CN219662489U - Closed-loop control system - Google Patents

Abstract

The embodiment of the utility model provides a closed-loop control system, which belongs to the technical field of biochemical medicines and comprises the following components: an electroosmotic pump, a sensor and a signal conversion module; wherein the electroosmotic pump comprises a first electrode layer, a second electrode layer and an intermediate membrane layer; the sensor comprises a substrate, a microneedle array arranged on one side of the substrate, and an electrode covered on the microneedle array and the substrate; the substrate is connected with the second electrode layer, and the tip of the microneedle array faces to one side away from the second electrode layer; the signal conversion module comprises a first conversion module, a control module and a second conversion module; the first conversion module is used for receiving and converting the electric signals output by the sensor; the second conversion module is used for receiving and converting the command output by the control module and transmitting the converted command signal to the electroosmosis pump so as to control the opening or closing of the electroosmosis pump. The closed-loop control system provided by the embodiment of the utility model can control the switch of the electroosmosis pump according to the blood sugar concentration of a patient.

Description

Closed-loop control system

Technical Field

The embodiment of the utility model relates to the technical field of biochemical medicines, in particular to a closed-loop control system.

Background

Diabetes is a metabolic abnormality-based disease caused by insufficient secretion of insulin, a hormone, by the pancreas. Diabetes patients can inject insulin into the body as one of the positive therapeutic methods. Insulin can be appropriately injected into the body according to a change in blood glucose of a patient by using an insulin injection device.

Disclosure of Invention

The embodiment of the utility model provides a closed-loop control system, which aims to measure the blood glucose concentration of a patient by using a biosensor and control the switch of an electroosmosis pump according to the signal of the biosensor.

The embodiment of the utility model provides a closed-loop control system, which comprises:

an electroosmotic pump, a sensor and a signal conversion module;

the electroosmosis pump comprises a first electrode layer, a second electrode layer and an intermediate membrane layer, wherein the intermediate membrane layer is positioned between the first electrode layer and the second electrode layer, and a plurality of through holes are formed in the intermediate membrane layer;

the sensor comprises a substrate, a microneedle array arranged on one side of the substrate, and a plurality of electrodes covered on the microneedle array and the substrate;

the substrate is connected with the second electrode layer, and the tips of the microneedle array face to one side away from the second electrode layer;

the signal conversion module comprises a first conversion module, a control module and a second conversion module;

the input end of the first conversion module is connected with the output end of the sensor, the output end of the first conversion module is connected with the input end of the control module, and the first conversion module is used for receiving and converting the electric signal output by the sensor;

the control module is used for receiving the electric signal converted by the first conversion module and sending a command to the second conversion module according to the electric signal;

the input end of the second conversion module is connected with the output end of the control module, the output end of the second conversion module is connected with the input end of the electroosmosis pump, and the second conversion module is used for receiving and converting the command output by the control module and transmitting the converted command signal to the electroosmosis pump so as to control the electroosmosis pump to be started or stopped.

Optionally, the first conversion module is a first signal converter;

the control module is a microcontroller;

the second conversion module is a second signal converter.

Optionally, the microneedle array comprises a plurality of microneedle bodies having a length of greater than or equal to 100 μm and less than or equal to 1000 μm.

Optionally, the microneedle array is a hollow microneedle array.

Optionally, the plurality of electrodes comprises an electrochemical sensor electrode comprising a working electrode and a counter electrode, or comprises a working electrode, a reference electrode and a counter electrode, and a reverse iontophoresis electrode comprising a positive electrode and a negative electrode; and the working electrode of the electrochemical sensor electrode and the negative electrode of the reverse iontophoresis electrode form an interdigital electrode;

glucose oxidase is fixed on the working electrode of the electrochemical sensor electrode;

the counter electrode of the electrochemical sensor electrode and the positive electrode of the reverse iontophoresis electrode are positioned at one side or two sides of the interdigital electrode;

the electrochemical sensor is used for detecting glucose in tissue fluid and generating an electric signal, and the reverse iontophoresis electrode is used for generating reverse iontophoresis action so as to attract the glucose in the deep layer of the skin to the upper part of the dermis layer where the needle points of the micro needle body are positioned.

Optionally, the material of the working electrode comprises gold, platinum, carbon, or a gold composite, a platinum composite, or a carbon composite;

the reference electrode material comprises silver/silver chloride;

the material of the counter electrode comprises gold, platinum, carbon or gold composite material, platinum composite material, carbon composite material or silver/silver chloride;

the material of the reverse iontophoresis electrode comprises silver/silver chloride, a silica gel material, a conductive polymer, graphene or gold.

