WO2003005015A1 - Glucose strip sensor and glucose measurement method using the glucose strip sensor - Google Patents
Glucose strip sensor and glucose measurement method using the glucose strip sensor Download PDFInfo
- Publication number
- WO2003005015A1 WO2003005015A1 PCT/KR2001/001702 KR0101702W WO03005015A1 WO 2003005015 A1 WO2003005015 A1 WO 2003005015A1 KR 0101702 W KR0101702 W KR 0101702W WO 03005015 A1 WO03005015 A1 WO 03005015A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- electrode
- glucose
- checking
- sensor
- blood sample
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/14—Devices for taking samples of blood ; Measuring characteristics of blood in vivo, e.g. gas concentration within the blood, pH-value of blood
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
- G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
- G01N27/28—Electrolytic cell components
- G01N27/30—Electrodes, e.g. test electrodes; Half-cells
- G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
- G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
- G01N27/3272—Test elements therefor, i.e. disposable laminated substrates with electrodes, reagent and channels
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
- G01N33/66—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving blood sugars, e.g. galactose
Definitions
- the present invention relates to a disposable glucose strip sensor configured to rapidly and conveniently measure the concentration of glucose in blood and a glucose measurement method using the glucose strip sensor.
- Known glucose measurement methods are based on oxidation of glucose by glucose-oxidase and peroxidase. They also use orthotolidine or a benzidine-based mixture as an indicator reagent, that is, a chromogen. In accordance with these methods, a color transition of the indicator reagent resulting from the oxidation of glucose is observed to measure the concentration of glucose in blood.
- an indicator reagent that is, a chromogen
- a solution which has a composition including: glucose oxidase and peroxidase as enzymes; a citric acid buffer to maintain a pH of 6.0; gelatin, alginic acid, polyvinylpyrrolidone, and polyvinyl alcohol as stabilizers; and orthotolidine, benzidine, 3-aminopropylcarbarsone, and 2 , 7-diaminofluorene as a chromogen.
- the solution is impregnated into a cellulose paper which has a desired thickness and size to be used as a carrier, and then dried.
- 85-1297 discloses a method for manufacturing a glucose-measuring test piece, to which the basic principle of an enzymatic measurement method using glucose oxidase and peroxidase is applied.
- concentration of glucose in blood is measured using the above mentioned glucose-measuring test pieces, it is difficult to accurately measure a glucose concentration because the measurement is based on a color transition exhibited on the test piece .
- glucose contained in the blood sample is oxidized by a glucose-oxidizing enzyme contained in the reaction layer.
- the glucose-oxidizing enzyme is reduced.
- the reduced glucose-oxidizing enzyme is then oxidized by an electron acceptor, whereby the electron acceptor is reduced.
- the reduced electron acceptor donates electrons at the surface of an electrode to which a desired voltage is applied.
- the electron acceptor is electrochemically reoxidized.
- the concentration of glucose in the blood sample is proportional to the amount of current generated during the process in which the electron acceptor is oxidized. Accordingly, the concentration of glucose can be measured by measuring the amount of current .
- FIG. 1 An example of the above mentioned glucose-measuring sensor is disclosed in Japanese Patent Laid-open Publication No. 61-294351.
- This sensor is illustrated in Fig. 1.
- operating and counter electrodes which are made of carbon or the like, are formed on a substrate 111 in a screen printing fashion.
- An insulator 115 is also formed on the substrate 111 while allowing the electrodes to be partially exposed.
- a porous reaction layer 117 which contains a reactive material such as a glucose-oxidizing enzyme and an electron acceptor, is arranged on the insulator 115.
- a holding frame 116 and a cover 118 are arranged on the insulator 115.
- reference numerals 112, 113, and 114 denote the operating and counter electrodes
- reference numerals 112', 113', and 114' denote the exposed portions of the operating and counter electrodes .
- These electrodes and electrode portions form an electrode system.
- this glucose-measuring sensor however, the amount of blood absorbed in the reaction layer 117 varies depending on the amount of the blood sample dropped onto the reaction layer 117. As a result, measurement errors may be caused by a variation in the amount of blood absorbed in the reaction layer 117.
- a biosensor has been proposed.
- An example of such a biosensor is disclosed in U.S. Patent No. 5,120,420 and illustrated in Fig. 2. As shown in Fig. 2, this biosensor includes a non-conductive substrate 211 made of polyethylene terephthalate . Silver is screen-printed on the non-conductive substrate 211 to form leads 212 and 213.
- Conductive carbon paste containing a resin binder is printed on the leads 212 and 213, thereby forming an operating electrode 214 and a counter electrode 215.
- An insulator 216 is then printed to allow the electrodes 214 and 215 to be partially exposed.
- a 0.5% aqueous solution of carboxymethyl cellulose (CMC) is spread onto the electrodes 214 and 215, and dried to form a CMC layer.
- the enzyme in a phosphate buffer solution is spread on the CMC layer, and dried to form a main reaction layer comprised of a CMC-GOD layer.
- a resin plate 217 and a cover 219 are attached to the resulting structure while defining a space 218.
- the reference numeral 220 denotes a sample introducing port
- the reference numeral 221 denotes a discharge port.
- the biosensor having the above mentioned structure, when a sample solution comes into contact with the sample introducing port 220, it is introduced into the space 218 by virtue of capillary phenomenon, so that it fills the space 218. Simultaneously, air existing in the space 218 is vented from the space 218 through the discharge port 221 formed opposite to the sample introducing port 220 or at the cover 219.
