CA2284634C - Sensor connection means - Google Patents
Sensor connection means Download PDFInfo
- Publication number
- CA2284634C CA2284634C CA002284634A CA2284634A CA2284634C CA 2284634 C CA2284634 C CA 2284634C CA 002284634 A CA002284634 A CA 002284634A CA 2284634 A CA2284634 A CA 2284634A CA 2284634 C CA2284634 C CA 2284634C
- Authority
- CA
- Canada
- Prior art keywords
- sensor according
- sensor
- cut
- contact area
- insulating substrate
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Classifications
-
- 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 (7). This permits the electrical contact means (31) to effect electrical connection with the first contact (23) which in tum 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 5 quantitative analysis, for example, of glucose levels in blood, for pH
measurement, or the tike. 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 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 pan of a cell. At one end of the assembly the electrode substrates are cut to provide laterally spaced protruding 15 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 turn 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 2o 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 96132635, WO 97/0041, WO 97/18465 and WO 97/18464 there are described various very thin electrochemical cells. Each __ _ CA 02284634 1999-09-20 cell is defined between facing spaced apart electrodes which are formed as thin metal 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 ~m or less.
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 by unskilled users. It is an object of the present 1 o invention to overcome or ameliorate at least one of the disadvantages of the prior art, or to provide a useful alternative.
DESCRIPTION OF THE INVENTION
According to a first aspect, the invention provides a sensor adapted for electrical connection with a power source having first contact 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 first insulating substrate and a spacer to expose a first contact area on the second insulating substrate to permit a first contact means 2o to effect electrical connection with the first contact area disposed on the second insulating substrate, the first contact area being in electrically conductive connection with the second electrode.
The first contact area may be maintained at a predetermined depth from the first insulating substrate.
TECHNICAL FIELD
This invention relates to disposable electrochemical sensors of the type used for 5 quantitative analysis, for example, of glucose levels in blood, for pH
measurement, or the tike. 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 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 pan of a cell. At one end of the assembly the electrode substrates are cut to provide laterally spaced protruding 15 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 turn 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 2o 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 96132635, WO 97/0041, WO 97/18465 and WO 97/18464 there are described various very thin electrochemical cells. Each __ _ CA 02284634 1999-09-20 cell is defined between facing spaced apart electrodes which are formed as thin metal 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 ~m or less.
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 by unskilled users. It is an object of the present 1 o invention to overcome or ameliorate at least one of the disadvantages of the prior art, or to provide a useful alternative.
DESCRIPTION OF THE INVENTION
According to a first aspect, the invention provides a sensor adapted for electrical connection with a power source having first contact 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 first insulating substrate and a spacer to expose a first contact area on the second insulating substrate to permit a first contact means 2o to effect electrical connection with the first contact area disposed on the second insulating substrate, the first contact area being in electrically conductive connection with the second electrode.
The first contact area may be maintained at a predetermined depth from the first insulating substrate.
According to a second aspect, the invention provides 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 1 o 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 of "including" or "containing". The term is not intended in an exclusive sense ("consisting ~ 5 of or "composed of') 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 embodiments the contactor is adapted for click engagement with the cut-out portion which extends through the first insulating substrate and the spacer.
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 1 o 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 of "including" or "containing". The term is not intended in an exclusive sense ("consisting ~ 5 of or "composed of') 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 embodiments the contactor is adapted for click engagement with the cut-out portion which extends through the first insulating substrate and the spacer.
With a connector according to the current invention the spacer layer provides extra strength. A rigid connector can therefore be formed using flexible materials.
This allows a wider range of materials to be utilised. An audible confirmation of connection can also be simply provided by the current invention unlike the connector described in US
This allows a wider range of materials to be utilised. An audible confirmation of connection can also be simply provided by the current invention unlike 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 mew.
Figure 2 shows 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 elevation of the sensor of Figure 3 in section on line A-A.
Figure 5 shows a second embodiment of the invention in plan view.
Figure 6 shows a cross-section of the embodiment of Figure S in end elevation when 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
With 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 5 mm and 100 microns thick and having a circular aperture 8 of 3.4 mm diameter.
