CN113820371A - Implanted three-electrode micro sensor and preparation process thereof - Google Patents

Implanted three-electrode micro sensor and preparation process thereof Download PDF

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Publication number
CN113820371A
CN113820371A CN202111196320.5A CN202111196320A CN113820371A CN 113820371 A CN113820371 A CN 113820371A CN 202111196320 A CN202111196320 A CN 202111196320A CN 113820371 A CN113820371 A CN 113820371A
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substrate
conductive layer
conducting layer
layer
electrode
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毛建
王晓飞
晋佳义
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Shanghai Tangjian Biosensor Technology Co ltd
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Shanghai Tangjian Biosensor Technology Co ltd
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14546—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring analytes not otherwise provided for, e.g. ions, cytochromes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1468—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means
    • A61B5/1473—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means invasive, e.g. introduced into the body by a catheter
    • 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 discloses an implanted three-electrode microsensor, which comprises two substrates and three conducting layers, wherein the two substrates are respectively a first substrate and a second substrate, the three conducting layers are respectively a first conducting layer, a second conducting layer and a third conducting layer, and the front surface of the first substrate and the back surface of the second substrate are bonded together; the first conductive layer is arranged on the front side of the first substrate or the back side of the second substrate; the second conducting layer is arranged on the front surface of the second substrate; the third conductive layer is arranged on the back of the first substrate; one of the three conducting layers is provided with Ag/AgCl to form a reference electrode; the other conductive layer is provided with an enzyme-containing sensing material to form a working electrode, and the last conductive layer is used as a counter electrode. The implanted three-electrode microsensor has the advantages of simple structure, reasonable layout, high reliability and strong anti-interference capability. The invention also discloses a preparation process of the implanted three-electrode micro sensor, which is simple and suitable for batch production.

Description

Implanted three-electrode micro sensor and preparation process thereof
Technical Field
The invention relates to an implanted three-electrode microsensor for analyte detection and a preparation process thereof.
Background
Electrodes are widely used in the biomedical field, and electrical signals can be acquired through electrochemical reactions with analytes on the pre-implanted electrodes, so that some biological characteristics and health conditions can be indirectly acquired. For example, in the field of blood sugar continuity detection of human body, a functional electrode is implanted in the surface layer of the body in advance, a microelectronic device is used for acquiring a current signal generated by glucose oxidation-reduction reaction on the electrode, and the signal is transmitted to a computer or an intelligent device, so that the concentration state of blood sugar of the human body is continuously detected and analyzed in such a way, and the health state of the human body is evaluated.
The analyte may be one or more of cholesterol, glucose, uric acid, creatinine, insulin, ketones, lactose, urea nitrogen, and the like.
In view of the reduced pain and improved long-term wear experience, electrode designs and fabrication, which are typically implanted into the body, require greater miniaturization and greater flexibility. Typically 3-10mm in length and not more than 2mm in width or thickness, and the substrate of choice is also typically a flexible material such as PVC, PET, PP, PC, etc.
For an electrode, a three-electrode design system with a working electrode, a reference electrode, and a counter electrode is typically chosen for obtaining a stable electrical signal. However, the miniaturization of the components and devices results in a great reduction in the thickness of the insulating layer, short circuits between the conductive layers may occur, which may result in an insufficient electrical signal, insufficient anti-interference capability, and a need for improvement in long-term stability. Meanwhile, the reliability of the sensor may be affected by the fine circuit structures such as the line arrangement of the electrodes and the lead wires of the electrodes; moreover, the design of the known miniature three-electrode sensor on the market is extremely complex, the difficulty of the production process is increased, and the mass production is not facilitated.
Disclosure of Invention
The invention aims to overcome the defects of the prior art and provides an implanted three-electrode micro sensor and a preparation process thereof, which have the advantages of simple structure, reasonable layout, high reliability, strong anti-interference capability, simple process and suitability for batch production, and can effectively avoid short circuit between every two conducting layers.
One technical scheme for achieving the above purpose is as follows: an implanted three-electrode microsensor comprising two matrices, a first matrix and a second matrix, respectively, and three conductive layers, a first conductive layer, a second conductive layer and a third conductive layer, respectively, wherein:
the front surface of the first substrate and the back surface of the second substrate are bonded together through an adhesive layer;
the first conductive layer is disposed on the front side of the first substrate between the first substrate and the adhesive layer; or the first conductive layer is arranged on the back surface of the second substrate and positioned between the second substrate and the adhesive layer; the first substrate and the second substrate are bonded together by an adhesive, and the first conductive layer is wrapped therein.