- the discharge port 221 is arranged at the upper surface of the biosensor, measurement errors may occur when the user unintentionally touches the discharge port 221. For this reason, there is inconvenience in handling the biosensor.
- the user can check whether or not a sufficient amount of sample solution is introduced in the biosensor, only with the naked eye. So, the measurement may be carried out even when an insufficient amount of sample solution is filled in the biosensor. In this case, however, the detected glucose level may erroneously be lower than the actual glucose concentration.
- the present invention has been made in view of the above mentioned problems involved with the conventional glucose- measuring sensors, and an object of the invention is to provide a glucose strip sensor including a sample introducing port arranged at a front surface of the sensor, and discharge ports respectively arranged at opposite side surfaces of the sensor, thereby being capable of achieving convenience in handling the sensor, while additionally including a checking electrode adapted, alone or along with a counter electrode, to determine whether or not a sufficient amount of blood sample is introduced in the sensor, thereby being capable of achieving an accurate glucose measurement, and to provide a glucose measurement method using the glucose strip sensor.
- the present invention provides a glucose strip sensor comprising a non-conductive substrate, a lead section formed on the substrate, the lead section including leads and lead terminals, an electrode section formed on the lead section and provided at an upper surface thereof with a reaction layer, the electrode section including an operating electrode, a counter electrode, and a checking electrode, a resin plate adapted to define, over the electrode section, a space for receiving a blood sample, a cover formed on the resin plate, a sample introducing port adapted to introduce the blood sample into the space, and discharge ports adapted to vent air from the space, wherein: the electrode section further includes at least one checking electrode adapted to check whether or not the blood sample is completely introduced in the space; and the lead section further includes a lead and a lead terminal for the checking electrode .
- the sample introducing port may be arranged at a front surface of the sensor, and the discharge ports are arranged at opposite side surfaces of the sensor, respectively.
- the present invention provides a glucose measurement method comprising the steps of checking whether or not an electrical connection is established between the counter electrode and the checking electrode included in the glucose strip sensor or between the checking electrode and another checking electrode, thereby determining whether or not a blood sample is introduced in the space in a sufficient amount; and if it is determined the blood sample is introduced in the space in a sufficient amount, then measuring a glucose concentration of the blood sample in accordance with a well-known method.
- Fig. 1 is an exploded perspective view illustrating a conventional sample-dropped glucose-measuring test piece
- Fig. 2 is an exploded perspective view illustrating a conventional glucose-measuring biosensor utilizing capillary phenomenon
- Fig. 3 is an exploded perspective view illustrating a glucose strip sensor according to an embodiment of the present invention.
- Fig. 4 is a sectional view of the glucose strip sensor illustrated in Fig. 3;
- Fig. 5 is an assembled perspective view of the glucose strip sensor illustrated in Fig. 3;
- Fig. 6 is a perspective view illustrating an electrode arrangement in the glucose strip sensor according to the present invention;
- Fig. 7 is a perspective view illustrating another electrode arrangement in the glucose strip sensor according to the present invention.
- Fig. 8 is a graph depicting the correlation of a signal generated by the glucose strip sensor according to the present invention with respect to glucose concentration.
- Fig. 3 is an exploded perspective view illustrating a glucose strip sensor according to an embodiment of the present invention.
- Fig. 4 is a sectional view of the glucose strip sensor illustrated in Fig. 3.
- Fig. 5 is an assembled perspective view of the glucose strip sensor illustrated in Fig. 3.
- the glucose strip sensor includes a non-conductive substrate 10, a lead section 20 formed on the substrate 10 by a silver ink or an ink mixture of silver and silver chloride, and an electrode section 30 formed on the lead section 20.
- the lead section 20 includes leads 21 and lead terminals 22, whereas the electrode section 30 includes an operating electrode 31, a counter electrode 32, and a checking electrode 33.
- the glucose strip sensor also includes an insulating layer 40 coated on the lead and electrode sections 20 and 30 while allowing the lead and electrode sections 20 and 30 to be partially exposed, a reaction layer 50 formed on the exposed portion of the electrode section 30, a resin plate 60 formed on the structure obtained after the formation of the reaction layer 50, and a cover 70 formed on the resin plate 60.
- the resin plate 60 defines a space 63, a sample introducing port 61, and discharge ports 62.
- the sample introducing port 61 is arranged at the front surface of the glucose strip sensor, whereas the discharge ports 62 are arranged at opposite side surfaces of the glucose strip sensor, respectively.
- the glucose strip sensor of the present invention is characterized in that it includes, in addition to the operating electrode 31 and counter electrode 32, the checking electrode 33 for checking whether or not a sample is completely introduced in the sensor.
- the glucose strip sensor of the present invention is also characterized in that the sample introducing port 61 is arranged at the front surface of the glucose strip sensor, whereas the discharge ports 62 are arranged at opposite side surfaces of the glucose strip sensor, respectively.
- the substrate 10 is prepared.
- a polymer substrate may be used which is made of a non- conductive material such as polyethylene terephthalate, polyvinyl chloride resin, or polycarbonate resin.
- the substrate 10 is preferably made of polyethylene terephthalate.
- the lead section 20 includes the leads 21 and lead terminals 22.
- the lead section 20 may be formed using a well-known screen printing method.
- the lead section 20 is formed by screen-printing a silver ink or an ink mixture of silver and silver chloride on the substrate 10.
