GLUCOSE-SENSING ELECTRODE AND DEVICE WITH NANOPOROUS LAYER

• US 20190328297A1
• Filed: 06/24/2019
• Published: 10/31/2019
• Est. Priority Date: 11/21/2017
• Status: Active Grant

• Current Assignee: UXN Co., Ltd.
• Original Assignee: UXN Co., Ltd.
• Inventors: Boo, Hankil, Chang, Rae Kyu
• Granted Patent: US 11,751,781 B2
• Time in Patent Office: Days
• CPC Class Codes: A61B 2560/0475 Special features of memory means, e.g. removable memory cards
• CPC Class Codes: A61B 2562/0285 Nanoscale sensors
• CPC Class Codes: A61B 2562/125 characterised by the manufacture of electrodes
• CPC Class Codes: A61B 5/0031 Implanted circuitry
• CPC Class Codes: A61B 5/14532 for measuring glucose, e.g. by tissue impedance measurement
• CPC Class Codes: A61B 5/1473 invasive, e.g. introduced into the body by a catheter A61B5/1482 takes precedence
• CPC Class Codes: A61B 5/1486 using enzyme electrodes, e.g. with immobilised oxidase
• CPC Class Codes: A61B 5/14865 invasive, e.g. introduced into the body by a catheter or needle or using implanted sensors
• CPC Class Codes: A61B 5/72 Signal processing specially adapted for physiological signals or for diagnostic purposes character recognition, recognising digital ink, document-oriented image-based pattern recognition G06V30/00; recognition or understanding of postal images G06V30/424
• CPC Class Codes: A61B 5/742 using visual displays A61B5/339 takes precedence
• CPC Class Codes: B01J 13/0013 from a precipitate
• CPC Class Codes: B05D 5/00 Processes for applying liquids or other fluent materials to surfaces to obtain special surface effects, finishes or structures
• CPC Class Codes: B05D 5/02 to obtain a matt or rough surface
• CPC Class Codes: B82Y 15/00 Nanotechnology for interacting, sensing or actuating, e.g. quantum dots as markers in protein assays or molecular motors
• CPC Class Codes: B82Y 30/00 Nanotechnology for materials or surface science, e.g. nanocomposites
• CPC Class Codes: B82Y 40/00 Manufacture or treatment of nanostructures
• CPC Class Codes: C09D 5/028 Pigments; Filters
• CPC Class Codes: C09D 5/24 Electrically-conducting paints conductive materials H01B1/00
• CPC Class Codes: C09D 7/67 Particle size smaller than 100 nm
• CPC Class Codes: C12Q 1/006 for glucose
• CPC Class Codes: G01N 2400/00 : Assays, e.g. immunoassays or enzyme assays, involving carbohydrates
• CPC Class Codes: G01N 27/327 : Biochemical electrodes , e.g. electrical or mechanical details for in vitro measurements
• CPC Class Codes: G01N 27/3271 : Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood amperometry per se G01N27/49; aspects concerning the enzyme reagent C12Q1/001
• CPC Class Codes: G01N 27/3335 : the membrane containing at least one organic component G01N27/3271 takes precedence; aspects concerning the enzyme reagent in enzyme electrodes C12Q1/001
• CPC Class Codes: G01N 27/4168 : Oxidation-reduction potential, e.g. for chlorination of water water analysis G01N33/18
• CPC Class Codes: G01N 33/49 : Blood chemical methods for determining blood cell populations G01N33/5094; chemical analysis of blood groups or blood types G01N33/80
• CPC Class Codes: G01N 33/66 : involving blood sugars, e.g. galactose
• CPC Class Codes: Y10S 977/773 : Nanoparticle, i.e. structure having three dimensions of 100 nm or less
• CPC Class Codes: Y10S 977/81 : Of specified metal or metal alloy composition
• CPC Class Codes: Y10S 977/896 : Chemical synthesis, e.g. chemical bonding or breaking
• CPC Class Codes: Y10S 977/92 : Detection of biochemical

