CA2696661A1 - Thermally conductive sensor - Google Patents
Thermally conductive sensor Download PDFInfo
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- CA2696661A1 CA2696661A1 CA 2696661 CA2696661A CA2696661A1 CA 2696661 A1 CA2696661 A1 CA 2696661A1 CA 2696661 CA2696661 CA 2696661 CA 2696661 A CA2696661 A CA 2696661A CA 2696661 A1 CA2696661 A1 CA 2696661A1
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- sensor
- strip
- gap
- heat conducting
- conducting layer
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- 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
Abstract
A sensor instrument for use with a sensor strip comprises a temperature sensor, at a side of a gap for accepting the sensor strip, opposite electrical contacts. The invention provides an accuratedetermination of the temperature of a sample. A sensor system comprises the sensor instrument and the sensor strip which may comprises an electrode substrate, an electrode set, on the electrode substrate, and a heat conducting layer, on the electrode substrate opposite the electrode set.
Description
THERMALLY CONDUCTIVE SENSOR
This application is a division of CA 2,328,750 filed December 18, 2000.
BACKGROUND OF THE INVENTION
The present invention relates to a sensor instrument for a thermally conductive electrochemical sensor; a sensor system and a method of measuring concentration of an analyte in a sample.
Electrochemical biosensors are well known. They have been used to determine the concentration of various analytes from biological samples, particularly from blood.
Electrochemical biosensors are described in U.S. Pat. Nos. 5,413,690;
5,762,770 and 5,798,031; as well as in International Publication No. W099/13101.
An electrochemical biosensor typically includes a sensor strip and a sensor instrument.
The sensor strip includes a space that holds the sample to be analyzed, may include reagents to be released into the sample, and includes an electrode set. The electrode set normally includes an insulating substrate, and electrodes that contact the sample, which have contact pads for electrically connecting the electrodes to the sensor instrument.
The temperature of the sample during analysis will affect the signal detected by the electrochemical biosensor. In order to compensate for variations in sample temperature, most electrochemical biosensors measure the ambient temperature, typically by using a temperature sensor in the sensor instrument, and contain electronics for electrochemical analysis. The temperature of the actual sample may vary from the ambient temperature, depending on the humidity and local air movements, by three degrees, or more.
DOCSMTL: 3811645\1 Furthermore, the ambient temperature is not necessarily stable, and therefore algorithms have been used to compensate for changes in ambient temperature (see, for example, U.S. Pat. No. 5,405,511). In addition, if the instrument is held in the hand during use, the recorded ambient temperature may be affected by the temperature of the hand.
None of these devices actually measures the temperature of the sample, but rather simply use the ambient temperature measurements to indirectly determine the temperature of at the sample site, or the temperature close to the sample. It would be desirable to more accurately measure the temperature of the sample, thus avoiding the need for compensatory algorithms, and improving measurement accuracy.
SUMMARY OF THE INVENTION
In one aspect, the invention is a sensor instrument for accepting a sensor strip comprising a gap, electrical contacts at a first side of said gap, and a temperature sensor, at a second side of the gap, opposite the electrical contacts.
In another aspect, the invention is an improvement in a sensor instrument for accepting a sensor strip, including electronics for electrochemical analysis, a gap having electrical contacts for contacting contact pads on the sensor strip, and having a temperature sensor, the improvement comprising: a temperature sensor in the gap.
In another aspect of the invention, there is provided a sensor system for measuring the concentration of an analyte in a biological sample, said sensor system comprising: a sensor instrument, said sensor instrument comprising a housing having a gap formed therein, said sensor instrument further comprising electrical contacts at a first side of said gap and a temperature sensor at a second side of said gap opposite said first side;
and a sensor strip, said sensor strip comprising: (a) an electrode substrate having first and second opposed faces, (b) an electrode set on said first face of said electrode substrate, said electrode set having a sensing region for the electrochemical analysis, and a reagent for the electrochemical analysis on said sensing region, and (c) a heat DOCSMTL: 381 I645\1 conducting layer on said second face of said electrode substrate opposite said electrode set.
In still another aspect of the invention, there is provided a method for measuring the concentration of an analyte in a sample, comprising: providing an electrochemical sensor system of the invention as described herein; inserting the sensor strip of the sensor system into the sensor instrument gap such that said electrodes electrically communicate with said electrical contacts, and said conducting portion thermally communicates with said temperature sensor; applying the sample to the sensing region of the sensing strip; and electrochemically reacting the analyte in the sample with a reagent to provide an electrochemical signal corresponding to a concentration of the analyte in the sample at a temperature of the conducting portion.
The invention also provides a sensor strip, comprising (a) an electrode substrate having first and second opposed faces, (b) an electrode set on the first face of the electrode substrate, and (c) a heat conducting layer on the second face of the electrode substrate opposite the electrode set.
The sensor strip may comprise (a) an electrode substrate, and (b) an electrode set, on the electrode substrate, where the sensor strip has a thermal conductivity of at least 10 W/m-K.
The invention further provides a method of making a sensor strip, comprising forming an electrode set on a first face of an electrode substrate; and attaching the electrode substrate to a heat conducting layer such that the heat conducting layer is on a second face of the electrode substrate opposite the electrode set.
An advantage of the present invention is that it allows for accurate temperature measurement of the sensing region and sample.
DOCSMTL: 3811645\1 As used herein, the phrase "electrode set" is a set of at least two electrodes, for example 2 to 60, or 3 to 20, electrodes. These electrodes may be, for example, a working electrode, a counter electrode, and a reference electrode.
Other features and advantages of the present invention will become apparent from the following detailed description. It should be understood, however, that the detailed description and the specific examples, while indicating embodiments of the invention, are given by way of illustration only, since various changes and modifications within the spirit and scope of the invention will become apparent to those skilled in the art from this detailed description.
BRIEF DESCRIPTION OF THE DRAWINGS
The following drawings form part of the present specification and are included to further demonstrate certain aspects of the present invention. The invention may be better understood by reference to one or more of these drawings in combination with the detailed description of specific embodiments presented herein:
DOCSMTL: 3811645\1 Figure 1 is an exploded view of an embodiment of a sensor strip of the invention;
Figure 2 is a top view of an embodiment of a sensor strip of the invention;
Figure 3 is a bottom view of an embodiment of a sensor strip of the invention;
Figure 4 is a detailed illustration of a side view, from the bottom, of a portion of the sensor 5 strip shown in Figure 3;
Figure 5 illustrates an exploded view of another embodiment of a sensor strip of the invention;
and Figure 6 illustrates a sensor instrument with a sensor strip inserted.
DETAILED DESCRIPTION OF THE INVENTION
Figure 2 is a top view of an embodiment of a sensor strip 12, Figure 3 is a bottom view, and Figure 1 is an exploded view. Illustrated in Figure 1, are an electrode substrate 3, the contact pads 9 and 9, and sensing region 10, all of which are part of the electrodes 11 and 11. The electrodes are, in part, covered with a dielectric 5 exposing the sensing region 10, through hole 22 in the dielectric, and the contact pads 9 and 9. Reagent 6 is on the sensing region 10. Also illustrated is heat conducting layer 24 under the electrode substrate 3, which is most clearly illustrated in Figure 3. In this embodiment, the sample is loaded from the top of the sensor strip via hole 22.
Figure 4 provides a detailed illustration of a side view, from the bottom, of a portion the sensor strip 12. In this embodiment, the heat conducting layer 24 is in contact with the electrode substrate 3, which in turn is in contact with the electrodes 11. The electrodes are covered (in part) with dielectric 5.
Figure 5 illustrates an exploded view of another embodiment of a sensor strip 12, which includes a base 1 on a heat conducting layer 24, and adhesive foil 2 for holding the base to the electrode substrate 3. The electrode set 16, which is made up of the two electrodes 11 and 11, is on the electrode substrate 3, and is partially covered by a dielectric 5. A
cover 8 is attached to one end of the dielectric with adhesive tape 7. A small gap 1,3 in the dielectric, and a space 14 in the adhesive tape, together with the cover and the electrodes, form a pocket inside of which may be placed reagent 6 used to aid in electrochemically detecting and quantifying an analyte.
This pocket can act as a capillary, drawing the fluid to be tested onto the sensing region 10 of the electrodes. Alternatively, the cover may be absent, exposing the sensing region of the electrodes, and the sample may be directly applied onto this region.
Figure 6 illustrates a sensor instrument with a sensor strip inserted. As shown, the sensor strip 12 is inserted into the instrument with the end having contact pads 9 and 9 physically inside the instrument. Electrical contacts 34 and 34 make electrical contact with the contact pads. A
temperature sensor 32 makes contact with the bottom of the sensor strip, at a surface opposite the contact pads. The temperature sensor is at a side of the gap which receives the sensor strip opposite the electrical contacts. Also shown in the figure is the sensing region 10.
