Preparation method of dynamic blood glucose meter sensor and implantable sensor

Abstract

The present invention provides a method for preparing a dynamic blood glucose meter sensor and an implantable sensor, which includes the following steps: (a) forming N first electrodes, N second electrodes and N third electrodes on the surface of a substrate layer, wherein N is an integer greater than or equal to 2, and the substrate layer is made of a flexible insulating material; (b) cutting the substrate layer to form a plurality of sensor units, each of which includes a needle implant part and an interface part; (c) forming a first drug coating on the surface of the first electrode of the needle implant part of each sensor unit, and forming a second drug coating on the surface of the third electrode of the needle implant part of each sensor unit. The present invention can greatly reduce the width of the needle implant part by forming a working electrode and a reference electrode for signal acquisition on both side surfaces of the flexible substrate layer, thereby reducing the foreign body sensation after implantation and improving the comfort of long-term wearing.

Description

Technical Field

[0001] The present invention relates to the field of blood sugar detection, and more specifically, to a preparation method of a dynamic blood sugar meter sensor and an implantable sensor. Background Art

[0002] Diabetes is a common metabolic endocrine disease caused by a lack of insulin or other receptor abnormalities in the human body. It is characterized by high blood sugar and is a worldwide epidemic disease. Its incidence has been rising significantly in recent years. Long-term high blood sugar leads to chronic damage and dysfunction of various tissues, especially the eyes, kidneys, heart, blood vessels, and nerves.

[0003] Glucose testing is very important for diabetic patients. Through glucose testing, it can be determined when to inject insulin to lower the glucose level in the body, or to supplement glucose to bring the glucose level to normal. The current diagnostic methods (a fasting blood glucose value and a glucose tolerance test) have obvious shortcomings, with high misdiagnosis and missed diagnosis rates. In addition, blood glucose can only be measured at one time point each time, and blood glucose needs to be monitored multiple times a day, but it is still impossible to fully understand blood glucose fluctuations.

[0004] The dynamic blood glucose meter can provide continuous blood glucose graphs, detect "hidden" high and low blood glucose, provide a full range of human blood glucose parameter information, and provide accurate and comprehensive data for the diagnosis of diabetes, thereby improving the diagnosis level. It helps doctors understand the impact of factors such as diet, exercise, medication, and mood swings on blood glucose levels in diabetic patients, find out the reasons for blood glucose fluctuations, and scientifically formulate or adjust corresponding medication, diet, exercise, and monitoring plans. At present, the dynamic blood glucose meter has been widely used in glucose testing for diabetic patients.

[0005] Most of the existing continuous blood glucose meters convert the blood glucose value in the tissue fluid into an electrical signal through a sensor implanted under the skin, and store, record, and output the electrical signal. In the existing continuous blood glucose sensors, the sensors usually use metal needles, which are usually hard. Since the metal needles need to be kept under the skin for a long time, patients often feel a foreign body sensation and are uncomfortable to wear. Summary of the invention

[0006] The technical problem to be solved by the present invention is to provide a method for preparing a sensor for a dynamic blood glucose meter and an implantable sensor, in view of the problem that the sensor of the dynamic blood glucose meter mentioned above is uncomfortable to wear due to the use of metal needles.

[0007] The technical solution of the present invention to solve the above technical problem is to provide a method for preparing a continuous blood glucose meter sensor, comprising the following steps:

[0008] (a) forming N first electrodes, N second electrodes and N third electrodes on the surface of a substrate layer, wherein N is an integer greater than or equal to 2; the substrate layer is made of a flexible insulating material, the first electrode is made of a first metal coating attached to the front surface of the substrate layer, the second electrode is made of a second metal coating attached to the front surface of the substrate layer, the third electrode is made of a second metal coating attached to the back surface of the substrate layer, and each of the third electrodes is electrically connected to one second electrode;

