WO1999051974A1 - Procede de determination d'un substrat - Google Patents
Procede de determination d'un substrat Download PDFInfo
- Publication number
- WO1999051974A1 WO1999051974A1 PCT/JP1999/001706 JP9901706W WO9951974A1 WO 1999051974 A1 WO1999051974 A1 WO 1999051974A1 JP 9901706 W JP9901706 W JP 9901706W WO 9951974 A1 WO9951974 A1 WO 9951974A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- electrode
- counter electrode
- substrate
- reaction layer
- counter
- Prior art date
Links
Classifications
-
- 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
- C12Q1/004—Enzyme electrodes mediator-assisted
Definitions
- the present invention relates to a quantitative method for quickly and easily performing a high-precision quantitative measurement of a substrate in a sample.
- the general rule of Glucose is that of the Glucose Age (Ec 1.
- GOD uses oxygen as an electron carrier and uses the substrate ⁇ — D — Dalco — D — Dalconone ⁇ 5 — In the presence of oxygen that selectively oxidizes lactones, it is in the process of oxidation reaction by GOD. As a result, oxygen is reduced to hydrogen peroxide.
- the oxygen electrode is used to measure the amount of reduction of the oxygen or the hydrogen peroxide is used to measure the increase in the amount of hydrogen peroxide. Since the reduced amount of oxygen and the increased amount of hydrogen peroxide are proportional to the amount of glucose contained in the sample solution, the amount of reduced or peroxidized oxygen is reduced. Glucose can be quantified from the increased amount of hydrogen.
- this method has a drawback in that the measurement results are greatly affected by the oxygen concentration contained in the sample solution. You. In addition, if oxygen is not present in the sample solution, measurement becomes impossible.
- the sample solution can be easily introduced simply by introducing the sample solution to the sensor that is detachably connected to the measuring instrument.
- the concentration of glucose can be measured with a measuring instrument. ⁇ Such a method is not limited to a fixed amount of glucose, but can be measured in the sample liquid. It can be applied to the fixed amount of other substrates included.
- the reduced electron carrier is oxidized on the working surface, and based on the value of the oxidizing current flowing at that time. Substrate concentration is determined. However, if blood or juice is used as a sample, the oxidizable property of scholvinic acid, uric acid, etc., contained in the sample, is high. The substance is also oxidized at the same time as the reduced electron carrier. The oxidation reaction of this easily oxidizable substance may affect the measurement result in some cases.
- the dissolved oxygen is transferred to the electron carrier at the same time when the electron carrier carried by the reaction layer is reduced.
- the reaction that produces hydrogen peroxide as a body progresses.
- hydrogen peroxide generated by this reaction reoxidizes the reduced electron carrier.
- the dissolved oxygen may give a negative error to the measurement result.
- the voltage is applied between the working and counter electrodes before the voltage is applied between the working and counter electrodes to obtain a current response.
- liquid junction detection is performed, that is, the detection that the sample liquid has been supplied is performed. At this time, the sample liquid is
- the resistance value between the ⁇ c action pole and the pole may change and the measurement may start, which may affect the measurement result There was a match. In addition, there were cases where the state of the working electrode surface changed, affecting the measurement results.
- the counter electrode is used in combination with the reference electrode.
- the reference electrode potential serving as the reference is the working electrode. Due to the force that fluctuates with the oxidation-reduction reaction, the measurement results could be affected by this.
- the present invention eliminates the above-mentioned disadvantages, eliminates the effects of oxidizable substances, and provides a quantitative method capable of measuring an accurate substance concentration. The purpose is to do so.
- the present invention is also aimed at providing a quantitative method for the substrate with a reduced response variability.
- the present invention has an electrically insulating substrate and a third electrode formed on the substrate that is used as a working electrode, a counter electrode, and an interfering substance detection electrode. Electrode system, and a reaction layer provided on the electrode system except for the third electrode and containing at least an oxidoreductase and an electron carrier. Using an sensor, the electron carrier is reduced by the electrons generated when reacting the substrate contained in the sample solution with the oxidoreductase, and the electron transfer is performed. By measuring the amount of body reduction electrochemically, A method for determining the concentration of a substrate in a sample solution, characterized by including the following steps:
- the present invention also includes an electrically insulating substrate and a working electrode, a counter electrode, and a third electrode formed on the substrate and used as an interfering substance detection electrode.
- a cover member that forms a sample liquid supply path that guides the sample liquid from the sample liquid supply port to the reaction layer, and the third electrode supplies the sample liquid more than the reaction layer.
- the third electrode as a reference electrode. That is, in the above step (f), a voltage is also applied between the working electrode and the third electrode.
- a layer supporting lecithin is arranged on the wall surface of the cover member exposed to the sample liquid supply passage. Is preferred.
- reaction layer preferably contains a hydrophilic high molecule.
- FIG. 1 is a plan view of the embodiment of the present invention in which the reaction layer of the glucose sensor has been removed.
- FIG. 2 is an exploded perspective view of a state in which the reaction layer of the glucose sensor has been removed according to another embodiment of the present invention. Best mode for carrying out the invention
- This sensor comprises a counter electrode 6, a working electrode 7, and a third electrode 8 on an insulative substrate 1, such as a polyethylene terephthalate, which serves as a power source. And leads 2, 3, and 4, which are electrically connected to them, are also provided.
- the carbon layer 9 is a layer provided for facilitating the fabrication of the reaction layer, and does not function as an electrode except for the third electrode 8.
- a circular reaction layer (not shown) containing the oxidoreductase and the electron carrier is provided on the counter electrode 6, the working electrode 7, and the carbon layer 9, a circular reaction layer (not shown) containing the oxidoreductase and the electron carrier is provided.
- reference numeral 5 denotes an insulating layer.
- FIG. 2 illustrates a second type of biosensor.
- This sensor is obtained by combining a cover member composed of a canopy 110 and a spacer 11 on a substrate 1 shown in FIG. These have a positional relationship as shown by a dashed line in FIG. The sensor is then bonded.
- the slit 11 that forms the sample liquid supply path is formed in the spacer 11, and the cover 10 has air holes 13 formed therein. You. When the force zone 10 is laminated and adhered on the substrate 1 via the spacer 11, the sample is formed by the substrate 1, the spacer 11, and the force bar 10. A space serving as a liquid supply path is formed in the slit 12 of the spacer 11. The end of the space communicates with the air holes 13.