An electrode set includes at least first and second electrodes. The electrodes are separated by a gap that prevents electrical contact between the two electrodes. In Figure 5, the sensing region of each electrode includes interdigitating fingers. The sensing region is where the actual electrochemical sensing takes place. In the sensing region only a simple straight gap may separate the electodes (as illustrated in Figure 1), or it may be more complex, for example, containing a rectilinear gap, forming a region of interlacing fingers of the two electrodes.
The length of the electrode set is preferably 2.5 to 250 mm, the width is preferably 0.4 to 40 mm, the gap between the contact pads is preferably 1 m to 5 mm, and the width of each contact pad is preferably 1 to 20 mm. The electrode pattern is preferably symmetric, however this is not required, and an irregular or asymmetric pattern (or electrode shapes) is possible.
The heat conducting layer improves the overall thermal conductivity of the sensor strip.
Without a heat conducting layer, the sensor strip can have a thermal conductivity of 1.41 W/m=K. The heat conducting layer itself has a thermal conductivity of at least 10 W/m=K, preferably of at least 50 W/m=K, more preferably at least 100 W/m=K, and most preferably at least 200 W/m=K. Preferably, the heat conducting layer contains copper, aluminum, which have a thermal conductivity of about 400 and 200 W/m=K, respectively, or alloys of these metals. The heat conducting layer may be a composite material, such as a polymer containing metallic particles or fibers. Furthermore, the heat conducting layer may be coated with one or more material, such as nickel and gold, or a polymer film, to improve its corrosion resistance or appearance. The volume of the heat conducting layer, as based on the total volume of the sensor strip, preferably at least 2%, more preferably at least 5%, even more preferably at least 20%, and most preferably at least 45%. The thickness of the heat conducting layer depends on the thermal conductivity of the heat conducting layer. Preferably the heat conducting layer has a thickness of 0.1 mils to 0.5 inches, more preferably, 0.5 mils to 0.1 inches, most preferably 1 mil to 50 mils.
The heat conducting layer extends at least from an area near the sensing region (but on the opposite side of the electrode substrate) to an area near the contact pads (but on the opposite side of the electrode substrate). Any shape is possible; for example the heat conducting layer may extend the full length and width of the electrode substrate, or it could be a narrow strip which extends from opposite the sensing region to opposite the contact pads.
Preferably, the heat conducting layer extends from a first end of the electrode substrate or base (i.e., the end having the contact pads) towards the second end of the substrate or base, to a position in general alignment with the sensing region. It would also be possible for the heat conducting layer to be irregularly shaped, as long as it serves to increase the thermal conductivity of the sensor strip.
The heat conducting layer is not required. Instead it is possible to simply use an electrode substrate that has a thermal conductivity of at least 10 W/m=K, preferably of at least 50 W/m=K, more preferably at least 100 W/m=K, and most preferably at least 200 W/m=K.
However, the electrode substrate must be electrically insulating, at least at its surface in order to prevent it from short circuiting the electrodes. Therefore, when a heat conducting layer is not used, the electrode substrate may be made from a highly thermally conductive ceramic, such as diamond, aluminum nitride, or aluminum oxide; or from a composite materials such as a composite of a polymer and metal particles or fibers.
With a heat conducting layer, or with an electrode substrate that has a thermal conductivity of at least 10 W/m=K, the thermal conductivity of the sensor strip is improved.
Preferably, the sensor strip has a thermal conductivity of at least 10 W/m=K, more preferably at least 20 W/m=K, even more preferably at least 85 W/m=K, and most preferably at least 190 W/m=K.
The thermal conductivity of the sensor strip is the average thermal conductivity as measured from the sensing region to the surface of the sensor strip opposite the contact pads.
The heat conducting layer may be attached to the electrode substrate.
Alternatively, if the electrode substrate is attached to a base, the heat conducting layer may be attached to the base.
The heat conducting layer may be attached to the electrode substrate or base by an adhesive, an adhesive foil, or directly laminating them together using heat and/or pressure. The heat conducting layer could also be mechanically attached using a clip or fastener.
It would also be possible to directly form the heat conducting layer onto the electrode substrate or base, for example, by sputtering or evaporation. Furthermore, it would also be possible to directly form the electrode substrate or base onto the heat conducting layer, for example, by sputtering, evaporation, or polymerizing monomers.
The method of forming of the remainder of the sensor strip is not limited. Any previous method may be used. For example, the electrodes may be formed by sealing foil onto the electrode substrate (for example, gold foil). The electrodes may be screen printed onto the electrode substrate, or a metallic layer may be sputtered and then electrodes formed in it by lithography. Alternatively, the electrodes may be formed by lamination, or laser ablation as described in U.S. Pat. No. 6,662,839.
Preferably, the electrode includes gold, platinum, palladium, iridium, or alloys of these metals, since such noble metals and their alloys are unreactive in biological systems.
The electrodes may be any thickness, but preferably are 10 nm to 1 mm, more preferably, 20 nm to 100 m, or even 25 nm to 1 m.
A UV curable dielectric and which is screen printable, may be used to form the dielectric, for example the polymer composition 5018 dielectric composition from DuPont. The clear cover is a clear material that is inert to biological fluids, for example glass, polyethylene, polypropylene, polyvinylchloride, polyimide, or polyester. The clear cover may have markings. The adhesive tape is also a flexible polymer having a surfaces covered with an adhesive; these materials are also well known to those of ordinary skill in the art.
The base is an optional supporting structure, and is preferably made of a flexible polymer material, with a thickness sufficient to provide support to the sensor strip, for example polyester with a thickness of 6 mils. The adhesive foil may be made for the same types of compositions as the adhesive tape.
The reagent is optional, and may be used to provide electrochemical probes for specific analytes. The starting reagents are the reactants or components of the reagent, and are DOCSMTL: 3811645\1 often compounded together in liquid form before application to the ribbons or reels. The liquid may then evaporate, leaving the reagent in solid form. The choice of specific reagent depends on the specific analyte or analytes to be measure, and are well known to those of ordinary skill in the art. For example, a reagent for measurement of glucose in a human blood sample contains 62.2 mg polyethylene oxide (mean molecular weight of 100-900 kilodaltons), 3.3 mg NATROSOL 250 M, 41.5 mg AVICEL RC-591 F, 89.4 mg monobasic potassium phosphate, 157.9 mg dibasic potassium phosphate, 437.3 mg potassium ferricyanide, 46.0 mg sodium succinate, 148.0 mg trehalose, 2.6 mg TRITON
X- 100 surfactant, and 2,000 to 9,000 units of enzyme activity per gram of reagent. The enzyme is prepared as an enzyme solution from 12.5 mg coenzyme PQQ and 1.21 million units of the apoenzyme of quinoprotein glucose dehydrogenase, forming a solution of quinoprotein glucose dehydrogenase. This reagent is described in WO
99/30152, pages 7-10.
When hematocrit is to be determined, the reagent includes oxidized and reduced forms of a reversible electroactive compound (potassium hexacyanoferrate (III) ("ferricyanide") and potassium hexacyanoferrate (II) ("ferrocyanide"), respectively), an electrolyte (potassium phosphate butter), and a microcrystalline material (Avicel RC-591F--a blend of 88% microcrystalline cellulose and 12% sodium carboxymethyl-cellulose, available from FMC Corp.). Concentrations of the components within the reagent before drying are as follows: 400 millimolar (mM) ferricyanide, 55 mM
ferrocyanide, 400 mM potassium phosphate, and 2.0% (weight:volume) Avicel. A
further description of the reagent for a hematocrit assay is found in U.S.
Pat. No.
5,385,846.
Other non-limiting examples of enzymes and mediators that may be used in measuring particular analytes in cell 10 of the present invention are listed below in Table 1.
DOCSMTL: 3811645\1 Analyte Enzymes Mediator Additional Mediator (Oxidized Form) Glucose Glucose Dehydrogenase Ferricyanide and Diaphorase Glucose Glucose-Dehydrogenase Ferricyanide Cholesterol (Quinoprotein) Ferricyanide 2,6-Dimethyl- 1,4-Cholesterol Esterase and Benzoquinone Cholesterol Oxidase 2,5-Dichloro- 1,4-Benzoquinone or Phenazine Ethosulfate HDL Cholesterol Esterase Ferricyanide 2,6-Dimethyl- 1,4-Cholesterol and Cholesterol Oxidase Benzoquinone 2,5-Dichloro-1,4-Benzoquinone or Phenazine Ethosulfate Triglycerides Lipoprotein Lipase, Ferricyanide or Phenazine Methosulfate Glycerol Kinase, and Phenazine Glycerol-3-Phosphate Ethosulfate Oxidase Lactate Lactate Oxidase Ferricyanide 2,6-Dichloro-1,4-Benzoquinone Lactate Lactate Dehydrogenase Ferricyanide and Diaphorase Phenazine Ethosulfate, or Phenazine Methosulfate Lactate Diaphorase Ferricyanide Phenazine Ethosulfate, or Dehydrogenase Phenazine Methosulfate Pyruvate Pyruvate Oxidase Ferricyanide Alcohol Alcohol Oxidase Phenylenediamine Bilirubin Bilirubin Oxidase 1-Methoxy-Phenazine Methosulfate Uric Acid Uricase Ferricyanide In some of the examples shown in Table 1, at least one additional enzyme is used as a reaction catalyst. Also, some of the examples shown in Table 1 may utilize an additional mediator, 5 which facilitates electron transfer to the oxidized form of the mediator.