Aperture 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 adhered by means of adhesive 3 to spacer 4 with palladium coating 2 adjacent spacer 4 and covering one side of aperture 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 to cylindrical side wall 10 and closed at one cylinder end by a first electrode of palladium 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-out aperture 21 pierces first insulating layer 1 and first ~ 5 metal layer 2. In the present example cut-out 21 is oval-shaped. A
cowesponding 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 pan 30 of measuring apparatus and to which is mounted a first resilient contactor 31 and a second resilient contactor 32. Upon insertion of sensor end 20 into the slot, contactor 31 rides over the 20 outer surface of insulating layer 1 and clicks into the well formed by apertures 21 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 area of cell 8. Contact area 23 is in effect 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 7 and second 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 extend 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 t o electrode 2 of cell 8.
Resilient connectors 31 and 32 are arranged in a slot 30 of the measuring 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 encounters first aperture 21,22 whereupon it click engages with the 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, 26 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 5, 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 embodiment and the first is that in the second embodiment cut-out portions 21, 22 are cut from one side edge of sensor l while cut-out portions 25, 26 are cut out from the opposite side edge of the sensor 1. In this case contactors 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 contact is only made when the sensor is inserted in a cprrect orientation and ensures correct polarity.
A third embodiment is shown schematically in Figure 8. In this case the openings take the form of slots 21, 25 extending longitudinally from edge 20. For preference spacer 4 extends around all edges of openings 21 and 25 of Figure 8 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 that 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 connected to a _g_ sensor by the means described. Any suitable form of contactor may be used with sensors according to the invention.
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 mew.
Figure 2 shows 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 elevation of the sensor of Figure 3 in section on line A-A.
Figure 5 shows a second embodiment of the invention in plan view.
Figure 6 shows a cross-section of the embodiment of Figure S in end elevation when 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
With 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 5 mm and 100 microns thick and having a circular aperture 8 of 3.4 mm diameter.
Aperture 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 adhered by means of adhesive 3 to spacer 4 with palladium coating 2 adjacent spacer 4 and covering one side of aperture 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 to cylindrical side wall 10 and closed at one cylinder end by a first electrode of palladium 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-out aperture 21 pierces first insulating layer 1 and first ~ 5 metal layer 2. In the present example cut-out 21 is oval-shaped. A
cowesponding 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 pan 30 of measuring apparatus and to which is mounted a first resilient contactor 31 and a second resilient contactor 32. Upon insertion of sensor end 20 into the slot, contactor 31 rides over the 20 outer surface of insulating layer 1 and clicks into the well formed by apertures 21 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 area of cell 8. Contact area 23 is in effect 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 7 and second 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 extend 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 t o electrode 2 of cell 8.
Resilient connectors 31 and 32 are arranged in a slot 30 of the measuring 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 encounters first aperture 21,22 whereupon it click engages with the 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, 26 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 5, 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 embodiment and the first is that in the second embodiment cut-out portions 21, 22 are cut from one side edge of sensor l while cut-out portions 25, 26 are cut out from the opposite side edge of the sensor 1. In this case contactors 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 contact is only made when the sensor is inserted in a cprrect orientation and ensures correct polarity.
A third embodiment is shown schematically in Figure 8. In this case the openings take the form of slots 21, 25 extending longitudinally from edge 20. For preference spacer 4 extends around all edges of openings 21 and 25 of Figure 8 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 that 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 connected to a _g_ sensor by the means described. Any suitable form of contactor may be used with sensors according to the invention.
Claims (24)
1. A sensor adapted for electrical connection with a power source having first contact means, the sensor comprising:
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 first insulating substrate and a spacer to expose a first contact area on the second insulating substrate to permit a first contact means to effect electrical connection with the first contact area disposed on the second insulating substrate, the first contact area being in electrically conductive connection with the second electrode.
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 first insulating substrate and a spacer to expose a first contact area on the second insulating substrate to permit a first contact means to effect electrical connection with the first contact area disposed on the second insulating substrate, the first contact area being in electrically conductive connection with the second electrode.
2. A sensor according to claim 1 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 the second contact area disposed on the first insulating substrate, the second contact area being in electrically conductive connection with the first electrode.
3. A sensor according to claim 1 or claim 2 wherein the first contact area is maintained at a predetermined depth from the first insulating substrate.
4. A sensor according to claim 2 wherein the second contact area is maintained at a predetermined depth from the second insulating substrate.
