WO1999045375A1 - Process for producing an electrochemical biosensor - Google Patents

Process for producing an electrochemical biosensor Download PDF

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Publication number
WO1999045375A1
WO1999045375A1 PCT/US1999/003781 US9903781W WO9945375A1 WO 1999045375 A1 WO1999045375 A1 WO 1999045375A1 US 9903781 W US9903781 W US 9903781W WO 9945375 A1 WO9945375 A1 WO 9945375A1
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WO
WIPO (PCT)
Prior art keywords
substrate
conductive material
sensor
channels
forming
Prior art date
Application number
PCT/US1999/003781
Other languages
English (en)
French (fr)
Inventor
James Say
Michael F. Tomasco
Adam Heller
Yoram Gal
Behrad Aria
Ephraim Heller
Phillip J. Plante
Mark S. Vreeke
Original Assignee
Therasense, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Therasense, Inc. filed Critical Therasense, Inc.
Priority to AU27797/99A priority Critical patent/AU2779799A/en
Priority to EP99908338.9A priority patent/EP1060388B1/en
Priority to JP2000534863A priority patent/JP4905906B2/ja
Publication of WO1999045375A1 publication Critical patent/WO1999045375A1/en

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1468—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means
    • A61B5/1473—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means invasive, e.g. introduced into the body by a catheter
    • A61B5/14735—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means invasive, e.g. introduced into the body by a catheter comprising an immobilised reagent
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1486—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using enzyme electrodes, e.g. with immobilised oxidase
    • A61B5/14865—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using enzyme electrodes, e.g. with immobilised oxidase invasive, e.g. introduced into the body by a catheter or needle or using implanted sensors
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12Q—MEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
    • C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/001—Enzyme electrodes
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/28—Electrolytic cell components
    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
    • G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
    • G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
    • G01N27/3272—Test elements therefor, i.e. disposable laminated substrates with electrodes, reagent and channels
    • G—PHYSICS
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    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
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    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G01N33/54393—Improving reaction conditions or stability, e.g. by coating or irradiation of surface, by reduction of non-specific binding, by promotion of specific binding
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/66—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving blood sugars, e.g. galactose
    • A—HUMAN NECESSITIES
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    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0271—Thermal or temperature sensors
    • A—HUMAN NECESSITIES
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    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/12—Manufacturing methods specially adapted for producing sensors for in-vivo measurements
    • A61B2562/125—Manufacturing methods specially adapted for producing sensors for in-vivo measurements characterised by the manufacture of electrodes
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    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T156/00—Adhesive bonding and miscellaneous chemical manufacture
    • Y10T156/10—Methods of surface bonding and/or assembly therefor
    • Y10T156/1052—Methods of surface bonding and/or assembly therefor with cutting, punching, tearing or severing
    • Y10T156/1062—Prior to assembly
    • Y10T156/1064—Partial cutting [e.g., grooving or incising]
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
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    • Y10T156/10—Methods of surface bonding and/or assembly therefor
    • Y10T156/1052—Methods of surface bonding and/or assembly therefor with cutting, punching, tearing or severing
    • Y10T156/1082—Partial cutting bonded sandwich [e.g., grooving or incising]
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
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    • Y10T29/00—Metal working
    • Y10T29/42—Piezoelectric device making
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
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Definitions

  • the present invention relates to a process for the manufacture of small sensors, including small electrochemical sensors. More particularly, the process of the invention includes disposing a conductive material on a substrate, preferably in channels formed on the surface of the substrate, thereby forming conductive traces and electrodes in a rapid, efficient manner, with reproducible surface areas and conductivites, and particularly forming very small conductive traces.
  • the monitoring of the level of glucose or other biochemicals, such as lactate, in individuals is often important. High or low levels of glucose or other biochemicals may be detrimental to an individual's health.
  • the monitoring of glucose is particularly important to individuals with diabetes as they must determine when insulin is needed to reduce glucose levels in their bloodstream or when additional glucose is needed to raise the level of glucose in the bloodstream.
  • Conventional techniques for monitoring blood glucose levels currently include the periodic drawing of blood, the application of that blood to a test strip, and the determination of the blood glucose concentration using electrochemical, colorimetric, or photometric methods. This technique does not allow for continuous monitoring of blood glucose levels, but must be performed on a periodic basis.
  • a variety of other devices have also been developed for continuous monitoring of analytes in the blood stream or subcutaneous tissue.
  • the user's comfort and the range of activities that can be performed while the sensor is implanted are important considerations in designing extended-use sensors for continuous in vivo monitoring of the level of an analyte, such as glucose. 2
  • Small sized non-electrochemical sensors including, for example, temperature probes, would also be useful if they could be reliably and reproducibly manufactured. A process for the manufacture of small sensors with reproducible surfaces is needed.
  • the present invention provides a process for the manufacture of small sensors which is efficient, reliable, and provides reproducible surfaces.
  • the process of the invention includes forming one or more channels on a surface of a substrate and disposing a conductive material within the formed channels to form an electrode.
  • Various embodiments of the process include the manufacture of electrochemical sensors by disposing a sensing layer on the conductive material within the formed channels; the manufacture of a sensor having one or more working electrodes; counter/reference electrodes, temperature sensors and the like formed in a plurality of channels on one or more surfaces of the substrate; and sensors having a plurality of electrode traces separated by very small distances to form a small electrochemical sensor.
  • One aspect of the present invention relates to a process for the manufacture of an electrochemical sensor using a web process, which may be continuous or non- continuous.
  • the process includes the steps of providing a substrate web, and disposing a pattern of a conductive material on the continuous substrate web to form an electrode, including one or more working electrodes and counter electrodes.
  • the 3 method also includes the step of disposing a sensing layer on the working electrode disposed on the web.
  • Such a continuous web process is adapted for relatively inexpensively, efficiently, reproducibly and precisely manufacturing electrochemical sensors.
  • Another aspect of the present invention includes a process for the manufacture of an electrochemical sensor having one or more working and/or counter electrodes disposed on a sensor substrate.
  • the method includes the steps of providing a substrate and disposing a conductive material on the substrate to form one or more working electrodes and/or counter electrodes, and optionally disposing a sensing layer on the working electrode.
  • a further aspect of the present invention relates to process for the manufacture of an electrochemical sensor having electrodes and conductive traces disposed within channels defined by a sensor substrate.
  • the process includes the steps of providing a substrate, and forming first and second channels in the substrate.
  • the process also includes the step of disposing a conductive material within the channels to form a working electrode located at the first channel, and a counter electrode located at the second channel.
  • the process further includes the optional step of disposing a sensing layer on the working electrode.
  • the invention includes a continuous process for multi-step preparation of sensors including the efficient and precise deposition of small electrode tracings; sensing layers; counter electrodes, temperature sensors, and like constituents to efficiently produce electrochemical and non-electrochemical biosensors.
  • Figure 1 is a block diagram of one embodiment of an analyte monitor using an analyte sensor, according to the invention
  • Figure 2 is a top view of one embodiment of an analyte sensor, according to the invention
  • Figure 3A is a cross-sectional view of the analyte sensor of Figure 2;
  • Figure 3B is a cross-sectional view of another embodiment of an analyte sensor, according to the invention.
  • Figure 4 A is a cross-sectional view of yet another embodiment of an analyte sensor, according to the invention.
  • Figure 4B is a cross-sectional view of a fourth embodiment of an analyte sensor, according to the invention.
  • Figure 5 is an expanded top view of a tip portion of the analyte sensor of Figure 2;
  • Figure 6 is a cross-sectional view of a fifth embodiment of an analyte sensor, according to the invention.
  • Figure 7 is an expanded top view of a tip-portion of the analyte sensor of Figure 6;
  • Figure 8 is an expanded bottom view of a tip-portion of the analyte sensor of Figure 6;
  • Figure 9 is a side view of the analyte sensor of Figure 2;
  • Figure 10 is a top view of the analyte sensor of Figure 6;
  • Figure 11 is a bottom view of the analyte sensor of Figure 6.
  • Figure 12 is a schematic illustration of an exemplary method or system for manufacturing the sensor of Figure 2;
  • Figure 13 is a perspective view of an exemplary embossing roller suitable for use in the system of Figure 12;
  • Figure 14 is a perspective of an alternative embossing roller
  • Figure 15A is cross sectional view taken along section line 15a-15a of Figure 12;
  • Figure 15B is a cross sectional view taken along section line 15b-15b of Figure 12; 5
  • Figure 15C is a cross sectional view taken along section line 15c-15c of Figure 12;
  • Figure 15D is a cross sectional view taken along section line 15d-15d of Figure 12;
  • Figure 16 illustrates a system in accordance with the principles of the present invention for making the sensor of Figures 10 and 11 ;
  • Figure 17 is a top view of another embodiment of an analyte sensor, according to the invention.
  • the process of the present invention is applicable to the manufacture of an analyte sensor for the in vivo and/or in vitro determination of an analyte, such as glucose or lactate, in a fluid.
  • the process is also applicable to the production of other sensors, including, for example biosensors relaying a chemical signal through a conductive tracing. .
  • the analyte sensors of the present invention can be utilized in a variety of contexts.
  • one embodiment of the analyte sensor is subcutaneously implanted in the interstitial tissue of a patient for the continuous or periodic monitoring of a level of an analyte in a patient's interstitial fluid. This can then be used to infer the analyte level in the patient's bloodstream.
  • Other in vivo analyte sensors can be made, according to the invention, for insertion into a vein, artery, or other portion of the body containing fluid in order to measure a bioanalyte.
  • the in vivo analyte sensors may be configured for obtaining a single measurement and/or for monitoring the level of the analyte over a time period which may range from hours to days or longer. 6
  • analyte sensor is used for the in vitro determination of the presence and/or level of an analyte in a sample, and, particularly, in a small volume sample (e.g., 1 to 10 microliters or less). While the present invention is not so limited, an appreciation of various aspects of the invention will be gained through a discussion of the examples provided below.
  • a "counter electrode” refers to an electrode paired with the working electrode, through which passes a current equal in magnitude and opposite in sign to the current passing through the working electrode.
  • the term “counter electrode” is meant to include counter electrodes which also function as reference electrodes (i.e., a counter/reference electrode).
  • An “electrochemical sensor” is a device configured to detect the presence and/or measure the level of an analyte in a sample via electrochemical oxidation and reduction reactions on the sensor. These reactions are transduced to an electrical signal that can be correlated to an amount, concentration, or level of an analyte in the sample.
  • Electrolysis is the electrooxidation or electroreduction of a compound either directly at an electrode or via one or more electron transfer agents.
  • a compound is "immobilized" on a surface when it is entrapped on or chemically bound to the surface.
  • non-leachable or “non-releasable” compound or a compound that is
  • non-leachably disposed is meant to define a compound that is affixed on the sensor such that it does not substantially diffuse away from the working surface of the working electrode for the period in which the sensor is used (e.g., the period in which the sensor is implanted in a patient or measuring a sample).
  • Components are "immobilized" within a sensor, for example, when the components are covalently, ionically, or coordinatively bound to constituents of the sensor and/or are entrapped in a polymeric or sol-gel matrix or membrane which precludes mobility.
  • An "electron transfer agent” is a compound that carries electrons between the analyte and the working electrode, either directly, or in cooperation with other 7 electron transfer agents.
  • One example of an electron transfer agent is a redox mediator.
  • a “working electrode” is an electrode at which the analyte (or a second compound whose level depends on the level of the analyte) is electrooxidized or electroreduced with or without the agency of an electron transfer agent.
  • a "working surface” is that portion of the working electrode which is coated with or is accessible to the electron transfer agent and configured for exposure to an analyte-containing fluid.
  • a “sensing layer” is a component of the sensor which includes constituents that facilitate the electrolysis of the analyte.
