US20080097171A1 - Silicon microprobe with integrated biosensor - Google Patents

Abstract

Microprobe device10provides an analyte signal from biosensor12to an external analyte meter indicating analyte presence in an analyte-containing bodily fluid of a subject (not shown).

Description

PRIORITY
• The present application is a continuation of U.S. patent application Ser. No. 09/816,472 filed on Mar. 26, 2001, which is hereby incorporated by reference in its entirety.
TECHNICAL FIELD
• This invention relates to silicon microprobes, and more particularly to microprobes with biosensor capability incorporated therein for measuring analyte concentrations in a subject's blood, tissue, or other bodily fluids.
BACKGROUND
• Diabetes mellitus is an insidious disease which affects more than 15 million Americans. About 1.5 million of these are Type I diabetics (insulin-dependent) and 12 to 14 million are Type II diabetics (noninsulin-dependent). The characteristics of diabetes include chronic and persistently high levels of glucose in blood and in urine. Although urine glucose has been used to monitor glucose levels, the measurement of blood glucose is more reliable and logistically feasible. Blood glucose has therefore become the most commonly followed clinical marker for monitoring the progress of diabetes (and other diseases) to determine treatment and control protocols. Glucose levels are routinely measured in doctors' offices, clinical laboratories, and hospitals. However, the most convenient and important measuring is in-home self-monitoring of blood glucose levels by the patients themselves to permit adjustment of the quantities of insulin and hypoglycemics administered. Such self-monitoring is known as self-monitored blood glucose. Normal blood glucose levels in humans are in the 70-100 mg/dl range and in the 160-200 mg/dl range after a heavy meal.
• There are many products for diabetes related testing of glucose for diagnostic and monitoring purposes. These products range from skin swabs, reagent test strips, portable electronic meters, sensors and other instruments, lancets and needles of various shapes and sizes, syringes and other paraphernalia. Most of the currently available technologies, especially for self-monitored blood glucose measurements, are not satisfactory because they require some kind of deep lancing or finger stick with associated pain and sometimes excessive bleeding.
• The smallest lancet or needle currently marketed for blood sampling has a diameter between 300 micrometers and 500 micrometers, and is constructed of stainless steel with beveled edges. Due to the large cross-section of these lancets, fingertip lancing is painful and frequent lancing causes calluses, impairment of the use of hands, psychological trauma and other unpleasant consequences. Further, blood samples recovered from the patient must be transferred to a test strip or cartridge for assaying analyte concentrations. Obtaining blood samples by lancing and performing the analysis can be messy as well as painful for the patient.
SUMMARY
• It is therefore an object of this invention to provide a miniature microprobe device with integrated analyte sensing capability. The analyte concentration is determined by a biosensor built into the microprobe, which is in data communication with an external meter via an analyte signal. A blood sample is not transferred from the subject to an external test mechanism as in the prior art. The present self-contained process minimizes messy blood smears, which is convenient for the subjects. Further, the closed nature of the present process also minimizes ambient exposure of the subject's blood. Blood may harbor undesirable biological forms (such as HIV) which could contaminate the local environment constituting a biohazard. By eliminating the blood transfer step, the present microprobe avoids such hazard.
• It is another object of this invention to provide such a miniature microprobe device which accesses the blood and determines the analyte concentration in one simple step. The subject simply places the microprobe in a holder against the skin and waits for a signal to be sent to an external meter. The microprobe penetrates the stratum corneum (the tough outer layer of the skin) and contacts the tissue within. A separate ex vivo testing step with testing strips and the like is not required. The present one-step process eliminates the following prior art steps:
• A) Preparation step in which the subject gathers required materials including a test strip or cartridge to receive the blood sample and absorbent material for controlling blood smear and leakage.
• B) Transfer step in which the subject transfers the blood sample to the test strip.