5. A sensor according to claim 2 wherein each insulating substrate is made of a flexible insulating material.
6. A sensor according to claim 5 wherein the flexible insulating material is polyester.
7. A sensor according to claim 2 wherein each electrode and its respective contact area are formed from a unified layer of metal deposited on the insulating substrate.
8. A sensor according to claim 7 wherein the metal is selected from the group consisting of palladium, gold, platinum, iridium and silver.
9. A sensor according to claim 7 or 8 wherein the metal is 10-1000 nanometers thick.
10. A sensor according to any one of claims 7 to 9 wherein the unified layer of metal is deposited on the substrate by sputter coating.
11. A sensor according to any one of claims 1 to 6 wherein each electrode and its respective contact area are formed from carbon.
12. A sensor according to claim 2 wherein the cut-out portions are laterally spaced apart relative to the longitudinal axis of the sensor.
13. A sensor according to claim 2 wherein the cut-out portions are longitudinally spaced relative to the longitudinal axis of the sensor.
14. A sensor according to claim 2 wherein the cut-out portions are laterally and longitudinally spaced relative to the longitudinal axis of the sensor.
15. A sensor according to claim 2 wherein at least one of the substrate or spacer extends around the entire periphery of the cut-out portion.
16. A sensor according to claim 1 wherein the cut-out portion is adapted for click engagement with the respective contact means.
17. A sensor according to any one of claims 1 to 15 wherein the cut-out portion is cut from an edge of the sensor such that the cut-out portion is open on at least one edge of the sensor.
18. A sensor according to claim 17 wherein a rib is formed along the open edge of the sensor.
19. A sensor according to claim 18 wherein the rib is formed by the spacer.
20. A sensor according to claim 18 or claim 19 wherein the rib is shaped to facilitate click engagement of the contact means with the contact area.
21. A sensor according to any one of claims 2 to 20 wherein the first cut-out portion is elongated relative to the second cut-out portion such that during sliding engagement of the sensor with said first and second contact means, a first click engagement occurs between the first contact means and first contact area, followed by the first contact means sliding over the first contact area until a second click engagement occurs between the second contact means and the second contact area.
22. A sensing system comprising a sensor according to claim 2, and a sensing apparatus including a first contact means and a second contact means adapted to effect electrical contact with the first and second contact area respectively.
23. A sensing system according to claim 22 wherein the contact means are resiliently biased to extend through the respective cut-out portion to make contact with the contact area.
24. A sensing system according to claims 22 or 23 wherein the contact means are adapted for click engagement with the respective cut-out portions.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CA002550198A CA2550198C (en) | 1997-03-21 | 1998-03-20 | Sensor connection means |
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| AUPO5813 | 1997-03-21 | ||
| AUPO5813A AUPO581397A0 (en) | 1997-03-21 | 1997-03-21 | Sensor connection means |
| PCT/AU1998/000184 WO1998043073A1 (en) | 1997-03-21 | 1998-03-20 | Sensor connection means |
Related Child Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002550198A Division CA2550198C (en) | 1997-03-21 | 1998-03-20 | Sensor connection means |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2284634A1 CA2284634A1 (en) | 1998-10-01 |
| CA2284634C true CA2284634C (en) | 2006-08-08 |
Family
ID=3800116
Family Applications (2)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002550198A Expired - Lifetime CA2550198C (en) | 1997-03-21 | 1998-03-20 | Sensor connection means |
| CA002284634A Expired - Lifetime CA2284634C (en) | 1997-03-21 | 1998-03-20 | Sensor connection means |
