Saliva glucose sensor and detection equipment

Abstract

The utility model provides a saliva glucose sensor and detection equipment, and relates to the technical field of saliva glucose detection. After saliva is dropwise added into the enzyme layer area, glucose in the saliva reacts with enzyme, electrons generated by the reaction are detected by the interdigital detection electrode, voltage is applied to the interdigital detection electrode to lead out the electric quantity through the transmission wire, and due to the fact that the electric quantity is in direct proportion to the glucose concentration, the glucose concentration can be detected. The purpose of detecting the saliva glucose concentration can be achieved by detecting the derived electric quantity. The reaction electrode further comprises a sampling trigger electrode located beside the interdigital detection electrode, electric quantity sampling of the interdigital detection electrode is carried out according to a feedback signal of the sampling trigger electrode, the situation that the detection electric quantity value is low due to insufficient sample suction amount is avoided, and the detection precision of the saliva glucose concentration is improved. The saliva glucose sensor is simple in structure, so that the saliva glucose sensor is low in cost and more suitable for batch production.

Description

TECHNICAL FIELD

[0001] The utility model relates to saliva glucose detection technical field, more specifically, relate to a saliva glucose sensor and detection equipment. BACKGROUND

[0002] The treatment of diabetes depends on the regular monitoring of blood glucose levels, especially the use of enzyme-based electrochemical biosensors. The current market products mainly collect the blood samples of patients through finger pricking or venipuncture. This invasive method causes people's pain rejection, especially the elderly and children when regularly monitoring blood glucose. Another continuous blood glucose monitoring product on the market is implanted subcutaneously in the human body in the form of microneedle, which detects the glucose of tissue fluid to respond to human blood glucose, solving the problem of pain, but still accompanied by the risk of infection caused by improper operation, and the product has complex manufacturing process and high cost. In recent years, non-invasive detection methods have been widely concerned. Diabetes can be diagnosed not only by blood glucose, but also by glucose levels in other body fluids, such as tears, sweat, urine and saliva. Research has found that saliva and serum glucose levels have a high correlation. In addition, collecting saliva is also a very simple process without pain, so saliva glucose detection has become one of the main research directions today. SUMMARY

[0003] Therefore, the utility model provides a saliva glucose sensor and detection equipment, which effectively solves the technical problems existing in the prior art, realizes the detection of saliva glucose concentration, and the structure of the saliva glucose sensor is simple, so that the saliva glucose sensor has lower cost and is more suitable for mass production.

[0004] To achieve the above-mentioned purpose, the technical scheme provided by the utility model is as follows:

[0005] A saliva glucose sensor, comprising:

[0006] a substrate;

[0007] a reaction electrode located on the substrate and a transmission lead wire electrically connected with the reaction electrode, the reaction electrode comprising a working electrode, a counter electrode and a sampling trigger electrode, the working electrode and the counter electrode constituting an interdigital detection electrode;

[0008] and an enzyme layer region located on the side of the reaction electrode away from the substrate, the enzyme layer region covering at least the interdigital region of the interdigital detection electrode and the sampling trigger electrode.

[0009] Optionally, the saliva glucose sensor further comprises:

[0010] An insulating layer on a side of the reaction electrode facing away from the substrate, the insulating layer comprising a reaction region, the reaction region exposing at least the interdigital region and the sampling trigger electrode, and the enzyme layer region being located at the reaction region.

[0011] Optionally, the insulating layer comprises an insulating ink layer.

[0012] Optionally, the reaction electrode further comprises a reference electrode, and the enzyme layer region further covers the reference electrode.

[0013] Optionally, the reference electrode comprises a superimposed carbon layer and a silver chloride layer, and the carbon layer is located between the substrate and the silver chloride layer.

[0014] Optionally, the material of the substrate comprises polyethylene terephthalate or polyimide.

[0015] Optionally, the material of at least one of the working electrode, the counter electrode and the sampling trigger electrode comprises carbon, gold or platinum.

[0016] The material of the transmission wire comprises silver.

[0017] Optionally, the length of the interdigital of the interdigital detection electrode is 2-8mm, the width of the interdigital is 0.1-1mm, and the distance between adjacent interdigital is 0.1-1mm.

[0018] The number of interdigital pairs of the interdigital detection electrode is 2-10 pairs.

[0019] Optionally, the saliva glucose sensor further comprises a start trigger wire.

