US20060275852A1

Movatterモバイル変換

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Publication number: US20060275852A1
Application number: US11/262,115
Authority: US
Inventors: Jean Montagu; Herman DeWeerd; Roger Dowd; Natalia Rodionova; Peter Maimonis; Nathan Tyburczy
Original assignee: Individual
Current assignee: Courtagen Life Sciences Inc
Priority date: 2005-06-06
Filing date: 2005-10-27
Publication date: 2006-12-07
Also published as: WO2006132666A1; CN101262948A; US8986983B2; EP1888235A1; CA2610875A1; CN101262948B; US20110319279A1

Abstract

Cassette (50) performs assays, e.g. multiplexed protein biomarker assays. Wide, bubble-free, slow flows are produced from liquids stored on cassette (50), flowing over wide array (20) of ligand receptors on a capture surface. Flows of Reynolds Number less than about 1, preferably 1×10⁻¹to 5×10⁻³, are heated in region (34) preceding and including bubble removal system (128). Analyte is introduced through compressed septum (32). External actuations of displacement pumps (30, 37) and valves (137A, B, and C) produce flows in response to flow-front optical sensors (150, 152). Elastic sheet provides pump and valve diaphragms and resilient expansion of mixing volume (131). Break-away cover portions are pistons. Heating is by conduction through cassette from external contact heater. Planar cassette body, when tilted from horizontal, enables upward flow from pumped storage (134, 135) to reaction (133) to waste (139), with buoyancy bubble removal before reaction. Reading of fluorescence is by external reader, employing calibration, control and reference features on capture surface. Extensive set of calibration features of differing intensities enables self-calibration.

Description

CROSS-REFERENCE TO RELATED APPLICATION

(Under 35 U.S.C. § 119(e)(1), this application claims the benefit of prior U.S. provisional application Ser. No. 60/688,269, filed Jun. 6, 2005.

FIELD OF INVENTION

The field of invention relates to solid phase assays for the detection of analytes in liquid samples.

BACKGROUND

Ligand receptor-ligand assays on solid surfaces, such as sandwich assays, have been a standard tool in chemical and biological research and in diagnostics for many decades. For instance, Enzyme-Linked Immunoabsorbent Assays (ELISA) have been standard for quantitative analysis of protein in blood and other body fluids. Assay results have often been read by quantitative measurement of fluorescence from tags associated with ligand receptor-ligand complexes on the solid surface.

In the recent decade there has been a strong effort to perform multiple ligand receptor-ligand assays simultaneously within a small geometry, in order to reduce reagents, labor and sample sizes. In the context of genetic research and elsewhere, especially where qualitative results are all that are required, microarray technology employing spotted arrays within portable cassettes has been adopted for the assays.

However, significant obstacles have confronted development of miniaturized quantitative assay formats that are both highly sensitive and highly reproducible, for which there is great need. The obstacles have been even greater when further desired features are sought, such as simplicity, rapidity, economy and broad range applicability.

In particular, in the area of protein analytes, significant obstacles have confronted development of miniaturized, multiplexed immunoassays that enable direct comparison to or substitution for the results of standard ELISA of analytes in body fluids, especially, blood. For qualification of drugs for human use and for medical diagnostics, such assays are required to be very precise, preferably with a coefficient of variation (CV) less than 10. (The coefficient of variation (CV), defined as the percent ratio between the standard deviation of a set of values from repeated testing of a given sample and the mean of those values, provides an estimate of the degree of variability among those values. The lower the CV, the more precise the assay and the more confidence one has in the results.)

Without attempting to be exhaustive in listing the obstacles to the development of precise miniaturized assays, a few examples will be mentioned.

Some workers in the field have suggested that conditions of equilibrium are prerequisite for achieving high sensitivity and low coefficient of variation in an assay. But, use of very small samples is particularly difficult in an equilibrium assay, because such an assay is generally volume-dependent. Accuracy and repeatability depend on controlling the accuracy of the sample volume. Unfortunately, when the sample volume is very small, an assay that depends on maintaining an accurate sample volume is prone to variation from assay to assay. Even if the sample size is controlled by an automated metering system, there is such variation.

Another proposal has been to detect analytes by a method based on an ambient analyte theory that requires particularly small spots of ligand receptors. This size requirement challenges the capabilities of conventional instruments used in producing spotted microarrays. Furthermore, very small spots present the difficulty, when reading the results, of lack of sufficient resolution and of sufficiently low background noise. Furthermore, such assays take long to perform, typically well over one hour.

Various approaches to the design of miniaturized multiplexed assays have employed microfluidic technology, with flow channels and reaction chambers having flow cross-section typically less than 0.02 mm². Numerous uncontrolled phenomena can influence the results in such a system. Liquid temperature change, as well as atmospheric pressure change, and localized liquid pressure change as liquids encounter sharp edges, space discontinuities, or variation of surface properties such as surface roughness or different surface tension properties, can all produce gas micro-bubbles that, we have realized, have heretofore not been adequately recognized or taken into account in the context of assay cassettes.

Other approaches, such as those employing capillary or osmotic forces for moving liquids through an assay, have been highly sensitive to the characteristics of the particular fluids and passage materials involved, and have required custom development for narrow groups of analytes. With some such approaches, a requirement of intersections with discrete lanes of migrating liquid has limited the amount of data obtainable in a desirable geometry and has prevented achieving desired coefficient of variation in quantitative results.

Still other approaches have suffered from complexity, high cost, requirement of skilled operators, or lack of suitability for implementation in disposable cassettes.

In general, the ability to measure analyte concentrations in miniaturized, multiplex assays suffers from what has appeared to be necessary tradeoffs between sensitivity, repeatability, performance, cost and ability to compare results with standardized assays.

Developers of biological assays have made various attempts to escape some of the constraints associated with conventional assay techniques. An example is by reading an assay by electrical measurement. Effort has been expended in the development of chemical sensors that can measure the presence or the concentration of chemical species in blood or other biological fluids in this manner. One of the drawbacks of such methods is the inability to enable direct comparison to standard ELISA results. Other drawbacks are the requirement of accurately controlled liquid volume, and the difficulty of performing the assay on multiple analytes simultaneously. Besides, there is the drawback of having to make electrical connection with an assay cassette; over time, the electrical terminals may introduce inaccuracies or require maintenance. Designs of this category, as well, may suffer from uncontrolled phenomena mentioned above, to which aspects of present invention offer solution.

In view of the limitations and drawbacks of prior approaches, there is considerable need for improved approaches to the problems of miniaturized quantitative assays using arrays on solid surfaces, both with respect to assays that employ ligand receptor-ligand systems, very generally, and in particular, with respect to immunoassays, especially immunoassays for protein in body fluids such as blood.

There is special need for miniaturized assays that can be analyzed using fluorescent detection and are otherwise comparable to standard ELISA results. There is particular need for sensitive, precise multiplex assays to enable simultaneous evaluation of multiple markers that may indicate disease, the effectiveness of a drug, toxic reactions to a drug, or suitability of subjects as candidates for a drug or drug study.

There is particular need for an assay technique (or “platform”) for protein biomarkers which, above all, is robust. An assay technique is needed that produces highly credible results with low coefficients of variation, is immune to interferences, and performs its function with sufficient margins that it is useful over a wide range of analytes, levels of dilution, and starting conditions. It is especially desirable that the technique also be sensitive, have significant throughput, be capable of conducting multiple assays at once and employ equipment which is easy to use. It would be beneficial, as well, for such a technique to enable simple design of particular assays and to require little sample or reagent and little handling of the sample.

SUMMARY OF INVENTION

According to one aspect of invention, an assay cassette is provided which comprises a capture surface that carries an array of spaced-apart regions of ligand receptors, and a liquid passage system constructed to direct over the array a slow flow of assay-supporting liquids having Reynolds numbers less than about 1, preferably, between about 1×10⁻¹and 5×10⁻³, the liquids including a ligand-containing liquid, the cassette including a gas bubble removal system to which the liquids are exposed, the gas bubble removal system constructed and arranged to remove gas micro-bubbles from the liquids prior to exposure of the liquids to the array.

According to another aspect of invention, the assay cassette as just described further incorporates heat transfer surfaces to which flows of the liquids are exposed for heating the liquids prior to exposure of the liquids to the gas bubble removal system, whereby gas micro-bubbles produced in the liquids by heat delivered via the heat transfer surfaces of the cassette can be removed before the liquids are exposed to the array. For instance, the cassette may be configured to receive heat from a heater member of an external device (e.g., the device constructed to operate the cassette), the cassette constructed and arranged to enable heat to flow through substance of the cassette to the heat transfer surfaces, thence to the liquid.

According to another aspect of invention, the assay cassette, in either of the arrangements just described, also includes a site for storage of an agent useful in the assay, the cassette constructed to enable combining a liquid with the agent to produce an assay-supporting liquid, and, respectively, to enable flow of the assay-supporting liquid through the liquid passage system, or through the passage system with exposure to a heat transfer surface, the cassette constructed to enable exposure of the assay-supporting liquid to the gas bubble removal system prior to reaching the array, whereby gas micro-bubbles previously produced in the liquid can be removed before the assay-supporting liquid is directed over the array. Preferably, the cassette separately stores a liquid and a desiccated agent, which can be combined to solubilize (or otherwise liquefy) the agent. Alternatively, the cassette may store a liquid agent in concentrated form which can be diluted by a stored buffer liquid.

It is recognized that a bubble removal system incorporated in such cassettes, preceding the capture surface, enables the liquid flow over the capture surface to be free of detrimental gas micro-bubbles that could otherwise attach to and effectively obscure a region of ligand receptors from the analyte or agent in the liquid. In particular, it is realized that harmful gas micro-bubbles may occur in a liquid merely by the act of bringing the liquid up to assay temperature, owing to the decrease in solubility of dissolved gases in liquids as the temperature of the liquids rises. Likewise, it is realized that agent-combining action and other activities in the cassette may produce gas micro-bubbles that impair the interaction of the analyte-containing liquid with the capture regions.

The gas bubble removal system on the cassette thus can minimize the consequences of bubble-producing effects of critical steps performed on liquid in the cassette, as well as of uncontrolled phenomena such as atmospheric pressure changes and localized liquid pressure changes as liquids within the cassette encounter either microscopic sharp edges, space discontinuities, or variation of surface properties such as surface roughness or different surface tension properties in the fluidic system of the cassette. Gas micro-bubbles produced by fluid displacement pumps and actuation of displacement valves of a cassette can be removed prior to the liquid reaching the capture surface of a reaction chamber, and therefore, simple designs of mechanical components can be employed.

The system for removing gas bubbles from liquids within cassette devices may avoid denaturing of analytes reagents as well as prevent micro-bubbles from interfering with binding.

Various kinds of gas bubble removal systems may be employed. As another aspect of invention, however, advantages are found in providing a passive gas bubble removal system based on the principle of buoyancy. Such a system is made possible in a cassette design by establishing the orientation of the cassette at a predetermined angle to horizontal during performance of the assay. Buoyancy forces bubbles of gas out of the liquid within the cassette and into a trap of suitable dimensions. This passive process is thus able to separate and capture detrimental gas bubbles present within a fixed volume of one or many liquids on the cassette device during liquid transport within the device. Gas bubbles can be extracted from a laminar flow at extremely low Reynolds number (N_Re), such as N_Reless than about 1. A selected duration in the bubble escape region, e.g. between about one and five seconds, can assure removal of detrimental bubbles. Such a device can be used to perform biological assays, such as sandwich immunoassays, with low CV, preferably a CV of less than 10%.

In the context of these aspects of invention, it is recognized that the slow flow of liquids, at Reynolds numbers N_Reof less than about 1, preferably between about 1×10⁻¹and 5×10⁻³, enables flow velocity and reaction chamber dimensions to have variation within reasonable tolerances, and the liquid and analyte to be of a wide selection, with negligible effect on the sensitivity and coefficient of variation of the assay. At such low Reynolds numbers, diffusion is the principal mechanism by which uniformity of distribution of the analyte in the liquid is maintained in the vicinity of the ligand receptors, hence modest local flow velocity variation over the capture surface is only of secondary effect. Transition from a narrow channel from the bubble removal system to a widened flow in the reaction chamber, e.g. to a flow width of 0.5 or 1 cm, enables a sheet-form, low Reynolds number flow of liquid over a capture surface that bears an array of many sets of spots of different ligand receptors. Each set may contain at least 3, preferably, 10, replicate spots of a ligand receptor, the spots preferably in rows oriented transversely to the direction of flow. This enables operations to be performed on the data to improve the sensitivity and coefficient of variation of the determined value with respect to each set of spots.

Other aspects of invention comprise a method of conducting an assay employing a cassette of any of the constructions previously described.

Another aspect of invention is a cassette for conducting an assay, the cassette comprising a solid surface carrying an array of spots of ligand receptor of diameter between about 50 micron and 500 micron, with spacing between spots at least about equal to the diameter of the spots, the array having a width greater than about 0.5 cm, the solid surface bearing the array constructed and arranged as one side of a flow passage having a width exceeding the width of the array, and a dimension of the gap between the surface bearing the array and an opposed, parallel, flow-confining surface of between about 80 and 300 micron, a pumping and passage system constructed to create a succession of flows through the width of the flow passage at Reynolds number less than about 1 of liquid sample containing ligand of interest and of developing liquid, or a succession of liquids, capable of attaching detectable tags to spots to which ligand of interest has attached, the cassette constructed to enable reading the detectable tags of the array. Preferably the gap is between about 100 and 200 micron and the pumping and passage system is constructed to provide the flows at Reynolds number between about 1×10⁻¹and 5×10⁻³, for instance the cassette is constructed with a gap of 100 micron, the spots of ligand receptor are of about 150 micron diameter, and the cassette is constructed for flows over the array at Reynolds number of about 2.7×10⁻².

Another aspect of invention is a method of conducting an assay employing an array of spots on a solid surface, the method comprising the steps of (a) providing on a solid surface an array of spots of ligand receptor of diameter between about 50 micron and 500 micron, with spacing between spots at least about equal to the diameter of the spots, the array having a width greater than about 0.5 cm; (b) arranging the solid surface bearing the array as one side of a flow passage having a width exceeding the width of the array, and a dimension of the gap between the surface bearing the array and an opposed, parallel, flow-confining surface of between about 80 and 300 micron; (c) creating a succession of flows through the width of the flow passage at Reynolds number less than about 1 of liquid sample containing ligand of interest and of developing liquid, or a succession of liquids, capable of attaching detectable tags to spots to which ligand of interest has attached; and (d) reading the detectable tags of the array. Preferably the gap is between about 100 and 200 micron and the flows over the array have a Reynolds number between about 1×10⁻¹and 5×10⁻³, for instance the gap is 100 micron, the spots are of about 150 micron diameter and the Reynolds number is about 2.7×10⁻². Preferably all steps of this method are performed using a cassette to house the liquids and to provide the pumping and passage system.

Assay cassettes and methods of conducting assays employing cassettes having one or more aspects of invention thus-far described can have one or more of the following features:

An agent stored on the cassette for combination with a liquid is a ligand or a substance comprising a detectable tag.

An agent stored in the chamber on the cassette is in dry state, exposed to air, the cassette constructed to enable introduction of the liquid to the chamber in combining action, a gas bubble removal system of the cassette being effective to remove micro-bubbles of the air produced by the combining action.

A chamber of the cassette in which combining of agent and liquid is to occur has an elastically distensible wall portion adapted to elastically expand in response to liquid displaced into the chamber, and to elastically contract when liquid flows out of the chamber.

The assay cassette comprises at least one liquid storage chamber associated with a displacement pump constructed to displace liquid in continuous flow from the storage chamber, to flow through the passage system or through the passage system with exposure to a heat transfer surface, the cassette constructed to enable exposure of the liquid to a gas bubble removal system prior to reaching the array, whereby gas micro-bubbles previously produced in the liquid can be removed before the liquid is directed in continuous flow over the array.

