US20090259146A1

US20090259146A1 - Method and apparatus for analyte detecting device

Info

Publication number: US20090259146A1
Application number: US12/421,776
Authority: US
Inventors: Dominique Freeman; Dirk Boecker; Don Alden
Original assignee: Individual
Current assignee: Sanofi Aventis Deutschland GmbH
Priority date: 2008-04-11
Filing date: 2009-04-10
Publication date: 2009-10-15
Also published as: WO2009126900A1; EP2265324B1; EP2265324A1; US9386944B2; EP2265324A4

Abstract

An integrated analyte measurement system includes a housing and a disposable configured to be positioned in the housing. A plurality of penetrating members are positioned in the disposable. A penetrating member driver is configured to be coupled to each of a penetrating member. A plurality of analyte sensors are positioned in the disposable. The disposable houses both used and unused penetrating members and analyte sensors.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims the benefit of U.S. Ser. No. 61/044,329 filed Apr. 11, 2008, which application is fully incorporated herein by reference.

BACKGROUND OF THE INVENTION

1. Field of the Invention
The present invention relates to lancing devices, and more particularly to an analyte sensor device that integrates sample generation, lancing with sample testing.
2. Description of the Related Art
Lancing devices are known in the medical health-care products industry for piercing the skin to produce blood for analysis. Biochemical analysis of blood samples is a diagnostic tool for determining clinical information. Many point-of-care tests are performed using whole blood, the most common being monitoring diabetic blood glucose level. Other uses for this method include the analysis of oxygen and coagulation based on Prothrombin time measurement. Typically, a drop of blood for this type of analysis is obtained by making a small incision in the fingertip, creating a small wound, which generates a small blood droplet on the surface of the skin.
Early methods of lancing included piercing or slicing the skin with a needle or razor. Current methods utilize lancing devices that contain a multitude of spring, cam and mass actuators to drive the lancet. These include cantilever springs, diaphragms, coil springs, as well as gravity plumbs used to drive the lancet. Typically, the device is pre-cocked or the user cocks the device. The device is held against the skin and the user, or pressure from the users skin, mechanically triggers the ballistic launch of the lancet. The forward movement and depth of skin penetration of the lancet is determined by a mechanical stop and/or dampening, as well as a spring or cam to retract the lancet. Such devices have the possibility of multiple strikes due to recoil, in addition to vibratory stimulation of the skin as the penetrating member driver 18 impacts the end of the launcher stop, and only allow for rough control for skin thickness variation. Different skin thickness may yield different results in terms of pain perception, blood yield and success rate of obtaining blood between different users of the lancing device.
Success rate generally encompasses the probability of producing a blood sample with one lancing action, which is sufficient in volume to perform the desired analytical test. The blood may appear spontaneously at the surface of the skin, or may be “milked” from the wound. Milking generally involves pressing the side of the digit, or in proximity of the wound to express the blood to the surface. The blood droplet produced by the lancing action must reach the surface of the skin to be viable for testing. For a one-step lance and blood sample acquisition method, spontaneous blood droplet formation is requisite. Then it is possible to interface the test strip with the lancing process for metabolite testing.
When using existing methods, blood often flows from the cut blood vessels but is then trapped below the surface of the skin, forming a hematoma. In other instances, a wound is created, but no blood flows from the wound. In either case, the lancing process cannot be combined with the sample acquisition and testing step. Spontaneous blood droplet generation with current mechanical launching system varies between launcher types but on average it is about 50% of lancet strikes, which would be spontaneous. Otherwise milking is required to yield blood. Mechanical launchers are unlikely to provide the means for integrated sample acquisition and testing if one out of every two strikes does not yield a spontaneous blood sample.
Many diabetic patients (insulin dependent) are required to self-test for blood glucose levels five to six times daily. Reducing the number of steps required for testing would increase compliance with testing regimes. A one-step testing procedure where test strips are integrated with lancing and sample generation would achieve a simplified testing regimen. Improved compliance is directly correlated with long-term management of the complications arising from diabetes including retinopathies, neuropathies, renal failure and peripheral vascular degeneration resulting from large variations in glucose levels in the blood. Tight control of plasma glucose through frequent testing is therefore mandatory for disease management.
Another problem frequently encountered by patients who must use lancing equipment to obtain and analyze blood samples is the amount of manual dexterity and hand-eye coordination required to properly operate the lancing and sample testing equipment due to retinopathies and neuropathies particularly, severe in elderly diabetic patients. For those patients, operating existing lancet and sample testing equipment can be a challenge. Once a blood droplet is created, that droplet must then be guided into a receiving channel of a small test strip or the like. If the sample placement on the strip is unsuccessful, repetition of the entire procedure including re-lancing the skin to obtain a new blood droplet is necessary.
What is needed is a device, which can reliably, repeatedly and painlessly generate spontaneous blood samples. In addition, a method for performing analytical testing on a sample that does not require a high degree of manual dexterity or hand-eye coordination is required. Integrating sample generation (lancing) with sample testing (sample to test strip) will result in a simple one-step testing procedure resulting in better disease management through increased compliance with self testing regimes.