[0009] (b) cutting the substrate layer to form a plurality of sensor units, each of the sensor units comprising a needle implanting portion and an interface portion, and on the front side of the sensor unit, the first electrode extends from the needle implanting portion to the interface portion, and the second electrode is located on the front side of the interface portion, and on the back side of the sensor unit, the third electrode extends from the needle implanting portion to the interface portion and is electrically connected to the second electrode on the front side of the interface portion;

[0010] (c) A first drug coating is formed on the surface of the first electrode of the needle-implanted portion of each sensor unit, and the first drug coating and the first electrode together constitute the working electrode of the sensor unit, and a second drug coating is formed on the surface of the third electrode of the needle-implanted portion of each sensor unit, and the second drug coating, the third electrode and the second electrode together constitute the reference electrode of the sensor.

[0011] As a further improvement of the present invention, the method further comprises:

[0012] At least one detection electrode is formed on the surface of the substrate layer, each of the detection electrodes is composed of a second metal coating layer attached to the back of the substrate layer and in a strip shape, and a plurality of third electrodes are arranged side by side on one side of the detection electrode, and the plurality of third electrodes are electrically connected to the detection electrodes respectively.

[0013] As a further improvement of the present invention, when the substrate layer is cut to form a plurality of sensor units, the substrate layer to which the detection electrode is attached is cut to form a connecting portion, and the sensor units in which a plurality of third electrodes are electrically connected to the detection electrode are connected via the connecting portion; the method further comprises:

[0014] Conducting conductivity detection on a plurality of sensor units respectively connected to the connection part through the detection electrodes;

[0015] The step (c) is performed after the conductivity test is passed; and after the step (c), the method further includes: separating the plurality of sensor units from the connecting portion to form a plurality of sensor monomers.

[0016] As a further improvement of the present invention, the substrate layer includes multiple groups of through holes. When N first electrodes, N second electrodes and N third electrodes are formed on the surface of the substrate layer, each of the first electrodes corresponds to a second electrode in a projection area of ​​the substrate layer and a third electrode in a projection area of ​​the substrate layer, and each group of through holes is respectively covered by a second electrode and a third electrode, and the second electrode and the third electrode are electrically connected through a second metal filled in the through holes.

[0017] As a further improvement of the present invention, the first metal coating is composed of gold, and the first metal coating is attached to the surface of the substrate layer by an electroplating process;

[0018] The second metal coating layer is made of silver, and the second metal coating layer is attached to the surface of the substrate layer through an electroplating process or a printing process.

[0019] As a further improvement of the present invention, the first drug coating includes an enzyme-containing sensing material; and the second drug coating contains a substance that prevents a human body from having an immune response.

[0020] As a further improvement of the present invention, when the substrate layer is cut to form a plurality of sensor units, the substrate layer is cut by a die-cutting device to form at least one sensor group, and each of the sensor groups includes a connecting portion and a plurality of sensor units connected to the connecting portion.

[0021] As a further improvement of the present invention, each of the third electrodes comprises a needle-shaped portion corresponding to the needle-implanting portion of the sensor unit and a sheet-shaped portion corresponding to the interface portion of the sensor unit;

[0022] The third electrode and the detection electrode on the surface of the substrate layer are formed simultaneously, and every two of the detection electrodes are arranged in parallel on the back side of the substrate layer, and there are two third electrode groups between the two detection electrodes, and each third electrode group includes a plurality of third electrodes arranged side by side; in the two third electrode groups, each third electrode group is adjacent to a detection electrode, and the sheet portions of all third electrodes in the same third electrode group are located on a straight line parallel to the detection electrode and are respectively connected to the detection electrode; the needle portions of the third electrodes in the two third electrode groups are located between two rows of sheet portions and are arranged alternately.

[0023] As a further improvement of the present invention, the width of the needle implant part is 0.2-0.4mm, and the width of the interface part is 5.0-8.0mm; the first electrode and the third electrode are respectively in the shape of a figure 7, the second electrode is rectangular, and the area of ​​the second electrode is not less than 1.8×2.0mm.

[0024] The present invention also provides an implantable sensor, which is prepared by the above-mentioned preparation method of the continuous blood glucose meter sensor.

