CN114778642B - Glucose concentration information acquisition device with three electrodes - Google Patents
Glucose concentration information acquisition device with three electrodes Download PDFInfo
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- CN114778642B CN114778642B CN202210286393.1A CN202210286393A CN114778642B CN 114778642 B CN114778642 B CN 114778642B CN 202210286393 A CN202210286393 A CN 202210286393A CN 114778642 B CN114778642 B CN 114778642B
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- WQZGKKKJIJFFOK-GASJEMHNSA-N Glucose Natural products OC[C@H]1OC(O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-GASJEMHNSA-N 0.000 title claims abstract description 83
- 239000008103 glucose Substances 0.000 title claims abstract description 83
- 238000006243 chemical reaction Methods 0.000 claims abstract description 64
- 238000012545 processing Methods 0.000 claims abstract description 27
- 210000004369 blood Anatomy 0.000 claims abstract description 24
- 239000008280 blood Substances 0.000 claims abstract description 24
- 238000001914 filtration Methods 0.000 claims abstract description 20
- 239000012530 fluid Substances 0.000 claims abstract description 10
- 238000005259 measurement Methods 0.000 claims description 28
- 238000004891 communication Methods 0.000 claims description 16
- 230000035945 sensitivity Effects 0.000 claims description 16
- 206010033675 panniculitis Diseases 0.000 claims description 11
- 210000004304 subcutaneous tissue Anatomy 0.000 claims description 11
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- 210000001519 tissue Anatomy 0.000 claims description 10
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- 102100036285 25-hydroxyvitamin D-1 alpha hydroxylase, mitochondrial Human genes 0.000 description 2
- 101000875403 Homo sapiens 25-hydroxyvitamin D-1 alpha hydroxylase, mitochondrial Proteins 0.000 description 2
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- 206010012601 diabetes mellitus Diseases 0.000 description 2
- 210000003722 extracellular fluid Anatomy 0.000 description 2
- 230000036541 health Effects 0.000 description 2
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1486—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using enzyme electrodes, e.g. with immobilised oxidase
- A61B5/14865—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using enzyme electrodes, e.g. with immobilised oxidase invasive, e.g. introduced into the body by a catheter or needle or using implanted sensors
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/01—Measuring temperature of body parts ; Diagnostic temperature sensing, e.g. for malignant or inflamed tissue
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
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Abstract
The disclosure describes a glucose concentration information acquisition device with three electrodes, comprising a current sensing module, an amplifying module, a low-pass filtering module, a first analog-to-digital conversion module, a micro-processing unit module and a temperature acquisition module, wherein the current sensing module comprises a working electrode, a reference electrode and a counter electrode, the glucose on the working electrode reacts with glucose in tissue fluid or blood to generate current, and the amplifying module amplifies analog signals; the low-pass filtering module filters high-frequency noise in the analog signal; the first analog-to-digital conversion module converts the analog signal into a digital signal; the temperature acquisition module acquires the temperature of the working electrode; the micro-processing unit module controls the acquisition frequency, the micro-processing unit module closes the first analog-to-digital conversion module to enable the acquisition device to be in a low-power consumption state, the micro-processing unit module controls the gain coefficient of the first analog-to-digital conversion module based on the magnitude of the analog signal to adjust the measuring range of the first analog-to-digital conversion module, and the current is measured through the proper measuring range.
Description
Technical Field
The disclosure relates to the technical field of medical instruments, in particular to a glucose concentration information acquisition device with three electrodes.
Background
In the process of rapid development of social and economic life, the quality of life of people is also developed, and the importance of physical health is also increasing, wherein diabetes and chronic complications thereof become one of the current diseases which seriously affect human health. In order to delay and reduce chronic complications of diabetes, the symptoms can be better judged by monitoring the glucose concentration in blood, and corresponding measures can be taken to control the glucose concentration, so that monitoring is realized by a plurality of devices or systems capable of collecting glucose information.
In the prior art, a dynamic blood glucose detector and a glucose sensor are combined to detect glucose in tissue fluid or blood, and in order to improve the accuracy of blood glucose detection, an electrode is often required to be arranged in the blood glucose detector to cooperate with the blood glucose detector, and an enzyme capable of reflecting with the glucose is arranged on the electrode, so that the enzyme reacts with the glucose to generate particle concentration change, and then current change occurs. From this, the glucose concentration in blood can be inferred by measuring the magnitude of the current. However, the existing blood glucose meter is difficult to maintain the stability of the measured environmental voltage during measurement, so that the accuracy of current measurement is difficult to ensure during measurement, and the glucose concentration in tissue fluid or blood cannot be detected well.
Disclosure of Invention
The present disclosure has been made in view of the above-described conventional circumstances, and an object thereof is to provide a portable glucose concentration information collection device having three electrodes, which has high interference immunity and high response sensitivity.