- the electrode section 30 is formed on the lead section 20.
- the electrode section 30 includes the checking electrode 33 in addition to the operating electrode 31 and counter electrode 32. Although one checking electrode 33 is illustrated, the electrode section 30 may include two or more checking electrodes . Where the checking electrode 33 is arranged as shown in Fig. 6, it is checked whether or not the checking electrode 33 is electrically connected with the counter electrode 32. Based on the result of the checking, it is possible to determine whether or not the blood sample is sufficiently filled in the sensor. Accordingly, the glucose concentration in the blood sample can be accurately measured.
- the checking electrode 33 can perform the same function as the counter electrode 32 because the checking electrode 33 is electrically connected with the counter electrode 32. In this case, an increased counter electrode area is obtained. By virtue of such an increased counter electrode area, it is possible to obtain a glucose measuring signal with an increased sensitivity when the amount of current flowing between the operating electrode and the counter electrode is measured.
- the operating electrode 31 and counter electrode 32, which form the electrode section 30, may be formed using a well-known method.
- the formation of the checking electrode 33 may also be achieved in the same manner as the formation of the counter electrode 32.
- the electrode section 30 is preferably formed in accordance with a screen printing method using a conductive carbon ink.
- an insulating material is screen-printed to form the insulating layer 40 for insulating the lead section 20 while partially exposing the electrode section 30.
- a non- conductive screen printing ink or an insulating ink may be used.
- the insulating screen printing ink is preferably used.
- the formation of the reaction layer 50 is carried out in such a fashion that the reaction layer 50 covers the exposed portion of the electrode section 30.
- the reaction layer 50 is made of a material including hydrogel and glucose oxidase (GOD) as major components thereof.
- the formation of the reaction layer 50 is achieved by preparing a solution obtained by respectively mixing hydrogel, GOD and a stabilizer in a liquid buffer at desired rates, dispensing the solution onto the surface of the electrode section 30, and then drying the dispensed solution in an incubator.
- a resin plate 60 is arranged to define a space 63. Also, the resin plate 60 defines the sample introducing port 61 at the front surface of the sensor and the discharge ports 62 at respective side surfaces of the sensor. Since the sample introducing port 61 and discharge ports 62 are formed at the front and side surfaces of the sensor, respectively, it is possible to conveniently handle the sensor, as compared to the conventional sensor including a discharge port formed at the upper surface of the sensor.
- the cover 70 is finally arranged on the resin plate 60 using a well-known method. Thus, the fabrication of the glucose strip sensor according to the present invention is completed.
- the glucose strip sensor having the above mentioned structure includes the checking sensor 33, it is possible to check whether or not the checking sensor 33 is electrically connected with the counter electrode 32, thereby determining whether or not the sensor is filled with a sufficient amount of blood sample. Accordingly, there is an advantage in that the measured glucose concentration has an increased accuracy. In addition, where the amount of current flowing between the counter electrode 32 and the checking electrode 33 is measured under the condition in which those electrodes are electrically connected using conduction means, there is an advantage in that a glucose measuring signal with an increased sensitivity can be obtained. Since the sample introducing port 61 and discharge ports 62 are formed at the front and side surfaces of the sensor, respectively, it is also possible to conveniently handle the sensor.
- the arrangement of the operating electrode 31, counter electrode 32, and checking electrode 33 is made in such a fashion that the counter electrode 32 and checking electrode 33 are arranged at front and rear sides of the operating electrode 31, respectively.
- the counter electrode 32 may be arranged near the sample introducing port 61
- the checking electrode 33 may be arranged near one of the discharge ports 62, as shown in Fig. 6.
- the checking electrode 33 is electrically connected with the counter electrode 32 under the condition in which the space 63 of the sensor is completely filled with a blood sample. Accordingly, it is possible to accurately check whether or not the space of the sensor is completely filled with a blood sample even when the space has an increased volume .
- air existing in the space 63 is vented from the space 63 through the discharge ports 62 respectively formed at opposite side surfaces of the sensor. Thereafter, it is checked, prior to a desired measurement of glucose concentration, whether or not a sufficient amount of blood sample is introduced in the space 63. That is, it is checked whether or not an electrical connection is established between the counter electrode 32 and the checking electrode 33.
- the blood sample filled in the space 63 of the sensor is impregnated into the reaction layer 50.
- the glucose of the impregnated blood sample enzymatically reacts with the GOD contained in the reaction layer 50, so that it is oxidized.
- the GOD is reduced.
- the reduced GOD is then oxidized as it reacts with the electron acceptor contained in the reaction layer 50, whereas the oxidized GOD reacts with the glucose not yet oxidized.
- the reduced electron acceptor migrates to the surface of the operating electrode 31, to which voltage of about 0.6 V is applied, and donates electrons at that surface.
- the electron acceptor is reoxidized so that it takes part again in the above reaction.
- the current generated during the oxidation of the electron acceptor is proportional to the concentration of glucose in the blood sample. Accordingly, the glucose concentration in the blood sample can be quantitatively derived by measuring the amount of current flowing between the operating electrode 31 and the counter electrode 32.