  • the sensing layer may include constituents such as an electron transfer agent, a catalyst which catalyzes a reaction of the analyte to produce a response at the electrode, or both.
  • the sensing layer is non-leachably disposed in proximity to or on the working electrode.
  • a "non-corroding" conductive material includes non-metallic materials, such as carbon and conductive polymers.
  • the sensors of the present invention can be utilized in a variety of devices and under a variety of conditions.
  • the particular configuration of a sensor may depend on the use for which the sensor is intended and the conditions under which the sensor will operate (e.g., in vivo or in vitro).
  • One embodiment of the analyte sensor is configured for implantation into a patient or user for in vivo operation.
  • implantation of the sensor may be made in the arterial or venous systems for direct testing of analyte levels in blood.
  • a sensor may be implanted in the interstitial tissue for determining the analyte level in interstitial fluid. This level may be correlated and/or converted to analyte levels in blood or other fluids.
  • the site and depth of implantation may affect the particular shape, components, and configuration of the sensor.
  • Subcutaneous implantation may be preferred, in some cases, to limit the depth of implantation of the sensor.
  • Sensors may also be implanted in other regions of the body to determine analyte levels in other fluids. Particularly useful sensors are described in U.S. Patent Application 8
  • An implantable analyte sensor may be used as part of an analyte monitoring system to continuously and/or periodically monitor the level of an analyte in a body fluid of a patient.
  • the analyte monitoring system 40 also typically includes a control unit 44 for operating the sensor 42 (e.g., providing a potential to the electrodes and obtaining measurements from the electrodes) and a processing unit 45 for analyzing the measurements from the sensor 42.
  • the control unit 44 and processing unit 45 may be combined in a single unit or may be separate.
  • Another embodiment of the sensor may be used for in vitro measurement of a level of an analyte.
  • the in vitro sensor is coupled to a control unit and/or a processing unit to form an analyte monitoring system.
  • an in vitro analyte monitoring system is also configured to provide a sample to the sensor.
  • the analyte monitoring system may be configured to draw a sample from, for example, a lanced wound using a wicking and/or capillary action. The sample may then be drawn into contact with the sensor. Examples of such sensors may be found in U.S. Patent Application Serial No. 08/795,767 and PCT Patent Application No. PCT/US98/02652, entitled "Small Volume in vitro Analyte Sensor", filed on February 6, 1998, Attorney Docket No. 12008.11WOI1, incorporated herein by reference.
  • Other methods for providing a sample to the sensor include using a pump, syringe, or other mechanism to draw a sample from a patient through tubing or the like either directly to the sensor or into a storage unit from which a sample is obtained for the sensor.
  • the pump, syringe, or other mechanism may operate continuously, periodically, or when desired to obtain a sample for testing.
  • Other useful devices for providing an analyte-containing fluid to the sensor include microfiltration and/or microdialysis devices.
  • the analyte may be drawn from the body fluid through a microporous membrane, for example, by osmotic pressure, into a carrier fluid which is then conveyed to the sensor for analysis.
  • Other useful devices for acquiring a sample are those that collect body fluids transported across the skin 9 using techniques, such as reverse iontophoresis, to enhance the transport of fluid containing analyte across the skin.
  • the Sensor A sensor 42 includes at least one working electrode 58 formed on a substrate 50, as shown in Figure 2.
  • the sensor 42 may also include at least one counter electrode 60 (or counter/reference electrode) and/or at least one reference electrode 62 (see Figure 8).
  • the counter electrode 60 and/or reference electrode 62 may be formed on the substrate 50 or may be separate units.
  • the counter electrode and/or reference electrode may be formed on a second substrate which is also implanted in the patient or, for some embodiments of the implantable sensors, the counter electrode and/or reference electrode may be placed on the skin of the patient with the working electrode or electrodes being implanted into the patient.
  • the use of an on-the-skin counter and/or reference electrode with an implantable working electrode is described in U.S. Patent No. 5,593, 852, incorporated herein by reference.
  • the working electrode or electrodes 58 are formed using conductive traces 52 disposed on the substrate 50.
  • the counter electrode 60 and/or reference electrode 62, as well as other optional portions of the sensor 42, such as a temperature probe 66 (see Figure 8), may also be formed using conductive traces 52 disposed on the substrate 50. These conductive traces 52 may be formed over a smooth surface of the substrate 50 or within channels 54 formed by, for example, embossing, indenting or otherwise creating a depression in the substrate 50.
  • a sensing layer 64 (see Figures 3 A and 3B) is often formed proximate to or on at least one of the working electrodes 58 to facilitate the electrochemical detection of the analyte and the determination of its level in the sample fluid, particularly if the analyte can not be electrolyzed at a desired rate and/or with a desired specificity on a bare electrode.
  • the sensing layer 64 may include an electron transfer agent to transfer electrons directly or indirectly between the analyte and the working electrode 58.
  • the sensing layer 64 may also contain a catalyst to catalyze a reaction of the analyte.
  • the components of the sensing layer may be in a fluid or gel that is proximate to or in contact with the working electrode 58.
  • the 10 components of the sensing layer 64 may be disposed in a polymeric or sol-gel matrix that is proximate to or on the working electrode 58.
  • the components of the sensing layer 64 are non-leachably disposed within the sensor 42. More preferably, the components of the sensor 42 are immobilized within the sensor 42.
  • the sensor 42 may also include a temperature probe 66 (see Figures 6 and 8), a mass transport limiting layer 74 (see Figure 9), a biocompatible layer 75 (see Figure 9), and/or other optional components, as described below. Each of these items enhances the functioning of and/or results from the sensor 42, as discussed below.
  • the substrate 50 may be formed using a variety of non-conducting materials, including, for example, polymeric or plastic materials and ceramic materials. Suitable materials for a particular sensor 42 may be determined, at least in part, based on the desired use of the sensor 42 and properties of the materials.
  • the substrate is flexible.
  • the sensor 42 may be made flexible (although rigid sensors may also be used for implantable sensors) to reduce pain to the patient and damage to the tissue caused by the implantation of and/or the wearing of the sensor 42.
  • a flexible substrate 50 often increases the patient's comfort and allows a wider range of activities.
  • a flexible substrate 50 is also useful for an in vitro sensor 42, particularly for ease of manufacturing. Suitable materials for a flexible substrate 50 include, for example, non-conducting plastic or polymeric materials and other non-conducting, flexible, deformable materials.
  • thermoplastics such as polycarbonates, polyesters (e.g., MylarTM and polyethylene terephthalate (PET)), polyvinyl chloride (PVC), polyurethanes, poly ethers, polyamides, polyimides, or copolymers of these thermoplastics, such as PETG (glycol-modified polyethylene terephthalate).
  • PET polyethylene terephthalate
  • PVC polyvinyl chloride
  • polyurethanes poly ethers
  • polyamides polyamides
  • polyimides polymer-modified polyethylene terephthalate
  • the sensors 42 are made using a relatively rigid substrate 50 to, for example, provide structural support against bending or breaking.
  • rigid materials that may be used as the substrate 50 include poorly conducting ceramics, such as aluminum oxide and silicon dioxide.
  • an implantable sensor 42 having a rigid substrate may have a sharp point and/or a sharp edge to aid in implantation of a sensor 42 without an additional insertion device.
  • rigid substrates 50 may also be used in sensors for in vitro analyte monitors. It will be appreciated that for many sensors 42 and sensor applications, both rigid and flexible sensors will operate adequately.
  • the flexibility of the sensor 42 may also be controlled and varied along a continuum by changing, for example, the composition and/or thickness of the substrate 50.
  • implantable sensors 42 as well as in vitro sensors which contact a fluid that is returned to a patient's body, should have a substrate 50 which is non-toxic.
  • the substrate 50 is approved by one or more appropriate governmental agencies or private groups for in vivo use.
  • the sensor 42 may include optional features to facilitate insertion of an implantable sensor 42, as shown in Figure 17.
  • the sensor 42 may be pointed at the tip 123 to ease insertion.
  • the sensor 42 may include a barb 125 which assists in anchoring the sensor 42 within the tissue of the patient during operation of the sensor 42.
  • the barb 125 is typically small enough that little damage is caused to the subcutaneous tissue when the sensor 42 is removed for replacement.
  • the substrate 50 in at least some embodiments has uniform dimensions along the entire length of the sensor 42, in other embodiments, the substrate 50 has a distal end 67 and a proximal end 65 with different widths 53, 55, respectively, as illustrated in Figure 2.
  • the distal end 67 of the substrate 50 may have a relatively narrow width 53.
  • the narrow width 53 of the distal end 67 of the substrate 50 may facilitate the implantation of the sensor 42. Often, the narrower the width of the sensor 42, the less pain the patient will feel during implantation of the sensor and afterwards.
  • a distal end 67 of the sensor 42 which is to be implanted into the patient has 12 a width 53 of 2mm or less, preferably 1mm or less, and more preferably 0.5mm or less. If the sensor 42 does not have regions of different widths, then the sensor 42 will typically have an overall width of, for example, 2 mm, 1.5 mm, 1 mm, 0.5 mm, 0.25 mm, or less.
  • wider or narrower sensors may be used. In particular, wider implantable sensors may be used for insertion into veins or arteries or when the movement of the patient is limited, for example, when the patient is confined in bed or in a hospital.
  • the narrow width 53 may reduce the volume of sample needed for an accurate reading.
  • the narrow width 53 of the sensor 42 results in all of the electrodes of the sensor 42 being closely congregated, thereby requiring less sample volume to cover all of the electrodes.
  • the width of an in vitro sensor 42 may vary depending, at least in part, on the volume of sample available to the sensor 42 and the dimensions of the sample chamber in which the sensor 42 is disposed.
  • the proximal end 65 of the sensor 42 may have a width 55 larger than the distal end 67 to facilitate the connection between contact pads 49 of the electrodes and contacts on a control unit. The wider the sensor 42 at this point, the larger the contact pads 49 can be made.
  • the maximum width of the sensor 42 may be constrained so that the sensor 42 remains small for the convenience and comfort of the patient and/or to fit the desired size of the analyte monitor.
  • the proximal end 65 of a subcutaneously implantable sensor 42 such as the sensor 42 illustrated in Figure 1, may have a width 55 ranging from 0.5mm to 15mm, preferably from 1mm to 10mm, and more preferably from 3mm to 7mm.
  • wider or narrower sensors may be used in this and other in vivo and in vitro applications.
  • the thickness of the substrate 50 may be determined by the mechanical properties of the substrate material (e.g., the strength, modulus, and/or flexibility of the material), the desired use of the sensor 42 including stresses on the substrate 50 arising from that use, as well as the depth of any channels or indentations formed in the substrate 50, as discussed below.
  • the substrate 50 of a subcutaneously 13 implantable sensor 42 for continuous or periodic monitoring of the level of an analyte while the patient engages in normal activities has a thickness of 50 to 500 ⁇ m and preferably 100 to 300 ⁇ m.
  • thicker and thinner substrates 50 may be used, particularly in other types of in vivo and in vitro sensors 42.
  • the length of the sensor 42 may have a wide range of values depending on a variety of factors.
  • Factors which influence the length of an implantable sensor 42 may include the depth of implantation into the patient and the ability of the patient to manipulate a small flexible sensor 42 and make connections between the sensor 42 and the sensor control unit 44.
  • a subcutaneously implantable sensor 42 for the analyte monitor illustrated in Figure 1 may have a length ranging from 0.3 to 5 cm, however, longer or shorter sensors may be used.
  • the length of the narrow portion of the sensor 42 e.g., the portion which is subcutaneously inserted into the patient, if the sensor 42 has narrow and wide portions, is typically about 0.25 to 2 cm in length. However, longer and shorter portions may be used. All or only a part of this narrow portion may be subcutaneously implanted into the patient.