Abstract

This disclosure relates to a glucose-sensing electrode including a nanoporous layer on an electrically conductive surface. The nanoporous layer includes a three-dimensional interconnected network of irregularly shaped bodies that are formed of numerous nanoparticles having a generally oval or spherical shape with a length ranging between about 2 nm and about 5 nm. Inside the three-dimensional interconnected network of irregularly shaped bodies, at least part of the nanoparticles are adjacent to each other without an intervening nanoparticle therebetween and apart from each other to define interparticular nanopores therebetween, wherein at least part of the interparticular nanopores inside the three-dimensional interconnected network of irregularly shaped bodies are in a size ranging between about 0.5 nm and about 3 nm. The nanoporous layer further comprises a three-dimensional interconnected network of irregularly shaped spaces that is geometrically complementary to the three-dimensional interconnected network of irregularly shaped bodies. The glucose-sensing electrode does not comprise a glucose-specific enzyme.

Claims

1. A glucose-sensing electrode comprising:

at least one electrically conductive layer comprising a surface; and

a nanoporous layer formed on the surface

wherein the nanoporous layer comprises a three-dimensional interconnected network of irregularly shaped bodies that are formed of numerous nanoparticles having a generally oval or spherical shape with a length ranging between about 2 nm and about 5 nm,

wherein, inside the three-dimensional interconnected network of irregularly shaped bodies, at least part of the nanoparticles are adjacent to each other without an intervening nanoparticle therebetween and apart from each other to define interparticular nanopores therebetween, wherein at least part of the interparticular nanopores inside the three-dimensional interconnected network of irregularly shaped bodies are in a size ranging between about 0.5 nm and about 3 nm,

wherein the nanoporous layer further comprises a three-dimensional interconnected network of irregularly shaped spaces that is geometrically complementary to the three-dimensional interconnected network of irregularly shaped bodies,

wherein the glucose-sensing electrode does not comprise a glucose-specific enzyme,

wherein the nanoporous layer is substantially free of a surfactant, wherein if any surfactant is contained in the nanoporous layer, the surfactant is in an amount smaller than 0.5 parts by weight with reference to 100 parts by weight of the deposit.

2. The glucose-sensing electrode of claim 1, wherein the interparticular nanopores inside the three-dimensional interconnected network of irregularly shaped bodies are directly or indirectly interconnected with the three-dimensional interconnected network of irregularly shaped spaces.

3. The glucose-sensing electrode of claim 1, wherein the interparticular nanopores are substantially interconnected inside the three-dimensional interconnected network of irregularly shaped bodies and are further connected to the three-dimensional interconnected network of irregularly shaped spaces.

4. The glucose-sensing electrode of claim 1, wherein adjacent ones of the irregularly shaped bodies abut one another while forming unoccupied spaces between non-abutting surfaces or portions of the adjacent ones of the irregularly shaped bodies,

wherein abutments between adjacent ones of the irregularly shaped bodies connect the adjacent ones with one another, which continues to other ones of the irregularly shaped bodies to form the three-dimensional interconnected network of irregularly shaped bodies.

5. The glucose-sensing electrode of claim 4, wherein the unoccupied spaces between non-abutting surfaces or portions of the adjacent ones of the irregularly shaped bodies are irregularly shaped and connect with other unoccupied spaces formed by other ones of the irregularly shaped bodies,

wherein connections between the unoccupied spaces form the three-dimensional interconnected network of irregularly shaped spaces that is geometrically complementary to and outside the three-dimensional interconnected network of irregularly shaped bodies inside the nanoporous layer.

6. The glucose-sensing electrode of claim 1, wherein at least part of the irregularly shaped spaces forming the three-dimensional interconnected network of irregularly shaped spaces are in a size ranging between about 25 nm and about 700 nm.

7. The glucose-sensing electrode of claim 1, wherein a mean size of the interparticular nanopores inside the three-dimensional interconnected network of irregularly shaped bodies is between about 1 nm and about 2 nm.

8. The glucose-sensing electrode of claim 1, wherein a mean size of the irregularly shaped spaces forming the three-dimensional interconnected network of irregularly shaped spaces is between about 150 nm and about 400 nm.

9. The glucose-sensing electrode of claim 1, wherein the nanoparticles are primarily made of platinum (Pt) or gold (Au), wherein the interparticular nanopores are distributed generally throughout inside the three-dimensional interconnected network of irregularly shaped bodies.

