CA2550198C - Sensor connection means - Google Patents
Sensor connection means Download PDFInfo
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- CA2550198C CA2550198C CA002550198A CA2550198A CA2550198C CA 2550198 C CA2550198 C CA 2550198C CA 002550198 A CA002550198 A CA 002550198A CA 2550198 A CA2550198 A CA 2550198A CA 2550198 C CA2550198 C CA 2550198C
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- Prior art keywords
- cut
- insulating substrate
- sensor
- electrode
- aperture
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Classifications
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
- G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
- G01N27/28—Electrolytic cell components
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
- G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
- G01N27/28—Electrolytic cell components
- G01N27/30—Electrodes, e.g. test electrodes; Half-cells
- G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
- G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
- G01N27/3272—Test elements therefor, i.e. disposable laminated substrates with electrodes, reagent and channels
Abstract
The invention relates to a sensor adapted for electrical connection to a power source having an electrical contact means (3). The sensor has a first insulating substrate (1) carrying a first electrode (2) and a second insulating substrate (7) carrying a second electrode (6). The electrodes are disposed to face each other in spaced apart relationship, sandwiching a spacer (4) therebetween. A first cut-out portion extends through the first insulating substrate (1) and a spacer (4) to expose a first contact area (23) on the second insulating substrate (1). This permits the electrical contact means (31) to effect electrical connection with the first contact (23) which in turn is in electrically conductive connection with the second electrode (6). A similar contact arrangement may be disposed on the opposite side of the sensor.
Description
TITLE: "SENSOR CONNECTION MEANS"
TECHNICAL FIELD
This invention relates to disposable electrochemical sensors of the type used for quantitative analysis, for example, of glucose levels in blood, for pH
measurement, or the like. More particularly the invention relates to means for electrical connection of such sensors to a measuring apparatus.
BACKGROUND ART
US Patent 5,437,999 discloses an electrochemical sensor of the kind which in use is ~o electrically connected with a power source. The sensor is constructed from two spaced apart printed circuit boards each having a metal layer on one side and disposed so that the metal layers are facing each other in spaced apart relationship. The metal layers are photolithographically treated to define electrode areas which form part of a cell. At one end of the assembly the electrode substrates are cut to provide laterally spaced protruding tabs bearing the metal layer. The exposed metal surfaces of the tabs act as contact pads, each contact pad being electrically connected with a corresponding electrode.
The contact pads in tum engage contact prongs connected to a power source and provide electrical connection between the sensor and a power source.
The arrangement of US Patent 5,437,999 suffers from the disadvantages that the substrate is required to be of considerable rigidity in order to ensure satisfactory and reliable electrical contact. Moreover the user is often left uncertain as to whether a sensor has satisfactorily been connected with the power source.
In co-pending applications WO 96/32635, WO 97/0041, WO 97/18465 and WO 97!18464 there are described various very thin electrochemical cells. Each
TECHNICAL FIELD
This invention relates to disposable electrochemical sensors of the type used for quantitative analysis, for example, of glucose levels in blood, for pH
measurement, or the like. More particularly the invention relates to means for electrical connection of such sensors to a measuring apparatus.
BACKGROUND ART
US Patent 5,437,999 discloses an electrochemical sensor of the kind which in use is ~o electrically connected with a power source. The sensor is constructed from two spaced apart printed circuit boards each having a metal layer on one side and disposed so that the metal layers are facing each other in spaced apart relationship. The metal layers are photolithographically treated to define electrode areas which form part of a cell. At one end of the assembly the electrode substrates are cut to provide laterally spaced protruding tabs bearing the metal layer. The exposed metal surfaces of the tabs act as contact pads, each contact pad being electrically connected with a corresponding electrode.
The contact pads in tum engage contact prongs connected to a power source and provide electrical connection between the sensor and a power source.
The arrangement of US Patent 5,437,999 suffers from the disadvantages that the substrate is required to be of considerable rigidity in order to ensure satisfactory and reliable electrical contact. Moreover the user is often left uncertain as to whether a sensor has satisfactorily been connected with the power source.
In co-pending applications WO 96/32635, WO 97/0041, WO 97/18465 and WO 97!18464 there are described various very thin electrochemical cells. Each
-2-cell is defined between facing spaced apart .electrodes which are formed as thin metai coatings (for example sputter coatings) deposited on thin inert plastic film (for example 100 micron thick PET). The electrodes are separated one from the other by a spacer of thickness of for example 500 Ftm or less.
s The connection arrangement of US 5,437,999 is not suitable for use with the extremely thin sensor devices of the kind discussed in our co-pending applications in view of the flexibility of the insulating electrode carriers. In general, it is desirable that the disposable sensor be capable- of simple, quick, reliable and effective connection with the power source in the measuring device bymskilled users. It is an object of the present 1o invention to overcome or ameliorate at least one of the disadvantages of the prior art, onto.
provide a useful alternative.
DESCRIPTION OF THE IlfVENTION
According to a first aspect, the invention provides a sensor adapted for electrical connection with a power source having first ccnt~,'~t means', the sensor comprising:
15 a first insulating substrate carrying a first electrode and a second insulating substrate carrying a second electrode, said electrodes being disposed to face each other in spaced apart relationship, a first cut-out portion extending through said f rst insulating substrate and a spacer to expose a first contact area on the second insulating substrate to permit a first contact means 20 to effect electrical connection with the first contact area disposed on the second insulating substrate, the first contact area being in electrically conductive cormection with the second electrode.
The first .contact area may be maintained at a predetermined depth from the first insulating substrate..
s The connection arrangement of US 5,437,999 is not suitable for use with the extremely thin sensor devices of the kind discussed in our co-pending applications in view of the flexibility of the insulating electrode carriers. In general, it is desirable that the disposable sensor be capable- of simple, quick, reliable and effective connection with the power source in the measuring device bymskilled users. It is an object of the present 1o invention to overcome or ameliorate at least one of the disadvantages of the prior art, onto.
provide a useful alternative.
DESCRIPTION OF THE IlfVENTION
According to a first aspect, the invention provides a sensor adapted for electrical connection with a power source having first ccnt~,'~t means', the sensor comprising:
15 a first insulating substrate carrying a first electrode and a second insulating substrate carrying a second electrode, said electrodes being disposed to face each other in spaced apart relationship, a first cut-out portion extending through said f rst insulating substrate and a spacer to expose a first contact area on the second insulating substrate to permit a first contact means 20 to effect electrical connection with the first contact area disposed on the second insulating substrate, the first contact area being in electrically conductive cormection with the second electrode.
The first .contact area may be maintained at a predetermined depth from the first insulating substrate..
-3-According to a second aspect, the invention providcs a sensor according to the first aspect further comprising a second cut-out portion extending through said second insulating substrate and the, or another, spacer to expose a second contact area on the first insulating substrate to permit a second contact means to effect electrical connection with a second contact area disposed on the first insulating substrate, the second contact area being in electrically conductive connection with the first electrode.
The second contact area may be maintained at a predetermined depth from the second insulating substrate: . .