• C) Waste blood step in which the subject cleans-up any waste blood, and disposes of the blood.
• D) Reset step in which the subject puts away the above material in readiness for the next blood sampling.
• It is a further object of this invention to provide such a miniature microprobe device which is fabricated from a silicon wafer. A biosensor may be integrated into the surface of the microprobe. Alternately, the biosensor may be placed in a cavity in the surface of the silicon.
• Silicon is compatible with integrated circuit (IC) fabrication and MEMS (microelectromechanical systems) technologies employing well established masking, deposition, etching, and high resolution photolithographic techniques. The present microprobe devices may be fabricated in mass quantities from silicon wafers through automatic IC and MEMS processing steps at minimal cost per device.
• It is a further object of this invention to provide such a miniature microprobe device which minimizes subject discomfort during probe penetration and analyte measurement. The dimensions of the probe (length, width, and thickness) are very small and cause minimal tissue displacement and related lateral tissue pressure and nerve ending contact. In some cases the displacement may be so minimal that the subject feels no sensation at all during the process. For example in a clinical trial of 62 patients using a microprobe with a thickness of 100 micrometers, the majority found the insertion and retraction of the microprobe device in the arm to be painless. Of the total patients tested, 15% could not even feel the probe penetration and an additional 58% found the penetration to be barely noticeable.
• It is a further object of this invention to provide such a miniature microprobe device which minimizes mechanical probe failure (breakage) during penetration and removal. Only minimal penetration effort is required due to the small probe cross-section defined by the width and thickness dimensions. These dimensions are much smaller than those of conventional metal lancets. The microprobe device retains the single-crystal structure of the silicon starting wafer and can reliably penetrate skin without breakage because of the strength provided by this single-crystal structure. The strength of the miniature probe may be further increased by optimal shaping. Data from skin puncturing tests show that the average force required to puncture the skin (0.038 Newton) is minimal compared to the buckling force required to break the probe (0.134 Newton).
• It is a further object of this invention to provide such a miniature microprobe device which functions in vivo. The biosensor may be located near the probe tip for maximum penetration. The biosensors may be placed in a cavity in the surface of the silicon. The probe accesses the blood, and the analyte signal is carried along the length of the probe to the ex vivo environment by conductive leads.
• It is a further object of this invention to provide such a miniature microprobe device which functions ex vivo. The biosensor may be distant from the probe on an ex vivo portion of the device, and not in direct contact with the analyte tissue. The blood is transported from the in vivo probe tip to the ex vivo portion by one or more channels.
• It is a further object of this invention to provide such a miniature microprobe device which may be emplaced into the skin of the subject for a single measurement of analytes.
• It is a further object of this invention to provide such a miniature microprobe device which may be installed on the subject for continuous monitoring of analytes.
• It is a further object of this invention to provide such a miniature microprobe device which has multiple biosensors. The biosensor(s) may be formed by IC fabrication and are significantly smaller than the microprobe. Several biosensors may be spaced along a single microprobe for sensing several analytes per penetration, or for sensing the same analyte at different depths.
• Briefly, these and other objects of the present invention are accomplished by providing a biosensor microprobe device for providing a signal to an external analyte meter. The signal indicates analyte presence in an analyte-containing fluid of a subject. The device is fabricated from a silicon wafer and has a body portion and a microprobe portion. The microprobe has a body end connected to the body portion, and having a penetration end extending away from the body portion for penetrating into the subject to access the bodily fluid. A biosensor integrated into the silicon substrate senses analyte presence and provides a signal in response to the analyte presence.
BRIEF DESCRIPTION OF THE DRAWINGS
