Source: http://www.google.com/patents/US20020179441?ie=ISO-8859-1&dq=6,202,00
Timestamp: 2014-08-20 23:56:26
Document Index: 528921719

Matched Legal Cases: ['arts 2', 'arts 2', 'arts 2', 'arts 2', 'arts 2', 'arts 2', 'arts 2', 'arts 2', 'arts 2', 'arts 2', 'arts 2', 'arts 2', 'arts 2', 'arts 2']

Patent US20020179441 - Biosensor and method of producing the same - Google PatentsSearch Images Maps Play YouTube News Gmail Drive More »Sign in<nobr>Advanced Patent Search</nobr>PatentsIn a biosensor comprising a pair of conductive lead parts 2 and 3 formed on an insulating substrate 1, a working electrode 4 and a counter electrode 5 formed at the ends of the conductive lead parts 2 and 3, respectively, and a reaction layer 7 which is formed so as to bridge the both electrodes and...http://www.google.com/patents/US20020179441?utm_source=gb-gplus-sharePatent US20020179441 - Biosensor and method of producing the sameAdvanced Patent SearchPublication numberUS20020179441 A1Publication typeApplicationApplication numberUS 09/959,816PCT numberPCT/JP2001/001812Publication dateDec 5, 2002Filing dateMar 8, 2001Priority dateMar 8, 2000Also published asCN1182388C, CN1364234A, EP1182451A1, EP1182451A4, EP1182451B1, US6860978, WO2001067081A1Publication number09959816, 959816, PCT/2001/1812, PCT/JP/1/001812, PCT/JP/1/01812, PCT/JP/2001/001812, PCT/JP/2001/01812, PCT/JP1/001812, PCT/JP1/01812, PCT/JP1001812, PCT/JP101812, PCT/JP2001/001812, PCT/JP2001/01812, PCT/JP2001001812, PCT/JP200101812, US 2002/0179441 A1, US 2002/179441 A1, US 20020179441 A1, US 20020179441A1, US 2002179441 A1, US 2002179441A1, US-A1-20020179441, US-A1-2002179441, US2002/0179441A1, US2002/179441A1, US20020179441 A1, US20020179441A1, US2002179441 A1, US2002179441A1InventorsEriko Yamanishi, Shoji Miyazaki, Noriyoshi TerashimaOriginal AssigneeEriko Yamanishi, Shoji Miyazaki, Noriyoshi TerashimaExport CitationBiBTeX, EndNote, RefManClassifications (9), Legal Events (7) External Links: USPTO, USPTO Assignment, EspacenetBiosensor and method of producing the sameUS 20020179441 A1Abstract In a biosensor comprising a pair of conductive lead parts 2 and 3 formed on an insulating substrate 1, a working electrode 4 and a counter electrode 5 formed at the ends of the conductive lead parts 2 and 3, respectively, and a reaction layer 7 which is formed so as to bridge the both electrodes and reacts with a measurement target substance in a specimen liquid, and measuring the content of the measurement target substance from an electric current value based on the reaction between the measurement target substance and the reaction layer 7, which current value is obtained through the pair of conductive lead parts 2 and 3, the reaction layer 7 which contacts the electrodes 4 and 5 is not provided above at least one of the conductive lead parts 2 and 3 so that the reaction layer 7 and the conductive lead parts 2 and 3 do not contact directly even when pin holes or cracks are generated in the both electrodes. The biosensor constructed as described above has high reliability and reproduction accuracy, and is able to improve preservation stability. Images(5) Claims(6)
BEST MODE TO EXECUTE THE INVENTION [0016] Hereinafter, a sensor for measuring a blood sugar level according to an embodiment of the present invention will be described with reference to FIG. 1. FIG. 1 is an exploded diagram illustrating a process of manufacturing the sensor for measuring a blood sugar level, and the same parts as those in the conventional constitution shown in FIG. 3 are denoted by the same reference numerals. [0017] First of all, conductive lead parts 2 and 3 are formed of a metal material such as silver paste on a substrate 1 as in the conventional process. A difference from the conventional process is that end parts 2 b and 3 b of the conductive lead parts 2 and 3 are not shaped to follow a working electrode and a counter electrode as conventional but are merely closed in straight lines. A working electrode 4 and a counter electrode 5, which are larger than prescribed shapes, are formed so as to partially overlap the end parts 2 b and 3 b of the lead parts, employing carbon paste which is mainly composed of carbon. [0018] An insulating paste is overprinted on the substrate 1 of this state so as to expose the working electrode 4, the counter electrode 5, and the connection terminals 2 a and 3 a, thereby forming an insulating layer 6. At this time, portions of the working electrode 4 and the counter electrode 5 formed on the end parts 2 b and 3 b of the conductive lead parts are covered with the insulating layer 6. [0019] A prescribed reagent reaction layer 7 which includes a hydrophilic polymer (carboxymethyl cellulose), an enzyme (glucose oxidase), and an electron acceptor (potassium ferricyanide) is formed on the electrodes 4 and 5 constructed as described above. At this time, even when the reaction layer 7 is extensively formed over the portions of the working electrode 4 and counter