According to a third aspect, the invention also provides ~a sensing system comprising to a sensor according to the first or second aspects and a sensing apparatus including a first contact means and/or second contact means adapted to effect electrical contact with the first and second contact areas respectively.
"Comprising" as herein used is used in an inclusive sense, that is to say in the sense _ _ . :- ~.i excluding" or "containing": 'f h:, tee v. aot intendcd in an exclusive sense ("consisting is of or "composed o~~.
In preferred embodiments the insulating substrate is made of a flexible insulating material. The second electrode and the first contact area are formed from a unified layer of metal deposited on the first substrate, and more preferably deposited by being sputter coated thereon. Suitable metals include, but are not limited to palladium, gold, platinum, 2o iridium, and silver. Carbon may also be used. Desirably the contactor is a metal contactor which is resiliently biased to extend through the first cut-out portion to make contact with the metal first contact area on the second substrate. In highly preferred embodinnents the contactor is adapted for click engagement with the cut-out portion which extends through the first insulating substrate and the space.
The second contact area may be maintained at a predetermined depth from the second insulating substrate: . .
According to a third aspect, the invention also provides ~a sensing system comprising to a sensor according to the first or second aspects and a sensing apparatus including a first contact means and/or second contact means adapted to effect electrical contact with the first and second contact areas respectively.
"Comprising" as herein used is used in an inclusive sense, that is to say in the sense _ _ . :- ~.i excluding" or "containing": 'f h:, tee v. aot intendcd in an exclusive sense ("consisting is of or "composed o~~.
In preferred embodiments the insulating substrate is made of a flexible insulating material. The second electrode and the first contact area are formed from a unified layer of metal deposited on the first substrate, and more preferably deposited by being sputter coated thereon. Suitable metals include, but are not limited to palladium, gold, platinum, 2o iridium, and silver. Carbon may also be used. Desirably the contactor is a metal contactor which is resiliently biased to extend through the first cut-out portion to make contact with the metal first contact area on the second substrate. In highly preferred embodinnents the contactor is adapted for click engagement with the cut-out portion which extends through the first insulating substrate and the space.
-4-With a connector according to the ciurent invention the spacer layer provides extra strength. A rigid connector ran therefore be formed using flexible materials.
This allows a wider range of materials to be utilised. An audible conf rmation of connection can also be simply provided by the current invention unidce the connector described in US
This allows a wider range of materials to be utilised. An audible conf rmation of connection can also be simply provided by the current invention unidce the connector described in US
5,437,999.
BRIEF DESCRIPTION OF THE DRAWINGS
The invention will now be described by way of example only with reference to the accompanying drawings in which:
Figure 1 shows a first embodiment of a sensor according to the invention in plan view.
Figure 2 shovVs a scrap side elevation of the sensor of Figure I in cross-section on line 10-10.
Figure 3 is a diagrammatic enlargement showing a part of the sensor of Figure 2 in engagement with contacts.
. . . - Figure 4 shows an end ele~=atiouvof +~he ~iaar of Figure 3 in se,.~on on line !~ A.
15 Figure 5 shows a second embodiment of the invention in plan view.
Figure 6 shows a cross-section of the embodiment of Figure 5 in end elevation whew viewed on line C-C, Figure 7 shows a cross-section of the embodiment of Figure 5 in side elevation on line D-D.
2o Figure 8 shows a third embodiment of the invention in plan view.
BEST MODES FOR CARRYING OUT THE INVENTION
RT'ith reference to Figures 1 to 3 there is shown a first embodiment of an electrochemical sensor. The sensor comprises a polyester spacer 4 approximately 25 mm x mm and 100 microns thick and having a circular aperhae 8 of 3.4 mm diameter.
Aperhn~e 8 defines a cylindrical cell wall 10. Adhered to one side of spacer 4 is a first insulating substrate polyester sheet 1 having a first coating of palladium 2.
The palladium was sputter coated on sheet 1 at between 4 and 5 millibar pressure in an atmosphere of argon gas to give a uniform coating thickness of about 100-1000 angstroms.
Sheet 1 is s adhered by means of adhesive 3 to spacer 4 with ~tladium coating 2 adjacent spacer 4 and covering one side of aperhne 8.
A second insulating substrate 7 consists of a polyester sheet having a second sputter coating 6 of palladium adhered by means of contact adhesive 5 to the other side of spacer 4 and covering the opposite side of aperture 8. There is thereby defined a cell having ' ~ o .. cylindrical. side wall 10 and closed at one-c~~t~ndsr end by a first electrode of palladi~zm metal 2. The other cylinder end wall is a second electrode formed from palladium 6. The assembly is notched at 9 to provide a means for admission of a solution to the cell, and to allow air to escape.
Adjacent one end 20 a cut~uf a~er~re-lI pierces first insulating layer I and first t 5 metal layer 2. In the present example cut-out 21 is oval-shaped. A
con~esponding cut-out portion 22 in spacer~4 is in registration with cut-out 21. Figure 3 shows a side elevation cross-section of sensor 1 inserted into a receiving slot formed in part 30 of measuring apparatus and to which is mounted a first resilient comaGtor 31 and a second resilient contactor 32. Upon insertion of sensor end 20 into the slot, conta~ctor 31 rides over the 20 outer surface of insulating layer 1 and clicks into the well formed by apertures Z 1 and 22 to engage a first contact area portion 23 of metal layer 6. First contact area 23 is a portion of the same metal layer 6 deposited on insulating layer 7 from which the second electrode is formed and is therefore in electrically conductive communication with the second electrode - __
BRIEF DESCRIPTION OF THE DRAWINGS
The invention will now be described by way of example only with reference to the accompanying drawings in which:
Figure 1 shows a first embodiment of a sensor according to the invention in plan view.
Figure 2 shovVs a scrap side elevation of the sensor of Figure I in cross-section on line 10-10.
Figure 3 is a diagrammatic enlargement showing a part of the sensor of Figure 2 in engagement with contacts.
. . . - Figure 4 shows an end ele~=atiouvof +~he ~iaar of Figure 3 in se,.~on on line !~ A.
15 Figure 5 shows a second embodiment of the invention in plan view.
Figure 6 shows a cross-section of the embodiment of Figure 5 in end elevation whew viewed on line C-C, Figure 7 shows a cross-section of the embodiment of Figure 5 in side elevation on line D-D.
2o Figure 8 shows a third embodiment of the invention in plan view.
BEST MODES FOR CARRYING OUT THE INVENTION
RT'ith reference to Figures 1 to 3 there is shown a first embodiment of an electrochemical sensor. The sensor comprises a polyester spacer 4 approximately 25 mm x mm and 100 microns thick and having a circular aperhae 8 of 3.4 mm diameter.
Aperhn~e 8 defines a cylindrical cell wall 10. Adhered to one side of spacer 4 is a first insulating substrate polyester sheet 1 having a first coating of palladium 2.
The palladium was sputter coated on sheet 1 at between 4 and 5 millibar pressure in an atmosphere of argon gas to give a uniform coating thickness of about 100-1000 angstroms.
Sheet 1 is s adhered by means of adhesive 3 to spacer 4 with ~tladium coating 2 adjacent spacer 4 and covering one side of aperhne 8.
