Conductive sensors and their use in diagnostic assays

• US 5,202,261 A
• Filed: 11/18/1991
• Issued: 04/13/1993
• Est. Priority Date: 07/19/1990
• Status: Expired due to Term

• Current Assignee: Miles, Inc. (Bayer AG)
• Original Assignee: Miles, Inc. (Bayer AG)
• Inventors: Musho, Matthew K., Noell, J. Oakey, Tse, Pius H.
• Primary Examiner(s): NOT, DEFINED
• Assistant Examiner(s): Trembley, T. A.
• Application Number:
  US07/793,180
• Time in Patent Office: 512 Days
• Field of Search: 435/288, 435/291, 435/817, 204/403
• US Class Current: 204/403.09
• CPC Class Codes: C12Q 1/002 Electrode membranes
• CPC Class Codes: C12Q 1/005 involving specific analytes or enzymes including groups of enzymes, e.g. oxydases; C12Q1/004 takes precedence
• CPC Class Codes: Y10S 435/817 Enzyme or microbe electrode

Abstract

A conductive sensor and its use in a diagnostic assay are disclosed. The miniaturized conductive sensor, utilizing a conducting polymer, is used in a diagnostic device to determine the presence or concentration of a predetermined analyte in a liquid test sample, wherein the predetermined analyte, like glucose, is assayed by an oxidase interaction. The interaction between the oxidase and a small amount of the predetermined analyte in the test sample generates, either directly or indirectly, a dopant compound in a reaction zone of the conductive sensor. The dopant compound then migrates to the detection zone of the conductive sensor of the diagnostic device to oxidize the conducting polymer and convert the conducting polymer from an insulating form to a conducting form. The resulting increase in conductivity of the conducting polymer is measured, then the conductivity increase is correlated to the concentration of the predetermined analyte in the test sample.

Claims

1. A conductive sensor for assaying a test sample for the presence or concentration of glucose, said conductive sensor comprising:

a) a semipermeable membrane capable of effectively separating cellular material and interfering components from a test sample and capable of allowing glucose to permeate through the semipermeable membrane at a uniform rate said semipermeable membrane having a diffusion constant for glucose in the range of from about 1×

10^-9 cm² /sec to about 5×

10^-8 cm² /sec and a diffusion constant for molecular oxygen in the range of from about 5×

10^-7 cm² /sec to about 5×

10^-6 cm² /sec and having a thickness of from about 3μ

to about 15μ

;

b) a layer of a host matrix in contact with the semipermeable membrane and permeable to the glucose, said hose matrix layer having homogeneously incorporated therein glucose oxidase, a compound having peroxidase activity and a dopant compound precursor, wherein the glucose, the glucose oxidase, the compound having peroxidase activity and the dopant compound precursor interact to form a dopant compound;

c) a layer of a polymer in its reduced form which demonstrates an increase in electrical conductivity when it is converted to its oxidized form in contact with the host matrix layer such that at least a portion of the dopant compound generated in the host matrix layer migrates to and oxidatively dopes the polymer layer to thereby increase the conductivity of this layer; and

d) means operatively connected to the polymer layer for measuring a change in conductivity of polymer layer.

2. The conductive sensor of claim 1 wherein the means for measuring the change in conductivity of the polymer layer comprises a microelectrode assembly in contact with the polymer layer, said microelectrode assembly constructed to sense the change in conductivity of the polymer layer in response to the oxidative doping of the polymer layer by the dopant compound.

3. The conductive sensor of claim 2 wherein the microelectrode assembly comprises an interdigited pair of metal electrodes having an insulating spacing of from about 10μ

to about 300μ

.

4. The conductive sensor of claim 1 wherein the compound having peroxidase activity is horseradish peroxidase, lactoperoxidase, microperoxidase or combinations thereof.

5. The conductive sensor of claim 1 wherein the host matrix layer has a thickness of from about 0.1μ

to about 10μ and

comprises gelatin, chitosan, silk fibroin, collagen, poly(2-hydroxyethylmethacrylate), polyacrylamide or combinations thereof.

