Low-power glucose concentration information acquisition device

Abstract

The disclosure describes a low-power glucose concentration information acquisition device, comprising a current sensing module, an amplification module, a first analog-digital conversion module, a micro-processing unit module, and a temperature acquisition module. The current sensing module is configured to be implanted into the subcutaneous tissue of a user and generate a current. The amplification module is configured to receive the current signal output by the current sensing module, amplify the current signal, and convert the current signal into a voltage signal. The first analog-digital conversion module receives the voltage signal and converts the analog signal within the range into a digital signal based on the gain coefficient. The temperature acquisition module acquires the body surface temperature of the human body. The micro-processing unit module is configured to control the acquisition frequency of the glucose concentration information, control the gain coefficient of the first analog-digital conversion module based on the size of the analog signal to adjust the range of the first analog-digital conversion module, and make the acquisition device in a low-power state by turning off the first analog-digital conversion module.

Description

[0001] This application is a divisional application of the patent application filed on March 23, 2022, with application number 2022102863931, entitled "A Glucose Concentration Information Acquisition Device with Three Electrodes". Technical Field

[0002] This disclosure relates to the field of medical device technology, specifically to a low-power glucose concentration information acquisition device. Background Technology

[0003] With the rapid development of society and the economy, people's quality of life has improved, and their attention to health has increased. Among these improvements, diabetes and its chronic complications have become one of the most serious diseases affecting human health today. To delay and reduce the chronic complications of diabetes, it is necessary to first monitor blood glucose levels to better diagnose the condition and then take corresponding measures to control glucose levels. Therefore, monitoring using devices or systems that can collect glucose information is required.

[0004] In existing technologies, continuous glucose monitoring (CGM) devices and glucose sensors are often used to detect glucose in tissue fluid or blood. To improve the accuracy of blood glucose detection, electrodes are often incorporated into the blood glucose meter, and enzymes that react with glucose are placed on the electrodes. The reaction between the enzyme and glucose causes a change in particle concentration, which in turn generates a change in current. The blood glucose concentration can then be inferred by measuring the magnitude of this current. However, existing blood glucose meters struggle to maintain stable ambient voltage during measurement, thus compromising the accuracy of current measurement and consequently hindering the accurate detection of glucose concentration in tissue fluid or blood. Summary of the Invention

[0005] This disclosure is made in view of the above-mentioned state of the prior art, and its purpose is to provide a glucose concentration information acquisition device with three electrodes that is highly resistant to interference, highly sensitive to response, and portable.

[0006] Therefore, this disclosure provides a glucose concentration information acquisition device with three electrodes, including a current sensing module, an amplification module, a low-pass filter module, a first analog-to-digital conversion module, a microprocessor unit module, and a temperature acquisition module. The current sensing module is configured to be implanted into the user's subcutaneous tissue and generate a current in the tissue fluid or blood within the subcutaneous tissue. The current sensing module includes a working electrode, a reference electrode, and a counter electrode. The working electrode is equipped with a glucose enzyme, which reacts with glucose in the tissue fluid or blood to generate a weak current. The reference electrode is configured to maintain a constant potential difference with the working electrode to promote the reaction between the glucose enzyme and glucose. The counter electrode is configured to form a circuit with the working electrode. The amplification module is connected to the working electrode and is configured to receive the analog signal of the weak current from the working electrode and perform computational amplification processing on the analog signal. The low-pass filter module... A filtering module is connected to the amplification module, and the low-pass filtering module is configured to filter high-frequency noise in the analog signal; a first analog-to-digital converter (ADC) module is connected to the low-pass filtering module, and the first ADC module converts the analog signal that has passed through the low-pass filtering module and is within its range into a digital signal based on a gain coefficient; the temperature acquisition module includes a temperature sensing module and a second ADC module connected to the temperature sensing module, the temperature sensing module is configured to measure the user's body surface temperature and obtain the temperature of the working electrode based on the body surface temperature; the microprocessor unit module is configured to control the acquisition frequency of the current acquisition device, the microprocessor unit module is configured to turn off the first ADC module to put the current acquisition device in a low-power state, and the microprocessor unit module is configured to control the gain coefficient of the first ADC module based on the magnitude of the analog signal to adjust the range of the first ADC module.