The additional mediator may be provided to the reagent in lesser amount than the oxidized form of the mediator. While the above assays are described, it is appreciated that a variety of electrochemical assays may be conducted with cell 10 in accordance with this disclosure.
The sensor strip of the present invention may also include microspheres, as described in U.S. Pat. No. 6,627,057 entitled "MICROSPHERE CONTAINING SENSOR", inventors Raghbir Singh Bhullar and Brian S. Hill, filed Dec. 23, 1999.
The processes and products described include disposable biosensors, especially for use in diagnostic devices. However, also included are electrochemical sensors for non-diagnostic uses, such as measuring an analyte in any biological, environmental, food or other sample. In addition, a plurality of the sensor strips are typically packaged in a vial, usually with a stopper. Furthermore, a new sensor instrument may be used with the sensor strips.
An electrochemical biosensor includes both a sensor strip, as well as a sensor instrument. The sensor strip is inserted into the sensor instrument so that the contact pads mate with electrical contacts in the sensor instrument. The sensor instrument used with the sensor strip of the present invention will also have a temperature sensor, similar to sensor instrument previously known, however, the temperature sensor will be located near the electrical contacts intended to mate with the contact pads, and situated so that the temperature sensor will come into contact with the sensor strip. This will allow the temperature sensor to measure the temperature of the sensor strip itsel Preferably the temperature sensor will be situated so that it will come into contact with the bottom of the sensor strip, more preferably the temperature sensor will come into contact with the heat conducting layer. In all other respects, the sensor instrument of the present invention will be similar to previous sensor instrument, for example the sensor instrument of U.S. Pat. No. 5,405,511, except that algorithms intended to determine the temperature of the sample are unnecessary; the temperature measured directly by the temperature sensor may be used as the temperature of the sample. For example, a gap in the sensor instrument, intended to accept the end of the sensor strip having contact pads, will have the electrical contacts for connecting to the contact pads at one end, and an embodiment of the present invention, will have a temperature sensor opposite the electrical contacts.
DOCSMTL: 3811645\1
This application is a division of CA 2,328,750 filed December 18, 2000.
BACKGROUND OF THE INVENTION
The present invention relates to a sensor instrument for a thermally conductive electrochemical sensor; a sensor system and a method of measuring concentration of an analyte in a sample.
Electrochemical biosensors are well known. They have been used to determine the concentration of various analytes from biological samples, particularly from blood.
Electrochemical biosensors are described in U.S. Pat. Nos. 5,413,690;
5,762,770 and 5,798,031; as well as in International Publication No. W099/13101.
An electrochemical biosensor typically includes a sensor strip and a sensor instrument.
The sensor strip includes a space that holds the sample to be analyzed, may include reagents to be released into the sample, and includes an electrode set. The electrode set normally includes an insulating substrate, and electrodes that contact the sample, which have contact pads for electrically connecting the electrodes to the sensor instrument.
The temperature of the sample during analysis will affect the signal detected by the electrochemical biosensor. In order to compensate for variations in sample temperature, most electrochemical biosensors measure the ambient temperature, typically by using a temperature sensor in the sensor instrument, and contain electronics for electrochemical analysis. The temperature of the actual sample may vary from the ambient temperature, depending on the humidity and local air movements, by three degrees, or more.
DOCSMTL: 3811645\1 Furthermore, the ambient temperature is not necessarily stable, and therefore algorithms have been used to compensate for changes in ambient temperature (see, for example, U.S. Pat. No. 5,405,511). In addition, if the instrument is held in the hand during use, the recorded ambient temperature may be affected by the temperature of the hand.
None of these devices actually measures the temperature of the sample, but rather simply use the ambient temperature measurements to indirectly determine the temperature of at the sample site, or the temperature close to the sample. It would be desirable to more accurately measure the temperature of the sample, thus avoiding the need for compensatory algorithms, and improving measurement accuracy.
SUMMARY OF THE INVENTION
In one aspect, the invention is a sensor instrument for accepting a sensor strip comprising a gap, electrical contacts at a first side of said gap, and a temperature sensor, at a second side of the gap, opposite the electrical contacts.
In another aspect, the invention is an improvement in a sensor instrument for accepting a sensor strip, including electronics for electrochemical analysis, a gap having electrical contacts for contacting contact pads on the sensor strip, and having a temperature sensor, the improvement comprising: a temperature sensor in the gap.
In another aspect of the invention, there is provided a sensor system for measuring the concentration of an analyte in a biological sample, said sensor system comprising: a sensor instrument, said sensor instrument comprising a housing having a gap formed therein, said sensor instrument further comprising electrical contacts at a first side of said gap and a temperature sensor at a second side of said gap opposite said first side;
and a sensor strip, said sensor strip comprising: (a) an electrode substrate having first and second opposed faces, (b) an electrode set on said first face of said electrode substrate, said electrode set having a sensing region for the electrochemical analysis, and a reagent for the electrochemical analysis on said sensing region, and (c) a heat DOCSMTL: 381 I645\1 conducting layer on said second face of said electrode substrate opposite said electrode set.
In still another aspect of the invention, there is provided a method for measuring the concentration of an analyte in a sample, comprising: providing an electrochemical sensor system of the invention as described herein; inserting the sensor strip of the sensor system into the sensor instrument gap such that said electrodes electrically communicate with said electrical contacts, and said conducting portion thermally communicates with said temperature sensor; applying the sample to the sensing region of the sensing strip; and electrochemically reacting the analyte in the sample with a reagent to provide an electrochemical signal corresponding to a concentration of the analyte in the sample at a temperature of the conducting portion.
The invention also provides a sensor strip, comprising (a) an electrode substrate having first and second opposed faces, (b) an electrode set on the first face of the electrode substrate, and (c) a heat conducting layer on the second face of the electrode substrate opposite the electrode set.
The sensor strip may comprise (a) an electrode substrate, and (b) an electrode set, on the electrode substrate, where the sensor strip has a thermal conductivity of at least 10 W/m-K.
The invention further provides a method of making a sensor strip, comprising forming an electrode set on a first face of an electrode substrate; and attaching the electrode substrate to a heat conducting layer such that the heat conducting layer is on a second face of the electrode substrate opposite the electrode set.
An advantage of the present invention is that it allows for accurate temperature measurement of the sensing region and sample.
DOCSMTL: 3811645\1 As used herein, the phrase "electrode set" is a set of at least two electrodes, for example 2 to 60, or 3 to 20, electrodes. These electrodes may be, for example, a working electrode, a counter electrode, and a reference electrode.
Other features and advantages of the present invention will become apparent from the following detailed description. It should be understood, however, that the detailed description and the specific examples, while indicating embodiments of the invention, are given by way of illustration only, since various changes and modifications within the spirit and scope of the invention will become apparent to those skilled in the art from this detailed description.
BRIEF DESCRIPTION OF THE DRAWINGS
The following drawings form part of the present specification and are included to further demonstrate certain aspects of the present invention. The invention may be better understood by reference to one or more of these drawings in combination with the detailed description of specific embodiments presented herein:
DOCSMTL: 3811645\1 Figure 1 is an exploded view of an embodiment of a sensor strip of the invention;
Figure 2 is a top view of an embodiment of a sensor strip of the invention;
Figure 3 is a bottom view of an embodiment of a sensor strip of the invention;
Figure 4 is a detailed illustration of a side view, from the bottom, of a portion of the sensor 5 strip shown in Figure 3;
Figure 5 illustrates an exploded view of another embodiment of a sensor strip of the invention;
and Figure 6 illustrates a sensor instrument with a sensor strip inserted.
DETAILED DESCRIPTION OF THE INVENTION
Figure 2 is a top view of an embodiment of a sensor strip 12, Figure 3 is a bottom view, and Figure 1 is an exploded view. Illustrated in Figure 1, are an electrode substrate 3, the contact pads 9 and 9, and sensing region 10, all of which are part of the electrodes 11 and 11. The electrodes are, in part, covered with a dielectric 5 exposing the sensing region 10, through hole 22 in the dielectric, and the contact pads 9 and 9. Reagent 6 is on the sensing region 10. Also illustrated is heat conducting layer 24 under the electrode substrate 3, which is most clearly illustrated in Figure 3. In this embodiment, the sample is loaded from the top of the sensor strip via hole 22.