To this end, the present disclosure provides a glucose concentration information collection device having three electrodes, including a current sensing module configured to be implanted into subcutaneous tissue of a user and to generate a current in interstitial fluid or blood within the subcutaneous tissue, an amplifying module, a low-pass filtering module, a first analog-to-digital conversion module, a micro-processing unit module, and a temperature collection module, the current sensing module including a working electrode provided with a glucose enzyme that reacts with glucose in the interstitial fluid or blood to generate a weak current, a reference electrode configured to maintain a constant potential difference with the working electrode to promote the reaction of the glucose enzyme with the glucose, and a counter electrode configured to form a loop with the working electrode; the amplifying module is connected with the working electrode and is configured to receive an analog signal of weak current from the working electrode and perform operational amplification processing on the analog signal; the low-pass filtering module is connected with the amplifying module and is configured to filter high-frequency noise in the analog signal; the first analog-to-digital conversion module is connected with the low-pass filtering module and converts an analog signal which passes through the low-pass filtering module and is in a measuring range into a digital signal based on a gain coefficient; the temperature acquisition module comprises a temperature sensing module and a second analog-to-digital conversion module connected with the temperature sensing module, and the temperature sensing module is configured to measure the body surface temperature of a user and obtain the temperature of the working electrode based on the body surface temperature; the micro-processing unit module is configured to control the acquisition frequency of the current acquisition device, the micro-processing unit module is configured to enable the current acquisition device to be in a low-power consumption state by closing the first analog-to-digital conversion module, and the micro-processing unit module is configured to control the gain coefficient of the first analog-to-digital conversion module based on the magnitude of an analog signal so as to adjust the range of the first analog-to-digital conversion module.
In the glucose concentration information collecting device according to the present disclosure, there is a current sensing module and three electrodes implanted in subcutaneous tissue of a user, among the three electrodes, a working electrode and a counter electrode form a loop and there is a stable potential difference between the working electrode and a reference electrode. In this case, when the current sensing module is in contact with glucose in tissue fluid in subcutaneous tissue of a user or glucose in blood, the glucose disposed on the working electrode reacts with glucose in tissue fluid in subcutaneous tissue of a user or glucose in blood, so that a weak and stable current signal can be generated, and the current signal can be correspondingly processed through the amplifying module, the low-pass filtering module, the first analog-to-digital conversion module, the micro-processing unit module and the temperature acquisition module, so that relatively accurate concentration information data of glucose can be obtained.
In addition, in the glucose concentration information acquisition device related to the disclosure, optionally, the device further comprises a power module, the power module is configured with a constant voltage chip, the power module is configured to provide battery voltage, an input end of the constant voltage chip is connected with the battery voltage, an output end of the constant voltage chip is sequentially connected with a first resistor, a second resistor and a ground end in series, a first constant voltage is formed between the output end of the constant voltage chip and the first resistor, and a second constant voltage is formed between the first resistor and the second resistor. Under the condition, the constant voltage chip in the power supply module can better maintain the stability of the circuit voltage so as to enable the three electrodes to maintain constant voltage, thereby reducing the interference of the unstable voltage on the measurement of the three electrodes and improving the measurement precision.
In addition, in the glucose concentration information collecting device according to the present disclosure, optionally, the reference electrode is connected in series with a third resistor and an inverting input terminal of the first operational amplifier in sequence, and a non-inverting input terminal of the first operational amplifier inputs the first constant voltage. In this case, due to the nature of the virtual short and virtual break of the operational amplifier, the current between the reference electrode and the inverting input terminal of the first operational amplifier is negligible, i.e. the reference electrode and the first constant voltage are the voltages of the reference electrode. Thus, the voltage of the reference voltage can be maintained at a relatively stable value.
In addition, in the glucose concentration information collecting apparatus according to the present disclosure, optionally, the working electrode is connected to an inverting input terminal of the second operational amplifier, and an in-phase output terminal of the second operational amplifier inputs the second constant voltage. In this case, the voltage of the working electrode is the second constant voltage according to the characteristics of the operational amplifier, such as the short-circuit and the short-circuit.
In addition, in the glucose concentration information collection device according to the present disclosure, optionally, the first constant voltage and the second constant voltage have a constant potential difference, and a voltage interval of the potential difference is 10 millivolts to 1000 millivolts.
In addition, in the glucose concentration information collecting device according to the present disclosure, optionally, the temperature sensing module is a thermistor. Thus, the temperature sensing module can have high sensitivity.
In addition, in the glucose concentration information collecting device according to the present disclosure, optionally, the low-pass filter module is a first-order low-pass filter. In this case, high-frequency noise in the voltage analog signal converted by the amplifying module can be filtered, interference of the high-frequency noise on the signal input to the analog-to-digital conversion module is reduced, and measurement accuracy can be improved.
In addition, in the glucose concentration information collecting device according to the present disclosure, optionally, the micro-processing unit module includes a serial port communication module configured to be capable of burning a program on the collecting device and calibrating current measurement accuracy and temperature measurement accuracy of the collecting device at the time of production. In this case, when factory calibration is performed, serial communication may be used to perform analysis to determine whether the accuracy of the current measurement and the temperature measurement of the acquisition device meets the calibration requirements.