10. The glucose-sensing electrode of claim 1, wherein the nanoparticles are primarily made of platinum (Pt) or gold (Au), wherein the unoccupied spaces of the three-dimensional interconnected network of irregularly shaped spaces are distributed generally throughout in the nanoporous layer between the surface of the at least one electrically conductive layer and a top of the nanoporous layer.

11. The glucose-sensing electrode of claim 1, wherein the interparticular nanopores are substantially free of nano-sized organic molecules, wherein if any organic molecules are contained in the nanoporous layer, the organic molecules are in an amount smaller than 0.5 parts by weight with reference to 100 parts by weight of the deposit.

12. The glucose-sensing electrode of claim 1, wherein the nanoparticles are made of at least one selected from the group consisting of platinum (Pt), gold (Au), palladium (Pd), rhodium (Rh), titanium (Ti), ruthenium (Ru), tin (Sn), nickel (Ni), copper (Cu), indium (In), thallium (Tl), zirconium (Zr), iridium (Ir), and one or more oxides of the foregoing metals.

13. The glucose-sensing electrode of claim 1, wherein the nanoporous layer has roughness factor between about 100 and about 2500.

14. The glucose-sensing electrode of claim 1, wherein the at least one electrically conductive layer comprises an electrically conductive metal layer and an electrically conductive carbon layer formed on the electrically conductive metal layer.

15. The glucose-sensing electrode of claim 1, wherein the glucose-sensing electrode does not comprise a biocompatible polymeric material formed over the nanoporous layer.

16. The glucose-sensing electrode of claim 1, wherein the glucose-sensing electrode comprises a biocompatible polymeric material formed over the nanoporous layer.

17. The glucose-sensing electrode of claim 1, further comprising:

an electrolyte ion-blocking layer formed over the nanoporous layer; and

a biocompatibility layer formed over the electrolyte ion-blocking layer,

wherein, when contacting liquid containing glucose, Na⁺, K⁺, Ca²⁺, Cl⁻

, PO₄³⁻

and CO₃²⁻

, the electrolyte ion-blocking layer is configured to inhibit Na⁺, K⁺, Ca²⁺, Cl⁻

, PO₄³⁻

and CO₃²⁻

contained in the liquid from diffusing toward the nanoporous layer such that there is a substantial discontinuity of a combined concentration of Na⁺, K⁺, Ca²⁺, Cl⁻

, PO₄³⁻

and CO₃²⁻

between over and below the electrolyte ion-blocking layer.

18. The glucose-sensing electrode of claim 17, wherein when applying a bias voltage of 0.2-0.45 V between the glucose-sensing electrode and a reference electrode, the glucose-sensing electrode is configured to cause oxidation of glucose in the nanoporous layer and configured to generate an electric current that is a sum of a glucose-oxidation current caused by the oxidation of glucose alone and a background current caused by other electrochemical interactions of the liquid and the glucose-sensing electrode,

wherein, when the liquid contains glucose at a concentration of 4-20 mM (72-360 mg/dL), at steady state the glucose-oxidation current is at a level higher than 0.1 μ

A/mMcm² (10 nA/mMcm²).

19. The glucose-sensing electrode of claim 17, wherein the combined concentration below the electrolyte ion-blocking layer is greater than 0% and lower than about 10% of the combined concentration above the electrolyte ion-blocking layer.

20. The glucose-sensing electrode of claim 17, wherein the combined concentration below the electrolyte ion-blocking layer is greater than 0% and lower than about 5% of the combined concentration above the electrolyte ion-blocking layer.

21. The glucose-sensing electrode of claim 17, wherein the electrolyte ion-blocking layer comprises a porous and hydrophobic polymer layer that is configured to limit mobility of Na⁺, K⁺, Ca²⁺, Cl⁻

, PO₄³⁻

and CO₃²⁻

therethrough while not limiting mobility of glucose molecules therethrough.