Figure 4 provides a detailed illustration of a side view, from the bottom, of a portion the sensor strip 12. In this embodiment, the heat conducting layer 24 is in contact with the electrode substrate 3, which in turn is in contact with the electrodes 11. The electrodes are covered (in part) with dielectric 5.
Figure 5 illustrates an exploded view of another embodiment of a sensor strip 12, which includes a base 1 on a heat conducting layer 24, and adhesive foil 2 for holding the base to the electrode substrate 3. The electrode set 16, which is made up of the two electrodes 11 and 11, is on the electrode substrate 3, and is partially covered by a dielectric 5. A
cover 8 is attached to one end of the dielectric with adhesive tape 7. A small gap 1,3 in the dielectric, and a space 14 in the adhesive tape, together with the cover and the electrodes, form a pocket inside of which may be placed reagent 6 used to aid in electrochemically detecting and quantifying an analyte.
This pocket can act as a capillary, drawing the fluid to be tested onto the sensing region 10 of the electrodes. Alternatively, the cover may be absent, exposing the sensing region of the electrodes, and the sample may be directly applied onto this region.
Figure 6 illustrates a sensor instrument with a sensor strip inserted. As shown, the sensor strip 12 is inserted into the instrument with the end having contact pads 9 and 9 physically inside the instrument. Electrical contacts 34 and 34 make electrical contact with the contact pads. A
temperature sensor 32 makes contact with the bottom of the sensor strip, at a surface opposite the contact pads. The temperature sensor is at a side of the gap which receives the sensor strip opposite the electrical contacts. Also shown in the figure is the sensing region 10.
An electrode set includes at least first and second electrodes. The electrodes are separated by a gap that prevents electrical contact between the two electrodes. In Figure 5, the sensing region of each electrode includes interdigitating fingers. The sensing region is where the actual electrochemical sensing takes place. In the sensing region only a simple straight gap may separate the electodes (as illustrated in Figure 1), or it may be more complex, for example, containing a rectilinear gap, forming a region of interlacing fingers of the two electrodes.
The length of the electrode set is preferably 2.5 to 250 mm, the width is preferably 0.4 to 40 mm, the gap between the contact pads is preferably 1 m to 5 mm, and the width of each contact pad is preferably 1 to 20 mm. The electrode pattern is preferably symmetric, however this is not required, and an irregular or asymmetric pattern (or electrode shapes) is possible.
The heat conducting layer improves the overall thermal conductivity of the sensor strip.
Without a heat conducting layer, the sensor strip can have a thermal conductivity of 1.41 W/m=K. The heat conducting layer itself has a thermal conductivity of at least 10 W/m=K, preferably of at least 50 W/m=K, more preferably at least 100 W/m=K, and most preferably at least 200 W/m=K. Preferably, the heat conducting layer contains copper, aluminum, which have a thermal conductivity of about 400 and 200 W/m=K, respectively, or alloys of these metals. The heat conducting layer may be a composite material, such as a polymer containing metallic particles or fibers. Furthermore, the heat conducting layer may be coated with one or more material, such as nickel and gold, or a polymer film, to improve its corrosion resistance or appearance. The volume of the heat conducting layer, as based on the total volume of the sensor strip, preferably at least 2%, more preferably at least 5%, even more preferably at least 20%, and most preferably at least 45%. The thickness of the heat conducting layer depends on the thermal conductivity of the heat conducting layer. Preferably the heat conducting layer has a thickness of 0.1 mils to 0.5 inches, more preferably, 0.5 mils to 0.1 inches, most preferably 1 mil to 50 mils.
The heat conducting layer extends at least from an area near the sensing region (but on the opposite side of the electrode substrate) to an area near the contact pads (but on the opposite side of the electrode substrate). Any shape is possible; for example the heat conducting layer may extend the full length and width of the electrode substrate, or it could be a narrow strip which extends from opposite the sensing region to opposite the contact pads.
Preferably, the heat conducting layer extends from a first end of the electrode substrate or base (i.e., the end having the contact pads) towards the second end of the substrate or base, to a position in general alignment with the sensing region. It would also be possible for the heat conducting layer to be irregularly shaped, as long as it serves to increase the thermal conductivity of the sensor strip.
The heat conducting layer is not required. Instead it is possible to simply use an electrode substrate that has a thermal conductivity of at least 10 W/m=K, preferably of at least 50 W/m=K, more preferably at least 100 W/m=K, and most preferably at least 200 W/m=K.
However, the electrode substrate must be electrically insulating, at least at its surface in order to prevent it from short circuiting the electrodes. Therefore, when a heat conducting layer is not used, the electrode substrate may be made from a highly thermally conductive ceramic, such as diamond, aluminum nitride, or aluminum oxide; or from a composite materials such as a composite of a polymer and metal particles or fibers.
With a heat conducting layer, or with an electrode substrate that has a thermal conductivity of at least 10 W/m=K, the thermal conductivity of the sensor strip is improved.
Preferably, the sensor strip has a thermal conductivity of at least 10 W/m=K, more preferably at least 20 W/m=K, even more preferably at least 85 W/m=K, and most preferably at least 190 W/m=K.
The thermal conductivity of the sensor strip is the average thermal conductivity as measured from the sensing region to the surface of the sensor strip opposite the contact pads.
The heat conducting layer may be attached to the electrode substrate.
Alternatively, if the electrode substrate is attached to a base, the heat conducting layer may be attached to the base.
The heat conducting layer may be attached to the electrode substrate or base by an adhesive, an adhesive foil, or directly laminating them together using heat and/or pressure. The heat conducting layer could also be mechanically attached using a clip or fastener.
It would also be possible to directly form the heat conducting layer onto the electrode substrate or base, for example, by sputtering or evaporation. Furthermore, it would also be possible to directly form the electrode substrate or base onto the heat conducting layer, for example, by sputtering, evaporation, or polymerizing monomers.
The method of forming of the remainder of the sensor strip is not limited. Any previous method may be used. For example, the electrodes may be formed by sealing foil onto the electrode substrate (for example, gold foil). The electrodes may be screen printed onto the electrode substrate, or a metallic layer may be sputtered and then electrodes formed in it by lithography. Alternatively, the electrodes may be formed by lamination, or laser ablation as described in U.S. Pat. No. 6,662,839.
Preferably, the electrode includes gold, platinum, palladium, iridium, or alloys of these metals, since such noble metals and their alloys are unreactive in biological systems.
The electrodes may be any thickness, but preferably are 10 nm to 1 mm, more preferably, 20 nm to 100 m, or even 25 nm to 1 m.
A UV curable dielectric and which is screen printable, may be used to form the dielectric, for example the polymer composition 5018 dielectric composition from DuPont. The clear cover is a clear material that is inert to biological fluids, for example glass, polyethylene, polypropylene, polyvinylchloride, polyimide, or polyester. The clear cover may have markings. The adhesive tape is also a flexible polymer having a surfaces covered with an adhesive; these materials are also well known to those of ordinary skill in the art.
The base is an optional supporting structure, and is preferably made of a flexible polymer material, with a thickness sufficient to provide support to the sensor strip, for example polyester with a thickness of 6 mils. The adhesive foil may be made for the same types of compositions as the adhesive tape.
The reagent is optional, and may be used to provide electrochemical probes for specific analytes. The starting reagents are the reactants or components of the reagent, and are DOCSMTL: 3811645\1 often compounded together in liquid form before application to the ribbons or reels. The liquid may then evaporate, leaving the reagent in solid form. The choice of specific reagent depends on the specific analyte or analytes to be measure, and are well known to those of ordinary skill in the art. For example, a reagent for measurement of glucose in a human blood sample contains 62.2 mg polyethylene oxide (mean molecular weight of 100-900 kilodaltons), 3.3 mg NATROSOL 250 M, 41.5 mg AVICEL RC-591 F, 89.4 mg monobasic potassium phosphate, 157.9 mg dibasic potassium phosphate, 437.3 mg potassium ferricyanide, 46.0 mg sodium succinate, 148.0 mg trehalose, 2.6 mg TRITON
X- 100 surfactant, and 2,000 to 9,000 units of enzyme activity per gram of reagent. The enzyme is prepared as an enzyme solution from 12.5 mg coenzyme PQQ and 1.21 million units of the apoenzyme of quinoprotein glucose dehydrogenase, forming a solution of quinoprotein glucose dehydrogenase. This reagent is described in WO
99/30152, pages 7-10.
