U.S. patent application number 11/980852 was filed with the patent office on 2008-04-24 for silicon microprobe with integrated biosensor.
Invention is credited to Eugene Orloff, Wilson Smart, Kumar Subramanian.
Application Number | 20080097171 11/980852 |
Document ID | / |
Family ID | 25220711 |
Filed Date | 2008-04-24 |
United States Patent
Application |
20080097171 |
Kind Code |
A1 |
Smart; Wilson ; et
al. |
April 24, 2008 |
Silicon microprobe with integrated biosensor
Abstract
Microprobe device 10 provides an analyte signal from biosensor
12 to an external analyte meter indicating analyte presence in an
analyte-containing bodily fluid of a subject (not shown).
Inventors: |
Smart; Wilson; (Palo Alto,
CA) ; Subramanian; Kumar; (Pleasanton, CA) ;
Orloff; Eugene; (Berkeley, CA) |
Correspondence
Address: |
BLAKELY SOKOLOFF TAYLOR & ZAFMAN
1279 OAKMEAD PARKWAY
SUNNYVALE
CA
94085-4040
US
|
Family ID: |
25220711 |
Appl. No.: |
11/980852 |
Filed: |
October 30, 2007 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
09816472 |
Mar 26, 2001 |
7310543 |
|
|
11980852 |
Oct 30, 2007 |
|
|
|
Current U.S.
Class: |
600/309 |
Current CPC
Class: |
A61B 5/14532 20130101;
A61B 5/14546 20130101; A61B 2560/0412 20130101; A61B 5/685
20130101; A61B 5/0002 20130101; A61B 5/6849 20130101 |
Class at
Publication: |
600/309 |
International
Class: |
A61B 5/145 20060101
A61B005/145 |
Claims
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 of claim 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 of claim 26, wherein the body and the microprobe are
made from a material used as a substrate for integrated circuit
fabrication.
29. The device of claim 26, wherein the body and the microprobe are
fabricated by MEMS processing.
30. The device of claim of claim 28, wherein the body and the
microprobe are made of silicon.
31. The device of claim 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 of claim 30, wherein the body is operable to limit
penetration of the microprobe during use.
33. The device of claim 26, where the biosensor is operable to
sense an analyte concentration.
34. The device of claim 26, wherein the biosensor is coupled to a
meter.
35. The device of claim 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 of claim 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 of claim 26, wherein the substrate has one or more
cavities extending into the substrate.
38. The device of claim 37, wherein the one or more cavities have a
cross-section suited to a fluid channel.
39. The device of claim 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 of claim 39, wherein the one or more sensors is in
one or more fluid channels.
41. The device of claim 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 of claim 42, wherein the open fluid channel extends
from a location away from the penetration end to the body end.
44. The device of claim 42, wherein the sensor is on a non-recessed
surface of the substrate.
45. The device of claim 42, wherein the sensor in fluid contact
with the open fluid channel.
46. The device of claim 42, wherein the sensor is located within
the fluid channel.
Description
PRIORITY
[0001] 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
[0002] 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
[0003] 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.
[0004] 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.
[0005] 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
[0006] 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.
[0007] 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:
[0008] 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.
[0009] B) Transfer step in which the subject transfers the blood
sample to the test strip.
[0010] C) Waste blood step in which the subject cleans-up any waste
blood, and disposes of the blood.
[0011] D) Reset step in which the subject puts away the above
material in readiness for the next blood sampling.
[0012] 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.
[0013] 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.
[0014] 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.
[0015] 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).
[0016] 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.
[0017] 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.
[0018] 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.
[0019] 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.
[0020] 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.
[0021] 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
[0022] 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:
[0023] FIG. 1A is a plan view of in vivo microprobe device 10
showing biosensor 12 on probe 16;
[0024] FIG. 1B is a side view of device 10 of FIG. 1A;
[0025] FIG. 2A is a plan view of ex vivo device 20 showing
biosensor 22 on body 24;
[0026] FIG. 2B is a sectional side view of device 20 of FIG. 2A
along line 2B-2B showing biosensor 22 mounted in cavity 20C on
silicon substrate 20S;
[0027] FIG. 2C is a sectional view across probe 20 of FIG. 2A along
line 2C-2C showing V-groove 26G in silicon substrate 20S;
[0028] FIG. 3A is a plan view of device 30 showing multiple
biosensors 32D and 32M and 32S on probe 36;
[0029] FIG. 3B is a side view of device 30 of FIG. 3A;
[0030] FIG. 4A is a plan view of device 40 showing optical
biosensor 42 and waveguide 42W on probe 46;
[0031] FIG. 4B is a sectional side view of device 40 of FIG. 4A
along line 4B-4B showing the optical biosensor mounted in hole 40H
through silicon substrate 40S;
[0032] FIG. 5A is a plan view of microprobe assembly 50A showing
cover member 58C and base member 58B;
[0033] FIG. 5B is a sectional side view of assembly 50A of FIG. 5A
along line 5B-5B showing transmitter 54T and battery 54B; and
[0034] FIG. 6 is a chart comparing the average pain perception
values for the silicon microprobe device with those for a
conventional metal lancet.