Optionally, the materials of the first electrode layer, the second electrode layer, and the intermediate film layer include: a rigid film or a flexible film.

The beneficial effects are that:

the utility model provides a closed-loop control system, which is characterized in that an electroosmosis pump, a sensor and a signal conversion module are arranged, the sensor is connected with a first conversion module of the signal conversion module, the electroosmosis pump is connected with a second conversion module of the signal conversion module, and then the first conversion module is connected with the second conversion module through a control module; the sensor can be used for detecting the glucose concentration of subcutaneous tissue fluid of a patient, and the glucose concentration of tissue fluid has strong correlation with the blood glucose concentration, so that the signal output by the sensor can reflect the magnitude of the blood glucose concentration; meanwhile, the sensor can output signals to the first conversion module, the first conversion module converts the received signals and then sends the signals to the control module, the control module generates commands according to the signals and sends the commands to the second conversion module, and the second conversion module converts the received commands into corresponding command signals so as to control the on or off of the electroosmosis pump, so that the on-off control of the electroosmosis pump according to the real-time blood glucose concentration of a patient is realized.

Drawings

In order to more clearly illustrate the technical solutions of the embodiments of the present utility model, the drawings that are needed in the description of the embodiments of the present utility model will be briefly described below, it being obvious that the drawings in the following description are only some embodiments of the present utility model, and that other drawings may be obtained according to these drawings without inventive effort for a person skilled in the art.

FIG. 1 is a schematic diagram of a closed loop control system according to an embodiment of the present utility model;

fig. 2 is a schematic structural diagram of an electroosmotic pump in a closed-loop control system according to an embodiment of the present utility model;

FIG. 3 is a schematic diagram of a curved electroosmotic pump in a closed-loop control system according to one embodiment of the present utility model;

FIG. 4 is a schematic diagram of a sensor in a closed loop control system according to an embodiment of the present utility model;

FIG. 5 is a schematic cross-sectional view of a sensor in a closed-loop control system according to an embodiment of the present utility model;

FIG. 6 is a schematic diagram of a sensor including a working electrode, a counter electrode and a reference electrode in a closed-loop control system according to an embodiment of the present utility model;

fig. 7 is a schematic structural diagram of a signal conversion module in a closed-loop control system according to an embodiment of the utility model.

Reference numerals illustrate: 1. an electroosmotic pump; 11. a first electrode layer; 12. a second electrode layer; 13. an intermediate film layer; 2. a sensor; 21. a substrate; 22. a microneedle array; 221. a microneedle body; 23. an electrode; 231. an electrochemical sensor electrode; 2311. a working electrode; 2312. a counter electrode; 2313. a reference electrode; 232. a reverse iontophoresis electrode; 2321. a positive electrode; 2322. a negative electrode; 3. a signal conversion module; 31. a first conversion module; 32. a control module; 33. and a second conversion module.

Detailed Description

The following description of the embodiments of the present utility model will be made clearly and fully with reference to the accompanying drawings, in which it is evident that the embodiments described are some, but not all embodiments of the utility model. All other embodiments, which can be made by those skilled in the art based on the embodiments of the utility model without making any inventive effort, are intended to be within the scope of the utility model.

In the related art, an electroosmotic pump is an emerging device for injecting insulin, and when the electroosmotic pump is used as an insulin pump for quantitatively injecting insulin into a patient, the electroosmotic pump needs to be controlled to be switched on or off according to the blood glucose concentration in the patient. However, there is currently no more sophisticated solution for controlling electroosmotic pumps.

In view of the above, an embodiment of the present utility model provides a closed-loop control system, in which an electroosmosis pump, a sensor and a signal conversion module are disposed, the sensor is connected with a first conversion module of the signal conversion module, the electroosmosis pump is connected with a second conversion module of the signal conversion module, and then the first conversion module is connected with the second conversion module through the control module; the sensor can be used for detecting the glucose concentration of subcutaneous tissue fluid of a patient, and the glucose concentration of tissue fluid has strong correlation with the blood glucose concentration, so that the signal output by the sensor can reflect the magnitude of the blood glucose concentration; meanwhile, the sensor can output signals to the first conversion module, the first conversion module converts the received signals and then sends the signals to the control module, the control module generates commands according to the signals and sends the commands to the second conversion module, and the second conversion module converts the received commands into corresponding command signals so as to control the on or off of the electroosmosis pump, so that the on-off control of the electroosmosis pump according to the real-time blood glucose concentration of a patient is realized.