A second insulating substrate 7 consists of a polyester sheet having a second sputter coating 6 of palladium adhered by means of contact adhesive 5 to the other side of spacer 4 and covering the opposite side of aperture 8. There is thereby defined a cell having ' ~ o .. cylindrical. side wall 10 and closed at one-c~~t~ndsr end by a first electrode of palladi~zm metal 2. The other cylinder end wall is a second electrode formed from palladium 6. The assembly is notched at 9 to provide a means for admission of a solution to the cell, and to allow air to escape.
Adjacent one end 20 a cut~uf a~er~re-lI pierces first insulating layer I and first t 5 metal layer 2. In the present example cut-out 21 is oval-shaped. A
con~esponding cut-out portion 22 in spacer~4 is in registration with cut-out 21. Figure 3 shows a side elevation cross-section of sensor 1 inserted into a receiving slot formed in part 30 of measuring apparatus and to which is mounted a first resilient comaGtor 31 and a second resilient contactor 32. Upon insertion of sensor end 20 into the slot, conta~ctor 31 rides over the 20 outer surface of insulating layer 1 and clicks into the well formed by apertures Z 1 and 22 to engage a first contact area portion 23 of metal layer 6. First contact area 23 is a portion of the same metal layer 6 deposited on insulating layer 7 from which the second electrode is formed and is therefore in electrically conductive communication with the second electrode - __
-6-area of cell 8. Contact area 23 is in defined by the diameter of cut-out 20 of spacer 4 in the present example.
In the embodiment shown in Figure 1 a second circular cut-out portion 25 spaced further from edge 20 than aperture 21 extends through second insulating layer
In the embodiment shown in Figure 1 a second circular cut-out portion 25 spaced further from edge 20 than aperture 21 extends through second insulating layer
7 and second s metal layer 6. A cut-out portion 26 (see Figure 2) of spacer 4 corresponds with and registers with cut-out portion 25 of insulating layer 7. Referring again to Figure 3, in use the sensor is configured to permit a second resiliently biased contactor 32.to extead through the well defined by-cut-out portions 25 and 26 whereby resilient contactor 32 engages and makes electrical contact with metal layer 2 at 27 and thereby with the first to electrode 2 of cell 8. - _ .
Resilient connectors 31 and 32 are arranged in a slot 30 of the metering device and are electrically connected in a measuring circuit, In use, the sensor is inserted into slot 30 with edge 20 leading. The first resilient contactor 31 rides over the end margin of the sensor ~ 1 until it encounleis tiist ~aper'~ue ~ 1,22 whereupon it click engages with the .
15 opening and makes electrical contact with the first contact area 23 of metal layer 6. Slight additional insertion of sensor 1 in slot 30 causes the second contactor 32 to click engage with the second aperture 25, 2b and make contact with second contact area 27 of metal layer 2.
Spacer 4 surrounds both apertures and ensures that, despite the intrinsic flexibility of 2o the insulating layers and the thinness of the sensor, electrical contact can be made with reliable precision.
A second embodiment of the invention is shown in Figures 3, 6 and 7 wherein parts corresponding in function to corresponding parts of the embodiment of Figures 1 and 2 are identified by corresponding numerals. The major difference between the second _7_ embodiment and the first is that in the second embodiment cut-out portions 21, 22 are cut from one side edge of sensor 1 while cut-out portions 25, 26 are cut out from the opposite side edge of the sensor 1. In this case coatactors 31 and 32 are spaced laterally and click substantially simultaneously into their respective cut-out opening. The cut-out openings are surrounded on three sides by spacer 4, the fourth side being exposed at respective edges of the sensor.
Although in the embodiment shown in Figures 5, 6 and 7 the openings are at a corresponding distance from end 20 in other embodiments they could be spaced in the longitudinal direction as is the case in the first described embodiment. This ensures that 1 o contact a only made when the sensor it inserted in a correct orientation and ensares correct polarity.
A third embodiment is shown schematically in Figure 8. In this case the openings take the form of slots 2I, 25 extending longitudinally from edge 20. For preference spaa~ceer ~ extentis around ail edges of op~nitt~s 21 and 15 of F figure g but in a less preferred _ embodiment spacer 4 only extends on three sides of slots 21 and 25 in which case click engagement is not obtained or is obtained only if the contacts extend from the opposite direction. However,the advantage that the contact pad area of the sensor is at a predetermined dimension from the opposite face is maintained. If desired the slots can differ in length and co-operation with contacts spaced longitudinally so thax contact with 2o both contacts requires correctly orientated insertion of the sensor.
It will be understood that both construction materials and dimensions are given merely by way of example and that sensors of a differing design or construction may utilise the invention. One, two or more than two contacts may be provided by the means shown.
The invention extends to include a power source or measuring device when conaect~ed to a _g_ sensor by the means. described. Any suitable form of contactor may be used with sensors according to the invention.
Resilient connectors 31 and 32 are arranged in a slot 30 of the metering device and are electrically connected in a measuring circuit, In use, the sensor is inserted into slot 30 with edge 20 leading. The first resilient contactor 31 rides over the end margin of the sensor ~ 1 until it encounleis tiist ~aper'~ue ~ 1,22 whereupon it click engages with the .
15 opening and makes electrical contact with the first contact area 23 of metal layer 6. Slight additional insertion of sensor 1 in slot 30 causes the second contactor 32 to click engage with the second aperture 25, 2b and make contact with second contact area 27 of metal layer 2.
Spacer 4 surrounds both apertures and ensures that, despite the intrinsic flexibility of 2o the insulating layers and the thinness of the sensor, electrical contact can be made with reliable precision.
A second embodiment of the invention is shown in Figures 3, 6 and 7 wherein parts corresponding in function to corresponding parts of the embodiment of Figures 1 and 2 are identified by corresponding numerals. The major difference between the second _7_ embodiment and the first is that in the second embodiment cut-out portions 21, 22 are cut from one side edge of sensor 1 while cut-out portions 25, 26 are cut out from the opposite side edge of the sensor 1. In this case coatactors 31 and 32 are spaced laterally and click substantially simultaneously into their respective cut-out opening. The cut-out openings are surrounded on three sides by spacer 4, the fourth side being exposed at respective edges of the sensor.
Although in the embodiment shown in Figures 5, 6 and 7 the openings are at a corresponding distance from end 20 in other embodiments they could be spaced in the longitudinal direction as is the case in the first described embodiment. This ensures that 1 o contact a only made when the sensor it inserted in a correct orientation and ensares correct polarity.
A third embodiment is shown schematically in Figure 8. In this case the openings take the form of slots 2I, 25 extending longitudinally from edge 20. For preference spaa~ceer ~ extentis around ail edges of op~nitt~s 21 and 15 of F figure g but in a less preferred _ embodiment spacer 4 only extends on three sides of slots 21 and 25 in which case click engagement is not obtained or is obtained only if the contacts extend from the opposite direction. However,the advantage that the contact pad area of the sensor is at a predetermined dimension from the opposite face is maintained. If desired the slots can differ in length and co-operation with contacts spaced longitudinally so thax contact with 2o both contacts requires correctly orientated insertion of the sensor.