  • the lengths of other implantable sensors 42 will vary depending, at least in part, on the portion of the patient into which the sensor 42 is to be implanted or inserted.
  • the length of in vitro sensors may vary over a wide range depending on the particular configuration of the analyte monitoring system and, in particular, the distance between the contacts of the control unit and the sample.
  • At least one conductive trace 52 is formed on the substrate for use in constructing a working electrode 58.
  • other conductive traces 52 may be formed on the substrate 50 for use as electrodes (e.g., additional working electrodes, as well as counter, counter/reference, and/or reference electrodes) and other components, such as a temperature probe.
  • the conductive traces 52 may extend most of the distance along a length 57 of the sensor 50, as illustrated in Figure 2, although this is not necessary. The placement of the conductive traces 52 may depend on the particular configuration of the analyte monitoring system (e.g., the placement of control unit contacts and/or the sample chamber in relation to the sensor 42).
  • the conductive traces typically extend close to the tip of the sensor 42 to minimize the amount of the sensor that must be implanted.
  • the conductive traces 52 may be formed on the substrate 50 by a variety of techniques, including, for example, photolithography, screen printing, or other impact or non-impact printing techniques.
  • the conductive traces 52 may also be formed by carbonizing conductive traces 52 in an organic (e.g., polymeric or plastic) substrate 50 using a laser.
  • Another method for disposing the conductive traces 52 on the substrate 50 includes the formation of recessed channels 54 in one or more surfaces of the substrate 50 and the subsequent filling of these recessed channels 54 with a conductive material 56, as shown in Figure 3A.
  • the recessed channels 54 may be formed by indenting, embossing, or otherwise creating a depression in the surface of the substrate 50.
  • the depth of the channels is typically related to the thickness of the substrate 50. In one embodiment, the channels have depths in the range of about 12.5 to 75 ⁇ m ( 0.5 to 3 mils), and preferably about 25 to 50 ⁇ m (1 to 2 mils).
  • the conductive traces are typically formed using a conductive material 56 such as carbon (e.g., graphite), a conductive polymer, a metal or alloy (e.g., gold or gold alloy), or a metallic compound (e.g., ruthenium dioxide or titanium dioxide).
  • a conductive material 56 such as carbon (e.g., graphite), a conductive polymer, a metal or alloy (e.g., gold or gold alloy), or a metallic compound (e.g., ruthenium dioxide or titanium dioxide).
  • a conductive material 56 such as carbon (e.g., graphite), a conductive polymer, a metal or alloy (e.g., gold or gold alloy), or a metallic compound (e.g., ruthenium dioxide or titanium dioxide).
  • the formation of films of carbon, conductive polymer, metal, alloy, or metallic compound are well-known and include, for example, chemical vapor deposition
  • the conductive material 56 which fills the channels 54 is often formed using a precursor material, such as a conductive ink or paste.
  • the conductive material 56 is deposited on the substrate 50 using methods such as coating, painting, or applying the material using a spreading instrument, such as a coating blade. Excess conductive material between the channels 54 is then removed by, for example, running a blade along the substrate surface.
  • the conductive material 56 is a part of a precursor material, such as a conductive ink, obtainable, for example, from Ercon, Inc. (Wareham, MA), Metech, Inc. (Elverson, PA), E.I. du Pont de Nemours and Co. (Wilmington, DE), Emca-Remex Products (Montgomeryville, PA), or MCA Services (Melbourn, Great Britain).
  • a conductive ink is typically applied as a 15 semiliquid or paste which contains particles of the carbon, metal, alloy, or metallic compound and a solvent or dispersant.
  • the solvent or dispersant evaporates to leave behind a solid mass of conductive material 56.
  • the conductive ink may also contain a binder.
  • the binder may optionally be cured to further bind the conductive material 56 within the channel 54 and/or on the substrate 50. Curing the binder increases the conductivity of the conductive material 56. However, this is typically not necessary as the currents carried by the conductive material 56 within the conductive traces 52 are often relatively low (usually less than 1 ⁇ A and often less than 100 nA).
  • Typical binders include, for example, polyurethane resins, cellulose derivatives, elastomers, and highly fluorinated polymers.
  • elastomers include silicones, polymeric dienes, and acrylonitrile-butadiene-styrene (ABS) resins.
  • ABS acrylonitrile-butadiene-styrene
  • a fluorinated polymer binder is Teflon ® (DuPont, Wilmington, DE). These binders are cured using, for example, heat or light, including ultraviolet (UV) light. The appropriate curing method typically depends on the particular binder which is used.
  • a liquid or semiliquid precursor of the conductive material 56 e.g., a conductive ink
  • the precursor fills the channel 54.
  • the conductive material 56 which remains may lose volume such that the conductive material 56 may or may not continue to fill the channel 54.
  • Preferred conductive materials 56 do not pull away from the substrate 50 as they lose volume, but rather decrease in height within the channel 54. These conductive materials 56 typically adhere well to the substrate 50 and therefore do not pull away from the substrate 50 during evaporation of the solvent or dispersant.
  • Suitable conductive materials 56 either adhere to at least a portion of the substrate 50 and/or contain another additive, such as a binder, which adheres the conductive material 56 to the substrate 50.
  • the conductive material 56 in the channels 54 is non-leachable, and more preferably immobilized on the substrate 50.
  • the conductive material 56 may be formed by multiple applications of a liquid or semiliquid precursor interspersed with removal of the solvent or dispersant. 16
  • the channels 54 are formed using a laser.
  • the laser carbonizes the polymer or plastic material.
  • the carbon formed in this process is used as the conductive material 56.
  • Additional conductive material 56 such as a conductive carbon ink, may be used to supplement the carbon formed by the laser.
  • the conductive traces 52 are formed by pad printing techniques. For example, a film of conductive material is formed either as a continuous film or as a coating layer deposited on a carrier film. This film of conductive material is brought between a print head and the substrate 50. A pattern on the surface of the substrate 50 is made using the print head according to a desired pattern of conductive traces 52. The conductive material is transferred by pressure and/or heat from the film of conductive material to the substrate 50.
  • the conductive material is deposited on the surface of the substrate 50 without forming substantial depressions.
  • the conductive traces 52 are formed by non-impact printing techniques. Such techniques include electrophotography and magnetography. In these processes, an image of the conductive traces 52 is electrically or magnetically formed on a drum. A laser or LED may be used to electrically form an image. A magnetic recording head may be used to magnetically form an image. A toner material (e.g., a conductive material, such as a conductive ink) is then attracted to portions of the drum according to the image. The toner material is then applied to the substrate by contact between the drum and the substrate. For example, the substrate may be rolled over the drum. The toner material may then be dried and/or a binder in the toner material may be cured to adhere the toner material to the substrate.
  • a conductive material such as a conductive ink
  • Another non-impact printing technique includes ejecting droplets of conductive material onto the substrate in a desired pattern. Examples of this technique include ink jet printing and piezo jet printing. An image is sent to the printer which then ejects the conductive material (e.g., a conductive ink) according to the pattern. The printer may provide a continuous stream of conductive material or the printer may eject the conductive material in discrete amounts at the desired points. 17
  • Yet another non-impact printing embodiment of forming the conductive traces includes an ionographic process.
  • a curable, liquid precursor such as a photopolymerizable acrylic resin (e.g., Solimer 7501 from Cubital, Bad Kreuznach, Germany) is deposited over a surface of a substrate 50.
  • a photomask having a positive or negative image of the conductive traces 52 is then used to cure the liquid precursor.
  • Light e.g., visible or ultraviolet light
  • Uncured liquid precursor is removed leaving behind channels 54 in the solid layer. These channels 54 can then be filled with conductive material 56 to form conductive traces 52.
  • Conductive traces 52 can be formed with relatively narrow widths, for example, in the range of 25 to 250 ⁇ m, a d including widths of, for example, 250 ⁇ m, 150 ⁇ m, 100 ⁇ m, 75 ⁇ m, 50 ⁇ m, 25 ⁇ m or less by the methods described above.
  • the conductive traces 52 are separated by distances sufficient to prevent conduction between the conductive traces 52.
  • the edge-to-edge distance between the conductive traces is preferably in the range of 25 to 250 ⁇ m and may be, for example, 150 ⁇ m, 100 ⁇ m, 75 ⁇ m, 50 ⁇ m, or less.
  • the density of the conductive traces 52 on the substrate 50 is preferably in the range of about 150 to 700 ⁇ m/trace and may be as small as 667 ⁇ m/trace or less, 333 ⁇ m/trace or less, or even 167 ⁇ m trace or less.
  • the working electrode 58 and the counter electrode 60 are often made using a conductive material 56, such as carbon.
  • a conductive material 56 such as carbon.
  • Suitable carbon conductive inks are available from Ercon, Inc. (Wareham, MA), Metech, Inc. (Elverson, PA), E.I. du Pont de Nemours and Co. (Wilmington, DE), Emca-Remex Products (Montgomeryville, PA), or MCA Services (Melbourn, Great Britain).
  • the working surface 51 of the working electrode 58 is at least a portion of the conductive trace 52 that is in contact with the analyte- containing fluid (e.g., implanted in the patient or in the sample chamber of an in vitro analyte monitor).
  • the analyte- containing fluid e.g., implanted in the patient or in the sample chamber of an in vitro analyte monitor.
  • the reference electrode 62 and/or counter/reference electrode are typically formed using conductive material 56 that is a suitable reference material, for 18 example silver/silver chloride or a non-leachable redox couple bound to a conductive material, for example, a carbon-bound redox couple.
  • suitable silver/silver chloride conductive inks are available from Ercon, Inc. (Wareham, MA), Metech, Inc.
  • Silver/silver chloride electrodes illustrate a type of reference electrode that involves the reaction of a metal electrode with a constituent of the sample or body fluid, in this case, Cl " .
  • Suitable redox couples for binding to the conductive material of the reference electrode include, for example, redox polymers (e.g., polymers having multiple redox centers.) It is preferred that the reference electrode surface be non-corroding so that an erroneous potential is not measured.
  • Preferred conductive materials include less corrosive metals, such as gold and palladium. Most preferred are non- corrosive materials including non-metallic conductors, such as carbon and conducting polymers.
  • a redox polymer can be adsorbed on or covalently bound to the conductive material of the reference electrode, such as a carbon surface of a conductive trace 52. Non-polymeric redox couples can be similarly bound to carbon or gold surfaces.
  • a variety of methods may be used to immobilize a redox polymer on an electrode surface.
  • One method is adsorptive immobilization. This method is particularly useful for redox polymers with relatively high molecular weights.
  • the molecular weight of a polymer may be increased, for example, by cross-linking.
  • Another method for immobilizing the redox polymer includes the functionalization of the electrode surface and then the chemical bonding, often covalently, of the redox polymer to the functional groups on the electrode surface.
  • This type of immobilization begins with a poly(4-vinylpyridine).
  • the polymer's pyridine rings are, in part, complexed with a reducible/oxidizable species, such as [Os(bpy) 2 Cl] + 2+ where bpy is 2,2'-bipyridine.
  • Part of the pyridine rings are quaternized by reaction with 2-bromoefhylamine.
  • the polymer is then crosslinked, for example, using a diepoxide, such as polyethylene glycol diglycidyl ether. 19
  • Carbon surfaces can be modified for attachment of a redox species or polymer, for example, by electroreduction of a diazonium salt.
  • reduction of a diazonium salt formed upon diazotization of p-aminobenzoic acid modifies a carbon surface with phenylcarboxylic acid functional groups.
  • These functional groups can then be activated by a carbodiimide, such as l-ethyl-3-(3- dimethylaminopropyl)-carbodiimide hydrochloride.
  • the activated functional groups are then bound with a amine-functionalized redox couple, such as the quaternized osmium-containing redox polymer described above or 2-aminoethylferrocene, to form the redox couple.
