Glucose concentration detection device and in-vivo glucose monitoring system

Abstract

The utility model discloses a glucose concentration detection device and an in-vivo glucose monitoring system, and belongs to the technical field of measuring instruments. The device takes electrochemistry as a basic principle, the structure can realize minimally invasive implantation of a sensor, specifically, subcutaneous implantation of glucose oxidase is carried out on a user through a disposable sensor implantation half-wall needle under the action of a boosting structure, and telecom for measuring the glucose oxidase in tissue fluid is obtained through the sensor in an application state; the transmitter is combined with the sensor, and the signal measured by the glucose oxidase is converted into the glucose concentration through the transmitter, so that the grape concentration in the tissue fluid is detected and continuously monitored in real time.

Description

Technical Field

[0001] The utility model relates to the technical field of measuring instruments, in particular to a glucose concentration detection device and an in vivo glucose monitoring system. Background Art

[0002] Traditional blood sugar testing generally uses venous blood sugar measurement and fingertip blood sugar testing. Patients with venous blood sugar need to go to the hospital for testing, mainly to test fasting blood sugar and 2 hours after a meal. Fasting blood sugar must be fasted for more than 8 hours. 2 hours after a meal refers to the period from the first bite of food to a full 2 ​​hours. Home blood sugar meters often use fingertip self-test blood sugar, and it is recommended to monitor according to the prescribed time. First, you need to disinfect your fingers with medical alcohol, usually the ring finger. Then put the disposable blood collection needle into the finger lancet pen, then pierce the finger to squeeze out an appropriate amount of blood. It is more appropriate to use the second drop of blood. Then drop the blood into the marked hole of the blood sugar test strip, insert the blood sugar test strip into the blood sugar meter. Some blood sugar meters require the test strip to be inserted into the instrument first, and then drop the blood on the test strip. Finally, after waiting for a few seconds or more than ten seconds, the blood sugar value is read on the blood sugar meter and the blood sugar data and test time are recorded in the record book.

[0003] For this reason, traditional blood sugar tests require going to the hospital for testing, or using a fingertip to prick blood to test blood sugar yourself. These testing procedures are cumbersome and increase the risk of wound infection.

[0004] People who are prone to diabetes need to continuously test their blood sugar in real time to promptly detect whether there is a disorder in blood sugar metabolism and to promptly control or intervene in blood sugar treatment. Therefore, the utility model provides a dynamic blood sugar monitoring system that allows patients to continuously monitor their blood sugar concentration in real time, which has great practical significance. Utility Model Content

[0005] The embodiment of the utility model provides a glucose concentration detection device and an in vivo glucose monitoring system. The technical solution is as follows:

[0006] According to one aspect of the utility model, a glucose concentration detection device is provided, the device comprising a disposable sensor 100 and a transmitter 200, wherein the disposable sensor 100 comprises a disposable sensor implanted half-wall needle 101, a sensor 102 and a boosting structure;

[0007] The disposable sensor implantation half-wall needle 101 is used to implant glucose oxidase subcutaneously in the user under the action of the booster structure; the sensor 102 is used to be applied to the subcutaneous implantation site under the action of the booster structure; in the applied state, the sensor 102 is also used to obtain the electrical signal of glucose oxidase measurement in the tissue fluid;

[0008] The transmitter 200 is installed on the sensor 102 , and is used to convert the electrical signal measured by the glucose oxidase into glucose concentration.

[0009] Optionally, the transmitter 200 is composed of a transmitter upper shell 201, a transmitter PCB 202, a transmitter bottom plate 203 and a transmitter insulating back cover 204, wherein the transmitter upper shell 201, the transmitter PCB 202 and the transmitter bottom plate 203 are sequentially connected to form a disengagement structure;

[0010] The transmitter 200 includes a use state and an unuse state;

[0011] When not in use, the transmitter upper shell 201 and the transmitter insulating rear cover 204 are snapped together to achieve sealing of the transmitter 200;

[0012] When in use, the detachment structure is detached from the transmitter insulating back cover 204 and contacts the sensor 102 through the transmitter base plate 203. In the contact state, the transmitter PCB 202 is used to convert the electrical signal obtained by the sensor 102 into glucose concentration.