Referring to fig. 1, a closed-loop control system is disclosed in an embodiment of the present utility model, and includes an electroosmotic pump 1, a sensor 2, and a signal conversion module 3.

Specifically, referring to fig. 2, the electroosmotic pump 1 includes a first electrode layer 11, a second electrode layer 12, and an intermediate film layer 13. Wherein the intermediate film layer 13 is located between the first electrode layer 11 and the second electrode layer 12.

The intermediate film layer 13 has a plurality of through holes (not shown), and the intermediate film layer 13 may be a flexible film material, such as a polycarbonate film having through holes, a polyester film having through holes, a polytetrafluoroethylene film having through holes, or a polyimide film having through holes, which is not particularly limited herein. Meanwhile, the middle film layer 13 can also be made of a hard film material.

The materials of the first electrode layer 11 and the second electrode layer 12 may be hard film materials, such as 304 stainless steel mesh and 316 stainless steel mesh, metal mesh, such as aluminum mesh, titanium mesh and platinum mesh, metal coating, such as gold metal coating and platinum metal coating, and gold-plated stainless steel mesh. Meanwhile, the first electrode layer 11 and the second electrode layer 12 may be made of flexible film materials.

Referring to fig. 3, when the first electrode layer 11, the second electrode layer 12 and the intermediate film layer 13 are made of flexible film materials, the electroosmotic pump can be integrally bent, which is more beneficial to the electroosmotic pump being applied to various environments.

After the electroosmotic pump 1 is started, that is, after the first electrode layer 11 and the second electrode layer 12 are electrified, an electric field is applied to the intermediate film layer 13 by the first electrode layer 11 and the second electrode layer 12, so that an electric double layer is formed on the intermediate film layer 13 through the inner wall of the hole, and then under the action of the electric field, charges in the electric double layer can be driven towards the electrode direction with opposite charges, and surrounding liquid is dragged to flow, so that continuous transfusion is provided.

Referring to fig. 4, the sensor 2 includes a substrate 21, a microneedle array 22 provided on one side of the substrate 21, and a plurality of electrodes 23 covering the microneedle array 22 and the substrate 21.

Specifically, referring to fig. 5, the substrate 21 and the microneedle array 22 are integrally formed, that is, the substrate 21 and the microneedle array 22 are manufactured together by the same method or by the same step. The microneedle array 22 includes a plurality of microneedles 221, the microneedles 221 are cones or pyramids having a certain length, and the interior of the microneedles 221 is hollow with both ends penetrating so that insulin solution can be injected into a patient through the microneedles 221.

The length of the microneedle 221 is greater than or equal to 100 μm and less than or equal to 1000 μm; illustratively, the microneedle 221 may have a length of 200 μm, 300 μm, 400 μm, 500 μm, 600 μm, 700 μm, 800 μm, 900 μm, 1000 μm, and so forth. In using the diabetes sensor, the microneedle array 22 needs to be pierced into the patient, so that the shorter length of the microneedle body 221 can reduce the pain feeling to the patient.

In the embodiment of the present utility model, the materials of the substrate 21 and the microneedle array 22 may be selected from polymer materials, biodegradable materials or biocompatible materials. Illustratively, when the materials of the substrate 21 and the microneedle array 22 are polymer materials, the materials of the substrate 21 and the microneedle array 22 may be Si; when the materials of the substrate 21 and the microneedle array 22 are biodegradable materials, the materials of the substrate 21 and the microneedle array 22 may be chitosan or polylactic acid; when the materials of the substrate 21 and the microneedle array 22 are biocompatible materials, the materials of the substrate 21 and the microneedle array 22 may be thermoplastic polyurethane, etc. Since the microneedle array 22 may be broken after penetrating into the patient, the use of the above materials can prevent damage to the human body caused by the broken microneedle 221 remaining in the patient.

Further, referring to fig. 1, the substrate 21 is connected to the second electrode layer 12, and the tips of the microneedle array 22 face toward the side facing away from the second electrode layer 12.

Specifically, when the closed-loop control system is used, insulin solution is located at the position of the first electrode layer 11, after the electroosmotic pump 1 is electrified, insulin flows to the second electrode layer 12 under the driving action of the intermediate film layer 13 and flows to the substrate 21 of the sensor 2 through the second electrode layer 12, and finally the insulin solution is injected into a patient through the hollow microneedle 221 on the substrate 21, so that insulin injection is realized.