Family Applications Before (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002550198A Expired - Lifetime CA2550198C (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) | KR100526086B1 (en) |
| CN (4) | CN100507541C (en) |
| AT (1) | ATE475881T1 (en) |
| AU (2) | AUPO581397A0 (en) |
| BR (1) | BR9807987B1 (en) |
| CA (2) | CA2550198C (en) |
| DE (1) | DE69841786D1 (en) |
| ES (1) | ES2349388T3 (en) |
| HK (1) | HK1064154A1 (en) |
| IL (3) | IL131980A (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 |
| US6338790B1 (en) * | 1998-10-08 | 2002-01-15 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
| US6591125B1 (en) | 2000-06-27 | 2003-07-08 | 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 |
| ATE468531T1 (en) * | 2001-05-30 | 2010-06-15 | I Sens Inc | BIOSENSOR |
| US8337419B2 (en) | 2002-04-19 | 2012-12-25 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| US9795747B2 (en) | 2010-06-02 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | Methods and apparatus for lancet actuation |
| US9427532B2 (en) | 2001-06-12 | 2016-08-30 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| US7344507B2 (en) | 2002-04-19 | 2008-03-18 | Pelikan Technologies, Inc. | Method and apparatus for lancet actuation |
| US7033371B2 (en) | 2001-06-12 | 2006-04-25 | Pelikan Technologies, Inc. | Electric lancet actuator |
| WO2002100461A2 (en) * | 2001-06-12 | 2002-12-19 | Pelikan Technologies, Inc. | Method and apparatus for improving success rate of blood yield from a fingerstick |
| EP1404233B1 (en) | 2001-06-12 | 2009-12-02 | Pelikan Technologies Inc. | Self optimizing lancing device with adaptation means to temporal variations in cutaneous properties |
| 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 |
| AU2002312521A1 (en) * | 2001-06-12 | 2002-12-23 | Pelikan Technologies, Inc. | Blood sampling apparatus and method |
| US7025774B2 (en) | 2001-06-12 | 2006-04-11 | Pelikan Technologies, Inc. | Tissue penetration device |
| US7981056B2 (en) | 2002-04-19 | 2011-07-19 | Pelikan Technologies, Inc. | Methods and apparatus for lancet actuation |
| 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 |
| US8702624B2 (en) | 2006-09-29 | 2014-04-22 | Sanofi-Aventis Deutschland Gmbh | Analyte measurement device with a single shot actuator |
| US7976476B2 (en) | 2002-04-19 | 2011-07-12 | Pelikan Technologies, Inc. | Device and method for variable speed lancet |
| 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 |
| US7229458B2 (en) | 2002-04-19 | 2007-06-12 | 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 |
| US8360992B2 (en) | 2002-04-19 | 2013-01-29 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for penetrating tissue |
| US7892183B2 (en) | 2002-04-19 | 2011-02-22 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
| US9795334B2 (en) | 2002-04-19 | 2017-10-24 | Sanofi-Aventis Deutschland Gmbh | 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 |
| US9314194B2 (en) | 2002-04-19 | 2016-04-19 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| US8784335B2 (en) | 2002-04-19 | 2014-07-22 | Sanofi-Aventis Deutschland Gmbh | Body fluid sampling device with a capacitive sensor |
| US9248267B2 (en) | 2002-04-19 | 2016-02-02 | Sanofi-Aventis Deustchland Gmbh | Tissue penetration device |
| US7232451B2 (en) | 2002-04-19 | 2007-06-19 | 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 |
| US7901362B2 (en) | 2002-04-19 | 2011-03-08 | 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 |
| 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 |
| US7491178B2 (en) | 2002-04-19 | 2009-02-17 | 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 |
| US7563232B2 (en) * | 2002-04-19 | 2009-07-21 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7297122B2 (en) | 2002-04-19 | 2007-11-20 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7291117B2 (en) | 2002-04-19 | 2007-11-06 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
| US7717863B2 (en) | 2002-04-19 | 2010-05-18 | 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 |
| US7141058B2 (en) * | 2002-04-19 | 2006-11-28 | Pelikan Technologies, Inc. | Method and apparatus for a body fluid sampling device using illumination |