- a blood sample was prepared by dissolving a desired amount of glucose in a buffer solution. Thereafter, the concentration of glucose in the blood sample was measured using an automatic glucose analyzer, which is the Model YSI 2300 STAT PLUS manufactured by YSI Inc. The signal intensity corresponding to the measured glucose concentration was then measured by the glucose strip sensor according to the present invention. The correlation between the measured glucose concentration and the measured signal intensity is depicted in Fig. 8. The measurement was repeated 6 times for each glucose concentration. Referring to Fig. 8, it can be seen that the correlation between the measured glucose concentration and the measured signal intensity is well established in a clinically important glucose concentration range, that is, a glucose concentration range of 50 to 600 mg/dL.
- the present invention provides a glucose strip sensor in which a checking electrode is additionally provided at an electrode section including an operating electrode and a counter electrode .
- the checking electrode serves to check whether or not it is electrically connected with the counter electrode, upon measuring the concentration of glucose in a blood sample introduced in the sensor. Based on the result of the checking, it is possible to determine whether or not a sufficient amount of blood sample is filled in the sensor. Accordingly, the measurement of glucose concentration can be accurately achieved.
- the amount of current flowing between the counter electrode and the checking electrode is measured under the condition in which those electrodes are electrically connected using conduction means, there is an advantage in that a glucose measuring signal with an increased sensitivity can be obtained.
- the glucose strip sensor also includes a sample introducing port arranged at the front surface of the sensor, and discharge ports arranged at respective side surfaces of the sensor. Accordingly, it is also possible to conveniently handle the sensor .
Abstract
Description
Claims
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP01976900A EP1405063A1 (en) | 2001-07-07 | 2001-10-10 | Glucose strip sensor and glucose measurement method using the glucose strip sensor |
US10/481,406 US7297248B2 (en) | 2001-07-07 | 2001-10-10 | Glucose strip sensor and glucose measurement method using the glucose strip sensor |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
KR10-2001-0040690A KR100426638B1 (en) | 2001-07-07 | 2001-07-07 | Glucose strip sensor and glucose measurement method by the strip sensor |
KR2001/40690 | 2001-07-07 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2003005015A1 true WO2003005015A1 (en) | 2003-01-16 |
Family
ID=19711914
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/KR2001/001702 WO2003005015A1 (en) | 2001-07-07 | 2001-10-10 | Glucose strip sensor and glucose measurement method using the glucose strip sensor |
Country Status (5)
Country | Link |
---|---|
US (1) | US7297248B2 (en) |
EP (1) | EP1405063A1 (en) |
KR (1) | KR100426638B1 (en) |
CN (1) | CN1241014C (en) |
WO (1) | WO2003005015A1 (en) |
Cited By (14)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2005008231A1 (en) * | 2003-06-20 | 2005-01-27 | Roche Diagnostics Gmbh | System and method for analyte measurement of biological fluids using dose sufficiency electrodes |
WO2005103663A1 (en) | 2004-04-23 | 2005-11-03 | Arkray, Inc. | Analyzer and method of manufacturing the same |
WO2007027678A1 (en) * | 2005-08-30 | 2007-03-08 | Bayer Healthcare Llc | A test sensor with a fluid chamber opening |
EP1927851A3 (en) * | 2006-11-30 | 2009-01-21 | Infopia Co., Ltd. | Biosensor |
WO2009104836A1 (en) * | 2008-02-22 | 2009-08-27 | Korea Research Institute Of Bioscience And Biotechnology | A glucose sensor comprising glucose oxidase variant |
EP2098161A1 (en) * | 2006-10-11 | 2009-09-09 | Bayer HealthCare LLC | Test sensor with a side vent and method of making the same |
US7727467B2 (en) | 2003-06-20 | 2010-06-01 | Roche Diagnostics Operations, Inc. | Reagent stripe for test strip |
US7797987B2 (en) | 2006-10-11 | 2010-09-21 | Bayer Healthcare Llc | Test sensor with a side vent and method of making the same |
US8071030B2 (en) | 2003-06-20 | 2011-12-06 | Roche Diagnostics Operations, Inc. | Test strip with flared sample receiving chamber |
US8287703B2 (en) | 1999-10-04 | 2012-10-16 | Roche Diagnostics Operations, Inc. | Biosensor and method of making |
US8298828B2 (en) | 2003-06-20 | 2012-10-30 | Roche Diagnostics Operations, Inc. | System and method for determining the concentration of an analyte in a sample fluid |
US8507289B1 (en) | 2003-06-20 | 2013-08-13 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
EP2764352A1 (en) * | 2011-10-03 | 2014-08-13 | CPFilms Inc. | Method of activation of noble metal for measurement of glucose and associated biosensor electrode |
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 (90)
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 |