[0013] Optionally, the transmitter PCB 202 includes a storage module, a master control microcontroller, an AFE chip, a power supply battery and a switch chip;

[0014] The switch chip is connected to the power supply battery, and the switch chip is connected to the master control microcontroller, wherein the switch chip is used to control the power supply of the power supply battery to the master control microcontroller on and off;

[0015] The AFE chip is provided with a bio-electrode channel connected to the sensor 102, and the bio-electrode channel is used to obtain the electrical signal at the sensor 102 when connected and transmit it to the master control microcontroller through the SPI transmission circuit;

[0016] The master control single chip microcomputer has a BLE Bluetooth function, and the master control single chip microcomputer exchanges data with the monitoring terminal via Bluetooth. The master control single chip microcomputer is used to convert the received electrical signal into the glucose concentration via the I2C transmission circuit and transmit it to the storage module for storage. The master control single chip microcomputer is also used to send the glucose concentration to the monitoring terminal via Bluetooth.

[0017] Optionally, the transmitter insulating back cover 204 contains a conductive rubber sheet, and the conductive rubber sheet is used to ground the switch chip when the transmitter upper shell 201 and the transmitter bottom plate 203 are buckled together.

[0018] Optionally, the boosting structure is composed of a disposable sensor compression spring 103 , a disposable sensor sleeve 104 and a disposable sensor tension spring 105 , and the disposable sensor compression spring 103 and the disposable sensor tension spring 105 are located inside the disposable sensor sleeve 104 .

[0019] Optionally, the disposable sensor sleeve 105 has a double-cylindrical hollow structure;

[0020] The disposable sensor compression spring 103 is embedded in the outer hollow structure, and the disposable sensor compression spring 103 is exposed from the disposable sensor sleeve 104 in a fully embedded state;

[0021] The disposable sensor tension spring 105 is embedded in the inner hollow structure, and the disposable sensor implant half-wall needle 101 is stored in the inner hollow structure of the disposable sensor sleeve 104 when not in use;

[0022] Among them, one side of the disposable sensor tension spring 105 is hooked on the bottom of the disposable sensor implantation half-wall needle 101, and the other side of the disposable sensor tension spring 105 is hooked on the hook point of the inner hollow structure.

[0023] Optionally, the device further comprises a disposable sensor button 106, wherein the disposable sensor button 106 is provided with a snap-fit ​​structure;

[0024] The disposable sensor tension spring 105 in the disposable sensor sleeve 104 is fixed by the buckle structure in the non-pressed state;

[0025] In the pressed state, the buckle structure is released and triggers the disposable sensor tension spring 105 in the disposable sensor sleeve 104 to move.

[0026] Optionally, the device further comprises a disposable sensor upper shell 107 and a disposable sensor lower shell 108;

[0027] The disposable sensor upper shell 107 and the disposable sensor lower shell 108 achieve sealing of the device when snapped together.

[0028] Optionally, the device further comprises a disposable sensor button base 109 and a disposable sensor motion base 110;

[0029] The disposable sensor button base 109 is used to carry the disposable sensor motion base 110 , and the disposable sensor motion base 110 is used to carry the sensor 102 .

[0030] According to another aspect of the present utility model, an in vivo glucose monitoring system is provided, the system comprising a monitoring terminal and the glucose concentration detection device described above;

[0031] The monitoring terminal receives the glucose concentration transmitted from the transmitter.

[0032] In the embodiment of the utility model, a glucose concentration detection device and an in vivo glucose monitoring system are provided. The electrochemistry is used as the basic principle, and the minimally invasive implantation of the sensor can be realized. Specifically, the glucose oxidase is implanted subcutaneously in the user through a disposable sensor implantation half-wall needle under the action of a booster structure. In the application state, the electrical information measured by the glucose oxidase in the tissue fluid is obtained by the sensor. The transmitter and the sensor are combined, and the electrical information measured by the glucose oxidase is converted into the glucose concentration through the transmitter, thereby detecting the real-time and continuous monitoring of the glucose concentration in the tissue fluid. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] Figure 1 It is a structural schematic diagram of a glucose concentration detection device provided by an exemplary embodiment of the utility model;

[0034] Figure 2 It is a structural schematic diagram of a disposable sensor provided by an illustrative embodiment of the utility model;

[0035] Figure 3 It is a structural schematic diagram of a transmitter provided by an exemplary embodiment of the utility model;

[0036] Figure 4 It is a structural schematic diagram of a transmitter PCB provided by an exemplary embodiment of the utility model;

[0037] Figure 5 This is a schematic diagram of an operation scenario provided by an exemplary embodiment of the utility model;

[0038] Figure 6 It is a schematic diagram of a monitoring terminal interface provided by an illustrative embodiment of the utility model. DETAILED DESCRIPTION

[0039] In order to make the purpose, technical solution and advantages of the present invention more clear, the implementation mode of the present invention will be further described in detail below with reference to the accompanying drawings.