[0007] The glucose concentration information acquisition device disclosed herein includes a current sensing module and three electrodes implanted in the user's subcutaneous tissue. The working electrode and the counter electrode form a circuit, and a stable potential difference exists between the working electrode and the reference electrode. In this configuration, when the current sensing module comes into contact with glucose in the tissue fluid or blood of the user's subcutaneous tissue, the glucose enzyme disposed on the working electrode reacts with the glucose in the tissue fluid or blood, generating a weak and stable current signal. This current signal can be processed by an amplification module, a low-pass filter module, a first analog-to-digital converter module, a microprocessor unit module, and a temperature acquisition module to obtain relatively accurate glucose concentration information.

[0008] Additionally, the glucose concentration information acquisition device disclosed herein may optionally include a power supply module. The power supply module is equipped with a constant voltage chip and is configured to provide battery voltage. The input terminal of the constant voltage chip is connected to the battery voltage, and the output terminal of the constant voltage chip is connected in series with a first resistor, a second resistor, and ground. A first constant voltage is formed between the output terminal of the constant voltage chip and the first resistor, and a second constant voltage is formed between the first resistor and the second resistor. In this configuration, the constant voltage chip in the power supply module can better maintain the stability of the circuit voltage, thereby ensuring a constant voltage across the three electrodes. This reduces interference from unstable voltages on the measurement of the three electrodes and improves measurement accuracy.

[0009] Furthermore, in the glucose concentration information acquisition device disclosed herein, optionally, the reference electrode is connected in series with the third resistor and the inverting input terminal of the first operational amplifier, and the first constant voltage is input to the non-inverting input terminal of the first operational amplifier. In this case, due to the virtual short and virtual open characteristics of the operational amplifier, the current between the reference electrode and the inverting input terminal of the first operational amplifier can be ignored, that is, the voltage between the reference electrode and the first constant voltage is the voltage of the reference electrode. Therefore, the reference voltage can be maintained at a relatively stable value.

[0010] Additionally, in the glucose concentration information acquisition device disclosed herein, optionally, the working electrode is connected to the inverting input terminal of the second operational amplifier, and the second constant voltage is input to the non-inverting output terminal of the second operational amplifier. In this case, based on the virtual short and virtual open characteristics of the operational amplifier, the voltage of the working electrode is the second constant voltage.

[0011] In addition, in the glucose concentration information acquisition device disclosed herein, optionally, the first constant voltage and the second constant voltage have a constant potential difference, wherein the voltage range of the potential difference is 10 millivolts to 1000 millivolts.

[0012] In addition, in the glucose concentration information acquisition device disclosed herein, the temperature sensing module may optionally be a thermistor. This allows the temperature sensing module to have high sensitivity.

[0013] Furthermore, in the glucose concentration information acquisition device disclosed herein, optionally, the low-pass filter module is a first-order low-pass filter. In this case, high-frequency noise in the voltage analog signal after conversion by the amplification module can be filtered out, reducing the interference of high-frequency noise on the signal input to the analog-to-digital conversion module, thereby improving the accuracy of the measurement.

[0014] Additionally, in the glucose concentration information acquisition device disclosed herein, optionally, the microprocessor unit module includes a serial communication module. This serial communication module is configured to program the acquisition device and calibrate its current and temperature measurement accuracy during production. In this case, during factory calibration, serial communication can be used for analysis to determine whether the accuracy of the current and temperature measurements of the acquisition device meets the calibration requirements.

[0015] Additionally, in the glucose concentration information acquisition device disclosed herein, optionally, the microprocessor unit module further includes a Bluetooth communication module configured to transmit acquired data information. In this case, the Bluetooth communication module can wirelessly receive the acquired data information and transmit it to the data analysis module. Thus, glucose concentration information can be obtained through the data analysis module, such as a mobile phone or computer.

[0016] Additionally, in the glucose concentration information acquisition device disclosed herein, optionally, the first analog-to-digital conversion module has a reference voltage. In this case, selecting different measurement ranges based on the reference voltage and different gain coefficients can yield more accurate data.

[0017] According to this disclosure, a glucose concentration information acquisition device with three electrodes that is highly resistant to interference, highly sensitive to response, and portable can be provided. Attached Figure Description

[0018] This disclosure will now be explained in further detail by way of example only with reference to the accompanying drawings, in which:

[0019] Figure 1 This is an exemplary block diagram illustrating a data acquisition device according to an embodiment of the present disclosure.

[0020] Figure 2 This is a circuit diagram showing some components of the acquisition device according to an embodiment of the present disclosure.