When hematocrit is to be determined, the reagent includes oxidized and reduced forms of a reversible electroactive compound (potassium hexacyanoferrate (III) ("ferricyanide") and potassium hexacyanoferrate (II) ("ferrocyanide"), respectively), an electrolyte (potassium phosphate butter), and a microcrystalline material (Avicel RC-591F--a blend of 88% microcrystalline cellulose and 12% sodium carboxymethyl-cellulose, available from FMC Corp.). Concentrations of the components within the reagent before drying are as follows: 400 millimolar (mM) ferricyanide, 55 mM
ferrocyanide, 400 mM potassium phosphate, and 2.0% (weight:volume) Avicel. A
further description of the reagent for a hematocrit assay is found in U.S.
Pat. No.
5,385,846.
Other non-limiting examples of enzymes and mediators that may be used in measuring particular analytes in cell 10 of the present invention are listed below in Table 1.
DOCSMTL: 3811645\1 Analyte Enzymes Mediator Additional Mediator (Oxidized Form) Glucose Glucose Dehydrogenase Ferricyanide and Diaphorase Glucose Glucose-Dehydrogenase Ferricyanide Cholesterol (Quinoprotein) Ferricyanide 2,6-Dimethyl- 1,4-Cholesterol Esterase and Benzoquinone Cholesterol Oxidase 2,5-Dichloro- 1,4-Benzoquinone or Phenazine Ethosulfate HDL Cholesterol Esterase Ferricyanide 2,6-Dimethyl- 1,4-Cholesterol and Cholesterol Oxidase Benzoquinone 2,5-Dichloro-1,4-Benzoquinone or Phenazine Ethosulfate Triglycerides Lipoprotein Lipase, Ferricyanide or Phenazine Methosulfate Glycerol Kinase, and Phenazine Glycerol-3-Phosphate Ethosulfate Oxidase Lactate Lactate Oxidase Ferricyanide 2,6-Dichloro-1,4-Benzoquinone Lactate Lactate Dehydrogenase Ferricyanide and Diaphorase Phenazine Ethosulfate, or Phenazine Methosulfate Lactate Diaphorase Ferricyanide Phenazine Ethosulfate, or Dehydrogenase Phenazine Methosulfate Pyruvate Pyruvate Oxidase Ferricyanide Alcohol Alcohol Oxidase Phenylenediamine Bilirubin Bilirubin Oxidase 1-Methoxy-Phenazine Methosulfate Uric Acid Uricase Ferricyanide In some of the examples shown in Table 1, at least one additional enzyme is used as a reaction catalyst. Also, some of the examples shown in Table 1 may utilize an additional mediator, 5 which facilitates electron transfer to the oxidized form of the mediator.
The additional mediator may be provided to the reagent in lesser amount than the oxidized form of the mediator. While the above assays are described, it is appreciated that a variety of electrochemical assays may be conducted with cell 10 in accordance with this disclosure.
The sensor strip of the present invention may also include microspheres, as described in U.S. Pat. No. 6,627,057 entitled "MICROSPHERE CONTAINING SENSOR", inventors Raghbir Singh Bhullar and Brian S. Hill, filed Dec. 23, 1999.
The processes and products described include disposable biosensors, especially for use in diagnostic devices. However, also included are electrochemical sensors for non-diagnostic uses, such as measuring an analyte in any biological, environmental, food or other sample. In addition, a plurality of the sensor strips are typically packaged in a vial, usually with a stopper. Furthermore, a new sensor instrument may be used with the sensor strips.
An electrochemical biosensor includes both a sensor strip, as well as a sensor instrument. The sensor strip is inserted into the sensor instrument so that the contact pads mate with electrical contacts in the sensor instrument. The sensor instrument used with the sensor strip of the present invention will also have a temperature sensor, similar to sensor instrument previously known, however, the temperature sensor will be located near the electrical contacts intended to mate with the contact pads, and situated so that the temperature sensor will come into contact with the sensor strip. This will allow the temperature sensor to measure the temperature of the sensor strip itsel Preferably the temperature sensor will be situated so that it will come into contact with the bottom of the sensor strip, more preferably the temperature sensor will come into contact with the heat conducting layer. In all other respects, the sensor instrument of the present invention will be similar to previous sensor instrument, for example the sensor instrument of U.S. Pat. No. 5,405,511, except that algorithms intended to determine the temperature of the sample are unnecessary; the temperature measured directly by the temperature sensor may be used as the temperature of the sample. For example, a gap in the sensor instrument, intended to accept the end of the sensor strip having contact pads, will have the electrical contacts for connecting to the contact pads at one end, and an embodiment of the present invention, will have a temperature sensor opposite the electrical contacts.
DOCSMTL: 3811645\1
Claims (30)
1. A sensor instrument for accepting a sensor strip, comprising:
a gap, electrical contacts at a first side of said gap, and a temperature sensor, at a second side of said gap, opposite said electrical contacts.
a gap, electrical contacts at a first side of said gap, and a temperature sensor, at a second side of said gap, opposite said electrical contacts.
2. In a sensor instrument for accepting a sensor strip, including electronics for electrochemical analysis, a gap having electrical contacts for contacting contact pads on the sensor strip, and having a temperature sensor, the improvement comprising:
a temperature sensor in the gap.
a temperature sensor in the gap.
3. A sensor system for measuring the concentration of an analyte in a biological sample, said sensor system comprising:
a sensor instrument, said sensor instrument comprising a housing having a gap formed therein, said sensor instrument further comprising electrical contacts at a first side of said gap and a temperature sensor at a second side of said gap opposite said first side;
and a sensor strip, said sensor strip comprising (a) an electrode substrate having first and second opposed faces, (b) an electrode set on said first face of said electrode substrate, said electrode set having a sensing region for the electrochemical analysis, and a reagent for the electrochemical analysis on said sensing region, and (c) a heat conducting layer on said second face of said electrode substrate opposite said electrode set.
a sensor instrument, said sensor instrument comprising a housing having a gap formed therein, said sensor instrument further comprising electrical contacts at a first side of said gap and a temperature sensor at a second side of said gap opposite said first side;
and a sensor strip, said sensor strip comprising (a) an electrode substrate having first and second opposed faces, (b) an electrode set on said first face of said electrode substrate, said electrode set having a sensing region for the electrochemical analysis, and a reagent for the electrochemical analysis on said sensing region, and (c) a heat conducting layer on said second face of said electrode substrate opposite said electrode set.
4. The sensor system of Claim 3, wherein said heat conducting layer comprises a metal or an alloy.
5. The sensor system of Claim 4, wherein said metal or alloy comprises at least 2%
by volume of said sensor strip.
by volume of said sensor strip.
6. The sensor system of Claim 5, wherein said metal or alloy comprises at least 20% by volume of said sensor strip.
7. The sensor system of any one of Claims 3 to 6, wherein said sensor strip further comprises:
(d) a base, between said electrode substrate and said heat conducting layer.
(d) a base, between said electrode substrate and said heat conducting layer.
8. The sensor system of any one of Claims 3 to 7, wherein said sensor strip has a thermal conductivity of at least 10W/m-K.
9. The sensor system of Claim 8, wherein said sensor strip has a thermal conductivity of at least 85W/m-K.
10. The sensor system of Claim 6, wherein said sensor strip has a thermal conductivity of at least 85W/m-K, and said heat conducting layer comprises copper, an alloy of copper, aluminum, or an alloy of aluminum.
11. The sensor system of any one of Claims 3 to 10, wherein said sensor strip further comprises:
(e) a dielectric, on said electrode set.
(e) a dielectric, on said electrode set.
12. A sensor system for measuring the concentration of an analyte in a biological sample, said sensor system comprising:
a sensor instrument, said sensor instrument comprising a housing having a gap formed therein, said sensor instrument further comprising electrical contacts at a first side of said gap and a temperature sensor at a second side of said gap opposite said first side;
and a sensor strip, said sensor strip comprising an electrically-insulating electrode substrate, an electrode set on a first side of said electrode substrate, and a heat conducting layer on a second side of said electrode substrate opposite said first side, said heat conducting layer comprising at least 20% by volume of said sensor strip and having a thermal conductivity of at least 10 W/m-K, said sensor strip receivable in said gap such that said electrode set electrically communicates with said electrical contacts, and said heat conducting layer communicates with said temperature sensor.
a sensor instrument, said sensor instrument comprising a housing having a gap formed therein, said sensor instrument further comprising electrical contacts at a first side of said gap and a temperature sensor at a second side of said gap opposite said first side;
and a sensor strip, said sensor strip comprising an electrically-insulating electrode substrate, an electrode set on a first side of said electrode substrate, and a heat conducting layer on a second side of said electrode substrate opposite said first side, said heat conducting layer comprising at least 20% by volume of said sensor strip and having a thermal conductivity of at least 10 W/m-K, said sensor strip receivable in said gap such that said electrode set electrically communicates with said electrical contacts, and said heat conducting layer communicates with said temperature sensor.