electrode 5 formed on the end parts 2 b and 3 b of the conductive lead parts, since these portions are covered with the insulating layer 6, the reaction layer 7 never comes in contact with the portions of the working electrode 4 and the counter electrode 5. That is, the reaction layer 7 is not substantially provided on the portions of the working electrode 4 and the counter electrode 5. [0020] Thereafter, a cover 9 having a specimen supply groove 10 is adhered as in the conventional process, and also at this time, the specimen supply groove 10 is never positioned above the portions of the working electrode 4 and the counter electrode 5 formed on the end parts 2 b and 3 b of the conductive lead parts. [0021]FIG. 2 illustrates a result obtained when purified water is measured (blank value) by the sensor of the above-described constitution, which is preserved in a hostile environment where the temperature is 40� C. and the humidity is 80%. An average at ten measurements is plotted, and it is shown that increase in blank value can be suppressed even in a hostile environment of high temperature and humidity. [0022] (Table 1) shows a comparison of sensor accuracy at twenty measurements with the blood glucose concentration of 42�600 mg/dl. The sensor accuracy is detected as follows. A reaction between a reagent and glucose in the blood is promoted for about twenty-five seconds after the blood is drawn into the capillary and, thereafter, a voltage of 0.5 V is applied between the connection terminal 2 a of the working electrode and the connection terminal 3 a of the counter electrode, and an electric current value is obtained five seconds later. The accuracy of variation in the electric current value is referred to as the sensor accuracy. The variation in measurement of the sensor according to this embodiment is significantly decreased and reduced as compared with that of the conventional sensor. TABLE 1 Glucose concentration Conventional sensor Sensor of embodiment 42 mg/dl 7.63% 4.20% 79 mg/dl 3.47% 2.75% 245 mg/dl 2.60% 2.31% 361 mg/dl 2.45% 2.20% 497 mg/dl 2.17% 1.64% 600 mg/dl 3.81% 1.40% [0023] As seen from FIG. 4 and the result of (Table 1), a biosensor which is excellent in preservation stability, is high in sensitivity, and has less variation can be realized by employing the sensor of the embodiment. [0024] While a sensor for measuring a blood sugar level is exemplified in this embodiment, the same effects can be achieved even in a similarly constituted sensor for measuring cholesterol, lactic acid, or the like. Further, while it is most desirable that there is no reaction layer on the lead parts on both of the working electrode and the counter electrode, the same effects can be also achieved when there is no reaction layer on either one of them. [0025] Applicability in Industry [0026] As described above, a biosensor according to the present invention can speedily determine the quantity of measurement target substance in a specimen liquid, thereby providing a biosensor which operates in high quality even in a high-humidity environment. Classifications U.S. Classification204/403.01International ClassificationC12Q1/00, G01N27/416, G01N27/28, G01N27/327Cooperative ClassificationC12Q1/001, C12Q1/006European ClassificationC12Q1/00B6B, C12Q1/00BLegal EventsDateCodeEventDescriptionApr 29, 2014ASAssignmentOwner name: PANASONIC HEALTHCARE HOLDINGS CO., LTD., JAPANFree format text: CHANGE OF NAME;ASSIGNOR:PHC HOLDINGS CO., LTD.;REEL/FRAME:032785/0563Effective date: 20140331Owner name: PHC HOLDINGS CO., LTD., JAPANFree format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:PANASONIC CORPORATION;REEL/FRAME:032785/0498Mar 19, 2014ASAssignmentOwner name: PANASONIC CORPORATION, JAPANFree format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:PANASONIC HEALTHCARE CO., LTD.;REEL/FRAME:032480/0433Effective date: 20140301Feb 27, 2014ASAssignmentOwner name: PANASONIC HEALTHCARE CO., LTD., JAPANFree format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:PANASONIC CORPORATION;REEL/FRAME:032360/0795Effective date: 20131127Feb 25, 2014ASAssignmentOwner name: PANASONIC CORPORATION, JAPANFree format text: CHANGE OF NAME;ASSIGNOR:MATSUSHITA ELECTRIC INDUSTRIAL CO., LTD.;REEL/FRAME:032332/0082Effective date: 20081001Aug 21, 2012FPAYFee paymentYear of fee payment: 8Aug 27, 2008FPAYFee paymentYear of fee payment: 4Dec 18, 2001ASAssignmentOwner name: MATSUSHITA ELECTRIC INDUSTRIAL CO., LTD., JAPANFree format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:YAMANISHI, ERIKO;MIYAZAKI, SHOJI;TERASHIMA, NORIYOSHI;REEL/FRAME:012377/0921Effective date: 20011127Owner name: MATSUSHITA ELECTRIC INDUSTRIAL CO., LTD. 1006, OAZFree format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:YAMANISHI, ERIKO /AR;REEL/FRAME:012377/0921RotateOriginal ImageGoogle Home - Sitemap - USPTO Bulk Downloads - Privacy Policy - Terms of Service - About Google Patents - Send FeedbackData provided by IFI CLAIMS Patent Services©2012 Google