[0035] 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
[0036] The table below lists the reference numerals employed in the
figures, and identifies the element designated by each numeral.
[0037] 10 Microprobe Device 10 [0038] 10A Front Side 10A [0039] 10F
Silicon Oxide Film 10F [0040] 10B Back Side 10B [0041] 10S Silicon
Substrate 10S [0042] 12 Biosensor 12 [0043] 12L Conductive Leads
12L [0044] 14 Body 14 [0045] 14P Electrical Interface Contact Pads
14P [0046] 16 Microprobe 16 [0047] 16B Body End 16B [0048] 16P
Penetration End 16P [0049] 20 Microprobe Device 20 [0050] 20A Front
Side 20A [0051] 20C Cavity 20C [0052] 20S Silicon Substrate 20S
[0053] 22 Biosensor 22 [0054] 24 Body 24 [0055] 26 Microprobe 26
[0056] 26A Apex 26A [0057] 26G Groove 26G [0058] 26P Point 26P
[0059] 30 Device 30 [0060] 30A Front Side 30A [0061] 30C Common
Return Path 30C [0062] 30F Silicon oxide layer 30F [0063] 30B Back
Surface 30B [0064] 30S Substrate 30S [0065] Multiple Biosensors 32D
32M 32S [0066] Multiple Leads 33D 33M 33S [0067] 34 Body 34 [0068]
Multiple interface Contacts 34D 34M 34S [0069] 36 Microprobe 36
[0070] 40 Device 40 [0071] 40A Front side 40A [0072] 40H Hole 40H
[0073] 40S Silicon Substrate 40S [0074] 42 Optical biosensor 42
[0075] 42C Optical Coupler 42C [0076] 42W Waveguide 42W [0077] 44
Body 44 [0078] 46 Microprobe 46 [0079] 46F Rounded Microfillet 46F
[0080] 50A Microprobe Assembly 50A [0081] 50M Microprobe Device 50M
[0082] 52 Biosensor 52 [0083] 54 Body 54 [0084] 54A A/D Converter
54A [0085] 54B Battery 54B [0086] 54T Transmitter 54T [0087] 56
Microprobe 56 [0088] 58A Adhesive Film 58A [0089] 58B Base Member
58B [0090] 58C Cover Member 58C [0091] 58S Stabilizing Surface
58S
GENERAL IN VIVO EMBODIMENT
FIGS. 1A and 1B
[0092] Microprobe device 10 provides an analyte signal from
biosensor 12 to an external analyte meter (not shown) indicating
analyte presence in an analyte-containing fluid of a subject (not
shown). Silicon substrate 10S extends in the X length dimension,
and the Y width dimension, and the Z thickness dimension, forming
large body portion 14 and pointed microprobe portion 16 (as shown
in FIG. 1A). The substrate has front side 10A into which the
biosensor is integrated and back side 10B (as shown in FIG. 1B).
The microprobe has a body end 16B connected to body 14, and a
penetration end 16P 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 as electrical
contact pads 14P may be deposited onto a side of silicon substrate
10S on body 14, for sliding contact connection with the analyte
meter. A suitable signal carrier such as conductive leads 12L may
be deposited onto a side of the silicon substrate between biosensor
12 and interface pads 14P 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.
[0093] 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 in FIG. 1A, in vivo biosensor 12 is positioned on microprobe
16 near penetration end 16P. 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.
[0094] 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
[0095] 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 (see FIG. 3B) from the initial
thickness of the silicon wafer across body 34 to a slender
thickness along probe 36. 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 side 30B of substrate 30S
may be etched away to about 50 micrometers to thin the Z thickness
dimension of the probe.