| 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 |
| 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 |
| US7544277B2 (en) * | 2003-06-12 | 2009-06-09 | Bayer Healthcare, Llc | Electrochemical test sensors |
| US7718439B2 (en) | 2003-06-20 | 2010-05-18 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
| US7645421B2 (en) | 2003-06-20 | 2010-01-12 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
| US7488601B2 (en) | 2003-06-20 | 2009-02-10 | Roche Diagnostic Operations, Inc. | System and method for determining an abused sensor during analyte measurement |
| PT1639352T (en) | 2003-06-20 | 2018-07-09 | Hoffmann La Roche | Method and reagent for producing narrow, homogenous reagent strips |
| US8058077B2 (en) | 2003-06-20 | 2011-11-15 | Roche Diagnostics Operations, Inc. | 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 |
| US7645373B2 (en) | 2003-06-20 | 2010-01-12 | Roche Diagnostic 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 |
| US8679853B2 (en) * | 2003-06-20 | 2014-03-25 | Roche Diagnostics Operations, Inc. | Biosensor with laser-sealed capillary space and method of making |
| US8206565B2 (en) | 2003-06-20 | 2012-06-26 | Roche Diagnostics Operation, Inc. | System and method for coding information on a biosensor test strip |
| 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 |
| US7822454B1 (en) | 2005-01-03 | 2010-10-26 | Pelikan Technologies, Inc. | Fluid sampling device with improved analyte detecting member configuration |
| EP1706026B1 (en) | 2003-12-31 | 2017-03-01 | Sanofi-Aventis Deutschland GmbH | Method and apparatus for improving fluidic flow and sample capture |
| RU2006132051A (en) | 2004-02-06 | 2008-03-20 | БАЙЕР ХЕЛТКЭР ЭлЭлСи (US) | OXIDIZABLE COMPOUNDS AS AN INTERNAL STANDARD FOR BIOSENSORS AND METHOD OF APPLICATION |
| EP1751546A2 (en) | 2004-05-20 | 2007-02-14 | Albatros Technologies GmbH & Co. KG | Printable hydrogel for biosensors |
| US9775553B2 (en) | 2004-06-03 | 2017-10-03 | Sanofi-Aventis Deutschland Gmbh | Method and apparatus for a fluid sampling device |
| EP1765194A4 (en) | 2004-06-03 | 2010-09-29 | Pelikan Technologies Inc | Method and apparatus for 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 |
| US8192599B2 (en) * | 2005-05-25 | 2012-06-05 | Universal Biosensors Pty Ltd | Method and apparatus for electrochemical analysis |
| US8323464B2 (en) * | 2005-05-25 | 2012-12-04 | Universal Biosensors Pty Ltd | Method and apparatus for electrochemical analysis |
| CA2609720C (en) | 2005-07-20 | 2015-06-30 | 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 |
| CA2986870A1 (en) | 2005-09-30 | 2007-04-12 | Ascensia Diabetes Care Holdings Ag | 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 |
| WO2007096730A1 (en) | 2006-02-21 | 2007-08-30 | Universal Biosensors Pty Ltd. | Fluid transfer mechanism |
| US8529751B2 (en) | 2006-03-31 | 2013-09-10 | Lifescan, Inc. | Systems and methods for discriminating control solution from a physiological sample |
| US8163162B2 (en) | 2006-03-31 | 2012-04-24 | Lifescan, Inc. | Methods and apparatus for analyzing a sample in the presence of interferents |
| US8398443B2 (en) * | 2006-04-21 | 2013-03-19 | Roche Diagnostics Operations, Inc. | Biological testing system and connector therefor |
| WO2009015292A1 (en) * | 2007-07-26 | 2009-01-29 | 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 |
| WO2009126900A1 (en) | 2008-04-11 | 2009-10-15 | Pelikan Technologies, Inc. | Method and apparatus for analyte detecting device |
| 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 |
| EP2455876A3 (en) * | 2009-06-30 | 2013-01-30 | Lifescan Scotland Limited | System and method for diabetes management |
| JP5654587B2 (en) * | 2009-06-30 | 2015-01-14 | ライフスキャン・インコーポレイテッドＬｉｆｅｓｃａｎ，Ｉｎｃ． | Analyte test method and apparatus for calculating basal insulin therapy |
| JP2012532323A (en) * | 2009-06-30 | 2012-12-13 | ライフスキャン・インコーポレイテッド | Analyte testing method and system |
| CN102639058B (en) * | 2009-09-29 | 2015-11-25 | 生命扫描苏格兰有限公司 | For the analyte test method and apparatus of diabetes management |