6. The conductive sensor of claim 1 wherein the dopant compound precursor is iodide ion, said iodide ion incorporated into the host matrix layer as an iodide salt selected from the group consisting of lithium iodide, sodium iodide, potassium iodide, a tetraalkylammonium iodide wherein the alkyl group includes from one to about four carbon atoms, and combinations thereof.

7. The conductive sensor of claim 6 wherein the compound having peroxidase activity is a molybdenum(VI) transition metal catalyst.

8. The conductive sensor of claim 6 wherein the polymer layer has a thickness of less than 10,000 Å

and comprises a poly(alkylthiophene), a polythiophene, a poly(thienylene vinylene), a poly(furylene vinylene), a polypyrrole, a polyfuran, a polyaniline or a combination thereof.

9. The conductive sensor of claim 8 wherein the poly(alkylthiophene) is a poly(3-alkylthiophene) wherein the alkyl group includes from about four carbon atoms to about 20 carbon atoms.

10. The conductive sensor of claim 1 wherein the semipermeable membrane has a thickness in the range of from about 5μ

to about 10μ

.

11. The conductive sensor of claim 1 wherein the semipermeable membrane has a thickness in the range of from about 6μ

to about 8μ

.

12. The conductive sensor of claim 1 wherein the semipermeable membrane is an elastomeric compound.

13. The conductive sensor of claim 1 wherein the semipermeable membrane is a silicone-containing elastomer.

14. The conductive sensor of claim 1 wherein the semipermeable membrane comprises polypropylene, nylon, polycarbonate, polyurethane or a combination thereof.

15. The conductive sensor of claim 1 wherein the glucose oxidase and compound peroxidase having activity are in a first matrix layer and the dopant compound precursor is in a second matrix layer immediately adjacent to the first matrix layer.

16. The conductive sensor of claim 15 wherein the first matrix layer and the second matrix layer are comprised of chitosan.

17. The conductive sensor of claim 16 wherein the dopant compound precursor is tetraethylammonium iodide.

18. The conductive sensor of claim 1 wherein the host matrix comprises a first layer containing the glucose oxidase and compound peroxidase having activity and a second layer immediately adjacent to the first layer which contains the dopant compound precursor material.

19. The conductive sensor of claim 18 wherein the first and second layers of the host matrix are comprised of chitosan.

20. The conductive sensor of claim 19 wherein the dopant compound precursor is tetraethylammonium iodide.

21. A conductive sensor for assaying a biological fluid for the presence or concentration of a predetermined analyte, said predetermined analyte capable of interacting with an oxidase enzyme, and said conductive sensor comprising:

a) an elastomer-based semipermeable membrane having a thickness of from about 5μ

to about 10μ

, said elastomer-based semipermeable membrane capable of effectively separating cellular material and interfering components from a biological fluid and capable of allowing a predetermined analyte to permeate through the elastomer-based semipermeable membrane at a uniform rate;

b) a layer of a host matrix, comprising gelatin, chitosan or a combination thereof and having a thickness of from about 0.2μ

to about 5μ

, in contact with the semipermeable membrane, said host matrix layer permeable to the predetermined analyte and said host matrix layer having homogeneously incorporated therein an oxidase enzyme capable of interacting with the predetermined analyte, a peroxidase enzyme or a molybdenum(VI) transition metal catalyst, and iodide ion, wherein the predetermined analyte, the oxidase enzyme, the peroxidase enzyme or the molybdenum(VI) catalyst, and the iodide ion interact to generate molecular iodine;

c) a layer of a conducting polymer having a thickness of from about 100 Å

to about 2000 Å

in contact with the host matrix layer such that at least a portion of the molecular iodine generated in the host matrix layer migrates to and oxidatively dopes the conducting polymer layer; and

d) a microelectrode assembly in contact with the conducting polymer layer, said microelectrode assembly adapted to sense a change in conductivity of the conducting polymer layer in response to the oxidative doping of the conducting polymer layer by the molecular iodine.