  • a amine-functionalized redox couple such as the quaternized osmium-containing redox polymer described above or 2-aminoethylferrocene
  • gold can be functionalized by an amine, such as cystamine,.
  • a redox couple such as [Os(bpy) 2 (pyridine-4-carboxylate)Cl] 0 + is activated by 1-ethyl- 3-(3-dimethylaminopropyl)-carbodiimide hydrochloride to form a reactive O- acylisourea which reacts with the gold-bound amine to form an amide.
  • two or more of the conductive traces 52 on the substrate 50 are used to give the patient a mild electrical shock when, for example, the analyte level exceeds a threshold level. This shock may act as a warning or alarm to the patient to initiate some action to restore the appropriate level of the analyte.
  • the mild electrical shock is produced by applying a potential between any two conductive traces 52 that are not otherwise connected by a conductive path.
  • two of the electrodes 58, 60, 62 or one electrode 58, 60, 62 and the temperature probe 66 may be used to provide the mild shock.
  • the working electrode 58 and the reference electrode 62 are not used for this purpose as this may cause some damage to the chemical components on or proximate to the particular electrode (e.g., the sensing layer on the working electrode or the redox couple on the reference electrode).
  • the current used to produce the mild shock is typically 0.1 to 1 mA. Higher or lower currents may be used, although care should be taken to avoid harm to the patient.
  • the potential between the conductive traces is typically 1 to 10 volts. However, higher or lower voltages may be used depending, for example, on the resistance of the conductive traces 52, the distance between the conductive traces 52 and the desired amount of current.
  • potentials at 20 the working electrode 58 and across the temperature probe 66 may be removed to prevent harm to those components caused by unwanted conduction between the working electrode 58 (and/or temperature probe 66, if used) and the conductive traces 52 which provide the mild shock.
  • each of the conductive traces 52 includes a contact pad 49.
  • the contact pad 49 may simply be a portion of the conductive trace 52 that is indistinguishable from the rest of the trace 52 except that the contact pad 49 is brought into contact with the conductive contacts of a control unit (e.g., the sensor control unit 44 of Figure 1). More commonly, however, the contact pad 49 is a region of the conductive trace 52 that has a larger width than other regions of the trace 52 to facilitate a connection with the contacts on the control unit.
  • the contact pads 49 are typically made using the same material as the conductive material 56 of the conductive traces 52. However, this is not necessary. Although metal, alloys, and metallic compounds may be used to form the contact pads 49, in some embodiments, it is desirable to make the contact pads 49 from a carbon or other non-metallic material, such as a conducting polymer. In contrast to metal or alloy contact pads, carbon and other non-metallic contact pads are not easily corroded if the contact pads 49 are in a wet, moist, or humid environment. Metals and alloys may corrode under these conditions, particularly if the contact pads 49 and contacts of the control unit are made using different metals or alloys.
  • One embodiment of the invention includes a sensor 42 having contact pads 49 and a control unit 44 having conductive contacts (not shown). During operation of the sensor 42, the contact pads 49 and conductive contacts are in contact with each other. In this embodiment, either the contact pads 49 or the conductive contacts are made using a non-corroding, conductive material. Such materials 21 include, for example, carbon and conducting polymers. Preferred non-corroding materials include graphite and vitreous carbon. The opposing contact pad or conductive contact is made using carbon, a conducting polymer, a metal, such as gold, palladium, or platinum group metal, or a metallic compound, such as ruthenium dioxide. This configuration of contact pads and conductive contacts typically reduces corrosion.
  • the signal arising due to the corrosion of the contact pads and/or conductive contacts is less than 3% of the signal generated by the sensor when exposed to concentration of analyte in the normal physiological range.
  • the current generated by analyte in a normal physiological range ranges from 3 to 500 nA.
  • Each of the electrodes 58, 60, 62, as well as the two probe leads 68, 70 of the temperature probe 66 (described below), are connected to contact pads 49 as shown in Figures 10 and 11.
  • the contact pads 49 are on the same side of the substrate 50 as the respective electrodes or temperature probe leads to which the contact pads 49 are attached.
  • the conductive traces 52 on at least one side are connected through vias in the substrate to contact pads 49a on the opposite surface of the substrate 50, as shown in Figures 10 and 11.
  • vias through the substrate are used to provide contact pads on both sides of the substrate 50 for each conductive trace 52.
  • the vias connecting the conductive traces 52 with the contact pads 49a can be formed by making holes through the substrate 50 at the appropriate points and then filling the holes with conductive material 56.
  • the sensor 42 includes two working electrodes 22
  • the senor includes one working electrode 58 a, one counter electrode 60, and one reference electrode 62, as shown in Figure 3B. Each of these embodiments is illustrated with all of the electrodes formed on the same side of the substrate 50.
  • one or more of the electrodes may be formed on an opposing side of the substrate 50.
  • the electrodes may be formed using two different types of conductive material 56 (e.g., carbon and silver/silver chloride). Then, at least in some embodiments, only one type of conductive material 56 needs to be applied to each side of the substrate 50, thereby reducing the number of steps in the manufacturing process and/or easing the registration constraints in the process.
  • the working electrode 58 is formed using a carbon-based conductive material 56 and the reference or counter/reference electrode is formed using a silver/silver chloride conductive material 56, then the working electrode and reference or counter/reference electrode may be formed on opposing sides of the substrate 50 for ease of manufacture.
  • two working electrodes 58 and one counter electrode 60 are formed on one side of the substrate 50 and one reference electrode 62 and a temperature probe 66 are formed on an opposing side of the substrate 50, as illustrated in Figure 6.
  • the opposing sides of the tip of this embodiment of the sensor 42 are illustrated in Figures 7 and 8.
  • each working electrode 58 has a sensing layer 64 formed proximate to or on a working surface of the working electrode 58.
  • the sensing layer 64 is formed near or on only a small portion of the working electrode 58, often near a tip 23 of the sensor 42. This limits the amount of material needed to form the sensor 42 and places the sensing layer 64 in the best position for contact with the analyte- containing fluid (e.g., a body fluid, sample fluid, or carrier fluid).
  • the sensing layer 64 includes one or more components designed to facilitate the electrolysis of the analyte.
  • the sensing layer 64 may include, for example, a catalyst to catalyze a reaction of the analyte and produce a response at the working electrode 58, an electron transfer agent to indirectly or directly transfer electrons between the analyte and the working electrode 58, or both.
  • the sensing layer 64 may be formed as a solid composition of the desired components (e.g., an electron transfer agent and/or a catalyst). These components are preferably non-leachable from the sensor 42 and more preferably are immobilized on the sensor 42. For example, the components may be immobilized on a working electrode 58. Alternatively, the components of the sensing layer 64 may be immobilized within or between one or more membranes or films disposed over the working electrode 58 or the components may be immobilized in a polymeric or sol-gel matrix. Examples of immobilized sensing layers are described in U.S. Patents Nos. 5,262,035, 5,264,104, 5,264,105, 5,320,725, 5,593,852, and 5,665,222, U.S. Patent Application No.
  • one or more of the components of the sensing layer 64 may be solvated, dispersed, or suspended in a fluid within the sensing layer 64, instead of forming a solid composition.
  • the fluid may be provided with the sensor 42 or may be absorbed by the sensor 42 from the analyte-containing fluid.
  • the components which are solvated, dispersed, or suspended in this type of sensing layer 64 are non-leachable from the sensing layer.
  • Non-leachability may be accomplished, for example, by providing barriers(e.g., the electrode, substrate, membranes, and/or films) around the sensing layer which prevent the leaching of the components of the sensing layer 64.
  • barriers e.g., the electrode, substrate, membranes, and/or films
  • a barrier is a microporous membrane or film which allows diffusion of the analyte into the sensing layer 64 to make contact with the components of the sensing layer 64, but 24 reduces or eliminates the diffusion of the sensing layer components (e.g., a electron transfer agent and/or a catalyst) out of the sensing layer 64.
  • the sensing layer 64 is deposited on the conductive material 56 of a working electrode 58a, as illustrated in Figures 3A and 3B.
  • the sensing layer 64 may extend beyond the conductive material 56 of the working electrode 58a.
  • the sensing layer 64 may also extend over the counter electrode 60 or reference electrode 62 without degrading the performance of the glucose sensor.
  • a portion of the sensing layer 64 may be formed within the channel 54 if the conductive material 56 does not fill the channel 54.
  • a sensing layer 64 in direct contact with the working electrode 58a may contain an electron transfer agent to transfer electrons directly or indirectly between the analyte and the working electrode, as well as a catalyst to facilitate a reaction of the analyte.
  • a glucose, lactate, or oxygen electrode may be formed having a sensing layer which contains a catalyst, such as glucose oxidase, lactate oxidase, or laccase, respectively, and an electron transfer agent that facilitates the electrooxidation of the glucose, lactate, or oxygen, respectively.
  • the sensing layer 64 is not deposited directly on the working electrode 58 a. Instead, the sensing layer 64 is spaced apart from the working electrode 58a, as illustrated in Figure 4 A, and separated from the working electrode 58a by a separation layer 61.
  • the separation layer 61 typically includes one or more membranes or films. In addition to separating the working electrode 58a from the sensing layer 64, the separation layer 61 may also act as a mass transport limiting layer or an interferent eliminating layer, as described below.
  • a sensing layer 64 which is not in direct contact with the working electrode 58a, includes a catalyst that facilitates a reaction of the analyte.
  • this sensing layer 64 typically does not include an electron transfer agent that transfers electrons directly from the working electrode 58a to the analyte, as the sensing layer 64 is spaced apart from the working electrode 58 a.
  • a glucose or lactate sensor which includes an enzyme (e.g., glucose oxidase or lactate oxidase, respectively) in the sensing layer 64.
  • the 25 glucose or lactate reacts with a second compound (e.g., oxygen) in the presence of the enzyme.
  • the second compound is then electrooxidized or electroreduced at the electrode. Changes in the signal at the electrode indicate changes in the level of the second compound in the fluid and are proportional to changes in glucose or lactate level and, thus, correlate to the analyte level.
  • two sensing layers 63, 64 are used, as shown in Figure 4B.
  • Each of the two sensing layers 63, 64 may be independently formed on the working electrode 58a or in proximity to the working electrode 58a.
  • One sensing layer 64 is typically, although not necessarily, spaced apart from the working electrode 58a.
  • this sensing layer 64 may include a catalyst which catalyzes a reaction of the analyte to form a product compound.
  • the product compound is then electrolyzed in the second sensing layer 63 which may include an electron transfer agent to transfer electrons between the working electrode 58a and the product compound and/or a second catalyst to catalyze a reaction of the product compound to generate a signal at the working electrode 58a.
  • a glucose or lactate sensor may include a first sensing layer 64 which is spaced apart from the working electrode and contains an enzyme, for example, glucose oxidase or lactate oxidase. The reaction of glucose or lactate in the presence of the appropriate enzyme forms hydrogen peroxide.
  • a second sensing layer 63 is provided directly on the working electrode 58a and contains a peroxidase enzyme and an electron transfer agent to generate a signal at the electrode in response to the hydrogen peroxide. The level of hydrogen peroxide indicated by the sensor then correlates to the level of glucose or lactate.
  • Another sensor which operates similarly can be made using a single sensing layer with both the glucose or lactate oxidase and the peroxidase being deposited in the single sensing layer.
  • one or more of the working electrodes 58b do not have a corresponding sensing layer 64, as shown in Figures 3 A and 4A, or have a sensing layer (not shown) which does not contain one or more components (e.g., an 26 electron transfer agent or catalyst) needed to electrolyze the analyte.
  • the signal generated at this working electrode 58b typically arises from interferents and other sources, such as ions, in the fluid, and not in response to the analyte (because the analyte is not electrooxidized or electroreduced).
  • the signal at this working electrode 58b corresponds to a background signal.