- the working electrode 7 has a sample liquid supply port 12a (equivalent to the open end of the slit 12) than the half-moon-shaped counter electrode 6.
- the third electrode 8 is arranged closer to the sample liquid supply port 12a than the working electrode 7 is. .
- Each of these electrodes 6, 7, and 8 is exposed to the above space.
- the third electrode 8 is set at a predetermined potential with reference to the counter electrode 6. In a state in which this potential is applied, a sample solution containing, for example, ascorbic acid as an interfering substance is dropped on the reaction layer, and the reaction layer is added to the sample solution. Dissolve.
- a system that detects the supply of the solution based on the electrical change between the counter electrode 6 of the electrode system and the third electrode 8 operates, and this is performed.
- the measurement will start in the evening.
- a potential is continuously applied between the counter electrode 6 and the third electrode 8, and the potential is kept constant after detecting that the sample liquid is supplied.
- the current value between the counter electrode 6 and the third electrode 8 is measured. Since no reaction layer is disposed on the third electrode 8, a reduced form of the electron carrier generated as a result of the enzyme reaction reaches the vicinity of the third electrode 8. It will take some time to complete. Therefore, the above-mentioned current value is caused by the oxidation reaction of ascorbic acid, which is contained as an interfering substance.
- the application of the voltage between the counter electrode 6 and the third electrode 8 is released. Thereafter, a potential for oxidizing the reducing element of the electron conductor is applied to the working electrode 7 with reference to the counter electrode 6, and the current between the counter electrode 6 and the working electrode 7 is applied. Measure the value. This current is caused by the reduction of the electron carrier and the oxidation reaction of the pre-existing interfering substance, ascorbic acid. In other words, ascorbic acid gives a positive error to the measurement result.
- the above-described current value between the counter electrode 6 and the third electrode 8 mainly reflects only the concentration of ascorbic acid, and is based on this current value. By correcting the measurement results, the effects of ascorbic acid can be removed and an accurate substrate concentration can be determined.
- the supply of the sample liquid is detected between the counter electrode 6 and the third electrode 8, so that all the exposed portions of the working electrode 7 are reliably sampled. Filled with liquid. As a result, the supply of the sample liquid can be determined more reliably.
- Example 1 Example 1
- Gluco Sensor The substrate shown in Fig. 1 was used. This Glucose sensor was made as follows.
- Silver paste is printed by screen printing on an insulative substrate 1 made of a polyethylene terephthalate, and leads 2, 3, and 3 are printed. And 4 were each formed.
- a conductive carbon paste containing a resin binder is printed on the substrate 1 so that the counter electrode 6, the working electrode 7, the third electrode 8, and the like. And carbon layer 9 were formed.
- the counter electrode 6, the working electrode 7, and the third electrode 8 are in electrical contact with the leads 2, 3, and 4, respectively.
- an insulating paste was printed on the substrate 1 to form an insulating layer 5.
- the insulating layer 5 covers the outer periphery of the counter electrode 6, the working electrode 7, the third electrode 8, and the force-bonding layer 9, thereby forming the counter electrode 6, the working electrode.
- the area of the exposed part of the electrode 7, the third electrode 8, and the carbon layer 9 is kept constant.
- the insulating layer 5 covers a part of the leads 2, 3, and 4.
- a carboxymethylcellulose (hereinafter abbreviated as CMC) is formed on the counter electrode 6, the working electrode 7, and the carbon layer 9.
- the CMC layer was formed by dropping and drying the aqueous solution of ⁇ ).
- an aqueous solution containing G ⁇ D as an enzyme and ferrici- nating lithium as an electron carrier is dropped onto the CMC layer, the hydrophilicity is increased.
- the CMC layer consisting of molecules dissolves once and forms a reaction layer in the subsequent drying process in a form mixed with enzymes and the like.
- no agitation is involved, a completely mixed state is not achieved, and the surface of the electrode system is covered only with CMC. That is, Since enzymes and electron carriers do not come into contact with the surface of the electrode system, it is possible to prevent adsorption of proteins to the surface of the electrode system.
- the system that detects the supply of the liquid based on the electrical change between the counter electrode 6 of the electrode system and the third electrode 8 operates. This has triggered the measurement timer. At this time, an electric potential is continuously applied between the counter electrode 6 and the third electrode 8, and after a certain period of time has passed since the detection of the supply of the sample solution was performed. The current value between the counter electrode 6 and the third electrode 8 was measured. This current value was caused by the oxidation reaction of ascorbic acid, which was contained as an interfering substance, and gave a proportional relationship to its concentration. After the current value between the counter electrode 6 and the third electrode 8 was measured, the voltage application between both electrodes was released.
- the ferrocyanated ion generated as a result of the enzyme reaction becomes the third electrode. It takes some time to reach the vicinity of the electrode 8. That is, between the counter electrode 6 and the third electrode 8 within the time until the ferrocyanization ion is reached.
- the current value mainly reflects only the concentration of ascorbic acid. Further, 25 seconds after the detection of the sample liquid, 50 OmV is applied to the working electrode 7 with reference to the counter electrode 6, and 5 seconds after the working electrode 7 and the counter electrode 6 are applied. The current value of was measured.
- the ferricionized ion, glucose, and G ⁇ D in the solution react, and as a result, the glucose is converted to the dalkonolactone. It is oxidized and the ferricioned ion is reduced to a ferrocyanized ion. The concentration of this ferrocyanated ion is proportional to the concentration of glucose.
- the current between the counter electrode 6 and the working electrode 30 30 seconds after the detection of the sample liquid is determined by the ferrocyanation ion and the pre-existing ascorbi. It is caused by oxidation reaction of phosphoric acid. In other words, ascorbic acid gives a positive error to the measurement result.
- the current value between the counter electrode 6 and the third electrode 8 mainly reflects only the concentration of ascorbic acid, as described above. Therefore, by correcting the measurement results based on the results, the effects of ascorbic acid are removed, and an accurate glucose concentration is determined. You can do it.
- Example 2
- electrodes 6, 7, 8, and a carbon layer 9 were formed on a substrate 1.
- a CMC aqueous solution is dropped on the counter electrode 6, the working electrode 7 and the carbon layer 9 except for the third electrode 8, and the CMC is dried.
- a layer is formed on the CMC layer, and the G ⁇ D and the electron transfer as enzymes are formed on the CMC layer.
- the reaction layer was formed by dropping an aqueous solution containing a ferricillinating reamer as a body and drying it.