[0020] Based on the same inventive concept, the utility model further provides a detection equipment, the detection equipment includes the saliva glucose sensor.

[0021] Compared with the prior art, the technical scheme provided by the utility model has at least the following advantages:

[0022] The utility model provides a saliva glucose sensor and detection equipment, include: substrate, be located on the reaction electrode and transmission wire of electric connection with reaction electrode, the reaction electrode includes working electrode, counter electrode and sampling trigger electrode, the working electrode and counter electrode constitute interdigital detection electrode, and enzyme layer region is located on the side of the reaction electrode away from the substrate, enzyme layer region at least covers the interdigital region of interdigital detection electrode and sampling trigger electrode.

[0023] From the above, the technical scheme of the saliva glucose sensor provided by the utility model, after the saliva droplet is added in the enzyme layer area, the glucose in the saliva reacts with the enzyme, the electrons generated by the reaction are detected by the interdigital detection electrode, the electrons are led out through the transmission wire by applying voltage to the interdigital detection electrode, since the electron size is proportional to the glucose concentration, the purpose of detecting the saliva glucose concentration can be achieved by detecting the exported electrons.

[0024] Meanwhile, the reaction electrode provided by the utility model further comprises a sampling trigger electrode located at the side of the interdigital detection electrode, when the saliva reaches the sampling trigger electrode, the sampling trigger electrode leads out the feedback signal through the transmission wire, thereby sampling the electrons of the interdigital detection electrode according to the feedback signal, avoiding the situation that the detected electron value is low due to insufficient sampling amount, and improving the detection precision of the saliva glucose concentration.

[0025] In addition, the saliva glucose sensor provided by the utility model has simple structure, low cost and is more suitable for batch production. BRIEF DESCRIPTION OF DRAWINGS

[0026] In order to more clearly illustrate the technical scheme in the embodiments of the utility model or the prior art, the drawings needed to be used in the embodiment or the prior art description will be briefly introduced, and obviously, the drawings in the following description are only the embodiments of the utility model, and for those skilled in the art, other drawings can be obtained according to the provided drawings without creative labor.

[0027] Figure 1 The structure schematic view of the saliva glucose sensor provided by the embodiment of the utility model is shown in the figure;

[0028] Figure 2 The structure schematic view of another saliva glucose sensor provided by the embodiment of the utility model is shown in the figure;

[0029] Figure 3 The structure schematic view of another saliva glucose sensor provided by the embodiment of the utility model is shown in the figure;

[0030] Figure 4 The structure schematic view of another saliva glucose sensor provided by the embodiment of the utility model is shown in the figure;

[0031] Figure 5 The detection result curve provided by the embodiment of the utility model is shown in the figure. DETAILED DESCRIPTION

[0032] Clearly and completely describe the technical scheme in the embodiments of the utility model with reference to the drawings in the embodiments of the utility model, obviously, the described embodiments are only some embodiments of the utility model, not all the embodiments. Based on the embodiments in the utility model, all other embodiments obtained by the ordinary skilled in the art without creative labor belong to the scope of protection of the utility model.

[0033] As described in the background, the current market products mainly collect the blood samples of patients through finger pricking or venipuncture, which causes people's pain rejection, especially the old and the children when monitoring blood sugar regularly. Another continuous blood glucose monitoring product on the market is implanted subcutaneously in the human body in the form of microneedle, which solves the problem of pain by detecting the glucose response of the human blood sugar in the interstitial fluid, but still has the risk of infection caused by improper operation, and the product has complex manufacturing process and high cost. In recent years, non-invasive detection methods have been widely concerned. Diabetes can be diagnosed not only by blood glucose, but also by glucose levels in other body fluids, such as tears, sweat, urine and saliva. It is found through research that the saliva and serum glucose levels have high correlation. In addition, collecting saliva is also a very simple process without pain, so saliva glucose detection has become one of the main research directions today.

[0034] Specifically, the saliva glucose content is about 1 / 100-1 / 50 of the blood glucose content, which is difficult to measure accurately. At present, the commonly used detection methods include colorimetric method, high-performance ion exchange chromatography method, electrochemical sensor method, etc. Among them, the colorimetric method is to put the test stick into the mouth, take it out after a few minutes, and compare the color with the colorimetric plate to obtain the glucose concentration range. Although the operation is convenient, the detection precision is poor. The high-performance ion exchange chromatography method has high detection precision, but the operation is complex, time-consuming, and expensive instruments are required, which is difficult to popularize. The electrochemical sensor method has the advantages of high detection precision, low cost, convenient operation, and portable instrument, and has very broad application prospect, but the development of this method is still in the initial stage, and there is no product on the market.

