Blood glucose sensor

Abstract

The utility model discloses a blood glucose sensor, which belongs to the technical field of blood glucose detection and comprises a PET (polyethylene terephthalate) substrate and an electrode layer arranged on the upper surface of the PET substrate, and two sections of laser etching partition gaps are arranged in the electrode layer to divide the electrode layer into a working electrode, a reference electrode and a counter electrode which are positioned on the same horizontal plane and are sequentially arranged. The blood glucose sensor solves the problems that an existing blood glucose sensor is too many in silk-screen procedure and complex in operation, and electrode alignment needs to be conducted in the silk-screen process.

Description

TECHNICAL FIELD

[0001] The utility model relates to blood sugar detection technical field, especially in a kind of blood sugar sensor. BACKGROUND

[0002] The existing blood sugar sensor is printed out by layered silk printing three electrodes, three electrodes are working electrode, reference electrode and counter electrode, since it is formed by layered superposition, thus each electrode needs to be combined after being printed out separately, thus there are too many silk printing procedures and the problems of complicated operation, and multiple printing can cause deviation of electrode alignment between layers in silk printing process, thereby leading to the quality decline of blood sugar sensor. UTILITY MODEL CONTENT

[0003] In order to overcome the defects existing in the prior art, the utility model provides a blood sugar sensor to solve the above problems.

[0004] The technical scheme adopted by the utility model to solve its technical problems is: a blood sugar sensor, including PET base and electrode layer being arranged on the upper surface of PET base, two laser engraving gap intervals are arranged in the electrode layer to divide the electrode layer into working electrode, reference electrode and counter electrode which are arranged in the same horizontal plane in sequence.

[0005] It is worth mentioning that the electrode layer is biological carbon paste layer.

[0006] Preferably, the electrode layer includes connected sensing end and extension output section, the sensing end is provided with three sensing branch parts, when working electrode, reference electrode and counter electrode are formed by laser engraving gap interval, three sensing branch parts correspond to sensing part of working electrode, sensing part of reference electrode and sensing part of counter electrode respectively, and insulating gap is arranged between adjacent two sensing branch parts.

[0007] Optionally, the upper surface of the electrode layer is provided with an insulating layer.

[0008] Specifically, the end of the extension output section of the electrode layer, away from the sensing end, is provided with a silver chloride paste layer.

[0009] The beneficial effects of this invention are as follows: In the blood glucose sensor, during screen printing, the entire electrode layer is printed onto the same layer of the PET substrate in one go. Then, during molding, two laser-engraved gaps are cut into the electrode layer to divide it into mutually insulated working electrode, reference electrode, and counter electrode. This reduces the number of printing steps by requiring only one printing operation. Furthermore, since the working electrode, reference electrode, and counter electrode do not need to be insulated by stacking different layers during formation, electrode alignment misalignment is avoided, ensuring the quality of the blood glucose sensor. Attached Figure Description

[0010] Figure 1 This is a schematic diagram of the electrode layer after laser engraving in one embodiment of the present invention;

[0011] Figure 2 This is a schematic diagram of the structure of a PET substrate in one embodiment of the present invention;

[0012] Figure 3 This is a schematic diagram of the electrode layer before laser engraving and cutting in one embodiment of the present invention;

[0013] Figure 4 This is a schematic diagram of the insulating layer structure in one embodiment of the present invention;

[0014] In the figure: 1 PET substrate; 2 electrode layer; 21 working electrode; 22 reference electrode; 23 counter electrode; 24 sensing end; 25 extended output section; 26 sensing branch; 27 insulation gap; 3 laser engraving partition gap; 4 insulation layer; 5 silver chloride paste layer. Detailed Implementation

[0015] The specific embodiments of this utility model will be further described below with reference to the accompanying drawings. It should be noted that these descriptions are for the purpose of aiding understanding of this utility model, but do not constitute a limitation thereof. Furthermore, the technical features involved in the various embodiments of this utility model described below can be combined with each other as long as they do not conflict with each other.

[0016] like Figures 1-4 As shown, a blood glucose sensor includes a PET substrate 1 and an electrode layer 2 disposed on the upper surface of the PET substrate 1. The electrode layer 2 is provided with two laser-engraved partition gaps 3 to divide the electrode layer 2 into a working electrode 21, a reference electrode 22 and a counter electrode 23 disposed sequentially on the same horizontal plane.

[0017] In the blood glucose sensor, during screen printing, the entire electrode layer 2 is printed onto the same layer of the PET substrate 1 in one go. Then, during molding, two laser-etched partition gaps 3 are cut into the electrode layer 2 using laser engraving, thereby dividing the electrode layer 2 into a mutually insulated working electrode 21, a reference electrode 22, and a counter electrode 23. This reduces the number of printing steps by requiring only one printing operation. Furthermore, since the working electrode 21, reference electrode 22, and counter electrode 23 do not need to be insulated by stacking different layers during formation, electrode alignment misalignment is avoided, ensuring the quality of the blood glucose sensor.

