i.e., originating within the body) or exogenous (i.e., introduced from or produced outside the body). As example of these classes of interferents, consider the analysis of a blood sample (or a blood component sample or a blood plasma sample) for the analyte glucose. Endogenous interferents include those blood components having origins within the body that affect the quantification of glucose, and may include water, hemoglobin, blood cells, and any other component that naturally occurs in blood. Exogenous interferents include those blood components having origins outside of the body that affect the quantification of glucose, and can include items administered to a person, such as medicaments, drugs, foods or herbs, whether administered orally, intravenously, topically, etc.

Independently of or in combination with the attributes of interferents described above, interferents can comprise components which are possibly but not necessarily present in the sample type under analysis. In the example of analyzing samples of blood or blood plasma drawn from patients who are receiving medical treatment, a medicament such as acetaminophen is possibly, but not necessarily present in this sample type. In contrast, water is necessarily present in such blood or plasma samples.

To facilitate an understanding of the inventions, embodiments are discussed herein where one or more analyte concentrations are obtained using spectroscopic measurements of a sample at wavelengths including one or more wavelengths that are identified with the analyte(s). The embodiments disclosed herein are not meant to limit, except as claimed, the scope of certain disclosed inventions which are directed to the analysis of measurements in general.

As an example, certain disclosed methods are used to quantitatively estimate the concentration of one specific compound (an analyte) in a mixture from a measurement, where the mixture contains compounds (interferents) that affect the measurement. Certain disclosed embodiments are particularly effective if each analyte and interferent component has a characteristic signature in the measurement, and if the measurement is approximately affine (i.e., includes a linear component and an offset) with respect to the concentration of each analyte and interferent. In one embodiment, a method includes a calibration process including an algorithm for estimating a set of coefficients and an offset value that permits the quantitative estimation of an analyte. In another embodiment, there is provided a method for modifying hybrid linear algorithm (HLA) methods to accommodate a random set of interferents, while retaining a high degree of sensitivity to the desired component. The data employed to accommodate the random set of interferents are (a) the signatures of each of the members of the family of potential additional components and (b) the typical quantitative level at which each additional component, if present, is likely to appear.

Certain methods disclosed herein are directed to the estimation of analyte concentrations in a material sample in the possible presence of an interferent. In certain embodiments, any one or combination of the methods disclosed herein may be accessible andexecutable processor210 ofsystem334.Processor210 may be connected to a computer network, and data obtained fromsystem334 can be transmitted over the network to one or more separate computers that implement the methods. The disclosed methods can include the manipulation of data related to sample measurements and other information supplied to the methods (including, but not limited to, interferent spectra, sample population models, and threshold values, as described subsequently). Any or all of this information, as well as specific algorithms, may be updated or changed to improve the method or provide additional information, such as additional analytes or interferents.

Certain disclosed methods generate a “calibration constant” that, when multiplied by a measurement, produces an estimate of an analyte concentration. Both the calibration constant and measurement can comprise arrays of numbers. The calibration constant is calculated to minimize or reduce the sensitivity of the calibration to the presence of interferents that are identified as possibly being present in the sample. Certain methods described herein generate a calibration constant by: 1) identifying the presence of possible interferents; and 2) using information related to the identified interferents to generate the calibration constant. These certain methods do not require that the information related to the interferents includes an estimate of the interferent concentration—they merely require that the interferents be identified as possibly present. In one embodiment, the method uses a set of training spectra each having known analyte concentration(s) and produces a calibration that minimizes the variation in estimated analyte concentration with interferent concentration. The resulting calibration constant is proportional to analyte concentration(s) and, on average, is not responsive to interferent-concentrations.

In one embodiment, it is not required (though not prohibited either) that the training spectra include any spectrum from the individual whose analyte concentration is to be determined. That is, the term “training” when used in reference to the disclosed methods does not require training using measurements from the individual whose analyte concentration will be estimated (e.g., by analyzing a bodily fluid sample drawn from the individual).

Several terms are used herein to describe the estimation process. As used herein, the term “Sample Population” is a broad term and includes, without limitation, a large number of samples having measurements that are used in the computation of a calibration—in other words, used to train the method of generating a calibration. For an embodiment involving the spectroscopic determination of glucose concentration, the Sample Population measurements can each include a spectrum (analysis measurement) and a glucose concentration (analyte measurement). In one embodiment, the Sample Population measurements are stored in a database, referred to herein as a “Population Database.”

The Sample Population may or may not be derived from measurements of material samples that contain interferents to the measurement of the analyte(s) of interest. One distinction made herein between different interferents is based on whether the interferent is present in both the Sample Population and the sample being measured, or only in the sample. As used herein, the term “Type-A interferent” refers to an interferent that is present in both the Sample Population and in the material sample being measured to determine an analyte concentration. In certain methods it is assumed that the Sample Population includes only interferents that are endogenous, and does not include any exogenous interferents, and thus Type-A interferents are endogenous. The number of Type-A interferents depends on the measurement and analyte(s) of interest, and may number, in general, from zero to a very large number. The material sample being measured, for example sample S, may also include interferents that are not present in the Sample Population. As used herein, the term “Type-B interferent” refers to an interferent that is either: 1) not found in the Sample Population but that is found in the material sample being measured (e.g., an exogenous interferent), or 2) is found naturally in the Sample Population, but is at abnormally high concentrations in the material sample (e.g., an endogenous interferent). Examples of a Type-B exogenous interferent may include medications, and examples of Type-B endogenous interferents may include urea in persons suffering from renal failure. In the example of mid-IR spectroscopic absorption measurement of glucose in blood, water is found in all blood samples, and is thus a Type-A interferent. For a Sample Population made up of individuals who are not taking intravenous drugs, and a material sample taken from a hospital patient who is being administered a selected intravenous drug, the selected drug is a Type-B interferent.

In one embodiment, a list of one or more possible Type-B Interferents is referred to herein as forming a “Library of Interferents,” and each interferent in the library is referred to as a “Library Interferent.” The Library Interferents include exogenous interferents and endogenous interferents that may be present in a material sample due, for example, to a medical condition causing abnormally high concentrations of the endogenous interferent.

In addition to components naturally found in the blood, the ingestion or injection of some medicines or illicit drugs can result in very high and rapidly changing concentrations of exogenous interferents. This results in problems in measuring analytes in blood of hospital or emergency room patients. An example of overlapping spectra of blood components and medicines is illustrated inFIG. 29 as the absorption coefficient at the same concentration and optical pathlength of pure glucose and three spectral interferents, specifically mannitol (chemical formula: hexane-1,2,3,4,5,6-hexaol), N acetyl L cysteine, dextran, and procainamide (chemical formula: 4-amino-N-(2-diethylaminoethyl)benzamid).FIG. 30 shows the logarithm of the change in absorption spectra from a Sample Population blood composition as a function of wavelength for blood containing additional likely concentrations of components, specifically, twice the glucose concentration of the Sample Population and various amounts of mannitol, N acetyl L cysteine, dextran, and procainamide. The presence of these components is seen to affect absorption over a wide range of wavelengths. It can be appreciated that the determination of the concentration of one species without a priori knowledge or independent measurement of the concentration of other species is problematic.

One method for estimating the concentration of an analyte in the presence of interferents is presented inflowchart3100 ofFIG. 31 as a first step (Block3110) where a measurement of a sample is obtained, a second step (Block3120), where the obtained measurement data is analyzed to identify possible interferents to the analyte, a third step (Block3130) where a model is generated for predicting the analyte concentration in the presence of the identified possible interferents, and a fourth step (Block3140) where the model is used to estimate the analyte concentration in the sample from the measurement. Preferably the step ofBlock3130 generates a model where the error is minimized for the presence of the identified interferents that are not present in a general population of which the sample is a member.