Referring to fig. 4 and 6, the plurality of electrodes 23 may include an electrochemical sensor electrode 231 and a reverse iontophoresis electrode 232, wherein the electrochemical sensor electrode 231 includes a working electrode 2311 and a counter electrode 2323; or working electrode 2311, reference electrode 2313 and counter electrode 2323; the reverse iontophoresis electrode 232 includes a positive electrode 2321 and a negative electrode 2322.

Specifically, the working electrode 2311 is immobilized with glucose oxidase, and when the working electrode 2311 contacts with the tissue fluid in the patient, the glucose oxidase can react with glucose contained in the tissue fluid of the patient, and a product is generated by the glucose oxidase reaction, and the product can undergo oxidation or reduction reaction on the working electrode 2311 to generate a change of an electric signal. The material of working electrode 2311 may be carbon, gold, platinum, a carbon composite, a gold composite, a platinum composite, or silver/silver chloride.

In one embodiment, the working electrode 2311 may also be coated with a liquid biocompatible polymer and the liquid biocompatible polymer may be heat dried to form a biocompatible polymer layer. The material of the biocompatible polymer layer can be perfluorosulfonic acid, and the biocompatible polymer layer can avoid damage to human body caused by Prussian blue layer contained in the working electrode.

Further, referring to fig. 4 and 6, when the electrochemical sensor electrode 231 includes only the working electrode 2311 and the counter electrode 2323, the counter electrode 2323 simultaneously serves as a connection circuit and stabilizes the voltage in the electrochemical sensor electrode 231, and the counter electrode 2331 may be made of silver/silver chloride; as shown in fig. 4, the electrochemical sensor electrode 231 may also include a working electrode 2311, a reference electrode 2313 and a counter electrode 2323, where the reference electrode 2313 plays a role in stabilizing a voltage in the electrochemical sensor electrode 231 and the counter electrode 2323 plays a role in communicating a circuit in the electrochemical sensor electrode 231; the material of the counter electrode 2323 may be gold, platinum, carbon, or a gold composite, a platinum composite, a carbon composite, or silver/silver chloride; the material of the reference electrode 2313 may be silver/silver chloride.

Referring to fig. 4, a reverse iontophoresis electrode 232 is disposed at one side of the working electrode 231, and the reverse iontophoresis electrode 232 may include a negative electrode 2321 and a positive electrode 2322, and the negative electrode 2321 and the working electrode 2311 form an interdigital electrode 13. Meanwhile, the counter electrode 2323 of the electrochemical sensor electrode 23 and the positive electrode 2322 of the reverse iontophoresis electrode 232 may be located at one side or both sides of the interdigital electrode.

Materials for the reverse iontophoresis electrode 122 include silver/silver chloride, silicone materials, conductive polymers, graphene, gold. Wherein the materials of the negative electrode 1221 and the positive electrode 1222 of the reverse iontophoresis electrode 122 may be the same material or different materials. For example, the negative electrode 1221 and the positive electrode 1222 of the reverse iontophoresis electrode 122 may both be silver/silver chloride materials.

Further, the input end of the control module 3 is connected with the output end of the sensor 2, and the output end is connected with the input end of the electroosmotic pump 1. Therefore, the control module 3 can receive the electrical signal output by the sensor 2, and the microneedle 221 on the sensor 2 enters the patient and contacts with the subcutaneous tissue fluid of the patient, so that the glucose concentration of the subcutaneous tissue fluid of the patient can be detected, and meanwhile, the glucose concentration of the tissue fluid has a strong correlation with the blood glucose concentration, so that the electrical signal output by the sensor 2 can reflect the magnitude of the blood glucose concentration. For example, the sensor 2 may detect a current at a constant voltage, and the magnitude of the current signal is proportional to the magnitude of the glucose concentration.

The control module 3 may then control the electro-osmotic pump 1 to be turned on or off, i.e. to energize or de-energize the electro-osmotic pump 1, in response to the electrical signal. For example, a preset value may be set in the control module 3, and if the value of the electrical signal is greater than or equal to the preset value, the electroosmotic pump 1 is powered, and if the value of the electrical signal is less than the preset value, the electroosmotic pump 1 is not powered.

Thus, the electroosmotic pump 1 can be controlled according to the real-time blood glucose concentration of the patient.