| 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 |
| 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 |
| US20110208435A1 (en) | 2010-02-25 | 2011-08-25 | Lifescan Scotland Ltd. | Capacitance detection in electrochemical assays |
| US8742773B2 (en) | 2010-02-25 | 2014-06-03 | Lifescan Scotland Limited | Capacitance detection in electrochemical assay with improved response |
| AU2010346623B2 (en) | 2010-02-25 | 2015-09-03 | Lifescan Scotland Limited | Analyte testing method and system with high and low blood glucose trends notification |
| BR112012021590A2 (en) | 2010-02-25 | 2016-09-13 | Lifescan Scotland Ltd | capacitance detection in electrochemical assay |
| US8773106B2 (en) | 2010-02-25 | 2014-07-08 | Lifescan Scotland Limited | Capacitance detection in electrochemical assay with improved sampling time offset |
| US8965476B2 (en) | 2010-04-16 | 2015-02-24 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
| RU2013103783A (en) | 2010-06-30 | 2014-08-10 | Лайфскэн Скотлэнд Лимитед | METHOD, SYSTEM AND DEVICE FOR PROVIDING STATISTICAL POWER WHEN GIVING MESSAGES ON THE DIFFERENCE OF MIDDLE GLUCOSE LEVELS BEFORE AND AFTER RECEIVING |
| AU2011287420B2 (en) | 2010-08-02 | 2015-05-07 | Cilag Gmbh International | Systems and methods for improved accuracy 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 |
| AU2013239446B2 (en) | 2012-03-30 | 2017-10-12 | Lifescan Scotland Limited | Battery status detection and storage method and system in medical monitoring |
| GB2505694B (en) * | 2012-09-07 | 2017-03-22 | Lifescan Scotland Ltd | Electrochemical-based analytical test strip with bare interferent electrodes |
| CA2884065C (en) * | 2012-09-07 | 2020-01-07 | Cilag Gmbh International | Electrochemical sensors and a method for their manufacture |
| 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 |
| 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 |
| 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 |
| US9459231B2 (en) | 2013-08-29 | 2016-10-04 | Lifescan Scotland Limited | Method and system to determine erroneous measurement signals during a test measurement sequence |
| US9243276B2 (en) | 2013-08-29 | 2016-01-26 | Lifescan Scotland Limited | Method and system to determine hematocrit-insensitive glucose values in a fluid sample |
| 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 |
| 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 |
| DK178995B1 (en) * | 2015-09-13 | 2017-07-31 | Pro-Ino Dev Aps | Handheld apparatus for testing a sample of body fluid |
Family Cites Families (55)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4301414A (en) | 1979-10-29 | 1981-11-17 | United States Surgical Corporation | Disposable sample card and method of making same |
| US4301412A (en) | 1979-10-29 | 1981-11-17 | United States Surgical Corporation | Liquid conductivity measuring system and sample cards therefor |
| US4303887A (en) | 1979-10-29 | 1981-12-01 | United States Surgical Corporation | Electrical liquid conductivity measuring system |
| 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 |
| CA1231136A (en) | 1984-06-13 | 1988-01-05 | Ian A. Shanks | Capillary action chemical test device |
| CN85107234A (en) * | 1985-09-24 | 1987-04-01 | 物理传感器公司 | Use the chemical selection sensor of admittance modulating membrane |
| JP2514083B2 (en) | 1986-11-28 | 1996-07-10 | ユニリーバー・ナームローゼ・ベンノートシヤープ | Electrochemical measuring device |
| 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 |
| US5128015A (en) | 1988-03-15 | 1992-07-07 | Tall Oak Ventures | Method and apparatus for amperometric diagnostic analysis |
| US5108564A (en) * | 1988-03-15 | 1992-04-28 | 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 |
| DE69025134T2 (en) | 1989-11-24 | 1996-08-14 | Matsushita Electric Ind Co Ltd | Method of manufacturing a 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 |
| ZA92803B (en) * | 1991-02-06 | 1992-11-25 | Igen Inc | Method and apparatus for magnetic microparticulate based luminescene asay including plurality of magnets |
| 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 |