US7344507B2 (en) | 2002-04-19 | 2008-03-18 | Pelikan Technologies, Inc. | Method and apparatus for lancet actuation |
WO2002100461A2 (en) | 2001-06-12 | 2002-12-19 | Pelikan Technologies, Inc. | Method and apparatus for improving success rate of blood yield from a fingerstick |
US9795747B2 (en) | 2010-06-02 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | Methods and apparatus for lancet actuation |
AU2002312521A1 (en) | 2001-06-12 | 2002-12-23 | Pelikan Technologies, Inc. | Blood sampling apparatus and method |
US7033371B2 (en) | 2001-06-12 | 2006-04-25 | Pelikan Technologies, Inc. | Electric lancet actuator |
US7981056B2 (en) | 2002-04-19 | 2011-07-19 | Pelikan Technologies, Inc. | Methods and apparatus for lancet actuation |
US9226699B2 (en) | 2002-04-19 | 2016-01-05 | Sanofi-Aventis Deutschland Gmbh | Body fluid sampling module with a continuous compression tissue interface surface |
WO2002100254A2 (en) | 2001-06-12 | 2002-12-19 | Pelikan Technologies, Inc. | Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge |
US7025774B2 (en) | 2001-06-12 | 2006-04-11 | Pelikan Technologies, Inc. | Tissue penetration device |
EP1404233B1 (en) | 2001-06-12 | 2009-12-02 | Pelikan Technologies Inc. | Self optimizing lancing device with adaptation means to temporal variations in cutaneous properties |
US8337419B2 (en) | 2002-04-19 | 2012-12-25 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
US9427532B2 (en) | 2001-06-12 | 2016-08-30 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
US7955559B2 (en) | 2005-11-15 | 2011-06-07 | Nanomix, Inc. | Nanoelectronic electrochemical test device |
US7312095B1 (en) * | 2002-03-15 | 2007-12-25 | Nanomix, Inc. | Modification of selectivity for sensing for nanostructure sensing device arrays |
US8267870B2 (en) | 2002-04-19 | 2012-09-18 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for body fluid sampling with hybrid actuation |
US7331931B2 (en) | 2002-04-19 | 2008-02-19 | 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 |
US8360992B2 (en) | 2002-04-19 | 2013-01-29 | 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 |
US7976476B2 (en) | 2002-04-19 | 2011-07-12 | Pelikan Technologies, Inc. | Device and method for variable speed lancet |
US8702624B2 (en) | 2006-09-29 | 2014-04-22 | Sanofi-Aventis Deutschland Gmbh | Analyte measurement device with a single shot actuator |
US7648468B2 (en) | 2002-04-19 | 2010-01-19 | Pelikon Technologies, Inc. | Method and apparatus for penetrating tissue |
US9314194B2 (en) | 2002-04-19 | 2016-04-19 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
US7892185B2 (en) | 2002-04-19 | 2011-02-22 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
US7232451B2 (en) | 2002-04-19 | 2007-06-19 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7717863B2 (en) | 2002-04-19 | 2010-05-18 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7713214B2 (en) | 2002-04-19 | 2010-05-11 | Pelikan Technologies, Inc. | Method and apparatus for a multi-use body fluid sampling device with optical analyte sensing |
US7909778B2 (en) | 2002-04-19 | 2011-03-22 | 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 |
US7674232B2 (en) | 2002-04-19 | 2010-03-09 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7491178B2 (en) | 2002-04-19 | 2009-02-17 | 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 |
US7892183B2 (en) | 2002-04-19 | 2011-02-22 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
US7229458B2 (en) | 2002-04-19 | 2007-06-12 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7901362B2 (en) | 2002-04-19 | 2011-03-08 | 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 |
US8784335B2 (en) | 2002-04-19 | 2014-07-22 | Sanofi-Aventis Deutschland Gmbh | Body fluid sampling device with a capacitive sensor |
US9795334B2 (en) | 2002-04-19 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
US8579831B2 (en) | 2002-04-19 | 2013-11-12 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
KR100441152B1 (en) | 2002-05-20 | 2004-07-21 | 주식회사 인포피아 | Biosensor |
CN1467496A (en) * | 2002-06-03 | 2004-01-14 | 松下电器产业株式会社 | Biosensor |
US8574895B2 (en) | 2002-12-30 | 2013-11-05 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus using optical techniques to measure analyte levels |
US9234867B2 (en) | 2003-05-16 | 2016-01-12 | Nanomix, Inc. | Electrochemical nanosensors for biomolecule detection |
DE602004028463D1 (en) | 2003-05-30 | 2010-09-16 | Pelikan Technologies Inc | METHOD AND DEVICE FOR INJECTING LIQUID |
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 |
US8282576B2 (en) | 2003-09-29 | 2012-10-09 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for an improved sample capture device |
EP1680014A4 (en) | 2003-10-14 | 2009-01-21 | Pelikan Technologies Inc | Method and apparatus for a variable user interface |
EP1706026B1 (en) | 2003-12-31 | 2017-03-01 | Sanofi-Aventis Deutschland GmbH | Method and apparatus for improving fluidic flow and sample capture |