22. The glucose-sensing electrode of claim 17, wherein the electrolyte ion-blocking layer comprises at least one selected from the group consisting of poly(methyl methacrylate) (PMMA), poly(hydroxyethyl methacrylate) (PHEMA), and poly(methyl methacrylate-co-ethylene glycol dimethacrylate) (PMMA-EG-PMMA).

23. A glucose-sensing device comprising:

a first electrode comprising the glucose-sensing electrode of claim 1; and

a second electrode configured to contact a test liquid when the first electrode contacts the test liquid,

wherein the nanoporous layer is configured to cause oxidation of glucose molecules therein in the absence of a glucose-specific enzyme when a bias voltage applied between the first and second electrodes in a range between about 0.2 V and about 0.45 V.

24. The device of claim 23, further comprising an electric circuit configured to supply the bias voltage between the first and second electrodes,

wherein, when the bias voltage is applied between the first and second electrodes, the glucose-sensing electrode is configured to cause oxidation of glucose in the nanoporous layer and configured to generate an electric current that is a sum of a glucose-oxidation current caused by the oxidation of glucose and a background current caused by other electrochemical interactions of the liquid and at least one of the first and second electrodes,

wherein, when the liquid contains glucose at a concentration of 4-20 mM (72-360 mg/dL), at steady state the glucose-oxidation current is at a level higher than 0.1 μ

A/mMcm² (10 nA/mMcm²).

25. The device of claim 23, wherein the at least one conductive layer comprises an electrically conductive or semiconductive material,

wherein the first electrode further comprises an electrolyte ion-blocking layer formed over the nanoporous layer and a biocompatibility layer formed over the electrolyte ion-blocking layer,

wherein, when contacting liquid containing glucose, Na⁺, K⁺, Ca²⁺, Cl⁻

, PO₄³⁻

and CO₃²⁻

, the electrolyte ion-blocking layer is configured to inhibit Na⁺, K⁺, Ca²⁺, Cl⁻

, PO₄³⁻

and CO₃²⁻

contained in the liquid from diffusing toward the nanoporous layer such that there is a substantial discontinuity of a combined concentration of Na⁺, K⁺, Ca²⁺, Cl⁻

, PO₄³⁻

and CO₃²⁻

between over and below the electrolyte ion-blocking layer.

26. The device of claim 23, wherein the interparticular nanopores are substantially free of nano-sized organic molecules, wherein the first electrode does not comprise a biocompatibility layer that is configured to inhibit immunological rejection.

27. The device of claim 23, wherein the nanoparticles are made of at least one selected from the group consisting of platinum (Pt), gold (Au), palladium (Pd), rhodium (Rh), titanium (Ti), ruthenium (Ru), tin (Sn), nickel (Ni), copper (Cu), indium (In), thallium (Tl), zirconium (Zr), iridium (Ir), and one or more oxides of the foregoing metals.

28. The device of claim 23, wherein the nanoporous layer has roughness factor between about 100 and about 2500, wherein the device is a continuous glucose monitoring device or blood glucose monitoring device.

29. A method of non-enzymatic glucose sensing, the method comprising:

providing the device of claim 23;

applying the bias voltage between the first electrode and the second electrode while a test fluid contacts both the first electrode and the second electrode, which causes oxidation of glucose contained in the test fluid at the nanoporous layer; and

measuring electric current from the first electrode; and

processing the electric current with or without additional data to provide a glucose level that corresponds to glucose contained in the test fluid.

30. A method of non-enzymatic glucose sensing, the method comprising:

providing the device of claim 25;

applying the bias voltage between the first electrode and the second electrode while a test fluid contacts both the first electrode and the second electrode, which causes oxidation of glucose contained in the test fluid at the nanoporous layer; and

measuring electric current from the first electrode; and

processing the electric current with or without additional data to provide a glucose level that corresponds to glucose contained in the test fluid.

31. A method of non-enzymatic glucose sensing, the method comprising:

providing the device of claim 26;

applying the bias voltage between the first electrode and the second electrode while a test fluid contacts both the first electrode and the second electrode, which causes oxidation of glucose contained in the test fluid at the nanoporous layer; and

measuring electric current from the first electrode; and

processing the electric current with or without additional data to provide a glucose level that corresponds to glucose contained in the test fluid.