[0040] The term "multiple" as used herein refers to two or more than two. "And / or" describes the relationship between related objects, indicating that three relationships can exist. For example, A and / or B can mean: A exists alone, A and B exist at the same time, and B exists alone. The character " / " generally indicates that the related objects are in an "or" relationship.

[0041] First, the electrochemical principle involved in the utility model is explained.

[0042] The utility model designs a method based on electrochemistry as the basic principle, which detects the glucose concentration in the tissue fluid by implanting a minimally invasive sensor to achieve continuous monitoring of glucose.

[0043] Based on the principle of electrochemical reaction, the biological enzyme (glucose oxidase) fixed on the sensor is implanted into the subcutaneous tissue. A certain voltage is applied to the blood after the enzyme reaction. The current generated will increase with the increase of blood glucose concentration in the blood. By accurately measuring these weak currents and the relationship between the current value and the blood glucose concentration, the glucose concentration in the tissue fluid is measured. The electrical signal measured by glucose oxidase is converted into glucose concentration through the transmitter or receiver of the continuous glucose monitoring system and algorithm processing, and displayed on the display or software (monitoring terminal) to form a glucose monitoring map.

[0044] Based on the monitoring graph, the patient's daily maximum glucose value, minimum glucose value and glucose value fluctuation pattern can be analyzed. When the glucose value is displayed in real time, the patient can also be provided with high and low glucose alarms, as well as information such as the direction and rate of glucose trend changes.

[0045] Please refer to Figures 1 to 3 , Figure 1 FIG. 1 shows a schematic structural diagram of a glucose concentration detection device provided by an exemplary embodiment of the utility model. Figure 2 is a schematic structural diagram of a disposable sensor provided by an exemplary embodiment of the utility model, Figure 3 It is a structural schematic diagram of a transmitter provided by an illustrative embodiment of the utility model.

[0046] like Figure 1 As shown, the device includes a disposable sensor 100 and a transmitter 200, wherein the disposable sensor 100 includes a disposable sensor implantable half-wall needle 101, a sensor 102 and a boosting structure.

[0047] The disposable sensor implantation half-wall needle 101 is used to implant glucose oxidase subcutaneously in the user under the action of the booster structure; the sensor 102 is used to be applied to the subcutaneous implantation site under the action of the booster structure; in the applied state, the sensor 102 is also used to obtain the electrical signal of the glucose oxidase measurement in the tissue fluid.

[0048] The transmitter 200 is mounted on the sensor 102 and is used to convert the electrical signal measured by the glucose oxidase into glucose concentration.

[0049] Optionally, the transmitter 200 is composed of a transmitter upper shell 201, a transmitter PCB 202, a transmitter bottom plate 203 and a transmitter insulating back cover 204, wherein the transmitter upper shell 201, the transmitter PCB 202 and the transmitter bottom plate 203 are sequentially connected to form a disengagement structure.

[0050] The transmitter 200 includes a use state and an unuse state. In the use state, the transmitter 200 is used in combination with the disposable sensor 100. In the unuse state, the transmitter 200 is an independent structure. The two states are described below.

[0051] When not in use, the transmitter upper shell 201 and the transmitter insulating rear cover 204 are snapped together to achieve sealing of the transmitter 200 .

[0052] When in use, the detachment structure is detached from the transmitter insulating back cover 204 and contacts the sensor 102 through the transmitter base plate 203. In the contact state, the transmitter PCB 202 is used to convert the electrical signal obtained by the sensor 102 into glucose concentration.

[0053] The transmitter PCB 202 is a key component, and its structure is further described below.