It will be understood that both construction materials and dimensions are given merely by way of example and that sensors of a differing design or construction may utilise the invention. One, two or more than two contacts may be provided by the means shown.
The invention extends to include a power source or measuring device when conaect~ed to a _g_ sensor by the means. described. Any suitable form of contactor may be used with sensors according to the invention.
Claims (18)
1. A method of making a sensor adapted for electrical connection with a power source having a contactor, the method comprising the steps of:
providing a first insulating substrate carrying a first electrode and having an aperture, a spacer having an aperture, and a second insulating substrate carrying a second electrode;
adhering the first insulating substrate to one side of the spacer, whereby the first electrode defines a first end wall of an electrochemical cell;
adhering the second insulating substrate to an opposite side of the spacer, whereby the second electrode defines a second end wall of the cell;
wherein the aperture of the first insulating substrate defines a first cut-out aperture that provides a first contact area on the second insulating substrate that is adapted to permit electrical contact with the second electrode.
providing a first insulating substrate carrying a first electrode and having an aperture, a spacer having an aperture, and a second insulating substrate carrying a second electrode;
adhering the first insulating substrate to one side of the spacer, whereby the first electrode defines a first end wall of an electrochemical cell;
adhering the second insulating substrate to an opposite side of the spacer, whereby the second electrode defines a second end wall of the cell;
wherein the aperture of the first insulating substrate defines a first cut-out aperture that provides a first contact area on the second insulating substrate that is adapted to permit electrical contact with the second electrode.
2. A method according to claim 1, wherein each insulating substrate is formed from a flexible insulating material.
3. A method according to claim 2, wherein the flexible insulating material is polyester.
4. A method according to claim 1, further comprising the step of depositing metal on the first and second insulating substrates to form the first and second electrodes and the first contact area.
5. A method according to claim 4, wherein the metal is selected from the group consisting of palladium, gold, platinum, iridium and silver.
6. A method according to claim 4, wherein the metal is 10-1000 nanometers thick.
7. A method according to claim 4, further comprising the step of depositing the layer of metal is on the insulating substrate by sputter coating.
8. A method according to claim 1, wherein each electrode and the first contact area are formed from carbon.
9. A method according to claim 1, wherein the first cut-out aperture is spaced adjacent one end of the sensor.
10. A method according to claim 1, wherein the first cut-out aperture is cut from an edge of the sensor such that the first cut-out aperture is open on at least one edge of the sensor.
11. A method according to claim 1, wherein at least one of the insulating substrates or the spacer extends around the entire periphery of the first cut-out aperture.
12. A method according to claim 1, wherein the spacer comprises a cut-out aperture that corresponds to the first cut-out aperture of the first insulating substrate.
13. A method according to claim 12, wherein the cut-out aperture of the spacer is in registration with the first cut-out aperture of the first insulating substrate.
14. A method according to claim 1, wherein the first cut-out aperture is adapted for click engagement with a contactor.
15. A method according to claim 1, further providing that the second insulating substrate have an aperture, wherein the aperture defines a second cut-out aperture that provides a second contact area on the first insulating substrate that is adapted to permit electrical contact with the first electrode.
16. A method according to claim 15, wherein the first and second contact areas are laterally spaced apart relative to the longitudinal axis of the sensor.
17. A method according to claim 15, wherein the first and second contact areas are longitudinally spaced apart relative to the longitudinal axis of the sensor.
18. A method according to claim 15, wherein the first and second contact areas are laterally and longitudinally spaced relative to the longitudinal axis of the sensor.
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AUPO5813A AUPO581397A0 (en) | 1997-03-21 | 1997-03-21 | Sensor connection means |
AUPO5813 | 1997-03-21 | ||
CA002284634A CA2284634C (en) | 1997-03-21 | 1998-03-20 | Sensor connection means |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002284634A Division CA2284634C (en) | 1997-03-21 | 1998-03-20 | Sensor connection means |
Publications (2)
Publication Number | Publication Date |
---|---|
CA2550198A1 CA2550198A1 (en) | 1998-10-01 |
CA2550198C true CA2550198C (en) | 2007-06-19 |
Family
ID=3800116
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002284634A Expired - Lifetime CA2284634C (en) | 1997-03-21 | 1998-03-20 | Sensor connection means |
CA002550198A Expired - Lifetime CA2550198C (en) | 1997-03-21 | 1998-03-20 | Sensor connection means |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002284634A Expired - Lifetime CA2284634C (en) | 1997-03-21 | 1998-03-20 | Sensor connection means |
Country Status (15)
Country | Link |
---|---|
US (4) | US6379513B1 (en) |
EP (1) | EP0968415B1 (en) |
JP (1) | JP3766109B2 (en) |
KR (2) | KR100576660B1 (en) |
CN (4) | CN1936560B (en) |
AT (1) | ATE475881T1 (en) |
AU (2) | AUPO581397A0 (en) |
BR (1) | BR9807987B1 (en) |
CA (2) | CA2284634C (en) |
DE (1) | DE69841786D1 (en) |
ES (1) | ES2349388T3 (en) |
HK (1) | HK1064154A1 (en) |
IL (3) | IL154066A0 (en) |
RU (2) | RU2213345C2 (en) |
WO (1) | WO1998043073A1 (en) |
Families Citing this family (151)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6413410B1 (en) | 1996-06-19 | 2002-07-02 | Lifescan, Inc. | Electrochemical cell |
AUPN661995A0 (en) | 1995-11-16 | 1995-12-07 | Memtec America Corporation | Electrochemical cell 2 |
FR2748605B1 (en) * | 1996-05-07 | 1998-08-07 | Gerard Lemaire | METHOD FOR MANUFACTURING A BASIC BATTERY GENERATOR OR INTELLIGENT BATTERY |
US6632349B1 (en) | 1996-11-15 | 2003-10-14 | Lifescan, Inc. | Hemoglobin sensor |
EP0958495B1 (en) | 1997-02-06 | 2002-11-13 | Therasense, Inc. | Small volume in vitro analyte sensor |