US7822454B1 (en) | 2005-01-03 | 2010-10-26 | Pelikan Technologies, Inc. | Fluid sampling device with improved analyte detecting member configuration |
EP1751546A2 (en) | 2004-05-20 | 2007-02-14 | Albatros Technologies GmbH & Co. KG | Printable hydrogel for biosensors |
EP1765194A4 (en) | 2004-06-03 | 2010-09-29 | 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 |
GB0426822D0 (en) * | 2004-12-07 | 2005-01-12 | Precisense As | Sensor for detection of glucose |
US8652831B2 (en) | 2004-12-30 | 2014-02-18 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for analyte measurement test time |
KR100680267B1 (en) | 2005-09-16 | 2007-02-08 | 주식회사 인포피아 | Biosensor had the identification information and reading apparatus for the identification information recorded a biosensor |
KR100739865B1 (en) * | 2005-12-27 | 2007-07-16 | 주식회사 인포피아 | Bio-sensor |
US20070205114A1 (en) * | 2006-03-01 | 2007-09-06 | Mathur Vijaywanth P | Method of detecting biosensor filling |
KR100757297B1 (en) * | 2006-09-30 | 2007-09-11 | 케이엠에이치 주식회사 | Sample injection time improved biosensor and measurement method |
KR100885074B1 (en) * | 2007-07-26 | 2009-02-25 | 주식회사 아이센스 | Microfluidic sensor complex structures |
KR100906023B1 (en) | 2007-10-23 | 2009-07-06 | 주식회사 헬스피아 | Blood sugar metering system |
KR100911927B1 (en) * | 2007-11-13 | 2009-08-13 | 주식회사 필로시스 | Device for analyzing quantitatively material of living creature |
WO2009126900A1 (en) | 2008-04-11 | 2009-10-15 | Pelikan Technologies, Inc. | Method and apparatus for analyte detecting device |
US20090294302A1 (en) * | 2008-05-28 | 2009-12-03 | John Pasqua | Use of Alginate to Reduce Hematocrit Bias in Biosensors |
KR100972108B1 (en) | 2008-07-09 | 2010-07-26 | 주식회사 올메디쿠스 | Bio-sensor |
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 |
KR101090947B1 (en) | 2009-08-28 | 2011-12-08 | 주식회사 필로시스 | Test strip and living creature analyzing device and analyzing method using it |
US8965476B2 (en) | 2010-04-16 | 2015-02-24 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
CN102359984B (en) * | 2011-08-16 | 2013-10-09 | 苏州悦安医疗电子有限公司 | Portable noninvasive blood sugar monitor |
CN102384931B (en) * | 2011-08-16 | 2013-10-09 | 苏州悦安医疗电子有限公司 | Salivary glucose concentration acquiring device |
US9523653B2 (en) | 2013-05-09 | 2016-12-20 | Changsha Sinocare Inc. | Disposable test sensor with improved sampling entrance |
KR101462019B1 (en) * | 2013-05-27 | 2014-11-18 | 재단법인 다차원 스마트 아이티 융합시스템 연구단 | Blood glucose measuring instrument |
US9518951B2 (en) | 2013-12-06 | 2016-12-13 | Changsha Sinocare Inc. | Disposable test sensor with improved sampling entrance |
US9897566B2 (en) | 2014-01-13 | 2018-02-20 | Changsha Sinocare Inc. | Disposable test sensor |
US9939401B2 (en) | 2014-02-20 | 2018-04-10 | Changsha Sinocare Inc. | Test sensor with multiple sampling routes |
KR20170035668A (en) | 2015-09-23 | 2017-03-31 | 한국과학기술연구원 | Method for sensing sugars using terahertz electromagnetic waves with high sensitivity and selectivity and device used therein |
KR101768331B1 (en) * | 2015-10-23 | 2017-08-14 | 계명대학교 산학협력단 | Portable blood coagulation factor measurement system |
KR101725693B1 (en) * | 2015-12-29 | 2017-04-12 | 성균관대학교산학협력단 | Apparatus and method for synthesizing frequency capable of maintaining frequency over variation of operational conditions |
CN106226379A (en) * | 2016-07-10 | 2016-12-14 | 浙江亿联健医疗器械有限公司 | A kind of biosensor eliminating sample introduction process influence and method of testing |
WO2018122856A1 (en) | 2016-12-29 | 2018-07-05 | Dalibor Hodko | An electrophoretic chip for electrophoretic applications |
KR20180092563A (en) | 2017-02-10 | 2018-08-20 | 김경원 | Blood Glucose Test Strip |
CN109758164B (en) * | 2017-11-10 | 2024-03-08 | 上海瀚联医疗技术股份有限公司 | Blood glucose monitoring method of blood glucose meter |
CN108303454A (en) * | 2018-02-23 | 2018-07-20 | 南京鱼跃软件技术有限公司 | A kind of uric acid electrochemical sensor |
EP4246139A1 (en) * | 2020-11-11 | 2023-09-20 | Leadway (HK) Limited | Biosensor |
KR20210029736A (en) | 2021-02-24 | 2021-03-16 | 백석문화대학교 산학협력단 | Blood sugar management system using ultrasound |
CN113588747B (en) * | 2021-07-12 | 2024-01-19 | 成都云芯医联科技有限公司 | Electrochemical test card for simultaneously measuring glutamic pyruvic transaminase and glutamic oxaloacetic transaminase |
Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1999013099A1 (en) * | 1997-09-05 | 1999-03-18 | Abbott Laboratories | Electrochemical sensor having equalized electrode areas |
WO1999013100A1 (en) * | 1997-09-05 | 1999-03-18 | Abbott Laboratories | Electrode with thin working layer |
WO1999058709A1 (en) * | 1998-05-08 | 1999-11-18 | Abbott Laboratories | Test strip |
WO2000073785A2 (en) * | 1999-06-02 | 2000-12-07 | Nova Biomedical Corporation | Low interference disposable sensor and method of making |
WO2000073778A1 (en) * | 1999-06-02 | 2000-12-07 | Nova Biomedical Corporation | Disposable sub-microliter volume sensor and method of making |
WO2000079258A1 (en) * | 1999-06-18 | 2000-12-28 | Abbott Laboratories | Electrochemical sensor for analysis of liquid samples |