The second conductive layer is arranged on the front surface of the second substrate;
the third conductive layer is disposed on the back side of the first substrate;
the part of the second conducting layer and the third conducting layer, where the analyte or the human skin is implanted, is covered by a protective film;
one of the three conducting layers is provided with an Ag/AgCl forming reference electrode; the other conducting layer is provided with an enzyme-containing sensing material to form a working electrode, and the last conducting layer is used as a counter electrode;
one end of the first substrate, the second substrate, the first conducting layer, the second conducting layer and the third conducting layer is a connecting end, and the other end of the first substrate, the second substrate, the first conducting layer, the second conducting layer and the third conducting layer is a far end; the connecting end of each conducting layer is connected with one pin; the distal end of the first substrate is flush with the distal end of the second substrate; the length relationship expressed below is premised on the connection ends being flush, and the connection ends can be connected in various ways in practical application.
The two substrates are equal in width; the width of the first conductive layer is less than the width of the substrate; the width of the second conductive layer is less than or equal to the width of the substrate; the width of the third conductive layer is less than or equal to the width of the substrate.
The embedded three-electrode microsensor is characterized in that the Ag/AgCl is printed on the first conductive layer; the enzyme-containing sensing material is coated on the second conductive layer or the third conductive layer, and the enzyme-containing sensing material is positioned between the corresponding conductive layer and the protective film.
The embedded three-electrode microsensor is characterized in that the printing width of the Ag/AgCl is larger than the width of the first conductive layer and is equal to the width of the substrate.
When the enzyme-containing sensing material is coated on the second conducting layer, the coating width of the enzyme-containing sensing material is larger than or equal to the width of the second conducting layer; when the enzyme-containing sensing material is coated on the third conducting layer, the coating width of the enzyme-containing sensing material is larger than or equal to the width of the third conducting layer.
In the three-electrode microsensor, the length of the first conducting layer is less than or equal to that of the first substrate, and when the first conducting layer is arranged on the back surface of the second substrate, the length of the first conducting layer is less than or equal to that of the second substrate.
The length of the second conductive layer is less than or equal to the length of the second substrate.
The length of the third conductive layer is less than or equal to the length of the first substrate.
The Ag/AgCl is printed at the far end of the first conducting layer;
the enzyme-containing sensing material is coated on the distal end of the second conductive layer or the third conductive layer.
The distance between the distal end of the second conductive layer and the distal end of the second substrate is equal to the distance between the distal end of the third conductive layer and the distal end of the first substrate, and the distance is greater than or equal to the printing length of Ag/AgCl.
When the first conductive layer is arranged on the front surface of the first substrate, the distance between the distal end of the first conductive layer and the distal end of the first substrate is greater than or equal to the coating length of the enzyme-containing sensing material;
when the first conducting layer is arranged on the back surface of the second substrate, the distance between the far end of the first conducting layer and the far end of the second substrate is larger than or equal to the coating length of the enzyme-containing sensing material.
The implanted three-electrode microsensor comprises a substrate, a conductive layer, an enzyme-containing sensing material and a substrate, wherein the substrate is one of PVC, PET, PP and PC, the conductive layer is one or more of carbon, gold, silver, platinum and titanium, the enzyme-containing sensing material is a nano conductive material containing platinum, titanium or gold, and enzyme in the enzyme-containing sensing material is glucose oxidase or dehydrogenase.
The other technical scheme for realizing the purpose is as follows: a preparation process of an implanted three-electrode microsensor comprises the following steps:
s1, firstly, printing a first conducting layer on the back surface of one piece of substrate material, printing a second conducting layer on the front surface of the substrate material and printing a third conducting layer on the other piece of substrate material by adopting a screen printing mode; the thickness of the substrate material is 100-300 um, and the printing thickness of each conductive layer is 5-20 um;
s2, drying the two pieces of substrate materials printed with the conducting layers at high temperature, then printing Ag/AgCl with the printing thickness of 10-30 um at the far end of the first conducting layer, cleaning and drying the substrate materials of the first conducting layer printed with Ag/AgCl;
s3, aligning and bonding the back surface of one substrate material with one surface of the other substrate material, which is not printed with the conductive layer, through an adhesive, wherein the adhesive forms an adhesive layer between the two substrate materials, and the adhesive is selected from UV glue;
s4, coating an enzyme-containing sensing material at the far end of the third conducting layer of the two bonded substrate materials, wherein the coating thickness of the enzyme-containing sensing material is 10-20 um; respectively covering protective films on the front surface of the second conductive layer and the back surface of the third conductive layer, wherein the thickness of the protective films is 5-30 micrometers, and manufacturing a sensor blank;
and S5, cutting the sensor blank according to the size and shape of the micro sensor, and manufacturing a plurality of implanted three-electrode micro sensors in batches, wherein in the implanted three-electrode micro sensors, the first conducting layer printed with Ag/AgCl is used as a reference electrode, the third conducting layer coated with an enzyme-containing sensing material is used as a working electrode, and the second conducting layer is used as a counter electrode.