- an organic solvent solution of lecithin for example, toluene
- the en solution was spread over the reaction layer from the sample solution supply port 12a and dried to form a lecithin layer.
- the cover 10 and the spacer 11 are attached to the substrate 1 with a positional relationship as shown by a dashed line in FIG. The sensor was made.
- This sensor was set in a measuring instrument, and a potential of 50 OmV was applied to the third electrode 8 with reference to the counter electrode 6. With this potential applied, an aqueous glucose solution 31 containing ascorbic acid as an interfering substance is used as the sample liquid supply port 12 as a sample liquid. a Supplied more. The sample solution reached the air holes 13 through the sample solution supply path, and the reaction layer on the electrode system was dissolved.
- the system that detects the supply of the liquid based on the electrical change between the counter electrode 6 of the electrode system and the third electrode 8 operates, This has triggered the measurement timer.
- a potential is continuously applied between the counter electrode 6 and the third electrode 8, and after a lapse of a certain time from the detection of the sample liquid supply, the counter electrode 6 and the third electrode 8.
- the current value between the two was measured. This current value was caused by the oxidation reaction of ascorbic acid, which is included as an interfering substance, and gave a proportional relationship to its concentration.
- the application of the voltage between both electrodes was released.
- the reaction layer is disposed on the third electrode 8. It takes some time before the ferrocyanated ion produced as a result of the enzymatic reaction reaches the vicinity of the third electrode 8. Is required. That is, the current value between the counter electrode 6 and the third electrode 8 during the time up to the arrival of the ferrocyanization ion is mainly determined by ascorbi. Reflects only the acid concentration.
- the reaction of ferricionized ion, glucose, and GOD in the solution causes the oxidation of glucose to dalkonolactone. Then, the ferricioned ion is reduced to a ferrocyanized ion. The concentration of this ferrocyanated ion is proportional to the concentration of glucose.
- the current between the counter electrode 6 and the working electrode 30 seconds after the detection of the sample liquid is determined by the presence of fluorinated ion and pre-existing ascorbic acid. It is caused by the oxidation reaction. In other words, ascorbic acid gives a positive error to the measurement result.
- the current value between the counter electrode 6 and the third electrode 8 mainly reflects only the concentration of ascorbic acid, as described above. Therefore, by correcting the measurement results based on the results, the effects of ascorbic acid are removed, and an accurate glucose concentration is determined. You can do it.
- a glucose sensor was produced in the same manner as in Example 2.
- a sensor was set in the measuring instrument, and a potential of 500 mV was applied to the third electrode 8 with reference to the counter electrode 6.
- a potential of 500 mV was applied to the third electrode 8 with reference to the counter electrode 6.
- an aqueous glucose solution 3a1 containing ascorbic acid is used as a sample liquid, and a sample liquid supply port is used as a sample liquid.
- Supplied from 12a The sample solution reached the air holes 13 through the sample solution supply path, and the reaction layer on the electrode system was dissolved.
- the measurement timer started. At this time, a potential is continuously applied between the counter electrode 6 and the third electrode 8, and after a lapse of a fixed time from the detection of the sample liquid supply, the counter electrode 6 and the third electrode 8 are not applied. The current value between the two was measured. This current value was caused by the oxidation reaction of ascorbic acid, which is included as an interfering substance, and gave a proportional relationship to its concentration. After the current value between the counter electrode 6 and the third electrode 8 was measured, the application of the voltage between both electrodes was released.
- the reaction layer is not disposed on the third electrode 8, the ferrocyanated ion generated as a result of the enzymatic reaction is formed. It takes some time to reach the vicinity of the third electrode 8. That is, the current value between the counter electrode 6 and the third electrode 8 during the time until the ferrocyanation ion is reached is mainly due to ascorbic acid Reflects only the concentration of Further, after 25 seconds from the sample liquid detection force, 500 mV is applied to the working electrode 7 based on the third electrode 8, and the voltage between the counter electrode 6 and the working electrode 7 is applied. The current value after 5 seconds was measured.
- the reaction of phenylation, glucose, and GOD in the solution causes the oxidation of glucose to gluconanolone.
- the fermentation ion is reduced to ferrocationization.
- the concentration of the fermentation ion is determined by the concentration of glucose.
- the current between the counter electrode 6 and the working electrode 7 after 30 seconds, which is proportional to the sample concentration, is proportional to the concentration of the sample solution. It is caused by the oxidation reaction of existing ascorbic acid, that is, ascorbic acid gives a positive error to the measurement results.
- the current value between the counter electrode 6 and the third electrode 8 mainly reflects only the concentration of ascorbic acid, as described above. Therefore, the effect of ascorbic acid is removed and the accurate glucose concentration is corrected by correcting the measurement result based on the result. Can be obtained.
- Example 2 As in Example 2, a reaction layer was formed on the counter electrode 6, the working electrode 7, and the carbon layer 9 except for the third electrode 8.
- the groove formed on the cover member for forming the sample liquid supply passage makes the supply of the sample liquid to the reaction layer smoother.
- an organic solvent solution of lecithin for example, a toluene solution
- the power bar 10 and the spacer 11 are attached to the substrate 1 with a positional relationship as shown by a dashed line in FIG. We made sa.
- the opening on which the lecithin layer is disposed over the third electrode 8 from the upper surface of the reaction layer, and the surface of the third electrode 8 is changed by the lecithin layer.
- the response characteristics may vary greatly. (As described above, if the resin layer is placed on the power bar member side, Example 5 in which such variations were suppressed and the response characteristics were improved
- a glucose sensor was produced in the same manner as in Example 4.
- a sensor was set in the measuring instrument, and a potential of 110 OmV was applied to the third electrode 8 with reference to the counter electrode 6. With this potential applied, an air-saturated aqueous solution of glucose 3PL1 was supplied from the sample liquid supply port 12a as a sample liquid. The sample liquid reached the air hole 13 through the sample liquid supply path, and the reaction layer on the electrode system was dissolved.
- a system that detects the supply of the solution based on the electrical change between the counter electrode 6 of the electrode system and the third electrode 8 operates, and as a result, The measurement timer has started.
- the potential is continuously applied between the counter electrode 6 and the third electrode 8, and after a lapse of a certain time from the detection of the sample liquid supply, the current value between the counter electrode 6 and the third electrode 8 is changed. It was measured. This current value was caused by the reduction reaction of dissolved oxygen. When a dalcos solution degassed with argon was supplied, the reduction current decreased sharply. After the current value between the counter electrode 6 and the third electrode 8 was measured, the voltage application between both electrodes was released.