Family Cites Families (15)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
SE173761C1 (en) * | 1956-11-07 | 1960-12-20 | ||
NL7309384A (en) | 1973-07-05 | 1975-01-07 | Philips Nv | FIBER SHEET WITH A REGULAR STACKING OF RECTANGULAR FIBERS. |
JPH0648256B2 (en) | 1985-06-21 | 1994-06-22 | 松下電器産業株式会社 | Biosensor |
DE68924026T3 (en) * | 1988-03-31 | 2008-01-10 | Matsushita Electric Industrial Co., Ltd., Kadoma | BIOSENSOR AND ITS MANUFACTURE. |
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 |
JP3365184B2 (en) * | 1996-01-10 | 2003-01-08 | 松下電器産業株式会社 | Biosensor |
JPH10170471A (en) * | 1996-12-06 | 1998-06-26 | Casio Comput Co Ltd | Biosensor |
GB9711395D0 (en) * | 1997-06-04 | 1997-07-30 | Environmental Sensors Ltd | Improvements to electrodes for the measurement of analytes in small samples |
JP3267936B2 (en) * | 1998-08-26 | 2002-03-25 | 松下電器産業株式会社 | Biosensor |
US6338790B1 (en) * | 1998-10-08 | 2002-01-15 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
JP2001183330A (en) * | 1999-12-27 | 2001-07-06 | Matsushita Electric Ind Co Ltd | Biosensor |
KR100446468B1 (en) * | 2001-05-18 | 2004-09-01 | 주식회사 아이센스 | Biosensors with porous chromatographic membranes and enhanced sampling capability |
US6793802B2 (en) * | 2001-01-04 | 2004-09-21 | Tyson Bioresearch, Inc. | Biosensors having improved sample application and measuring properties and uses thereof |
US6491803B1 (en) * | 2001-05-18 | 2002-12-10 | Apex Biotechnology Corporation | Test strip and biosensor incorporating with nanometer metal particles |
KR100851297B1 (en) | 2005-11-29 | 2008-08-08 | 엠텍비젼 주식회사 | Universal Serial Bus Cable Apparatus |
-
2001
- 2001-07-07 KR KR10-2001-0040690A patent/KR100426638B1/en active IP Right Grant
- 2001-10-10 CN CNB018234496A patent/CN1241014C/en not_active Expired - Fee Related
- 2001-10-10 US US10/481,406 patent/US7297248B2/en not_active Expired - Lifetime
- 2001-10-10 WO PCT/KR2001/001702 patent/WO2003005015A1/en active Application Filing
- 2001-10-10 EP EP01976900A patent/EP1405063A1/en not_active Ceased
Patent Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1999013099A1 (en) * | 1997-09-05 | 1999-03-18 | Abbott Laboratories | Electrochemical sensor having equalized electrode areas |
WO1999013100A1 (en) * | 1997-09-05 | 1999-03-18 | Abbott Laboratories | Electrode with thin working layer |
WO1999058709A1 (en) * | 1998-05-08 | 1999-11-18 | Abbott Laboratories | Test strip |
WO2000073785A2 (en) * | 1999-06-02 | 2000-12-07 | Nova Biomedical Corporation | Low interference disposable sensor and method of making |
WO2000073778A1 (en) * | 1999-06-02 | 2000-12-07 | Nova Biomedical Corporation | Disposable sub-microliter volume sensor and method of making |
WO2000079258A1 (en) * | 1999-06-18 | 2000-12-28 | Abbott Laboratories | Electrochemical sensor for analysis of liquid samples |
Cited By (27)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8551308B2 (en) | 1999-10-04 | 2013-10-08 | Roche Diagnostics Operations, Inc. | Biosensor and method of making |
US8287703B2 (en) | 1999-10-04 | 2012-10-16 | Roche Diagnostics Operations, Inc. | Biosensor and method of making |
US7749437B2 (en) | 2003-06-20 | 2010-07-06 | Roche Diagnostics Operations, Inc. | Method and reagent for producing narrow, homogenous reagent stripes |
US8222044B2 (en) | 2003-06-20 | 2012-07-17 | Roche Diagnostics Operations, Inc. | Test strip with flared sample receiving chamber |
US8507289B1 (en) | 2003-06-20 | 2013-08-13 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
US8298828B2 (en) | 2003-06-20 | 2012-10-30 | Roche Diagnostics Operations, Inc. | System and method for determining the concentration of an analyte in a sample fluid |
US8663442B2 (en) | 2003-06-20 | 2014-03-04 | Roche Diagnostics Operations, Inc. | System and method for analyte measurement using dose sufficiency electrodes |
US7727467B2 (en) | 2003-06-20 | 2010-06-01 | Roche Diagnostics Operations, Inc. | Reagent stripe for test strip |
US8211379B2 (en) | 2003-06-20 | 2012-07-03 | Roche Diagnostics Operations, Inc. | Test strip with slot vent opening |
US8586373B2 (en) | 2003-06-20 | 2013-11-19 | Roche Diagnostics Operations, Inc. | System and method for determining the concentration of an analyte in a sample fluid |
US7829023B2 (en) | 2003-06-20 | 2010-11-09 | Roche Diagnostics Operations, Inc. | Test strip with vent opening |
US7879618B2 (en) | 2003-06-20 | 2011-02-01 | Roche Diagnostics Operations, Inc. | Method and reagent for producing narrow, homogenous reagent strips |
WO2005008231A1 (en) * | 2003-06-20 | 2005-01-27 | Roche Diagnostics Gmbh | System and method for analyte measurement of biological fluids using dose sufficiency electrodes |
US8071030B2 (en) | 2003-06-20 | 2011-12-06 | Roche Diagnostics Operations, Inc. | Test strip with flared sample receiving chamber |
US8119414B2 (en) | 2003-06-20 | 2012-02-21 | Roche Diagnostics Operations, Inc. | Test strip with slot vent opening |