In the implanted three-electrode micro sensor and the preparation process thereof, the three-electrode micro sensor has the advantages of simple structure, reasonable layout, high reliability, strong anti-interference capability and suitability for batch production, and can effectively avoid short circuit among all conducting layers.
Drawings
Fig. 1 is a side view of an implantable three-electrode microsensor of example 1;
FIG. 2 is a sectional view taken along line A-A of FIG. 1;
FIG. 3 is a sectional view taken along line B-B of FIG. 1;
FIG. 4 is an exploded structural view of the implantable three-electrode microsensor of example 1;
fig. 5 is a side view of the implantable three-electrode microsensor of example 2;
FIG. 6 is a sectional view taken along line A-A of FIG. 5;
FIG. 7 is a sectional view taken along line B-B of FIG. 5;
fig. 8 is a flow chart of a manufacturing process of the implanted three-electrode microsensor of the present invention.
Detailed Description
In order that those skilled in the art will better understand the technical solution of the present invention, the following detailed description is given with reference to the accompanying drawings:
example 1:
referring to fig. 1 to 4, an implanted three-electrode micro sensor includes two substrates, i.e., a first substrate 1 and a second substrate 2, and three conductive layers, i.e., a first conductive layer 3, a second conductive layer 4, and a third conductive layer 5.
The front surface of the first substrate 1 and the back surface of the second substrate 2 are bonded together by an adhesive layer 10; the first conductive layer 3 is disposed on the back side of the second substrate 2 between the second substrate 2 and the adhesive layer 10; the second conductive layer 4 is arranged on the front surface of the second substrate 2; the third conductive layer 5 is disposed on the back surface of the first substrate 1; the front surface of the second conductive layer 4 is covered with a protective film 6, and the back surface of the third conductive layer 5 is covered with a protective film 7.
One end of the first substrate 1, the second substrate 2, the first conducting layer 3, the second conducting layer 4 and the third conducting layer 5 is a connecting end, the other end of the first substrate is a far end, and the distance between the connecting end and the far end is the length direction; when the device is used, the far end is placed in a reaction environment, and the connecting end is used for being connected with an external electronic component. The length relationship expressed below is premised on the connection ends being flush, and the connection ends can be connected in various ways in practical application. The first substrate 1 has a length L1Width W1(ii) a The second substrate 2 has a length L2Width W2(ii) a The first conductive layer 3 has a length L3Width W3(ii) a The second conductive layer 4 has a length L4Width W4(ii) a The third conductive layer 5 has a length L5Width W5。
Width W of the first substrate 11And the width W of the second substrate 22Equal; width W of first conductive layer 33Less than the width of the substrate; width W of second conductive layer 44Is equal to the width W of the second substrate 22(ii) a Width W of third conductive layer 55Is equal to the width W of the first substrate 11。
The distal end of the first substrate 1 is flush with the distal end of the second substrate 2; length L of first conductive layer 33Is equal to the length L of the second substrate 22(ii) a Length L of second conductive layer 44Less than the length L of the second substrate 22(ii) a Length L of third conductive layer 55Less than or equal to the length L of the first substrate 11。
One of the three conducting layers is provided with Ag/AgCl to form a reference electrode; the other conducting layer is provided with an enzyme-containing sensing material to form a working electrode, and the last conducting layer is used as a counter electrode, so that a three-electrode system is formed. The connecting end of each conductive layer is connected with one pin.