[0025] The present invention has the following beneficial effects: by forming working electrodes and reference electrodes for signal acquisition on both side surfaces of a flexible substrate layer, respectively, the width of the needle implant can be greatly reduced, thereby reducing the foreign body sensation after implantation and improving the comfort of long-term wearing. BRIEF DESCRIPTION OF THE DRAWINGS

[0026] Figure 1 It is a schematic flow chart of a method for preparing a continuous blood glucose meter sensor provided by an embodiment of the present invention;

[0027] Figure 2 It is a structural schematic diagram of the back side of the substrate layer in the method for preparing the continuous blood glucose meter sensor provided by an embodiment of the present invention;

[0028] Figure 3 It is a structural schematic diagram of the front side of the substrate layer in the method for preparing the continuous blood glucose meter sensor provided by an embodiment of the present invention;

[0029] Figure 4 This is a schematic diagram of the decomposed structure of a sensor monomer prepared by the preparation method of a continuous blood glucose meter sensor provided by an embodiment of the present invention;

[0030] Figure 5 This is another schematic diagram of the structure of a sensor monomer prepared by the method for preparing a continuous blood glucose meter sensor provided by an embodiment of the present invention. DETAILED DESCRIPTION

[0031] In order to make the purpose, technical solution and advantages of the present invention more clearly understood, the present invention is further described in detail below in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain the present invention and are not intended to limit the present invention.

[0032] like Figure 1 , which is a flow chart of a method for preparing a continuous blood glucose meter sensor provided by an embodiment of the present invention, and the method can be used to manufacture a sensor that is implanted subcutaneously in a human body and continuously monitors blood glucose data of a human body. Specifically, the method for preparing a continuous blood glucose meter sensor in this embodiment includes the following steps:

[0033] Step S11: Combination Figures 2-3 As shown, N first electrodes 22 , N second electrodes 23 and N third electrodes 24 are formed on the surface of the substrate layer 21 , where N is an integer greater than or equal to 2.

[0034] In this embodiment, the substrate layer 21 can be made of a flexible insulating material such as PET (Polyethylene terephthalate). The first electrode 22 is made of a first metal coating attached to the front of the substrate layer 21, the second electrode 23 is made of a second metal coating attached to the front of the substrate layer 21, and the third electrode 24 is made of a second metal coating attached to the back of the substrate layer 21, and each third electrode 24 is electrically connected to a second electrode 23. That is, the second electrode 23 and the third electrode 24 are made of the same metal coating, and the first electrode 22 is made of a different metal coating.

[0035] In order to ensure the structural strength of the sensor and reduce the foreign body sensation after being implanted in the skin, the thickness of the substrate layer 21 can be set to 0.15-0.25 mm.

[0036] Step S12: Cut the substrate layer 21 to form a plurality of sensor units, and combine Figure 5 As shown, each sensor unit includes a needle implant part 281 and an interface part 282, and on the front side of the sensor unit, the first electrode 22 extends from the needle implant part 281 to the interface part 282, and the second electrode 23 is located on the front side of the interface part 282; on the back side of the sensor unit, the third electrode 24 extends from the needle implant part 281 to the interface part 282 and is electrically connected to the second electrode 23.

[0037] In order to reduce the discomfort after the needle implantation part 281 is implanted into the human body, the width L1 of the needle implantation part 281 is 0.2-0.4 mm, and in order to ensure the stability of the connection with the printed circuit board, the width L2 of the interface part 282 is 5.0-8.0 mm. At the same time, in order to allow the sensor unit to contact the human body tissue fluid after being implanted into the skin, the length (height) L3 of the needle implantation part 281 of the sensor unit is 4.5-6 mm, and the length (height) L4 of the interface part 282 can be 2.0-3.0 mm.

[0038] In particular, in this step, the substrate layer 21 can be cut by a mechanical cutting device. Compared with other methods (such as laser cutting, etc.), this method is not only fast, but also will not cause harmful substances to be produced in the substrate layer 21 due to high temperature.