The assay cassette includes a displacement pump in the form of an elastic diaphragm forming a wall portion of a liquid storage chamber which is operable by an external, continuously movable actuator to produce a continuous flow.

The assay cassette comprises at least one liquid storage chamber associated with a displacement pump constructed to displace liquid in continuous flow from the storage chamber, an outlet to the passage system is located at the top of the liquid storage chamber, exposed to air present in the chamber, the cassette and pump, e.g. an elastic diaphragm, being constructed and arranged to expel air from the chamber followed by forcing liquid through the passage system in continuous flow via the gas bubble removal system and over the array.

The assay cassette has a liquid storage chamber constructed to contain a sealed pouch of liquid for the assay, the chamber associated with a device for puncturing the pouch to release the liquid.

The assay cassette has a liquid storage volume constructed to receive and store a liquid introduced to the cassette from the exterior, whereby gas micro-bubbles produced in the liquid by the step of introduction of the liquid to the cassette can be removed by a gas bubble removal system before the liquid flows over the array.

The assay cassette has a liquid storage chamber constructed to receive the liquid from the exterior via a needle or pipette projected through a septum, the septum comprising an elastomeric mass that has a pierced passage, the elastomeric mass mounted under substantial compression relative to the pierced passage, the compression effective to maintain the pierced passage closed but enabling insertion and removal of a plastic liquid-supply needle or pipette through the pierced passage.

The assay cassette has at least one waste chamber to which liquid flows after being pumped in continuous flow by a displacement pump, exposed to a gas bubble removal system and directed over the array, whereby the liquid is contained within the cassette throughout the assay.

The assay cassette is constructed and arranged so that during performance of the assay the capture surface and the liquid flow over it have an upward extent, and a waste chamber is positioned in the cassette to receive gravity flow of liquid that has passed over the capture surface.

The assay cassette is of generally planar extent and constructed to be disposed at a substantial angle to the horizontal during performance of the assay to dispose the capture surface to extend upwardly in the direction of the liquid flow to an upper end, and to locate a waste outlet for gravity flow from the upper end of the capture surface to a waste chamber.

The assay cassette has a liquid passage system which includes at least one actuatable valve through which liquid flows prior to being exposed to a gas bubble removal system, whereby gas micro-bubbles produced in the liquid by passage through the valve can be removed before the liquid is directed over the array.

The assay cassette has a valve comprising a valve seat across which liquid flows, the valve seat defining inlet and outlet passages, and an elastic diaphragm extends over the valve seat and is displaceable to engage the valve seat to interrupt the flow.

The assay cassette has a stop valve followed by a surface-tension burst valve, the burst valve being capable of blocking migrating liquid that may leak past the stop valve when the stop valve is closed, but, at flow pressure, capable of transmitting liquid to flow over the array.

The assay cassette has a flow passage system constructed and arranged to enable more than one slow flow of liquid of Reynolds number less than about 1, preferably, between about 1×10⁻¹and 5×10⁻³, over the array after exposure of the liquids to a gas bubble removal system.

The assay cassette is constructed to perform a sandwich assay in which liquid flows of the assay are exposed to the bubble removal system, the cassette comprising storage sites for liquid sample and all substances employed in the sandwich assay, the cassette having at least one waste chamber, the cassette being constructed and arranged to contain all liquids throughout the performance of the sandwich assay.

The assay cassette has a capture surface of extended width and carries a two-dimensional array of ligand-receptor regions comprised of spots of characteristic dimension between about 50 μm and 500 μm, and the liquid passage system includes a flow transition section preceding the capture surface that spreads the continuous, slow liquid flow to a width corresponding to the width of the capture surface.

The assay cassette has a capture surface exposed to the slow liquid flow of dimensions of at least about 0.5 cm in the direction of the flow and in the direction transverse to the direction of the flow.

The assay device has a flow transition section preceding the capture surface, the cross-section area of flow preceding the transition section is about 0.25 mm²or less and the cross-section area of the slow flow over the capture surface is at least 0.75 mm².

The assay cassette carries at least 3 replicate regions of each of a multiplicity of ligand receptors arrayed transversely to the direction of flow of the liquid over the capture surface, preferably the array on the capture surface also including, in regions in proximity to the regions of a given ligand receptor, reference regions of known quantity of the ligand to which the receptor is specific.

A bubble removal system of the assay cassette preferably comprises at least one buoyancy chamber to which the liquid is exposed.

The assay cassette is of generally planar extent and constructed to be disposed at a substantial angle to the horizontal during performance of the assay to dispose a gas bubble removing buoyancy chamber above a discharge outlet through which the liquid is directed to the capture surface.

The assay cassette is constructed so that when disposed at a substantial angle to the horizontal, the capture surface is located above a flow transition passage that receives liquid from a buoyancy chamber and spreads the liquid flow to a width corresponding with the width of the capture surface, the transition passage constructed to direct the liquid in continuous upward flow over the capture surface. In one preferred form, the assay cassette is constructed so that when disposed at the substantial angle to the horizontal, a waste outlet is located in position to receive the liquid following flow over the capture surface for gravity flow to a waste chamber in the cassette.

The assay cassette comprises a liquid storage chamber having an outlet passage, the cassette is constructed so that when disposed at a substantial angle to the horizontal, the storage chamber is below the capture surface, the storage chamber associated with an externally actuatable displacement pump that is effective to force liquid from the storage chamber in continuous flow through a buoyancy chamber and upwardly over the capture surface to a waste outlet.

The assay cassette, in operating orientation, has a buoyancy chamber with a top and bottom, a liquid inlet and a liquid outlet, both the liquid inlet and outlet being located near the bottom, in flow-aligned relationship.

The assay cassette has a buoyancy chamber and is constructed to enable initial filling of the buoyancy chamber by a liquid stored in the cassette, and to have a plurality of liquids of the cassette flow through the so-filled chamber in sequence, in laminar flow between the inlet and the outlet of the buoyancy chamber.

The assay cassette is constructed to enable exposure of each increment of liquid flow to a buoyancy chamber for a period between about 1 and 5 seconds.

The assay cassette has a buoyancy chamber comprising a depression molded in a face of a plastic body and channels molded in the face of the plastic body for liquid leading to and from the depression, and an adhesive sheet overlies the molded depression and the channels and is adhered to face portions of the molded body bounding the depression and channels.

A bubble removal system includes, in succession, at least two bubble capture zones to which a flow is exposed. Preferably, the bubble capture zones are constructed and arranged to enable bubbles to rise by buoyancy effects. In a preferred form, a buoyancy chamber is constructed for liquid flow from an inlet, along a path exposed to enable bubbles to rise by buoyancy effects for capture, to an outlet, there being at least one divider wall spaced along and above the liquid path to define upstream and downstream bubble capture zones exposed to the path such that a large bubble in liquid flow at the inlet, for instance during original liquid filling of the buoyancy chamber, will tend to be trapped in the upstream capture zone, leaving the downstream capture zone free to receive liquid flow. In one preferred form, the divider wall terminates in an upward region above which liquid entering the downstream zone can fill the upstream zone above any bubble lodged in a lower portion of the upstream zone. In preferred forms, this buoyancy chamber comprises a depression molded in a plastic body, there being a molded upstanding rib defining the divider wall, and an adhesive sheet overlies the molded depression, being adhered to face portions of the molded body bounding the depression, and adhered to an outer edge of the molded rib.

Another aspect of invention is a molded body for an assay cassette, the body defining at least one molded receptacle of depth suitable to hold an assay liquid, and a molded face wall, the molded receptacle being open at a face-side plane and the molded face wall having an outer face generally aligned with the face-side plane, the outer face of the face wall having at least one molded channel forming a liquid passage for directing liquid from the receptacle to an assay region of the cassette the face wall having a thickness substantially less than the depth of the receptacle and having a back surface at a heater cavity that is open from the backside of the body, the heater cavity constructed and arranged to removably receive a cooperatively constructed external heater to engage portions of the back surface of the face wall in surface-to-surface heat-transfer contact to heat liquid flowing in the molded channel by heat conduction through the thickness of the molded face wall.

Preferred embodiments of this aspect have one or more of the following features.

A chip-receiving opening is defined in the face wall to receive and position an assay chip so that the chip bounds a reaction chamber into which a molded channel of the face wall directs liquid, the heater cavity in the molded body extending below the chip-receiving opening to expose the chip for surface-to-surface heat-transfer contact with the external heater to heat liquid in the reaction chamber by heat conduction through the thickness of the assay chip. Preferably a portion of the backside of the chip is exposed to a temperature sensor to control the energization of the heater.

A receptacle is an analyte-receiving receptacle arranged to discharge into a molded channel of heat-exchange contour, preferably a serpentine contour, in a portion of the face wall that is arranged to receive heat from the heater.

One side of at least one liquefying chamber is molded as a depression in a portion of the face wall through which a liquid channel directs liquid, this portion of the face wall having a back surface exposed for engagement by the external heater for surface-to-surface heat transfer contact to heat liquid in the liquefying chamber by heat conduction through the thickness of the molded face wall.

One side of a bubble removal device is molded as a depression in a portion of the face wall through which a liquid channel directs liquid, this portion of the face wall having a back surface exposed for engagement by the external heater for surface-to-surface heat transfer contact to heat liquid in the bubble removal device by heat conduction through the thickness of the molded face wall, preferably this bubble removal device being a liquid-filled bubble trap.

An assay cassette comprises the molded body and a cover assembly secured over the receptacle and the face-wall of the molded body, the cover assembly including an elastic diaphragm portion lying over the receptacle, the diaphragm portion adapted to be deflected to displace liquid from the receptacle through the molded channel. In preferred forms, a portion of the face wall is molded in the form of a valve seat, and the cover assembly includes a diaphragm portion adapted to be deflected to engage the valve seat to stop flow.

The molded body is of generally planar extent and bound, at least substantially, by a perimeter wall of substantially constant depth extending between respective parallel planes.

The back surface of the face wall of the molded body is planar, preferably parallel to face-side and back-side planes of the cassette, and arranged to be engaged by a planar heat-delivering face of a heater. Preferably the heater comprises a flexible, sheet-form resistance heater mounted on a resilient planar pad carried on a rigid, planar plate that is mounted in floating manner enabling the corresponding planar surfaces of the molded body and the heater to self-adjust into face-to-face heat-transfer contact.

Another aspect of invention is a molded body for an assay cassette, the body defining at least one molded receptacle of depth suitable to hold an assay liquid and a molded face wall, the molded receptacle being open at a face-side plane and the molded face wall having an outer face generally aligned with the face-side plane, the outer face of the face wall having at least one molded channel forming a liquid passage for directing liquid from the receptacle to an assay region of the cassette, the front surface of the face wall being planar and adhered to an adhesive side of an adhesive sheet, at least one portion of the adhesive sheet lying over a channel in the face wall, closing the respective side of the channel. In preferred forms the adhesive sheet carries adhesive on its oppositely directed sides, the adhesive sheet having at least one window corresponding to a liquid receptacle or valve seat, one adhesive side of the adhesive sheet being adhered to the face wall and the oppositely directed adhesive side adhered to an elastic diaphragm sheet, a portion of the elastic diaphragm sheet lying over the window defining a deflectable pump diaphragm or valve diaphragm at a respective feature in the molded body. In preferred form, a second adhesive sheet carrying adhesive on its oppositely directed sides is adhered on one side to the outer side of the diaphragm sheet, and the oppositely directed adhesive side adhered to a relatively rigid cover member. In preferred cases, there is a window in the second adhesive sheet overlying a pump receptacle and a breakaway portion of the cover overlying the diaphragm at the pump receptacle is constructed to break from the cover to act as a pump piston head for deflecting the respective portion of the diaphragm in response to externally applied actuation force. In preferred cases the break away portions of the cover are adhered to corresponding outer surface portions of the diaphragm sheet.

The assay cassette is constructed for use with a protocol which produces light-emitting tags associated with complexes of receptor and ligand, the cassette having a window constructed and arranged to enable reading of light emitted from the tags, preferably the capture surface comprising a nitrocellulose layer of less than about 1 micron thickness.

The assay cassette is constructed as a disposable sandwich assay cassette for optical reading, the cassette operable by external apparatus, and having: a liquid storage chamber and associated displacement pump for producing a continuous flow of liquid sample containing an analyte ligand, at least a second liquid storage chamber and an associated displacement pump for producing flows of assay-supporting liquids for completing the assay, a flow-through reaction chamber in which a capture surface of extended width is situated, at least one waste chamber for receiving waste liquid from the reaction chamber, the liquid passage system including a flow transition section which spreads the liquid flow to the width of the capture surface, the capture surface carrying a two-dimensional array which includes spaced-apart replicate regions of ligand receptors, the capture surface being positioned and arranged for optical reading, the liquid passage system comprising a flow network for directing flows of the sample and assay-supporting liquids through the reaction chamber, over the capture surface, a venting arrangement for air displaced by liquid forced through the system, and heat transfer surfaces arranged to receive heat to bring the liquids to about desired assaying temperature prior to entering the bubble removal system and to maintain the reaction chamber at assaying temperature, and the liquid displacement pumps of the storage chambers, the flow network including the associated gas bubble removal system and transition section, and the reaction chamber cooperatively constructed to produce relatively widened flows of Reynolds numbers less than about 1 of a sequence of liquids over the capture surface, thence to the waste chamber.

The assay cassette, constructed as a disposable sandwich assay cassette, has heat transfer surfaces to which the liquids are exposed that are in heat-transfer relationship to an exterior surface of the cassette, the exterior surface of the cassette adapted to be placed in heat-receiving relationship with a heater member of the external apparatus.

According to another aspect of invention, an assay cassette combines, in particular, a capture surface for a receptor ligand, a liquid passage system for liquid flows at Reynolds numbers less than about 1, preferably between about 1×10⁻¹and 5×10⁻³, a temperature control region constructed to enable all liquids associated with the assay to be brought approximately to an assaying temperature, and a gas bubble removal system following the temperature control region to which the liquid is exposed prior to reaching the capture surface, the gas bubble removal system constructed to remove gas micro-bubbles from the liquid to improve capture of a ligand in the liquid, the gas bubble removal system comprising an upwardly extending buoyancy chamber adapted to contain liquid and having a top, a liquid inlet and a liquid outlet, the outlet located lower than the top of the buoyancy chamber in position adapted to be submerged in liquid of the buoyancy chamber, there being a vent passage from the upper portion of the buoyancy chamber.

According to another aspect of invention, in embodiments of the cassette that have a buoyancy chamber, the liquid passage system is constructed to initially fill the buoyancy chamber with liquid from a first storage volume in a manner that a further flow passage to be connected to provide flow of another liquid through the buoyancy chamber can be isolated and remain empty during the filling of the buoyancy chamber, and the buoyancy chamber is sized to receive and contain air displaced from the empty passage when liquid is forced through the further passage on its way to the buoyancy chamber without exposing the liquid outlet from the buoyancy chamber to air filling the top of the buoyancy chamber.

In embodiments of various aspects of invention, the assay cassette comprises a generally planar molded body of rectangular form of length of about 8 cm. or less and width of about 5 cm. or less, constructed to be oriented with its longitudinal axis disposed at a substantial angle to the horizontal during use; in such orientation, substantially the lower half of the body defining, in side-by-side manner, a storage chamber for a pouch of buffer liquid, a chamber for a detection ligand stored therein in desiccated form, and a chamber for a fluorescent tag agent stored therein in desiccated form; a reaction chamber containing the capture surface located adjacent the opposite longitudinal end of the molded body, at least one storage chamber disposed laterally to one side of the reaction chamber, positioned to receive gravity flow of waste from the reaction chamber; and a temperature control region arranged to heat liquids prior to the liquids entering the gas bubble removal system.