[0035] Based on this, the utility model embodiment provides a kind of saliva glucose sensor and detection equipment, effectively solve the technical problems existing in prior art, realize the detection purpose of saliva glucose concentration, and the structure of saliva glucose sensor is simple, so that the cost of saliva glucose sensor is lower and more suitable for mass production.

[0036] To achieve the above object, the technical scheme provided by the utility model embodiment is as follows, specifically combined Figures 1 to 5 The technical scheme provided by the utility model embodiment is described in more detail.

[0037] ReferenceFigure 1 As shown in the structural schematic diagram of the saliva glucose sensor, the saliva glucose sensor comprises:

[0038] a substrate 100.

[0039] a reaction electrode and a transmission wire 200 electrically connected with the reaction electrode, the reaction electrode comprises a working electrode 311, a counter electrode 312 and a sampling trigger electrode 320, and the working electrode 311 and the counter electrode 312 constitute an interdigital detection electrode 310.

[0040] and an enzyme layer area 400 located on the side, away from the substrate 100, of the reaction electrode, the enzyme layer area 400 covers at least the interdigital area of the interdigital detection electrode 310 and the sampling trigger electrode 320.

[0041] It can be understood that, after the saliva droplet is added to the enzyme layer area, the glucose in the saliva reacts with the enzyme, the electrons generated by the reaction are detected by the interdigital detection electrode, and the electric quantity is led out through the transmission wire by applying voltage to the interdigital detection electrode, since the electric quantity is proportional to the glucose concentration, the purpose of detecting the saliva glucose concentration can be achieved by detecting the led-out electric quantity.

[0042] Meanwhile, the reaction electrode provided by the embodiment of the present application further comprises a sampling trigger electrode located beside the interdigital detection electrode, the sampling trigger electrode is equivalent to an electrode for starting detection, the sampling trigger electrode is located beside the interdigital detection electrode, and the saliva is mainly added to the interdigital area when the saliva is added to the enzyme layer area, therefore, a sufficient amount of saliva needs to be added to the enzyme layer area to be collected by the sampling trigger electrode. When the saliva reaches the sampling trigger electrode, the sampling trigger electrode leads out a feedback signal through the transmission wire, and thus the electric quantity sampling of the interdigital detection electrode is carried out according to the feedback signal, the situation that the detection electric quantity value is low due to insufficient sampling amount is avoided, and the detection precision of the saliva glucose concentration is improved.

[0043] In addition, the saliva glucose sensor provided by the embodiment of the present application has simple structure, low cost and is more suitable for batch production. In addition, the operation mode in the detection process is simple, and the saliva glucose sensor is more suitable for popularization of glucose detection.

[0044] The technical scheme provided by the embodiment of the present application will be further described in combination with the following Figure 1As shown, the reaction electrode and the transmission wire 200 provided by the embodiment of the present application are sequentially arranged in the first direction Y, one end side of the transmission wire 200 is electrically connected with the reaction electrode, and the other end side is used as an external pin of the sensor. Wherein, the interdigital detection electrode 310 composed of the working electrode 311 and the counter electrode 312 can be arranged on the side of the reaction electrode away from the transmission wire 200, and the sampling trigger electrode 320 is located between the interdigital detection electrode 310 and the transmission wire 200. The transmission wire 200 includes the working wire 211, the counter wire 212 and the trigger wire 213, the working wire 211 is electrically connected with the working electrode 311, the counter wire 212 is electrically connected with the counter electrode 312, and the trigger wire 213 is electrically connected with the sampling trigger electrode 320.

[0045] In the embodiment of the present application, the material of the transmission wire provided by the embodiment of the present application can be silver, which not only has low price, but also can reduce the resistance of the transmission wire and improve the conductivity of the transmission wire. The transmission wire can be made on the substrate in the form of silk screen printing, such as selecting the required silver paste, and making the silver paste on the substrate in the form of silk screen printing.