SUMMARY OF THE INVENTION

An object of the present invention is to provide an analyte sensor device, and its methods of use, that can reliably, repeatedly and painlessly generate spontaneous blood samples.
Another object of the present invention is to provide an analyte sensor device, and its methods of use, that does not require a high degree of manual dexterity or hand-eye coordination for analyte capture and detection.
A further object of the present invention is to provide an analyte sensor device, and its methods of use, that integrates sample generation, lancing, with sample testing, sample to analyte sensor, resulting in a simple one-step testing procedure resulting in better disease management through increased compliance with self testing regimes.
These and other objects of the present invention are achieved in an integrated analyte measurement system that includes a housing and a disposable configured to be positioned in the housing. A plurality of penetrating members are positioned in the disposable. A penetrating member driver is configured to be coupled to each of a penetrating member. A plurality of analyte sensors are positioned in the disposable. The disposable houses both used and unused penetrating members and analyte sensors.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is an exploded diagram illustrated one embodiment of an integrated analyte measurement system of the present invention.

FIG. 2 illustrates one embodiment of a disposable that is position in the integrated analyte measurement system of the present invention.

FIG. 3 is an exploded view of the FIG. 2 disposable.

FIG. 4 illustrates one embodiment of a front surface of an integrated analyte measurement system of the present invention.

FIG. 5 illustrates one embodiment of the electronics used in the integrated analyte measurement system of the present invention.

FIG. 6 illustrates a front end of the FIG. 5 embodiment.

FIG. 7 illustrates one embodiment of a front end used with the integrated analyte measurement system of the present invention.

FIG. 8 illustrates an exploded view of a skin stabilizer that can be used with the integrated analyte measurement system of the present invention.

FIG. 9 is an exploded view of one embodiment of a skin stabilizer and finger positioning device with a disposable used with the integrated analyte measurement system of the present invention.

FIG. 10 is a block diagram of the bleed to read steps implemented by the integrated analyte measurement system of the present invention.

FIG. 11 illustrates the electronic lancing device of the present invention.

FIG. 12 illustrates one embodiment of a seal punch device that can be used with the integrated analyte measurement system of the present invention.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