According to another aspect of invention, a method of conducting an assay comprises providing an assay cassette, selected from any of the constructions described above, and external apparatus suitable to control the assay, introducing a sample to a sample chamber of the cassette, and, according to a predetermined assay protocol, conducting the assay under control by the external apparatus, including continuously flowing the sample and supporting liquids over the capture surface at Reynolds numbers less than about 1, preferably between about 1×10⁻¹and 5×10⁻³, for selected durations and reading the capture surface of the cassette.

According to another aspect of invention, a method of conducting a sandwich assay comprises providing a sandwich assay cassette selected from any of the types described above for sandwich assays, and external apparatus suitable to control the assay, wherein the capture surface carries an array of replicate regions of ligand receptor specific to a ligand of an analyte molecule, introducing a liquid sample that includes the analyte to the sample chamber and, according to a predetermined sandwich assay protocol suitable for optical reading, under control of the external apparatus, at Reynolds numbers less than about 1, preferably between about 1×10⁻¹and 5×10⁻³, causing, sequentially, continuous flow through the reaction chamber of the sample at a predetermined flow rate for a predetermined time, and continuous flows of assay-supporting liquids for appropriate times, and optically reading the capture surface of the cassette. In some cases the capture surface carries replicate deposits of receptor ligands in the form of an antigen or antibody specific to an analyte molecule, and the sample contains the analyte molecule.

Another aspect of invention is a method for determining the concentration of at least one analyte in a liquid sample employing only liquids contained in a cassette, comprising the steps of: (a) providing a cassette, the cassette including: (i) a capture surface having, for each analyte, immobilized binding agent having replicate binding sites specific for the analyte, the binding agent being divided into a set of at least 3 spatially separated locations on the capture surface; and (ii) a liquid developing system capable of providing at least one liquid for developing the complex of analyte and binding agent by attaching thereto a signal-producing tag in manner to quantitatively indicate by strength of signal the amount of analyte bound to each location; (b) inserting the liquid sample into a storage volume in the cassette; (c) producing from the stored sample a continuous flow at controlled rate of the liquid sample over the capture surface for a predetermined interval to enable binding of the at least one analyte to the respective locations of binding agent; (d) developing the complexes of analyte and binding agent at the sites by producing from the liquid developing system stored on the cassette at least one continuous flow at controlled rate of liquid over the capture surface for predetermined duration, sufficient to bind the tag to complexes at the locations in manner to provide quantitative indication of the amount of analyte bound to each of the locations; (e) with liquid stored on the cassette, washing the capture surface to remove unbound material capable of producing false signal; (f) measuring signal produced by the tag at locations on the capture surface to obtain a value representing the fraction of binding sites occupied by the analyte at each location; and (g) performing an operation on the values for the set of locations to determine a value of the concentration of the analyte in the liquid sample.

Preferred embodiments of this method have one or more of the following features:

Each increment of the liquid flows of the method is exposed to heating, and to a bubble removal region for a period of between about 1 and 5 seconds, before flowing over the capture surface.

Each set of locations of binding agent for the method comprises at least 5 locations and the operation performed on the set of values comprises discarding at least one highest and one lowest value and employing intermediate values to determine a mean value.

The developing system employed in the method comprises a detection agent capable of binding at each location in manner based on the quantity of analyte bound at the location, and a signal-producing tag capable of binding to the detection agent, the method including producing, in sequence, continuous controlled flows of a liquid containing the detection agent and a liquid containing the tag. In many cases, preferably, the binding agent is an antigen or antibody and the analyte is, respectively, an antibody or antigen.

The method employs fluorescent tags and measuring is performed by exciting the tags and measuring the resultant fluorescence.

The method is performed with at least 3 locations of binding agent distributed in a row across the width of a flow path for the continuous flow over the capture surface. In preferred cases, the method includes use of at least one row of locations bearing preformed calibration deposits of analyte of predetermined concentration, which are developed, measured, and employed to correlate the signal with concentration and to determine that the system has performed correctly. In preferred cases, there are calibration locations having analyte deposits of differing known concentrations.

The method is performed with flows over the capture surface at Reynolds numbers of the order of 1 or lower, preferably between about 1×10⁻¹and 5×10⁻³.

The method is employed to screen serum banks, which are available in only limited quantities. The method reduces the volume of sample required per assay, increasing the utility and value of the serum banks.

Other aspects of invention concern other combinations of cassette features and their method of use.

According to another such aspect, an assay cassette is constructed to perform a predetermined multi-flow assay in response to control by external apparatus, comprising: a reaction chamber having a capture surface of extended width that carries a two dimensional array of spaced-apart regions of ligand receptors, the two dimensional array including at least three replicates each of multiplicity of ligand receptors; a storage chamber for liquid sample, a storage site for at least one substance required by the assay, and at least one waste chamber, the cassette being constructed and arranged to contain all liquids used in the assay throughout the performance of the assay; heat transfer surfaces arranged to receive heat to heat the liquids to about a desired assaying temperature prior to entering the reaction chamber and to maintain the reaction chamber at about such assaying temperature; and a liquid passage system defining a flow network which includes a transition section that spreads liquid flow to a width corresponding to the width of the capture surface, the cassette adapted, under control of the external apparatus, to direct a succession of continuous flows from the storage chamber and storage site over the capture surface of extended width to the waste chamber in accordance with a multi-flow assay protocol. In preferred embodiments, the assay cassette includes a gas bubble removal system, the cassette constructed to enable exposure of the liquid to the gas bubble removal system prior to reaching the array, whereby gas bubbles produced in the liquid by the temperature change can be removed before the liquid is directed over the array.

Embodiments of assay cassettes featuring this aspect can have one or more of the features described above or one or more of the following features:

The assay cassette is constructed for use with a protocol which produces, on the array, light-emitting tags associated with complexes of receptor and ligand, the cassette having a window constructed and arranged to enable reading of light emitted from tags associated with complexes of receptor and ligand on the capture surface.

The assay cassette has a flow network which includes at least one valve operated by actuating motion applied by the external apparatus to alter a flow path in the flow network.

The assay cassette has a flow network which includes at least one sensing station adapted to receive an optical sensing beam and enable the beam to pass through a flow passage and thence to a detector in the manner that the beam at the detector is altered in detectable manner by arrival of a liquid-air interface in the flow passage at the sensing station, the altered beam useful as a control signal by external apparatus during conduct of the assay. In preferred embodiments of this feature the sensing station includes a mirror constructed to reflect the beam after it passes through the passage, to return the beam through the passage to a detector of the external apparatus, or the sensing station defines a path for the beam to reach a detector on the side of the passage opposite from the side at which the beam was received.

The assay cassette contains an assay-supporting liquid stored in a rupturable pouch, the flow network incorporating a combining chamber for desiccated material useful as a detection antibody or antigen and a second combining chamber for a dry fluorescent or luminescent tag agent, the flow network associated with valves operable by the external apparatus for successively causing continuous flow through the reaction chamber of sample, detection antibodies or antigen in buffer, tag agent in buffer, and wash. In preferred embodiments of this feature, the assay cassette is constructed to deliver wash liquid by the flow network via a dedicated wash passage extending from a storage chamber or it is constructed to deliver wash liquid via a detection antibody or antigen flow passage.

According to another aspect of invention, an assay cassette is provided comprising: a capture surface that carries a two-dimensional array of spaced-apart regions of ligand receptors, at least one liquid storage chamber associated with a displacement pump constructed to displace liquid from the storage chamber to flow through a liquid passage system and over the array, a vented waste chamber to which the liquid is directed after being directed over the capture surface, the cassette constructed and arranged so that during performance of the assay the capture surface lies above the waste chamber, and the waste chamber is arranged in the cassette to receive gravity flow of liquid that has passed over the capture surface. Embodiments featuring this aspect can have one or more of the features described above or the following feature:

The assay cassette is constructed to be disposed at an angle in assaying position relative to a rest position, in which a venting arrangement comprises an air vent communicating with the waste chamber, the air vent comprised of material that is permeable to air until wetted, the material located not to be wetted by liquid in the waste chamber when the cassette is in assaying position and to be wetted by liquid from the waste chamber when the cassette is placed in rest position after use.

According to another aspect of invention, an assay cassette is provided comprising: a capture surface that carries a two-dimensional array of spaced-apart regions of ligand receptors, and a liquid passage system defining a flow network constructed to direct a flow of ligand-containing liquid over the array, the assay cassette having a body of generally planar extent defining at least one liquid storage chamber and at least one valve seat associated with a passage of the flow network, the cassette having a generally sheet-form elastic member mated with a first side of the body, the sheet-form elastic member having a portion over-lying the liquid storage chamber to define a displacement diaphragm for displacing fluid from the chamber in response to a linear pump actuator of external apparatus and the sheet form elastic member having a portion overlying the valve seat to define a valve diaphragm responsive to a linear valve actuator of the external apparatus.

Embodiments featuring this aspect can have one or more of the features described above or one or more of the following features:

The assay cassette defines a sample liquid chamber and a buffer liquid chamber, each associated with a pump diaphragm, and at least two valve seats for valves associated with passages of the flow network, portions of the sheet-form elastic member defining pump diaphragms and valve diaphragms respectively for the liquid chambers and the valves.

The assay cassette includes a combining chamber containing a material to be combined with a liquid, the sheet-form elastic member having a portion overlying the chamber to define an elastic diaphragm adapted to distend and restore in response, respectively, to forward and backward flow to and from the combining chamber of liquid from a liquid storage chamber. A relatively rigid molded cover may lie over the diaphragm, the cover having a molded cavity facing the diaphragm, defining an expansion cavity for the diaphragm and liquid during combining action. The combining chamber may be associated with a displacement pump constructed to operate in both pressure-producing and suction-producing directions.

The assay cassette has a molded body defining on one side the liquid passage system, the valve seat and the volume of the liquid storage chamber and defining on its opposite side a heat transfer surface configured to receive heat conducted from a heater member of the external apparatus.

The assay cassette has a cover of relatively rigid material located outside of and extending over a side of the body of the cassette, a break-away portion of the cover over-lying the displacement diaphragm and connected to surrounding portions of the cover by breakable connections, the break-away portion of the cover adapted to be engaged on its outside by a linear actuator of an external apparatus in the manner that initial displacement of the actuator breaks the breakable connections to form a piston surface of the break-away portion, and continued motion of the actuator displaces the break-away portion and engaged diaphragm to displace fluid beneath the diaphragm into a portion of the liquid passage system.

The assay cassette has a viewing window and a cover lying over the viewing window is sized and arranged to form a light baffle that substantially limits light exposure to the spotted array on the capture surface.

The assay cassette has a liquid storage chamber constructed to receive and store a sealed pouch of liquid for the assay, and protruding from the diaphragm, a projection capable of puncturing the pouch to release the liquid for pumping. A break-away portion of a relatively rigid cover of the cassette may carry the projection, exterior actuation force applied to the break-away portion of the cover effective to separate the break-away portion, and force the projection to puncture the pouch. The projection and elastic diaphragm may be united in predetermined manner in which the projection extends through the diaphragm, and a seal extending between the diaphragm and the breakaway portion extends around the projection.

According to another aspect of invention an assay cassette is provided comprising: a capture surface that carries an array of spaced-apart regions of ligand receptors, a liquid passage system constructed to direct a flow of ligand-containing liquid over the array, and at least one liquid storage chamber, the liquid storage chamber associated with a displacement pump in the form of an elastic diaphragm forming a wall of the liquid storage chamber, the diaphragm constructed to displace liquid from the storage chamber to flow through the liquid passage system and over the array, the liquid storage volume constructed to receive and store a sealed pouch of liquid for the assay, and protruding beyond the diaphragm, a projection capable of puncturing the pouch to release the liquid for pumping and flow over the array.

The assay cassette has the projection and elastic diaphragm united in predetermined manner in which the projection extends through the diaphragm, and a seal extending between the diaphragm and the breakaway portion extends around the projection.

The pouch, prior to use, is held in position separated from the diaphragm and the projection. The pouch may have spacer members constructed to space the pouch from the diaphragm while leaving the pouch accessible to the diaphragm when the diaphragm is displaced.

According to another aspect of invention, an assay cassette is provided comprising: a capture surface that carries an array of spaced-apart regions of ligand receptors, a liquid passage system constructed to direct a flow of ligand-containing liquid over the array, and a liquid storage chamber constructed to receive the liquid from the exterior via a needle or pipette projected through a septum, the septum comprising an elastomeric mass that has a pierced passage, the elastomeric mass mounted under substantial compression relative to the pierced passage (e.g. mounted under compression transverse to the passage, e.g. radially), the compression effective to maintain the pierced passage closed but enabling insertion and removal of a plastic liquid-supply needle or pipette through the pierced passage.

According to another aspect of invention, an assay cassette is provided which is controllable by external apparatus and comprising: a capture surface that carries an array of spaced-apart regions of ligand receptors, a liquid passage system constructed to direct a flow of ligand-containing liquid over the array, the liquid passage system comprising a flow network which includes at least one sensing station adapted to receive an optical sensing beam and enable the beam to pass through a flow passage and thence to a detector in the manner that the beam at the detector is altered in detectable manner by arrival of a liquid-air interface in the flow passage at the sensing station, the altered beam useful as a control signal by the external apparatus during conduct of the assay. The sensing station may include a mirror constructed to reflect the beam after it passes through the passage, to return the beam through the passage to a detector of the external apparatus, or the sensing station may define a path for the beam to reach a detector on the side of the passage opposite from the side at which the beam was received.

According to another aspect of invention, an assay cassette comprises: a capture surface that carries an array of spaced-apart regions of ligand receptors, a liquid passage system constructed to direct a flow of ligand-containing liquid over the array, and a liquid storage chamber arranged to discharge via a portion of the liquid passage system into a combining chamber containing a material to be combined with liquid, the chamber having a wall defined by an elastic diaphragm adapted to distend and restore in response respectively to forward and backward flow of the liquid from its storage chamber. The material to be combined with liquid may be desiccated detection antibody, antigen or tag agent stored in the chamber prior to use. A relatively rigid molded cover may lie over the diaphragm, the cover having a molded cavity facing the diaphragm, defining an expansion cavity for the diaphragm and liquid. The chamber may be associated with a displacement pump constructed to operate in both pressure-producing and suction-producing directions.

According to another aspect of invention, an assay control apparatus is provided for performing an assay with any of the assay cassettes described above, the cassette having at least one displaceable membrane associated with a liquid storage chamber to form a displacement pump, the apparatus having a linear actuator mutually constructed and arranged to progressively displace the displaceable membrane over a controlled period to produce a timed continuous flow of liquid through the passage system and over the capture surface of the cassette.

The assay control apparatus may have one or more of the following features.

The assay control apparatus has multiple linear actuators of similar construction for use with an assay cassette having a corresponding number of membrane displacement pumps.

The assay control apparatus has one or more valve actuators for engaging diaphragm stop valves of the cassettes.

The assay control apparatus has a cassette receiving station constructed and arranged to dispose a cassette at substantial angle to the horizontal relative to the rest position of the cassette to orient a gas bubble removal chamber of the cassette in operating position and to dispose a waste chamber to receive waste from the capture surface by gravity flow.

The assay control apparatus incorporates an optical reader.

The assay control apparatus incorporates an optical system for detecting arrival of a liquid air interface within a liquid passage of a cassette.

According to another aspect of invention an assay system comprises a cassette and an assay control apparatus, the cassette comprising a capture surface that carries an array of spaced-apart regions of ligand receptors and a liquid passage system constructed to direct over the array a slow flow of assay-supporting liquids having Reynolds numbers less than about 1, the liquids including a ligand-containing liquid, the cassette including a gas bubble removal system to which the liquids are exposed, the gas bubble removal system constructed and arranged to remove gas micro-bubbles from the liquids prior to exposure of the liquids to the array, the bubble removal system of the assay cassette comprises at least one buoyancy chamber to which the liquid is exposed, the assay control apparatus having a cassette receiving station constructed and arranged to dispose a cassette at substantial angle to the horizontal relative to the rest position of the cassette to orient the buoyancy chamber of the cassette in operating position and to dispose a waste chamber to receive waste from the capture surface by gravity flow.