The method Blocks3110,3120,3130, and3140 may be repeatedly performed for each analyte whose concentration is required. If one measurement is sensitive to two or more analytes, then the methods of

Blocks

3120,3130, and3140 may be repeated for each analyte. If each analyte has a separate measurement, then the methods of

Blocks

3110,3120,3130, and3140 maybe repeated for each analyte.

An embodiment of the method offlowchart3100 for the determination of an analyte from spectroscopic measurements will now be discussed. Further, this embodiment will estimate the amount of glucose concentration in blood sample S, without limit to the scope of the inventions disclosed herein. In one embodiment, the measurement ofBlock3110 is an absorbance spectrum, C_s(λ_i), of a measurement sample S that has, in general, one analyte of interest, glucose, and one or more interferents. In one embodiment, the methods include generating a calibration constant κ(λ_i) that, when multiplied by the absorbance spectrum C_s(λ_i), provides an estimate, g_est, of the glucose concentration g_s.

As described subsequently, one embodiment ofBlock3120 includes a statistical comparison of the absorbance spectrum of sample S with a spectrum of the Sample Population and combinations of individual Library Interferent spectra. After the analysis ofBlock3120, a list of Library Interferents that are possibly contained in sample S has been identified and includes, depending on the outcome of the analysis ofBlock3120, either no Library Interferents, or one or more Library Interferents.Block3130 then generates a large number of spectra using the large number of spectra of the Sample Population and their respective known analyte concentrations and known spectra of the identified Library Interferents.Block3130 then uses the generated spectra to generate a calibration constant matrix to convert a measured spectrum to an analyte concentration that is the least sensitive to the presence of the identified Library Interferents.Block3140 then applies the generated calibration constant to predict the glucose concentration in sample S.

As indicated inBlock3110, a measurement of a sample is obtained. For illustrative purposes, the measurement, C_s(λ_i), is assumed to be a plurality of measurements at different wavelengths, or analyzed measurements, on a sample indicating the intensity of light that is absorbed by sample S. It is to be understood that spectroscopic measurements and computations may be performed in one or more domains including, but not limited to, the transmittance, absorbance and/or optical density domains. The measurement C_s(λ_i) is an absorption, transmittance, optical density or other spectroscopic measurement of the sample at selected wavelength or wavelength bands. Such measurements may be obtained, for example, usinganalyte detection system334. In general, sample S contains Type-A interferents, at concentrations preferably within the range of those found in the Sample Population.

In one embodiment, absorbance measurements are converted to pathlength normalized measurements. Thus, for example, the absorbance is converted to optical density by dividing the absorbance by the optical pathlength, L, of the measurement. In one embodiment, the pathlength L is measured from one or more absorption measurements on known compounds. Thus, in one embodiment, one or more measurements of the absorption through a sample S of water or saline solutions of known concentration are made and the pathlength, L, is computed from the resulting absorption measurement(s). In another embodiment, absorption measurements are also obtained at portions of the spectrum that are not appreciably affected by the analytes and interferents, and the analyte measurement is supplemented with an absorption measurement at those wavelengths.

Some methods are “pathlength insensitive,” in that they can be used even when the precise pathlength is not known beforehand. The sample can be placed in the

sample chamber

903 or2464,

sample element

1730 or2448, or in a cuvette or other sample container. Electromagnetic radiation (in the mid-infrared range, for example) can be emitted from a radiation source so that the radiation travels through the sample chamber. A detector can be positioned where the radiation emerges, on the other side of the sample chamber from the radiation source, for example. The distance the radiation travels through the sample can be referred to as a “pathlength.” In some embodiments, the radiation detector can be located on the same side of the sample chamber as the radiation source, and the radiation can reflect off one or more internal walls of the sample chamber before reaching the detector.

As discussed above, various substances can be inserted into the sample chamber. For example, a reference fluid such as water or saline solution can be inserted, in addition to a sample or samples containing an analyte or analytes. In some embodiments, a saline reference fluid is inserted into the sample chamber and radiation is emitted through that reference fluid. The detector measures the amount and/or characteristics of the radiation that passes through the sample chamber and reference fluid without being absorbed or reflected. The measurement taken using the reference fluid can provide information relating to the pathlength traveled by the radiation. For example, data may already exist from previous measurements that have been taken under similar circumstances. That is, radiation can be emitted previously through sample chambers with various known pathlengths to establish reference data that can be arranged in a “look-up table,” for example. With reference fluid in the sample chamber, a one-to-one correspondence can be experimentally established between various detector readings and various pathlengths, respectively. This correspondence can be recorded in the look-up table, which can be recorded in a computer database or in electronic memory, for example.

One method of determining the radiation pathlength can be accomplished with a thin, empty sample chamber. In particular, this approach can determine the thickness of a narrow sample chamber or cell with two reflective walls. (Because the chamber will be filled with a sample, this same thickness corresponds to the “pathlength” radiation will travel through the sample). A range of radiation wavelengths can be emitted in a continuous manner through the cell or sample chamber. The radiation can enter the cell and reflect off the interior cell walls, bouncing back and forth between those walls one or multiple times before exiting the cell and passing into the radiation detector. This can create a periodic interference pattern or “fringe” with repeating maxima and minima. This periodic pattern can be plotted where the horizontal axis is a range of wavelengths and the vertical axis is a range of transmittance, measured as a percentage of total transmittance, for example. The maxima occur when the radiation reflected off of the two internal surfaces of the cell has traveled a distance that is an integral multiple N of the wavelength of the radiation that was transmitted without reflection. Constructive interference occurs whenever the wavelength is equal to 2b/N, where “b” is the thickness (or pathlength) of the cell. Thus, if ΔN is the number of maxima in this fringe pattern for a given range of wavelengths λ₁-λ₂, then the thickness of the cell b is provided by the following relation: b=ΔN/2(λ₁-λ₂). This approach can be especially useful when the refractive index of the material within the sample chamber or fluid cell is not the same as the refractive index of the walls of the cell, because this condition improves reflection.

Once the pathlength has been determined, it can be used to calculate or determine a reference value or a reference spectrum for the interferents (such as protein or water) that may be present in a sample. For example, both an analyte such as glucose and an interferent such as water may absorb radiation at a given wavelength. When the source emits radiation of that wavelength and the radiation passes through a sample containing both the analyte and the interferent, both the analyte and the interferent absorb the radiation. The total absorption reading of the detector is thus fully attributable to neither the analyte nor the interferent, but a combination of the two. However, if data exists relating to how much radiation of a given wavelength is absorbed by a given interferent when the radiation passes through a sample with a given pathlength, the contribution of the interferent can be subtracted from the total reading of the detector and the remaining value can provide information regarding concentration of the analyte in the sample. A similar approach can be taken for a whole spectrum of wavelengths. If data exists relating to how much radiation is absorbed by an interferent over a range of wavelengths when the radiation passes through a sample with a given pathlength, the interferent absorbance spectrum can be subtracted from the total absorbance spectrum, leaving only the analyte's absorbance spectrum for that range of wavelengths. If the interferent absorption data is taken for a range of possible pathlengths, it can be helpful to determine the pathlength of a particular sample chamber first so that the correct data can be found for samples measured in that sample chamber.

This same process can be applied iteratively or simultaneously for multiple interferents and/or multiple analytes. For example, the water absorbance spectrum and the protein absorbance spectrum can both be subtracted to leave behind the glucose absorbance spectrum.

The pathlength can also be calculated using an isosbestic wavelength. An isosbestic wavelength is one at which all components of a sample have the same absorbance. If the components (and their absorption coefficients) in a particular sample are known, and one or multiple isosbestic wavelengths are known for those particular components, the absorption data collected by the radiation detector at those isosbestic wavelengths can be used to calculate the pathlength. This can be advantageous because the needed information can be obtained from multiple readings of the absorption detector that are taken at approximately the same time, with the same sample in place in the sample chamber. The isosbestic wavelength readings are used to determine pathlength, and other selected wavelength readings are used to determine interferent and/or analyte concentration. Thus, this approach is efficient and does not require insertion of a reference fluid in the sample chamber.