[0054] Combination Figure 4 , Figure 4 This is a schematic diagram of the structure of a transmitter PCB provided by an exemplary embodiment of the utility model. It should be noted that: Figure 4 The structure other than the mobile phone APP and the CGM sensor is a schematic diagram of the overall structure of the transmitter PCB, the mobile phone APP is a schematic form of a monitoring terminal, and the CGM sensor is a schematic type of sensor 102. In addition, in order to achieve signal transmission, Figure 4 It also includes various transmission circuits or functional circuits. In one example, an I2C circuit is provided between the storage module and the master control microcontroller, an impedance matching circuit is provided between the master control microcontroller and the Bluetooth RF antenna, an SPI transmission circuit is provided between the AFE chip and the master control microcontroller, a current collection circuit is provided between the CGM sensor and the AFE chip, and a power supply control circuit is provided between the switch chip and the power supply battery.

[0055] The transmitter PCB 202 includes an E storage module, a master control microcontroller ( Figure 4 The BLE microcontroller with Bluetooth BLE function is shown in the figure), AFE chip, power supply battery and switch chip. The switch chip is connected to the power supply battery, and the switch chip is connected to the master control microcontroller. The switch chip is used to control the power supply of the power supply battery to the master control microcontroller. The AFE chip has a bioelectrode channel ( Figure 4 The bioelectrode channel is used to obtain the electrical signal at the sensor 102 when connected and transmit it to the master control microcontroller through the SPI transmission circuit.

[0056] In the embodiment of the utility model, the models of the power supply battery and the master control microcontroller are not limited. For example, a CR1632 battery can be used for power supply, and the battery power supply can be controlled on and off by a MAX40203 switch chip. Those skilled in the art can also use components of other equivalent models.

[0057] In one example, the AFE chip is connected to the CGM sensor through four bio-electrode channels to obtain its sensor current value, which is then transmitted to the master control microcontroller through the SPI transmission circuit.

[0058] In the embodiment of the utility model, the master control microcontroller has a BLE Bluetooth function, and exchanges data with monitoring terminals such as mobile phone APPs through Bluetooth. There is no limitation on the specific model, and components of equivalent functional models are mainly used, such as the NRF52832 chip. Technical personnel in this field may also use microcontrollers of other equivalent models.

[0059] In one example, after the master control microcontroller receives the electrical signal from the AFE chip, it converts the received electrical signal into glucose concentration through the I2C transmission circuit and transmits it to the storage module for storage, and at the same time sends the data to the mobile phone APP via Bluetooth.

[0060] like Figure 4 In the embodiment, taking the AFE chip with 4 bio-electrode channels as an example, the 4 bio-electrode channels obtain the electrical signal at the sensor through the current acquisition circuit, and transmit it to the BLE microcontroller through the SPI transmission circuit.

[0061] In a possible implementation, in order to achieve interaction with other terminals, the master control microcontroller is a BLE microcontroller with BLE Bluetooth function. The master control microcontroller interacts with the monitoring terminal mobile phone APP through a Bluetooth radio frequency antenna. The master control microcontroller is used to convert the received electrical signal into glucose concentration through an I2C transmission circuit and transmit it to a storage module for storage. The storage module is provided with a storage circuit. The master control microcontroller is also used to send the glucose concentration to the monitoring terminal via Bluetooth.

[0062] Optionally, the transmitter insulating back cover 204 contains a conductive rubber sheet, which is used to ground the switch chip when the transmitter upper shell 201 and the transmitter bottom plate 203 are buckled together. For example, in one example, the MAX40203 chip enable pin is grounded to disconnect the battery power supply.

[0063] Optionally, the boosting structure is composed of a disposable sensor compression spring 103 , a disposable sensor sleeve 104 and a disposable sensor tension spring 105 , and the disposable sensor compression spring 103 and the disposable sensor tension spring 105 are located inside the disposable sensor sleeve 104 .

[0064] Optionally, the disposable sensor sleeve 105 has a double-cylindrical hollow structure.

[0065] The disposable sensor compression spring 103 is embedded in the outer hollow structure, and the disposable sensor compression spring 103 is exposed from the disposable sensor sleeve 104 when fully embedded.

[0066] The disposable sensor tension spring 105 is embedded in the inner hollow structure, and the disposable sensor implant half-wall needle 101 is stored in the inner hollow structure of the disposable sensor sleeve 104 when not in use.

[0067] Among them, one side of the disposable sensor tension spring 105 is hooked on the bottom of the disposable sensor implanted half-wall needle 101, and the other side of the disposable sensor tension spring 105 is hooked on the hook point of the inner hollow structure.