AUPO581397A0 (en) * | 1997-03-21 | 1997-04-17 | Memtec America Corporation | Sensor connection means |
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 |
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 |
US6591125B1 (en) | 2000-06-27 | 2003-07-08 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
US6338790B1 (en) * | 1998-10-08 | 2002-01-15 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
US20050103624A1 (en) * | 1999-10-04 | 2005-05-19 | Bhullar Raghbir S. | Biosensor and method of making |
US6616819B1 (en) * | 1999-11-04 | 2003-09-09 | Therasense, Inc. | Small volume in vitro analyte sensor and methods |
US6612111B1 (en) * | 2000-03-27 | 2003-09-02 | Lifescan, Inc. | Method and device for sampling and analyzing interstitial fluid and whole blood samples |
US6444115B1 (en) | 2000-07-14 | 2002-09-03 | Lifescan, Inc. | Electrochemical method for measuring chemical reaction rates |
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 |
CN100405051C (en) * | 2001-05-30 | 2008-07-23 | 爱-森斯株式会社 | Biosensor |
US9795747B2 (en) | 2010-06-02 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | Methods and apparatus for lancet actuation |
US8337419B2 (en) | 2002-04-19 | 2012-12-25 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
CA2448905C (en) * | 2001-06-12 | 2010-09-07 | Pelikan Technologies, Inc. | Blood sampling apparatus and method |
US7981056B2 (en) | 2002-04-19 | 2011-07-19 | Pelikan Technologies, Inc. | Methods and apparatus for lancet actuation |
US7344507B2 (en) | 2002-04-19 | 2008-03-18 | Pelikan Technologies, Inc. | Method and apparatus for lancet actuation |
ATE497731T1 (en) * | 2001-06-12 | 2011-02-15 | Pelikan Technologies Inc | DEVICE FOR INCREASING THE SUCCESS RATE OF BLOOD YIELD OBTAINED BY A FINGER PICK |
US7025774B2 (en) * | 2001-06-12 | 2006-04-11 | Pelikan Technologies, Inc. | Tissue penetration device |
US9427532B2 (en) | 2001-06-12 | 2016-08-30 | 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 |
ATE485766T1 (en) | 2001-06-12 | 2010-11-15 | Pelikan Technologies Inc | ELECTRICAL ACTUATING ELEMENT FOR A LANCET |
WO2002100254A2 (en) | 2001-06-12 | 2002-12-19 | Pelikan Technologies, Inc. | Method and apparatus for lancet launching device integrated onto a blood-sampling cartridge |
US9226699B2 (en) | 2002-04-19 | 2016-01-05 | Sanofi-Aventis Deutschland Gmbh | Body fluid sampling module with a continuous compression tissue interface surface |
ATE479089T1 (en) * | 2001-11-16 | 2010-09-15 | Stefan Ufer | FLEXIBLE SENSOR AND MANUFACTURING METHOD |
US6946067B2 (en) * | 2002-01-04 | 2005-09-20 | Lifescan, Inc. | Method of forming an electrical connection between an electrochemical cell and a meter |
US6863800B2 (en) * | 2002-02-01 | 2005-03-08 | Abbott Laboratories | Electrochemical biosensor strip for analysis of liquid samples |
US20060134713A1 (en) | 2002-03-21 | 2006-06-22 | Lifescan, Inc. | Biosensor apparatus and methods of use |
US6866758B2 (en) * | 2002-03-21 | 2005-03-15 | Roche Diagnostics Corporation | Biosensor |
US7892183B2 (en) | 2002-04-19 | 2011-02-22 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
US7909778B2 (en) | 2002-04-19 | 2011-03-22 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7229458B2 (en) | 2002-04-19 | 2007-06-12 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7141058B2 (en) * | 2002-04-19 | 2006-11-28 | Pelikan Technologies, Inc. | Method and apparatus for a body fluid sampling device using illumination |
US7563232B2 (en) * | 2002-04-19 | 2009-07-21 | 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 |
US8579831B2 (en) | 2002-04-19 | 2013-11-12 | Sanofi-Aventis Deutschland Gmbh | 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 |
US7481776B2 (en) * | 2002-04-19 | 2009-01-27 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7648468B2 (en) | 2002-04-19 | 2010-01-19 | Pelikon Technologies, Inc. | Method and apparatus for penetrating tissue |
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 |
US7371247B2 (en) * | 2002-04-19 | 2008-05-13 | Pelikan Technologies, Inc | Method and apparatus for penetrating tissue |
US9248267B2 (en) | 2002-04-19 | 2016-02-02 | Sanofi-Aventis Deustchland Gmbh | Tissue penetration device |
US7717863B2 (en) | 2002-04-19 | 2010-05-18 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7892185B2 (en) | 2002-04-19 | 2011-02-22 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
US7674232B2 (en) | 2002-04-19 | 2010-03-09 | 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 |
US7901362B2 (en) | 2002-04-19 | 2011-03-08 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US9314194B2 (en) | 2002-04-19 | 2016-04-19 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
US7547287B2 (en) | 2002-04-19 | 2009-06-16 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7226461B2 (en) | 2002-04-19 | 2007-06-05 | Pelikan Technologies, Inc. | Method and apparatus for a multi-use body fluid sampling device with sterility barrier release |
US8784335B2 (en) | 2002-04-19 | 2014-07-22 | Sanofi-Aventis Deutschland Gmbh | Body fluid sampling device with a capacitive sensor |
US7331931B2 (en) | 2002-04-19 | 2008-02-19 | 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 |
US7976476B2 (en) | 2002-04-19 | 2011-07-12 | Pelikan Technologies, Inc. | Device and method for variable speed lancet |
US9795334B2 (en) | 2002-04-19 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
US8574895B2 (en) | 2002-12-30 | 2013-11-05 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus using optical techniques to measure analyte levels |
AU2003300154A1 (en) * | 2002-12-31 | 2004-07-29 | Pelikan Technologies Inc. | Method and apparatus for loading penetrating members |
ATE476137T1 (en) | 2003-05-30 | 2010-08-15 | Pelikan Technologies Inc | METHOD AND DEVICE FOR INJECTING LIQUID |
WO2004107964A2 (en) | 2003-06-06 | 2004-12-16 | Pelikan Technologies, Inc. | Blood harvesting device with electronic control |
WO2006001797A1 (en) | 2004-06-14 | 2006-01-05 | Pelikan Technologies, Inc. | Low pain penetrating |
US7544277B2 (en) * | 2003-06-12 | 2009-06-09 | Bayer Healthcare, Llc | Electrochemical test sensors |
US7488601B2 (en) | 2003-06-20 | 2009-02-10 | Roche Diagnostic Operations, Inc. | System and method for determining an abused sensor during analyte measurement |
US7718439B2 (en) | 2003-06-20 | 2010-05-18 | Roche Diagnostics Operations, Inc. | System and 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 |
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 |
US7452457B2 (en) | 2003-06-20 | 2008-11-18 | Roche Diagnostics Operations, Inc. | System and method for analyte measurement using dose sufficiency electrodes |