  • the background signal can be removed from the analyte signal obtained from other working electrodes 58a that are associated with fully-functional sensing layers 64 by, for example, subtracting the signal at working electrode 58b from the signal at working electrode 58a.
  • Sensors having multiple working electrodes 58a may also be used to obtain more precise results by averaging the signals or measurements generated at these working electrodes 58a. In addition, multiple readings at a single working electrode 58a or at multiple working electrodes may be averaged to obtain more precise data.
  • the sensing layer 64 contains one or more electron transfer agents in contact with the conductive material 56 of the working electrode 58, as shown in Figures 3A and 3B.
  • Other in vitro sensors may utilize a carrier fluid which contains the electron transfer agent. The analyte is transferred to the carrier fluid from the original sample fluid by, for example, osmotic flow through a microporous membrane or the like.
  • the electron transfer agent there is little or no leaching of the electron transfer agent away from the working electrode 58 during the period in which the sensor 42 is implanted in the patient or measuring an in vitro analyte- containing sample.
  • a diffusing or leachable (i.e., releasable) electron transfer agent often diffuses into the analyte-containing fluid, thereby reducing the effectiveness of the electrode by reducing the sensitivity of the sensor over time.
  • a diffusing or leaching electron transfer agent in an implantable sensor 42 may also cause damage to the patient.
  • the electron transfer agent preferably, at least 90%, more preferably, at least 95%, and, most preferably, at least 99%, of the electron transfer agent remains disposed on the sensor after immersion in the analyte-containing fluid 27 for 24 hours, and, more preferably, for 72 hours.
  • the electron transfer agents are bound or otherwise immobilized on the working electrode 58 or between or within one or more membranes or films disposed over the working electrode 58.
  • the electron transfer agent may be immobilized on the working electrode 58 using, for example, a polymeric or sol-gel immobilization technique.
  • the electron transfer agent may be chemically (e.g., ionically, covalently, or coordinatively) bound to the working electrode 58, either directly or indirectly through another molecule, such as a polymer, that is in turn bound to the working electrode 58.
  • the electron transfer agent mediates the transfer of electrons to electrooxidize or electroreduce an analyte and thereby permits a current flow between the working electrode 58 and the counter electrode 60 via the analyte.
  • the mediation of the electron transfer agent facilitates the electrochemical analysis of analytes which are not suited for direct electrochemical reaction on an electrode.
  • the preferred electron transfer agents are electroreducible and electrooxidizable ions or molecules having redox potentials that are a few hundred millivolts above or below the redox potential of the standard calomel electrode (SCE).
  • the electron transfer agents are not more reducing than about - 150 mV and not more oxidizing than about +400 mV versus SCE.
  • the electron transfer agent may be organic, organometallic, or inorganic.
  • organic redox species are quinones and species that in their oxidized state have quinoid structures, such as Nile blue and indophenol.
  • Some quinones and partially oxidized quinhy drones react with functional groups of proteins such as the thiol groups of cysteine, the amine groups of lysine and arginine, and the phenolic groups of tyrosine which may render those redox species unsuitable for some of the sensors of the present invention because of the presence of the interfering proteins in 28 an analyte-containing fluid.
  • substituted quinones and molecules with quinoid structure are less reactive with proteins and are preferred.
  • a preferred tetrasubstituted quinone usually has carbon atoms in positions 1, 2, 3, and 4.
  • electron transfer agents suitable for use in the invention have structures or charges which prevent or substantially reduce the diffusional loss of the electron transfer agent during the period of time that the sample is being analyzed.
  • the preferred electron transfer agents include a redox species bound to a polymer which can in turn be immobilized on the working electrode.
  • the bond between the redox species and the polymer may be covalent, coordinative, or ionic.
  • Useful electron transfer agents and methods for producing them are described in U.S. Patent Nos. 5,264,104; 5,356,786; 5,262,035; and 5,320,725, incorporated herein by reference.
  • the preferred redox species is a transition metal compound or complex.
  • the preferred transition metal compounds or complexes include osmium, ruthenium, iron, and cobalt compounds or complexes. The most preferred are osmium compounds and complexes. It will be recognized that many of the redox species described below may also be used, typically without a polymeric component, as electron transfer agents in a carrier fluid or in a sensing layer of a sensor where leaching of the electron transfer agent is acceptable.
  • Non-releasable polymeric electron transfer agent contains a redox species covalently bound in a polymeric composition.
  • An example of this type of mediator is poly(vinylferrocene).
  • Non-releasable electron transfer agent contains an ionically- bound redox species.
  • this type of mediator includes a charged polymer coupled to an oppositely charged redox species.
  • examples of this type of mediator include a negatively charged polymer such as Nafion ® (DuPont) coupled to a positively charged redox species such as an osmium or ruthenium polypyridyl cation.
  • a positively charged polymer such as quaternized poly(4-vinyl pyridine) or poly(l -vinyl imidazole) coupled to a negatively charged redox species such as ferricyanide or ferrocyanide.
  • the preferred ionically-bound redox species is a highly charged redox species bound within an oppositely charged redox polymer.
  • suitable non-releasable electron transfer agents include a redox species coordinatively bound to a polymer.
  • the mediator may be formed by coordination of an osmium or cobalt 2, 2'- bipyridyl complex to poly(l -vinyl imidazole) or poly (4- vinyl pyridine).
  • the preferred electron transfer agents are osmium transition metal complexes with one or more ligands, each ligand having a nitrogen-containing heterocycle such as 2,2'-bipyridine, 1,10-phenanthroline, or derivatives thereof. Furthermore, the preferred electron transfer agents also have one or more ligands covalently bound in a polymer, each ligand having at least one nitrogen-containing heterocycle, such as pyridine, imidazole, or derivatives thereof. These preferred electron transfer agents exchange electrons rapidly between each other and the working electrodes 58 so that the complex can be rapidly oxidized and reduced.
  • One example of a particularly useful electron transfer agent includes (a) a polymer or copolymer having pyridine or imidazole functional groups and (b) osmium cations complexed with two ligands, each ligand containing 2,2'-bipyridine, 1,10-phenanthroline, or derivatives thereof, the two ligands not necessarily being the same.
  • Preferred derivatives of 2,2'-bipyridine for complexation with the osmium cation are 4,4'-dimethyl-2,2'-bipyridine and mono-, di-, and polyalkoxy-2,2'- bipyridines, such as 4,4'-dimethoxy-2,2'-bipyridine.
  • Preferred derivatives of 1,10- phenanthroline for complexation with the osmium cation are 4,7-dimethyl-l,10- phenanthroline and mono, di-, and polyalkoxy-l,10-phenanthrolines, such as 4,7- dimethoxy- 1 , 10-phenanthroline.
  • Preferred polymers for complexation with the osmium cation include polymers and copolymers of poly(l -vinyl imidazole)
  • poly(l -vinyl imidazole) examples include acrylonitrile, acrylamide, and substituted or quaternized N-vinyl imidazole. Most preferred are electron transfer agents with osmium complexed to a polymer or copolymer of poly(l -vinyl imidazole).
  • the preferred electron transfer agents have a redox potential ranging from - 100 mV to about +150 mV versus the standard calomel electrode (SCE).
  • SCE standard calomel electrode
  • the potential of the electron transfer agent ranges from -100 mV to +150 mV and more preferably, the potential ranges from -50 mV to +50 mV.
  • the most preferred electron transfer agents have osmium redox centers and a redox potential ranging from +50 mV to -150 mV versus SCE.
  • the sensing layer 64 may also include a catalyst which is capable of catalyzing a reaction of the analyte.
  • the catalyst may also, in some embodiments, act as an electron transfer agent.
  • a suitable catalyst is an enzyme which catalyzes a reaction of the analyte.
  • a catalyst such as a glucose oxidase, glucose dehydrogenase (e.g., pyrroloquinoline quinone glucose dehydrogenase (PQQ)), or oligosaccharide dehydrogenase, may be used when the analyte is glucose.
  • a lactate oxidase or lactate dehydrogenase may be used when the analyte is lactate. Laccase may be used when the analyte is oxygen or when oxygen is generated or consumed in response to a reaction of the analyte.
  • the catalyst is non-leachably disposed on the sensor, whether the catalyst is part of a solid sensing layer in the sensor or solvated in a fluid within the sensing layer. More preferably, the catalyst is immobilized within the sensor (e.g., on the electrode and/or within or between a membrane or film) to prevent unwanted leaching of the catalyst away from the working electrode 58 and into the patient.
  • This may be accomplished, for example, by attaching the catalyst to a polymer, cross linking the catalyst with another electron transfer agent (which, as described above, can be polymeric), and/or providing one or more barrier membranes or films with pore sizes smaller than the catalyst.
  • a second catalyst may also be used. This second catalyst is often used to catalyze a reaction of a product compound resulting from the catalyzed reaction of the analyte.
  • the second catalyst typically operates with an electron transfer agent to electrolyze the product compound to generate a signal at the working electrode.
  • the second catalyst may be provided in an interferent-eliminating layer to catalyze reactions that remove interferents, as described below. 31
  • One embodiment of the invention is an electrochemical sensor in which the catalyst is mixed or dispersed in the conductive material 56 which forms the conductive trace 52 of a working electrode 58.
  • This may be accomplished, for example, by mixing a catalyst, such as an enzyme, in a carbon ink and applying the mixture into a channel 54 on the surface of the substrate 50.
  • the catalyst is immobilized in the channel 53 so that it can not leach away from the working electrode 58.
  • This may be accomplished, for example, by curing a binder in the carbon ink using a curing technique appropriate to the binder. Curing techniques include, for example, evaporation of a solvent or dispersant, exposure to ultraviolet light, or exposure to heat.
  • the mixture is applied under conditions that do not substantially degrade the catalyst.
  • the catalyst may be an enzyme that is heat-sensitive.
  • the enzyme and conductive material mixture should be applied and cured, preferably, without sustained periods of heating.
  • the mixture may be cured using evaporation or UV curing techniques or by the exposure to heat that is sufficiently short that the catalyst is not substantially degraded.
  • thermostability of the catalyst Another consideration for in vivo analyte sensors is the thermostability of the catalyst. Many enzymes have only limited stability at biological temperatures. Thus, it may be necessary to use large amounts of the catalyst and/or use a catalyst that is thermostable at the necessary temperature (e.g., 37°C or higher for normal body temperature).
  • a thermostable catalyst may be defined as a catalyst which loses less than 5% of its activity when held at 37°C for at least one hour, preferably, at least one day, and more preferably at least three days.
  • a thermostable catalyst is soybean peroxidase.
  • thermostable catalyst may be used in a glucose or lactate sensor when combined either in the same or separate sensing layers with glucose or lactate oxidase or dehydrogenase.
  • a further description of thermostable catalysts and their use in electrochemical inventions is found in U.S. Patent No. 5,665,222 U.S. Patent Application No. 08/540,789, and PCT Application No. PCT/US98/02403 entitled “Soybean Peroxidase Electrochemical Sensor", filed on February 11, 1998, Attorney Docket No. M&G 12008.8WOI2. 32
  • a potential (versus a reference potential) is applied across the working and counter electrodes 58, 60.
  • the minimum magnitude of the applied potential is often dependent on the particular electron transfer agent, analyte (if the analyte is directly electrolyzed at the electrode), or second compound (if a second compound, such as oxygen or hydrogen peroxide, whose level is dependent on the analyte level, is directly electrolyzed at the electrode).
  • the applied potential usually equals or is more oxidizing or reducing, depending on the desired electrochemical reaction, than the redox potential of the electron transfer agent, analyte, or second compound, whichever is directly electrolyzed at the electrode.
  • the potential at the working electrode is typically large enough to drive the electrochemical reaction to or near completion.
  • the magnitude of the potential may optionally be limited to prevent significant (as determined by the current generated in response to the analyte) electrochemical reaction of interferents, such as urate, ascorbate, and acetaminophen.