[0018] Specifically, the electrode layer 2 is a bio-carbon paste layer. The use of a bio-carbon paste layer in the blood glucose sensor has the following advantages:

[0019] Biocompatibility: Biocarbon paste has good biocompatibility and can be used in the body for a long time without causing rejection. This characteristic is very important for long-term implantable devices because it reduces the risk of reaction with materials in the body.

[0020] Conductivity: The conductivity of bio-carbon paste makes it an ideal material for electrochemical sensors. In the blood glucose sensor, bio-carbon paste can effectively conduct electrical signals, improving the sensor's sensitivity and response speed.

[0021] Stability: The bio-carbon paste material has good chemical and physical stability and can maintain its performance in the complex physiological environment in vivo. This means that the blood glucose sensor can provide accurate and reliable glucose readings without the need for frequent calibration or replacement.

[0022] It is worth noting that the electrode layer 2 includes a connected sensing end 24 and an extended output section 25. The sensing end 24 has three sensing branches 26. When the working electrode 21, reference electrode 22, and counter electrode 23 are formed by laser engraving and separating the gaps 3, the three sensing branches 26 correspond to the sensing portions of the working electrode 21, the reference electrode 22, and the counter electrode 23, respectively. An insulating gap 27 is provided between adjacent sensing branches 26. Therefore, before laser engraving and cutting, when printing the electrode layer 2 on the PET substrate 1, the three sensing ends 24 are separated by two insulating gaps 27 and then connected in parallel to the extended output section 25. In this embodiment, laser engraving is used to cut the extended output section 25. The cutting line formed by the laser engraving gap 3 extends from the insulation gap 27 to the end of the extended output section 25 away from the sensing end 24, thereby dividing the extended output section 25 into three independent segments to achieve insulation between them. Each of the three independent segments is connected to a corresponding sensing branch 26 to achieve conductivity.

[0023] Preferably, the upper surface of the electrode layer 2 is provided with an insulating layer 4. This layer, in conjunction with the PET substrate 1, encapsulates the electrode layer 2, thereby protecting it.

[0024] Specifically, a silver chloride paste layer 5 is provided at the end of the extended output section 25 of the electrode layer 2 that is away from the sensing end 24. Specifically, the silver chloride paste layer 5 is disposed on a section of the reference electrode that is away from its sensing portion. The placement of the silver chloride paste layer 5 on the reference electrode has the following advantages:

[0025] Good stability: The potential of silver chloride paste layer 5 is stable and less affected by temperature, and can provide a stable potential over a wide temperature range;

[0026] Preparation is simple: Silver chloride paste layer 5 is relatively easy to prepare and convenient to use;

[0027] Accurate potential: The silver chloride paste layer 5 has an accurate potential, which can provide accurate measurement results;

[0028] Wide range of applications: Silver chloride paste layer 5 is suitable for various electrochemical measurements, including conductivity measurement, potentiometric titration, etc.

[0029] Good long-term stability: Under appropriate storage and use conditions, silver chloride paste layer 5 has good long-term stability, is not prone to aging, and can be used for a long time.

[0030] The embodiments of this utility model have been described in detail above with reference to the accompanying drawings, but this utility model is not limited to the described embodiments. For those skilled in the art, various changes, modifications, substitutions, and variations can be made to these embodiments without departing from the principles and spirit of this utility model, and these variations still fall within the protection scope of this utility model.

Claims

1. A blood glucose sensor, characterized in that: It includes a PET substrate and an electrode layer disposed on the upper surface of the PET substrate. The electrode layer has two laser-engraved partition gaps to divide the electrode layer into a working electrode, a reference electrode and a counter electrode disposed sequentially on the same horizontal plane.

2. A blood glucose sensor according to claim 1, characterized in that: The electrode layer is a bio-carbon paste layer.

3. A blood glucose sensor according to claim 1, characterized in that: The electrode layer includes a connected sensing end and an extended output section. The sensing end has three sensing branches. When the working electrode, reference electrode and counter electrode are formed by laser engraving the gap, the three sensing branches correspond to the sensing part of the working electrode, the sensing part of the reference electrode and the sensing part of the counter electrode, respectively. An insulating gap is provided between two adjacent sensing branches.

4. A blood glucose sensor according to claim 1, characterized in that: An insulating layer is provided on the upper surface of the electrode layer.

5. A blood glucose sensor according to claim 3, characterized in that: A silver chloride paste layer is provided at the end of the extended output section of the electrode layer that is away from the sensing end.

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