US8058077B2 (en) | 2003-06-20 | 2011-11-15 | Roche Diagnostics Operations, Inc. | 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 |
US7645421B2 (en) | 2003-06-20 | 2010-01-12 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
US8071030B2 (en) | 2003-06-20 | 2011-12-06 | Roche Diagnostics Operations, Inc. | Test strip with flared sample receiving chamber |
ES2681398T3 (en) * | 2003-06-20 | 2018-09-12 | F. Hoffmann-La Roche Ag | Test strip with widened sample reception chamber |
US8206565B2 (en) | 2003-06-20 | 2012-06-26 | Roche Diagnostics Operation, Inc. | System and method for coding information on a biosensor test strip |
EP1671096A4 (en) | 2003-09-29 | 2009-09-16 | Pelikan Technologies Inc | 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 |
BRPI0507376A (en) | 2004-02-06 | 2007-07-10 | Bayer Healthcare Llc | oxidizable species as an internal reference for biosensors and method of use |
US8828203B2 (en) | 2004-05-20 | 2014-09-09 | Sanofi-Aventis Deutschland Gmbh | Printable hydrogels 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 |
US7569126B2 (en) | 2004-06-18 | 2009-08-04 | Roche Diagnostics Operations, Inc. | System and method for quality assurance of a biosensor test strip |
US8652831B2 (en) | 2004-12-30 | 2014-02-18 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for analyte measurement test time |
US7545272B2 (en) | 2005-02-08 | 2009-06-09 | Therasense, Inc. | RF tag on test strips, test strip vials and boxes |
US8323464B2 (en) * | 2005-05-25 | 2012-12-04 | Universal Biosensors Pty Ltd | Method and apparatus for electrochemical analysis |
US8192599B2 (en) * | 2005-05-25 | 2012-06-05 | Universal Biosensors Pty Ltd | Method and apparatus for electrochemical analysis |
AU2006272909B2 (en) | 2005-07-20 | 2013-02-07 | Bayer Healthcare Llc | Gated amperometry |
US20070037057A1 (en) * | 2005-08-12 | 2007-02-15 | Douglas Joel S | Non printed small volume in vitro analyte sensor and methods |
KR101477815B1 (en) | 2005-09-30 | 2015-01-02 | 바이엘 헬스케어 엘엘씨 | Gated voltammetry |
US7749371B2 (en) | 2005-09-30 | 2010-07-06 | Lifescan, Inc. | Method and apparatus for rapid electrochemical analysis |
EP1780541B1 (en) * | 2005-10-25 | 2008-10-15 | F.Hoffmann-La Roche Ag | Analysis device for analysing a sample on a test element |
ES2389382T3 (en) | 2006-02-21 | 2012-10-25 | Universal Biosensors Pty Limited | Fluid transfer mechanism |
US8163162B2 (en) | 2006-03-31 | 2012-04-24 | Lifescan, Inc. | Methods and apparatus for analyzing a sample in the presence of interferents |
US8529751B2 (en) | 2006-03-31 | 2013-09-10 | Lifescan, Inc. | Systems and methods for discriminating control solution from a physiological sample |
US8398443B2 (en) | 2006-04-21 | 2013-03-19 | Roche Diagnostics Operations, Inc. | Biological testing system and connector therefor |
EP2176651B1 (en) * | 2007-07-26 | 2015-09-09 | Agamatrix, Inc. | Electrochemical test strips |
US8778168B2 (en) * | 2007-09-28 | 2014-07-15 | Lifescan, Inc. | Systems and methods of discriminating control solution from a physiological sample |
WO2009076302A1 (en) | 2007-12-10 | 2009-06-18 | Bayer Healthcare Llc | Control markers for auto-detection of control solution and methods of use |
US8097674B2 (en) * | 2007-12-31 | 2012-01-17 | Bridgestone Corporation | Amino alkoxy-modified silsesquioxanes in silica-filled rubber with low volatile organic chemical evolution |
US8603768B2 (en) | 2008-01-17 | 2013-12-10 | Lifescan, Inc. | System and method for measuring an analyte in a sample |
JP2009178367A (en) * | 2008-01-31 | 2009-08-13 | Sumitomo Electric Ind Ltd | Biosensor measuring device |
EP2265324B1 (en) | 2008-04-11 | 2015-01-28 | Sanofi-Aventis Deutschland GmbH | Integrated analyte measurement system |
US8551320B2 (en) * | 2008-06-09 | 2013-10-08 | Lifescan, Inc. | System and method for measuring an analyte in a sample |
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 |
US8173008B2 (en) | 2009-06-24 | 2012-05-08 | Lifescan, Inc. | Method for determining an analyte in a bodily fluid sample using an analyte test strip with combination electrode contact and meter identification feature |
US20100332445A1 (en) * | 2009-06-30 | 2010-12-30 | Lifescan, Inc. | Analyte testing method and system |
BRPI1016004A2 (en) * | 2009-06-30 | 2016-04-26 | Lifescan Inc | methods for testing analytes and device for calculating basal insulin therapy. |
EP2455875A3 (en) * | 2009-06-30 | 2013-01-16 | Lifescan Scotland Limited | System and method for diabetes management |
BR112012007134A2 (en) * | 2009-09-29 | 2016-08-23 | Lifescan Scotland Ltd | diabetes control analyte test device and method |
US8221994B2 (en) | 2009-09-30 | 2012-07-17 | Cilag Gmbh International | Adhesive composition for use in an immunosensor |
US8877034B2 (en) * | 2009-12-30 | 2014-11-04 | Lifescan, Inc. | Systems, devices, and methods for measuring whole blood hematocrit based on initial fill velocity |
US8101065B2 (en) | 2009-12-30 | 2012-01-24 | Lifescan, Inc. | Systems, devices, and methods for improving accuracy of biosensors using fill time |
US20110208435A1 (en) | 2010-02-25 | 2011-08-25 | Lifescan Scotland Ltd. | Capacitance detection in electrochemical assays |
CN102802522B (en) | 2010-02-25 | 2015-12-09 | 生命扫描苏格兰有限公司 | There is analyte testing method and the system of insulin administration safety warning |
US8742773B2 (en) | 2010-02-25 | 2014-06-03 | Lifescan Scotland Limited | Capacitance detection in electrochemical assay with improved response |
EP2590098B1 (en) | 2010-02-25 | 2014-11-05 | Lifescan Scotland Limited | Analyte testing method and system with high and low blood glucose trends notification |
US8773106B2 (en) | 2010-02-25 | 2014-07-08 | Lifescan Scotland Limited | Capacitance detection in electrochemical assay with improved sampling time offset |
ES2456899T3 (en) | 2010-02-25 | 2014-04-23 | Lifescan Scotland Limited | Capacitance detection in electrochemical test |
US8965476B2 (en) | 2010-04-16 | 2015-02-24 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
JP5795368B2 (en) | 2010-06-30 | 2015-10-14 | ライフスキャン・スコットランド・リミテッドLifeScan Scotland, Ltd. | Method, system and apparatus for ensuring statistical power for message display of average pre-meal and post-meal glucose differences |
ES2478255T3 (en) | 2010-08-02 | 2014-07-21 | Cilag Gmbh International | System and methods for higher pressure for temperature correction of glucose results for control solution |
US8617370B2 (en) | 2010-09-30 | 2013-12-31 | Cilag Gmbh International | Systems and methods of discriminating between a control sample and a test fluid using capacitance |