• Further objects and advantages of the present microprobe and the operation of the biosensor become apparent from the following detailed description and drawings (not drawn to scale) in which:
• FIG. 1A is a plan view of invivo microprobe device10 showingbiosensor12 onprobe16;
• FIG. 1B is a side view ofdevice10 ofFIG. 1A;
• FIG. 2A is a plan view of ex vivodevice20 showingbiosensor22 onbody24;
• FIG. 2B is a sectional side view ofdevice20 ofFIG. 2A alongline2B-2B showing biosensor22 mounted incavity20C onsilicon substrate20S;
• FIG. 2C is a sectional view acrossprobe20 ofFIG. 2A alongline2C-2C showing V-groove26G insilicon substrate20S;
• FIG. 3A is a plan view ofdevice30 showingmultiple biosensors32D and32M and32S onprobe36;
• FIG. 3B is a side view ofdevice30 ofFIG. 3A;
• FIG. 4A is a plan view ofdevice40 showingoptical biosensor42 andwaveguide42W onprobe46;
• FIG. 4B is a sectional side view ofdevice40 ofFIG. 4A alongline4B-4B showing the optical biosensor mounted inhole40H throughsilicon substrate40S;
• FIG. 5A is a plan view ofmicroprobe assembly50A showingcover member58C andbase member58B;
• FIG. 5B is a sectional side view ofassembly50A ofFIG. 5A alongline5B-5B showing transmitter54T andbattery54B; and
• FIG. 6 is a chart comparing the average pain perception values for the silicon microprobe device with those for a conventional metal lancet.
• The first digit of each reference numeral in the above figures indicates the figure in which an element or feature is most prominently shown. The second digit indicates related elements or features, and a final letter (when used) indicates a sub-portion of an element or feature.
REFERENCE NUMERALS IN DRAWINGS
• The table below lists the reference numerals employed in the figures, and identifies the element designated by each numeral.
• • 10Microprobe Device10
    • 10A Front Side10A
    • 10FSilicon Oxide Film10F
    • 10B Back Side10B
    • 10S Silicon Substrate10S
  • 12Biosensor12
    • 12L Conductive Leads12L
  • 14Body14
    • 14P ElectricalInterface Contact Pads14P
  • 16Microprobe16
    • 16B Body End16B
    • 16P Penetration End16P
  • 20Microprobe Device20
    • 20A Front Side20A
    • 20C Cavity20C
    • 20S Silicon Substrate20S
  • 22Biosensor22
  • 24Body24
  • 26Microprobe26
    • 26A Apex26A
    • 26G Groove26G
    • 26P Point26P
  • 30Device30
    • 30A Front Side30A
    • 30CCommon Return Path30C
    • 30FSilicon oxide layer30F
    • 30B Back Surface30B
    • 30S Substrate30S
      • MultipleBiosensors32D32M32S
      • MultipleLeads33D33M33S
  • 34Body34
    • MultipleinterfaceContacts34D34M34S
  • 36Microprobe36
  • 40Device40
    • 40A Front side40A
    • 40H Hole40H
    • 40S Silicon Substrate40S
  • 42Optical biosensor42
    • 42C Optical Coupler42C
    • 42W Waveguide42W
  • 44Body44
  • 46Microprobe46
    • 46F RoundedMicrofillet46F
  • 50A Microprobe Assembly50A
  • 50M Microprobe Device50M
  • 52Biosensor52
  • 54Body54
    • 54A A/D Converter54A
    • 54B Battery54B
    • 54T Transmitter54T
  • 56Microprobe56
    • 58AAdhesive Film58A
    • 58B Base Member58B
    • 58C Cover Member58C
    • 58S Stabilizing Surface58S
GENERAL IN VIVO EMBODIMENTFIGS.1A and1B
• Microprobe device10 provides an analyte signal frombiosensor12 to an external analyte meter (not shown) indicating analyte presence in an analyte-containing fluid of a subject (not shown).Silicon substrate10S extends in the X length dimension, and the Y width dimension, and the Z thickness dimension, forminglarge body portion14 and pointed microprobe portion16 (as shown inFIG. 1A). The substrate hasfront side10A into which the biosensor is integrated and backside10B (as shown inFIG. 1B). The microprobe has abody end16B connected tobody14, and apenetration end16P extending away from the body in the X length dimension for penetrating into the subject to access the bodily fluid. A suitable signal interface structure such aselectrical contact pads14P may be deposited onto a side ofsilicon substrate10S onbody14, for sliding contact connection with the analyte meter. A suitable signal carrier such as conductive leads12L may be deposited onto a side of the silicon substrate betweenbiosensor12 andinterface pads14P for carrying the signal. The X length of the body may be from about 0.3 mm to about 2 mm, and the Y width of the body may be from about 0.3 mm to about 2 mm. Smaller body dimensions permit higher wafer density of microprobe devices (acreage) during manufacture.