[0096] The convergence of the microprobe taper may be uniform (as
shown in FIG. 1A) establishing a constant change in the Y width
dimension and a corresponding constant decrease in the
cross-section of probe 16. Alternatively, the convergence of the
microprobe taper may be nonuniform (as shown in FIG. 2A)
establishing a continuous change in the Y width dimension. This
smooth change in width optimizes stress distribution within
microprobe 26 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
microfillet 46F (see FIG. 4A) provides a smooth transition along
the connection between body 44 and the body end of microprobe 46
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 in FIG. 1A) or chisel shaped
point 26P (shown in FIG. 2A).
GENERAL EX VIVO EMBODIMENT
FIGS. 2A, 2B and 2C
[0097] In the ex vivo embodiment biosensor 22 is positioned on body
24 of device 20, 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 along microprobe 26 to
biosensor 22 through a suitable conduit such as open fluid channel
or groove 26G 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 of microprobe 26. The minute
dimensions along apex 26A of triangular groove 26G (shown in FIG.
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.
ELECTROBIOSENSORS
FIGS. 1A and 1B
[0098] In general the biosensor may be an electrotype biosensor
(see FIG. 1A), in which the signal is electrical energy carried on
electrically conductive leads 12L and interface pads 14P. 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
biosensor 42 (see FIG. 4A) in which senses reaction light. The
light signal alterations are photon energy propagating along
optical signal carrier 42W which widens into optical coupler 42C
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.
[0099] 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 of side 10A of
silicon substrate 10S is planar (see FIG. 1B), and biosensor 12 is
deposited onto this flat surface. Cavity 20C (see in FIG. 2B) is
etched into side 20A of silicon substrate 20S. Cavity 20C extends
into the silicon substrate in the Z thickness dimension. The
biosensor is deposited onto the silicon within the cavity. Hole 40H
(see FIG. 4B) is etched into side 40A of silicon substrate 40S.
Hole 40H extends through the silicon substrate in the Z thickness
dimension.
[0100] The electrotype biosensor may have a suitable electrically
insulative layer such as silicon oxide film 10F (see FIG. 1A) on
side 10A between conductive leads 12L and silicon substrate 10S.
Silicon oxide is a better insulator than silicon, and may be
employed to reduce shunt signal loss between the signal leads.
Biosensor 12 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 (see FIG. 3A).
MULTIPLE BIOSENSOR EMBODIMENT
FIGS. 3A and 3B
[0101] 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 of microprobe 36 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 (see FIGS. 3A and 3B),
three biosensor 32D (deep), 32M (medium), and 32S (shallow) may be
deposited onto side 30A of silicon substrate 30S. These multiple
biosensors require multiple conductive leads 33D, 33M, and 33S and
multiple interface contacts 34D, 34M, and 34S. Silicon substrate
30S is conductive and forms common return conductive path 30C (or
ground) cooperating with conductive leads 33D, 33M, and 33S and
interface contacts 34D, 34M, and 34S. The return conductive path
completes the electric circuit from the biosensors 32D, 32M, and
32S to an external meter and back to the biosensors. Silicon oxide
layer 30F insulates the conductive return path from the source
paths and source pads.
[0102] Further, the multiple biosensors may be located on either or
both sides of the microprobe. Biosensor 32S is located on back side
30B on insulating layer 31F, with conductive lead 33S extending
though layer 31F and substrate 30S and layer 30F to front side
30A.
TRANSMITTER EMBODIMENT
FIGS. 5a and 5b
[0103] Microprobe device 50M may be sealed within a housing or
cover 58C with signal transmitter 54T forming monitoring assembly
50A as shown in FIGS. 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 portion 56 penetrates into the subject to access the
analyte-containing fluid. Biosensor 52 on the microprobe senses
analyte presence and provides a sensed signal in response to the
analyte presence.
[0104] Base 58B extends in the Y dimension and Z dimension
generally normal to the X dimension of microprobe portion 56, and
forms the bottom of the assembly. Cover 58C is installed over body
portion 54 of the substrate and engages base 58B for sealing the
assembly. Stabilizing surface 58S forms an in vivo face of base
member 58B 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 have adhesive film 58A 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 of
probe 56 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.
[0105] Signal transmitter 54T provides a transmitted analyte signal
to a meter (not shown). Analog to digital converter 54A converts
the sensed signal from the biosensor into a digital transmitted
signal. A suitable power source such as battery 54B may be provided
to activate the signal transmitter and the converter. The
transmitter, converter and battery may be deposited into the
silicon of body portion 54.
PAIN PERCEPTION TESTING
[0106] 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 the FIG. 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
[0107] 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
[0108] 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.
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