[0039] Step S13: forming a first drug coating 26 on the surface of the first electrode 22 of the needle-implanting portion 281 of each sensor unit, and the first drug coating 26 and the first electrode 22 together constitute the working electrode of the sensor unit, and forming a second drug coating 27 on the surface of the third electrode 24 of the needle-implanting portion 281 of each sensor unit, and the second drug coating 27, the third electrode 24 and the second electrode 23 together constitute the reference electrode of the sensor. Specifically, the first drug coating 26 and the second drug coating 27 can be attached to the outer surfaces of the first electrode 22 and the third electrode 24 respectively by mask printing or the like, and the first drug coating 26 and the second drug coating 27 are only attached to the portions of the first electrode 22 and the third electrode 24 corresponding to the needle-implanting portion 281.

[0040] In one embodiment of the present invention, the first drug coating 26 includes an enzyme-containing sensing material, for example, the first drug coating 26 may include glucose oxidase or dehydrogenase, etc.; and the second drug coating 27 contains a substance that prevents the human body from having an immune response, for example, the second drug coating 27 may include a substance that inhibits the synthesis of purine or pyrimidine, etc.

[0041] In this way, when the needle implantation part 281 is implanted into the human body through a hard needle or other tool, the glucose in the human tissue fluid generates gluconolactone under the action of the first drug coating 26 (such as glucose oxidase or dehydrogenase), and the enzyme changes from an oxidized state to a reduced state. In this process, electrons are transferred, and the electrons are passed through the circuit formed by the enzyme through the first electrode 22 and the third electrode 24 and the second electrode 23. The voltage difference is collected by the collection circuit of the dynamic blood glucose meter, etc., and the magnitude of the voltage difference has a certain linear correspondence with the concentration of glucose, thereby monitoring the glucose concentration in human blood. The second drug coating 27 on the outer surface of the third electrode 24 does not undergo an oxidation-reduction reaction with the human tissue fluid, and it can release substances used to prevent the human body from having an immune response to the human tissue fluid when it contacts the human tissue fluid. In this way, by detecting the voltage difference between the first electrode 22 and the second electrode 23 (i.e., the third electrode 24), the corresponding blood sugar value can be obtained.

[0042] The sensor prepared by the preparation method of the above-mentioned continuous blood glucose meter sensor can greatly reduce the width L1 of the needle implantation part 281 by forming a working electrode and a reference electrode for signal acquisition on the two side surfaces of the flexible substrate layer 21, compared with the arrangement of the working electrode and the reference electrode on the same surface of the substrate layer, thereby reducing the foreign body sensation after implantation and improving the comfort of long-term wearing. At the same time, since the first electrode 22 and the second electrode 23 for the external printed circuit board (PC) are located on the same surface of the substrate layer 21, the connection between the sensor and the printed circuit board is convenient. And since there is no adhesive layer and the second drug coating 27 is added at the same time, the rejection reaction caused by long-term wearing can be prevented.

[0043] In one embodiment of the present invention, the first metal coating is made of gold (Au), and accordingly, the first metal coating is attached to the surface of the substrate layer 21 by an electroplating process, and the thickness of the first metal coating is less than 0.05 mm. Compared with other materials, the first metal coating uses gold electroplated on the surface of the substrate layer 21, which not only has better conductivity and strong adhesion, but also will not fall off and affect the conductivity even if it is bent many times compared with materials such as carbon, and the physical and chemical properties of gold are extremely stable, and it will not be oxidized even if a long-term redox reaction occurs on its surface, which can avoid the generation of oxides soluble in human tissue fluid and causing harm to the human body.

[0044] The second metal coating is made of silver (Ag), and the thickness of the second metal coating is less than 0.05 mm. The second metal coating can be attached to the surface of the substrate layer 21 by electroplating or printing. The second metal coating is made of silver to ensure that it has extremely high conductivity. At the same time, since the second drug coating 27 does not undergo redox reaction, the second metal coating will not be oxidized.