In some embodiments, a method of determining concentration of an analyte in a sample can include inserting a fluid sample into a sample container, emitting radiation from a source through the container and the fluid sample, obtaining total sample absorbance data by measuring the amount of radiation that reaches the detector, subtracting the correct interferent absorbance value or spectrum from the total sample absorbance data, and using the remaining absorbance value or spectrum to determine concentration of an analyte in the fluid sample. The correct interferent absorbance value can be determined using the calculated pathlength.

The concentration of an analyte in a sample can be calculated using the Beer-Lambert law (or Beer's Law) as follows: If T is transmittance, A is absorbance, P₀is initial radiant power directed toward a sample, and P is the power that emerges from the sample and reaches a detector, then T=P/P₀, and A=−log T=log(P₀/P). Absorbance is directly proportional to the concentration (c) of the light-absorbing species in the sample, also known as an analyte or an interferent. Thus, if e is the molar absorptivity (1/M 1/cm), b is the path length (cm), and c is the concentration (M), Beer's Law can be expressed as follows: A=e b c. Thus, c=A/(e b).

Referring once again toflowchart3100, the next step is to determine which Library Interferents are present in the sample. In particular,Block3120 indicates that the measurements are analyzed to identify possible interferents. For spectroscopic measurements, it is preferred that the determination is made by comparing the obtained measurement to interferent spectra in the optical density domain. The results of this step provide a list of interferents that may, or are likely to, be present in the sample. In one embodiment, several input parameters are used to estimate a glucose concentration g_estfrom a measured spectrum, C_s. The input parameters include previously gathered spectrum measurement of samples that, like the measurement sample, include the analyte and combinations of possible interferents from the interferent library; and spectrum and concentration ranges for each possible interferent. More specifically, the input parameters are:

- Library of Interferent Data: Library of Interferent Data includes, for each of “M” interferents, the absorption spectrum of each interferent, IF={IF₁, IF₂, . . . , IF_M}, where m=1, 2, . . . , M; and a maximum concentration for each interferent, Tmax={Tmax₁, Tmax₂, . . . , Tmax_M}; and
- Sample Population Data: Sample Population Data includes individual spectra of a statistically large population taken over the same wavelength range as the sample spectrum, Cs_i, and an analyte concentration corresponding to each spectrum. As an example, if there are N Sample Population spectra, then the spectra can be represented as C={C₁, C₂, . . . , C_N}, where n=1, 2, . . . , N, and the analyte concentration corresponding to each spectrum can be represented as g={g₁, g₂, . . . , g_N}.

Preferably, the Sample Population does not have any of the M interferents present, and the material sample has interferents contained in the Sample Population and none or more of the Library Interferents. Stated in terms of Type-A and Type-B interferents, the Sample Population has Type-A interferents and the material sample has Type-A and may have Type-B interferents. The Sample Population Data are used to statistically quantify an expected range of spectra and analyte concentrations. Thus, for example, for a

system

10 or334 used to determine glucose in blood of a person having unknown spectral characteristics, the spectral measurements are preferably obtained from a statistical sample of the population.

The following discussion, which is not meant to limit the scope of the present disclosure, illustrates embodiments for measuring more than one analyte using spectroscopic techniques. If two or more analytes have non-overlapping spectral features, then a first embodiment is to obtain a spectrum corresponding to each analyte. The measurements may then be analyzed for each analyte according to the method offlowchart3100. An alternative embodiment for analytes having non-overlapping features, or an embodiment for analytes having overlapping features, is to make one measurement comprising the spectral features of the two or more analytes. The measurement may then be analyzed for each analyte according to the method offlowchart3100. That is, the measurement is analyzed for each analyte, with the other analytes considered to be interferents to the analyte being analyzed for.

Interferent Determination

One embodiment of the method ofBlock3120 is shown in greater detail with reference to the flowchart ofFIG. 32. The method includes forming a statistical Sample Population model (Block3210), assembling a library of interferent data (Block3220), comparing the obtained measurement and statistical Sample Population model with data for each interferent from an interferent library (Block3230), performing a statistical test for the presence of each interferent from the interferent library (Block3240), and identifying each interferent passing the statistical test as a possible Library Interferent (Block3250). The steps ofBlock3220 can be performed once or can be updated as necessary. The steps of

Blocks

3230,3240, and3250 can either be performed sequentially for all interferents of the library, as shown, or alternatively, be repeated sequentially for each interferent.

One embodiment of each of the methods of

Blocks

3210,3220,3230,3240, and3250 are now described for the example of identifying Library Interferents in a sample from a spectroscopic measurement using Sample Population Data and a Library of Interferent Data, as discussed previously. Each Sample Population spectrum includes measurements (e.g., of optical density) taken on a sample in the absence of any Library Interferents and has an associated known analyte concentration. A statistical Sample Population model is formed (Block3210) for the range of analyte concentrations by combining all Sample Population spectra to obtain a mean matrix and a covariance matrix for the Sample Population. Thus, for example, if each spectrum at n different wavelengths is represented by an n×1 matrix, C, then the mean spectrum, μ, is a n×1 matrix with the (e.g., optical density) value at each wavelength averaged over the range of spectra, and the covariance matrix, V, is the expected value of the deviation between C and μ as V=E((C−μ) (C−μ)^T). The matrices p and V are one model that describes the statistical distribution of the Sample Population spectra.

In another step, Library Interferent information is assembled (Block3220). A number of possible interferents are identified, for example as a list of possible medications or foods that might be ingested by the population of patients at issue or measured by

system

10 or334, and their spectra (in the absorbance, optical density, or transmission domains) are obtained. In addition, a range of expected interferent concentrations in the blood, or other expected sample material, are estimated. Thus, each of M interferents has spectrum IF and maximum concentration Tmax. This information is preferably assembled once and is accessed as needed.

The obtained measurement data and statistical Sample Population model are next compared with data for each interferent from the interferent library (Block3230) to perform a statistical test (Block3240) to determine the identity of any interferent in the mixture (Block3250). This interferent test will first be shown in a rigorous mathematical formulation, followed by a discussion ofFIGS. 33A and 33B which illustrates the method.

Mathematically, the test of the presence of an interferent in a measurement proceeds as follows. The measured optical density spectrum, C_s, is modified for each interferent of the library by analytically subtracting the effect of the interferent, if present, on the measured spectrum. More specifically, the measured optical density spectrum, C_s, is modified, wavelength-by-wavelength, by subtracting an interferent optical density spectrum. For an interferent, M, having an absorption spectrum per unit of interferent concentration, IF_M, a modified spectrum is given by C′_s(T)=C_s−IF_MT, where T is the interferent concentration, which ranges from a minimum value, Tmin, to a maximum value Tmax. The value of Tmin may be zero or, alternatively, be a value between zero and Tmax, such as some fraction of Tmax.

Next, the Mahalanobis distance (MD) between the modified spectrum C′_s(T) and the statistical model (μ, V) of the Sample Population spectra is calculated as:
MD²(C_s−(T t),μ; ρ_s)=(C_s−(T IF_m)−μ)^TV⁻¹(C_s−(T IF_m)−μ) Eq. (1)

The test for the presence of interferent IF is to vary T from Tmin to Tmax (i.e., evaluate C′_s(T) over a range of values of T) and determine whether the minimum MD in this interval is in a predetermined range. Thus for example, one could determine whether the minimum MD in the interval is sufficiently small relative to the quantiles of a χ²random variable with L degrees of freedom (L=number of wavelengths).

FIG. 33A is agraph3300 illustrating the steps of

Blocks

3230 and3240. The axes ofgraph3300, OD_iand OD_j, are used to plot optical densities at two of the many wavelengths at which measurements are obtained. Thepoints3301 are the measurements in the Sample Population distribution.Points3301 are clustered within an ellipse that has been drawn to encircle the majority of points.Points3301 insideellipse3302 represent measurements in the absence of Library Interferents.Point3303 is the sample measurement. Presumably,point3303 is outside of the spread ofpoints3301 due the presence of one or more Library Interferents.