  • the limitation of the potential may be obviated if these interferents have been removed in another way, such as by providing an interferent-limiting barrier, as described below, or by including a working electrode 58b (see Figure 3 A) from which a background signal may be obtained.
  • the electrochemical reaction occurs via an electron transfer agent and the optional catalyst.
  • Many analytes B are oxidized (or reduced) to products C by an electron transfer agent species A in the presence of an appropriate catalyst (e.g., an enzyme).
  • the electron transfer agent A is then oxidized (or reduced) at the electrode. Electrons are collected by (or removed from) the electrode and the resulting current is measured. This process is illustrated by reaction equations (1) and (2) (similar equations may be written for the reduction of the analyte B by a redox mediator A in the presence of a catalyst): 33
  • an electrochemical sensor may be based on the reaction of a glucose molecule with two non-leachable ferricyanide anions in the presence of glucose oxidase to produce two non-leachable ferrocyamde anions, two hydrogen ions, and gluconolactone.
  • the amount of glucose present is assayed by electrooxidizing the non-leachable ferrocyanide anions to non-leachable ferricyanide anions and measuring the current.
  • a second compound whose level is affected by the analyte is electrolyzed at the working electrode.
  • the analyte D and the second compound in this case, a reactant compound E, such as oxygen, react in the presence of the catalyst, as shown in reaction equation (3).
  • reaction equation (4) The reactant compound E is then directly oxidized (or reduced) at the working electrode, as shown in reaction equation (4)
  • the reactant compound E is indirectly oxidized (or reduced) using an electron transfer agent H (optionally in the presence of a catalyst), that is subsequently reduced or oxidized at the electrode, as shown in reaction equations (5) and (6).
  • changes in the concentration of the reactant compound, as indicated by the signal at the working electrode correspond inversely to changes in the analyte (i.e., as the level of analyte increase then the level of reactant compound and the signal at the electrode decreases.)
  • the relevant second compound is a product compound
  • the product compound F is formed by the catalyzed reaction of analyte D and then be directly electrolyzed at the electrode or indirectly electrolyzed using an electron transfer agent and, optionally, a catalyst.
  • the signal arising from the direct or indirect electrolysis of the product compound F at the working electrode corresponds directly to the level of the analyte (unless there are other sources of the product compound). As the level of analyte increases, the level of the product compound and signal at the working electrode increases.
  • reaction equations (1) through (6) illustrate non-limiting examples of such reactions.
  • Temperature Probe A variety of optional items may be included in the sensor.
  • One optional item is a temperature probe 66 ( Figures 8 and 11).
  • the temperature probe 66 may be made using a variety of known designs and materials.
  • One exemplary temperature probe 66 is formed using two probe leads 68, 70 connected to each other through a temperature-dependent element 72 that is formed using a material with a temperature-dependent characteristic.
  • An example of a suitable temperature- dependent characteristic is the resistance of the temperature-dependent element 72.
  • the two probe leads 68, 70 are typically formed using a metal, an alloy, a semimetal, such as graphite, a degenerate or highly doped semiconductor, or a small- band gap semiconductor.
  • suitable materials include gold, silver, ruthenium oxide, titanium nitride, titanium dioxide, indium doped tin oxide, tin doped indium oxide, or graphite.
  • the temperature-dependent element 72 is typically made using a fine trace (e.g., a conductive trace that has a smaller cross-section than 35 that of the probe leads 68, 70) of the same conductive material as the probe leads, or another material such as a carbon ink, a carbon fiber, or platinum, which has a temperature-dependent characteristic, such as resistance, that provides a temperature-dependent signal when a voltage source is attached to the two probe leads 68, 70 of the temperature probe 66.
  • the temperature-dependent characteristic of the temperature-dependent element 72 may either increase or decrease with temperature.
  • the temperature dependence of the characteristic of the temperature-dependent element 72 is approximately linear with temperature over the expected range of biological temperatures (about 25 to 45 °C), although this is not required.
  • a signal (e.g., a current) having an amplitude or other property that is a function of the temperature can be obtained by providing a potential across the two probe leads 68, 70 of the temperature probe 66.
  • the signal from the temperature probe 66 (e.g., the amount of current flowing through the probe) may be combined with the signal obtained from the working electrode 58 by, for example, scaling the temperature probe signal and then adding or subtracting the scaled temperature probe signal from the signal at the working electrode 58. In this manner, the temperature probe 66 can provide a temperature adjustment for the output from the working electrode 58 to offset the temperature dependence of the working electrode 58.
  • the temperature probe includes probe leads 68, 70 formed as two spaced-apart channels with a temperature-dependent element 72 formed as a cross-channel connecting the two spaced-apart channels, as illustrated in Figure 8.
  • the two spaced-apart channels contain a conductive material, such as a metal, alloy, semimetal, degenerate semiconductor, or metallic compound.
  • the cross-channel may contain the same material (provided the cross-channel has a smaller cross-section than the two spaced-apart channels) as the probe leads 68, 70. In other embodiments, the material in the cross-channel is different than the material of the probe leads 68, 70. 36
  • One exemplary method for forming this particular temperature probe includes forming the two spaced-apart channels and then filling them with the metallic or alloyed conductive material. Next, the cross-channel is formed and then filled with the desired material. The material in the cross-channel overlaps with the conductive material in each of the two spaced-apart channels to form an electrical connection.
  • the temperature-dependent element 72 of the temperature probe 66 can not be shorted by conductive material formed between the two probe leads 68, 70.
  • a covering may be provided over the temperature-dependent element 72, and preferably over the portion of the probe leads 68, 70 that is implanted in the patient.
  • the covering may be, for example, a non-conducting film disposed over the temperature-dependent element 72 and probe leads 68, 70 to prevent the ionic conduction.
  • Suitable non-conducting films include, for example, KaptonTM polyimide films (DuPont, Wilmington, DE).
  • Another method for eliminating or reducing conduction by ionic species in the body or sample fluid is to use an ac voltage source connected to the probe leads 68, 70. In this way, the positive and negative ionic species are alternately attracted and repelled during each half cycle of the ac voltage. This results in no net attraction of the ions in the body or sample fluid to the temperature probe 66. The maximum amplitude of the ac current through the temperature-dependent element 72 may then be used to correct the measurements from the working electrodes 58.
  • the temperature probe can be placed on the same substrate as the electrodes. Alternatively, a temperature probe may be placed on a separate substrate. In addition, the temperature probe may be used by itself or in conjunction with other devices.
  • An optional film layer 75 is formed over at least that portion of the sensor 42 which is subcutaneously inserted into the patient, as shown in Figure 9.
  • This optional film layer 74 may serve one or more functions.
  • the film layer 74 prevents 37 the penetration of large biomolecules into the electrodes. This is accomplished by using a film layer 74 having a pore size that is smaller than the biomolecules that are to be excluded.
  • Such biomolecules may foul the electrodes and/or the sensing layer 64 thereby reducing the effectiveness of the sensor 42 and altering the expected signal amplitude for a given analyte concentration.
  • the fouling of the working electrodes 58 may also decrease the effective life of the sensor 42.
  • the biocompatible layer 74 may also prevent protein adhesion to the sensor 42, formation of blood clots, and other undesirable interactions between the sensor 42 and body.
  • the sensor may be completely or partially coated on its exterior with a biocompatible coating.
  • a preferred biocompatible coating is a hydrogel which contains at least 20 wt.% fluid when in equilibrium with the analyte- containing fluid. Examples of suitable hydrogels are described in U.S. Patent No. 5, 593, 852, incorporated herein by reference, and include crosslinked polyethylene oxides, such as polyethylene oxide tetraacrylate.
  • An interferent-eliminating layer may be included in the sensor 42.
  • the interferent-eliminating layer may be incorporated in the biocompatible layer 75 or in the mass transport limiting layer 74 (described below) or may be a separate layer.
  • Interferents are molecules or other species that are electroreduced or electrooxidized at the electrode, either directly or via an electron transfer agent, to produce a false signal.
  • a film or membrane prevents the penetration of one or more interferents into the region around the working electrodes 58.
  • this type of interferent-eliminating layer is much less permeable to one or more of the interferents than to the analyte.
  • the interferent-eliminating layer may include ionic components, such as Nafion®, incorporated into a polymeric matrix to reduce the permeability of the interferent-eliminating layer to ionic interferents having the same charge as the ionic components.
  • ionic components such as Nafion®
  • negatively charged compounds or compounds that form negative ions may be incorporated in the interferent-eliminating layer to reduce the permeation of negative species in the body or sample fluid.
  • an interferent-eliminating layer includes a catalyst for catalyzing a reaction which removes interferents.
  • a catalyst for catalyzing a reaction which removes interferents.
  • One example of such a catalyst is a peroxidase. Hydrogen peroxide reacts with interferents, such as acetaminophen, urate, and ascorbate. The hydrogen peroxide may be added to the analyte-containing fluid or may be generated in situ, by, for example, the reaction of glucose or lactate in the presence of glucose oxidase or lactate oxidase, respectively.
  • interferent eliminating layers include a peroxidase enzyme crosslinked (a) using gluteraldehyde as a crosslinking agent or (b) oxidation of oligosaccharide groups in the peroxidase glycoenzyme with NaIO 4 , followed by coupling of the aldehydes formed to hydrazide groups in a polyacrylamide matrix to form hydrazones are describe in U.S. Patents Nos. 5,262,305 and 5,356,786, incorporated herein by reference.
  • Mass Transport Limiting Layer A mass transport limiting layer 74 may be included with the sensor to act as a diffusion-limiting barrier to reduce the rate of mass transport of the analyte, for example, glucose or lactate, into the region around the working electrodes 58.
  • the steady state concentration of the analyte in the proximity of the working electrode 58 (which is proportional to the concentration of the analyte in the body or sample fluid) can be reduced. This extends the upper range of analyte concentrations that can still be accurately measured and may also expand the range in which the current increases approximately linearly with the level of the analyte.
  • the permeability of the analyte through the film layer 74 vary little or not at all with temperature, so as to reduce or eliminate the variation of current with temperature. For this reason, it is preferred that in the biologically relevant temperature range from about 25°C to about 45°C, and most importantly from 30°C to 40°C, neither the size of the pores in the film nor its hydration or swelling change excessively.
  • the mass transport limiting layer is made using a film that absorbs less than 5 wt.% of fluid over 24 hours. This may reduce or obviate any need for a temperature probe.
  • the mass transport limiting layer is made using a film that absorbs less than 5 wt.% of fluid over 24 hours at 37°C.
  • Particularly useful materials for the film layer 74 are membranes that do not swell in the analyte-containing fluid that the sensor tests.
  • Suitable membranes include 3 to 20,000 nm diameter pores.
  • Membranes having 5 to 500 nm diameter pores with well-defined, uniform pore sizes and high aspect ratios are preferred.
  • the aspect ratio of the pores is preferably two or greater and more preferably five or greater.
  • Well-defined and uniform pores can be made by track etching a polymeric membrane using accelerated electrons, ions, or particles emitted by radioactive nuclei.
  • Most preferred are anisotropic, polymeric, track etched membranes that expand less in the direction perpendicular to the pores than in the direction of the pores when heated.
  • Suitable polymeric membranes included polycarbonate membranes from Poretics (Livermore, CA, catalog number 19401, 0.01 ⁇ m pore size polycarbonate membrane) and Corning Costar Corp. (Cambridge, MA,
  • the permeability of the mass transport limiting membrane changes no more than 4%, preferably, no more than 3%, and, more preferably, no more than 2%, per °C in the range from 30°C to 40°C when the membranes resides in the subcutaneous interstitial fluid.
  • the mass transport limiting layer 74 may also limit the flow of oxygen into the sensor 42. This can improve the stability of sensors 42 that are used in situations where variation in the partial pressure of oxygen causes non-linearity in sensor response.