[0021] Figure 3 This is a circuit diagram illustrating an amplification module involved in an embodiment of the present disclosure.

[0022] Figure 4 This is a circuit diagram illustrating a low-pass filter module according to an embodiment example of this disclosure.

[0023] Figure 5 This is a circuit diagram illustrating a constant voltage chip according to an example embodiment of the present disclosure.

[0024] Figure 6 This is a circuit diagram illustrating a temperature acquisition module according to an example embodiment of the present disclosure.

[0025] Figure label:

[0026] 1…data acquisition device,

[0027] 10… Current sensing module, 20… Amplification module, 30… Low-pass filter module, 40… First analog-to-digital converter module, 50… Microprocessor unit module, 60… Temperature acquisition module, 70… Power supply module, 80… Constant voltage chip, 90… Second analog-to-digital converter module. Detailed Implementation

[0028] Hereinafter, preferred embodiments of the present disclosure will be described in detail with reference to the accompanying drawings. In the following description, the same reference numerals are used for the same components, and repeated descriptions are omitted. Furthermore, the drawings are merely schematic diagrams, and the proportions of the components or the shapes of the components may differ from actual figures.

[0029] It should be noted that the terms "comprising" and "having" and any variations thereof in this disclosure, such as a process, method, system, product, or device that includes or has a series of steps or units, are not necessarily limited to those steps or units that are explicitly listed, but may include or have other steps or units that are not explicitly listed or that are inherent to such processes, methods, products, or devices.

[0030] Furthermore, the subheadings and similar terms used in the following description of this disclosure are not intended to limit the content or scope of this disclosure; they are merely intended to serve as reading prompts. Such subheadings should not be construed as dividing the content of the article, nor should the content under a subheading be limited to the scope of that subheading.

[0031] This disclosure relates to a glucose concentration information acquisition device with three electrodes. The "glucose concentration information acquisition device with three electrodes" can be simply referred to as a "glucose acquisition device," or hereinafter referred to as the "acquisition device." The glucose concentration information acquisition device with three electrodes disclosed herein can acquire glucose concentration with high sensitivity and relatively high accuracy.

[0032] When glucose in blood undergoes a reaction under the action of enzymes, the concentration of ions changes, generating a weak electric current. By collecting the current and temperature data, and then processing the data using a computer, the glucose concentration in tissue fluid or blood can be determined. In some examples, "glucose concentration information" may refer to the current and temperature required to obtain the glucose concentration.

[0033] The data acquisition device involved in this embodiment will be described below with reference to the accompanying drawings.

[0034] Figure 1 This is a block diagram showing the acquisition device 1 according to an embodiment of the present disclosure.

[0035] In some examples, the acquisition device 1 can be used to acquire the weak current generated when blood glucose reacts. In some examples, the range of the weak current can be 1–100 nA.

[0036] In some examples, such as Figure 1 As shown, the acquisition device 1 may include a current sensing module 10, an amplification module 20, a low-pass filter module 30, and a first analog-to-digital converter module 40. The current sensing module 10 can be implanted into the user's subcutaneous tissue to generate current. The amplification module 20 can be configured to receive the current signal output by the current sensing module 10 and amplify it into a larger voltage. The low-pass filter module 30 can be configured to filter high-frequency noise in the signal output by the amplification module 20. The first analog-to-digital converter module 40 can be configured to convert the analog signal into a digital signal.

[0037] In some examples, the acquisition device 1 may further include a microprocessor unit module 50 and a temperature acquisition module 60 (described later). The microprocessor unit module 50 may be configured to control the acquisition frequency of glucose concentration information. In some examples, the microprocessor unit module 50 may also be used to control a first analog-to-digital converter module 40. The microprocessor unit module 50 may control the first analog-to-digital converter module 40 to be in a turned-off state so that the acquisition device 1 is in a low-power state. This improves the energy storage capacity of the acquisition device 1 and extends its service life.

[0038] In some examples, the data acquisition device 1 can store the data for up to 12 months. In some examples, the data acquisition device 1 can also operate continuously inside the human body for 14 days. In some examples, the body surface temperature can be acquired by the temperature acquisition module 60. In some examples, after the temperature acquisition module 60 acquires the body surface temperature, it can transmit the relevant data to the microprocessor unit module 50 for processing.

[0039] Figure 2 This is a circuit diagram showing some of the components of the acquisition device 1 according to an embodiment of the present disclosure.