The present invention is an integrated analyte measurement system, more particularly, a glucose measurement system. The system has macro-electrodes. When a species in a sample, such as glucose in blood is detected, the glucose travels in a planar path of travel relative to the macro-electrodes. The system has a disposable containing the lancets and electrochemical glucose sensors and an instrument and may contain both used and unused lancets, and used and unused glucose sensors during its lifetime. Micro fluidic configurations exist for transporting blood to the sensing area from the wound created in the skin by the lancet. In one embodiment, the instrument has a glucose meter, LCD and electronic lancet actuation mechanism.
The system of the present invention is an integrated body fluid sampling system suitable for body fluid sampling and analyte measurement, particularly for blood glucose monitoring. The glucose measurement system of the present invention uses an electromechanical driver with position and velocity sensing capabilities to advance a penetrating member into a target tissue, creating a wound from which body fluid will flow. A disposable can be provided for use with the electromechanical driver. The disposable houses a plurality of penetrating members. A plurality of analyte detecting members, each containing three electrodes are positioned in sample chambers in the disposable for analyte sensing. The glucose monitoring system has a disposable member that houses the penetrating members and the analyte detecting members. The system of the present invention combines minimal pain lancing with a low-volume sensor in a multi-test disposable. The present invention provides a blood glucose measurement system that reduces pain and increases the convenience of testing.
Referring now to FIGS. 1-3, the present invention is an integrated analyte measurement system, generally denoted as 10, that includes a housing 12 and a disposable 14 configured to be positioned in the housing 10. A plurality of penetrating members 16 are positioned in the disposable 14. A penetrating member driver 18 is configured to be coupled to each of a penetrating member 16.
The housing 12 can be made of plastic molded housings. By way of illustration, and without limitation, a chassis of the housing 12 can be Thixol molded, and miscellaneous molded/thixol parts. The housing 12 contains the penetrating member driver 18 for actuating a penetrating member 16 into the skin for sampling and transporting blood from a finger to a chemical reagent and associated disposable opening mechanisms including punches, and disposable moving mechanisms such as a motor drive, as more fully described below.
In one embodiment, illustrated in FIG. 4, the housing 10 is easily held in one hand and ergonomically contoured. The design can be a keyhole shape, with a rounded zone at the top to accommodate the round disposable, and a narrower handle zone.
The penetrating member driver 18 is coupled to a processor 20, FIG. 5, that provides for position and velocity sensing capabilities to advance a penetrating member 16 into a target tissue to create a wound from which body fluid will flow. A plurality of analyte sensors 22 are positioned in the disposable 14. The disposable 14 houses both used and unused penetrating members 16 and analyte sensors 22. Blood capture is achieved through microfluidic capture of a spontaneously generated blood droplet from the surface of the finger after lancing. Blood is drawn using microfluidic structures which transport the blood rapidly to the analyte sensors 22.
To lance skin in order to obtain a blood sample, the plurality of penetrating members 16 in disposable 14 can be each designed to be removably coupled to the penetrating member driver 18 and then advanced to pierce tissue positioned inside the analyte sensor 22. During sample acquisition and measurement the tip of the penetrating member remains within the analyte sensor. Blood generated from the wound is brought to the sample chamber using the microfluidic structures. The blood covers the electrodes which are used in a specific sequence to measure the amount of glucose in capillary whole blood As a non-limiting example, the sample chamber can be sized to detect glucose in an amount of about 0.06 uL.
A display 24, user interface 26, and a rechargeable battery can be included. In one embodiment, the penetrating member driver 18 is electromechanical driver. Micro fluidic configurations are provided for transporting blood to the analyte sensors 22 which are typically positioned in sample chambers, not shown. The system 10 can include a glucose meter, LCD and other components including but not limited to, a power supply, memory, connectors, motor drive and the like, as illustrated in FIG. 5.
A shutter 28, FIG. 6, covers at least a portion of a front end 30 of the housing 12. As illustrated in FIGS. 7-9, the front end 30 can include a tissue stabilizer 32. The tissue stabilizer 32 can be an elastomer structure affixed to the housing 12 and be configured to convert a force applied by the finger parallel to a penetrating member axis into a pressure profile in the finger skin and underlying tissue to express a blood sample from a wound created by a penetrating member 16. The tissue stabilizer 32 promotes the automatic expression of blood to the surface of the skin for sample capture without the need to manually manipulate the finger (“milking”). Spontaneity success rate (or ‘spontaneity’) is the ratio of spontaneous blood samples achieved to the number of lancet penetrations.
The front end 30 can be coupled to a connector device and a finger positioning system to properly position the finger. The connector device can provide an electrical connection between analyte sensor electrode pads and the glucose read electronics of processor 20. This can be shaped to support the front end 30 or can have other shapes that enable metal pins of the electrode pads to connect to the carbon electrode pads of the analyte sensor 22 once a humidity seal has been opened by, as more fully explained hereafter.
Once a blood sample has been acquired and the reading complete the connector is removed from an analyte sensor pocket. In addition to stabilization of the finger provided by the front end 30, a finger surface of the front end 30 should be precisely positioned with respect to a front face of an analyte sensor 22 during a test. If the positioning is not correct, there is increased risk that the blood droplet that forms on the skin surface will either not be captured or will be captured improperly. The distance of the finger from the surface of the analyte sensor 22 can be provided by the walls of pockets in the disposable 14. The finger positioning system detects that the finger is in contact with the disposable walls and then relays that information to the user. Additionally that the blood droplet that forms on knowing the pressure applied by the finger to the wall adds a performance improvement.