• In the in vivo embodiment the biosensor is positioned on the microprobe sufficiently distant from the body end to pass into the subject during penetration. Positioning the biosensor ex vivo affords greater flexibility in biosensor reagent selection. As shown inFIG. 1A, invivo biosensor12 is positioned onmicroprobe16 nearpenetration end16P. The biosensor accesses the analyte fluid by penetrating into the subject and contacting the fluid. The analyte fluid may be any suitable body fluid such as blood, serum, or interstitial fluid or intracellular fluid. Preferably the in vivo biosensor is located sufficiently back from the penetration end of the microprobe so as not to affect the sharpness of the point or interfere with penetration of the probe. Access may be assisted by fluid seepage along the microspace between probe and tissue up the side of the probe from the tip to the biosensor.
• Diabetes monitoring is the primary focus of this disclosure for illustrative purposes. However, the microprobe device has uses in the diagnostic procedures and treatment of other diseases, emergency room status monitoring, sports medicine, veterinary medicine, research and development, with human subjects or experimental animals.
• Probe Shape
• The microprobe may be width tapered along the X length dimension, converging from a larger Y width dimension (of about 200 micrometers excluding the width of the microfillet portion) at the body end to a smaller Y width dimension at the penetration end. The X length of the microprobe may be from about 0.5 mm to about 2.5 mm with a penetration depth of from about 0.5 mm to about 2 mm. The discomfort or sensation experienced by the subject normally decreases with decreasing probe cross-section and length. However, a sensation floor exists where sensation is so minimal that probes smaller then this floor threshold do not offer any advantage. The taper permits easier penetration due to the gradually increasing cross-section of the probe. In addition, the taper reduces the volume of the probe causing less tissue displacement and less discomfort to the subject. The volume of the probe may be further reduced by thinning the Z dimension (seeFIG. 3B) from the initial thickness of the silicon wafer acrossbody34 to a slender thickness alongprobe36. For example, the thickness of the silicon wafer may be from about 500 micrometers (for a 4″ wafer) to about 700 micrometers (for a 6″ wafer).Back side30B ofsubstrate30S may be etched away to about 50 micrometers to thin the Z thickness dimension of the probe.
• The convergence of the microprobe taper may be uniform (as shown inFIG. 1A) establishing a constant change in the Y width dimension and a corresponding constant decrease in the cross-section ofprobe16. Alternatively, the convergence of the microprobe taper may be nonuniform (as shown inFIG. 2A) establishing a continuous change in the Y width dimension. This smooth change in width optimizes stress distribution withinmicroprobe26 during penetration and reduces material failure. That is, the probe is less likely to “snap-off” in the skin of the subject during use. The function for such a continuous change may be generated by stress analysis computer programs.Rounded microfillet46F (seeFIG. 4A) provides a smooth transition along the connection betweenbody44 and the body end ofmicroprobe46 which assists in eliminating stress points. The fillet transition prevents stress concentrations produced by cantilever bending of the probe. The Y width dimension of the microprobe may terminate in a suitably shaped point at the penetration end, such as symmetrically shaped point (shown inFIG. 1A) or chisel shapedpoint26P (shown inFIG. 2A).
GENERAL EX VIVO EMBODIMENTFIGS.2A,2B and2C
• In the exvivo embodiment biosensor22 is positioned onbody24 ofdevice20, and does not to pass into the subject during penetration. Alternatively, the biosensor may be positioned on the microprobe sufficiently close to the body end so as not to penetrate. The analyte fluid may be guided alongmicroprobe26 tobiosensor22 through a suitable conduit such as open fluid channel or groove26G formed along the probe. The channel extends between the penetration end of the probe and the biosensor, and conveys the fluid by capillary action. The absence of a prior art type internal bore along the length of the probe reduces the probe diameter and simplifies probe fabrication. The open fluid channel may be a V-groove etched in the silicon ofmicroprobe26. The minute dimensions along apex26A oftriangular groove26G (shown inFIG. 2C cross-section view) produce strong capillary forces that are more reliable than fluid seepage. The width and depth of V-grooves may be precisely controlled by V-groove etching IC technology. However other channel cross-sections may be produced by other techniques such as plasma etching.
ELECTROBIOSENSORSFIGS.1A and1B