[0046] In order to avoid the problem of short circuit of the detection circuit, the embodiment of the present application can also make an insulation structure to cover the reaction electrode. Referring to Figure 2 As shown, another structure diagram of the saliva glucose sensor provided by the embodiment of the present application, wherein the saliva glucose sensor provided by the embodiment of the present application further comprises:

[0047] The insulation layer 500 located on the side of the reaction electrode away from the substrate 100, the insulation layer 500 includes a reaction area, the reaction area at least exposes the interdigital area and the sampling trigger electrode 320, and the enzyme layer area 400 is located at the reaction area.

[0048] It can be understood that the insulation layer is made on the reaction electrode in the embodiment of the present application, the insulation layer can cover the reaction electrode (wherein the reaction area at least exposes the interdigital area and the sampling trigger electrode) and further extend to cover at least part of the transmission wire, thereby preventing the problem of short circuit of the circuit of the reaction electrode. The material of the insulation layer provided by the embodiment of the present application can be insulating ink, that is, the insulation layer includes an insulating ink layer, which can be prepared above the reaction electrode in the form of silk screen printing, and the insulation layer includes a hollow reaction area, the reaction area at least exposes the interdigital area and the sampling trigger electrode at the reaction electrode, and then the enzyme layer area is arranged at the reaction area, which is convenient for the enzyme operation of the enzyme layer area.

[0049] Further referring to Figure 3As shown in the structure schematic diagram of the saliva glucose sensor, the reaction electrode further comprises a reference electrode 330, and the enzyme layer area 400 further covers the reference electrode 330. The reference electrode 330 can be located in the area between the interdigital detection electrode 310 and the transmission wire 200, and the reference electrode 330 can be arranged opposite to the sampling trigger electrode 320, and the utility model does not make specific limitation on this. In order to export the electric quantity of the reference electrode 330, the transmission wire 300 further comprises a reference wire 214, and the reference wire 214 is electrically connected with the reference electrode 330.

[0050] It can be understood that, by arranging the reference electrode, a reference electric quantity is provided through the reference electrode, and then the electric quantity of the detected interdigital detection electrode can be compared with the reference electric quantity of the detected reference electrode, so that the detection precision is improved. In an embodiment of the utility model, the reference electrode can comprise a superimposed carbon layer and silver chloride layer, and the carbon layer is located between the substrate and the silver chloride layer, wherein the silver chloride layer completely covers the carbon layer, and the silver chloride layer can be prepared by printing silver chloride ink on the carbon layer by using a silk screen printing process.

[0051] Reference Figure 4 As shown in the structure schematic diagram of the saliva glucose sensor, the saliva glucose sensor further comprises a start trigger wire 600, wherein the start trigger wire 600 can be located beside the transmission wire 200. When the saliva glucose sensor is connected with the detection instrument, the start trigger wire 600 can be used as a switch to connect the power supply loop of the detection instrument, and trigger the detection instrument to start.

[0052] The saliva glucose sensor provided by the utility model will be described in more detail in combination with the manufacturing method of the saliva glucose sensor. The manufacturing method of the saliva glucose sensor can comprise the following steps:

[0053] S1, selecting a substrate.

[0054] In an embodiment of the utility model, the material of the substrate can include polyethylene terephthalate (PET) or polyimide (PI). The PET substrate has the advantages of smooth surface, good electrical insulation, good mechanical properties, high temperature resistance (can be used at a temperature range of 120 DEG C for a long time), and easy ink curing, and can be used as a substrate for screen printing. The PI substrate has excellent temperature resistance, chemical stability and mechanical properties, and is commonly used as a substrate material for magnetron sputtering. Therefore, the substrate can be selected according to the subsequent component preparation and requirements, and the utility model does not make specific limitations on this.

[0055] S2, preparing a transmission conductor and a start-up trigger conductor on the substrate.

[0056] In an embodiment of the utility model, the material of the transmission conductor and the start-up trigger conductor can include silver. Specifically, the transmission conductor and the start-up printed conductor can be prepared on the substrate by using the screen printing process and selecting appropriate silver paste for printing on the substrate. Silver has a low price and can effectively reduce the resistance of the transmission conductor and the start-up trigger conductor, thereby improving the conductivity of the transmission conductor and the start-up trigger conductor and the performance of the saliva glucose sensor.

[0057] S3, preparing a reaction electrode on the substrate.