A simple “Testing Mode” of the system 10 can be initiated. This can be achieved by sliding open the shutter 28. This allows the user to adjust lancing depth setting prior to testing, as well as immediately after an unsuccessful lancing attempt, or after a successful result is achieved. It can also include “Finger Mapping” functionality that will allow the user to graphically select the finger to be tested, and set the desired depth for that finger, to be remembered for the next test. Status such as time, remaining tests, battery life, and the like, can be displayed. The system 10 can also provide more sophisticated data management features which may include, for example, color graphing of trends and results.
The processor 20, is coupled with resources that include a microprocessor and provides one or more of, data processing, calibration curves, look-up tables, electronic control of penetrating member trajectory during skin cutting, velocity and the like.
Electronic control of penetrating members 16 provides for control of penetrating member position and velocity profile during an entire lancing process of the penetrating member 16. In one embodiment, the system 10, through penetrating member driver 18 and processor 20, provides an electronic brake for each of penetrating member 16. The system 10 provides for control of drive power to a penetrating member 16 and a lancing speed to account for variations in skin thickness.
Electronic control, through processor 20 of the lancet trajectory during skin cutting and retraction, allows the user to optimize lancing parameters for reproducible lancing with blood droplet generation at the surface of the skin with reduced pain, and rapid wound healing. The result is a “bleed-to-read” device which allows the user to press a single button and achieve a blood glucose reading in a single step. FIG. 10 illustrates the bleed to read steps and includes, test preparation, lancing, spontaneity, blood sample capture, blood sample transport, analyte measurement and presentation of results.
Electronic control of penetrating member trajectory during skin cutting and retraction allows the user to optimize lancing parameters for reproducible lancing with blood droplet generation at the surface of the skin with reduced pain, and rapid wound healing. Programmable control of penetrating member position, and its velocity profile, is possible over the entire lancing process (including the start of the lancet acceleration, tracking the lancet position, measuring the lancet velocity, controlling the distal stop, and controlling the skin penetration depth) provides a number of advantages.
Controlling the drive power from penetrating member driver 18, FIG. 11, as well as lancing speed can take into account variation in skin thickness. With the present invention, electronic braking provides a soft stop of a penetrating member 16 when a required depth of penetration through the skin surface has been reached. Avoiding a hard mechanical stop at the end of the inbound process reduces the pain perceived post lancing which is a direct result of vibrational energy transferred to the finger at the peak of the lancing event, e.g., residual pain. The electronic drive and the control of penetrating member motion using rapid lancet cutting speed in an inward direction, and a slower withdrawal speed, with a lightweight penetrating member, and accurate depth control reduces the initial pain of the lancing, as well as the residual pain and improves wound healing
Rapid cutting of tissue with the penetrating member 16 minimizes the shock waves produced when the penetrating member strikes the skin in addition to compressing the skin for efficient cutting. This reduces the pain perceived by the user during the skin cutting process. Slow withdrawal of the lancet ensures spontaneity of blood droplet formation at the surface of the finger so that milking of the finger is not required.
Accurate control of penetration depth has two major benefits, less pain and sufficient blood. Less pain is achieved by cutting only the amount of tissue necessary to reach the blood vasculature, namely the superficial reticular layer (SRL). This minimizes the number of severed nerve fibers and amount of damaged tissue. Secondly, only the required amount of blood is generated. The present invention provides a system 10 with more repeatable, precise depth penetration allows the user to minimize depth while still being confident of getting sufficient blood for a test.
The penetrating member driver 18 can function as a variable reluctance device and can be composed of an electronic drive unit or solenoid, an optical position sensor and a penetrating member gripping mechanism that couples to penetrating members 16. The processor 20 controls the display. The processor 20 also controls solenoid drive coils when they are included in the system. A penetrating member 16 can be driven by a series of solenoid coils enclosed in a coil pack which surrounds a drive shaft coupled to the penetrating member 16. A ferromagnetic bead can be attached to the drive shaft and slides within a lumen of the solenoid drive coils which drive the penetrating member 16 using magnetic attraction of the slug. A feedback loop modulates the penetrating member 16 derived to follow a predetermined velocity versus position or time profile. The advancement and retraction profiles of the penetrating member 16 through the skin govern the pain, success and spontaneous generation of the blood sample. The user can be prompted for information at a beginning and at the end of a lancing event to more adequately suit the user. In this manner a different profile can be changed or implemented, or an existing profile can be modified. Position sensing can be achieved by coupling the penetrating member driver 18 with an optical position sensor and the like that feeds velocity and position information to a microprocessor for accurate position determination of the penetrating member 16 throughout its entire trajectory.
The system 10 of the present invention can measure the position or velocity of the penetrating member 16 using a feedback or servomechanism. In keeping track of the velocity and position of the penetrating member 16 as the penetrating member 16 moves towards or away from the patient's skin, the processor 20 also monitors and adjusts the electrical current to the coils. In transitioning current between the coils, the processor 20 can take into account various factors, including but not limited to, the speed of the penetrating member 16, position of the penetrating member relative to the coils, and the level of current to be applied to the coils to achieve a desired speed or acceleration. In this manner the processor 20 provides a controlled force to the penetrating member 20 that directs the movement of the penetrating member 16 in to or out of the skin.