• In general the biosensor may be an electrotype biosensor (seeFIG. 1A), in which the signal is electrical energy carried on electrically conductive leads12L andinterface pads14P. More specifically, the biosensor may be an electrochemical biosensor responsive to the analyte presence by altering the electrical energy of the signal in proportion to the concentration of the analyte presence. The analyte signal may be voltage based or current based, and may be a modulation of a quiescent value. The biosensor may be an oscillating electrogravimetric biosensor responsive to the analyte presence by altering the oscillation frequency. The magnitude of the alteration in frequency indicates the concentration of the analyte presence, and may be a.c. coupled to an analyte meter (not shown) through a suitable coupling circuit such as a capacitance device. Gravimetric devices are typically quartz crystal based and alter frequency in response to mass accumulation due to reactant buildup during the analyte sensing. Alternatively, the biosensor may be a thermal biosensor which senses heat generated in an analyte reaction, or an optical biosensor42 (seeFIG. 4A) in which senses reaction light. The light signal alterations are photon energy propagating alongoptical signal carrier42W which widens intooptical coupler42C for interfacing with a meter (not shown). The optical signal carrier may be any suitable photon containment device such as a waveguide or optical fiber transparent at the photon wavelength. The biosensor may be self-luminescent or merely return incident interrogation light.
• The biosensor may be integrated into the surface of the substrate, or housed in a cavity formed in the substrate or in a hole extending through the substrate. The surface ofside10A ofsilicon substrate10S is planar (seeFIG. 1B), andbiosensor12 is deposited onto this flat surface.Cavity20C (see inFIG. 2B) is etched intoside20A ofsilicon substrate20S.Cavity20C extends into the silicon substrate in the Z thickness dimension. The biosensor is deposited onto the silicon within the cavity.Hole40H (seeFIG. 4B) is etched intoside40A ofsilicon substrate40S.Hole40H extends through the silicon substrate in the Z thickness dimension.
• The electrotype biosensor may have a suitable electrically insulative layer such assilicon oxide film10F (seeFIG. 1A) onside10A betweenconductive leads12L andsilicon substrate10S. Silicon oxide is a better insulator than silicon, and may be employed to reduce shunt signal loss between the signal leads.Biosensor12 is deposited on the insulative layer and is electrically isolated from the silicon substrate. The conductive leads and the conductive contacts of the electrotype biosensors may be a suitably conductive material also deposited on the insulative layer such as metal (sputtered Al Au Ti Ag W Cr for example) or carbon or doped silicon. Doped silicon leads may have a customized electrical resistance (and other characteristics) to optimize electrical features such as impedance matching or current limiting. The silicon substrate may also be sufficiently doped to form the conductive material for one of the pair of conductive leads and one of the pair of conductive contacts (seeFIG. 3A).
MULTIPLE BIOSENSOR EMBODIMENTFIGS.3A and3B
• Multiple biosensors may be employed on a single probe. Each of these multiple biosensors may sense the presence of a different analyte. Further, each of the multiple biosensors may be positioned at a different location along the X dimension ofmicroprobe36 to sense analyte presence at a different penetration depth (deep, medium, and shallow). In other embodiments, multiple biosensors may sense the same analyte at different depths, or sense different analytes at the same depth. For example (seeFIGS. 3A and 3B), threebiosensor32D (deep),32M (medium), and32S (shallow) may be deposited ontoside30A ofsilicon substrate30S. These multiple biosensors require multipleconductive leads33D,33M, and33S andmultiple interface contacts34D,34M, and34S.Silicon substrate30S is conductive and forms common returnconductive path30C (or ground) cooperating withconductive leads33D,33M, and33S andinterface contacts34D,34M, and34S. The return conductive path completes the electric circuit from thebiosensors32D,32M, and32S to an external meter and back to the biosensors.Silicon oxide layer30F insulates the conductive return path from the source paths and source pads.
• Further, the multiple biosensors may be located on either or both sides of the microprobe.Biosensor32S is located onback side30B on insulatinglayer31F, withconductive lead33S extending thoughlayer31F andsubstrate30S andlayer30F tofront side30A.
TRANSMITTER EMBODIMENTFIGS.5aand5b