Embodiments of this aspect may have any of the features described above for assay control apparatus and for cassettes having buoyancy chambers for gas bubble removal.

The aspects of invention described above contribute to a robust general approach to achieving multiple ligand receptor-ligand assays in a miniaturized format with high sensitivity and high precision, and to solving the problems of implementation in low-cost, highly reliable ways.

Another aspect of invention is a general improvement of microfluidic biological assays carried out under extremely low Reynolds Number (N_Re). Such assays depend on the diffusion behavior of the analyte, as the molecular motion by diffusion is greater than that achieved by liquid motion. The diffusion properties (the time to mix by diffusion) are strongly influenced by the temperature of the liquid. The diffusion coefficient for bio-molecules in water is proportional to the absolute temperature of the assay and inversely proportional to the viscosity of water. For example when an assay temperature is raised from 25 to 37 degree Celsius, the diffusion coefficient is multiplied by 1.34 and the time to mix by diffusion to reach the same assaying condition is reduced by the same amount. Protein based bioassays are commonly terminated prior to equilibrium condition having been reached as equilibrium may require as long as a few hours. It is highly desirable to heat the analyte preferably to the normal body temperature rather than proceed at room temperature or storage temperature. Aspects of invention presented here enable this to occur without detriment.

Another aspect of invention deals, generally, with deficiency in the application of microfluidic systems to protein-based biological assays, concerned with the difficulty of sensing the passage of fluids through small channels. The absorption difference between air and water in a channel of less that 100 micron thick is extremely small, and peaks at 0.5% of that of air alone when viewed in the near IR. Aspects of invention presented here solve this dilemma by detecting not the change in liquids but the liquid-to-air interface as it arrives due to index of refraction at the interface.

Another aspect of invention deals, generally, with deficiency in microfluidics concerning the necessity of introducing samples containing protein, such as serum, into microfluidic devices through narrow typically stainless steel needles that have high internal surface area vs. volume. This has seemed to be a requirement due to the fact that, heretofore, septums used to seal ports of the device are made from materials that are highly rigid and impermeable. The rigidity of the material was thought necessary to provide a sufficient seal to ensure that the device would not leak. This has been a disadvantage, because commonly-used plastic pipette tips are not sharp enough to puncture a rigid septum, and thus could not be used to inject sample in the device. A transversely or radially compressed, pre-pierced septum provides a microfluidic device for performing a protein-based biological assay that is sealed with a septum that can be penetrated by a blunt instrument, and preferably by an instrument having a thicker bore, such as a plastic pipette tip.

In another aspect of invention, features are provided to prevent a user from improper handling of the microfluidic cassette device.

Another aspect of invention features a device, i.e. a cassette or cartridge, that includes one or more capture agents specific for one or more analytes, e.g., a panel, or biomarkers. The cassette or cartridge is used to perform several functions in a single device, such as sample capture, gas bubble removal, system calibration, and the measurement of analytes in a liquid sample. Preferably, the device is used in combination with a processing/reading instrument for the simultaneous measurement of one or more analytes. The device can be inserted in the associated processor/optical reader instrument, which automatically operates a number of necessary functions and images the reaction chamber for analysis of the assays as described below. Preferably, the device is a disposable device.

Another aspect of invention permits the simultaneous performance of a multitude of miniaturized sandwich assays, combining dilution series of a given capture molecule as well as a choice of different capture molecules. A fluorescent label can be used to provide a signal that can be read using an optical reading station, such as that exemplified in WO/04/017374A2 (PCT/US03/25702), hereby incorporated by reference. Other detection labels can also be used, such as luminescent molecules and chromogenic dyes. Capture molecules are preferably adsorbed to a nitrocellulose based surface exemplified by associated patent application WO/04/018623A2 (PCT/US03/25685). In addition, the device described herein can be used to perform nucleic acid based assays.

Another aspect of invention involves use of larger (in comparison e.g. to some cassettes available for genetic research) reaction-chambers on a cassette with assay redundancy, and consequently less ambitious reaction/assay densities, that lead to greater assay reliability. By these provisions, analyte molecule depletion by the capture sites is minimized and gap dimension tolerances can be relaxed to yield economic manufacturing of the cassette. Micro-bubbles and other perturbations can be statistically minimized and have relatively little consequence. Larger reaction chamber and appropriate temperature control and flow duration alleviate the effect of substantial differences in viscosity and diffusivity of analyte. Control assays can be incorporated and processed simultaneously. Thus one can simultaneously perform a plurality of sandwich assays or complimentary assays with a high degree of certitude.

Another aspect of invention is a self-calibrating biochip for conducting an assay comprising a capture surface bearing a set of replicate deposits of a given ligand receptor for the assay and bearing, in association with that set, a set of calibration deposits that comprises a number of groups of replicate deposits of the ligand for which the ligand receptor is specific, the groups being of respectively different known dilutions of the ligand, the known dilutions, selected, when developed, to be sufficient to define a calibration curve for assay measurements made at the deposits of the given ligand receptor after their exposure to a sample containing the ligand, the groups of calibration deposits being adapted to be developed by attachment of a readable tag to all ligand on the capture surface at the deposits of ligand. Preferably at least one row of control deposits of given measurable intensity is also included on the capture surface of the biochip for verification of operation of the measuring system.

Preferred embodiments of this aspect of invention have one or more of the following features.

The deposits comprise spots in a spotted array.

The tag is a fluorescent tag.

The biochip is constructed for exposure to a sheet-form stream of sample and reagent having a direction of flow, the replicate deposits being spots arranged in at least one row oriented transverse to the direction of the flow, and the groups of calibration deposits being spots arranged in rows transverse to the direction of the flow.

The replicate deposits of ligand receptor are in one or more rows transverse to the flow, for instance a row of ten spots, and calibration deposits of each given dilution are arranged in one or more rows transverse to the flow, for instance each group comprising a row of ten spots.

A row of replicate deposits of the ligand receptor may, for instance, occur in lead position relative to the flow, followed by successive rows of calibration deposits. The successive rows of calibration deposits may be arranged in order of dilution, the highest dilution being first occurring following the replicate deposits of ligand receptor. The deposits of ligand receptor and ligand may be, for instance, of spot form oriented in a pattern relative to the flow such that each spot is most closely followed by spots that are offset from alignment in the direction of flow with the preceding spot.

The capture surface is of extended width carrying, in transverse arrangement, deposits of more than one ligand receptor and associated calibration deposits.

Another aspect of invention is an assay method employing a self-calibrating chip of any of the kinds just described, which includes exposing the capture surface to a flow of sample containing the ligand followed by exposing the capture surface to conditions by which a readable tag becomes attached to all ligand present, reading the tag by a reader to obtain measurements of each deposit, analyzing the data from the group of calibration deposits to develop a table of calibration values, comparing a value derived from the group of ligand receptors with values from that table and deriving therefrom a value representing the concentration of the ligand in the analyte. In preferred embodiments the tag is a fluorescent tag, and the reader is a fluorescence reader.

In general, the analyte to be detected is a compound, composition, aggregation, or other substance that can be specifically captured from a complex mixture of compounds, compositions and aggregations. That is, the analyte, or portion thereof, will be antigenic or haptenic having at least one determinant site, or will be a member of a naturally-occurring binding pair, e.g., carbohydrate and lectin, hormone and receptor, complementary nucleic acids, and the like. Analytes of particular interest include antigens, antibodies, proteins, carbohydrates, haptens, drugs, hormones, hormone metabolites, macromolecules, toxins, bacteria, viruses, enzymes, tumor markers, nucleic acids, and the like, although other types of substances may also be detected.

The systems presented are useful in assaying for a wide variety of analytes in virtually any type of sample which can be provided in a liquid form. Especially suitable are biological specimens, such as blood, serum, plasma, urine, cerebral fluid, spinal fluid, ocular lens liquid (tears), saliva, sputum, semen, cervical mucus, scrapings, swab samples, and the like. Cell lysates (cell culture supernates) can be used. In addition, the method is suitable for industrial, environmental and food samples, such as water, reservoirs, process streams, milk, meat, poultry, fish, conditioned media, and the like. Under certain circumstances, it may be desirable to pre-treat the sample, such as by suspending in liquid, separation, dilution, concentration, filtration, chemical treatment, or a combination thereof, in order to improve the compatibility of the sample with the remaining steps of the assay. The selection and pretreatment of biological, industrial, and environmental samples prior to immunological testing is well known in the art.

Categories of immunoassays that may be performed include direct and indirect competitive assays, and non-competitive assays such as sandwich assays. A competitive assay relies on competition for binding to a specific binding agent between a known amount of labeled analyte and an unknown amount of analyte in the sample. The more analyte that is present in the sample, the less binding agent available to bind to a competing analyte or analyte-analogue. Preferably, the method is based on a sandwich immunoassay. In a sandwich assay, a binding agent (ligand receptor) is immobilized on a solid support to serve as a capture agent. Analyte (the ligand) in the test sample is allowed to react with the binding agent on the support. Afterward, a second, detectable agent (that includes a tag or can receive a tag) binds specifically to a different epitope on the analyte, the analyte becoming “sandwiched” between the detectable binding agent and the immobilized binding agent. After any excess detectable binding agent or later-added tag is washed away, observations are made of the detectable agent in the sandwich complex. The observed signal is directly proportional to the amount of analyte in the test sample.

An especially important contribution here is the provision of features that contribute to a single assay technique (or “platform”) for protein biomarkers which, above all, is robust. The assay technique can produce highly credible results, with low coefficients of variation (and so is highly repeatable), and is immune to interferences and performs its function with sufficient margins that it is useful over a wide range of analytes, levels of dilution and starting conditions that heretofore have called for using a number of different assay techniques. Furthermore, such a robust assay technique is provided that also is sensitive, is capable of significant throughput, employs equipment that is easy to use and has small footprint, and is capable of extensive multiplexing (conducting multiple assays at once). Preferred embodiments are implemented to require little sample or reagent, to require little handling of the sample, and to enable simple design of particular assays.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows, by isometric diagram, a wide capture surface in a reaction chamber exposed to a flow of analyte, whileFIG. 1A depicts separated spots of ligand receptor on the capture surface and the volume of ligand-containing liquid to which a spot is exposed.

FIG. 2, as one example of prior art, shows one of multiple lanes of a cross-lane flow configuration, whileFIG. 2A depicts the area of analyte flow exposed to a cross-lane of capture reagent.

FIG. 3 depicts a capture surface and spotted array of an assay cassette;FIG. 3A is a summary plot of a series of computer simulations of the cassette design ofFIG. 3, showing the average concentration of ligand receptor-ligand complex on the first row of a 2 dimensional array produced by use of various flow rates and gap heights H, referencingFIG. 1.

FIG. 4 is a diagram of a generalized disposable assay cassette and steps performed on the cassette, whileFIG. 4A depicts one preferred embodiment of it.

FIG. 5 is a diagram of a disposable cassette with activatable components to perform an immunoassay of sandwich type;FIG. 5A, similar toFIG. 5, illustrates the relationship of the cassette to external apparatus that activates the components and performs the assay.

FIG. 6 is a plan view of the interior of the face side of a presently preferred embodiment of the cassette concept ofFIG. 5, in this case employing a buoyancy chamber as a preferred bubble removal system;FIG. 6A is a plan view of the exterior of the back side of the cassette, shown in relation to an external heater.

FIG. 7 is an exploded isometric view of elements of the cassette ofFIG. 6.

FIG. 7A is an isometric view of the back side of a cassette body of slightly different construction having the same functioning elements as the embodiment ofFIGS. 6, 6A and7.

FIG. 8 is an isometric view of a system control unit which incorporates a reading capability;FIG. 8A is a plan view of the interface of the unit with the face side of the cassette ofFIG. 6;FIG. 8B is a perspective view of interfaces of the control unit for engagement with the cassette;FIGS. 8C and 8D are plan and cross section views showing details of the heater of the control unit;FIG. 8E, is a diagrammatic cut-away view of the control unit showing mechanical actuators for the cassette;FIG. 8F is a similar cut-away view of the reader system within the control unit.

FIG. 9 is a schematic illustration of a passive microfluidic capillary burst valve.

FIGS. 10 and 10A are schematic illustrations of alternate versions of a bubble trap implementation of a bubble removal system of a cassette.

FIG. 11 is an exploded view of the components of a liquid-containing pouch useful with the cassette.

FIG. 12 illustrates puncturing the pouch ofFIG. 11 using a projection that protrudes from an elastic diaphragm of the cassette;FIGS. 12A, 12B and12C, illustrate progressive positions of the linear actuator relative to the pouch.

FIGS. 13 and 13A illustrate a diaphragm valve of the cassette ofFIGS. 6 and 7, respectively in open and closed positions, whileFIG. 13B is a magnified view of a region where slight leakage may occur andFIG. 13C illustrates a combination that can overcome leakage if the leakage is sufficient to be detrimental.

FIG. 14 is a diagram of an optical-sensor employed to sense the arrival of a liquid-air interface in a channel of the cassette.

FIGS. 15 and 15A are exploded and cross-sectional installed views of a system that seals a sample injection port to the cassette and facilitates introduction of plastic pipettes and the like.

FIGS. 16, 16A and16B are formats of spotted arrays.

FIG. 17 is a diagram illustrating the automated assay action, whileFIG. 18 illustrates the reading of the results of the assay when fluorescent tags are employed.

DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS

FIG. 1 shows, in magnified view, cassette reaction chamber A receiving flow B of a ligand-containing liquid. The liquid flows over array C of ligand receptors on a capture surface D. In preferred embodiments, characteristic dimensions of the two-dimensional array C are greater than about 0.5 cm; in one preferred embodiment the capture surface is 9.7 mm wide, W, and 12.5 mm long, L. The gap height H of sheet-form flow over the capture surface is preferably between about 80 and 300 μm (micron). In preferred embodiments, gap H is between 100 and 200 μm. The array C of capture reagent is located at a safe distance from the channel corners, typically 1.5 mm. This helps avoid any gas micro-bubbles that might grow in the corners.

FIGS. 1 and 1A show capture reagents attached to the surface D of a solid support as round spots R are grouped in subsets associated with specific ligand receptors. While spots shown inFIG. 1 are in rectangular groups, which can be effective, rows of replicate receptors arranged transversely to the flow followed, by rows of reference spots, as inFIGS. 16 and 16A, have advantages that will be described. In thepreferred embodiment 6 to 10 replicate spots of diameter between about 50 and 500 μm are employed in each group or row.

Another option suggested inFIG. 1 is the printing of ligand receptors in the shape of lanes E with one or a number of lanes, possibly 125 μm×1,000 μm, spaced apart 250 to 500 μm.

As will be explained, statistical analysis of replicate data can minimize errors due to spotting inaccuracies, obscured regions, highly polluting fluorescent particulates, and other causes. In another method, pixel data signal from all spots or lanes with equal capture reagent may be aggregated prior to use in analysis.

With reference toFIGS. 2 and 2A, one example of a prior art cassette employs microchannels to define a small reaction interface. A lane of capture reagent C′ is intersected by a microchannel filled with analyte B′. In an idealized immunoassay, equilibrium might be attained, but in practice the assay is usually terminated before reaching equilibrium or, as may be the case, without knowing if equilibrium has been reached. Numerous variables contribute to reaction inconsistency in a given assay of this type. These include variations in the molecular density in the liquids as well as in viscosity and diffusivity, and include binding of micro-bubbles of air or gas as well as micro-particulates. All of these can disrupt the accuracy of the reaction. Micro-bubbles tend to lodge in corners, especially where surface properties exhibit a discontinuity such as where capture analyte intercepts a microchannel. Note that a 50 μm diameter micro-bubble lodging on a 100×100 μm square area assay region would obscure 20% of the assay region and cause a similar signal level error. Provision of redundancy to minimize these sources of error would tend to defeat benefits of units of this type.