Further, the substrate 21 and the microneedle array 22 of the sensor 2 may be manufactured by using a mold having a microneedle array shape. In a specific fabrication, the substrate 21 may be formed by casting a liquid polymer material onto the mold having the shape of the microneedle array 22 and demolding after drying. Wherein, the liquid polymer material can be biodegradable material such as chitosan, polylactic acid, silk fibroin; biocompatible materials such as thermoplastic polyurethane may also be used; when the biodegradable material is adopted, the microneedle sensor 2 has degradability and can be naturally decomposed after being used; the biocompatible material is adopted, so that the microneedle sensor 2 has stronger biocompatibility, and damage to a human body can be avoided during use.

In an alternative embodiment, the substrate of the sensor 2 and the microneedle array 22 may also be manufactured by 3D printing, and specifically, the material of the sensor 2 may be selected from epoxy, ceramic, metal, biocompatible material, biodegradable material, and the like.

Referring to fig. 7, the signal conversion module 3 includes a first conversion module 31, a control module 32, and a second conversion module 33. Specifically, the input end of the first conversion module 31 is connected to the output end of the sensor 2, the output end of the first conversion module 31 is connected to the input end of the control module 32, the input end of the second conversion module 33 is connected to the output end of the control module 32, and the output end of the second conversion module 33 is connected to the input end of the electroosmotic pump 1.

When the electroosmosis pump closed-loop control system is used, one end of the sensor 2 enters the patient and contacts subcutaneous tissue fluid of the patient so as to detect the glucose concentration of the subcutaneous tissue fluid of the patient, and the glucose concentration of the tissue fluid has strong correlation with the blood glucose concentration, so that the signal output by the sensor 2 can reflect the magnitude of the blood glucose concentration;

specifically, the sensor 2 can detect a current at a constant voltage, and the magnitude of the current signal is proportional to the magnitude of the glucose concentration. The first conversion module 31, in addition to detecting the current signal, also provides the sensor 2 with a constant voltage, which may be a different voltage such as 0.1V, -0.1V, or 0.6V.

And the sensor 2 is arranged at one end outside the patient, and is sequentially provided with a signal conversion module 3 and an electroosmosis pump 1, and the electroosmosis pump 1 is clung to the skin of the patient so as to realize insulin injection for the patient. And, with the sensor 2 having the microneedle array, it is possible to go deep into the dermis or fat layer of the patient, so that the effect of injecting insulin is more remarkable for injecting insulin into the fat layer.

Specifically, the second switching module 33 may provide a constant voltage to drive the electroosmotic pump and control the amount of insulin injected by controlling the magnitude and duration of the voltage, which may be 0.1 to 20V.

Thus, after the sensor 2 detects the glucose concentration and generates an electrical signal, the first conversion module 31 of the signal conversion module 3 receives and converts the electrical signal, and then sends the converted electrical signal to the control module 32, after the control module 32 receives the electrical signal converted by the first conversion module 31, different command information can be generated according to different electrical signals, for example, the control module 32 can generate an on command or an off command, and meanwhile, the control module 32 sends the generated command to the second conversion module 33, and the second conversion module 33 converts the received command into a corresponding signal and controls the on or off of the electroosmosis pump 1 according to the signal, so that the electroosmosis pump 1 is controlled according to the real-time blood glucose concentration of the patient.

In a possible embodiment, the first conversion module 31 is a first signal converter, the control module 32 is a microcontroller, and the second conversion module 33 is a second signal converter.

Specifically, the person skilled in the art can use the devices in the related art as the first signal converter and the second signal converter, and only the control module 32 is required to achieve the effect of controlling the electro-osmotic pump 1 to be turned on or off, so this embodiment is not specifically limited, and the specific contents of the related art are not described again.

In one possible implementation, the closed-loop control system further includes a cloud server, and the control module 32 is electrically connected to the cloud server;

the cloud server is configured to receive and store information sent by the control module 32, and the information sent by the control module 32 may include a blood glucose concentration in the patient.

In one possible implementation, the closed-loop control system further includes a display module, the display module is electrically connected to the control module, and the display module may be further connected to the cloud server.

The display module is configured to receive and display the information sent by the control module 32. The display module may be a computer, display, tablet, etc. as a specific application.

It should be noted that, in the present specification, each embodiment is described in a progressive manner, and each embodiment is mainly described as different from other embodiments, and identical and similar parts between the embodiments are all enough to be referred to each other.