US8142721B2 (en) | 2003-06-20 | 2012-03-27 | Roche Diagnostics Operations, Inc. | Test strip with slot vent opening |
EP1739414A4 (en) * | 2004-04-23 | 2011-08-31 | Arkray Inc | Analyzer and method of manufacturing the same |
EP1739414A1 (en) * | 2004-04-23 | 2007-01-03 | Arkray, Inc. | Analyzer and method of manufacturing the same |
WO2005103663A1 (en) | 2004-04-23 | 2005-11-03 | Arkray, Inc. | Analyzer and method of manufacturing the same |
US9410915B2 (en) | 2004-06-18 | 2016-08-09 | Roche Operations Ltd. | System and method for quality assurance of a biosensor test strip |
WO2007027678A1 (en) * | 2005-08-30 | 2007-03-08 | Bayer Healthcare Llc | A test sensor with a fluid chamber opening |
US7797987B2 (en) | 2006-10-11 | 2010-09-21 | Bayer Healthcare Llc | Test sensor with a side vent and method of making the same |
EP2098161A1 (en) * | 2006-10-11 | 2009-09-09 | Bayer HealthCare LLC | Test sensor with a side vent and method of making the same |
EP1927851A3 (en) * | 2006-11-30 | 2009-01-21 | Infopia Co., Ltd. | Biosensor |
WO2009104836A1 (en) * | 2008-02-22 | 2009-08-27 | Korea Research Institute Of Bioscience And Biotechnology | A glucose sensor comprising glucose oxidase variant |
EP2764352A1 (en) * | 2011-10-03 | 2014-08-13 | CPFilms Inc. | Method of activation of noble metal for measurement of glucose and associated biosensor electrode |
EP2764352A4 (en) * | 2011-10-03 | 2015-03-11 | Cpfilms Inc | Method of activation of noble metal for measurement of glucose and associated biosensor electrode |
Also Published As
Publication number | Publication date |
---|---|
KR100426638B1 (en) | 2004-04-08 |
KR20030004933A (en) | 2003-01-15 |
CN1527938A (en) | 2004-09-08 |
EP1405063A1 (en) | 2004-04-07 |
CN1241014C (en) | 2006-02-08 |
US20040146958A1 (en) | 2004-07-29 |
US7297248B2 (en) | 2007-11-20 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7297248B2 (en) | Glucose strip sensor and glucose measurement method using the glucose strip sensor | |
JP4814952B2 (en) | Method for measuring hematocrit value of blood sample, method for measuring concentration of analyte in blood sample, sensor chip and sensor unit | |
US7070680B2 (en) | Biosensor | |
AU763723B2 (en) | Disposable test strips with integrated reagent/blood separation layer | |
EP0255291B1 (en) | Method and apparatus for electrochemical measurements | |
US10352890B2 (en) | Biosensor system, sensor chip, and method of measuring analyte concentration in blood sample | |
AU2007201377A1 (en) | Systems and methods of discriminating control solution from a physiological sample | |
JPWO2008047843A1 (en) | Method for measuring hematocrit value of blood sample, method for measuring concentration of analyte in blood sample, sensor chip and sensor unit | |
US20100089774A1 (en) | Non-enzymatic electrochemical method for simultaneous determination of total hemoglobin and glycated hemoglobin | |
US6860978B2 (en) | Biosensor and method of producing the same | |
JP2001330581A (en) | Substrate concentration determination method | |
US7678261B2 (en) | Apparatus and method for measuring reaction result of samples on biosensor | |
JPH05340915A (en) | Biosensor and measuring method using the same | |
CN114264713A (en) | Biosensor and method for measuring the same | |
EP1357194A2 (en) | Adapter for the connection of a biosensor to a measuring device | |
JPH11344462A (en) | Method for determining substrate | |
JP4352108B2 (en) | Substrate quantification method | |
JP2548147B2 (en) | Biosensor | |
JP2004004057A (en) | Biosensor, adapter used for the same and measuring apparatus | |
JPH0610662B2 (en) | Biosensor | |
JPH08338824A (en) | Biosensor, manufacture for biosensor and method for determining specific compound |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AK | Designated states |
Kind code of ref document: A1 Designated state(s): AE AG AL AM AT AU AZ BA BB BG BR BY BZ CA CH CN CO CR CU CZ DE DK DM DZ EC EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KZ LC LK LR LS LT LU LV MA MD MG MK MN MW MX MZ NO NZ PH PL PT RO RU SD SE SG SI SK SL TJ TM TR TT TZ UA UG US UZ VN YU ZA ZW |
|
AL | Designated countries for regional patents |
Kind code of ref document: A1 Designated state(s): GH GM KE LS MW MZ SD SL SZ TZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE TR BF BJ CF CG CI CM GA GN GQ GW ML MR NE SN TD TG |
|
DFPE | Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101) | ||
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
WWE | Wipo information: entry into national phase |
Ref document number: 10481406 Country of ref document: US |
|
WWE | Wipo information: entry into national phase |
Ref document number: 2001976900 Country of ref document: EP Ref document number: 20018234496 Country of ref document: CN |
|
WWP | Wipo information: published in national office |
Ref document number: 2001976900 Country of ref document: EP |
|
REG | Reference to national code |
Ref country code: DE Ref legal event code: 8642 |
|
NENP | Non-entry into the national phase |
Ref country code: JP |