An aspect of invention here is, within the confines of a cassette, using continuous, wide flows with low Reynolds numbers, to create a comparatively large area of bound reagent of approximately equal molar density, to produce a digital image which can be analyzed according to statistical principles to determine the most probable result of the assay in question.

FIGS. 1A and 2A help visualize the relationship of fluid flow to reaction areas ofFIGS. 1 and 2.

InFIG. 2A there is a small diffusion distance H, typically less than 50 μm, in which analyte depletion is a concern. To counter this, a comparatively high fluid flow rate, as compared to diffusion travel, is employed. This is used to replenish complexed analyte and consequently achieve attachment of a sufficient amount of label that a high signal to noise ratio can be obtained, to quantify the amount of analyte present in the liquid. This high flow rate as well as the critical geometric tolerance of the design ofFIG. 2A directly impacts the diffusion efficiency and consequently the availability of analyte molecules to be complexed on the capture array. In addition, the exact dimensions of the capture area A₂that is exposed to liquid becomes critical to the measurement. For such reasons, coefficients of variation of 20% or above may be obtained with such approaches.

FIG. 1A suggests that a capture area A₁can be supplied by a large source of analyte molecules both to the sides of the ligand receptor spots R and in a greater gap (gap H). Using sufficiently low Reynolds numbers, diffusion is the dominant mode of molecular motion. Because the source of analyte is large relative to capture area, neither flow rate nor geometric tolerances are critical factors. In addition, with flow rate comparatively slow, the occurrence of micro-bubbles and the necessary volume of analyte can be reduced.

InFIG. 3 a capture surface D and spotted array C (see alsoFIG. 1) are modeled for a disposable cassette.

FIG. 3A is a plot of a computer simulation of the performance of the system ofFIG. 3A. It shows a change in the average flow velocity from 45 μm/s to 613 μm/s (a 13.6 ratio) coupled with a gap dimension H change from 220 to 80 μm causes a maximum of only a 50% change in complex concentration in the linear region of the time dependent assay (approximately 10 to 30% of the time required for equilibrium condition, defined as 95% of theoretical equilibrium). Extrapolation indicates that a 10% change in flow velocity and in gap tolerances would have a worst case consequence of complex concentration varying less than 1%, indicating the worthiness of the general system design ofFIG. 3.

In preferred cases, all liquids employed in an assay are stored on board an assay cassette, and out of concern for keeping the liquids on board the cassette to be of small volume, the flow in the reaction chamber has N_Reless than about 1×10⁻¹, preferably between about 1×10⁻¹and 5×10⁻³, and the gap H is maintained between about 80 and 200 micron. For instance, in one preferred embodiment, employing the design ofFIGS. 6 and 7 constructed for a sandwich assay, to be described, employing 2 ml of buffer liquid in thepouch12, and adapted to receive 0.2 ml of liquid sample, with gap H of 0.1 mm (100 micron) at the reaction chamber, the flow through the chamber may be approximately uniform and have N_Reof about 2.7×10⁻². This specific embodiment is considered to be another important aspect of invention.

Besides being of importance in their own right, the principles ofFIGS. 1, 1A,3 and3A when combined with a gas bubble removal system on the cassette itself, (seeFIG. 4) leads to many advantages.

As previously mentioned, gas micro-bubbles can be produced by liquid temperature change, as well as by atmospheric pressure change and localized liquid pressure change, as liquids encounter sharp edges, space discontinuities, or variation of surface properties such as surface roughness or different surface tension properties. We have realized, that in the context of assay cassettes, the generation of gas micro-bubbles has heretofore not been adequately recognized or taken into account. Assay cassette systems employing the concept ofFIG. 4 overcome these difficulties, and enable performance of complex assays, with all liquid confined within the cassette, without need for expert personnel.

In many circumstance, prior to use, it is desirable to store a cassette with its liquids on board under refrigeration or under ambient conditions. By use of the principle ofFIG. 4, the cassette may be brought to standard temperature, e.g. to living body temperature for biological assays, and despite release of gas micro-bubbles, very good results can still be obtained. Likewise, economical and reliable pumping, valving and liquefication actions, that may tend to produce detrimental gas micro-bubbles, can all be accommodated.

Various kinds of gas bubble removal systems, developed in other fields such as for liquid jet printing and diesel fuel systems may be employed in the embodiments ofFIG. 4 orFIG. 5 (see bubble removal system indicated generically at128 inFIG. 5). Examples include the use of diffusion membranes that are permeable to gas but not to liquid and use of the principle of a capillary gradient transverse to an axis of capillary transport to guide gas bubbles in a direction different from the transport direction of the liquid, as shown in U.S. Pat. No. 6,682,186, incorporated herein by reference in respect to the gas bubble removal technique.

However, for reliability and ease of implementation using simple features molded in plastic, a flow-through buoyancy chamber is presently preferred. Referring toFIG. 4A, a complex immunoassay is performed on a cassette in which the concepts ofFIGS. 1, 1A,3 and3A are combined with the concept ofFIG. 4, and implemented with a flow-through buoyancy chamber, (inFIG. 4A, “Bubble Trap”.) A preferred form of bubble trap shown at130 inFIG. 6 will later be described in detail in reference toFIGS. 10 and 10A.

Referring toFIG. 4A, a common flow path M is provided for successive continuous, timed flows of analyte ligand, detection ligand and fluorescent tag. In this case, wash liquid also flows through passage M. Passage M directs the flow through a lower portion F_Lof a buoyancy chamber F (“Bubble Trap”). At least the lower portion F_Lof chamber F constantly contains liquid. With laminar flow through this portion of the chamber, each increment of liquid flow is exposed for a sufficient period (preferably between 1 and 5 seconds) that micro-bubbles rise toward the upper portion F_Uof the Bubble Trap under buoyancy force attributable to the much lower density of gas micro-bubbles than the liquid which displaces it. Thus by gravity effect, the micro-bubbles are forced to leave the flow and rise to upper portions of chamber F. An outlet passage G guides the exiting bubble-free laminar flow through a flow transition section T where the liquid flow spreads to a sheet-form flow over the capture surface D. It spreads e.g. from a flow cross-section of about 0.25 mm²or less, to a flow cross-section of at least 0.75 mm².

Preceding the buoyancy chamber, the liquid has been subjected to actions appropriate to the assay being performed. InFIG. 4A heating is the action illustrated. As shown, three liquids: analyte ligand, detection ligand and fluorescent tag flow over the heat transfer surface J. Each liquid can be brought to approximately assay temperature preceding the buoyancy chamber. Gas micro-bubbles produced due to reduced gas solubility with increased temperature can thus be removed. For simplicity of design, the wash liquid may likewise transit the path through the bubble chamber, albeit presence of gas micro-bubbles at wash stage may be of no consequence.

According to the general principle ofFIG. 4A, one or more of the liquids for the assay may originate from exterior of the cassette. Another aspect of invention, however, is the possibility, owing to the slow flow characteristics of the preferred system, that all liquids, may be stored in suitable quantity on board the cassette, as inFIG. 6.

Another feature of the design ofFIG. 4A is waste chamber system K, sized to receive and contain all waste liquids from the assay. In this design the components of the assay are in a generally planar format. In operation the plane is inclined to the horizontal, as indicated by “up” and “down”. Besides orienting the buoyancy chamber above the liquid flow path, it enables uniform upward sheet-form flow over the array C on the capture surface D, and thence, by gravity flow, to the waste system K.

An air vent arrangement V₁, at the buoyancy chamber, enables the chamber to be filled with liquid, and air vent V₂at the waste chamber enables air to be expelled from the liquid passage system during initiating phases of the assay. The vents may be obstructed by material that passes air but not liquid. Thus after the performance of the assay, the cassette plane PL defined by coordinates X and Y, may be placed horizontally without escape of the liquid.

Referring toFIGS. 5 and 5A, a scheme embodies the concepts ofFIGS. 1, 1A,3,3A, and4, without limitation to type of bubble removal system. Though useful in general for ligand receptor-ligand assays, it is shown adapted for an immunoassay.

InFIGS. 5 and 5A,liquid sample15 containing the analyte, e.g. blood serum, is introduced through aseptum32 to a sample chamber orreservoir134 withincassette50. Adisplacement pump30 is associated withsample reservoir134 for forcingsample15 throughpassage31 into other regions of the system.Heat exchanger33 heatsliquid sample15 while other parts ofheating system34 heat other liquids for the assay. The heating system may be arranged to bring the liquids to approximately assaying temperature, e.g. physiological temperature, 37° C. For other parts of a liquid containment system, liquid storage cavity orchamber135 is provided, e.g. for buffer liquid, associated withdisplacement pump37.Pump37 provides liquids as needed to support the assay, e.g. wash liquid and liquid to

chambers

131 and142 to liquefy, dilute or mix other reagents contained within the body ofcassette50. For an immunoassay, dry detection antibody may be coated on a surface ofchamber131 and dry fluorescent tag coated on a surface ofchamber142.

Abubble removal system128, shown generically, receives a succession of continuous liquid flows from

chambers

134,131 and142. It removes micro-bubbles produced previously in the liquids, following which the liquids proceed, in succession, throughreaction chamber133 for exposure to a capturesurface carrying array20 of ligand receptors. The flows are produced by a system of passages controlled by externally driven

pumps

30 and37 and externally activatedvalves137A, B and C driven in response to

sensors

150 and152 that sense the arrival of a liquid-air interface in the respective passages.

Waste chamber

139 receives liquid waste from flows through thereaction chamber133. As indicated by “up” and “down”, the plane PL of the cassette is oriented at a substantial angle to horizontal during use to produce gravity flow from thereaction chamber133 to wastechamber139. The waste chamber is vented at140 and the upward flow arrangement of the passage system to the waste outlet enables air in the system to be expelled by action of the displacement pumps30 and37 prior to initiation of the assay.

FIG. 5A illustrates the functional relation between features of the cassette and features of external apparatus.

FIGS. 8 and 8A show asystem control unit60. In this case it incorporates all external functional components. Alternatively, the components can be in separate units under electronic control.Control unit60 includessystem display63 and areceptacle66 for thecassette50. The surfaces of the receptacle dispose the planar cassette at a substantial angle α to horizontal, here 60°, at which it is latched into place. Referring toFIG. 8E, two stepper motor linear actuators70 (one shown in the diagram) operate the two

diaphragm pumps

30 and37. Three valve actuators71 (one shown in the diagram) operate the three active valves of the cassette. The progress, performance, and results of the assay can be observed and monitored bysystem display63 or by the monitor of an associated computer. After the reaction is complete and all measurements have been read,cassette50 can be removed and discarded.

Cassette

One preferred implementation of the cassette and control system ofFIGS. 5 and 5A is shown inFIGS. 6-15. It employs a bubble removal system based on the buoyancy principle illustrated inFIG. 4A.FIG. 6 is a plan view of the face side of molded body (base)13 ofcassette50 whileFIG. 7 is a perspective, exploded view of the cassette assembly. The assembly comprisescover1, double-sided adhesive sheet3,elastic membrane7, double-sided adhesive sheet8 and a liquid-containingpouch12 in the sequence of their assembly tobase13. Additional components of the assembly includeclear window5 for the reaction chamber, mirrors11A and11B and

clear windows

6A and6B for

optical sensing stations

150 and152 for detection of liquid-air interfaces in the passages,septum member137 and itsretainer136 for receiving liquid sample, ventplug9 for the waste system andclosure panel14 used at the back of the base to complete liquid passages to waste chambers of the cassette. Referring toFIG. 6, the moldedplastic body13 is configured to define all of the liquid storage and passage system. These includeseptum receptacle32,sample reservoir134,liquid chamber135, firstdry reagent reservoir131, seconddry reagent reservoir142, a bubble removal system in the form of abuoyancy bubble trap130,reaction chamber133,waste receptacles139A and B,receptacle140 forvent plug9, and communication passages underbridge10 which together withclosure panel14 join thewaste receptacles139A and B.

receptacles

139A and139B have depth corresponding substantially to the overall thickness t of moldedbody13. Their bottom walls are generally coplanar with the lower edge E_Lof the perimeter wall PW of the cassette, seeFIG. 6A, forming part of the backside of the cassette. Septum receptacle32 (accessed from the backside) andsample reservoir134 have substantial but less depth. The remainder of the fluidic system is relatively shallow, formed as channels and depressions in a generally planar face wall FW of the cassette that lies substantially aligned with the upper edge E_Uof the perimeter wall PW. The backside of face wall FW defines planarbottom surface13A for receiving the heater as later described with reference toFIGS. 6A and 7A.

The moldedbody13 thus defines (in face wall FW) all connecting passages, including a serpentine passage inregion33′ for heating pumped liquid sample, the valve seats forvalves137A, B and C, microfluidic capillary burstvalves138A through G, and the

optical sensing stations

150 and152.

Referring toFIGS. 6 and 7, the cassette is formed by attachingcover1 tobase13 via the intervening

adhesive sheets

3 and8 and themembrane7. When assembled,cassette50 has a flow network of interconnected cavities and channels for liquids of the assay, closed by over-lyingadhesive sheet8. Integral portions of the elastic membrane respectively define displaceable pump diaphragms over

chambers

134 and135, valve diaphragms overvalve seats138A, B and C, and an elastically expansible wall over one of the liquefyingchambers131. Thecover1 is formed of relatively rigid plastic and has break-away

portions

1A,1B that overlie the sample and liquid chambers,134,135, to act as heads of diaphragm-actuating pistons.Sample chamber134 is assembled as apump30 when double-sided adhesive sheet8 bonds a region ofelastic membrane7 tobase13 and double-sidedadhesive sheet portion2 bondsdetachable segment1A of the cover to the elastic membrane, to form a piston head suitable to be driven by an external linear actuator.

Preferably,base13 is of non-fluorescent, rigid thermoplastic, and can be injection molded. Flow of liquid in the channels is favored by preparingbase13 with material that is hydrophilic, such as glass, Cyclic Olephine Copolymer (COC), polyethylene tetraphtalate glycol (PETG), LEXAN® (General Electric Company Corporation, NY, N.Y.), or a form of polymethyl methacrylate (PMMA) such as, e.g., Plexiglas® (Rohm & Haas Company, Philadelphia, Pa.) or Lucite® (E.I. Du Pont Nemours And Company, Wilmington, Del.).

Preferably, the doubled-

sided adhesive sheet

3 or8 has an adhesive strength in the range of 1300 g/25 cm width. A suitable material is Medical Double Coated Tape # 1509, 1510 or 1512 (3M Innovations Co.). It is provided with exterior dimensions generally corresponding with those of the planar moldedbody13. Strategically located regions ofsheet8 are removed prior to assembly to provide openings (“windows”) tobase13 below. These cut-outs regions form

sensor windows

8A and8B,window8C to formsample pump30,window8D to form liquefyingchamber131,window8E to formliquid storage pump37,windows8F, G and H to form active stop valves and window8I to form reaction chamber window.Membrane7, an elastic membrane material, is attached by adhesive of the top side ofsheet8 and forms elastic diaphragms at the pump and valve openings or windows insheet8.

Membrane

7 is preferably a sheet-form rubber material, e.g. rubber latex. To be suitable formembrane7, a material should be capable of being perforated or cut into shapes with clean edges, be lightweight, smooth, capable of stretching without slippage, tear-resistant, high in tensile strength, e.g., tensile strength within the range of 100 psi to 10,000 psi, or 4,000 psi, and have an elongation factor ranging between 200% and 750%. Suitable materials formembrane7 include, latex sheeting of ˜0.006″ thickness (Latex Sheeting B-LRS-6, Small Parts Inc., Miami Lakes, Fla.).

The second double-sided adhesive sheet3 is situated on top ofmembrane7.