Lines

3304,3307, and3309 indicate the measurement ofpoint3303 as corrected for increasing concentration, T, of three different Library Interferents over the range from Tmin to Tmax. The three interferents of this example are referred to asinterferent #1,interferent #2, andinterferent #3. Specifically,

lines

3304,3307, and3309 are obtained by subtracting from the sample measurement an amount T of a Library Interferent (interferent #1,interferent #2, andinterferent #3, respectively), and plotting the corrected sample measurement for increasing T.

FIG. 33B is a graph further illustrating the method ofFIG. 32. In the graph ofFIG. 33B, the squared Mahalanobis distance, MD²has been calculated and plotted as a function of t for

lines

3304,3307, and3309. Referring toFIG. 33A,line3304 reflects decreasing concentrations ofinterferent #1 and only slightly approaches points3301. The value of MD²ofline3304, as shown inFIG. 33B, decreases slightly and then increases with decreasinginterferent #1 concentration.

Referring toFIG. 33A,line3307 reflects decreasing concentrations ofinterferent #2 and approaches or passes throughmany points3301. The value of MD²ofline3307, as shown inFIG. 33B, shows a large decrease at someinterferent #2 concentration, then increases. Referring toFIG. 33A,line3309 has decreasing concentrations ofinterferent #3 and approaches or passes through evenmore points3303. The value of MD²ofline3309, as shown inFIG. 33B, shows a still larger decrease at someinterferent #3 concentration.

In one embodiment, a threshold level of MD²is set as an indication of the presence of a particular interferent. Thus, for example,FIG. 33B shows a line labeled “original spectrum” indicating MD²when no interferents are subtracted from the spectrum, and a line labeled “95% Threshold”, indicating the 95% quantile for the chi²distribution with L degrees of freedom (where L is the number of wavelengths represented in the spectra). This level is the value which should exceed 95% of the values of the MD²metric; in other words, values at this level are uncommon, and those far above it should be quite rare. Of the three interferents represented inFIGS. 33A and 33B, onlyinterferent #3 has a value of MD²below the threshold. Thus, this analysis of the sample indicates thatinterferent #3 is the most likely interferent present in the sample.Interferent #1 has its minimum far above the threshold level and is extremely unlikely to be present;interferent #2 barely crosses the threshold, making its presence more likely thaninterferent #1, but still far less likely to be present thaninterferent #1.

As described subsequently, information related to the identified interferents is used in generating a calibration constant that is relatively insensitive to a likely range of concentration of the identified interferents. In addition to being used in certain methods described subsequently, the identification of the interferents may be of interest and may be provided in a manner that would be useful. Thus, for example, for a hospital based glucose monitor, identified interferents may be reported ondisplay141 or be transmitted to a hospital computer via communications link216.

Calibration Constant Generation Embodiments

Once Library Interferents are identified as being possibly present in the sample under analysis, a calibration constant for estimating the concentration of analytes in the presence of the identified interferents is generated (Block3130). More specifically, afterBlock3120, a list of possible Library Interferents is identified as being present. One embodiment of the steps ofBlock3120 are shown in the flowchart ofFIG. 34 asBlock3410, where synthesized Sample Population measurements are generated,Block3420, where the synthesized Sample Population measurements are partitioned in to calibration and test sets,Block3430, where the calibration are is used to generate a calibration constant,Block3440, where the calibration set is used to estimate the analyte concentration of the test set,Block3450 where the errors in the estimated analyte concentration of the test set is calculated, andBlock3460 where an average calibration constant is calculated.

One embodiment of each of the methods of

Blocks

3410,3420,3430,3440,3450, and3460 are now described for the example of using identifying interferents in a sample for generating an average calibration constant. As indicated inBlock3410, one step is to generate synthesized Sample Population spectra, by adding a random concentration of possible Library Interferents to each Sample Population spectrum. The spectra generated by the method ofBlock3410 are referred to herein as an Interferent-Enhanced Spectral Database, or IESD. The IESD can be formed by the steps illustrated inFIGS. 35-38, whereFIG. 35 is a schematic diagram3500 illustrating the generation of Randomly-Scaled Single Interferent Spectra, or RSIS;FIG. 36 is a graph3600 of the interferent scaling;FIG. 37 is a schematic diagram illustrating the combination of RSIS into Combination Interferent Spectra, or CIS; andFIG. 38 is a schematic diagram illustrating the combination of CIS and the Sample Population spectra into an IESD.

The first step inBlock3410 is shown inFIGS. 35 and 36. As shown schematically inflowchart3500 inFIG. 35, and in graph3600 inFIG. 36, a plurality of RSIS (Block3540) are formed by combinations of each previously identified Library Interferent having spectrum IF_m(Block3510), multiplied by the maximum concentration Tmax_m(Block3520) that is scaled by a random factor between zero and one (Block3530), as indicated by the distribution of the random number indicated in graph3600. In one embodiment, the scaling places the maximum concentration at the 95^thpercentile of a log-normal distribution to produce a wide range of concentrations with the distribution having a standard deviation equal to half of its mean value. The distribution of the random numbers in graph3600 are a log-normal distribution of μ=100, σ=50.

Once the individual Library Interferent spectra have been multiplied by the random concentrations to produce the RSIS, the RSIS are combined to produce a large population of interferent-only spectra, the CIS, as illustrated inFIG. 37. The individual RSIS are combined independently and in random combinations, to produce a large family of CIS, with each spectrum within the CIS consisting of a random combination of RSIS, selected from the full set of identified Library Interferents. The method illustrated inFIG. 37 produces adequate variability with respect to each interferent, independently across separate interferents.

The next step combines the CIS and replicates of the Sample Population spectra to form the IESD, as illustrated inFIG. 38. Since the Interferent Data and Sample Population spectra may have been obtained at different pathlengths, the CIS are first scaled (i.e., multiplied) to the same pathlength. The Sample Population database is then replicated M times, where M depends on the size of the database, as well as the number of interferents to be treated. The IESD includes M copies of each of the Sample Population spectra, where one copy is the original Sample Population Data, and the remaining M-1 copies each have an added random one of the CIS spectra. Each of the IESD spectra has an associated analyte concentration from the Sample Population spectra used to form the particular IESD spectrum.

In one embodiment, a 10-fold replication of the Sample Population database is used for 130 Sample Population spectra obtained from 58 different individuals and 18 Library Interferents. Greater spectral variety among the Library Interferent spectra requires a smaller replication factor, and a greater number of Library Interferents requires a larger replication factor.

The steps of

Blocks

3420,3430,3440, and3450 are executed to repeatedly combine different ones of the spectra of the IESD to statistically average out the effect of the identified Library Interferents. First, as noted inBlock3420, the IESD is partitioned into two subsets: a calibration set and a test set. As described subsequently, the repeated partitioning of the IESD into different calibration and test sets improves the statistical significance of the calibration constant. In one embodiment, the calibration set is a random selection of some of the IESD spectra and the test set are the unselected IESD spectra. In a preferred embodiment, the calibration set includes approximately two-thirds of the IESD spectra.

In an alternative embodiment, the steps of

Blocks

3420,3430,3440, and3450 are replaced with a single calculation of an average calibration constant using all available data.