[0040] In some examples, as described above, the current sensing module 10 can be implanted in the user's subcutaneous tissue to generate an electric current. In some examples, the current sensing module 10 can use a three-electrode system to acquire the current. For example... Figure 2 As shown, the current sensing module 10 may include a working electrode WE, a reference electrode RE, and a counter electrode CE. After the three electrodes are implanted in the user, each electrode begins to form a circuit loop and detect the current.

[0041] In some examples, the working electrode WE can be equipped with a glucosidase. In this case, the glucosidase can react with glucose in the tissue fluid / blood and produce ionic changes in the tissue / blood. This allows a weak current to be generated between the working electrode WE and the tissue fluid / blood.

[0042] In some examples, the current value of the working electrode WE can range from 1 to 100 nA. This allows for relatively accurate acquisition of the weak current in the blood glucose response. However, the examples disclosed herein are not limited to this; the current value of the working electrode WE can range from approximately 1 to 100 nA. For example, the current value range of the working electrode WE can also exhibit slight fluctuations.

[0043] In some examples, the reference electrode RE can maintain a constant potential difference with the working electrode WE (described later). In this case, a stable reaction can occur between the glucosidase and glucose, thereby generating a stable current. This allows glucose concentration information to be reflected through the current. Generating a stable current also helps improve the accuracy of glucose concentration data acquisition.

[0044] In some examples, a loop can be formed between the counter electrode CE and the working electrode WE. This enables the transmission of current data in the current sensing module 10.

[0045] In some examples, the reference electrode RE can be connected in series with the third resistor R1 and the inverting input of the first operational amplifier U1, and the non-inverting input of the first operational amplifier U1 can be input with a first constant voltage.

[0046] In some examples, the working electrode WE can be connected to the inverting input of the second operational amplifier U2 (described later), and a second constant voltage can be input to the non-inverting output of the second operational amplifier U2.

[0047] Figure 3 This is a circuit diagram illustrating the amplification module 20 involved in an embodiment example of this disclosure.

[0048] In some examples, amplification module 20 can be used to convert and amplify a current signal into a larger voltage. In some examples, amplification module 20 can amplify a weak current measured at the working electrode WE into a larger voltage. In some examples, the voltage converted and output by amplification module 20 can be 0–2V.

[0049] In some examples, the amplification module 20 may have a second operational amplifier U2 (see...) Figure 3 ).

[0050] In some examples, the inverting input of the second operational amplifier U2 can be connected to the working electrode WE. In this case, when the circuit is stable, due to the "virtual short and virtual open" characteristics of the operational amplifier, the voltage input to the non-inverting input of the second operational amplifier U2 is the same as the voltage input to the inverting input of the second operational amplifier U2. In other words, the voltage input to the non-inverting input of the second operational amplifier U2 is equal to the voltage of the working electrode WE of the current sensing module 10.

[0051] In some examples, the inverting input of the second operational amplifier U2 can be connected in sequence to the resistor R2, the output of the second operational amplifier U2, and the low-pass filter module 30.

[0052] Figure 4 This is a circuit diagram illustrating a low-pass filter module 30 according to an example embodiment of the present disclosure.

[0053] In some examples, the low-pass filter module 30 can be connected to the output of the second operational amplifier U2 and the first analog-to-digital converter module 40. In some examples, the low-pass filter module 30 can receive the signal output from the second operational amplifier U2, filter the signal, and then transmit it to the first analog-to-digital converter module 40.

[0054] See Figure 3 In some examples, the non-inverting input voltage of the second operational amplifier U2 can be VDD2, and the measured weak current I can be the current flowing through resistor R2. In this case, the output voltage U of the second operational amplifier U2 can be calculated using the formula: U = I * R2 + VDD2.

[0055] In some examples, the low-pass filter module 30 can be a first-order low-pass filter. In some examples, the low-pass filter module 30 can be composed of a resistor R3 and a capacitor C3. (See also...) Figure 4 )

[0056] In some examples, a low-pass filter can filter high-frequency noise from the signal, thereby improving the signal's immunity to interference and reducing the possibility of signal oscillation caused by high-frequency noise. It also reduces the impact of high-frequency noise on the input signal of the first analog-to-digital converter module 40.