[0068] Optionally, the device also includes a disposable sensor button 106, which is provided with a snap structure; in an unpressed state, the disposable sensor tension spring 105 in the disposable sensor sleeve 104 is fixed by the snap structure; in a pressed state, the snap structure is released and triggers the disposable sensor tension spring 105 in the disposable sensor sleeve 104 to move.

[0069] Optionally, the device further comprises a disposable sensor upper shell 107 and a disposable sensor lower shell 108, and the disposable sensor upper shell 107 and the disposable sensor lower shell 108 achieve sealing of the device in a snap-fit ​​state.

[0070] Optionally, the device further comprises a disposable sensor button base 109 and a disposable sensor motion base 110. The disposable sensor button base 109 is used to carry the disposable sensor motion base 110, and the disposable sensor motion base 110 is used to carry the sensor 102.

[0071] In summary, the utility model provides a glucose concentration detection device, which takes electrochemistry as the basic principle and can realize minimally invasive implantation of sensors. Specifically, a disposable sensor is implanted with a half-wall needle, and glucose oxidase is implanted subcutaneously in the user under the action of a booster structure. In the application state, the electrical conductivity measured by glucose oxidase in the tissue fluid is obtained by the sensor. The transmitter is combined with the sensor, and the electrical conductivity measured by glucose oxidase is converted into glucose concentration through the transmitter, thereby detecting the real-time and continuous monitoring of the glucose concentration in the tissue fluid. The structure is a portable assembly form, and the blood glucose concentration can be monitored by measuring the magnitude of the current at evenly spaced time intervals.

[0072] By adopting this technology, it is avoided to draw blood from the human body, and it is avoided to touch the area rich in nerve endings when piercing the skin. The pain felt by the patient is minimal, which can reduce the psychological burden of the patient when using it, and realize long-term continuous blood glucose monitoring of the human body without causing accidental infection. That is, the utility model solves the problem that the current blood sugar disease monitoring must be carried out for blood drawing and testing, which causes cumbersome work. The microneedle electrode provided by this technology penetrates the stratum corneum of the skin, and the glucose concentration in the tissue fluid can be tested quickly and accurately in a long-term manner. The microneedle electrode is small in size and easy to carry.

[0073] In addition, the product usage and implantation methods have been further improved. The transmitter shell has skin glue, which is directly attached to the skin, and then the silicon-based microneedle is implanted into the stratum corneum of the skin with the needle of the booster for collection. The signal is transmitted to the blood glucose meter through the electrode, and then transmitted to the monitoring terminal mobile phone APP for data collection and analysis of blood glucose concentration based on the current.

[0074] Based on the above embodiments, an in vivo glucose monitoring system is also provided. The system includes a monitoring terminal and the glucose concentration detection device in the above embodiments. The monitoring terminal receives the glucose concentration emitted by the transmitter. Figure 4 Connection relationship.

[0075] It can be seen that the utility model takes into account the user's usage scenario, and real-time blood sugar information can be obtained on the mobile phone APP, such as Figure 5 and Figure 6 As shown, Figure 5 is a schematic diagram of an operation scenario provided by an exemplary embodiment of the utility model, Figure 6 It is a schematic diagram of a monitoring terminal interface provided by an illustrative embodiment of the utility model.

[0076] The in-body glucose monitoring system provides users with a portable sensor monitoring product that can be used by people with diabetes and other people who need blood sugar monitoring, allowing users to quickly and painlessly implant the monitoring sensor into the body and perform blood sugar monitoring.

[0077] The above description is only an optional embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent substitutions, improvements, etc. made within the spirit and principles of the present invention shall be included in the protection scope of the present invention.

Claims

1. A glucose concentration detection device, characterized in that: The device comprises a disposable sensor (100) and a transmitter (200), wherein the disposable sensor (100) comprises a disposable sensor implantation half-wall needle (101), a sensor (102) and a boosting structure; The disposable sensor implantation half-wall needle (101) is used to implant glucose oxidase subcutaneously in a user under the action of the boosting structure; the sensor (102) is used to be applied to the subcutaneous implantation site under the action of the boosting structure; in the applied state, the sensor (102) is also used to obtain an electrical signal of glucose oxidase measurement in tissue fluid; The transmitter (200) is mounted on the sensor (102), and the transmitter (200) is used to convert the electrical current measured by the glucose oxidase into glucose concentration.