At least one indexer 34, FIG. 3, indexes the plurality of analyte sensors 22 and penetrating members 16. In one embodiment the penetrating members 16 are coupled to a support, and the support is coupled to a frame that includes the analyte sensors 22.
The system 10 includes at least one sterility seal 36 and at least one humidity seal 38, FIG. 3. One or more openers 40, including but not limited to a punch, FIG. 12, is used to open the sterility seal 36 and the humidity seal 38. In one embodiment a punch 40 opens one or more sterility seals 36 so that the penetrating member 16 can be gripped and actuated, and the humidity seal 38 can be opened using a punch 40 at a front of the disposable 14 so that the penetrating member 16 can exit the sterilized disposable 14. In one embodiment, inner and outer humidity deals 38 are provided and are opened so that a penetrating member 16 can transect the protected analyte sensor 22 into the skin for blood sample acquisition.
A desiccant can be provided and included in one or both of an interior of the housing 12 and the disposable 14. The desiccant for the humidity seal 38 can be co-molded during an injection molding process. In one embodiment, a disk 42, FIG. 3, of 50 radially arranged lancets is provided on a plastic support, attached to which is the frame or cage that holds 50 individual analyte sensors 22, desiccant and the seals 36 and 38.
The disposable 14 can be inserted through a door of the housing, indexed, a bar then read, sterility and humidity seals 36 and 38, opened and a connection with the analyte sensors 22 made in readiness for a blood glucose test.
The analyte sensors 22 can be glucose sensors with three electrodes. A mediator can be part of the working electrode. The mediator is not a separate element from the working electrode. The glucose sensors 22 can include the following layers, conductive layer, insulating layer, reference and counter electrode, working electrode, hydrophilic membrane, spacer layer and adhesive layer. In one embodiment, a carbon paste can be provided on top of a substrate to form conducting layers for a screen-printed three-electrode system. A spacer layer can also be provided. The reference and the counter electrodes can be made of a formulation of Ag/AgCl. The analyte sensor 22 can be based on chrono-amperometry measurement technique using glucose oxidase (Gox) enzyme and N, N, N′, N′-Tetramethyl-p-phenylenediamine (TMPD), as electron transfer mediator. The working electrode can be a carbon paste blended with Gox, the mediator, a buffer and a thinner. A hydrophilic layer or membrane can be provided on top of the electrodes. In some embodiments, only the working electrode has the hydrophilic layer.
The analyte sensor 22 can be an electrochemical glucose sensor that has 3 electrodes and associated chemistry. The test strip can be based on chrono-amperometry measurement technique using glucose oxidase (Gox) enzyme and N,N,N,N′-Tetramethyl-p-phenylenediamine (TMPD), as electron transfer mediator.
The sensor can be a screen-printed three-electrode system. The conducting layers can be made with a commercially available carbon paste. The reference and the counter electrodes can be made of a commercial formulation of Ag/AgCl. The working electrode can be made from the same commercial carbon paste blended with Gox, the mediator, a buffer and a thinner. The test strip has optimized the composition of the working electrode material to lower the response time. A phosphate buffer can be used to mitigate pH sensitivity of the mediator. In one embodiment, the sensor has a hydrophilic membrane with a surfactant that stabilizes an otherwise sublimable mediator. This is, presumably, achieved due to low solubility of the mediator in the hydrophilic membrane.
The glucose reading uses the three electrode system where signal is a current source provided by a constant oxidation potential of 130 mV between the working electrode and the reference electrode. The average of current readings after reaching a predetermined equilibrium point is read out. The measuring time can be 4 seconds and the test time (from thought to result) can be 12 seconds or less. The average of the current reading from 3.75-4 sec can be taken as the signal for the corresponding glucose value. A calibration curve can be constructed from this information as well reference glucose values.
In the starting condition, a counter array can be closed. If the blood sample wets the working electrode a current can be detected (non-regulated potential). After that, the relays are switched to the open modus. If the blood sample wets the reference electrode, the measurement starts. Then, the counter relays closes and an amperometric measurement for the detection of the glucose occurs. This gives the opportunity to measure the flow rate of the blood and reload the system with more blood. If the time difference (current peak, if working electrode has been wet, and current peak, if reference electrode has been wet) can be too long; the measurement can be omitted (time control for reloading). The threshold level (value for auto trigger) can be adjustable from 50 to 2,000 nA.
A polymer substrate supports various layers that can be printed or laminated. Electrical contact pads for making the electrical connection between the glucose meter and the single-use glucose sensor are present. The sensor and support can be oriented perpendicularly to the longitudinal axis of the lancet. There can be an opening in the sensor substrate through which the lancet can pass. Microfluidic ample capture structures can be arranged around this through-hole to capture blood from the surface of the skin. A fluid channel conveys blood from the sample capture structure to the glucose sensor. This fluid channel can be enclosed, except at the ends, which are open to the sample capture structure and the atmosphere, respectively. The channel walls and surface of the sample capture structure may be coated with a sponge like porous membrane to aid drawing blood into the sensor.
The analyte sensors 22 can be manufactured in sheets where a 2-D grid can be created using a combination of screen printing and laminating. The sheet can be then cut into ribbons, which each have a 1-D array of sensors. Individual sensors can be then punched or cut out of these ribbons and inserted into the individual pockets.
Expected variations or differences in the results are contemplated in accordance with the objects and practices of the present invention. It is intended, therefore, that the invention be defined by the scope of the claims which follow and that such claims be interpreted as broadly as is reasonable.