[0057] In some examples, the second operational amplifier can be a transimpedance amplifier. The inverting input of the second operational amplifier U2 can be connected to its output via a third resistor R2. For example... Figure 3As shown, the input voltage at the non-inverting input terminal of the second operational amplifier U2 is VDD2, which can be used as the reference voltage for the second operational amplifier U2. In some examples, the voltage at the working electrode WE can be the input voltage at the non-inverting input terminal of the second operational amplifier U2. That is, the voltage at the working electrode WE can be VDD2. In this case, amplifying the voltage at the working electrode WE by the second operational amplifier module 20 can increase the strength of the voltage signal output by the second operational amplifier module 20, so as to facilitate the subsequent measurement of the sensor current by the first analog-to-digital converter module 40.

[0058] In some examples, the first analog-to-digital converter (ADC) module 40 can convert analog signals into digital signals. Specifically, after receiving the sensing voltage output by the amplification module 20 and filtered by the low-pass filter module 30, the ADC value of the voltage is acquired by the first ADC module 40, and the value of the sensor current can be obtained according to Ohm's law. In this case, the microprocessor unit module 50 can receive and process the digital signal output by the first ADC module 40.

[0059] Figure 5 This is a circuit diagram illustrating a constant voltage chip 80 according to an example embodiment of the present disclosure.

[0060] In some examples, the acquisition device 1 may also include a power module 70. In some examples, the power module may be configured with a constant voltage chip 80. In some examples, the power module 70 can provide the constant voltage chip 80 with a battery voltage VDD1. In some examples, the output terminal of the constant voltage chip 80 may be connected in series with a first resistor R4, a second resistor R5, and ground (see [reference]). Figure 5 The battery voltage VDD1 is input through the input terminal of the constant voltage chip 80, and VDD2 can be obtained at the output terminal of the constant voltage chip 80. VDD2 is divided by the first resistor R4 and the second resistor R5, and a stable voltage such as VDD2 and VDD3 can be formed across the first resistor R4. The voltage configuration range can be 10mV-1000mV.

[0061] In some examples, the output voltage of the constant voltage chip 80 can form a first constant voltage through the first resistor R4, and a second constant voltage can be formed between the first resistor R4 and the second resistor R5. In this case, the constant voltage chip 80 in the power supply module can maintain the stability of the circuit voltage so that the three electrodes maintain a stable voltage, thereby reducing the possibility of unstable voltage interfering with the measurement current of the three electrodes and improving the measurement accuracy.

[0062] In some examples, the first constant voltage can be VDD2, and the second constant voltage can be VDD3. In some examples, the first and second constant voltages can have a constant potential difference. In some examples, the voltage range of the potential difference can be from 10 millivolts to 1000 millivolts.

[0063] Figure 6 This is a circuit diagram illustrating a temperature acquisition module 60 according to an example embodiment of the present disclosure.

[0064] In some examples, the temperature acquisition module 60 may include a temperature sensing module and a second analog-to-digital converter (ADC) module 90, which may be connected to the temperature sensing module. The temperature sensing module may be connected to voltage VDD2 via resistor R6.

[0065] In some examples, the temperature sensing module can be a thermistor R7.

[0066] In some examples, the resistance of the thermistor can change with temperature. Therefore, the resistance of the temperature sensing module (i.e., thermistor R7) will also change when the ambient temperature changes. In this case, when the acquisition device 1 acquires the human body's glucose temperature, the body surface temperature can be acquired by measuring the resistance of the temperature sensing module (i.e., thermistor R7).

[0067] In some examples, the resistor R6 in the temperature acquisition module 60 can achieve an accuracy of one-thousandth. This allows the temperature acquisition module 60 to acquire ambient temperature more accurately, thereby improving the accuracy of glucose concentration measurement.

[0068] In some examples, the analog-to-digital conversion value of the voltage of the thermistor R7 can be acquired by the second analog-to-digital conversion module 90, and the voltage of the thermistor R7 can be calculated. Then, the resistance value of the thermistor R7 can be calculated through the voltage division relationship between resistor R6 and the thermistor R7. Finally, the temperature value of the thermistor R7 can be obtained by looking up the resistance-temperature relationship table of the thermistor R7.

[0069] In some examples, a sensor for collecting current can be formed by the interaction of three electrodes and various modules. The sensor can infer the glucose concentration at the time of sampling based on the collected current. In some examples, the sensor's temperature and sensitivity can be directly proportional. Therefore, the sensor's sensitivity can be determined by measuring its temperature.