Regions are cut out ofsheet3 prior to assembly oversample reservoir134,buffer pouch12 and liquefyingchamber131. Adhesive cut-outs registering with

detachable elements

1A and1B of the cover serve to join those elements to theelastic membrane7 to form the liquid displacement pistons previously mentioned.Sheet3 is also suitably configured to provide exterior access tobody13 for actuators for the valves and light paths to and from the sensors.

Thecover1 is attached to the top side of exposedadhesive sheet3 and is sealable to base13 by using adhesive, heat, or ultrasonic welding techniques. Preferably,cover1 is made of a non fluorescent polymer similar to that ofbase13 and is preferably black to serve as a light baffle bounding the aperture by which the capture surface is to be optically read.Cover1 is molded with breakable tab portions T of stress-concentrating configurations to break and release

detachable elements

1A and1B. In this embodiment, overchamber131,cover1 has a molded upward impression in its undersurface. The impression corresponds to the shape of liquefyingchamber131 and is of uniform depth. It defines an expansion region for the corresponding portion of theelastic diaphragm7 to enable increase of thechamber volume131 during liquefication of dry agent. In another embodiment,cover1 is a membrane or a film, for example a bonded resilient plastic film. Where it is desired that the user of the cassette device be able to view the interior contents of the device,cover1 can be transparent in desired regions.

The liquid passage network shown inFIG. 6 is formed by channels molded inbody13, and closed by corresponding areas of the adhesive sheet. The passage network connects all liquid storage chambers to asingle inlet160 to buoyancy chamber130 (formed also as a depression in face wall FW of body B, as shown, and closed by overlying adhesive sheet8). Sample flow, when initiated bypump30 ofsample chamber134, is received bybuoyancy chamber130 fromheater labyrinth33′. Reagents and wash liquids when displaced bypump37 ofliquid storage chamber135, under valve control, are received via

reagent chambers

131 and142 and washchannel143. Asingle outlet130B transmits liquid flow from the buoyancy chamber viaflow transition section133A toreaction chamber133.

As shown inFIGS. 6A and 7A, the backside of moldedbody13 hascavity16 coextensive with and extending slightly beyond the shaded region ofFIG. 6A (representing external heater101).Cavity16 has planarbottom surface13A formed by the back-side of face wall FW. It underlies those portions of the flow system to be heated. The portions to be heated include: serpentineliquid sample passage33′,

reagent chambers

131 and142, the connecting passage network leading to and including thebuoyancy chamber130, and the further passage to, and including thereaction chamber133.

The molded body ofFIG. 6 has alignment openings G¹to receive alignment pins G of the control unit, seeFIG. 8A. Likewise the molded body has a set of space-apart raised reference pedestals for establishing planar alignment of the cassette with reference surfaces of the control unit.

FIG. 7A, further shows the back-side of the cassette body.Portions135′,139A′ and139B′, relating respectively, toliquid chamber135 and the twowaste receptacles139A and B are coplanar with the lower edge E_Lof the perimeter wall PW of the cassette body.Planar bottom surface13A underlies shallow portions of the fluidic system defined by the opposite side of face wall FW.

FIG. 7A also shows mountingreceptacles150′,152′, for opto-

sensor mirrors

11A and11B, seeFIG. 14;receptacle14A forclosure panel14 for completing the waste passage to the waste receptacles; andchip receptacle133A for receiving a support which defines capture surface D,FIGS. 1, 1A,4A, carrying an array of ligand receptors. Capture surface D forms the bottom ofreaction chamber133 while its opposite side is formed byglass window5,FIG. 7.

External heater assembly

101 ofFIGS. 6A and 8C, is constructed for face-to-face heat transfer relationship withcassette surface13A atcavity16.Assembly101 is part ofcontrol unit60 ofFIG. 8. Under control of a temperature sensor at thereaction chamber133 it raises the contained liquids to approximately uniform temperature, preferably 37 degree Celsius.

In operation, the substantial angle to horizontal at whichcassette50 is held (angle α,FIG. 8) placeswaste vent9 at the top of the cassette. The cassette may be inserted intocontrol unit60 and thecover62 closed, after which liquid sample is injected intoreservoir134. Thefluid reagent pouch12 inchamber135 is pierced, e.g., by an internal or an external lancet, to release the liquid. By pumping of liquid, air within the cassette is expelled through thereaction chamber133, andwaste receptacle139, to exit throughvent filter9. All stages of operation are controlled electronically e.g., bysystem controller60.

Operation and further details, of the embodiment ofFIGS. 6 and 7 will now be described for the example of a multiplexed immunoassay according toFIG. 17 in which the analyte is an antigen ligand and the ligand receptor (capture agent) is an antibody.

Referring toFIGS. 6 and 8E, and to the general system ofFIGS. 5 and 5A, performance of an assay is initiated bysystem controller60

closing label valve

137A and washvalve137B, and activatingpump37 to displace fluid fromreservoir135. With the left side of the cassette ofFIG. 6 elevated, air and then liquid is displaced through intake manifold135blocated at the high side ofstorage chamber135. Fluids fromreservoir135 travel into firstdry reagent reservoir131 until liquid displaces all air from the reservoir. The liquid liquefies dry reagent inreservoir131, e.g. detection antibody,reservoir131 thus serving as a liquefying chamber. Followingchamber131, as liquid reaches the opto-sensor150 the liquid-air interface is detected. In response,sensor150 directs thesystem control unit60 to close thevalve137C to block further liquid flow. By design, the system may delay valve closing for the time of a few steps of the linear stepper motor to enable advance of liquid sufficient to displace air up to connection with the next branch of the passage system.

Valve

137A is then opened, and pump37 ofchamber135 is actuated for a predetermined number of steps of the linear stepper motor to fill the seconddry reagent reservoir142 and the discharge passage branch with liquid, thereby expelling any air.

Valve

137A is then closed,valve137C remaining closed, and washvalve137B is opened.Pump37 is operated a predetermined number of steps of the stepper motor to displace air withinwash channel143.Valve137B then closes.

Thesample pump30 associated withsample chamber134 displaces air and then sample liquid from the high side ofchamber134, through theheated serpentine passage33′. This heats the sample liquid to a temperature of approximately 37 C. Movement of liquid into the serpentine passage displaces air ahead of the liquid front.

By continuous pumping; the sample liquid fills thebubble trap130 so that it will operate properly. The pair of passive

micro-fluidic burst valves

138C,138D, at theoutlet130B of thebubble trap130, blocks sample liquid from passing until the bubble trap is filled with sample liquid. Air in the bubble trap is displaced through the air vent circuit formed through a pair of passive

micro-fluidic burst valves

138A,138B arranged in opposition.Valve138A blocks liquid from escaping from thebubble trap130.Valve138B blocks liquid from back-filling into thebubble trap130. Thus air and then liquid is directed toward thereaction chamber133.

By control of the stepper motor of the linear actuator forsample pump30, the pump displaces sample at a predetermined rate and program until the sample opto-sensor152 detects arrival of the liquid-air interface. This is the start event. It triggerscontrol unit60 to drive thesample pump30 according to a predetermined rate and duration to transport sample through thereaction chamber133, as required by the particular assay for which the cassette is being used. Gas micro-bubbles produced by heating the sample, etc., are removed from the sample liquid by thebubble trap130 before the sample reaches thereaction chamber133.

Either simultaneously or sequentially, dried reagent within firstdry reagent reservoir131, e.g., a dried coating of detection antibody reagent, is liquefied by oscillatory fluidic agitation. For this,valves137A,valve137B andvalve137C remain closed. By repeated forward and backward motion of the associated linear actuator,reagent pump37 displaces liquid forward and backward. Forward motion causes a predetermined volume of reagent to bulge the elastic membrane coveringdetection storage chamber131, while backward motion causes the membrane to contract and liquid to flow backward.Pump37 is programmed bysystem control unit60 to cycle in oscillatory motion a predetermined number of times at predetermined rate and volume. This system enables various modes of agitation. One is by slow filling and emptying e.g. at a frequency under 10 Hz. Another mode is in short steps with a frequency up to 10 Kz. (See Masterangelo Carlos & al., “Simulation of Interfacial Dynamics of Time-Dependent Converging Flow in Microchannels”, Proc. SPIE,4560:108-116 (2002).

Sample liquid is caused to flow through the reaction chamber for a pre-established duration, as determined by the control program, and pump30 is then stopped.Detection antibody valve137C is then opened, and pump37 activated to force now-liquefied and heated detection antibody, that had been stored in the drydetection antibody reservoir131, throughbubble trap130 and into thereaction chamber133. The liquid bearing the detection antibody displaces any sample in thereaction chamber133, and during a continuous flow for a programmed duration, the detection antibodies bind to any analyte bound to capture agents within the reaction chamber. Any detrimental gas micro-bubbles produced by the heating or agitation are removed by thebubble chamber130.

Thefluidic burst valve138E is intended to block reagent/buffer from entering theserpentine passage33′ only when the passage is dry. This condition occurs when, instead of the procedure described here, it is elected to fill the bubble trap with reagent or buffer liquid rather than serum or analyte.

The dryfluorescent label cavity142 has previously been filled with buffer liquid and liquefied. At a predetermined time,system controller60 closes thedetection antibody valve137C and opens the label (tag)valve137A to change the drive mode ofdiaphragm pump37. Further operation ofpump37 now displaces heated liquid fromfluorescent label reservoir142, through thebubble trap130 and thereaction chamber133. This enables the label (tag) to bind to the complexed antibodies in the absence of detrimental gas micro-bubbles.

When the final step of the assay proper has been completed, namely binding of label to the detection antibodies (Abd) on the capture surface, the unbound label present in the chamber is washed out to minimize label-induced background signal during later imaging (reading). Therefore, at a predetermined time the system controller closeslabel valve137A and opens washvalve137B.Pump37 then causes wash liquid to move liquid via the bubble trap into the reaction chamber to accomplish washing. The array capture surface in the reaction chamber is now ready for reading. This may be done in the presence of wash liquid or the reaction chamber may be cleared of liquid by runningpump37 backward to suck liquid from the reaction chamber.

Storage of Materials

The capture antibodies (or other ligand receptors) specific to an application are deposited and adsorbed as groups of spots in aligand receptor array20 on a treated surface of thin, solid nitrocellulose film. The film is carried on a glass “bio-chip” which is contained in the “reaction chamber.” (See portions of WO 04/018632A2 (PCT/US03/25685) relating to solid nitrocellulose film of thickness less than 1 micron, and treatment of its surface, hereby incorporated by reference.) Treatment (surface activation) of the film by corona discharge is preferred.

The detection antibodies (Abd) or equivalent are stored as a dried coating on a surface of thedetection antibody reservoir131. Fluorescent label material is stored as a dried coating on a surface offluorescent tag reservoir142. The buffer liquid is stored in a fluid-tight “fluid pouch”12 located in thefluid reagent cavity135. The sample, after introduction, is stored for the assay inreservoir134.

Reaction Chamber

Thereaction chamber133 is a tunnel, approximately 9.5 mm wide and 12.5 mm long. It is formed on one side by the biochip capturesurface carrying array20 and on the other side bytransparent window5. The tunnel communicates with theflow transition section133A and washdischarge133B at the 9.5 mm dimension, and is closed on the other sides. Thearray20 on the biochip surface and the window are spaced apart with an approximately uniform gap between 80 and 300 micron, preferably between about 100 and 200 micron. The backside of the biochip is exposed for contact by the heater and to a temperature sensor embedded in the heater.

Spotted Array

In one preferred embodiment,reaction chamber133 has dimensions of 9.5 mm×12.5 mm×0.20 mm (200 micron gap) and in another the gap is reduced to 0.10 mm (100 micron). The surface of the solid support used for attachment of capture agent is 6.5 mm×9.5 mm. A typical assay searching for one analyte consists of a number of spots of ligand receptor, preferably spots with diameter between about 50 micron and 500 micron separated by a distance similar to one spot diameter. A typical spot diameter is nominally 150 micron, 300 micron on center.

Preferably, referring toFIGS. 16 and 16A, a first row of spots arranged transversely to the direction of flow consists of two regions of 10 adjacent replicate ligand receptor spots 300 micron on center, each group of 10 forming one assay for one ligand,Analyte1 andAnalyte2.

InFIG. 16, following rows, as the serum (or other sample liquid) flows, are used for signal calibration (see below, “Analysis of Data). These may be spotted with an equal number of spots of ligand (e.g. protein) associated with the adjacent ligand receptor (e.g. capture antibodies) and preferably consisting of known concentration of the ligand. A number of such calibration rows of different concentrations, sufficient to define a calibration curve,e.g. calibration rows1A-1G, may be used, seeFIG. 16, to achieve self-calibration. Preferably, as shown, reference spots in the row are displaced, locating the reference spots between the spots of capture antibodies rather than directly behind (in the direction of flow) to reduce depletion consequences. Similar rows are provided for

Analytes

3,4;5,6 and7,8. A row of control spots control A and control B is also provided.

In the case ofFIG. 16A, intended for use with pre-established calibration curves, most of the capture surface is occupied by rows of replicate analyte spots, Analytes1-16, concluding with a row of control spots.

In another arrangement alternating rows of ligand receptors for the analyte and pairs of rows of ligand reference spots of two different dilutions may be provided, seeFIG. 16B.

Other arrangements are possible.

In a case where only two rows are used for capture and reference and each row has 2 analyte regions, a 12.5 mm length can accommodate 40 rows with spots 300 micron on center and consequently 40 different assays.

Liquid Reservoir

FIG. 11 shows apouch12 for liquid for the assay, e.g. buffer liquid for liquefying the reagents and for washing. It is formed from a female “blister”cavity12B, and covered and sealed with aflat element12A. Generally,pouch12 provides a high barrier to moisture, oxygen and light, and holds its shape after being formed into the pouch. Materials suitable are known to those skilled in packaging of biologically sensitive products such as pharmaceuticals, and include, without limitation, cold-form foil (e.g., “Hueck DMF7273” cold-form foil material, Hueck Foil L.L.C., Wall, N.J.) and, e.g., laminated polyester-polyethylene-aluminum foil-CRC-1-polyethylene (Flex-Pak Packaging Products Inc., Batavia Ill.).

Releasing the Liquid from Reservoir

FIG. 12 showspouch12 incavity135 closed bymembrane7 bonded tobase13. It also showsplunger head1B (a broken-away portion of cover1) bonded tomembrane7 by anisland4 of double sided adhesive sheet.Plunger head1B is engaged on its outer surface byend plate72 on shaft L oflinear motor70 located insystem control unit60.Plunger1B also has awl (piercing projection)1D molded as part of the cover, protruding through both double-sidedadhesive tape island4 andelastic membrane7.Pouch12 has bentfeatures12C (not shown onFIG. 11) holdingpouch12 away fromawl1D. Breakaway tabs T holdplunger1B withincover1.

At the start of operation,cassette50 is held incontrol unit60 as shown inFIGS. 8 and 8E, in approximately vertical position andvalves137A andvalve137B are closed whilevalve137C is opened; linear motor shaft L propels theplunger head1B which (seeFIGS. 12A and 12B) severs tabs T, detachingplunger head1B fromcover1. The awl (piercing projection)1D piercespouch cover12A such that liquid withinpouch12 escapes intocavity135 and accumulates at the bottom ofcavity135. Asplunger1B moves forward,pouch12 is compressed, thus pushing out liquid and reducing the volume ofcavity135. Air withincavity135 accumulates in collecting manifold135B in the upper region of cavity135 (seeFIG. 6) and is displaced throughduct135A,reservoir131 and finallyair vent9 inreceptacle140.

When all air has been expelled, liquid is then displaced through the same channels, asplunger1B continues to be moved withincavity135. When liquid reaches opto-sensor150 thecontrol unit60 actuates avalve actuator71 to closevalve137C.

(In an alternate method, not shown here, an externally driven pin may traverse a septum, not shown, to piercefluid reagent pouch12 to release liquid frompouch12 into thepump cavity135.)