It should also be noted that, in this document, the terms "center", "upper", "lower", "left", "right", "vertical", "horizontal", "inner", "outer", etc. indicate orientations or positional relationships based on those shown in the drawings, and are merely for convenience in describing the present utility model and simplifying the description, and do not indicate or imply that the apparatus or elements to be referred to must have a specific orientation, be configured and operated in a specific orientation, and thus should not be construed as limiting the present utility model. Moreover, relational terms such as "first" and "second" may be used solely to distinguish one entity or action from another entity or action without necessarily requiring or implying any actual such relationship or order between such entities or actions, or order, and without necessarily being construed as indicating or implying any relative importance. Moreover, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or terminal that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or terminal. Without further limitation, an element defined by the phrase "comprising one … …" does not exclude the presence of other like elements in a process, method, article, or terminal device comprising the element.

The foregoing has outlined rather broadly the more detailed description of the utility model in order that the detailed description of the utility model that follows may be better understood, and in order that the present contribution to the art may be better appreciated. While various modifications of the embodiments and applications of the utility model will occur to those skilled in the art, it is not necessary and not intended to be exhaustive of all embodiments, and obvious modifications or variations of the utility model are within the scope of the utility model.

Claims (7)

1. A closed loop control system, comprising:

an electroosmotic pump, a sensor and a signal conversion module;

the electroosmosis pump comprises a first electrode layer, a second electrode layer and an intermediate membrane layer, wherein the intermediate membrane layer is positioned between the first electrode layer and the second electrode layer, and a plurality of through holes are formed in the intermediate membrane layer;

the sensor comprises a substrate, a microneedle array arranged on one side of the substrate, and a plurality of electrodes covering the microneedle array and the substrate, wherein the plurality of electrodes comprise an electrochemical sensor electrode and a reverse iontophoresis electrode;

the substrate is connected with the second electrode layer, and the tips of the microneedle array face to one side away from the second electrode layer;

the signal conversion module comprises a first conversion module, a control module and a second conversion module;

the input end of the first conversion module is connected with the output end of the sensor, the output end of the first conversion module is connected with the input end of the control module, and the first conversion module is used for receiving and converting the electric signal output by the sensor;

the control module is used for receiving the electric signal converted by the first conversion module and sending a command to the second conversion module according to the electric signal;

the input end of the second conversion module is connected with the output end of the control module, the output end of the second conversion module is connected with the input end of the electroosmosis pump, and the second conversion module is used for receiving and converting the command output by the control module and transmitting the converted command signal to the electroosmosis pump so as to control the electroosmosis pump to be started or stopped.

2. The closed loop control system of claim 1, wherein:

the first conversion module is a first signal converter;

the control module is a microcontroller;

the second conversion module is a second signal converter.

3. The closed loop control system of claim 1, wherein:

the microneedle array includes a plurality of microneedle bodies having a length of greater than or equal to 100 μm and less than or equal to 1000 μm.

4. The closed loop control system of claim 1, wherein:

the microneedle array is a hollow microneedle array.

5. The closed loop control system of claim 1, wherein:

the electrochemical sensor electrode comprises a working electrode and a counter electrode, or comprises a working electrode, a reference electrode and a counter electrode, and the reverse iontophoresis electrode comprises a positive electrode and a negative electrode; and the working electrode of the electrochemical sensor electrode and the negative electrode of the reverse iontophoresis electrode form an interdigital electrode;

glucose oxidase is fixed on the working electrode of the electrochemical sensor electrode;

the counter electrode of the electrochemical sensor electrode and the positive electrode of the reverse iontophoresis electrode are positioned at one side or two sides of the interdigital electrode;

the electrochemical sensor is used for detecting glucose in tissue fluid and generating an electric signal, and the reverse iontophoresis electrode is used for generating reverse iontophoresis action so as to attract the glucose in the deep layer of the skin to the upper part of the dermis layer where the needle points of the micro needle body are positioned.

6. The closed loop control system of claim 5, wherein:

the material of the working electrode comprises gold, platinum, carbon or a gold composite material, a platinum composite material or a carbon composite material;

the reference electrode material comprises silver/silver chloride;

the material of the counter electrode comprises gold, platinum, carbon or gold composite material, platinum composite material, carbon composite material or silver/silver chloride;

the material of the reverse iontophoresis electrode comprises silver/silver chloride, a silica gel material, a conductive polymer, graphene or gold.

7. The closed loop control system of claim 1, wherein:

the materials of the first electrode layer, the second electrode layer and the intermediate film layer include: a rigid film or a flexible film.