• Microprobe device50M may be sealed within a housing or cover58C withsignal transmitter54T formingmonitoring assembly50A as shown inFIGS. 5A and 5B. The assembly is emplaced at a suitable site on the subject (not shown) for continuous monitoring of the analyte. Analyte data may be transmitted during an extended monitoring period of a few hours or several days or even weeks. Alternatively, the monitoring may be for a short period or even for a single transmission. The assembly transmits analyte concentration data to a remote meter (not shown). Preferably the emplacement site is not subject to disturbance by daily activity of the subject. The inside of the subject's arm is a convenient protected site.Microprobe portion56 penetrates into the subject to access the analyte-containing fluid.Biosensor52 on the microprobe senses analyte presence and provides a sensed signal in response to the analyte presence.
• Base58B extends in the Y dimension and Z dimension generally normal to the X dimension ofmicroprobe portion56, and forms the bottom of the assembly.Cover58C is installed overbody portion54 of the substrate and engagesbase58B for sealing the assembly. Stabilizingsurface58S forms an in vivo face ofbase member58B and is disposed toward the subject when emplaced. The stabilizing surface engages the subject to maintain the penetration orientation of the microprobe portion into the subject. The stabilizing surface may haveadhesive film58A thereon for retaining the assembly at the emplacement site for the duration of the monitoring period. The adhesive holds the assembly onto the skin preventing displacement along the X dimension. The adhesive prevents the probe from working loose during the monitoring period as the subject moves around. In addition, the adhesive prevents lateral displacement of the assembly along the Y and Z dimensions. This lateral retention minimizes shear forces along the length ofprobe56 preventing the probe from snapping off during subject activity. As the assembly is emplaced, the stabilizing surface engages the subject's skin and limits the penetration of the microprobe portion.
• Signal transmitter54T provides a transmitted analyte signal to a meter (not shown). Analog todigital converter54A converts the sensed signal from the biosensor into a digital transmitted signal. A suitable power source such asbattery54B may be provided to activate the signal transmitter and the converter. The transmitter, converter and battery may be deposited into the silicon ofbody portion54.
PAIN PERCEPTION TESTING
• FIG. 6 shows the averaged response from 62 patients in a clinical trial to determine the relative pain perceived from punctures with a silicon microprobe in the arm compared with punctures in the arm and finger with conventional metal lancets. As can be seen from theFIG. 6, the punctures from the silicon microprobe were found to be noticeably less painful than those from the lancet, with the more painful of the two lancet tests being the finger stick, as expected. The test subjects repeatedly commented that the microprobe puncture was virtually painless and far more comfortable than the finger stick with the lancet.
INDUSTRIAL APPLICABILITY
• It will be apparent to those skilled in the art that the objects of this invention have been achieved as described hereinbefore by providing a microprobe device with integrated analyte sensing capability, which accesses the blood and determines the analyte concentration in one simple step. The device is fabricated from a silicon wafer for compatibility with IC fabrication and MEMS technologies. Because the strength of the single-crystal structure of the starting silicon wafer is retained in the finished device, the microprobe can penetrate skin reliably without breaking. The small length, width, and thickness dimensions of the probe introduce minimal tissue displacement, rendering probe insertion and retraction essentially painless. Minimal penetration effort is required which also minimizes mechanical probe failure. The device may function in vivo or ex vivo with one or multiple biosensors, and has both single measurement and continuous monitoring applications.
CONCLUSION
• Various changes may be made in the structure and embodiments shown herein without departing from the concept of the invention. For example, the various types of biosensors may be employed in either the ex vivo embodiment (FIG. 2A) or the in vivo embodiment (FIG. 1A). The stress reducing microfillet shown in the optical biosensor embodiment (FIG. 4A) may be employed in other types of biosensors. The cavity housing (FIG. 2B) and hole housing (FIG. 4B) of the biosensor may be employed in other embodiments. Further, features of embodiments shown in various figures may be employed in combination with embodiments shown in other figures. Therefore, the scope of the invention is to be determined by the terminology of the following claims and the legal equivalents thereof.