[0070] In some examples, when measurements are initiated via the sensor, since the current sensing module 10 is inserted into the user's subcutaneous tissue, the temperature of the implanted sensor can be calculated based on the body surface temperature after the temperature sensing module measures the body surface temperature. This temperature can then be used to determine whether the sensor's sensitivity meets the required standards. In this case, the temperature sensing module can monitor the sensor's sensitivity in real time and fine-tune it based on feedback to meet the standard requirements. This improves the accuracy of the sensor's current measurement.

[0071] In some examples, the first analog-to-digital converter module 40 may have a reference voltage. The first analog-to-digital converter module 40 may have different gain coefficients. In some examples, by setting a reference voltage and a specific gain coefficient, a specific measurement range can be obtained. In this case, different measurement ranges can be selected based on the reference voltage and different gain coefficients, thereby enabling the acquisition of accurate sensor current data.

[0072] In some examples, sensor current can be measured using a range-based current measurement method. When the current range used to measure the sensor current is too large or too small, an appropriate range can be switched to obtain a more accurate measurement. The following is a description of using the range-based current measurement method to measure sensor current.

[0073] In some examples, a reference voltage can be set inside the first analog-to-digital converter module 40, and the input voltage range is equal to the reference voltage divided by the gain of the first analog-to-digital converter module 40. In this case, when the reference voltage is fixed, the current test range can be switched by changing the gain of the first analog-to-digital converter module 40. In some examples, the number of current test ranges can be four. Thus, the sensor current measurement range can be configured to four different ranges.

[0074] In some examples, when measuring sensor current, the internal reference voltage of the first analog-to-digital converter (ADC) 40 can be set, and the ADC 40 can be configured with multiple gains. The gain is then adjusted to the first position, and the current range is set to the first level, meaning the initial state is to measure the sensor current through the first range. When the output sensor current is less than the first range, the current value is directly output. When the output sensor current is greater than the first range, the gain of the ADC 40 is switched to change the current measurement range, switching to the second level. If the output current is still greater than the second level, the above operation is repeated, switching to the third level again, and so on, until the measured sensor current is within a suitable range. In this case, outputting the current value through the appropriate range can reduce measurement errors and lower the load on the ADC 40. This improves the accuracy of the sensor current measurement.

[0075] In some examples, the internal reference voltage of the 40-channel chip of the first analog-to-digital converter (ADC) can be 0.6V, and the gain of the first ADC 40 can be set to 4, 2, 1, and 1 / 2. In some examples, the input voltage range can be equal to the reference voltage divided by the gain of the first ADC 40, resulting in input voltage ranges of 0–0.15V, 0–0.3V, 0–0.6V, and 0–1.2V. Assuming the resistance of R2 is 10MΩ, dividing the input voltage by the resistance of R2 yields the corresponding current range. In this case, the current measurement ranges of the first ADC 40 are 0–15nA, 0–30nA, 0–60nA, and 0–120nA.

[0076] To begin current testing, in the first test range, the software can configure the first analog-to-digital converter (ADC) 40 to use 0.6V as the reference voltage and set its gain to 4. This gives the ADC 40 a current measurement range of 0–15nA in the first test range. After the ADC 40 completes current acquisition, the software determines the current magnitude, for example, whether the sensor current is less than the first-range measurement range of 0–15nA. If the sensor current is less than 15nA, the current value is output normally. If the sensor current is greater than 15nA, the software switches to the second range and tests the current again. In the second test range, the software can configure the ADC 40 to use 0.6V as the reference voltage and switch its gain to 2. This gives the ADC 40 a current measurement range of 0–30nA in the second test range. After switching to the second range, the current is measured again, and it is determined whether the sensor current is less than the second-range measurement range. Similarly, when the sensor current does not exceed the current measurement range of the first analog-to-digital conversion module 40, the current value is output; otherwise, a larger range needs to be switched again to measure the sensor current.

[0077] However, the examples disclosed herein are not limited to this. In other examples, a larger measurement range can be used initially to measure the sensor current. When the measured current of the sensor is significantly smaller than the range, the measurement range can be switched to a smaller range. This process continues until a suitable range is selected.

[0078] In some examples, the microprocessor unit module 50 may also include a serial communication module. In some examples, the program for the acquisition device 1 can be programmed via the serial communication module during production. In some examples, the current measurement accuracy and temperature measurement accuracy of the acquisition device 1 can also be calibrated via the serial communication module. This improves the accuracy of the acquired glucose concentration data.