During assembly ofcassette50,pouch12 is placed incavity135. Optionally, the shape ofpouch12 can be configured to fitcavity135 so as to keep the pouch clear ofawl1D, to prevent premature piercing of the pouch and leakage of fluid. Preferably, thecorners12A ofpouch12, bent upward as shown inFIG. 12, keep the pouch against the closed end ofcavity135 and clear ofawl1D.

Dry Detection Antibody Reservoir

FIG. 6 showsreservoir131 where the detection antibodies (or other detection ligands) are stored in desiccated condition. During the assembly of the cassette, the region dedicated to receive these reagents is first coated with a “blocker” typically available from Pierce and intended to create a coating that can be readily liquefied to prevent the reagents from adhering to the surface ofreservoir131. The blocker fluid is “painted” or spotted on the surface of the bottom ofreservoir131 and left to air dry. Subsequently a mix in appropriate ratios of all the reagents associated with the capture antibodies (or other ligand receptors) spotted onbio-chip20 are “painted’ in suitable amount over the protected area at the bottom ofreservoir131 and left to air dry. Detection antibodies, for instance, may have a biotin molecule attached to bind to the fluorescent tag bound to a streptavidin molecule in a reaction that is well known to those skilled in the art, seeFIG. 17.

Dry Fluorescent Tag Reservoir

FIG. 6 also showsreservoir142 where the fluorescent tag (“FLR LABEL” ofFIG. 17) is stored in a desiccated condition. The fluorescent tag is preferably a Cy3 molecule bound to a streptevidin protein and can be purchased from Amersham, a division of General Electric Co. It is “painted”, in suitable amount and concentration to meet the need of the assays, as is well known to those skilled in the art, directly on the surface ofreservoir142 and left to air dry. The dry fluorescent tag is readily liquefied when brought in contact with the liquid buffer.

Liquid Introduction System—Septum

Referring toFIGS. 6 and 7, liquid can be introduced intocassette50 by use of an external pipette or needle. Alternatively, liquid can be introduced intocassette50 with a needle that is built into the body ofcassette50 itself. Referring toFIGS. 15 and 15A, in the preferred embodiment described herein, liquid sample (analyte or serum) is introduced intosample chamber134 through aseptum passage system32 utilizing an external pipette or needle. Those of skill in the art can understand that, in the alternative, liquid sample can be introduced by an internal needle system and/or the liquid can be introduced by an external system of different construction.

FIGS. 15 and 15A show a sample introduction system that includesseptum cavity32,sample injection port144, andsample injection channel145.Septum closure assembly61 atcavity32 serves as a seal between the exterior ofcassette body13 andsample injection port144.Septum closure assembly61 is composed of acompressible septum material137, that is elastically compressed transversely and tends to expand within theseptum cavity32, as shown by the outward arrows ofFIG. 15A. Suitable materials forseptum closure137 are known to those skilled in art, and include, e.g., rubber, preferably a silicone rubber. By way of example, in one embodiment,septum cavity32 is approximately 3/16 inch diameter,septum closure137 can be approximately 1/16 inch thick and approximately ¼ inch diameter when uncompressed, made of silicon rubber of 60 durometer.

Septum clamp

136 serves as a retainer for holdingclosure137 in place withincavity32.

Septum closure

137 is pre-punctured prior to being inserted into septum cavity32 (pierced, as indicated by axial line P) by a sharp steel needle or other member that has significant sharpness and columnar stiffness. The pre-puncture path P provides a region withinclosure137 that is low in resistance, providing a spot through which a relatively blunt or weak (low columnar stiffness) instrument such as a plastic pipette tip can be pushed. Despite pre-puncture ofseptum closure61 prior to assembly, fluid does not leak fromcassette body13 because the rubber ofseptum closure137, under transverse compression closes path P, ensuring no leakage. The weak spot permits a blunt, relatively large pipette tip to find a point of low resistance, and slide through the septum in liquid-tight manner.

Sample Containment System

FIGS. 6, 7 andFIG. 15A showsample chamber134 inbase13. It is covered byelastic membrane7 and connected toseptum cavity32 viaduct145. It is connected tobubble trap130 via temperature controlledregion33′ viaduct146 having itsinlet134A located in the upper region ofcavity134. Serum or analyte is introduced intocavity134 via theseptum32 following installation of the cassette in a receptacle incontrol unit60 in an approximately vertical position. The cassette is held in place with hingedcover62 as shown inFIG. 8b.Port67 throughcover62 is aligned withseptum32, to offer direct access to the septum.

Sample Pump

Serum (sample or analyte) pump30 is formed by moldedsample chamber134,FIGS. 6, 7 and15A andelastic membrane7, in conjunction withbreakaway plunger head1A.Head1A is suitably bonded with double sidedadhesive sheet2,FIG. 7. With the cassette installed incontrol unit60, shaft L from the linear motor withincontrol unit60 engagesplunger1A and drives it downwardly under control determined by the appropriate software.

Retaining tabs T are broken, freeingplunger1A to move with shaftL. Exit duct134A fromcavity134 is located at the top ofcavity134 when the cassette is in use position so that first the air within the pump is displaced, followed by liquid (serum or analyte). Whenpump30 is activated, liquid sample is propelled intochannel146.Channel146 makes a number of convolutions as a serpentine passage before connecting to theinlet160 tobubble trap130. Theheater101 extends incavity16 underchannel146 for heating the sample. Consequently, preceding the bubble trap, the serum oranalyte15 is brought to reaction temperature preferably 37° from room temperature, about 25° or storage temperature, e.g., 4°. This process most commonly causes gas microbubbles to form within the liquid, which are removed as the liquid travels through bubble-trap130.

Reagent Pump

The reagent pump37 (for propelling buffer or reagent) is composed of elements incorporated incassette50 and elements incorporated incontrol unit60. The elements withincassette50 are thechamber135, theliquid holding pouch12, theelastic membrane7 and thedetachable piston head1B. Incorporated incontrol unit60 is thelinear stepper motor70, its motor shaft L,FIG. 8E terminated with aplate72. One of the functions ofplate72 is to spread actuating force sufficiently to ensure that all breakable tab connections T, holdingpiston head1B to cover1, break tofree piston head1B.

In operation,control unit60 directslinear motor70 to drivepiston head1B, breaking it free fromcover1, seeFIGS. 12A, 12B. Aspiston head1B moves downwardly, it reduces the available volume withinchamber135. Air is expelled via a channel in the upper region ofcavity135 intomanifold135B. In the same time,awl1D, protruding through thediaphragm7, penetrates and piercespouch cover12A so that liquid flows to the lower region ofcavity135.

Thecontrol unit60 directs the linear motor further. Air is displaced by the pouch liquid and is expelled. When all air has been expelled with piston movement, liquid is then pushed out through the same manifold and channel.

Cassette

50 may be stored at low temperature and taken out as needed. The liquid in the pouch, warmed e.g. to 37°, contains microbubbles which are removed by passage of the liquid throughbubble chamber130.

Temperature Controller & Heater

It is necessary to perform the assay at a known temperature because the complexing efficiency of a sandwich assay is strongly influenced by the rate of diffusion of ligand molecule within its carrier liquid, which itself is a strong function of temperature. Prior to use, normally the cassette as well as serum are kept at room temperature or below. For heating to the desired reaction temperature, preferably 37°, theheating element101 is an integral part of thecontrol unit60. Whencassette50 is installed inreceptacle66, and hingedcover62 is closed,heating element101, carried oncover62, nests withincavity16 in the back of thecassette50, and engagessurface13A, seeFIG. 6A. Heat passes through thin wall regions of the cassette to heat all liquids that interact during the assay.

Referring toFIGS. 8C and 8D, theheater101 comprises a thin, flexible sheet-form heater element102 manufactured by Minco Co. to fitcavity16 at the back of thecassette body13. It is mounted on a low durometer (60 durometer) siliconerubber foam backing103 and floating planarrigid support104. The planar surface ofheater101 can thus be pressed into conformity withplanar surface13A at the bottom ofcavity16, and the backside of the biochip at thereaction chamber133. A temperature sensor incorporated in the heater unit is arranged to sense the temperature of the biochip for control of the heater.

Gas Removal System: Bubble Trap

FIG. 10 illustrates an embodiment of thebuoyancy bubble trap130. In the preferred embodiment, sample enters fromchannel160 and fills the lower region of thebubble trap130 but is prevented from proceeding to thereaction chamber133 as microfluidic capillary burst

valves

138C and138D are designed to conditionally block passage of liquid and burst only when a predetermined back pressure has been reached. Sample (serum or analyte) fills thebubble trap130 as air is forced up and escapes via microfluidic capillary burstvalve138A and throughchannel162, through microfluidiccapillary burst valve138B and out to thereaction chamber133, thewaste receptacle139 and finally out through thevent passage140 containingfilter9.

When thebubble trap130 is filled with liquid, the pressure atexit164 causes microfluidic capillary burstvalves138C and D to be overcome and serum or analyte proceeds to the serum opto-sensor152,FIG. 6, from which a signal is sent tosystem control unit60 as the liquid-air interface traverses the viewing area. Microfluidic capillary burstvalve138B prevents liquid from entering intochannel162 and nulling the effectiveness of microfluidic capillary burstvalve138A. The system controller is programmed to actuate the sample pump to propel sample through thereaction chamber133 at a predetermined rate for a precise duration.

When serum or other liquid enter the liquid-filledbubble trap130, fromchannel160, entrapped or dissolved gases rise by buoyancy to the “upper” region of the trap. They are prevented from enteringchannel162 aschannel161 is filled with liquid held in place by microfluidic capillary burstvalve138A. The liquid entering thebubble trap130 exits viachannel164. Thus gas bubbles having greater buoyancy rise and the liquid continues free of detrimental bubbles.

Preferably, as shown, theliquid inlet160 andoutlet164 of the bubble trap are located in alignment at opposite ends of atrough160A extending across the bottom of thebuoyancy chamber130. In this relationship, laminar flow can be maintained with little influence by the nature of the liquids immediately above. Hence a succession of different liquids can flow through the chamber with little cross-contamination. In other designs however, the bubble removal system may comprise multiple bubble chambers through which respectively different liquids of the assay may flow.

Thebubble trap130 ofFIG. 10 has a dividingrib130D located in the middle of the chamber, beginning at the high side oftrough160A. Viewed in operating position,rib130D extends upwardly a substantial distance, ending short of the upper end of the trap volume. Itsouter edge130E lies at the plane of face wall FW, to be adhered and sealed to the overlyingadhesive sheet8.

Dividingrib130D thus forms two successive

bubble capture zones

130F and130G which are open to flow intrough160A. These zones communicate at their upper ends. This provides a fail-safe feature. In absence of the rib, should a gross air bubble enter frominlet160, so large that it spans the full width of the bubble trap, the gross bubble could become lodged and prevent proper liquid filling of the trap volume. In the presence of dividingrib130D, such a gross bubble instead would be captured in the initial (upstream)capture zone130F, leavingdownstream zone130G open to receive liquid and continue filling of the trap. Thus, the upper region ofzone130F may be filled despite lodging of a blocking bubble in lower portions of that zone. In other embodiments, not shown, the trap could be configured with one or more additional ribs that form a succession of three or more such regions to provide further fail-safe protection.

In other embodiments two or more independent bubble traps, in series, may be provided to provide a series of bubble capture zones for a given liquid flow.

FIG. 10A provides an alternate bubble trap design. Venting is by aporous plug9A inserted at the top of the bubble trap, offering an air escape route which becomes blocked when thetrap cavity130 is filled with liquid.

Vents

In order for fluid to both enter and exit the device in an efficient manner,cassette50 includesvent port140, which is a closeable air vent.Vent port140 is preferably a conduit, of cylindrical shape, for the passage of air.Vent port140 can be filled with an air-porous material to formvent plug9.

Vent plug9 (or thevent plug9A provided for the bubble trap, is of porous material permeable to gases but permanently obstructed following contact with a liquid. When used in a vent passage, while dry, it ensures an escape route for air and other gases contained in thecassette50 or separating from liquids. It also ensures that thecassette50 is at atmospheric pressure when liquid sample is being collected and injected into the device, and, by sealing when contacted with liquid, it ensures thatcassette50 is sealed from atmospheric contact after air has been removed from the device.

Suitable materials for use as a vent plug include a thermoplastic material, polyethylene, polypropylene, polytetrafluoroethylene (PTFE; e.g., GORE-TEX®, W.L. Gore & Associates, Inc., Newark Del.), e.g., porous plastic (e.g., porous plastic marketed by M.A. Industries (Peachtree City, Ga.), and thermoplastics, e.g., supplied by Trexel, Inc. (Woburn, Mass.), or POREX® (Porex Technologies Corporation, Fairburn, Ga.). Although porous when dry, such materials are designed to become fully closed when wet. (See, U.S. Pat. No. 5,916,814, issued Jun. 29, 1999, hereby incorporated by reference in entirety). Alternatively, ventplug9 can be replaced with a membrane with similar properties such as is available from the W.L. Gore and Associates, Inc. (Newark, Del.).

When thevent port140 is dry, the porous region permits air to traverse, so as to permit any gas to escape the cassette. When thevent plug9 is wet, it is closed, and neither gasses nor liquids can escape the device. In the illustrative embodiment depicted inFIGS. 6 and 7, thevent plug9 can absorb 1 to 5 ml of liquid, depending upon the dimensions and size of the plug.

Vent plug

9 is located such that, when the cassette is in a substantially vertical position, buoyancy causes air to reach thevent port140 ahead of the liquid front. Preferably, ventport140 is proximal to, or connected to,waste receptacle139.

In some situations, such as during storage, when it is desirable to prevent vapor transfer, the outside ofvent port140 can be further sealed with a tape (not shown). Optionally, the tape can form part of a labeling system, that can then be detached and relocated for identifying the source of the analyte sample. (See, U.S. Pat. No. 4,884,827, issued Dec. 5, 1989, hereby incorporated by reference in entirety.)

Waste System

FIGS. 6 and 7 show

waste receiving cavities

139 A and139B connected together via a passage in the back of the base13 closed withpanel14. This construction is desirable for molded manufacturing. In operating position, the waste cavities are located at the highest end of the cassette to receive all gasses and liquid that pass throughreaction chamber133. The waste cavities are constructed and located such that liquids having entered, shall not readily return toreaction chamber133. The system incorporatesair vent140 and filterplug9.

Liquid Channels

Channels have flow cross-section typically, between about 0.1 mm²and 1 mm²and have smooth surfaces to avoid bubble nucleation. On three sides they are formed by molded surface ofbody13. They are closed on the fourth side by the overlyingadhesive sheet8. Some channels may be treated to have hydrophilic or hydrophobic properties or be treated to alter these. The channels of the preferred embodiment have a flow cross-section of 0.25 mm².

Valves

Active Valves

FIGS. 13-13C illustrate the operation of an active valve. The valve stem A as well as the valve seat V are of circular design in planes perpendicular to the axis shown.Flow channels90 are open at opposite sides of the conical valve seat. During the open condition ofFIG. 13, thechannels90 are open to through-flow. When the valve stem A is moved forward by a valve actuator of thecontrol unit60, as shown inFIG. 13A, stem A deforms theelastic membrane7 and blocks the channels. Referring toFIG. 13B, it should be noted that the opening in the double sidedadhesive sheet8 should be sufficiently greater than the base diameter of the valve seat in order to permit the elastic membrane to minimize wicking via the circular gap and present a sufficient pressure drop so that flow can be stopped by the microfluidic capillary burst valve further along in the same channel such as microfluidic capillary burstvalve138F, seeFIG. 13C.

Valve stem A is an integral element ofcontrol unit60 and may have various forms depending on space considerations. In one case a 2 mm diameter axial extension of a linear actuator acts directly as the valve stem. In another case, the stem is of hammer shape of 90 degree included angle with a shaft diameter approximately 2 mm, actuated by a linear actuator in a lever action.