Claims

1. An integrated analyte measurement system, comprising:

a housing;

a disposable configured to be position in the housing;

a plurality of penetrating members positioned in the disposable;

a driver configured to be coupled to the penetrating member, the driver coupled to a processor and having position and velocity sensing capabilities to advance a penetrating member into a target tissue to create a wound from which body fluid will flow; and

a plurality of analyte sensors positioned in the disposable, the disposable housing used and unused penetrating members and analyte sensors.

2. The system of claim 1, wherein the driver is an electromechanical driver.

3. The system of claim 1, wherein the system provides for electronic control of penetrating member trajectory during skin cutting.

4. The system of claim 1, further comprising:

a display; and

a user interface.

5. The system of claim 1, further comprising:

a shutter that covers at least a portion of a front end of the housing.

6. The system of claim 5, wherein a testing mode of the system is initiated by opening the shutter.

7. The system of claim 1, further comprising:

resources that include a microprocessor which provides at least one of, data processing, calibration curves and look-up tables.

8. The system of claim 1, further comprising:

at least one indexer for indexing the plurality of analyte sensors and penetrating members.

9. The system of claim 1, wherein the housing includes a front end with a skin stabilizer.

10. The system of claim 1, wherein the plurality of penetrating members are coupled to a support, the support being coupled to a frame that includes the plurality of analyte sensors.

11. The system of claim 1, further comprising:

at least one sterility seal and at least one humidity seal.

12. The system of claim 11, further comprising:

an opening member for opening at least one of, the at least one sterility seal and the humidity seal.

13. The system of claim 1, further comprising: a desiccant positioned in an interior of at least one of the housing and the disposable.

14. The system of claim 3, wherein the electronic control provides for control of penetrating member position and velocity profile during an entire lancing process of the penetrating member.

15. The system of claim 3, wherein the system has an electronic brake for each of a penetrating member.

16. The system of claim 3, wherein the system provides for control of drive power to a penetrating member and a lancing speed to account for variations in skin thickness.

17. The system of claim 1, wherein each of a sensor includes three electrodes position in a sample chamber.

18. The system of claim 1, wherein each sensor is a glucose sensor with three electrodes positioned in a sample chamber.

19. The system of claim 18, wherein a mediator is included as part of a working electrode.

20. The system of claim 19, wherein the mediator is not a separate element from the working electrode.

21. The system of claim 18, wherein each glucose sensor includes a, conductive layer, insulating layer, reference and counter electrode and working electrode.

22. The system of claim 21, wherein each glucose sensor includes a, hydrophilic membrane, spacer layer and adhesive layer.

23. The system of claim 18, wherein the sensors are screen-printed.

24. The system of claim 23, wherein a carbon paste is provided on top of a substrate to form conducting layers for a screen-printed three-electrode system.

25. The system of claim 1, wherein during sample acquisition and measurement a tip of a penetrating member remains within an associated analyte sensor.