- the current value between the counter electrode 6 and the third electrode 8 during the time required for the ferricionized ion to reach the third electrode 8 is mainly Reflects only the dissolved oxygen concentration. Further, 25 seconds after the detection of the sample liquid, 50 OmV is applied to the working electrode 7 based on the third electrode 8 as a reference, and the voltage between the counter electrode 6 and the working electrode 7 is applied. The current value after 5 seconds was measured.
- ferric ionic ion The reaction of ferric ionic ion, glucose, and GOD in the solution causes the oxidation of glucose to dalkonolactone as a result. Along with this reaction, the ferricionized ion is reduced to a ferrocyanated ion.
- dissolved oxygen in the sample solution acts as an electron carrier, and glucose is converted to acid by darkonolactone.
- the reaction proceeds, the dissolved oxygen is reduced to hydrogen peroxide, and the reaction proceeds at the same time.
- Hydrogen peroxide generated by this reaction reoxidizes ferricioned ion to ferricified ion. Therefore, when measuring the glucose concentration based on the oxidation current value of ferrocyanated ion, the dissolved oxygen has a negative effect on the measurement result. Gives an error.
- the current value between the counter electrode 6 and the third electrode 8 mainly reflects only the dissolved oxygen concentration. Therefore, by correcting the measurement results based on the results, it is possible to eliminate the influence of dissolved oxygen and to obtain an accurate glucose concentration. it can.
- Example 7
- a glucose sensor was produced in the same manner as in Example 4.
- a sensor was set in the measuring instrument, and an electric potential of 50 OmV was applied to the third electrode 8 based on the counter electrode 6 as a reference. Mark this potential In this condition, the aqueous solution of glucose, containing ascorbic acid as an interfering substance, 31 is used as the sample liquid, and the sample liquid supply port 1 is used as the sample liquid.
- a system that detects the supply of the solution based on the electrical change between the counter electrode 6 and the third electrode 8 of the electrode system operates. This caused the measurement timer to start. At this time, the potential is applied between the counter electrode 6 and the third electrode 8 and continues to be applied. Further, two seconds after the detection of the supply of the sample liquid, the B potential applied to the third electrode 8 was stepped to 1300 mV.
- the current value between the first electrode and the third electrode 8 was measured.
- the current value immediately before stepping the potential to 1300 mV mainly depends on the concentration of ascorbic acid.
- the current value 3 seconds after stepping to 110 OmV mainly depends on the concentration of dissolved oxygen contained in the sample solution.
- 50 OmV is applied to the working electrode 7 with reference to the third electrode 8 for 5 seconds between the counter electrode 6 and the working electrode 7. The current value was measured later.
- the current value between the counter electrode 6 and the third electrode 8 mainly reflects the concentrations of ascorbic acid and dissolved oxygen.
- the concentration of both substances can be obtained based on the current value. Therefore, by correcting the measurement results based on the results, the effects of ascorbic acid and dissolved oxygen are removed, and accurate glucose conversion is achieved. Can be determined.
- the supply of the sample solution is detected and the third electrode 8 is applied to the third electrode 8 for detecting ascorbic acid or dissolved oxygen.
- the potential was set at 50 OmV, and the potential was set at 130 OmV, but it is not limited to this, and the action to obtain the response current
- the applied potential to pole 7 was set at 50 OmV, but is not limited to this, and the reduced form of the electron carrier resulting from a series of reactions was oxidized. As long as the potential is as high as possible, the time for measuring the current value is not limited to the above embodiment.
- carboxymethylcellulose was used as the hydrophilic high molecular weight, but the hydrophilic high molecular weight layer forming the hydrophilic high molecular weight layer was used.
- a variety of substances can be used for high-potential molecules. For example, hydroxyethyl cellulose, hydroxypropyl cellulose, methylcellulose, ethylcellulose , Ethyl hydroxyethyl cellulose, carboxyl methyl cellulose, polyvinyl polypyridone, polyvinyl Polyamino acids such as rualcohol and polylysine, polystyrene sulfonate, gelatin and its derivatives, polyacrylyl Acids and their salts, polymethacrylic acid and its salts, starch and its derivatives, anhydrous maleic acid Alternatively, a polymer of a salt thereof is obtained. Of these, carboxymethylcellulose, hydroxypropyl cellulose, and hydroxypropyl cellulose are preferred.
- the oxidoreductase contained in the reaction layer is selected according to the substrate contained in the sample solution.
- oxidoreductases include, for example, fructosylhydrogenase, dalcoxidase, alcohol oxidase, and lactate. And cholesterol oxidase, xanthine oxidase, amino acid oxidase and the like.
- Electron carriers include potassium ferricyanide, P-benzoquinone, phenazine metsulfurate, methylene blue, and phenylene. Mouth-sene derivatives are required. One or more of these electron carriers are used.
- the above enzyme and electron carrier may be dissolved in the sample solution, and the reaction layer is fixed to a substrate or the like so that it does not dissolve in the sample solution. Is also good.
- the reaction layer preferably contains the above hydrophilic high molecule.
- the electrode shape, the arrangement of the electrodes and the leads, and the like are not limited to these.