In this embodiment, Ag/AgCl 8 is printed at the distal end of the first conductive layer 3, and the printing width W of Ag/AgCl 88Is larger than the width W of the first conductive layer 33And equal to that of the second substrate 2Width W2. In the printing, the Ag/AgCl extends in the width direction to both sides to cover the width of the second substrate 2. The Ag/AgCl has a larger area on one hand, and cannot be completely wrapped by the first substrate 1 and the second substrate 2, the outermost side of the Ag/AgCl in the width direction is exposed outside, and the Ag/AgCl can be contacted with detection liquid in actual use, so that a closed-loop circuit is formed between the Ag/AgCl and the working electrode. The enzyme-containing sensitive material 9 is printed at the distal end of the third conductive layer 5 between the third conductive layer 5 and the protective film 7, and the printing width W of the enzyme-containing sensitive material 99Is equal to the width W of the third conductive layer 55. The first conducting layer 3 and the Ag/AgCl thereon form a reference electrode, the connecting end of the first conducting layer 3 is connected with a reference electrode pin 17, the third conducting layer 5 and the enzyme-containing sensing material 9 thereon form a working electrode, the connecting end of the third conducting layer 5 is connected with a working electrode pin 18, a part of the second conducting layer 4 is exposed in a working environment to form a counter electrode, and the connecting end of the second conducting layer 4 is connected with a pair of electrode pins 16.
The distance between the distal end of the second electrically conductive layer 4 and the distal end of the second substrate 2 is equal to the distance between the distal end of the third electrically conductive layer 5 and the distal end of the first substrate 1, both L0And the distance L0Printing length L greater than Ag/AgCl8Of course, the distance L0May also be equal to the printing length L of Ag/AgCl8. The design can effectively avoid the phenomenon of short circuit caused by the working electrode, the reference electrode and the counter electrode being close to each other.
The first substrate 1 and the second substrate 2 can be made of flexible materials such as PVC, PET, PP, PC and the like so as to reduce the foreign body sensation after being implanted into the skin. As the material of the first conductive layer 3, the second conductive layer 4, and the third conductive layer 5, a material having good conductivity such as carbon, gold, or platinum can be used. The enzyme-containing sensing material on the third conductive layer 5 is a nano material with good conductive performance and containing one of platinum, titanium and gold, and glucose oxidase or dehydrogenase commonly used for blood sugar detection is added into the material. The protective film 6 and the protective film 7 coated on the second conductive layer 4, the third conductive layer 5 and the enzyme-containing sensitive material 9 are a semi-permeable membrane having a selective filtration function for glucose. The semipermeable membrane can effectively prevent other substances with redox characteristics such as lactose, uric acid and the like from entering the reaction layer, and avoid the substances from interfering the sensor. Meanwhile, since the amount of glucose oxidase or dehydrogenase on the working electrode is generally limited, glucose entering the enzyme-containing sensing layer cannot be completely redox, and thus, another characteristic of the protective film is to limit the amount of glucose entering the sensing layer, thereby obtaining a better linear measurement range.
Example 2:
referring to fig. 5 to 7, an implanted three-electrode micro sensor is different from embodiment 1 in that:
length L of first conductive layer 33Less than the length L of the second substrate 22(ii) a The distance L between the distal end of the first conductive layer 3 and the distal end of the second substrate 210Is longer than the coating length L of the enzyme-sensitive material 99Of course, the distance L between the distal end of the first conductive layer 3 and the distal end of the second substrate 210Or equal to the coating length L of the enzyme-sensitive material 99。
The design advantage of example 2 above over example 1 is that it is possible to have the enzyme-containing sensing material 9 on the third conductive layer 5 positioned at the most distal end of the sensor. The enzyme-containing sensing material 9 is an area where glucose to be detected generates redox reaction under the action of oxidase or dehydrogenase, and when the sensor is implanted into the skin, the area will penetrate into the innermost layer of subcutaneous tissue, so as to obtain more stable test data. Or on the premise of obtaining stable data, the sensor can be made shorter, and foreign body sensation after implantation can be reduced.
The inventive implantable three-electrode microsensor can be modified in that, for example, the first conductive layer 3 can be disposed on the front side of the first substrate 1 between the first substrate 1 and the adhesive layer 10, in which case the length of the first conductive layer 3 is less than or equal to the length of the first substrate 1. For another example, the enzyme-containing sensitive material 9 may be coated on the second conductive layer 4, with the enzyme-containing sensitive material 9 being located between the corresponding second conductive layer 4 and the protective film 6. The first substrate 1 and the second substrate 2 can be bonded together by the adhesive layer 10, or the two substrates can be directly bonded by hot melting without using an adhesive.