2. The device according to claim 1, characterized in that The transmitter (200) is composed of a transmitter upper shell (201), a transmitter PCB (202), a transmitter bottom plate (203) and a transmitter insulating back cover (204), wherein the transmitter upper shell (201), the transmitter PCB (202) and the transmitter bottom plate (203) are sequentially connected to form a disengagement structure; The transmitter (200) includes a use state and a non-use state; When not in use, the transmitter upper shell (201) and the transmitter insulating rear cover (204) are snapped together to achieve sealing of the transmitter (200); In the use state, the detachment structure is detached from the transmitter insulating back cover (204) and contacts the sensor (102) through the transmitter base plate (203). In the contact state, the transmitter PCB (202) is used to convert the electrical signal obtained by the sensor (102) into glucose concentration.

3. The device according to claim 2, characterized in that The transmitter PCB (202) comprises a storage module, a master control single chip computer, an AFE chip, a power supply battery and a switch chip; The switch chip is connected to the power supply battery, and the switch chip is connected to the master control microcontroller, wherein the switch chip is used to control the power supply of the power supply battery to the master control microcontroller on and off; The AFE chip is provided with a bioelectrode channel connected to the sensor (102), and the bioelectrode channel is used to obtain the electrical signal at the sensor (102) when connected and transmit it to the master control microcontroller through the SPI transmission circuit; The master control single chip microcomputer has a BLE Bluetooth function, and the master control single chip microcomputer exchanges data with the monitoring terminal via Bluetooth. The master control single chip microcomputer is used to convert the received electrical signal into the glucose concentration via the I2C transmission circuit and transmit it to the storage module for storage. The master control single chip microcomputer is also used to send the glucose concentration to the monitoring terminal via Bluetooth.

4. The device according to claim 3, characterized in that The transmitter insulating back cover (204) contains a conductive rubber sheet, and the conductive rubber sheet is used to ground the switch chip when the transmitter upper shell (201) and the transmitter bottom plate (203) are buckled together.

5. The device according to any one of claims 1 to 4, characterized in that: The boosting structure is composed of a disposable sensor compression spring (103), a disposable sensor sleeve (104) and a disposable sensor tension spring (105), and the disposable sensor compression spring (103) and the disposable sensor tension spring (105) are located inside the disposable sensor sleeve (104).

6. The device according to claim 5, characterized in that The disposable sensor sleeve (104) has a double-cylindrical hollow structure; The disposable sensor compression spring (103) is embedded in the outer hollow structure, and the disposable sensor compression spring (103) is exposed from the disposable sensor sleeve (104) in a completely embedded state; The disposable sensor tension spring (105) is embedded in the inner hollow structure, and the disposable sensor implant half-wall needle (101) is stored in the inner hollow structure of the disposable sensor sleeve (104) when not in use; One side of the disposable sensor tension spring (105) is hooked on the bottom of the disposable sensor implantation half-wall needle (101), and the other side of the disposable sensor tension spring (105) is hooked on the hook point of the inner hollow structure.

7. The device according to claim 1, characterized in that The device further comprises a disposable sensor button (106), wherein the disposable sensor button (106) is provided with a snap-fit ​​structure; The disposable sensor tension spring (105) in the disposable sensor sleeve (104) is fixed by the buckle structure in a non-pressed state; In the pressed state, the buckle structure is released and triggers the disposable sensor tension spring (105) in the disposable sensor sleeve (104) to move.

8. The device according to claim 1, characterized in that The device also includes a disposable sensor upper shell (107) and a disposable sensor lower shell (108); The disposable sensor upper shell (107) and the disposable sensor lower shell (108) achieve sealing of the device when snapped together.

9. The device according to claim 1, characterized in that The device also includes a disposable sensor button base (109) and a disposable sensor motion base (110); The disposable sensor button base (109) is used to carry the disposable sensor motion base (110), and the disposable sensor motion base (110) is used to carry the sensor (102).

10. An in vivo glucose monitoring system, characterized in that: The system comprises a monitoring terminal and a glucose concentration detection device as claimed in any one of claims 1 to 9; The monitoring terminal receives the glucose concentration transmitted from the transmitter.

Images