13. The sensor system of claim 12, wherein said heat conducting layer comprises a metal or an alloy.
14. The sensor system of claim 13, wherein said metal or Alloy comprises at least 45% by volume of said sensor strip.
15. The sensor system of any one of claims 12 to 14, wherein said sensor strip further comprises a base between said electrode substrate and said heat conducting layer.
16. The sensor system of any one of claims 12 to 15, wherein said heat conducting layer has a thermal conductivity of at least 100 W/m-K.
17. The sensor system of any one of claims 12 to 15, wherein said heat conducting layer has a thermal conductivity of at least 200 W/m-K.
18. The sensor system of any one of claims 12 to 17, wherein said heat conducting layer comprises copper, an alloy of copper, aluminum, or an alloy of aluminum.
19. The sensor system of claim 18, wherein said heat conducting layer comprises copper.
20. The sensor system of any one of claims 12 to 19, wherein said sensor strip further comprises a reagent disposed on said electrode set.
21. The sensor system of claim 20, wherein said reagent comprises at least one agent catalytically reactive with said analyte for electrochemically measuring said analyte concentration.
22. The sensor system of any one of claims 12 to 21, wherein said sensor strip further comprises a dielectric disposed on said electrode set.
23. The sensor system of claim 21, wherein the analyte is glucose, and the reagent comprises glucose dehydrogenase.
24. The sensor system of claim 21, wherein the analyte is glucose, and the reagent comprises glucose dehydrogenase and ferricyanide.
25. The sensor system of claim 21, wherein the analyte is glucose, and the reagent comprises glucose dehydrogenase and diaphorase.
26. A method for measuring the concentration of an analyte in a sample, comprising:
providing an electrochemical sensor system, said electrochemical sensor system comprising a sensor instrument and a sensor strip, said sensor instrument comprising a housing having a gap formed therein for receiving said sensor strip, electrical contacts at a first side of said gap, and a temperature sensor at a second side of said gap; said sensor strip comprising an electrically-insulating electrode substrate, an electrode set on a first side of said electrode substrate, and a conducting portion on a second side of said electrode substrate, said conducting portion comprising at least 20% by volume of said sensor strip and having a thermal conductivity of at least 10 W/m-K, said electrode set comprising at least two electrodes, said sensor strip further comprising a sensing region for receiving said sample;
inserting said sensor strip into said sensor instrument gap such that said electrodes electrically communicate with said electrical contacts, and said conducting portion thermally communicates with said temperature sensor;
applying said sample to said sensing region of said sensing strip; and electrochemically reacting said analyte in said sample with a reagent to provide an electrochemical signal corresponding to a concentration of the analyte in the sample at a temperature of said conducting portion.
providing an electrochemical sensor system, said electrochemical sensor system comprising a sensor instrument and a sensor strip, said sensor instrument comprising a housing having a gap formed therein for receiving said sensor strip, electrical contacts at a first side of said gap, and a temperature sensor at a second side of said gap; said sensor strip comprising an electrically-insulating electrode substrate, an electrode set on a first side of said electrode substrate, and a conducting portion on a second side of said electrode substrate, said conducting portion comprising at least 20% by volume of said sensor strip and having a thermal conductivity of at least 10 W/m-K, said electrode set comprising at least two electrodes, said sensor strip further comprising a sensing region for receiving said sample;
inserting said sensor strip into said sensor instrument gap such that said electrodes electrically communicate with said electrical contacts, and said conducting portion thermally communicates with said temperature sensor;
applying said sample to said sensing region of said sensing strip; and electrochemically reacting said analyte in said sample with a reagent to provide an electrochemical signal corresponding to a concentration of the analyte in the sample at a temperature of said conducting portion.
27. The method of claim 26, wherein said electrical contacts are at an upper side of said gap, and said temperature sensor is at a lower side of said gap, and wherein said temperature sensor contacts a bottom portion of said sensor strip.
28. The method of claim 27, wherein said bottom portion of said sensor strip comprises a heat conducting layer.
29. The method of claim 28, wherein said heat conducting layer comprises at least one of copper, an alloy of copper, aluminum, or an alloy of aluminum.
30. The method of claim 28, wherein said heat conducting layer comprises copper.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US09/471,570 | 1999-12-23 | ||
| US09/471,570 US6780296B1 (en) | 1999-12-23 | 1999-12-23 | Thermally conductive sensor |
| CA 2328750 CA2328750C (en) | 1999-12-23 | 2000-12-18 | Thermally conductive sensor |
Related Parent Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA 2328750 Division CA2328750C (en) | 1999-12-23 | 2000-12-18 | Thermally conductive sensor |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2696661A1 true CA2696661A1 (en) | 2001-06-23 |
Family
ID=23872129
Family Applications (2)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA 2696661 Abandoned CA2696661A1 (en) | 1999-12-23 | 2000-12-18 | Thermally conductive sensor |
| CA 2328750 Expired - Fee Related CA2328750C (en) | 1999-12-23 | 2000-12-18 | Thermally conductive sensor |
Family Applications After (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA 2328750 Expired - Fee Related CA2328750C (en) | 1999-12-23 | 2000-12-18 | Thermally conductive sensor |
Country Status (4)
| Country | Link |
|---|---|
| US (2) | US6780296B1 (en) |
| EP (1) | EP1114994A3 (en) |
| JP (2) | JP3382604B2 (en) |
| CA (2) | CA2696661A1 (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US8721851B2 (en) | 2008-11-28 | 2014-05-13 | Panasonic Healthcare Co., Ltd. | Sensor chip, biosensor system, method for measuring temperature of biological sample, method for measuring temperature of blood sample, and method for measuring concentration of analyte in blood sample |
| US8859292B2 (en) | 2009-01-30 | 2014-10-14 | Panasonic Healthcare Co., Ltd. | Method for measuring temperature of biological sample, method for measuring concentration of biological sample, sensor chip and biosensor system |
Families Citing this family (88)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6036924A (en) | 1997-12-04 | 2000-03-14 | Hewlett-Packard Company | Cassette of lancet cartridges for sampling blood |
| US6391005B1 (en) | 1998-03-30 | 2002-05-21 | Agilent Technologies, Inc. | Apparatus and method for penetration with shaft having a sensor for sensing penetration depth |
| US8641644B2 (en) | 2000-11-21 | 2014-02-04 | Sanofi-Aventis Deutschland Gmbh | Blood testing apparatus having a rotatable cartridge with multiple lancing elements and testing means |
| EP2388585B1 (en) * | 2000-11-30 | 2018-05-02 | Panasonic Healthcare Holdings Co., Ltd. | Method of quantifying substrate |
| US9226699B2 (en) | 2002-04-19 | 2016-01-05 | Sanofi-Aventis Deutschland Gmbh | Body fluid sampling module with a continuous compression tissue interface surface |
| EP1404233B1 (en) | 2001-06-12 | 2009-12-02 | Pelikan Technologies Inc. | Self optimizing lancing device with adaptation means to temporal variations in cutaneous properties |
| ATE497731T1 (en) | 2001-06-12 | 2011-02-15 | Pelikan Technologies Inc | DEVICE FOR INCREASING THE SUCCESS RATE OF BLOOD YIELD OBTAINED BY A FINGER PICK |
| US7682318B2 (en) | 2001-06-12 | 2010-03-23 | Pelikan Technologies, Inc. | Blood sampling apparatus and method |
| US7025774B2 (en) | 2001-06-12 | 2006-04-11 | Pelikan Technologies, Inc. | Tissue penetration device |
| EP1404235A4 (en) | 2001-06-12 | 2008-08-20 | Pelikan Technologies Inc | Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge |
| US9427532B2 (en) | 2001-06-12 | 2016-08-30 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| US8337419B2 (en) | 2002-04-19 | 2012-12-25 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| JP4149911B2 (en) | 2001-06-12 | 2008-09-17 | ペリカン テクノロジーズ インコーポレイテッド | Electric lancet actuator |
| US7981056B2 (en) | 2002-04-19 | 2011-07-19 | Pelikan Technologies, Inc. | Methods and apparatus for lancet actuation |
| US9795747B2 (en) | 2010-06-02 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | Methods and apparatus for lancet actuation |
| WO2003062812A1 (en) * | 2002-01-18 | 2003-07-31 | Arkray, Inc. | Analyzer having temperature sensor |
| US9795334B2 (en) | 2002-04-19 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
| US7491178B2 (en) | 2002-04-19 | 2009-02-17 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US8784335B2 (en) | 2002-04-19 | 2014-07-22 | Sanofi-Aventis Deutschland Gmbh | Body fluid sampling device with a capacitive sensor |
| US7229458B2 (en) | 2002-04-19 | 2007-06-12 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7291117B2 (en) | 2002-04-19 | 2007-11-06 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US8221334B2 (en) | 2002-04-19 | 2012-07-17 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
| US9248267B2 (en) | 2002-04-19 | 2016-02-02 | Sanofi-Aventis Deustchland Gmbh | Tissue penetration device |
| US7175642B2 (en) | 2002-04-19 | 2007-02-13 | Pelikan Technologies, Inc. | Methods and apparatus for lancet actuation |
| US9314194B2 (en) | 2002-04-19 | 2016-04-19 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| US7901362B2 (en) | 2002-04-19 | 2011-03-08 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7226461B2 (en) | 2002-04-19 | 2007-06-05 | Pelikan Technologies, Inc. | Method and apparatus for a multi-use body fluid sampling device with sterility barrier release |
| US8360992B2 (en) | 2002-04-19 | 2013-01-29 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
| US8372016B2 (en) | 2002-04-19 | 2013-02-12 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for body fluid sampling and analyte sensing |
| US7976476B2 (en) | 2002-04-19 | 2011-07-12 | Pelikan Technologies, Inc. | Device and method for variable speed lancet |
| US7892183B2 (en) | 2002-04-19 | 2011-02-22 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
| US7331931B2 (en) | 2002-04-19 | 2008-02-19 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7297122B2 (en) | 2002-04-19 | 2007-11-20 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7547287B2 (en) | 2002-04-19 | 2009-06-16 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7232451B2 (en) | 2002-04-19 | 2007-06-19 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US8267870B2 (en) | 2002-04-19 | 2012-09-18 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for body fluid sampling with hybrid actuation |
| US8702624B2 (en) | 2006-09-29 | 2014-04-22 | Sanofi-Aventis Deutschland Gmbh | Analyte measurement device with a single shot actuator |
| US7909778B2 (en) | 2002-04-19 | 2011-03-22 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US8579831B2 (en) | 2002-04-19 | 2013-11-12 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
| US7717863B2 (en) | 2002-04-19 | 2010-05-18 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7371247B2 (en) | 2002-04-19 | 2008-05-13 | Pelikan Technologies, Inc | Method and apparatus for penetrating tissue |
| US7648468B2 (en) | 2002-04-19 | 2010-01-19 | Pelikon Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7674232B2 (en) | 2002-04-19 | 2010-03-09 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US8574895B2 (en) | 2002-12-30 | 2013-11-05 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus using optical techniques to measure analyte levels |
| EP1443325A1 (en) * | 2003-02-01 | 2004-08-04 | Roche Diagnostics GmbH | System and method for determining a coagulation parameter |
| ES2347248T3 (en) | 2003-05-30 | 2010-10-27 | Pelikan Technologies Inc. | PROCEDURE AND APPLIANCE FOR FLUID INJECTION. |
| US7850621B2 (en) | 2003-06-06 | 2010-12-14 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
| WO2006001797A1 (en) | 2004-06-14 | 2006-01-05 | Pelikan Technologies, Inc. | Low pain penetrating |
| EP1671096A4 (en) | 2003-09-29 | 2009-09-16 | Pelikan Technologies Inc | Method and apparatus for an improved sample capture device |
| WO2005037095A1 (en) | 2003-10-14 | 2005-04-28 | Pelikan Technologies, Inc. | Method and apparatus for a variable user interface |
| US7822454B1 (en) | 2005-01-03 | 2010-10-26 | Pelikan Technologies, Inc. | Fluid sampling device with improved analyte detecting member configuration |
| US8668656B2 (en) | 2003-12-31 | 2014-03-11 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for improving fluidic flow and sample capture |
| US7964883B2 (en) * | 2004-02-26 | 2011-06-21 | Lighting Science Group Corporation | Light emitting diode package assembly that emulates the light pattern produced by an incandescent filament bulb |
| EP1751546A2 (en) | 2004-05-20 | 2007-02-14 | Albatros Technologies GmbH & Co. KG | Printable hydrogel for biosensors |
| WO2005120365A1 (en) | 2004-06-03 | 2005-12-22 | Pelikan Technologies, Inc. | Method and apparatus for a fluid sampling device |
| US9775553B2 (en) | 2004-06-03 | 2017-10-03 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for a fluid sampling device |
| AT502915B1 (en) * | 2004-12-23 | 2008-01-15 | Hoffmann La Roche | DEVICE FOR THERMOSTATIZING A MEASURING CELL IN AN ANALYZER AND MEASURING CELL, WHICH CAN BE REPLACED INTO AN ANALYZER REPLACEABLE |
| US8652831B2 (en) | 2004-12-30 | 2014-02-18 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for analyte measurement test time |
| WO2006091607A2 (en) * | 2005-02-21 | 2006-08-31 | University Of South Florida | Micro sensor system for liquid conductivity, temperature and depth |
| KR20070114802A (en) * | 2005-03-04 | 2007-12-04 | 바이엘 헬쓰케어, 엘엘씨 | Stabilizing enzyme activity in electrochemical biosensors |
| CN101495855B (en) * | 2006-07-05 | 2013-04-17 | 松下电器产业株式会社 | Method and apparatus for measuring liquid sample |
| EP2156348B1 (en) | 2007-05-30 | 2018-08-01 | Ascensia Diabetes Care Holdings AG | System and method for managing health data |
| WO2009052222A1 (en) * | 2007-10-15 | 2009-04-23 | Bayer Healthcare Llc | Method and assembly for determining the temperature of a test sensor |
| WO2009119118A1 (en) | 2008-03-27 | 2009-10-01 | パナソニック株式会社 | Sample measurement device, sample measurement system and sample measurement method |
| JP2009250806A (en) | 2008-04-07 | 2009-10-29 | Panasonic Corp | Biosensor system, sensor chip and measuring method of concentration of analyte in blood sample |
| WO2009126900A1 (en) | 2008-04-11 | 2009-10-15 | Pelikan Technologies, Inc. | Method and apparatus for analyte detecting device |
| JP5487467B2 (en) * | 2008-06-16 | 2014-05-07 | パナソニックヘルスケア株式会社 | Analytical object measuring method, biosensor and measuring instrument |
| JP5369551B2 (en) * | 2008-09-04 | 2013-12-18 | パナソニック株式会社 | Biological information measuring device |
| CN102203574B (en) * | 2008-10-21 | 2013-10-30 | 生命扫描有限公司 | Infrared temperature measurement of strip |
| US9375169B2 (en) | 2009-01-30 | 2016-06-28 | Sanofi-Aventis Deutschland Gmbh | Cam drive for managing disposable penetrating member actions with a single motor and motor and control system |
| WO2010151592A1 (en) | 2009-06-23 | 2010-12-29 | Bayer Healthcare Llc | System and apparatus for determining temperatures in a fluid analyte system |
| WO2011001917A1 (en) | 2009-06-30 | 2011-01-06 | アークレイ株式会社 | Analysis device and analysis method |
| JP4725665B2 (en) * | 2009-08-04 | 2011-07-13 | パナソニック株式会社 | Biosensor, biosensor measuring apparatus, and substrate quantification method |
| KR100980316B1 (en) | 2009-12-09 | 2010-09-06 | 동진메디칼 주식회사 | Strip having thermal compensating function and method for measuring blood sugar using it |
| US8965476B2 (en) | 2010-04-16 | 2015-02-24 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| JP4930642B2 (en) * | 2011-02-16 | 2012-05-16 | パナソニック株式会社 | Biosensor, biosensor measuring apparatus, and substrate quantification method |
| US9823214B2 (en) * | 2011-11-01 | 2017-11-21 | Panasonic Healthcare Holdings Co., Ltd. | Biological sample measuring apparatus |