  • the mass transport limiting layer 74 restricts oxygen transport by at least 40%, preferably at least 60%, and more preferably at least 80%, than the membrane restricts transport of the analyte.
  • films having a greater density e.g., a density closer to that of the crystalline polymer
  • Polyesters such as polyethylene terephthalate, are typically less permeable to oxygen and are, therefore, preferred over polycarbonate membranes. 40
  • An implantable sensor may also, optionally, have an anticlotting agent disposed on a portion the substrate which is implanted into a patient.
  • This anticlotting agent may reduce or eliminate the clotting of blood or other body fluid around the sensor, particularly after insertion of the sensor. Blood clots may foul the sensor or irreproducibly reduce the amount of analyte which diffuses into the sensor.
  • useful anticlotting agents include heparin and tissue plasminogen activator (TPA), as well as other known anticlotting agents.
  • the anticlotting agent may be applied to at least a portion of that part of the sensor 42 that is to be implanted.
  • the anticlotting agent may be applied, for example, by bath, spraying, brushing, or dipping.
  • the anticlotting agent is allowed to dry on the sensor 42.
  • the anticlotting agent may be immobilized on the surface of the sensor or it may be allowed to diffuse away from the sensor surface.
  • the quantities of anticlotting agent disposed on the sensor are far below the amounts typically used for treatment of medical conditions involving blood clots and, therefore, have only a limited, localized effect.
  • the sensor 42 may be designed to be a replaceable component in an in vivo or in vitro analyte monitor, and particularly in an implantable analyte monitor.
  • the senor 42 is capable of operation over a period of days.
  • the period of operation is at least one day, more preferably at least three days, and most preferably at least one week.
  • the sensor 42 can then be removed and replaced with a new sensor.
  • the lifetime of the sensor 42 may be reduced by the fouling of the electrodes or by the leaching of the electron transfer agent or catalyst.
  • the temperature stability of the catalyst is Another primary limitation on the lifetime of the sensor 42 .
  • Many catalysts are enzymes, which are very sensitive to the ambient temperature and may degrade at temperatures of the patient's body (e.g., approximately 37°C for the human body). Thus, robust enzymes should be used 41 where available.
  • the sensor 42 should be replaced when a sufficient amount of the enzyme has been deactivated to introduce an unacceptable amount of error in the measurements.
  • FIG 12 is a schematic illustration of an exemplary system 200, in accordance with the principles of the present invention, for manufacturing the sensor 42.
  • the system 200 utilizes a continuous film or substrate web 202 that is guided along a serpentine pathway by a series of rollers 206.
  • the web 202 is processed at the various processing stations or zones. For example, at one station channels can be formed in the web 202.
  • conductive material can be placed in the channels, sensor chemistry can be deposited over portions of the conductive material corresponding with working electrodes, and a protective film or micro-porous membrane can be affixed to the web 202.
  • the sensor 42 can be cut, stamped or otherwise removed from the continuous web 202. A more detailed description of the various steps is provided in the following paragraphs.
  • the continuous substrate web 202 ultimately forms the substrate 50 of the sensor 42. Consequently, for certain applications, the web 202 is made of nonconducting plastic or polymeric materials such as those previously identified in the specification with respect to the substrate 50.
  • the web 202 comprises a continuous plastic or polymeric film having a thickness in the range of 50 to 500 ⁇ m (2-20 mil), and preferably in the range of 100 to 300 ⁇ m (4-12 mil).
  • the heater 204 includes two heated platens arranged and configured to allow the web 202 to pass between parallel heated surfaces at a predetermined feed rate and distance.
  • the web 202 is heated to a sufficient temperature, for example, to a glass transition temperature of the substrate web 202 to soften the web 202 in preparation for subsequent embossing or stamping steps. 42
  • the heating step it will be appreciated that certain web materials may have sufficient deformability to allow channels to be pressed therein without requiring a heating step. Similarly, if no channels are desired to be formed in the web 202, or channels are to be formed through non-mechanical techniques such as laser or chemical etching, the initial heating step can also be eliminated from the process. Furthermore, if it is desired to soften the web 202 via heat, it will be appreciated that any number of known heating sources/configurations, such as radiant or convection heaters, can be utilized. Alternatively, the forming tool may be heated and not the web. After the web 202 has been heated to a desired temperature by the heater
  • the web 202 is preferably conveyed to a channel formation station/zone 205 where the channels 54 are preferably mechanically pressed into the web 202 by a continuous embossing process.
  • the channels 54 of the sensor 42 are formed in the web 202 by pressing the web 202 between a flat roller 207 and an embossing roller 208 having a desired embossing pattern formed on its outer surface. As the web 202 passes between the rollers 207 and 208, a desired channel pattern is stamped, embossed, formed or otherwise pressed into one side of the web 202.
  • an outline or planform of the sensor 42 can optionally be pressed into the web 202 to generate perforations that extend partially through the web 202.
  • the web 202 is perforated to a depth of about 70% of the thickness of the web 202.
  • about 70%) of the perimeter of the planform is completely perforated. Perforating the web 202 facilitates subsequently removing the sensor 42 and provides the advantage of lessening registration constraints at later stages of the manufacturing process.
  • Figure 15 A is a cross-sectional view taken through the web 202 immediately after the sensor channels 54 have been formed within the web 202.
  • the channels 54 are generally uniformly spaced across the width of the web 202 and have generally rectangular cross-sectional profiles.
  • the width of the channels may be in the range of about 25 to about 250 ⁇ m.
  • the channels have individual widths of 250 ⁇ m (about 8 mils), 150 ⁇ m, 100 ⁇ m, 75 ⁇ m, 50 ⁇ m, 25 ⁇ m or less.
  • the depth of the 43 channels is typically related to the thickness of the web 202.
  • the channels have depths in the range of about 12.5 to 75 ⁇ m (0.5 to 3 mils), and preferably about 25 to 50 ⁇ m (1 to 2 mils).
  • the distance between the conductive traces may be in the range of about 25 to 150 ⁇ m , and may be, for example, 150 ⁇ m, 100 ⁇ m, 75 ⁇ m, 50 ⁇ m, or less.
  • the density of the conductive traces 52 on the substrate 50 may be in the range of about 150 to 700 ⁇ m and may be as small as 667 ⁇ m/trace or less, 333 ⁇ m/trace or less, or even 167 ⁇ m/trace or less.
  • embossing rollers suitable for use with the present invention can be designed to form a wide range of different channel patterns.
  • Figure 13 provides a perspective view of one embossing roller 208 that is adapted for forming the channel configuration of the sensor 42.
  • the embossing stamp or roller 208 includes a pattern of raised members or portions 210 that project radially outward from the outer surface of the roller 208.
  • the raised portions 210 extend about the circumference of the roller 208 and are arranged in a configuration that corresponds to the desired channel configuration shown in Figure 2.
  • the raised portions 210 include generally parallel, relatively closely spaced raised lines 211 corresponding to the channel pattern desired to be formed along the narrow portion 65 of the sensor 42.
  • the raised portions 210 also include angled or diverging/converging raised lines 213 corresponding to the channel pattern desired to be formed along the wider portion 67 of the sensor 42.
  • the raised lines 211 and 213 have widths less than about 150 microns, preferably less than about 100 microns, and most preferably less than about 50 microns.
  • the raised portions 210 further include tabs or punch members 215 adapted for forming contact pad depressions in which conductive material can be disposed to form the contact pads 49 of the sensor 42.
  • the raised portions 210 project or extend into the web 202 causing the web 202 to deform or indent such that the channels 54 and contact pad depressions are formed within the web 202.
  • the raised portions 210 of the roller 208 form a pattern of depressions in the web 202 that includes such features as the channels 54 and the contact pad depressions. 44
  • a single embossing pattern is disposed on the outer surface of the roller 208.
  • multiple identical patterns can be arranged about the circumference of the roller.
  • multiple different patterns can be arranged about the circumference of the roller to allow different sensor configurations to be manufactured with a single embossing roller.
  • the alternative roller 208' includes a plurality of raised annular rings 210' that extend about the circumference of the roller 208'. Each ring 210' can extend continuously about the entire circumference of the roller 208', or can be separated into discrete segments by gaps located at predetermined intervals about the roller 208'.
  • the roller 208' is adapted to form a plurality of substantially parallel, straight channels in the web 202.
  • One use of such a roller 208' relates to the manufacture of sensors having substantially constant widths.
  • embossing tools suitable for use with the present invention such as rollers, presses or stamps, can be manufactured using a variety of techniques. For example, such tools can be molded, formed or cast using conventional techniques. Exemplary materials for making such embossing tools include steel and other metals, minerals such as sapphire and silicon, epoxides, ceramics, and appropriate polymers.
  • silicon is used to make an embossing tool such as an embossing roller or stamp.
  • an embossing tool such as an embossing roller or stamp.
  • a desired pattern of raised portions is formed on the embossing surface of the tool using photolithographic and etching techniques to remove selected portions of the tool. It has been determined that such a process can yield an embossing tool having a desirable surface finish, precisely shaped features at small sizes, no burrs, and sharp features (e.g., small radii between intersecting features).
  • Silicon is preferred for a flat (non-cylindrical) tool, and may be etched using techniques common to the integrated circuit industry to create profiles in the wafer surface. Such profiles may be either positive in relief above the surface or negative below the wafer surface. Positive profiles may be used directly as tools to create indentations in a softer substrate. Negative profiles may be used as a master to 45 create a series of second generation positives that are used as the final tool.
  • the second generation positives may be made from any castable material with the appropriate mechanical properties.
  • the web 202 is conveyed to a channel filling station/zone 210 where conductive material is placed, flowed, applied, filled, flooded or otherwise disposed within the channels 54.
  • the conductive material can be applied as a precursor conductive material having a liquid form.
  • An exemplary precursor conductive material includes conductive material dissolved or suspended in a solvent or dispersant.
  • a preferred precursor conductive material is a carbon based ink that can be flooded in liquid form into the channels 54.
  • Other conductive inks or pastes that include carbon or metal, such as, for example, gold, copper, or silver, may be used.
  • Other techniques for applying the conductive material or precursor conductive material include spraying, coating, flooding, applying with a saturated roller, pumping, as well as electrostatic, ionographic, magnetographic, and other impact and non-impact printing methods.
  • the web 202 is preferably passed through an arrangement/device for scraping or wiping excess conductive material/precursor conductive material from the surface of the web 202.
  • a coating blade 212 and roller 214 are used to remove excess material from the web 202.
  • the conductive material/precursor conductive material substantially fills the channels 54 such that the web and conductive material/precursor conductive material together form a substantially flat or planar surface.
  • Figure 15B shows a cross section through the web 202 after the excess conductive material/precursor conductive material has been wiped from the web 202. While it is preferred for the channels 54 to be substantially filled with the conductive material/precursor conductive material, it will be appreciated that in certain embodiments it may be desirable to only partially fill the channels 54, or to 46 slightly overfill the channels 54 with conductive material/precursor conductive material.
  • a single series of channel forming, filling and wiping steps are used to fill the channels 54. It will be appreciated that in alternative embodiments, multiple channel formation, filling and wiping steps can be utilized to fill channels formed in the substrate 50. For example, to manufacture the sensor
  • the reference electrode channel could initially be formed in the substrate, and then filled with a suitable conductive material such as silver/silver chloride. Subsequently, the working electrode channels of the sensor 42 could be formed in the substrate and filled with a conductive material such as carbon. Separating the various channel formation, filling and wiping steps can assist in inhibiting cross contamination of conductive materials between the various electrodes.
  • a suitable conductive material such as silver/silver chloride.
  • the working electrode channels of the sensor 42 could be formed in the substrate and filled with a conductive material such as carbon.