[0045] In one embodiment of the present invention, the first drug coating 26 may include an enzyme-containing sensing material layer (e.g., composed of glucose oxidase or dehydrogenase, etc.) and a diffusion control layer, and the diffusion control layer is located outside the enzyme-containing sensing material layer, that is, the enzyme-containing sensing material layer is located between the diffusion control layer and the first electrode 22. The diffusion control layer can effectively reduce the amount of glucose diffused into the enzyme-containing sensing material layer by a certain proportion, ensuring that the enzyme-containing sensing material layer has sufficient material, and the glucose concentration becomes the main (basically the only) factor limiting the electrode voltage, so that the voltage can correctly reflect the glucose concentration, and can greatly increase the linear range of the implantable sensor, while improving the effective use time of the sensor.

[0046] In one embodiment of the present invention, in addition to steps S11-S13, the following may be included: forming at least one detection electrode 25 on the surface of the substrate layer 21, each detection electrode 25 being composed of a second metal coating layer attached to the back of the substrate layer 21 and in a strip shape, a plurality of third electrodes 24 being arranged side by side on one side of the detection electrode 25, and the plurality of third electrodes 24 being electrically connected to the detection electrode 25. In practical applications, the detection electrode 25 and the third electrode 24 may be formed simultaneously in the same process.

[0047] Accordingly, in step S12, when the substrate layer 21 is cut to form a plurality of sensor units, the substrate layer 21 to which the detection electrode 25 is attached needs to be cut to form a connection portion 211, and a plurality of sensor units (the third electrodes 24 of the plurality of sensor units are respectively electrically connected to the detection electrodes 25 of the connection portion 211) are connected via the connection portion 211. That is, when the substrate layer 21 is cut to form a plurality of sensor units in step S12, the substrate layer 21 is cut by a die-cutting device to form at least one sensor group, and each sensor group includes a connection portion 211 and a plurality of sensor units connected to the connection portion 211.

[0048] Furthermore, after the above step S12 and before the step S13, the method further includes: testing the conductivity of the plurality of sensor units respectively connected to the connection portion 211 through the detection electrode 25. For example, the detection electrode 25 can be connected to the circuit with the plurality of second electrodes 23 in sequence, and a conduction test can be performed. If the voltage difference between the detection electrode 25 and the second electrode 23 is less than a preset value (for example, 0V), it is confirmed that the conductivity test has passed.

[0049] Step S13 is performed only after the conductivity test is passed; and after step S13, it also includes: separating the plurality of sensor units from the connecting portion 211 to form a plurality of sensor monomers.

[0050] Combination Figure 4 As shown, in one embodiment of the present invention, the substrate layer 21 includes a plurality of through holes. In step S11, when N first electrodes, N second electrodes and N third electrodes are formed on the surface of the substrate layer, each first electrode 22 corresponds to a projection area of ​​a second electrode 23 on the substrate layer 21 and a projection area of ​​a third electrode 24 on the substrate layer 21. Each group of through holes 213 is covered by a second electrode 23 and a third electrode 24, respectively, and the second electrode 23 and the third electrode 24 are electrically connected through the second metal filled in the through hole 213. In this way, the process and the structure of the sensor can be simplified.

[0051] Combination Figure 2 As shown, in one embodiment of the present invention, in order to save materials, each third electrode 24 includes a needle-shaped portion 241 corresponding to the needle implanting portion 281 of the sensor unit and a sheet-shaped portion 242 corresponding to the interface portion 282 of the sensor unit. Specifically, the sheet-shaped portion 242 may be rectangular, for example, the needle-shaped portion 241 and the sheet-shaped portion 242 are connected to form a 7 shape, that is, one side edge of the needle-shaped portion 241 is flush with the edge of the corresponding side of the sheet-shaped portion 242.