- the power electrode has been described as the electrode material of the third electrode, the present invention is not limited to this, and other conductive materials and silver may be used. Z-silver chloride electrode can be used. Industrial applicability
Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP99910795A EP0987544B1 (en) | 1998-04-02 | 1999-03-31 | Substrate determining method |
US09/424,715 US6340428B1 (en) | 1998-04-02 | 1999-03-31 | Device and method for determining the concentration of a substrate |
DE69937326T DE69937326T2 (de) | 1998-04-02 | 1999-03-31 | Verfahren zur bestimmung eines substrates |
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP10/89740 | 1998-04-02 | ||
JP8974098 | 1998-04-02 | ||
JP17276698A JP3267933B2 (ja) | 1998-01-27 | 1998-06-19 | 基質の定量法 |
JP10/172766 | 1998-06-19 |
Related Child Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/424,715 A-371-Of-International US6340428B1 (en) | 1998-04-02 | 1999-03-31 | Device and method for determining the concentration of a substrate |
US10/023,734 Division US6790327B2 (en) | 1998-04-02 | 2001-12-21 | Device and method for determining the concentration of a substrate |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1999051974A1 true WO1999051974A1 (fr) | 1999-10-14 |
Family
ID=26431146
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/JP1999/001706 WO1999051974A1 (fr) | 1998-04-02 | 1999-03-31 | Procede de determination d'un substrat |
Country Status (5)
Country | Link |
---|---|
US (2) | US6340428B1 (ja) |
EP (1) | EP0987544B1 (ja) |
CN (1) | CN1122178C (ja) |
DE (1) | DE69937326T2 (ja) |
WO (1) | WO1999051974A1 (ja) |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6978912B2 (en) | 2002-08-02 | 2005-12-27 | Conair Corporation | Heated dispenser |
US9410915B2 (en) | 2004-06-18 | 2016-08-09 | Roche Operations Ltd. | System and method for quality assurance of a biosensor test strip |
Families Citing this family (152)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6001067A (en) | 1997-03-04 | 1999-12-14 | Shults; Mark C. | Device and method for determining analyte levels |
US7657297B2 (en) * | 2004-05-03 | 2010-02-02 | Dexcom, Inc. | Implantable analyte sensor |
US7899511B2 (en) | 2004-07-13 | 2011-03-01 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
US8527026B2 (en) | 1997-03-04 | 2013-09-03 | Dexcom, Inc. | Device and method for determining analyte levels |
US6036924A (en) | 1997-12-04 | 2000-03-14 | Hewlett-Packard Company | Cassette of lancet cartridges for sampling blood |
US8071384B2 (en) | 1997-12-22 | 2011-12-06 | Roche Diagnostics Operations, Inc. | Control and calibration solutions and methods for their use |
US7407811B2 (en) * | 1997-12-22 | 2008-08-05 | Roche Diagnostics Operations, Inc. | System and method for analyte measurement using AC excitation |
US7390667B2 (en) * | 1997-12-22 | 2008-06-24 | Roche Diagnostics Operations, Inc. | System and method for analyte measurement using AC phase angle measurements |
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 |
EP0987544B1 (en) * | 1998-04-02 | 2007-10-17 | Matsushita Electric Industrial Co., Ltd. | Substrate determining method |
US8688188B2 (en) | 1998-04-30 | 2014-04-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8974386B2 (en) | 1998-04-30 | 2015-03-10 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8346337B2 (en) | 1998-04-30 | 2013-01-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8465425B2 (en) | 1998-04-30 | 2013-06-18 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US9066695B2 (en) | 1998-04-30 | 2015-06-30 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US6949816B2 (en) | 2003-04-21 | 2005-09-27 | Motorola, Inc. | Semiconductor component having first surface area for electrically coupling to a semiconductor chip and second surface area for electrically coupling to a substrate, and method of manufacturing same |
US8480580B2 (en) | 1998-04-30 | 2013-07-09 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US6175752B1 (en) | 1998-04-30 | 2001-01-16 | Therasense, Inc. | Analyte monitoring device and methods of use |
US6591125B1 (en) | 2000-06-27 | 2003-07-08 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
US6849185B1 (en) * | 1999-05-14 | 2005-02-01 | Pall Corp | Charged membrane |
US6841052B2 (en) | 1999-08-02 | 2005-01-11 | Bayer Corporation | Electrochemical-sensor design |
US20050103624A1 (en) | 1999-10-04 | 2005-05-19 | Bhullar Raghbir S. | Biosensor and method of making |
US6858433B1 (en) * | 2000-04-03 | 2005-02-22 | Roche Diagnostics Operations, Inc. | Biosensor electromagnetic noise cancellation |
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 |
US6560471B1 (en) | 2001-01-02 | 2003-05-06 | Therasense, Inc. | Analyte monitoring device and methods of use |
US6960287B2 (en) | 2001-06-11 | 2005-11-01 | Bayer Corporation | Underfill detection system for a test sensor |
US7981056B2 (en) | 2002-04-19 | 2011-07-19 | Pelikan Technologies, Inc. | Methods and apparatus for lancet actuation |
EP1404232B1 (en) | 2001-06-12 | 2009-12-02 | Pelikan Technologies Inc. | Blood sampling apparatus and method |
US9226699B2 (en) | 2002-04-19 | 2016-01-05 | Sanofi-Aventis Deutschland Gmbh | Body fluid sampling module with a continuous compression tissue interface surface |
US8337419B2 (en) | 2002-04-19 | 2012-12-25 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
US7316700B2 (en) | 2001-06-12 | 2008-01-08 | Pelikan Technologies, Inc. | Self optimizing lancing device with adaptation means to temporal variations in cutaneous properties |
US9427532B2 (en) | 2001-06-12 | 2016-08-30 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
ES2357887T3 (es) | 2001-06-12 | 2011-05-03 | Pelikan Technologies Inc. | Aparato para mejorar la tasa de éxito de obtención de sangre a partir de una punción capilar. |