[0058] The reaction electrode provided in the embodiment of the utility model can include an interdigital detection electrode composed of a working electrode and a counter electrode, a reference electrode and a sampling trigger electrode. The interdigital detection electrode composed of the working electrode and the counter electrode can improve the detection signal of trace glucose in saliva. The greater the length-width ratio and the density of the interdigital detection electrode, the smaller the initial resistance, and the higher the sensitivity and response speed of the saliva glucose sensor. Optionally, the length of the interdigital detection electrode can be 2-8 mm, the width of the interdigital detection electrode can be 0.1-1 mm, and the distance between adjacent interdigital detection electrodes can be 0.1-1 mm. The number of interdigital detection electrodes can be 2-10 pairs.

[0059] The sampling trigger electrode provided by the embodiment of the utility model judges whether the sample volume is enough, and when the saliva is added to the enzyme layer area, the forked area is aligned, and when the added saliva reaches the sampling trigger electrode, the detection of glucose is carried out, so that the situation that the detection value is low due to insufficient sample volume is avoided. The material of at least one of the working electrode, the counter electrode and the sampling trigger electrode comprises carbon, gold or platinum. The working electrode, the counter electrode and the sampling trigger electrode can be made by silk screen printing, magnetron sputtering or inkjet printing process, and when the electrode is made by silk screen printing, conductive carbon paste, gold paste or platinum paste and the like inks are selected, so that the electrode has the advantages of stable performance and no reaction with the enzyme solution system; or when the electrode is made by the method of magnetron sputtering, gold and platinum and the like materials are preferably selected, so that the electrode has excellent conductivity and electrocatalytic performance.

[0060] The reference electrode provided by the embodiment of the utility model can be used to provide a reference electric quantity for the electric quantity of the obtained forked detection electrode, and improve the accuracy of detection. The reference electrode can comprise a superimposed carbon layer and a silver chloride layer, and the carbon layer is located between the substrate and the silver chloride layer, wherein the silver chloride layer completely covers the carbon layer, and the silver chloride layer can be prepared by printing silver chloride ink on the carbon layer by using a silk screen printing process.

[0061] S4, forming an insulating layer on the reaction electrode, wherein the enzyme layer area can be located at a hollowed-out reaction area of the insulating layer.

[0062] The insulating layer provided by the embodiment of the utility model plays a role in preventing short circuit of the circuit, wherein the insulating layer comprises a hollowed-out reaction area, the reaction area at least exposes the forked area of the forked detection electrode, the sampling trigger electrode and the reference electrode, and at least part of at least one of the other areas of the reaction electrode, the transmission wire and the start trigger wire can be covered by the insulating layer. The utility model does not make specific limitation on the covered area of the insulating layer, and specific design needs to be made according to actual application.

[0063] In the concentration detection of glucose in saliva, the enzyme needs to be spotted at the enzyme layer area. The enzyme layer provided by the embodiment of the present application can include biological enzymes, and the biological enzymes have an electronic medium, a buffer, a surfactant and a stabilizer. The biological enzymes can include glucose oxidase or dehydrogenase. The electronic medium can include potassium ferricyanide, ferrocene, hexaammine ruthenium chloride, osmium compounds and the like, which are used to quickly transfer the electrons generated by the enzyme reaction center to the surface of the reaction electrode. The buffer can include phosphate, tris(hydroxymethyl) aminomethane hydrochloride, N-carbamoylmethyl ethanesulfonic acid, N-(2-hydroxyethyl) piperazine-N-(2-ethanesulfonic acid) and the like, which are used to keep the pH value of the solution relatively stable. The surfactant can include triton, polyvinylpyrrolidone and the like, which makes other substances uniformly dispersed in the solution, so as to enhance the fluidity of the solution and facilitate the uniform diffusion of the enzyme solution on the electrode. The stabilizer can include sucrose, sodium citrate, trehalose and the like, which are used to protect the enzyme molecular structure from being destroyed and enhance the stability of the enzyme. The above biological enzymes, electronic medium, buffer, surfactant and stabilizer are mixed into a solution to obtain an enzyme solution, and the enzyme solution can be made in the enzyme layer area by using a spot enzyme machine, a spraying machine or the like. The amount of the enzyme spotted in the enzyme layer area provided by the embodiment of the present application can be 0.5-10 microliters.

[0064] Based on the same inventive concept, the embodiment of the present application further provides a detection device, which comprises the saliva glucose sensor provided by any one of the above embodiments. In addition, the detection device further comprises a detection instrument, and the saliva glucose sensor is connected to the detection instrument to detect the concentration of saliva glucose.