[0052] Correspondingly, each first electrode 22 also includes a needle-shaped portion 221 corresponding to the needle-implanting portion 281 of the sensor unit and a sheet-shaped portion 222 corresponding to the interface portion 282 of the sensor unit, that is, the first electrode 22 and the third electrode 24 are respectively in a 7-shape, and the second electrode 23 is rectangular. The needle-implanting portion 281 and the interface portion 282 of the sensor unit cut in step S12 are also connected to form a 7-shape.

[0053] Through the above structure, the wound of the needle implanting part 281 when implanted into the human body can be kept small, while the needle implanting part 281 can provide enough surface area for the first drug coating 26 and the second drug coating 27 to adhere, so as to ensure that the first drug coating 26 reacts with the glucose in the human tissue fluid to form a sufficient voltage difference between the working electrode and the reference electrode. In addition, the 7-shaped structure is also conducive to the production and manufacturing of the sensor, for example, the edge position only needs to be cut in sequence. Of course, in actual applications, the needle implanting part 281 and the interface part 282 can also be connected in a T shape, etc.

[0054] In order to ensure the stability and reliability of the conductive connection between the sensor and the printed circuit board, the dimensions of the sheet portion 222 of the first electrode 22 and the second electrode 23 are not less than 1.8×2.0 mm, that is, the surface area of ​​the first electrode 22 and the second electrode 23 on the front side of the interface portion 282 are not less than 1.8×2.0 mm.

[0055] In the above step S12, the third electrodes 24 and the detection electrodes 25 on the surface of the substrate layer 21 are formed simultaneously, and every two detection electrodes 25 are arranged in parallel on the back of the substrate layer 21, and there are two third electrode groups between the two detection electrodes 25, and each third electrode group includes a plurality of third electrodes 24 arranged side by side. In the two third electrode groups, each third electrode group is adjacent to a detection electrode 25, and the sheet portions 242 of all the third electrodes 24 in the same third electrode group are located on a straight line parallel to the detection electrode 25 and are respectively connected to the detection electrode 25. The needle-shaped portions 241 of the third electrodes 24 in the two third electrode groups are located between two rows of sheet portions 242 and are arranged alternately.

[0056] Combination Figure 4-5As shown, the present invention also provides an implantable sensor, which is prepared by the preparation method of the above-mentioned continuous blood glucose meter sensor. Specifically, the implantable sensor includes a substrate layer 21, a first electrode 22, a second electrode 23, a third electrode 24, a first drug coating 26 and a second drug coating 27, and the first electrode 22 is attached to the front of the substrate layer 21 and extends from the needle implant part 281 to the front of the interface part 282, the second electrode 23 is attached to the front of the interface part 282 and is insulated from the first electrode 22, the third electrode 24 is attached to the back of the substrate layer 21 and extends from the back of the needle implant part 281 to the back of the interface part 282, and the third electrode 24 is electrically connected to the second electrode 23. The first drug coating 26 is attached to the outer surface of the first electrode 22 of the needle implant part 281, and the second drug coating 27 is attached to the outer surface of the third electrode 24 of the interface part 282.

[0057] The above is only a preferred specific embodiment of the present invention, but the protection scope of the present invention is not limited thereto. Any changes or substitutions that can be easily thought of by a person skilled in the art within the technical scope disclosed by the present invention should be included in the protection scope of the present invention. Therefore, the protection scope of the present invention should be based on the protection scope of the claims.