Next, as indicted inBlock3430, the calibration set is used to generate a calibration constant for predicting the analyte concentration from a sample measurement. First an analyte spectrum is obtained. For the embodiment of glucose determined from absorption measurements, a glucose absorption spectrum is indicated as a_G. The calibration constant is then generated as follows. Using the calibration set having calibration spectra C={c₁, c₂, . . . , c_n} and corresponding glucose concentration values G={g₁, g₂, . . . , g_n}, then glucose-free spectra C′={c′₁, c′₂, . . . , c′_n} can be calculated as: c′_j=c_j−a_Gg_j. Next, the calibration constant, κ, is calculated from C′ and a_G, according to the following 5 steps:

- 1) C′ is decomposed into C′=A_C′ Δ_C′ B_C′, that is, a singular value decomposition, where the A-factor is an orthonormal basis of column space, or span, of C′;
- 2) A_C′ is truncated to avoid overfitting to a particular column rank r, based on the sizes of the diagonal entries of Δ (the singular values of C′). The selection of r involves a trade-off between the precision and stability of the calibration, with a larger r resulting in a more precise but less stable solution. In one embodiment, each spectrum C includes 25 wavelengths, and r ranges from 15 to 19;
- 3) The first r columns of A_C′ are taken as an orthonormal basis of span(C′);
- 4) The projection from the background is found as the product P_C′=A_C′ A_C′^T, that is the orthogonal projection onto the span of C′, and the complementary, or nulling projection P_C′^⊥=1−P_C′, which forms the projection onto the complementary subspace C′^⊥, is calculated; and
- 5) The calibration vector κ is then found by applying the nulling projection to the absorption spectrum of the analyte of interest: κ_RAW=P_C′^⊥ a_G, and normalizing: κ=κ_RAW/(κ_RAW, a_G), where the angle brackets <,> denote the standard inner (or dot) product of vectors. The normalized calibration constant produces a unit response for a unit a_Gspectral input for one particular calibration set.

Next, the calibration constant is used to estimate the analyte concentration in the test set (Block3440). Specifically, each spectrum of the test set (each spectrum having an associated glucose concentration from the Sample Population spectra used to generate the test set) is multiplied by the calibration vector K fromBlock3430 to calculate an estimated glucose concentration. The error between the calculated and known glucose concentration is then calculated (Block3450). Specifically, the measure of the error can include a weighted value averaged over the entire test set according to 1/rms².

Blocks

3420,3430,3440, and3450 are repeated for many different random combinations of calibration sets. Preferably,

Blocks

3420,3430,3440, and3450 are repeated are repeated hundreds to thousands of times. Finally, an average calibration constant is calculated from the calibration and error from the many calibration and test sets (Block3460). Specifically, the average calibration is computed as weighted average calibration vector. In one embodiment the weighting is in proportion to a normalized rms, such as the κ_ave=κ*rms²/Σ(rms²) for all tests.

With the last ofBlock3130 executed according toFIG. 34, the average calibration constant κ_aveis applied to the obtained spectrum (Block3140).

Accordingly, one embodiment of a method of computing a calibration constant based on identified interferents can be summarized as follows:

- 1. Generate synthesized Sample Population spectra by adding the RSIS to raw (interferent-free) Sample Population spectra, thus forming an Interferent Enhanced Spectral Database (IESD)—each spectrum of the IESD is synthesized from one spectrum of the Sample Population, and thus each spectrum of the IESD has at least one associated known analyte concentration
- 2. Separate the spectra of the IESD into a calibration set of spectra and a test set of spectra
- 3. Generate a calibration constant for the calibration set based on the calibration set spectra and their associated known correct analyte concentrations (e.g., using the matrix manipulation outlined in five steps above)
- 4. Use the calibration constant generated instep 3 to calculate the error in the corresponding test set as follows (repeat for each spectrum in the test set):
  - a. Multiply (the selected test set spectrum)×(average calibration constant generated in step 3) to generate an estimated glucose concentration
  - b. Evaluate the difference between this estimated glucose concentration and the known, correct glucose concentration associated with the selected test spectrum to generate an error associated with the selected test spectrum
- 5. Average the errors calculated instep 4 to arrive at a weighted or average error for the current calibration set—test set pair
- 6. Repeat steps 2 through 5 n times, resulting in n calibration constants and n average errors
- 7. Compute a “grand average” error from the n average errors and an average calibration constant from the n calibration constants (preferably weighted averages wherein the largest average errors and calibration constants are discounted), to arrive at a calibration constant which is minimally sensitive to the effect of the identified interferents

EXAMPLE 1

One example of certain methods disclosed herein is illustrated with reference to the detection of glucose in blood using mid-IR absorption spectroscopy. Table 2 lists 10 Library Interferents (each having absorption features that overlap with glucose) and the corresponding maximum concentration of each Library Interferent. Table 2 also lists a Glucose Sensitivity to Interferent without and with training. The Glucose Sensitivity to Interferent is the calculated change in estimated glucose concentration for a unit change in interferent concentration. For a highly glucose selective analyte detection technique, this value is zero. The Glucose Sensitivity to Interferent without training is the Glucose Sensitivity to Interferent where the calibration has been determined using the methods above without any identified interferents. The Glucose Sensitivity to Interferent with training is the Glucose Sensitivity to Interferent where the calibration has been determined using the methods above with the appropriately identified interferents. In this case, least improvement (in terms of reduction in sensitivity to an interferent) occurs for urea, seeing a factor of 6.4 lower sensitivity, followed by three with ratios from 60 to 80 in improvement. The remaining six all have seen sensitivity factors reduced by over 100, up to over 1600. The decreased Glucose Sensitivity to Interferent with training indicates that the methods are effective at producing a calibration constant that is selective to glucose in the presence of interferents.

TABLE 2


Rejection of 10 interfering substances

		Glucose	Glucose
		Sensitivity to	Sensitivity to
Library	Maximum	Interferent	Interferent
Interferent	Concentration	w/o training	w/training

Sodium Bicarbonate	103	0.330	0.0002
Urea	100	−0.132	0.0206
Magnesium Sulfate	0.7	1.056	−0.0016
Naproxen	10	0.600	−0.0091
Uric Acid	12	−0.557	0.0108
Salicylate	10	0.411	−0.0050
Glutathione	100	0.041	0.0003
Niacin	1.8	1.594	−0.0086
Nicotinamide	12.2	0.452	−0.0026
Chlorpropamide	18.3	0.334	0.0012

EXAMPLE 2

Another example illustrates the effect of the methods for 18 interferents. Table 3 lists of 18 interferents and maximum concentrations that were modeled for this example, and the glucose sensitivity to the interferent without and with training. The table summarizes the results of a series of 1000 calibration and test simulations that were performed both in the absence of the interferents, and with all interferents present.FIG. 39 shows the distribution of the R.M.S. error in the glucose concentration estimation for 1000 trials. While a number of substances show significantly less sensitivity (sodium bicarbonate, magnesium sulfate, tolbutamide), others show increased sensitivity (ethanol, acetoacetate), as listed in Table 3. The curves inFIG. 39 are for calibration set and the test set both without any interferents and with all 18 interferents. The interferent produces a degradation of performance, as can be seen by comparing the calibration or test curves ofFIG. 39. Thus, for example, the peaks appear to be shifted by about 2 mg/dL, and the width of the distributions is increased slightly. The reduction in height of the peaks is due to the spreading of the distributions, resulting in a modest degradation in performance.

TABLE 3


List of 18 Interfering Substances with maximum concentrations
and Sensitivity with respect to interferents, with/without training

		Glucose	Glucose
		Sensitivity	Sensitivity
		to Interferent	to
Library	Conc.	w/o	Interferent w/
Interferent	(mg/dL)	training	training

1	Urea	300	−0.167	−0.100
2	Ethanol	400.15	−0.007	−0.044
3	Sodium Bicarbonate	489	0.157	−0.093
4	Acetoacetate Li	96	0.387	0.601
5	Hydroxybutyric Acid	465	−0.252	−0.101
6	Magnesium Sulfate	29.1	2.479	0.023
7	Naproxen	49.91	0.442	0.564
8	Salicylate	59.94	0.252	0.283
9	Ticarcillin Disodium	102	−0.038	−0.086
10	Cefazolin	119.99	−0.087	−0.006
11	Chlorpropamide	27.7	0.387	0.231
12	Nicotinamide	36.6	0.265	0.366
13	Uric Acid	36	−0.641	−0.712
14	Ibuprofen	49.96	−0.172	−0.125
15	Tolbutamide	63.99	0.132	0.004
16	Tolazamide	9.9	0.196	0.091
17	Bilirubin	3	−0.391	−0.266
18	Acetaminophen	25.07	0.169	0.126

EXAMPLE 3

In a third example, certain methods disclosed herein were tested for measuring glucose in blood using mid-IR absorption spectroscopy in the presence of four interferents not normally found in blood (Type-B interferents) and that may be common for patients in hospital intensive care units (ICUs). The four Type-B interferents are mannitol, dextran, n-acetyl L cysteine, and procainamide.