Claims (22)

1-25. (canceled)

26. A microprobe device comprising:

a substrate comprising a body, and a microprobe having a body end connected to the body and a penetration end terminating in a point configured to make an incision in the stratum corneum, the penetration end extending along the microprobe from a location recessed from any area of tip formation to the termination of the microprobe and being completely uncovered, any change in overall microprobe thickness along an entire length of the penetration end having a smooth transition; and

one or more sensors non-displaceably adhered to the substrate and located away from the penetration end, such that no sensors are located in any part of the penetration end.

27. The device ofclaim 26, wherein the one or more sensors are located sufficiently close to the penetration end to pass uncovered into the subject during use.

28. The device ofclaim 26, wherein the body and the microprobe are made from a material used as a substrate for integrated circuit fabrication.

29. The device ofclaim 26, wherein the body and the microprobe are fabricated by MEMS processing.

30. The device of claim ofclaim 28, wherein the body and the microprobe are made of silicon.

31. The device ofclaim 29, further comprising an interface structure on an uncovered surface of the body, the body extending integrally from the body end of the microprobe.

32. The device ofclaim 30, wherein the body is operable to limit penetration of the microprobe during use.

33. The device ofclaim 26, where the biosensor is operable to sense an analyte concentration.

34. The device ofclaim 26, wherein the biosensor is coupled to a meter.

35. The device ofclaim 26, wherein the microprobe converges along a length of the microprobe, wherein the microprobe converges along an entire length of the terminal point at a rate greater than the rate of convergence along a portion of the microprobe separate from the terminal point.

36. The device ofclaim 26, wherein the microprobe device converges along an entire length of the penetration end, wherein the rate of convergence along the terminal point is greater than the rate of convergence along a portion of the penetration end separate therefrom.

37. The device ofclaim 26, wherein the substrate has one or more cavities extending into the substrate.

38. The device ofclaim 37, wherein the one or more cavities have a cross-section suited to a fluid channel.

39. The device ofclaim 38, wherein the substrate has one or more open fluid channels, each defined a cavity extending along a surface of the substrate.

40. The device ofclaim 39, wherein the one or more sensors is in one or more fluid channels.

41. The device ofclaim 37, wherein the one or more sensors are in direct contact with one or more cavities.

42. A microprobe device comprising:

a substrate comprising a body and a microprobe having a body end connected to the body and a penetration end;

an open fluid channel formed in the substrate, the channel opening along a surface of the substrate; and

a sensor located on the substrate, wherein at least part of the sensor is positioned to pass uncovered into a subject during use.

43. The device ofclaim 42, wherein the open fluid channel extends from a location away from the penetration end to the body end.

44. The device ofclaim 42, wherein the sensor is on a non-recessed surface of the substrate.

45. The device ofclaim 42, wherein the sensor in fluid contact with the open fluid channel.

46. The device ofclaim 42, wherein the sensor is located within the fluid channel.

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