Microfluidic Capillary Burst Valves; Passive Microfluidic Valves

FIG. 9 illustrates the basic design, with cover indicated by lightened lines, of a microfluidic capillary burst valve incorporated within the cassette. As with the channels, it is formed on three sides by molded surfaces ofbody13, and, on the fourth side, byadhesive sheet8.

Basic theoretical holding pressure P of a against an air chamber of a passive microfluidic valve—defined as a cylindrical or square capillary duct terminated normally in a flat plane—in the model used by J. Zeng and al.—“Fluidic Capacitance Model of Capillary-Driven Stop Valves; 5th Microfluidics Symposium IMECE Nov. 5-10, 2000 Orlando Fla.; MEMS-18A- is calculated as:
P=4γ sin θ/(d)^1.14
where γ is the surface tension of the fluid—approximately 0.070 N/m for water at 37 deg. C., about twice that of most common carbon based fluids—and θ is the contact angle, typically 45 degree at bursting point, and d the dimension of the side of a square duct of the opening.

When d=0.1 mm, P=1.4, E3 N/m2 (Pa)=0.21 psi=5.7 in H₂O=14 cm H₂O Here, (referring toFIGS. 6 and 10) the relevant point is the necessity that

valves

138C and138D have a higher bursting capacity thanvalve138A in order to ensure that thebubble trap130 will fill with liquid while permitting the air to escape viavalve138A. To that effect,

valve

138C and138D have a smaller section thanvalve138A.

FIG. 9 is a schematic illustration of a passive one way micro-fluidic burst valve, representative ofvalves138 A, B, C, D and E. The dimensions ofneck200 and the exit angle define the holding forces holding the fluid against the air interface. Those knowledgeable in the art (see Inhibition and Flow of wetting liquids in Non circular Capillaries—J of Physical Chemistry B Vol. 101, pp 855-8630) define these dimensions so that air can pass through the bubble trap and the reaction chamber to void in the atmosphere via the vent filter.

Opto-Sensor

FIG. 14 shows an opto-sensor for sensing the arrival of a liquid-air interface in a channel. The opto-sensor is constructed from a light source-sensor/phototransistor unit S such as, e.g., a “Reflective Object Sensor” (Type OPB606A OPTEK, Carrollton Tex.) and installed as recommended. The opto-sensors150 and152 (FIG. 6) optically monitor the channel, where liquid containing either analyte or buffer is to pass, through

clear windows

6A and6B, such as that cut from a common microscope slide cover (ERIE Scientific). These are installed over a liquid channel formed in the face wall FW of thecassette body13. Light emitted by the LED element of the opto-sensor is returned to the phototransistor of the unit via

mirrors

11A and11B respectively imbedded and hermetically sealed (at I) within the rigid element of thebase13.

As both the liquids and air are present in very small volumes in the optical path of the opto-sensor, both are nearly equally transparent to the wavelength of the LED, and discrimination via absorption is unreliable. The absorption difference between air and water in a channel of less that 100 micron thick is extremely small, and peaks at only 0.5% of that of air alone when viewed in the near IR, at 950 nm, the wavelength of the OPB606A OPTEK unit.

The novelty is in sensing the interface (or “liquid front”) between gas and liquid as analyte or buffer liquid displaces air. The index of refraction of air is approximately 1.000 and of water 1.332, a significant difference, such that the presence of a liquid front diffracts and deflects the incident light, from the LED, in the fashion of a prism or a lens. This interface (front) is found easy to detect as it causes a fraction of the light to be deflected away from its normal path. As the front passes in the field of view of the opto-sensor, it causes a large momentary change in signal which is easy to monitor and interpret.

Information Tracking

The sample collection device can be equipped with an optional means of recording or displaying information about the sample, such as a bar code or a surface area suitable for writing or applying markings. The recorded or displayed information can be any information desired for performing or tracking the sample and/or the diagnostic assay for which the sample is intended. In another option, additional identification tags or bar coded labels can be provided with the cassette for recording corresponding information; the second tags or labels can then be removed from the cassette to be, e.g., attached to a patient record or to an animal's cage, or to be included with the diagnostic assay, as desired. By way of example, double labels, each having identification and serialized numbers or codes, are affixed to the sample collection device, so that one is permanently attached to the sample collection device, and the other is removable and capable of being subsequently attached or bonded elsewhere, as described above, or scanned or otherwise recorded in another informational storage medium. Thecassette50 preferably has a bar code label located on the cover such as to be readable with acommercial barcode reader69 within receivingcavity66 of thecontrol unit60.

Reader (to Read Optical Signals from Array)

Reading the result of an assay consists in measuring the level of fluorescence of the level/number of fluorescent tags that have bound to the capture surface, e.g. to detecting ligand (e.g. antibody) molecules that themselves have attached to the analyte molecules that themselves have attached to the ligand receptors (e.g. capture protein molecules).

The level of fluorescence is represented by an aggregate of the signal level of the image pixels from the region of the image captured of the reaction chamber. Each region of interest is associated with the area and location where a specific assay has taken place. The processing instrument (system controller)60 may have an integral reading station that captures an image of theentire biochip20 for analysis. Alternatively a reading station separated from the processing station may be preferred.Reader station60 has areading system64 that captures an image of the reaction chamber for further processing, seeFIGS. 8E and F andFIG. 18.

System Controller

Algorithm for Controlling Steps of Operation

All operations are initiated by logic and implemented by the System Controller Unit. Manual operations are indicated as such. The sequence of operations for the cassette ofFIGS. 6 and 7 andsystem controller60 used in an immunoassay is as follows:

- 1) Install the cassette containing the biochip in thefluidics station66—a manual operation
- 2) Inject serum intodiaphragm pump reservoir134—a manual operation
- 3) Close thelabel valve137A—note that all valves are normally open
- 4) Close thewash valve137B
- 5) Expel the air in theAbd chamber131 by operatingliquid pump37 to ruptureblister pouch12 inchamber135 and fillchamber131 with buffer liquid (contents of blister pack12); the Abd opto-sensor triggers150 timing and end of flow
- 6) Close theAbd valve137C
- 7) Open thelabel valve137A
- 8) Operate theliquid pump37 for a predetermined duration to expel the air in thelabel chamber142 by filling it with buffer liquid.
  - a) Employ a predetermined interval (or if a label opto-sensor is provided, use it to trigger timing and end of flow)
- 9) Close thelabel valve137A
- 10) Prime the bubble trap with serum:
- 11)—run the stepper motor of theserum pump30,
- 12)—the serum opto-sensor triggers152 timing at end of filling thebubble chamber130
- 13) Flow the serum through the reaction chamber133:
- 14)—run theserum pump30 stepper motor for a predetermined duration
- 15) Liquefy the Abd with buffer liquid
- 16)—run thepump37 three steps forward and three steps back in oscillating manner; the cover membrane ofchamber131 elastically deforms. This function may be performed simultaneously with the serum flow function.
- 17) Open theAbd valve137C
- 18) Flow the liquefied Abd through the reaction chamber by pushing it through with buffer liquid, operatingpump37
- 19)—run thepump37 for a predetermined duration
- 20) Close theAbd valve137C
- 21) Open thelabel valve137A
- 22) Flow the label through the reaction chamber:
- 23)—run thepump37 for a pre-determined duration.
- 24) Close thelabel valve137A
- 25) Open thewash valve137B
- 26) Flow wash liquid through the reaction chamber:
- 27)—run thepump37 for a pre-determined duration.
- 28) Drain the reaction chamber by operating thepump37 in reverse direction for a pre-established duration
- 29) The disposable cassette may then be removed from the processing station and the reaction chamber imaged for analysis at a later time. Alternately reading module ofcontrol unit60 in the processing station may be employed.
- 30) The cassette with biochip may than be discarded.
  Alternative Algorithm
- 31) Alternately the wash step can be processed through the antibody reservoir131:
- 32) Close thewash valve137B
- 33) Open the Abd valve
- 34) Flow wash liquid through the reaction chamber via the Abd reservoir:
- 35)—run thepump37 stepper motor for a pre-determined number of steps

In an alternate operation mode, buffer liquid may be used to prime the bubble trap and passivemicro-fluidic valve138E blocks it from entering the sample circuit.

Analysis of Data

General

As is well known, the goal of an assay is to determine the number of molecules of interest present in a certain volume of the analyte in question: the molecular density. In immunoassays based on fluorescence this is achieved by attaching a fluorescent tag to the complexed pairs and measuring the light intensity of a defined region where the tags have attached. This results in a voltage level, a number, that must be correlated to molecular density of the molecule of interest within the sample.

When a spotted array is employed in a biochip, the information comes as a voltage level at a number of replicate spots. An operation is performed on those values to determine a representative value. For instance the highest and lowest detected value of the set may be discarded. To establish a representative value, an average or mean value may be calculated from the remaining values of the set, this value taken to be the representative value of the set of spots.

The Variables

Protein-protein interactions (or other ligand-ligand receptor interactions) are equilibrium reactions in a fluid environment where the complexing (coupling or association) of two molecules (designed or selected for highly specific associative properties) is a function of the density of each molecule in the fluid. The equilibrium condition of each pair of molecules is defined by their coupling coefficient. Historically, complexing has been defined in a stationary and fixed volume of fluid. It has been determined that the rate of complexing is strongly determined by the ability of molecules to find each other.

One class of molecule, the capture molecule (ligand receptor), is normally bound to a solid surface, to a well of a multi well plate or the support of a spotted array—in the cassette described above the support is glass coated with Activated Nitrocellulose. The other molecule (the ligand) present in the analyte, is introduced in liquid.

Using an ELISA multi-well plate for the assay, mixing for molecular association is by diffusion and very slow because the molecular distances of travel (6 mm well diameter) are large and no mechanical mixing takes place. Control of the critical parameters is poor. Fluid diffusivity is a strong function of the viscosity, temperature, and molecular weight (protein size) of the molecules.

In a flow microchannel, molecular association is faster and affected by the same variables and to a small degree by flow rate. Flow conditions are also different as molecular density at the coupling sites changes with time and flow rate.

At very low Reynolds Number (extremely slow) liquid flow over a spotted array, molecular association is also dominated by diffusion but the diffusion travel distances are very small and the reaction time accordingly shorter.

The complexing rate for a given set of parameters is not linear and reaches equilibrium in an asymptotic manner as indicated inFIG. 3A, discussed above.

In an equilibrium assay, after a period of time, equilibrium is reached where the rate of association between the analyte and capture molecules is equal to the rate of disassociation between those molecules. This takes a great amount of time: in a multi-well plate, a substantial fraction of an hour for very high molecular density and over night for low molecular densities.

It is common to terminate an assay without reaching a state of equilibrium because of the long duration required to achieve the equilibrium.

The variables when employing spotted arrays are numerous even after the operator's idiosyncrasies have been eliminated by use of a machine and the controlled environment of a cassette:

- the quality & quantity of molecules of interest and their affinity constant
- the reaction temperature
- atmospheric pressure
- humidity
- the geometry of the reaction chamber
- the spot size
- the density of capture molecule on each spot
- the properties of the support surface, e.g. the nitrocellulose coating
- the flow rate and distribution
- the duration of the assay
- the sensitivity of the “Reader”
- the tolerances of the processing system
  Calibration and Control

Due to the large number of variables it has been common for a correlation constant—a curve—to be pre-established. At the time of an assay performance of the reading System is verified, (referred to as “Control”) and the biology and chip are verified, referred to as “Calibration”:

1. For each manufacturing run of a specific bio-chip it has been common to establish a set of Standard Curves using some of the biochips of the run and the process and protocol of the assay. This correlates signal level and concentration for each molecule of interest under standard conditions. This is done (typically by the manufacturer) by running a set of known concentration samples through identical chips all constructed in the one manufacturing run. A minimum of 6 different concentrations (and a corresponding number of chips) has been required to define such a curve. When a new run of chips is manufactured, it has been necessary to create a new set of Standard Curves, with further consumption of chips.

2. “Control”: This is to ascertain that the reading instrumentation is working correctly. This is done with the use of “control spots.” The control spots are printed on all bio-chips and are expected to give a pre-determined signal. The spots may be loaded with Cy3 dye, bound protein or inert reference material such as Kapton. The control spots are deposited at the same time that all assay spots are deposited. Typically only one row is needed. One must keep in mind that there are numerous things that can go wrong and that the number obtained is always tainted with a CV percentage.

3. “Calibration”: This has been performed by the user before an assay is performed with chips from a given manufacturing lot. Typically 2 chips of the lot are run (expanded) against known dilutions to verify or adjust the overall system performance against the Standard Curves established by the manufacturer for that lot.

An aspect of invention will now be described.

Self-Calibrating Bio-Chip

As mentioned, according to common procedures, a number of identical chips from a run have been considered in an identical environment to develop Standard Calibration curves for the remaining chips.

In contrast, according toFIG. 16, an extensive set of calibration spots and control spots are printed on each chip in addition to the ligand receptor. The concept is to spot known dilutions sufficient in number and dilution levels to effectively establish a calibration curve following passage of the detection reagents, e.g. antibodies and tag liquids, over the chip. Each chip is thus made to be self calibrating.

For example, the chip of an assay designed to evaluate the presence of specific protein in the analyte is spotted in a conventional manner with a row of the capture antibody (ligand receptor) specific to the protein of interest. According toFIG. 16, the array is also spotted down stream with rows of spots of the very protein under evaluation in sufficient number of different dilutions, six as shown, to effectively establish a calibration curve. These spots are referred to here as the Intrinsic Calibration Spots—ICSs. (InFIG. 16 the ligand receptor spots are depicted as larger than the reference and control spots, to signify their biological difference. In practice all spots may be the same size.)

Referring toFIG. 16,calibration rows1A through1G comprise analyte ligand specific to the spots of the receptor foranalyte1;calibration rows2A through2G comprise spots of the ligand specific to the spots of the receptor foranalyte2, and so on. In this example, all spots of each given row of the set ofrows1A through1G are of the same dilution, this dilution being different from spots of the other calibration rows.

For this system to be effective, the detection reagents, e.g. antibodies and tags, are presented in sufficient abundance in flow over the array to bind to practically all protein (ligand) of interest present at the capture antibodies (ligand receptors) as well as at all the sites on the ICSs. Calibration curves specific to an individual chip may thus be derived as part of the reading process for that chip.

The rows of ICSs are located to minimize competitive molecular attraction between rows as well as local molecular depletion. This can be determined experimentally. In many cases, preferably the spots with highest dilution are located closest to the flow intake, followed by the next highest dilution, and so on. Successive rows may be offset from the travel path of the preceding row as shown inFIG. 16 and some rows may be separated extra distances, to facilitate homogenization of the flow before reaching the next ICS row.

With software, the signal derived from the spots with the molecules of interest within the analyte can then be compared to the signal derived from the ICS. (Interpolation between measured values makes the process equivalent to comparison to a calibration curve.) The molecular density in the analyte can thus be determined by reference to information derived from the bio-chip itself. Such self-calibrating bio-chips may be employed in the cassettes described.

Other Bio-Chip Formats

Biochips having the format ofFIG. 16A may likewise be employed. In this case pre-established calibration data is employed by the instrument to calibrate the readings. Control deposits on the biochip enable verification of operation of the system, or adjustment of its sensitivity based upon the detected value of the known fluorescent value of the control deposits.

Biochips having the format ofFIG. 16B may likewise be employed with pre-established calibration curve data employed by the instrument to calibrate the readings. In the embodiment ofFIG. 16B, each analyte is accompanied by two reference deposits of ligand A and B at different predetermined dilutions. These are employed, in reference to the predetermined calibration curve for the respective manufacturing lot, to adjust the detected results to the calibration curve.

IN CONCLUSION

While much of the detailed discussion has related to a particular example of an immunoassay, it will be understood that techniques described are applicable to the general class of assays employing ligand receptors attached to a solid substrate and ligands in the liquid flowing over it.