Of the four Type-B interferents, mannitol and dextran have the potential to interfere substantially with the estimation of glucose: both are spectrally similar to glucose (seeFIG. 1), and the dosages employed in ICUs are very large in comparison to typical glucose levels. Mannitol, for example, may be present in the blood at concentrations of 2500 mg/dL, and dextran may be present at concentrations in excess of 5000 mg/dL. For comparison, typical plasma glucose levels are on the order of 100-200 mg/dL. The other Type-B interferents, n-acetyl L cysteine and procainamide, have spectra that are quite unlike the glucose spectrum.

FIGS. 40A, 40B,40C, and40D each have a graph showing a comparison of the absorption spectrum of glucose with different interferents taken using two different techniques: a Fourier Transform Infrared (FTIR) spectrometer having an interpolated resolution of 1 cm⁻¹(solid lines with triangles); and by 25 finite-bandwidth IR filters having a Gaussian profile and full-width half-maximum (FWHM) bandwidth of 28 cm⁻¹corresponding to a bandwidth that varies from 140 nm at 7.08 μm, up to 279 nm at 10 μm (dashed lines with circles). Specifically, the figures show a comparison of glucose with mannitol (FIG. 40A), with dextran (FIG. 40B), with n-acetyl L cysteine (FIG. 40C), and with procainamide (FIG. 40D), at a concentration level of 1 mg/dL and path length of 1 μm. The horizontal axis inFIGS. 40A-40D has units of wavelength in microns (μm), ranging from 7 μm to 10 μm, and the vertical axis has arbitrary units.

The central wavelength of the data obtained using filter is indicated inFIGS. 40A, 40B,40C, and40D by the circles along each dashed curve, and corresponds to the following wavelengths, in microns: 7.082, 7.158, 7.241, 7.331, 7.424, 7.513, 7.605, 7.704, 7.800, 7.905, 8.019, 8.150, 8.271, 8.598, 8.718, 8.834, 8.969, 9.099, 9.217, 9.346, 9.461, 9.579, 9.718, 9.862, and 9.990. The effect of the bandwidth of the filters on the spectral features can be seen inFIGS. 40A-40D as the decrease in the sharpness of spectral features on the solid curves and the relative absence of sharp features on the dashed curves.

FIG. 41 shows a graph of the blood plasma spectra for 6 blood samples taken from three donors in arbitrary units for a wavelength range from 7 μm to 10 μm, where the symbols on the curves indicate the central wavelengths of the 25 filters. The 6 blood samples do not contain any mannitol, dextran, n-acetyl L cysteine, and procainamide—the Type-B interferents of this Example, and are thus a Sample Population. Three donors (indicated as donor A, B, and C) provided blood at different times, resulting in different blood glucose levels, shown in the graph legend in mg/dL as measured using a YSI Biochemistry Analyzer (YSI Incorporated, Yellow Springs, Ohio). The path length of these samples, estimated at 36.3 μm by analysis of the spectrum of a reference scan of saline in the same cell immediately prior to each sample spectrum, was used to normalize these measurements. This quantity was taken into account in the computation of the calibration vectors provided, and the application of these vectors to spectra obtained from other equipment would require a similar pathlength estimation and normalization process to obtain valid results.

Next, random amounts of each Type-B interferent of this Example are added to the spectra to produce mixtures that, for example could make up an Interferent Enhanced Spectral. Each of the Sample Population spectra was combined with a random amount of a single interferent added, as indicated in Table 4, which lists an index number N, the Donor, the glucose concentration (GLU), interferent concentration (conc(IF)), and the interferent for each of 54 spectra. The conditions of Table 4 were used to form combined spectra including each of the 6 plasma spectra was combined with 2 levels of each of the 4 interferents.

TABLE 4


Interferent Enhanced Spectral Database for Example 3.

	N	Donor	GLU	conc(IF)	IF

1	A	157.7		N/A
2	A	382		N/A
3	B	122		N/A
4	B	477.3		N/A
5	C	199.7		N/A
6	C	399		N/A
7	A	157.7	1001.2	Mannitol
8	A	382	2716.5	Mannitol
9	A	157.7	1107.7	Mannitol
10	A	382	1394.2	Mannitol
11	B	122	2280.6	Mannitol
12	B	477.3	1669.3	Mannitol
13	B	122	1710.2	Mannitol
14	B	477.3	1113.0	Mannitol
15	C	199.7	1316.4	Mannitol
16	C	399	399.1	Mannitol
17	C	199.7	969.8	Mannitol
18	C	399	2607.7	Mannitol
19	A	157.7	8.8	N Acetyl L Cysteine
20	A	382	2.3	N Acetyl L Cysteine
21	A	157.7	3.7	N Acetyl L Cysteine
22	A	382	8.0	N Acetyl L Cysteine
23	B	122	3.0	N Acetyl L Cysteine
24	B	477.3	4.3	N Acetyl L Cysteine
25	B	122	8.4	N Acetyl L Cysteine
26	B	477.3	5.8	N Acetyl L Cysteine
27	C	199.7	7.1	N Acetyl L Cysteine
28	C	399	8.5	N Acetyl L Cysteine
29	C	199.7	4.4	N Acetyl L Cysteine
30	C	399	4.3	N Acetyl L Cysteine
31	A	157.7	4089.2	Dextran
32	A	382	1023.7	Dextran
33	A	157.7	1171.8	Dextran
34	A	382	4436.9	Dextran
35	B	122	2050.6	Dextran
36	B	477.3	2093.3	Dextran
37	B	122	2183.3	Dextran
38	B	477.3	3750.4	Dextran
39	C	199.7	2598.1	Dextran
40	C	399	2226.3	Dextran
41	C	199.7	2793.0	Dextran
42	C	399	2941.8	Dextran
43	A	157.7	22.5	Procainamide
44	A	382	35.3	Procainamide
45	A	157.7	5.5	Procainamide
46	A	382	7.7	Procainamide
47	B	122	18.5	Procainamide
48	B	477.3	5.6	Procainamide
49	B	122	31.8	Procainamide
50	B	477.3	8.2	Procainamide
51	C	199.7	22.0	Procainamide
52	C	399	9.3	Procainamide
53	C	199.7	19.7	Procainamide
54	C	399	12.5	Procainamide

FIGS. 42A, 42B,42C, and42D contain spectra formed from the conditions of Table 4. Specifically, the figures show spectra of the Sample Population of 6 samples having random amounts of mannitol (FIG. 42A), dextran (FIG. 42B), n-acetyl L cysteine (FIG. 42C), and procainamide (FIG. 42D), at a concentration levels of 1 mg/dL and path lengths of 1 μm.

Next, calibration vectors were generated using the spectra ofFIGS. 42A-42D, in effect reproducing the steps ofBlock3120. The next step of this Example is the spectral subtraction of water that is present in the sample to produce water-free spectra. As discussed above, certain methods disclosed herein provide for the estimation of an analyte concentration in the presence of interferents that are present in both a sample population and the measurement sample (Type-A interferents), and it is not necessary to remove the spectra for interferents present in Sample Population and sample being measured. The step of removing water from the spectrum is thus an alternative embodiment of the disclosed methods.