| JP2014178143A (en) * | 2013-03-13 | 2014-09-25 | Dainippon Printing Co Ltd | Concentration measurement sensor, concentration measurement sensor sheet, and manufacturing method thereof |
| JP6356707B2 (en) | 2013-03-15 | 2018-07-11 | エフ．ホフマン−ラ ロシュ アーゲーＦ． Ｈｏｆｆｍａｎｎ−Ｌａ Ｒｏｃｈｅ Ａｋｔｉｅｎｇｅｓｅｌｌｓｃｈａｆｔ | Method for detecting high antioxidant levels during electrochemical measurements and then fail-safe analyte concentration and devices, apparatus and systems incorporating the same |
| EP3388823A1 (en) | 2013-03-15 | 2018-10-17 | Roche Diabetes Care GmbH | Methods of scaling data used to construct biosensor algorithms as well as devices, apparatuses and systems incorporating the same |
| WO2014140172A1 (en) | 2013-03-15 | 2014-09-18 | Roche Diagnostics Gmbh | Methods of failsafing electrochemical measurements of an analyte as well as devices, apparatuses and systems incorporating the same |
| JP6352954B2 (en) | 2013-03-15 | 2018-07-04 | エフ．ホフマン−ラ ロシュ アーゲーＦ． Ｈｏｆｆｍａｎｎ−Ｌａ Ｒｏｃｈｅ Ａｋｔｉｅｎｇｅｓｅｌｌｓｃｈａｆｔ | Method and device for using information from recovery pulses in electrochemical analyte measurement, apparatus and system incorporating them |
| JP6300057B2 (en) * | 2013-03-18 | 2018-03-28 | 大日本印刷株式会社 | Concentration measurement sensor and method for manufacturing the same, sheet for concentration measurement sensor and flash annealing method |
| KR102270616B1 (en) | 2013-06-17 | 2021-06-30 | 씨티바 스웨덴 에이비 | Bioreactor system with a temperature sensor |
| DE102013110042A1 (en) * | 2013-09-12 | 2015-03-12 | Endress + Hauser Conducta Gesellschaft für Mess- und Regeltechnik mbH + Co. KG | Electrochemical sensor |
| US20160228678A1 (en) * | 2015-01-02 | 2016-08-11 | Pacific Diabetes Technologies | Highly Durable Dual Use Catheter for Analyte Sensing and Drug Delivery |
| KR102372113B1 (en) | 2016-10-05 | 2022-03-07 | 에프. 호프만-라 로슈 아게 | Detection reagents and electrode arrangements for multi-analyte diagnostic test elements, and methods of using the same |
| DE102022107214A1 (en) * | 2022-03-28 | 2023-09-28 | Senslab - Gesellschaft Zur Entwicklung Und Herstellung Bioelektrochemischer Sensoren Mbh | Method and sensor for determining a plasma-related analyte concentration in whole blood |
Family Cites Families (26)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4062750A (en) * | 1974-12-18 | 1977-12-13 | James Francis Butler | Thin film electrochemical electrode and cell |
| US4464552A (en) * | 1981-10-29 | 1984-08-07 | James River-Dixie/Northern, Inc. | Packaging |
| EP0270868B1 (en) * | 1984-06-28 | 1991-01-30 | Roche Diagnostics GmbH | Container for diagnostic indicators |
| US4894137A (en) * | 1986-09-12 | 1990-01-16 | Omron Tateisi Electronics Co. | Enzyme electrode |
| US5431806A (en) * | 1990-09-17 | 1995-07-11 | Fujitsu Limited | Oxygen electrode and temperature sensor |
| US5342498A (en) * | 1991-06-26 | 1994-08-30 | Graves Jeffrey A | Electronic wiring substrate |
| US5264103A (en) * | 1991-10-18 | 1993-11-23 | Matsushita Electric Industrial Co., Ltd. | Biosensor and a method for measuring a concentration of a substrate in a sample |
| US5232667A (en) * | 1992-05-21 | 1993-08-03 | Diametrics Medical, Inc. | Temperature control for portable diagnostic system using a non-contact temperature probe |
| US5284568A (en) * | 1992-07-17 | 1994-02-08 | E. I. Du Pont De Nemours And Company | Disposable cartridge for ion selective electrode sensors |
| US5344754A (en) * | 1993-01-13 | 1994-09-06 | Avocet Medical, Inc. | Assay timed by electrical resistance change and test strip |
| US5385846A (en) | 1993-06-03 | 1995-01-31 | Boehringer Mannheim Corporation | Biosensor and method for hematocrit determination |
| US5405511A (en) | 1993-06-08 | 1995-04-11 | Boehringer Mannheim Corporation | Biosensing meter with ambient temperature estimation method and system |
| US5413690A (en) | 1993-07-23 | 1995-05-09 | Boehringer Mannheim Corporation | Potentiometric biosensor and the method of its use |
| DE4328815A1 (en) * | 1993-08-27 | 1995-03-02 | Boehringer Mannheim Gmbh | System for the storage of test elements |
| AU1075395A (en) | 1993-11-25 | 1995-06-13 | Technobiochip | Potentiometric biosensors, control and applications thereof |
| US5762770A (en) * | 1994-02-21 | 1998-06-09 | Boehringer Mannheim Corporation | Electrochemical biosensor test strip |
| JPH08154903A (en) * | 1994-12-09 | 1996-06-18 | Hitachi Ltd | Living body information monitoring sheet |
| AUPP238898A0 (en) * | 1998-03-12 | 1998-04-09 | Usf Filtration And Separations Group Inc. | Heated electrochemical cell |
| US5972715A (en) | 1996-12-23 | 1999-10-26 | Bayer Corporation | Use of thermochromic liquid crystals in reflectometry based diagnostic methods |
| US6391645B1 (en) | 1997-05-12 | 2002-05-21 | Bayer Corporation | Method and apparatus for correcting ambient temperature effect in biosensors |
| US5798031A (en) | 1997-05-12 | 1998-08-25 | Bayer Corporation | Electrochemical biosensor |
| GB9711395D0 (en) * | 1997-06-04 | 1997-07-30 | Environmental Sensors Ltd | Improvements to electrodes for the measurement of analytes in small samples |
| US6046051A (en) * | 1997-06-27 | 2000-04-04 | Hemosense, Inc. | Method and device for measuring blood coagulation or lysis by viscosity changes |
| US6129823A (en) | 1997-09-05 | 2000-10-10 | Abbott Laboratories | Low volume electrochemical sensor |
| US5997817A (en) | 1997-12-05 | 1999-12-07 | Roche Diagnostics Corporation | Electrochemical biosensor test strip |
| US6662439B1 (en) | 1999-10-04 | 2003-12-16 | Roche Diagnostics Corporation | Laser defined features for patterned laminates and electrodes |
-
1999
- 1999-12-23 US US09/471,570 patent/US6780296B1/en not_active Expired - Fee Related
-
2000
- 2000-12-18 CA CA 2696661 patent/CA2696661A1/en not_active Abandoned
- 2000-12-18 CA CA 2328750 patent/CA2328750C/en not_active Expired - Fee Related
- 2000-12-19 EP EP20000127765 patent/EP1114994A3/en not_active Withdrawn
- 2000-12-22 JP JP2000391541A patent/JP3382604B2/en not_active Expired - Fee Related
-
2002
- 2002-05-14 JP JP2002138184A patent/JP3595315B2/en not_active Expired - Fee Related
-
2004
- 2004-07-08 US US10/887,191 patent/US7510643B2/en not_active Expired - Fee Related
Cited By (8)
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|---|---|---|---|---|
| US8721851B2 (en) | 2008-11-28 | 2014-05-13 | Panasonic Healthcare Co., Ltd. | Sensor chip, biosensor system, method for measuring temperature of biological sample, method for measuring temperature of blood sample, and method for measuring concentration of analyte in blood sample |
| US9658182B2 (en) | 2008-11-28 | 2017-05-23 | Panasonic Healthcare Holdings Co., Ltd. | Method for measuring concentration of analyte in blood sample, and biosensor system |
| US10690620B2 (en) | 2008-11-28 | 2020-06-23 | Phc Holdings Corporation | Method for measuring concentration of analyte in blood sample, and biosensor system |
| US8859292B2 (en) | 2009-01-30 | 2014-10-14 | Panasonic Healthcare Co., Ltd. | Method for measuring temperature of biological sample, method for measuring concentration of biological sample, sensor chip and biosensor system |
| US9395320B2 (en) | 2009-01-30 | 2016-07-19 | Panasonic Healthcare Holdings Co., Ltd. | Method for measuring temperature of biological sample, measuring device, and biosensor system |
| US9664639B2 (en) | 2009-01-30 | 2017-05-30 | Panasonic Healthcare Holdings Co., Ltd. | Method for measuring temperature of biological sample, measuring device, and biosensor system |
| US9874537B2 (en) | 2009-01-30 | 2018-01-23 | Panasonic Healthcare Holdings Co., Ltd. | Method for measuring temperature of biological sample, measuring device, and biosensor system |
| US10520461B2 (en) | 2009-01-30 | 2019-12-31 | Phc Holdings Corporation | Method for measuring temperature of biological sample, measuring device, and biosensor system |
Also Published As
| Publication number | Publication date |
|---|---|
| EP1114994A3 (en) | 2004-01-07 |
| US20040238357A1 (en) | 2004-12-02 |
| US6780296B1 (en) | 2004-08-24 |
| CA2328750A1 (en) | 2001-06-23 |
| JP2001235444A (en) | 2001-08-31 |
| EP1114994A2 (en) | 2001-07-11 |
| CA2328750C (en) | 2010-07-06 |
| JP3595315B2 (en) | 2004-12-02 |
| JP3382604B2 (en) | 2003-03-04 |
| US7510643B2 (en) | 2009-03-31 |
| JP2003042995A (en) | 2003-02-13 |
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