AU2002348683A1 (en) | 2001-06-12 | 2002-12-23 | Pelikan Technologies, Inc. | Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge |
WO2002100460A2 (en) | 2001-06-12 | 2002-12-19 | Pelikan Technologies, Inc. | Electric lancet actuator |
US9795747B2 (en) | 2010-06-02 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | Methods and apparatus for lancet actuation |
US7041068B2 (en) | 2001-06-12 | 2006-05-09 | Pelikan Technologies, Inc. | Sampling module device and method |
DE60237463D1 (de) * | 2001-11-16 | 2010-10-07 | Roche Diagnostics Gmbh | Flexibler sensor und herstellungsverfahren |
US8858434B2 (en) | 2004-07-13 | 2014-10-14 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7379765B2 (en) | 2003-07-25 | 2008-05-27 | Dexcom, Inc. | Oxygen enhancing membrane systems for implantable devices |
WO2003076919A1 (fr) * | 2002-03-08 | 2003-09-18 | Matsushita Electric Industrial Co., Ltd. | Procede de determination de substrat |
US7648468B2 (en) | 2002-04-19 | 2010-01-19 | Pelikon 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 |
US9248267B2 (en) | 2002-04-19 | 2016-02-02 | Sanofi-Aventis Deustchland Gmbh | Tissue penetration device |
US7901362B2 (en) | 2002-04-19 | 2011-03-08 | 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 |
US7491178B2 (en) | 2002-04-19 | 2009-02-17 | Pelikan 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 |
US8360992B2 (en) | 2002-04-19 | 2013-01-29 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
US7909778B2 (en) | 2002-04-19 | 2011-03-22 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7175642B2 (en) | 2002-04-19 | 2007-02-13 | Pelikan Technologies, Inc. | Methods and apparatus for lancet actuation |
US7547287B2 (en) | 2002-04-19 | 2009-06-16 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US9795334B2 (en) | 2002-04-19 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | 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 |
US8221334B2 (en) | 2002-04-19 | 2012-07-17 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
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 |
US7232451B2 (en) | 2002-04-19 | 2007-06-19 | 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 |
US7291117B2 (en) | 2002-04-19 | 2007-11-06 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7708701B2 (en) | 2002-04-19 | 2010-05-04 | Pelikan Technologies, Inc. | Method and apparatus for a multi-use body fluid sampling device |
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 |
US9314194B2 (en) | 2002-04-19 | 2016-04-19 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
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 |
US7229458B2 (en) | 2002-04-19 | 2007-06-12 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
KR100485671B1 (ko) * | 2002-09-30 | 2005-04-27 | 주식회사 인포피아 | 바이오 센서의 시료 반응결과 측정장치 및 그 방법 |
EP1574848A1 (en) * | 2002-12-20 | 2005-09-14 | Matsushita Electric Industrial Co., Ltd. | Biosensor |
US8574895B2 (en) | 2002-12-30 | 2013-11-05 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus using optical techniques to measure analyte levels |
US20040238359A1 (en) * | 2003-05-28 | 2004-12-02 | Matsushita Electric Industrial Co., Ltd. | Biosensor |
ES2347248T3 (es) | 2003-05-30 | 2010-10-27 | Pelikan Technologies Inc. | Procedimiento y aparato para la inyeccion de fluido. |
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 |
US8206565B2 (en) | 2003-06-20 | 2012-06-26 | Roche Diagnostics Operation, Inc. | System and method for coding information on a biosensor test strip |
US7645421B2 (en) | 2003-06-20 | 2010-01-12 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
US7597793B2 (en) * | 2003-06-20 | 2009-10-06 | Roche Operations Ltd. | System and method for analyte measurement employing maximum dosing time delay |
PL1639354T3 (pl) | 2003-06-20 | 2018-11-30 | F.Hoffmann-La Roche Ag | Pasek testowy z otworem szczeliny wentylacyjnej |
US7718439B2 (en) | 2003-06-20 | 2010-05-18 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
US8058077B2 (en) | 2003-06-20 | 2011-11-15 | Roche Diagnostics Operations, Inc. | Method for coding information on a biosensor test strip |
US7645373B2 (en) | 2003-06-20 | 2010-01-12 | Roche Diagnostic Operations, Inc. | System and method for coding information on a biosensor test strip |
US8679853B2 (en) * | 2003-06-20 | 2014-03-25 | Roche Diagnostics Operations, Inc. | Biosensor with laser-sealed capillary space and method of making |
US8148164B2 (en) | 2003-06-20 | 2012-04-03 | Roche Diagnostics Operations, Inc. | System and method for determining the concentration of an analyte in a sample fluid |
US7488601B2 (en) | 2003-06-20 | 2009-02-10 | Roche Diagnostic Operations, Inc. | System and method for determining an abused sensor during analyte measurement |
US8071030B2 (en) | 2003-06-20 | 2011-12-06 | Roche Diagnostics Operations, Inc. | Test strip with flared sample receiving chamber |
US7452457B2 (en) * | 2003-06-20 | 2008-11-18 | Roche Diagnostics Operations, Inc. | System and method for analyte measurement using dose sufficiency electrodes |
US7591801B2 (en) | 2004-02-26 | 2009-09-22 | Dexcom, Inc. | Integrated delivery device for continuous glucose sensor |
US20190357827A1 (en) | 2003-08-01 | 2019-11-28 | Dexcom, Inc. | Analyte sensor |
US7519408B2 (en) | 2003-11-19 | 2009-04-14 | Dexcom, Inc. | Integrated receiver for continuous analyte sensor |
US7920906B2 (en) | 2005-03-10 | 2011-04-05 | Dexcom, Inc. | System and methods for processing analyte sensor data for sensor calibration |
WO2005033659A2 (en) | 2003-09-29 | 2005-04-14 | Pelikan Technologies, Inc. | Method and apparatus for an improved sample capture device |
US9351680B2 (en) | 2003-10-14 | 2016-05-31 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for a variable user interface |