| EP0525723B1 (en) * | 1991-07-29 | 1997-05-14 | Mochida Pharmaceutical Co., Ltd. | 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 |
| DE69318332T2 (en) | 1992-03-12 | 1998-09-03 | Matsushita Electric Ind Co Ltd | Biosensor with a catalyst made of 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 |
| FR2710414A1 (en) | 1993-09-21 | 1995-03-31 | Asulab Sa | Measuring device for removable multi-zone sensors comprising an ejection system for these sensors. |
| FR2710413B1 (en) * | 1993-09-21 | 1995-11-03 | Asulab Sa | Measuring device for removable 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 |
| AUPN661995A0 (en) | 1995-11-16 | 1995-12-07 | Memtec America Corporation | Electrochemical cell 2 |
| US6174420B1 (en) * | 1996-11-15 | 2001-01-16 | Usf Filtration And Separations Group, Inc. | Electrochemical cell |
| 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 |
| EP0958495B1 (en) * | 1997-02-06 | 2002-11-13 | Therasense, Inc. | Small volume in vitro analyte sensor |
| JP2002524021A (en) | 1997-02-06 | 2002-07-30 | ザ・ユニヴァーシティ・オヴ・ノース・キャロライナ・アト・チャペル・ヒル | Electrochemical probes for detection of molecular interactions and drug discovery |
| 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 |
| JP4948737B2 (en) | 2000-07-14 | 2012-06-06 | ライフスキャン・インコーポレイテッド | An electrochemical method for measuring chemical reaction rates. |
-
1997
- 1997-03-21 AU AUPO5813A patent/AUPO581397A0/en not_active Abandoned
-
1998
- 1998-03-20 AT AT98907775T patent/ATE475881T1/en active
- 1998-03-20 BR BRPI9807987-5A patent/BR9807987B1/en not_active IP Right Cessation
- 1998-03-20 IL IL13198098A patent/IL131980A/en not_active IP Right Cessation
- 1998-03-20 CA CA002550198A patent/CA2550198C/en not_active Expired - Lifetime
- 1998-03-20 KR KR10-1999-7008615A patent/KR100526086B1/en not_active IP Right Cessation
- 1998-03-20 CA CA002284634A patent/CA2284634C/en not_active Expired - Lifetime
- 1998-03-20 CN CNB2005100939913A patent/CN100507541C/en not_active Expired - Lifetime
- 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 KR KR1020057007153A patent/KR100576660B1/en not_active IP Right Cessation
- 1998-03-20 EP EP98907775A patent/EP0968415B1/en not_active Expired - Lifetime
- 1998-03-20 CN CNB031306187A patent/CN1229639C/en not_active Expired - Lifetime
- 1998-03-20 WO PCT/AU1998/000184 patent/WO1998043073A1/en active IP Right Grant
- 1998-03-20 CN CN2006100958001A patent/CN1936560B/en not_active Expired - Lifetime
- 1998-03-20 CN CN98804325A patent/CN1117275C/en not_active Expired - Lifetime
- 1998-03-20 ES ES98907775T patent/ES2349388T3/en not_active Expired - Lifetime
- 1998-03-20 IL IL15406698A patent/IL154066A0/en active IP Right Grant
- 1998-03-20 JP JP54453298A patent/JP3766109B2/en not_active Expired - Lifetime
- 1998-03-20 AU AU66044/98A patent/AU745740B2/en not_active Expired
-
1999
- 1999-09-20 US US09/399,512 patent/US6379513B1/en not_active Expired - Lifetime
-
2001
- 2001-11-13 US US10/012,680 patent/US7045046B2/en not_active Expired - Lifetime
-
2003
- 2003-01-21 IL IL154066A patent/IL154066A/en not_active IP Right Cessation
- 2003-04-28 RU RU2003112450/28A patent/RU2320986C2/en active
-
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
-
2006
- 2006-05-15 US US11/434,442 patent/US20060201804A1/en not_active Abandoned
Also Published As
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2284634C (en) | Sensor connection means | |
| EP1181538B1 (en) | Electrochemical biosensor test strip, fabrication method thereof and electrochemical biosensor | |
| US7357851B2 (en) | Electrochemical cell | |
| CA2122690A1 (en) | Electrochemical sensor with multiple zones on a disc and its application to the quantitative analysis of glucose | |
| CA2292505A1 (en) | Electrodes for the measurement of analytes in small sample volumes | |
| EP3641646A1 (en) | Analyte sensor | |
| AU784485B2 (en) | Sensor connection means | |
| JPH1183787A (en) | Connector for biosensor | |
| JP2004309351A (en) | Biosensor | |
| CA2566824A1 (en) | Improved electrochemical cell |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKEX | Expiry |
Effective date: 20180320 |