  • the channels can be formed by removing or carbonizing a portion of the substrate 50 or web 202 using a laser, or photolithographic patterning and etching of the substrate 50 or web 202.
  • channels may not be formed in the substrate 50 or web 202 at all.
  • the conductive traces 52 can be formed on the substrate 50 by a variety of techniques, including photolithography, screen printing, other printing techniques, stamping traces into the substrate or web 202, or using a laser to micro-machine traces into the substrate 50 or web 202.
  • Another method for forming the conductive traces uses techniques common to pad printing or hot stamping methods, whereby a film of conductive material is formed, for example, as a continuous sheet or as a coating layer deposited on a 47 carrier film.
  • the film of conductive material is brought between a print head and the substrate 500.
  • a pattern of conductive traces 52 is formed on the substrate 50 using the print head.
  • the conductive material is transferred by pressure and/or heat from the conductive film to the substrate 50.
  • This technique may produce channels (e.g., depressions caused by impact of the print head on the substrate 50).
  • the conductive material is deposited directly without forming substantial depressions in the surface of the substrate 50.
  • the conductive traces 52 are formed by non-impact printing techniques. These methods do not require the formation of channels in the substrate. Instead, conductive traces may be formed directly on a planer substrate. Such techniques include electrophotography and magnetography. In these processes, an image of the conductive traces 52 is electrically or magnetically formed on a drum. A laser or LED may be used to electrically form the image or a magnetic recording head may be used to magnetically form the image. A toner material (e.g., a conductive material, such as a conductive ink) is then attracted to portions of the drum according to the image. The toner material is then applied to the substrate by contact between the drum and the substrate. For example, the substrate may be rolled over the drum. The toner material may then be dried and/or a binder in the toner material may be cured to adhere the toner material to the substrate.
  • non-impact printing techniques do not require the formation of channels in the substrate. Instead, conductive traces may be formed directly on a planer substrate. Such techniques include electrophoto
  • Another non-impact printing technique includes ejecting droplets of conductive material onto the substrate in a desired pattern. Examples of this technique include ink jet printing and piezo jet printing. An image is sent to the printer which then ejects the conductive material (e.g., a conductive ink) according to the pattern. The printer may provide a continuous stream of conductive material or the printer may eject the conductive material in discrete amounts at the desired points.
  • conductive material e.g., a conductive ink
  • a curable, liquid precursor such as a photopolymerizable acrylic resin (e.g., Solimer 7501 from Cubital, Bad Kreuznach, Germany)
  • a photomask having a positive or negative image of the conductive traces 52 is then used to cure the liquid 48 precursor.
  • Light e.g., visible or ultraviolet light
  • Uncured liquid precursor is removed leaving behind channels 54 in the solid layer. These channels 54 can then be filled with conductive material 56 to form conductive traces 52.
  • the web 202 is moved through a drying chamber 216.
  • the drying chamber 216 preferably provides sufficient heat to drive off or evaporate solvents or dispersants that may be contained in precursor conductive material within the channels 54. After heating, conductive material is preferably left as a residue in the channels 54. In certain cases, the drying chamber 216 exposes the web 202 to sufficient temperatures to cure optional binders that may be present with the conductive material. It will be appreciated that ultraviolet light could also be used to cure optional binders interspersed with the conductive material.
  • FIG. 15C is a cross-sectional view cut through the web 202 after the sensor chemistry has been deposited on the web 202.
  • sensor chemistry is only deposited over the conductive material corresponding to the working electrodes 58, which in one embodiment, as illustrate in Figure 4A, are formed at the two outer channels 54. Consequently, a relatively precise application technique is preferably used to inhibit sensor chemistry from being applied to both the working electrodes 58 and electrodes that should not be coated. It is acceptable, in some situations, for the sensing layer to also coat the counter electrode 60.
  • piezo jet technology or the like is used to deposit the chemistry upon the web 202 to form the sensing layers 64.
  • a solenoid valve can be rapidly shuttered and when supplied with liquid under a precisely controlled over-pressure condition, a droplet of controlled size will be ejected from the valve. Resolutions to 500 picoliters can be achieved. Conventional ink jet printers can also be used.
  • the surface of the web 202 can optionally be roughened by techniques such as abrasion or plasma treatment prior to applying the sensor chemistry .
  • abrasion or plasma treatment for example, by pre-treating the surface of the web 202, for example, by a corona discharge, free radicals are generated on the web surface to enhance adhesion of the sensor chemistry to the web 202 and working electrodes 58.
  • the web 202 is preferably conveyed through another heating chamber 220.
  • the heating chamber 220 preferably provides sufficient temperature/heating to release solvents from the deposited sensor chemistry.
  • the heating chamber 220 can also heat the web 202 to sufficient temperatures to cause potential polymerization reactions such as cross link reactions between polymers and the redox mediator and/or redox enzyme.
  • the substrate web 202 Upon exiting the heating station 220, the substrate web 202 is brought into alignment with a membrane web 222 adapted for forming a membrane layer, that may include one or more individual membranes, such as a mass transport limiting layer 74 or a biocompatible layer 75, over at least some portions of the electrodes.
  • the membrane layer may be applied to only one or two or more surfaces of the substrate.
  • solvents such as methyl ethyl ketone and acetone can be applied, for example, sprayed, on the web 202 to soften the web 202 and solvent bond it to the membrane web 222.
  • the two webs 202 and 222 can be bonded together such that the web 222 covers and protects portions of the sensor adapted to be implanted.
  • the two webs 202 and 222 can be bonded or fused together at a welding station 224 such as a sonic or laser welding station.
  • individual membrane webs 222 are bonded to two or more surfaces of the web 202.
  • the membrane layer may include one or membranes that individually or in combination serve a number of functions. These include protection of the electrode surface, prevention of leaching of components in the sensing layer, mass transport limitation of the analyte, exclusion of interfering substances, reduction or enhancement of oxygen mass transport, and/or biocompatibility.
  • a membrane is selected which has mass transport limiting pores that do not change appreciably in size over a physiologically relevant temperature range
  • the laminated webs 202 and 222 enter a cutting station/zone 226 in which the sensor 42 planform, as shown in Figure 2, is cut from the continuous webs 202 and 222.
  • the cutting station 226 can include a die stamper, embosser, embossing roller, laser cutter or any other mechanism for cutting, pressing or otherwise removing the sensors 42 from the webs 202 and 204.
  • This cutting step may result in discrete sensor components or the sensors may be partially cut out and retained on the webs for secondary operations such as surface mounting of electronic components or packaging.
  • a take-up reel 230 accumulates the web material remaining after the sensors 42 have been cut from the web.
  • FIG 16 is a schematic illustration of an exemplary system 300, in accordance with the principles of the present invention, for manufacturing the sensor 42 of Figures 6-8 and 10-11.
  • the system 300 utilizes a continuous film or web 302 that is guided along a serpentine pathway by a series of rollers 305. To provide channels on opposite sides of the web 302, the system utilizes a series of embossing steps.
  • the system 300 includes a first embossing roller 308 configured 51 for forming the channels for the working and counter electrode 58, 60, respectively, in a first side of the web 302, a second embossing roller 310 configured for forming the channel for the temperature probe/sensor 66 and the reference electrode 62 in a second opposite side of the web 302, and a third embossing roller 312 configured for forming the channel for the temperature-dependent element 72 extending between the channels for the two temperature probe leads 68, 70.
  • opposing embossing rollers are used to emboss both sides simultaneously in a single step.
  • the web 302 is first pulled from a spool or reel 301 and preferably heated.
  • the channels for the working electrode and counter electrodes 58, 60 are formed in the first side of the web 302 by the first embossing roller 308.
  • the first embossing roller 308 preferably includes a pattern of raised portions having a configuration that corresponds to the channel configuration depicted in Figure 7.
  • the channels of the working and counter electrodes 58, 60 are filled with conductive material/precursor conductive material, such as a flowable conductive carbon ink, at a first channel filling station 314.
  • the second embossing roller 310 preferably includes a pattern of raised portions having a configuration that corresponds to the channel configuration depicted in Figure 8 (except for channel for the temperature-dependent element 72). It will also be appreciated that the embossing roller 310 can be equipped with projections or punch members for forming vias through the web 302 at desired pad 49 locations of the sensor 42.
  • channels for the temperature probe leads 68, 70 and reference electrode 72 have been formed in the web 202, such channels are filled with suitable 52 conductive material/precursor conductive material at a second channel filling station 318 and excess conductive material/precursor conductive material is wiped from the web 302 at wiping mechanism 320. While one filling station 318 is shown for filling both channels for the temperature probe leads 68, 70 and the reference electrode 62, it will be appreciated that the filling station 318 may include multiple separate filling steps for individually or separately filling each channel.
  • the channel for the temperature-dependent element 72 of the temperature probe 66 is formed between the channels for the temperature probe leads 68, 70 by the third embossing roller 312. Subsequently, the channel for the temperature- dependent element 72 is filled with appropriate material at channel filling station 322, and excess material is wiped from the web 302 by wiping mechanism 324.
  • sensor chemistry is applied to the working electrodes 58 at a sensor chemical application station 326. The sensor chemistry can be applied at the sensor chemical application station 326 by a variety of techniques.
  • Exemplary techniques include piezo jet printing, ink jet printing, spraying, flowing the sensor chemistry onto the electrodes, coating chemistry on the electrodes, or any other technique suitable for applying chemistry to a relatively precise location.
  • the working electrodes 58 optionally have ends that are staggered with respect to the end of the counter electrode 60. Such a configuration assists in inhibiting the sensor chemistry from unintentionally being applied to the counter electrode 60.
  • a protective membrane web 328 is then bought into contact with the substrate web 302 such that at least portions of the working and counter electrodes 58 and 60 are covered by the membrane 328.
  • the protective membrane 328 and the substrate web 302 are bonded or fused together by techniques such as solvent bonding, adhesive bonding, laser bonding, laser welding, and/or sonic welding.
  • solvent bonding the solvent is applied before the protective membrane is brought into contact with the substrate web.
  • a second membrane may optionally be laminated onto the 53 opposing side of the substrate web to protect the reference electrode and temperature probe.
  • the resulting laminate structure that exits the membrane bonding station 330 is conveyed to a cutting station 332 in which individual discrete planforms of the sensor 42" are cut, pressed, stamped or otherwise separated from the continuous web 302.
  • Figure 16 is strictly exemplary and that variations can be made in the number of steps and the sequence of steps without departing from the principles of the present invention.
  • various heating or energy dispersive stations can be placed at locations along the web pathway to heat the web 302 for such purposes as plasticizing the substrate web 302 prior to embossing, curing binders contained within conductive material deposited within the channels of the sensors, and evaporating solvents or dispersants.
  • Figures 12 and 16 each relate to continuous web processes, it will be appreciated that the present invention is not limited to continuous web processes.
  • the various process steps disclosed herein can be performed with respect to discrete or individual sensors completely separate from a web.
  • Sheet fed processing may also be employed as an alternative to a continuous web. Moreover, while in certain embodiments of the present invention the web can be moved continuously through various processing steps at a substantially constant speed, in other embodiments the web can be intermittently stopped and started, or the speed of the web can be varied.
  • the process of the invention for the manufacture of sensors is rapid and efficient. The process of the invention can produce approximately 5000 conductive traces per hour. Within batch variation of the sensors will be less than between batch variation, thus it is desirable to produce the sensors in large batches. For example, batches of 100 or more or of 1000 or more sensors may be produced.
  • the sensor may be provided with a code, for example a batch code, during processing. The code may be applied to the sensor, for example by printing the code on the substrate.
  • the sensor code may include information such as the batch 54 number, the type and quantity of chemistry applied to the sensor, and/or calibration data.

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PCT/US1999/003781 1998-03-04 1999-02-22 Process for producing an electrochemical biosensor WO1999045375A1 (en)

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