ES2285536T3 (es) * | 2003-10-31 | 2007-11-16 | Lifescan Scotland Ltd | Metodo para reducir el efecto de una corriente de interferencia directa en una tira de ensayo electroquimica. |
US7655119B2 (en) * | 2003-10-31 | 2010-02-02 | Lifescan Scotland Limited | Meter for use in an improved method of reducing interferences in an electrochemical sensor using two different applied potentials |
US9247900B2 (en) | 2004-07-13 | 2016-02-02 | Dexcom, Inc. | Analyte sensor |
US8535497B2 (en) | 2003-12-04 | 2013-09-17 | Panasonic Corporation | Method of measuring blood component, sensor used in the method, and measuring device |
CN100432663C (zh) * | 2003-12-04 | 2008-11-12 | 松下电器产业株式会社 | 血细胞比容(Hct)的测定方法及该方法中使用的传感器和测定装置 |
US8423114B2 (en) | 2006-10-04 | 2013-04-16 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US11633133B2 (en) | 2003-12-05 | 2023-04-25 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8532730B2 (en) | 2006-10-04 | 2013-09-10 | Dexcom, Inc. | Analyte sensor |
US8364231B2 (en) | 2006-10-04 | 2013-01-29 | Dexcom, Inc. | Analyte sensor |
EP1711790B1 (en) | 2003-12-05 | 2010-09-08 | DexCom, Inc. | Calibration techniques for a continuous analyte sensor |
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 |
WO2005078118A1 (en) | 2004-02-06 | 2005-08-25 | Bayer Healthcare Llc | Oxidizable species as an internal reference for biosensors and method of use |
US8808228B2 (en) * | 2004-02-26 | 2014-08-19 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
EP1742045B1 (en) * | 2004-04-19 | 2016-11-02 | Panasonic Healthcare Holdings Co., Ltd. | Method for measuring blood components and biosensor and measuring instrument for use therein |
US8277713B2 (en) | 2004-05-03 | 2012-10-02 | Dexcom, Inc. | Implantable analyte sensor |
US8792955B2 (en) | 2004-05-03 | 2014-07-29 | Dexcom, Inc. | Transcutaneous analyte sensor |
EP1739407B1 (en) * | 2004-05-06 | 2018-05-30 | Panasonic Intellectual Property Management Co., Ltd. | Sensor, measuring equipment and measuring method |
US8828203B2 (en) | 2004-05-20 | 2014-09-09 | Sanofi-Aventis Deutschland Gmbh | Printable hydrogels for biosensors |
US9775553B2 (en) | 2004-06-03 | 2017-10-03 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for a fluid sampling device |
EP1765194A4 (en) | 2004-06-03 | 2010-09-29 | Pelikan Technologies Inc | METHOD AND APPARATUS FOR MANUFACTURING A DEVICE FOR SAMPLING LIQUIDS |
US7556723B2 (en) * | 2004-06-18 | 2009-07-07 | Roche Diagnostics Operations, Inc. | Electrode design for biosensor |
US20060003400A1 (en) * | 2004-06-30 | 2006-01-05 | Byrd Patricia A | Methods and compositions for characterizing a redox reagent system enzyme |
US7905833B2 (en) | 2004-07-13 | 2011-03-15 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7857760B2 (en) * | 2004-07-13 | 2010-12-28 | Dexcom, Inc. | Analyte sensor |
US20060270922A1 (en) | 2004-07-13 | 2006-11-30 | Brauker James H | Analyte sensor |
US8652831B2 (en) | 2004-12-30 | 2014-02-18 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for analyte measurement test time |
US8744546B2 (en) | 2005-05-05 | 2014-06-03 | Dexcom, Inc. | Cellulosic-based resistance domain for an analyte sensor |
US20070017824A1 (en) * | 2005-07-19 | 2007-01-25 | Rippeth John J | Biosensor and method of manufacture |
WO2007013915A1 (en) | 2005-07-20 | 2007-02-01 | Bayer Healthcare Llc | Gated amperometry |
US8430999B2 (en) * | 2005-09-02 | 2013-04-30 | Arkray, Inc. | Method for detecting sample supply condition, and analyzer |
CN101273266B (zh) | 2005-09-30 | 2012-08-22 | 拜尔健康护理有限责任公司 | 门控伏特安培法 |
US8057404B2 (en) * | 2005-10-12 | 2011-11-15 | Panasonic Corporation | Blood sensor, blood testing apparatus, and method for controlling blood testing apparatus |
US9757061B2 (en) | 2006-01-17 | 2017-09-12 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
EP2069772B1 (en) | 2006-10-04 | 2014-05-21 | DexCom, Inc. | Dual electrode system for a continuous analyte sensor |
KR100829400B1 (ko) * | 2006-11-30 | 2008-05-15 | 주식회사 인포피아 | 바이오센서 |
ES2627188T3 (es) * | 2007-05-18 | 2017-07-27 | Aytu Bioscience, Inc. | Medición y usos del estado oxidativo |
US8709709B2 (en) | 2007-05-18 | 2014-04-29 | Luoxis Diagnostics, Inc. | Measurement and uses of oxidative status |
US20080306434A1 (en) | 2007-06-08 | 2008-12-11 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
EP4159114B1 (en) | 2007-10-09 | 2024-04-10 | DexCom, Inc. | Integrated insulin delivery system with continuous glucose sensor |
TWI460423B (zh) | 2007-10-31 | 2014-11-11 | Arkray Inc | Biosensor and its manufacturing method |
WO2009076302A1 (en) | 2007-12-10 | 2009-06-18 | Bayer Healthcare Llc | Control markers for auto-detection of control solution and methods of use |
EP2261646B1 (en) * | 2008-03-27 | 2015-07-29 | Panasonic Healthcare Holdings Co., Ltd. | Measurement device, measurement system, and concentration measurement method |
US9386944B2 (en) | 2008-04-11 | 2016-07-12 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for analyte detecting device |
US8560039B2 (en) | 2008-09-19 | 2013-10-15 | Dexcom, Inc. | Particle-containing membrane and particulate electrode for analyte sensors |
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 |
CN103487476B (zh) * | 2009-05-25 | 2015-09-09 | 利多(香港)有限公司 | 生物传感器 |
US8691075B2 (en) | 2009-12-30 | 2014-04-08 | Roche Diagnostics Operations, Inc. | Method for measuring analyte concentration in a liquid sample |
US8965476B2 (en) | 2010-04-16 | 2015-02-24 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
JP5973444B2 (ja) | 2010-09-13 | 2016-08-23 | ライフスキャン・スコットランド・リミテッド | ヘマトクリット補正を有する分析物測定方法及びシステム |
ES2658709T3 (es) | 2011-02-28 | 2018-03-12 | Aytu Bioscience, Inc. | Aparato para medir el potencial oxidación-reducción |
WO2012142502A2 (en) | 2011-04-15 | 2012-10-18 | Dexcom Inc. | Advanced analyte sensor calibration and error detection |
JP5708878B2 (ja) * | 2012-03-15 | 2015-04-30 | 株式会社村田製作所 | バイオセンサおよびその製造方法 |