US8932445B2 (en) | 2010-09-30 | 2015-01-13 | Cilag Gmbh International | Systems and methods for improved stability of electrochemical sensors |
US20130229288A1 (en) | 2010-11-15 | 2013-09-05 | Lifescan Scotland Limited | Server-side initiated communication with analyte meter-side completed data transfer |
US8956518B2 (en) | 2011-04-20 | 2015-02-17 | Lifescan, Inc. | Electrochemical sensors with carrier field |
US9157881B2 (en) * | 2011-05-16 | 2015-10-13 | Panasonic Healthcare Holdings Co., Ltd. | Organism sample measurement sensor and housing container that houses same |
US9903830B2 (en) | 2011-12-29 | 2018-02-27 | Lifescan Scotland Limited | Accurate analyte measurements for electrochemical test strip based on sensed physical characteristic(s) of the sample containing the analyte |
EP2833790B1 (en) | 2012-03-30 | 2017-12-27 | Lifescan Scotland Limited | Battery status detection and storage method and system in medical monitoring |
BR112015005055A2 (en) | 2012-09-07 | 2017-07-04 | Cilag Gmbh Int | electrochemical sensors and method for their manufacture |
GB2505694B (en) * | 2012-09-07 | 2017-03-22 | Lifescan Scotland Ltd | Electrochemical-based analytical test strip with bare interferent electrodes |
US9005426B2 (en) | 2012-09-28 | 2015-04-14 | Cilag Gmbh International | System and method for determining hematocrit insensitive glucose concentration |
US9080196B2 (en) | 2012-09-28 | 2015-07-14 | Cilag Gmbh International | System and method for determining hematocrit insensitive glucose concentration |
US8926369B2 (en) | 2012-12-20 | 2015-01-06 | Lifescan Scotland Limited | Electrical connector for substrate having conductive tracks |
US9435762B2 (en) | 2013-06-27 | 2016-09-06 | Lifescan Scotland Limited | Fill error trap for an analyte measurement determined from a specified sampling time derived from a sensed physical characteristic of the sample containing the analyte |
US9835578B2 (en) | 2013-06-27 | 2017-12-05 | Lifescan Scotland Limited | Temperature compensation for an analyte measurement determined from a specified sampling time derived from a sensed physical characteristic of the sample containing the analyte |
US9435764B2 (en) | 2013-06-27 | 2016-09-06 | Lifescan Scotland Limited | Transient signal error trap for an analyte measurement determined from a specified sampling time derived from a sensed physical characteristic of the sample containing the analyte |
US9243276B2 (en) | 2013-08-29 | 2016-01-26 | Lifescan Scotland Limited | Method and system to determine hematocrit-insensitive glucose values in a fluid sample |
US9459231B2 (en) | 2013-08-29 | 2016-10-04 | Lifescan Scotland Limited | Method and system to determine erroneous measurement signals during a test measurement sequence |
US9828621B2 (en) | 2013-09-10 | 2017-11-28 | Lifescan Scotland Limited | Anomalous signal error trap for an analyte measurement determined from a specified sampling time derived from a sensed physical characteristic of the sample containing the analyte |
US20150096906A1 (en) * | 2013-10-07 | 2015-04-09 | Cilag Gmbh International | Biosensor with bypass electrodes |
US20160091451A1 (en) | 2014-09-25 | 2016-03-31 | Lifescan Scotland Limited | Accurate analyte measurements for electrochemical test strip to determine analyte measurement time based on measured temperature, physical characteristic and estimated analyte value |
US20160091450A1 (en) | 2014-09-25 | 2016-03-31 | Lifescan Scotland Limited | Accurate analyte measurements for electrochemical test strip to determine analyte measurement time based on measured temperature, physical characteristic and estimated analyte value and their temperature compensated values |
DK178995B1 (en) * | 2015-09-13 | 2017-07-31 | Pro-Ino Dev Aps | Handheld apparatus for testing a sample of body fluid |
DK178966B1 (en) * | 2015-09-13 | 2017-07-10 | Pro-Ino Dev Aps | Handheld apparatus for testing a sample of prepared food for allergens and/or food intolerance ingredients |
Family Cites Families (55)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4303887A (en) | 1979-10-29 | 1981-12-01 | United States Surgical Corporation | Electrical liquid conductivity measuring system |
US4301412A (en) | 1979-10-29 | 1981-11-17 | United States Surgical Corporation | Liquid conductivity measuring system and sample cards therefor |
US4301414A (en) | 1979-10-29 | 1981-11-17 | United States Surgical Corporation | Disposable sample card and method of making same |
CA1226036A (en) | 1983-05-05 | 1987-08-25 | Irving J. Higgins | Analytical equipment and sensor electrodes therefor |
US5509410A (en) | 1983-06-06 | 1996-04-23 | Medisense, Inc. | Strip electrode including screen printing of a single layer |
US5141868A (en) | 1984-06-13 | 1992-08-25 | Internationale Octrooi Maatschappij "Octropa" Bv | Device for use in chemical test procedures |
AU581669B2 (en) | 1984-06-13 | 1989-03-02 | Applied Research Systems Ars Holding N.V. | Photometric instruments, their use in methods of optical analysis, and ancillary devices therefor |
CN85107234A (en) * | 1985-09-24 | 1987-04-01 | 物理传感器公司 | Use the chemical selection sensor of admittance modulating membrane |
US4900424A (en) | 1986-11-28 | 1990-02-13 | Unilever Patent Holdings B.V. | Electrochemical measurement cell |
CN87201212U (en) * | 1987-04-06 | 1988-03-09 | 上海第二工业大学 | Oxygen content sensor |
JP2690053B2 (en) * | 1988-01-08 | 1997-12-10 | マルハ株式会社 | Biosensor |
US5108564A (en) * | 1988-03-15 | 1992-04-28 | Tall Oak Ventures | Method and apparatus for amperometric diagnostic analysis |
US5128015A (en) | 1988-03-15 | 1992-07-07 | Tall Oak Ventures | Method and apparatus for amperometric diagnostic analysis |
DE68924026T3 (en) | 1988-03-31 | 2008-01-10 | Matsushita Electric Industrial Co., Ltd., Kadoma | BIOSENSOR AND ITS MANUFACTURE. |
JPH01284748A (en) | 1988-05-11 | 1989-11-16 | Omron Tateisi Electron Co | Connector for connecting sensor |
CA1316572C (en) | 1988-07-18 | 1993-04-20 | Martin J. Patko | Precalibrated, disposable, electrochemical sensors |
GB8817421D0 (en) | 1988-07-21 | 1988-08-24 | Medisense Inc | Bioelectrochemical electrodes |
JPH03128848A (en) | 1989-10-12 | 1991-05-31 | Toshiba Corp | Dancer roll control device |
EP0429076B1 (en) | 1989-11-24 | 1996-01-31 | Matsushita Electric Industrial Co., Ltd. | Preparation of biosensor |
US5508171A (en) | 1989-12-15 | 1996-04-16 | Boehringer Mannheim Corporation | Assay method with enzyme electrode system |
US5320732A (en) | 1990-07-20 | 1994-06-14 | Matsushita Electric Industrial Co., Ltd. | Biosensor and measuring apparatus using the same |