[0065] Reference Figure 5 As shown in the figure, the detection result curve provided by the embodiment of the present application is a curve diagram, wherein the concentrations of the successively detected glucose are 0.02, 0.05, 0.1, 0.2, 0.3, 0.4 and 0.5 mM, 0.1V voltage is applied to the interdigital detection electrode for 60s, and the detection curve is recorded to obtain the cumulative electric quantity. It can be seen that the detection limit of the saliva glucose sensor provided by the embodiment of the present application is as low as 20uM, the sensitivity is 8E-06 C / mM, the linearity is 0.99, and the resolution is good in the range of 0.02-0.5 mM, which can meet the detection requirements of low-concentration saliva glucose.

[0066] The embodiment of the present application provides a saliva glucose sensor and a detection device, which comprises: a substrate; a reaction electrode and a transmission lead wire electrically connected to the reaction electrode, the reaction electrode comprising a working electrode, a counter electrode and a sampling trigger electrode, the working electrode and the counter electrode forming an interdigital detection electrode; and an enzyme layer area located on the side of the reaction electrode away from the substrate, the enzyme layer area covering at least the interdigital area of the interdigital detection electrode and the sampling trigger electrode.

[0067] From the above, the technical scheme provided by the embodiment of the utility model, after the saliva drop is added in the enzyme layer area, the glucose in the saliva reacts with the enzyme, the electron produced by the reaction is detected by the interdigital detection electrode, the electric quantity is led out through the transmission wire by applying voltage to the interdigital detection electrode, because the electric quantity is proportional to the glucose concentration, the purpose of detecting the glucose concentration of the saliva can be achieved by detecting the exported electric quantity.

[0068] Meanwhile, the reaction electrode provided by the embodiment of the utility model further includes a sampling trigger electrode located beside the interdigital detection electrode, when the saliva reaches the sampling trigger electrode, the sampling trigger electrode leads out the feedback signal through the transmission wire, thereby sampling the electric quantity of the interdigital detection electrode according to the feedback signal, avoiding the situation that the detected electric quantity value is low due to insufficient sampling amount, and improving the detection precision of the glucose concentration of the saliva.

[0069] In addition, the structure of the saliva glucose sensor provided by the embodiment of the utility model is simple, so that the cost of the saliva glucose sensor is low and more suitable for batch production. And the operation mode in the detection process is simple, more suitable for the popularization of glucose detection.

[0070] In the description of the utility model, it should be understood that, if the terms "center", "longitudinal", "transverse", "length", "width", "thickness", "upper", "lower", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential" and the like indicate the orientation or positional relationship shown in the drawings, which is only for the convenience of describing the utility model and simplifying the description, and does not indicate or imply that the device or element referred to must have a particular orientation, be constructed and operated in a particular orientation, therefore it cannot be understood as a limitation of the utility model.

[0071] In addition, if the terms "first", "second" are used for description purposes only, and cannot be understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features. Therefore, the features limited by "first", "second" can explicitly or implicitly include at least one of the features. In the description of the utility model, the meaning of "multiple" is at least two, such as two, three, etc., unless otherwise specifically limited.

[0072] In the present application, unless otherwise explicitly specified and limited, the terms such as "mounting", "connecting", "connecting", "fixing" and the like should be understood in a broad sense, for example, it can be fixedly connected, or it can be detachably connected, or it can be integrated; it can be mechanically connected, or it can be electrically connected or can communicate with each other; it can be directly connected, or it can be indirectly connected through an intermediate medium, or it can be the internal communication of two elements or the interaction relationship between two elements, unless otherwise explicitly limited. For ordinary skilled in the art, the specific meaning of the above terms in the present application can be understood according to the specific circumstances.

[0073] In the present application, unless otherwise explicitly specified and limited, the first feature is "on" or "under" the second feature. The first and second features can be directly contacted, or the first and second features can be indirectly contacted through an intermediate medium. Moreover, the first feature "above", "above" and "above" the second feature can be directly above or obliquely above the first feature, or only indicate that the horizontal height of the first feature is higher than that of the second feature. The first feature "below", "below" and "below" the second feature can be directly below or obliquely below the first feature, or only indicate that the horizontal height of the first feature is less than that of the second feature.