The calibration vectors are shown inFIGS. 43A-43D for mannitol (FIG. 43A), dextran (FIG. 43B), n-acetyl L cysteine (FIG. 43C), and procainamide (FIG. 43D) for water-free spectra. Specifically each one ofFIGS. 43A-43D compares calibration vectors obtained by training in the presence of an interferent, to the calibration vector obtained by training on clean plasma spectra alone. The calibration vector is used by computing its dot-product with the vector representing (pathlength-normalized) spectral absorption values for the filters used in processing the reference spectra. Large values (whether positive or negative) typically represent wavelengths for which the corresponding spectral absorbance is sensitive to the presence of glucose, while small values generally represent wavelengths for which the spectral absorbance is insensitive to the presence of glucose. In the presence of an interfering substance, this correspondence is somewhat less transparent, being modified by the tendency of interfering substances to mask the presence of glucose.

It will be understood that the steps of methods discussed are performed in one embodiment by an appropriate processor (or processors) of a processing (i.e., computer) system executing instructions (code segments) stored in appropriate storage. It will also be understood that the disclosed methods and apparatus are not limited to any particular implementation or programming technique and that the methods and apparatus may be implemented using any appropriate techniques for implementing the functionality described herein. The methods and apparatus are not limited to any particular programming language or operating system. In addition, the various components of the apparatus may be included in a single housing or in multiple housings that communication by wire or wireless communication.

Further, the interferent, analyte, or population data used in the method may be updated, changed, added, removed, or otherwise modified as needed. Thus, for example, spectral information and/or concentrations of interferents that are accessible to the methods may be updated or changed by updating or changing a database of a program implementing the method. The updating may occur by providing new computer readable media or over a computer network. Other changes that may be made to the methods or apparatus include, but are not limited to, the adding of additional analytes or the changing of population spectral information.

One embodiment of each of the methods described herein may include a computer program accessible to and/or executable by a processing system, e.g., a one or more processors and memories that are part of an embedded system. Thus, as will be appreciated by those skilled in the art, embodiments of the disclosed inventions may be embodied as a method, an apparatus such as a special purpose apparatus, an apparatus such as a data processing system, or a carrier medium, e.g., a computer program product. The carrier medium carries one or more computer readable code segments for controlling a processing system to implement a method. Accordingly, various ones of the disclosed inventions may take the form of a method, an entirely hardware embodiment, an entirely software embodiment or an embodiment combining software and hardware aspects. Furthermore, any one or more of the disclosed methods (including but not limited to the disclosed methods of measurement analysis, interferent determination, and/or calibration constant generation) may be stored as one or more computer readable code segments or data compilations on a carrier medium. Any suitable computer readable carrier medium may be used including a magnetic storage device such as a diskette or a hard disk; a memory cartridge, module, card or chip (either alone or installed within a larger device); or an optical storage device such as a CD or DVD.

In view of the foregoing, certain disclosed embodiments comprise an apparatus for analyzing the composition of bodily fluid. This apparatus includes a first fluid passageway, at least one pump, an analyte detection system, and a fluid sensor.

The first fluid passageway (such as, without limitation, thepassageway112 and/or the passageway113) has a patient end configured to provide fluid communication with a bodily fluid within a patient. Where the first fluid passageway comprises thepassageway112, the patient end can comprise the end or region of thepassageway112 which is nearest the patient P, such as thepatient connector110/1100/1200, or any other suitable interface with any intervening fluid passageways or fluid network between the first fluid passageway and the patient P. Alternatively the patient end can comprise theconnector230; or the end of theconnector110 opposite theapparatus140; or the end of thesampling assembly220 adjacent theconnector1100/1200 when employed as shown in FIGS.11 or12. The patient end of the first fluid passageway of certain embodiments can provide the apparatus with fluid communication to the bodily fluid within the patient indirectly, where an intervening tube or passageway, such as thecatheter11, I.V. tubing, or other fluid handling apparatus, is positioned between the first fluid passageway and the patient to provide a fluid handling link between the patient and the first fluid passageway.

In some embodiments the apparatus also includes a second fluid passageway (such as, without limitation, the passageway113) in fluid communication with the first fluid passageway via a junction between the first and second fluid passageways with the fluid sensor configured to sense the arrival of bodily fluid near the junction of the first and second fluid passageways. Thus, in several embodiments, the junction of the first and second fluid passageways can be the junction of the

passageways

112 and113 as depicted in any ofFIGS. 3, 5,6A,6B,7A-7J, or9.

The at least one pump is coupled to the first fluid passageway and has an infusion mode and a sample draw mode. In the infusion mode (an example of which is described herein in reference toFIG. 7A), the pump is operable to deliver infusion fluid to the patient through the patient end of the first fluid passageway. In the sample draw mode (an example of which is described herein in reference toFIG. 7C), the pump is operable to draw a sample of the bodily fluid from the patient through the patient end of the first fluid passageway. The at least one pump can comprise any of the pumps discussed herein, including

pumps

203 and328,pump roller1005a, anddisplacement pump905. In certain embodiments, the apparatus comprises at least one pump having both the infusion mode and the sample draw modes. In certain other embodiments, the at least one pump of the apparatus comprises two unidirectional or single-mode pumps, wherein one unidirectional or single-mode pump provides the infusion mode and a second unidirectional or single-mode pump provides the sample draw mode.

The analyte detection system is accessible via the first fluid passageway such that the analyte detection system can receive at least one component of the drawn sample of bodily fluid and determine the concentration of at least one analyte. For example, in certain embodiments, the analyte detection system receives the bodily fluid (e.g., blood) in its whole state and determines the concentration of at least one analyte. For another example, in certain embodiments, the analyte detection system receives plasma (a component) separated from a whole blood drawn sample and determines the concentration of at least one analyte. In certain embodiments, the analyte detection system determines the analyte concentration in the component under analysis, in the drawn sample, in the patient, or in a combination of one or more of the component, drawn sample, and patient. The analyte detection system is generally positioned at a distance (e.g., one foot to eight feet), from the patient end of the first fluid passageway. Some embodiments of the analyte detection system include

analyte detection systems

334 and1700, described herein. Alternatively, the analyte detection system can comprise any suitable optical, spectroscopic, enzymatic (e.g. glucose), reagent-based (e.g., TPH or heart condition markers), and/or electrochemical (e.g., pH) analyte detection system.

The fluid sensor is located at or near the patient end of the first fluid passageway and spaced from the analyte detection system. The fluid sensor is configured to sense a property of the fluid within the first fluid passageway. In some embodiments, the fluid sensor is located between the patient end of the first fluid passageway and the analyte detection system. In various embodiments, the fluid sensor can comprise a colorimetric sensor, a hemoglobin sensor, a hematocrit sensor, a pressure sensor, a bubble sensor, a dilution sensor, or a combination thereof. Examples of such sensors are discussed herein, includingcolorimetric sensor311,hemoglobin sensor1003, pressure sensors and

sensor units

317,507,1011, and1102, and bubble sensors and

sensor units

314a,314b,321,505,1001a,100b, and1001c. A dilution sensor compatible with certain embodiments described herein provides a signal indicative of the dilution of the fluid within the first fluid passageway. In certain embodiments, this signal from the dilution sensor is used to indicate that the system can discontinue drawing body fluid from the patient and can draw a sample of the body fluid to the analyzer. The fluid sensor of certain embodiments is useful for detecting the arrival of body fluid in the first fluid passageway, or for identifying the type and/or condition of the fluid in proximity to the fluid sensor to facilitate directing the fluid to one or more appropriate locations in the system. For example, in certain embodiments, one or more signals from the fluid sensor are used to indicate that the system can discontinue drawing body fluid from the patient and can draw a sample of the body fluid to the analyzer, thereby facilitating directing a drawn blood sample to the analyte detection system forsubsequent analysis of one or more desired blood analytes, as discussed herein. In some embodiments, the fluid sensor is located in a near-patient module (e.g., thepatient connector110 or the sampling assembly220) located on the first fluid passageway between the patient end and the analyte detection system. The near-patient module can be spaced from the analyte detection system.