ZA92804B (en) | 1991-02-06 | 1992-12-30 | Igen Inc | Methods and apparatus for improved luminescence assays |
US5192415A (en) | 1991-03-04 | 1993-03-09 | Matsushita Electric Industrial Co., Ltd. | Biosensor utilizing enzyme and a method for producing the same |
JP3118015B2 (en) | 1991-05-17 | 2000-12-18 | アークレイ株式会社 | Biosensor and separation and quantification method using the same |
CA2074752A1 (en) | 1991-07-29 | 1993-01-30 | Tadakazu Yamauchi | Process and device for specific binding assay |
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 |
EP0560336B1 (en) | 1992-03-12 | 1998-05-06 | Matsushita Electric Industrial Co., Ltd. | A biosensor including a catalyst made from phosphate |
JP2541081B2 (en) | 1992-08-28 | 1996-10-09 | 日本電気株式会社 | Biosensor and method of manufacturing and using biosensor |
US5400782A (en) * | 1992-10-07 | 1995-03-28 | Graphic Controls Corporation | Integral medical electrode including a fusible conductive substrate |
US5372932A (en) | 1992-12-22 | 1994-12-13 | Eastman Kodak Company | Analytical element and method for the determination of a specific binding ligand using a 4-hydroxy or 4-alkoxyarylacetamide as stabilizer |
FR2701117B1 (en) * | 1993-02-04 | 1995-03-10 | Asulab Sa | Electrochemical measurement system with multizone sensor, and its application to glucose measurement. |
US5338429A (en) * | 1993-03-05 | 1994-08-16 | Mine Safety Appliances Company | Electrochemical toxic gas sensor |
US5385846A (en) | 1993-06-03 | 1995-01-31 | Boehringer Mannheim Corporation | Biosensor and method for hematocrit determination |
US5405511A (en) | 1993-06-08 | 1995-04-11 | Boehringer Mannheim Corporation | Biosensing meter with ambient temperature estimation method and system |
US5413690A (en) | 1993-07-23 | 1995-05-09 | Boehringer Mannheim Corporation | Potentiometric biosensor and the method of its use |
FR2710413B1 (en) * | 1993-09-21 | 1995-11-03 | Asulab Sa | Measuring device for removable sensors. |
FR2710414A1 (en) | 1993-09-21 | 1995-03-31 | Asulab Sa | Measuring device for removable multi-zone sensors comprising an ejection system for these sensors. |
GB9325189D0 (en) | 1993-12-08 | 1994-02-09 | Unilever Plc | Methods and apparatus for electrochemical measurements |
US5437999A (en) * | 1994-02-22 | 1995-08-01 | Boehringer Mannheim Corporation | Electrochemical sensor |
AUPM506894A0 (en) | 1994-04-14 | 1994-05-05 | Memtec Limited | Novel electrochemical cells |
JP3498105B2 (en) * | 1995-04-07 | 2004-02-16 | アークレイ株式会社 | Sensor, method for manufacturing the same, and measuring method using the sensor |
AUPN363995A0 (en) | 1995-06-19 | 1995-07-13 | Memtec Limited | Electrochemical cell |
US5628890A (en) | 1995-09-27 | 1997-05-13 | Medisense, Inc. | Electrochemical sensor |
US6174420B1 (en) * | 1996-11-15 | 2001-01-16 | Usf Filtration And Separations Group, Inc. | Electrochemical cell |
AUPN661995A0 (en) * | 1995-11-16 | 1995-12-07 | Memtec America Corporation | Electrochemical cell 2 |
JPH09145665A (en) | 1995-11-24 | 1997-06-06 | Mitsubishi Pencil Co Ltd | Oxygen sensor |
JPH09159642A (en) | 1995-12-04 | 1997-06-20 | Dainippon Printing Co Ltd | Bio sensor and its manufacturing method |
JPH09159644A (en) | 1995-12-11 | 1997-06-20 | Dainippon Printing Co Ltd | Biosensor and manufacture thereof |
IL116921A (en) | 1996-01-26 | 2000-11-21 | Yissum Res Dev Co | Electrochemical system for determination of an analyte in a liquid medium |
KR20000070821A (en) | 1997-02-06 | 2000-11-25 | 프란시스 제이 메이어 | Electrochemical probes for detection of molecular interactions and drug discovery |
EP0958495B1 (en) * | 1997-02-06 | 2002-11-13 | Therasense, Inc. | Small volume in vitro analyte sensor |
AUPO581397A0 (en) | 1997-03-21 | 1997-04-17 | Memtec America Corporation | Sensor connection means |
AUPO585797A0 (en) | 1997-03-25 | 1997-04-24 | Memtec America Corporation | Improved electrochemical cell |
US5997817A (en) | 1997-12-05 | 1999-12-07 | Roche Diagnostics Corporation | Electrochemical biosensor test strip |
MXPA03000382A (en) | 2000-07-14 | 2004-09-13 | Lifescan Inc | Electrochemical method for measuring chemical reaction rates. |
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1997
- 1997-03-21 AU AUPO5813A patent/AUPO581397A0/en not_active Abandoned
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1998
- 1998-03-20 CN CN2006100958001A patent/CN1936560B/en not_active Expired - Lifetime
- 1998-03-20 ES ES98907775T patent/ES2349388T3/en not_active Expired - Lifetime
- 1998-03-20 AT AT98907775T patent/ATE475881T1/en active
- 1998-03-20 IL IL15406698A patent/IL154066A0/en active IP Right Grant
- 1998-03-20 CA CA002284634A patent/CA2284634C/en not_active Expired - Lifetime
- 1998-03-20 JP JP54453298A patent/JP3766109B2/en not_active Expired - Lifetime
- 1998-03-20 CN CNB2005100939913A patent/CN100507541C/en not_active Expired - Lifetime
- 1998-03-20 CN CNB031306187A patent/CN1229639C/en not_active Expired - Lifetime
- 1998-03-20 KR KR1020057007153A patent/KR100576660B1/en not_active IP Right Cessation
- 1998-03-20 CA CA002550198A patent/CA2550198C/en not_active Expired - Lifetime
- 1998-03-20 WO PCT/AU1998/000184 patent/WO1998043073A1/en active IP Right Grant
- 1998-03-20 KR KR10-1999-7008615A patent/KR100526086B1/en not_active IP Right Cessation
- 1998-03-20 IL IL13198098A patent/IL131980A/en not_active IP Right Cessation
- 1998-03-20 CN CN98804325A patent/CN1117275C/en not_active Expired - Lifetime
- 1998-03-20 BR BRPI9807987-5A patent/BR9807987B1/en not_active IP Right Cessation
- 1998-03-20 DE DE69841786T patent/DE69841786D1/en not_active Expired - Lifetime
- 1998-03-20 RU RU99122339/28A patent/RU2213345C2/en active
- 1998-03-20 EP EP98907775A patent/EP0968415B1/en not_active Expired - Lifetime
- 1998-03-20 AU AU66044/98A patent/AU745740B2/en not_active Expired
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1999
- 1999-09-20 US US09/399,512 patent/US6379513B1/en not_active Expired - Lifetime
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2001
- 2001-11-13 US US10/012,680 patent/US7045046B2/en not_active Expired - Lifetime
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2003
- 2003-01-21 IL IL154066A patent/IL154066A/en not_active IP Right Cessation
- 2003-04-28 RU RU2003112450/28A patent/RU2320986C2/en active
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2004
- 2004-09-07 HK HK04106747A patent/HK1064154A1/en not_active IP Right Cessation
- 2004-09-24 US US10/950,111 patent/US20050034983A1/en not_active Abandoned
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2006
- 2006-05-15 US US11/434,442 patent/US20060201804A1/en not_active Abandoned
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