[0074] In the present application, if the terms "one embodiment", "some embodiments", "example", "specific example" or "some examples" appear, it means that the specific features, structures, materials or characteristics described in conjunction with the embodiment or example are included in at least one embodiment or example of the present application. In the present application, the illustrative description of the above terms does not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials or characteristics described can be combined in any one or more embodiments or examples in a suitable manner. In addition, the skilled in the art can combine and combine the different embodiments or examples described in the present application and the features of the different embodiments or examples without contradiction.

[0075] Although the embodiments of the present application have been shown and described above, it can be understood that the above embodiments are exemplary and cannot be understood as limiting the present application, and the skilled in the art can change, modify, replace and modify the above embodiments within the scope of the present application.

Claims

1. A salivary glucose sensor, characterized by, The saliva glucose sensor comprises: a substrate; a reaction electrode and a transmission lead wire electrically connected to the reaction electrode, the reaction electrode comprising a working electrode, a counter electrode and a sampling trigger electrode, the working electrode and the counter electrode forming an interdigital detection electrode, and the sampling trigger electrode being located beside the interdigital detection electrode; and an enzyme layer region located on a side of the reaction electrode away from the substrate, the enzyme layer region covering at least the interdigital region of the interdigital detection electrode and the sampling trigger electrode.

2. The salivary glucose sensor according to claim 1, characterized in that, The saliva glucose sensor further comprises: an insulating layer located on a side of the reaction electrode away from the substrate, the insulating layer comprising a reaction region, the reaction region exposing at least the interdigital region and the sampling trigger electrode, and the enzyme layer region being located at the reaction region.

3. The salivary glucose sensor of claim 2, wherein, The insulating layer comprises an insulating ink layer.

4. The salivary glucose sensor of claim 1, wherein, The reaction electrode further comprises a reference electrode, and the enzyme layer region further covers the reference electrode.

5. The salivary glucose sensor of claim 4, wherein, The reference electrode comprises a superimposed carbon layer and a silver chloride layer, and the carbon layer is located between the substrate and the silver chloride layer.

6. The salivary glucose sensor of claim 1, wherein, The material of the substrate comprises polyethylene terephthalate or polyimide.

7. The salivary glucose sensor of claim 1, wherein, The material of at least one of the working electrode, the counter electrode and the sampling trigger electrode comprises carbon, gold or platinum; The material of the transmission lead wire comprises silver.

8. The salivary glucose sensor of claim 1, wherein, The length of the interdigital of the interdigital detection electrode is 2-8 mm, the width of the interdigital is 0.1-1 mm, and the distance between adjacent interdigital is 0.1-1 mm; The number of interdigital pairs of the interdigital detection electrode is 2-10 pairs.

9. The salivary glucose sensor of claim 1, wherein, The saliva glucose sensor further comprises a start trigger lead wire.

10. A detection device, characterized by The detection device comprises the saliva glucose sensor according to any one of claims 1-9. The saliva glucose sensor comprises: a substrate; a reaction electrode and a transmission lead wire electrically connected to the reaction electrode, the reaction electrode comprising a working electrode, a counter electrode and a sampling trigger electrode, the working electrode and the counter electrode forming an interdigital detection electrode, and the sampling trigger electrode being located beside the interdigital detection electrode; and an enzyme layer region located on a side of the reaction electrode away from the substrate, the enzyme layer region covering at least the interdigital region of the interdigital detection electrode and the sampling trigger electrode. The saliva glucose sensor further comprises: an insulating layer located on a side of the reaction electrode away from the substrate, the insulating layer comprising a reaction region, the reaction region exposing at least the interdigital region and the sampling trigger electrode, and the enzyme layer region being located at the reaction region. The insulating layer comprises an insulating ink layer. The reaction electrode further comprises a reference electrode, and the enzyme layer region further covers the reference electrode. The reference electrode comprises a superimposed carbon layer and a silver chloride layer, and the carbon layer is located between the substrate and the silver chloride layer. The material of the substrate comprises polyethylene terephthalate or polyimide. The material of at least one of the working electrode, the counter electrode and the sampling trigger electrode comprises carbon, gold or platinum; The material of the transmission lead wire comprises silver. The length of the interdigital of the interdigital detection electrode is 2-8 mm, the width of the interdigital is 0.1-1 mm, and the distance between adjacent interdigital is 0.1-1 mm; The number of interdigital pairs of the interdigital detection electrode is 2-10 pairs. The saliva glucose sensor further comprises a start trigger lead wire. The detection device comprises the saliva glucose sensor according to any one of claims 1-9.

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