WO2013158985A1 (en) | 2012-04-19 | 2013-10-24 | Luoxis Diagnostics, Inc. | Multiple layer gel |
GB2505694B (en) * | 2012-09-07 | 2017-03-22 | Lifescan Scotland Ltd | Electrochemical-based analytical test strip with bare interferent electrodes |
CN104737014B (zh) | 2012-10-23 | 2018-03-27 | 艾图生物科学股份有限公司 | 测量和使用生物样品的氧化还原电位的方法和系统 |
CN104535631B (zh) * | 2015-01-20 | 2017-03-15 | 三诺生物传感股份有限公司 | 一种电化学测量方法 |
US11331022B2 (en) | 2017-10-24 | 2022-05-17 | Dexcom, Inc. | Pre-connected analyte sensors |
CN212438615U (zh) | 2017-10-24 | 2021-02-02 | 德克斯康公司 | 可穿戴设备 |
Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH02310457A (ja) * | 1989-05-26 | 1990-12-26 | Matsushita Electric Ind Co Ltd | バイオセンサ |
JPH0354447A (ja) * | 1989-04-18 | 1991-03-08 | Matsushita Electric Ind Co Ltd | バイオセンサおよびその製造法 |
JPH05340915A (ja) * | 1991-10-18 | 1993-12-24 | Matsushita Electric Ind Co Ltd | バイオセンサおよびそれを用いた測定方法 |
JPH06109693A (ja) * | 1992-09-30 | 1994-04-22 | Matsushita Electric Ind Co Ltd | バイオセンサおよびそれを用いた測定方法 |
JPH08320304A (ja) * | 1995-03-17 | 1996-12-03 | Matsushita Electric Ind Co Ltd | バイオセンサ、それを用いた定量法および定量装置 |
JPH09101280A (ja) * | 1995-10-05 | 1997-04-15 | Casio Comput Co Ltd | バイオセンサ |
JPH09201337A (ja) * | 1996-01-25 | 1997-08-05 | Casio Comput Co Ltd | グルコース測定装置 |
JPH1019832A (ja) * | 1996-06-28 | 1998-01-23 | Nok Corp | 酸化還元酵素固定化バイオセンサを用いる濃度測定方法 |
Family Cites Families (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN1018387B (zh) * | 1990-11-23 | 1992-09-23 | 浙江大学 | 检测溶解氧的多电极传感器 |
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 |
US5582697A (en) * | 1995-03-17 | 1996-12-10 | Matsushita Electric Industrial Co., Ltd. | Biosensor, and a method and a device for quantifying a substrate in a sample liquid using the same |
EP0987544B1 (en) * | 1998-04-02 | 2007-10-17 | Matsushita Electric Industrial Co., Ltd. | Substrate determining method |
-
1999
- 1999-03-31 EP EP99910795A patent/EP0987544B1/en not_active Expired - Lifetime
- 1999-03-31 US US09/424,715 patent/US6340428B1/en not_active Expired - Lifetime
- 1999-03-31 DE DE69937326T patent/DE69937326T2/de not_active Expired - Lifetime
- 1999-03-31 WO PCT/JP1999/001706 patent/WO1999051974A1/ja active IP Right Grant
- 1999-03-31 CN CN99800436A patent/CN1122178C/zh not_active Expired - Lifetime
-
2001
- 2001-12-21 US US10/023,734 patent/US6790327B2/en not_active Expired - Lifetime
Patent Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH0354447A (ja) * | 1989-04-18 | 1991-03-08 | Matsushita Electric Ind Co Ltd | バイオセンサおよびその製造法 |
JPH02310457A (ja) * | 1989-05-26 | 1990-12-26 | Matsushita Electric Ind Co Ltd | バイオセンサ |
JPH05340915A (ja) * | 1991-10-18 | 1993-12-24 | Matsushita Electric Ind Co Ltd | バイオセンサおよびそれを用いた測定方法 |
JPH06109693A (ja) * | 1992-09-30 | 1994-04-22 | Matsushita Electric Ind Co Ltd | バイオセンサおよびそれを用いた測定方法 |
JPH08320304A (ja) * | 1995-03-17 | 1996-12-03 | Matsushita Electric Ind Co Ltd | バイオセンサ、それを用いた定量法および定量装置 |
JPH09101280A (ja) * | 1995-10-05 | 1997-04-15 | Casio Comput Co Ltd | バイオセンサ |
JPH09201337A (ja) * | 1996-01-25 | 1997-08-05 | Casio Comput Co Ltd | グルコース測定装置 |
JPH1019832A (ja) * | 1996-06-28 | 1998-01-23 | Nok Corp | 酸化還元酵素固定化バイオセンサを用いる濃度測定方法 |
Non-Patent Citations (1)
Title |
---|
See also references of EP0987544A4 * |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6978912B2 (en) | 2002-08-02 | 2005-12-27 | Conair Corporation | Heated dispenser |
US9410915B2 (en) | 2004-06-18 | 2016-08-09 | Roche Operations Ltd. | System and method for quality assurance of a biosensor test strip |
Also Published As
Publication number | Publication date |
---|---|
EP0987544A4 (en) | 2004-07-21 |
DE69937326D1 (de) | 2007-11-29 |
US6790327B2 (en) | 2004-09-14 |
US6340428B1 (en) | 2002-01-22 |
CN1122178C (zh) | 2003-09-24 |
EP0987544A1 (en) | 2000-03-22 |
CN1262739A (zh) | 2000-08-09 |
EP0987544B1 (en) | 2007-10-17 |
DE69937326T2 (de) | 2008-07-17 |
US20020043471A1 (en) | 2002-04-18 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
WO1999051974A1 (fr) | Procede de determination d'un substrat | |
JP3267936B2 (ja) | バイオセンサ | |
JP3690683B2 (ja) | バイオセンサ | |
JP3297630B2 (ja) | バイオセンサ | |
JP3375040B2 (ja) | 基質の定量法 | |
JP3874321B2 (ja) | バイオセンサ | |
JP3102627B2 (ja) | バイオセンサ、それを用いた定量法および定量装置 | |
JP2001183330A (ja) | バイオセンサ | |
WO2002008743A1 (fr) | Biocapteur | |
JP2001330581A (ja) | 基質濃度定量法 | |
JP3267933B2 (ja) | 基質の定量法 | |
JP3437016B2 (ja) | バイオセンサおよびそれを用いた基質の定量方法 | |
JP3267907B2 (ja) | バイオセンサおよびそれを用いた基質の定量法 | |
JP2001249103A (ja) | バイオセンサ | |
JP2000180399A (ja) | 基質の定量方法 | |
JP2002181757A (ja) | バイオセンサおよび基質の測定方法 | |
JP2001201480A (ja) | バイオセンサ | |
JP3245103B2 (ja) | バイオセンサおよびそれを用いた基質の定量法 | |
JP4036883B2 (ja) | バイオセンサ | |
JP2007256069A (ja) | バイオセンサーの測定方法 | |
JP3487064B2 (ja) | 基質の定量法 | |
JPH08338824A (ja) | バイオセンサ、バイオセンサの製造方法および特定化合物の定量法 | |
JPH10282037A (ja) | 生体成分中の基質の定量法 | |
JP2005010150A (ja) | バイオセンサ | |
JP2003270197A (ja) | バイオセンサ |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
WWE | Wipo information: entry into national phase |
Ref document number: 99800436.7 Country of ref document: CN |
|
AK | Designated states |
Kind code of ref document: A1 Designated state(s): CN US |
|
AL | Designated countries for regional patents |
Kind code of ref document: A1 Designated state(s): AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE |
|
WWE | Wipo information: entry into national phase |
Ref document number: 1999910795 Country of ref document: EP |
|
WWE | Wipo information: entry into national phase |
Ref document number: 09424715 Country of ref document: US |
|
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
WWP | Wipo information: published in national office |
Ref document number: 1999910795 Country of ref document: EP |
|
WWG | Wipo information: grant in national office |
Ref document number: 1999910795 Country of ref document: EP |