Claims

1. A method for preparing a continuous blood glucose meter sensor, characterized in that: The following steps are involved: (a) forming N first electrodes, N second electrodes and N third electrodes on the surface of a substrate layer, wherein N is an integer greater than or equal to 2; the substrate layer is made of a flexible insulating material, the first electrode is made of a first metal coating attached to the front surface of the substrate layer, the second electrode is made of a second metal coating attached to the front surface of the substrate layer, the third electrode is made of a second metal coating attached to the back surface of the substrate layer, and each of the third electrodes is electrically connected to one of the second electrodes; the first metal coating is made of gold and is attached to the surface of the substrate layer by an electroplating process; the second metal coating is made of silver and is attached to the surface of the substrate layer by an electroplating process or a printing process; (b) cutting the substrate layer to form a plurality of sensor units, each of the sensor units comprising a needle implanting portion and an interface portion, and on the front side of the sensor unit, the first electrode extends from the needle implanting portion to the interface portion, and the second electrode is located on the front side of the interface portion, and on the back side of the sensor unit, the third electrode extends from the needle implanting portion to the interface portion and is electrically connected to the second electrode on the front side of the interface portion; (c) forming a first drug coating on the surface of the first electrode of the implanted needle of each sensor unit, and the first drug coating and the first electrode together constitute the working electrode of the sensor unit, and forming a second drug coating on the surface of the third electrode of the implanted needle of each sensor unit, and the second drug coating, the third electrode and the second electrode together constitute the reference electrode of the sensor; The first drug coating includes an enzyme-containing sensing material; The second drug coating contains a substance that prevents the human body from having an immune rejection reaction; The method further comprises: At least one detection electrode is formed on the surface of the substrate layer, each of the detection electrodes is composed of a second metal coating layer attached to the back of the substrate layer and in a strip shape, and a plurality of third electrodes are arranged side by side on one side of the detection electrode, and the plurality of third electrodes are electrically connected to the detection electrodes respectively.

2. The method for preparing a continuous blood glucose meter sensor according to claim 1, characterized in that: When the substrate layer is cut to form a plurality of sensor units, the substrate layer to which the detection electrode is attached is cut to form a connecting portion, and the sensor units in which a plurality of third electrodes are electrically connected to the detection electrode are connected via the connecting portion; the method further comprises: Conducting conductivity detection on a plurality of sensor units respectively connected to the connection part through the detection electrodes; The step (c) is performed after the conductivity test is passed; and after the step (c), the method further includes: separating the plurality of sensor units from the connecting portion to form a plurality of sensor monomers.

3. The method for preparing a continuous blood glucose meter sensor according to claim 1, characterized in that: The substrate layer includes multiple groups of through holes. When N first electrodes, N second electrodes and N third electrodes are formed on the surface of the substrate layer, each of the first electrodes corresponds to a second electrode in a projection area of ​​the substrate layer and a third electrode in a projection area of ​​the substrate layer. Each group of through holes is covered by a second electrode and a third electrode respectively, and the second electrode and the third electrode are electrically connected through a second metal filled in the through holes.

4. The method for preparing a continuous blood glucose meter sensor according to claim 2, characterized in that: When the substrate layer is cut to form a plurality of sensor units, the substrate layer is cut by a die-cutting device to form at least one sensor group, and each sensor group includes a connecting portion and a plurality of sensor units connected to the connecting portion.

5. The method for preparing a continuous blood glucose meter sensor according to claim 2, characterized in that: Each of the third electrodes includes a needle-shaped portion corresponding to the implantation portion of the sensor unit and a sheet-shaped portion corresponding to the interface portion of the sensor unit; The third electrode and the detection electrode on the surface of the substrate layer are formed simultaneously, and every two of the detection electrodes are arranged in parallel on the back side of the substrate layer, and there are two third electrode groups between the two detection electrodes, and each third electrode group includes a plurality of third electrodes arranged side by side; in the two third electrode groups, each third electrode group is adjacent to a detection electrode, and the sheet portions of all third electrodes in the same third electrode group are located on a straight line parallel to the detection electrode and are respectively connected to the detection electrode; the needle portions of the third electrodes in the two third electrode groups are located between two rows of sheet portions and are arranged alternately.

6. The method for preparing a continuous blood glucose meter sensor according to claim 1, characterized in that: The width of the needle implant part is 0.2-0.4mm, and the width of the interface part is 5.0-8.0mm; the first electrode and the third electrode are respectively in the shape of a figure 7, the second electrode is rectangular, and the area of ​​the second electrode is not less than 1.8×2.0mm.

7. An implantable sensor, characterized in that: The implantable sensor is prepared by the preparation method of the continuous blood glucose meter sensor according to any one of claims 1 to 6.

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