[0079] In some examples, the microprocessor unit module 50 may also include a Bluetooth communication module. In some examples, the Bluetooth communication module can transmit collected data. In this case, after pairing the Bluetooth communication module with a data analysis module, such as a mobile phone or computer, the collected data can be wirelessly received via the Bluetooth communication module and transmitted to the data analysis module. Thus, the glucose concentration information can be viewed through the data analysis module.

[0080] While the present disclosure has been specifically described above in conjunction with the accompanying drawings and examples, it is to be understood that the foregoing description does not limit the present disclosure in any way. Those skilled in the art can make modifications and variations to the present disclosure as needed without departing from its essential spirit and scope, and all such modifications and variations shall fall within the scope of the present disclosure.

Claims

1. A low-power glucose concentration information acquisition device, characterized in that: The device includes a current sensing module, an amplification module, a first analog-to-digital converter (ADC), a microprocessor unit module, and a temperature acquisition module. The current sensing module is configured to be implanted in the user's subcutaneous tissue and generate a current. The amplification module is configured to receive the current signal output by the current sensing module, amplify the current signal, and convert it into a voltage signal. The first ADC receives the voltage signal and converts the analog signal within its range into a digital signal based on a gain coefficient. The temperature acquisition module acquires the body surface temperature. The microprocessor unit module is configured to receive the digital signal output by the first ADC and the body surface temperature output by the temperature acquisition module, control the acquisition frequency of glucose concentration information, control the gain coefficient of the first ADC based on the magnitude of the analog signal to adjust the range of the first ADC, and keep the acquisition device in a low-power state by turning off the first ADC. The current sensing module includes a working electrode, a reference electrode, and a counter electrode. The working electrode is equipped with a glucosidase, which reacts with glucose in tissue fluid or blood to generate a weak current. The reference electrode is configured to maintain a constant potential difference with the working electrode to promote the reaction between the glucosidase and glucose. The counter electrode is configured to form a circuit with the working electrode. The temperature acquisition module includes a temperature sensing module and a second analog-to-digital converter connected to the temperature sensing module. The temperature sensing module is configured to measure the user's body surface temperature and obtain the temperature of the working electrode based on the body surface temperature. The temperature of the working electrode is used to determine whether the sensitivity of the working electrode meets the standard requirements, and fine-tuning is performed based on the sensitivity feedback to ensure that the sensitivity meets the standard requirements. When measurement begins via the sensor, since the current sensing module is inserted into the user's subcutaneous tissue, after the temperature sensing module measures the human body surface temperature, the temperature of the sensor implanted under the skin is calculated based on the human body surface temperature. The sensor temperature is used to determine whether the sensitivity of the sensor meets the standard requirements. The temperature sensing module monitors the sensitivity of the sensor in real time and fine-tunes it based on the sensitivity feedback to ensure that it meets the standard requirements. The first analog-to-digital converter module has a reference voltage and different gain coefficients, and different ranges are selected according to the reference voltage and different gain coefficients.

2. The low-power glucose concentration information acquisition device according to claim 1, characterized in that: It also includes a low-pass filter module, which is connected to the amplification module and is configured to filter high-frequency noise in the analog signal.

3. The low-power glucose concentration information acquisition device according to claim 1, characterized in that: It also includes a power module, which is equipped with a constant voltage chip. The power module is configured to provide battery voltage. The input terminal of the constant voltage chip is connected to the battery voltage. The output terminal of the constant voltage chip is connected in series with a first resistor, a second resistor, and ground. A first constant voltage is formed between the output terminal of the constant voltage chip and the first resistor, and a second constant voltage is formed between the first resistor and the second resistor.

4. The low-power glucose concentration information acquisition device according to claim 3, characterized in that: The reference electrode is connected in series with the third resistor and the inverting input terminal of the first operational amplifier, and the first constant voltage is input to the non-inverting input terminal of the first operational amplifier.

5. The low-power glucose concentration information acquisition device according to claim 3, characterized in that: The amplification module has a second operational amplifier, the working electrode is connected to the inverting input terminal of the second operational amplifier, and the non-inverting output terminal of the second operational amplifier is input with the second constant voltage.

6. The low-power glucose concentration information acquisition device according to claim 3, characterized in that: The first constant voltage and the second constant voltage have the constant potential difference, the voltage range of which is 10 millivolts to 1000 millivolts.

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