Referring to fig. 8, the implantable three-electrode microsensor of the present invention can be prepared by the following preparation process, including the following steps:
s1, firstly, printing a first conducting layer on the back surface of one piece of substrate material, printing a second conducting layer on the front surface of the substrate material and printing a third conducting layer on the other piece of substrate material by adopting a screen printing mode; the thickness of the substrate material is 100-300 um, and the printing thickness of each conductive layer is 5-20 um;
s2, drying the two pieces of substrate materials printed with the conducting layers at high temperature, then printing Ag/AgCl with the printing thickness of 10-30 um at the far end of the first conducting layer, cleaning and drying the substrate materials of the first conducting layer printed with Ag/AgCl;
s3, aligning and bonding the back of one substrate material with one surface of the other substrate material, which is not printed with the conductive layer, through an adhesive, wherein the adhesive forms an adhesive layer between the two substrate materials, and the adhesive is UV adhesive;
s4, coating an enzyme-containing sensing material at the far end of the third conducting layer of the two bonded substrate materials, wherein the coating thickness of the enzyme-containing sensing material is 10-20 um; respectively covering protective films on the front surface of the second conductive layer and the back surface of the third conductive layer, wherein the thickness of the protective films is 5-30 micrometers, and manufacturing a sensor blank;
and S5, cutting the sensor blank according to the size and shape of the micro sensor, and batch-manufacturing a plurality of implanted three-electrode micro sensors, wherein the implanted three-electrode micro sensors comprise a first conductive layer printed with Ag/AgCl as a reference electrode, a third conductive layer coated with an enzyme-containing sensing material as a working electrode, and a second conductive layer as a counter electrode. The connecting end of each conductive layer is connected with one pin.
When the implanted three-electrode microsensor is used, the reference electrode, the working electrode and the counter electrode are externally connected with the detection circuit through the corresponding pins, after the distal end part of the microsensor is inserted into a human body, glucose in human tissue fluid generates glucolactone under the action of glucose oxidase or dehydrogenase, the enzyme is converted from an oxidation state to a reduction state, and the process can cause e-transfer. e-is detected by the enzyme through the loop formed by the working electrode and the counter electrode by an external circuit. And the magnitude of the current and the concentration of the glucose have a certain linear corresponding relation, so that the concentration of the glucose in human blood can be monitored.
In conclusion, in the implanted three-electrode microsensor and the preparation process thereof, the three-electrode microsensor has the advantages of simple structure, reasonable layout, high reliability, strong anti-interference capability, simple process and suitability for batch production, and can effectively avoid short circuit between every two conductive layers.
It should be understood by those skilled in the art that the above embodiments are only for illustrating the present invention and are not to be used as a limitation of the present invention, and that changes and modifications to the above described embodiments are within the scope of the claims of the present invention as long as they are within the spirit and scope of the present invention.

Claims (8)

1. An implanted three-electrode microsensor comprising two substrates, a first substrate and a second substrate, respectively, and three conductive layers, a first conductive layer, a second conductive layer and a third conductive layer, respectively, wherein:
the front surface of the first substrate and the back surface of the second substrate are bonded together through an adhesive layer;
the first conductive layer is disposed on the front side of the first substrate between the first substrate and the adhesive layer; or the first conductive layer is arranged on the back surface of the second substrate and positioned between the second substrate and the adhesive layer;
the second conductive layer is arranged on the front surface of the second substrate;
the third conductive layer is disposed on the back side of the first substrate;
protective films are covered on the front surface of the second conductive layer and the back surface of the third conductive layer respectively;
one of the three conducting layers is provided with an Ag/AgCl forming reference electrode; the other conducting layer is provided with an enzyme-containing sensing material to form a working electrode, and the last conducting layer is used as a counter electrode;
one end of the first substrate, the second substrate, the first conducting layer, the second conducting layer and the third conducting layer is a connecting end, and the other end of the first substrate, the second substrate, the first conducting layer, the second conducting layer and the third conducting layer is a far end; the connecting end of each conducting layer is connected with one pin; the distal end of the first substrate is flush with the distal end of the second substrate;
the two substrates are equal in width; the width of the first conductive layer is less than or equal to the width of the substrate; the width of the second conductive layer is less than or equal to the width of the substrate; the width of the third conductive layer is less than or equal to the width of the substrate.
2. The implantable three-electrode microsensor of claim 1, wherein the Ag/AgCl is printed on the first conductive layer; the enzyme-containing sensing material is coated on the second conductive layer or the third conductive layer, and the enzyme-containing sensing material is positioned between the corresponding conductive layer and the protective film.