Other disclosed embodiments comprise a sampling assembly to be used with a main analyzer (such as, without limitation, the fluid handling andanalysis apparatus140 or the analyte detection system334) which is configured to sense an analyte in a body fluid drawn or otherwise obtained from a patient through a first fluid passageway (e.g., thepassageway112 and/or the passageway113). The first fluid passageway extends from the main analyzer toward the patient. The assembly (which, in certain embodiments can comprise thesampling assembly220 or the patient connector110) includes an instrument portion (such as, without limitation, theinstrument portion813 or a sensing module). The instrument portion includes at least one sensor and is preferably separate from the main analyzer and removably engaged with the first fluid passageway. The at least one sensors of the instrument portion is in sensing engagement with the first fluid passageway such that the at least one sensors can sense a property of a fluid within the first fluid passageway.

Still other disclosed embodiments comprise a body fluid analysis system including a main analyzer (such as, without limitation, the fluid handling andanalysis apparatus140 or the analyte detection system334) and a sampling assembly (e.g., thesampling assembly220 or the patient connector110). The main analyzer is configured to measure an analyte in a sample of body fluid drawn or otherwise obtained from a patient, or in one or more components of such a drawn sample of body fluid. The sampling assembly is in communication with the main analyzer and includes a first fluid passageway (such as, without limitation, thepassageway112 and/or the passageway113) and an instrument portion or sensing module (which, in one embodiment, can comprise the instrument portion813). The first fluid passageway extends from the main analyzer and has a patient end spaced from the main analyzer. The instrument portion is removably engaged with the first fluid passageway and is located on the first fluid passageway spaced from the main analyzer. The instrument portion has at least one sensor in sensing engagement with the first fluid passageway.

In some embodiments, the sampling assemblies disclosed above can also include a second fluid passageway (such as, without limitation, the passageway113) in fluid communication with the first fluid passageway via a passageway junction (e.g., the junction829). The instrument portion or the sampling assembly removably engages both the first and second fluid passageways at or near the passageway junction. One or more of the at least one sensor of the instrument portion or the sampling assembly can be located between the passageway junction and a patient end of the first fluid passageway, or between the junction and the interface region of the passageway.

The at least one sensor of the sampling assemblies discussed above can comprise any one or more of the following, in various embodiments: dlution sensor,colorimetric sensor311,hemoglobin sensor1003, pressure sensors and

sensor units

317,507,1011, and1102, and bubble sensors and

sensor units

314a,314b,505,1001b, and1001c. The at least one sensor can be configured to detect the arrival of, or a property of, drawn body fluid in the first fluid passageway, or to identify the type and/or condition of the fluid next to the fluid sensor to facilitate directing the fluid to the appropriate location or locations in the system for, e.g., subsequent analysis of one or more desired blood analytes in the analyte detection system, as discussed herein.

The junction of the first and second fluid passageways of the above-described embodiments of the sampling assembly or body fluid analysis system can be the junction of the

passageways

112 and113 as depicted in any ofFIGS. 3, 5,6A,6B,7A-7J, or9.

Where the first fluid passageway comprises thepassageway112, the patient end can comprise the end or region of thepassageway112 which is nearest the patient P, such as thepatient connector110/1100/1200, or any other suitable interface with any intervening fluid passageways or fluid network between the first fluid passageway and the patient P. Alternatively the patient end can comprise theconnector230; or the end of theconnector110 opposite theapparatus140; or the end of thesampling assembly220 adjacent theconnector1100/1200 when employed as shown in FIGS.11 or12. The patient end of the first fluid passageway can provide fluid communication with the bodily fluid within the patient indirectly, where an intervening tube or passageway, such as thecatheter11, I.V. tubing, or other fluid handling apparatus, is positioned between the first fluid passageway and the patient to provide a fluid handling link between the patient and the first fluid passageway.

The instrument portion, in some embodiments of the sampling assembly or body fluid analysis system discussed above, can include at least one first valve portion (such as, without limitation,312,313,316, and/or613) in operative engagement with the first fluid passageway. An instrument portion including such a first valve portion can also include a second valve portion (such as, without limitation,312,313,316, and/or613) in operative engagement with a second fluid passageway connected to the first fluid passageway.

One advantage of some embodiments of the apparatus and methods disclosed herein (including thesampling assembly220 andpatient connector100, and methods of use thereof) is limiting blood damage. More particularly, when a sample or volume of blood is drawn or otherwise obtained from the patient for sensing by the one or more sensors of the sampling assembly or instrument portion, the sample passes through thepassageway112 from the patient end to reach the instrument portion, where it is stopped, preferably well short of theanalyte detection system334 orapparatus140. At least a first portion of this initial sample is then diverted and passed along to thesystem334 orapparatus140 for analysis, and a second portion (e.g., having a volume larger than a volume of the first portion) is returned to the patient via the passageway112 (e.g., by one or more valves). In certain embodiments in which this returned blood travels only a relatively short distance to thesampling assembly220 or patient connector110 (e.g., where the distance traveled by the second portion is shorter than the distance traveled by the first portion), rather than all the way to thesystem334 orapparatus140, damage to the returned blood is diminished. For example, this returned blood is much less likely to coagulate or to have lysed (incurred damage to the red blood cells) as a result of the shorter distance traveled in returning to the patient. Limiting coagulation prevents the formation of clots which can restrict the flow of blood, and maintaining the integrity of red blood cells prevents loss of the blood's oxygen transport functions. These benefits result in overall improved status of the patient as compared to patients analyzed by systems that require returning blood to travel longer distances (e.g. all the way to the analyte detection system and back to the patient). Accordingly, certain of the above-described apparatus and methods can be considered apparatus and methods for limiting damage to returned blood.

Reference throughout this specification to “one embodiment” or “an embodiment” means that a particular feature, structure or characteristic described in connection with the embodiment is included in at least one embodiment. Thus, appearances of the phrases “in one embodiment” or “in an embodiment” in various places throughout this specification are not necessarily all referring to the same embodiment. Furthermore, the particular features, structures or characteristics may be combined in any suitable manner, as would be apparent to one of ordinary skill in the art from this disclosure, in one or more embodiments.

Further information on analyte detection systems, sample elements, algorithms and methods for computing analyte concentrations, and other related apparatus and methods can be found in U.S. Patent Application Publication No. 2003/0090649, published May 15, 2003, titled REAGENT-LESS WHOLE BLOOD GLUCOSE METER; U.S. Patent Application Publication No. 2003/0178569, published Sep. 25, 2003, titled PATHLENGTH-INDEPENDENT METHODS FOR OPTICALLY DETERMINING MATERIAL COMPOSITION; U.S. Patent Application Publication No. 2004/0019431, published Jan. 29, 2004, titled METHOD OF DETERMINING AN ANALYTE CONCENTRATION IN A SAMPLE FROM AN ABSORPTION SPECTRUM; U.S. Patent Application Publication No. 2005/0036147, published Feb. 17, 2005, titled METHOD OF DETERMINING ANALYTE CONCENTRATION IN A SAMPLE USING INFRARED TRANSMISSION DATA; and U.S. Patent Application Publication No. 2005/0038357, published on Feb. 17, 2005, titled SAMPLE ELEMENT WITH BARRIER MATERIAL. The entire contents of each of the above-mentioned publications are hereby incorporated by reference herein and are made a part of this specification.

A number of applications, publications and external documents are incorporated by reference herein. Any conflict or contradiction between a statement in the bodily text of this specification and a statement in any of the incorporated documents is to be resolved in favor of the statement in the bodily text.

Although the invention(s) presented herein have been disclosed in the context of certain preferred embodiments and examples, it will be understood by those skilled in the art that the invention(s) extend beyond the specifically disclosed embodiments to other alternative embodiments and/or uses of the invention(s) and obvious modifications and equivalents thereof. Thus, it is intended that the scope of the invention(s) herein disclosed should not be limited by the particular embodiments described above, but should be determined only by a fair reading of the claims that follow.