3. The implantable three-electrode microsensor of claim 2, wherein the printed width of Ag/AgCl is greater than or equal to the width of the first conductive layer and equal to the width of the substrate;
when the enzyme-containing sensing material is coated on the second conducting layer, the coating width of the enzyme-containing sensing material is larger than or equal to the width of the second conducting layer; when the enzyme-containing sensing material is coated on the third conducting layer, the coating width of the enzyme-containing sensing material is larger than or equal to the width of the third conducting layer.
4. The implantable three-electrode microsensor of claim 2 or 3, wherein the length of the first conductive layer is less than or equal to the length of the first substrate when the first conductive layer is disposed on the front surface of the first substrate, and the connecting end of the first conductive layer is flush with the connecting end of the first substrate; when the first conducting layer is arranged on the back surface of the second substrate, the length of the first conducting layer is less than or equal to that of the second substrate, and the connecting end of the first conducting layer is flush with the connecting end of the second substrate;
the length of the second conducting layer is less than or equal to that of the second substrate, and the connecting end of the second conducting layer is flush with the connecting end of the second substrate;
the length of the third conducting layer is less than or equal to that of the first substrate, and the connecting end of the third conducting layer is flush with the connecting end of the first substrate;
the Ag/AgCl is printed at the far end of the first conducting layer;
the enzyme-containing sensing material is coated on the distal end of the second conductive layer or the third conductive layer.
5. The implantable three-electrode microsensor of claim 4, wherein the distance between the distal end of the second conductive layer and the distal end of the second substrate is equal to the distance between the distal end of the third conductive layer and the distal end of the first substrate, and the distance is greater than or equal to the print length of Ag/AgCl.
6. The implantable three-electrode microsensor of claim 4, wherein the distance between the distal end of the first conductive layer and the distal end of the first substrate is greater than or equal to the coated length of the enzyme-containing sensing material when the first conductive layer is disposed on the front side of the first substrate;
when the first conducting layer is arranged on the back surface of the second substrate, the distance between the far end of the first conducting layer and the far end of the second substrate is larger than or equal to the coating length of the enzyme-containing sensing material.
7. The implantable three-electrode microsensor of claim 1, wherein the substrate is selected from one of PVC, PET, PP and PC, the conductive layer is selected from one or more of carbon, gold, silver, platinum and titanium, the enzyme-containing sensing material is selected from a nano-conductive material containing platinum, titanium or gold, and the enzyme in the enzyme-containing sensing material is selected from glucose oxidase or dehydrogenase.
8. The process for preparing an implanted three-electrode microsensor according to claim 1, comprising the steps of:
s1, firstly, printing a first conducting layer on the back surface of one piece of substrate material, printing a second conducting layer on the front surface of the substrate material and printing a third conducting layer on the other piece of substrate material by adopting a screen printing mode; the thickness of the substrate material is 100-300 um, and the printing thickness of each conductive layer is 5-20 um;
s2, drying the two pieces of substrate materials printed with the conducting layers at high temperature, then printing Ag/AgCl with the printing thickness of 10-30 um at the far end of the first conducting layer, cleaning and drying the substrate materials of the first conducting layer printed with Ag/AgCl;
s3, aligning and bonding the back surface of one substrate material with one surface of the other substrate material, which is not printed with the conductive layer, through an adhesive, wherein the adhesive forms an adhesive layer between the two substrate materials, and the adhesive is selected from UV glue;
s4, coating an enzyme-containing sensing material at the far end of the third conducting layer of the two bonded substrate materials, wherein the coating thickness of the enzyme-containing sensing material is 10-20 um; respectively covering protective films on the front surface of the second conductive layer and the back surface of the third conductive layer, wherein the thickness of the protective films is 5-30 micrometers, and manufacturing a sensor blank;
and S5, cutting the sensor blank according to the size and shape of the micro sensor, and manufacturing a plurality of implanted three-electrode micro sensors in batches, wherein in the implanted three-electrode micro sensors, the first conducting layer printed with Ag/AgCl is used as a reference electrode, the third conducting layer coated with an enzyme-containing sensing material is used as a working electrode, and the second conducting layer is used as a counter electrode.
CN202111196320.5A 2021-10-14 2021-10-14 Implanted three-electrode micro sensor and preparation process thereof Withdrawn CN113820371A (en)

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Application publication date: 20211221