In addition, in the glucose concentration information collecting device related to the disclosure, optionally, the micro-processing unit module further includes a bluetooth communication module, and the bluetooth communication module is configured to transmit collected data information. In this case, the collected data information can be received wirelessly through the bluetooth communication module and transferred to the data analysis module. Thus, the concentration information of glucose can be obtained by a data analysis module such as a mobile phone or a computer.
In addition, in the glucose concentration information collecting apparatus according to the present disclosure, optionally, the first analog-to-digital conversion module has a reference voltage. In this case, more accurate data can be obtained by selecting different measurement ranges according to the reference voltage and different gain coefficients.
According to the present disclosure, a glucose concentration information collecting device having three electrodes, which has strong interference immunity, high reaction sensitivity, and portability, can be provided.
Drawings
The present disclosure will now be explained in further detail by way of example only with reference to the accompanying drawings, in which:
fig. 1 is an exemplary block diagram illustrating an acquisition device according to an embodiment of the present disclosure.
Fig. 2 is a circuit diagram showing part of elements of the acquisition device according to the embodiment of the present disclosure.
Fig. 3 is a circuit diagram illustrating an amplifying module according to an embodiment example of the present disclosure.
Fig. 4 is a circuit diagram illustrating a low-pass filtering module according to an embodiment example of the present disclosure.
Fig. 5 is a circuit diagram showing a constant voltage chip according to an embodiment example of the present disclosure.
Fig. 6 is a circuit diagram illustrating a temperature acquisition module according to an embodiment example of the present disclosure.
Reference numerals:
1 of the collection device …,
the device comprises a 10 … current sensing module, a 20 … amplifying module, a 30 … low-pass filtering module, a 40 … first analog-to-digital conversion module, a 50 … micro-processing unit module, a 60 … temperature acquisition module, a 70 … power module, an 80 … constant voltage chip and a 90 … second analog-to-digital conversion module.
Detailed Description
Hereinafter, preferred embodiments of the present disclosure will be described in detail with reference to the accompanying drawings. In the following description, the same members are denoted by the same reference numerals, and overlapping description thereof is omitted. In addition, the drawings are schematic, and the ratio of the sizes of the components to each other, the shapes of the components, and the like may be different from actual ones.
It should be noted that the terms "comprises" and "comprising," and any variations thereof, in this disclosure, such as a process, method, system, article, or apparatus that comprises or has a list of steps or elements is not necessarily limited to those steps or elements expressly listed or inherent to such process, method, article, or apparatus, but may include or have other steps or elements not expressly listed or inherent to such process, method, article, or apparatus.
In addition, headings and the like referred to in the following description of the disclosure are not intended to limit the disclosure or scope thereof, but rather are merely indicative of reading. Such subtitles are not to be understood as being used for segmenting the content of the article, nor should the content under the subtitle be limited only to the scope of the subtitle.
The present disclosure relates to a glucose concentration information acquisition device having three electrodes. The "glucose concentration information collecting device having three electrodes" may be simply referred to as a "glucose collecting device", and hereinafter simply referred to as a "collecting device". The glucose concentration information acquisition device with three electrodes can acquire the glucose concentration with high sensitivity and relatively accuracy.
When glucose in blood sugar reacts under the action of enzyme, the concentration of ions changes and weak current is generated, and at the moment, the concentration of glucose in tissue fluid or blood can be obtained by collecting current and temperature and calculating the collected data through a computer. In some examples, "glucose concentration information" may refer to the current and temperature required in obtaining glucose concentration.
The acquisition device according to the present embodiment will be described below with reference to the drawings.
Fig. 1 is a block diagram showing an acquisition device 1 according to an embodiment of the present disclosure.
In some examples, the collection device 1 may be used to collect weak currents that are generated by blood glucose when a reaction occurs. In some examples, the weak current may range from 1 to 100nA.
In some examples, as shown in fig. 1, the acquisition device 1 may include a current sensing module 10, an amplifying module 20, a low pass filtering module 30, and a first analog-to-digital conversion module 40. The current sensing module 10 may be used to implant into the subcutaneous tissue of a user and generate an electrical current. The amplifying module 20 may be configured to receive the current signal output from the current sensing module 10 and convert and amplify it to a larger voltage. The low pass filtering module 30 may be configured to filter high frequency noise of the signal output by the amplifying module 20. The first analog-to-digital conversion module 40 may be configured to convert an analog signal to a digital signal.
In some examples, the acquisition device 1 may further include a micro-processing unit module 50 and a temperature acquisition module 60 (described later). The microprocessor unit module 50 may be configured to control the frequency of acquisition of the glucose concentration information. In some examples, the microprocessor unit module 50 may also be used to control the first analog-to-digital conversion module 40. The micro-processing unit module 50 may control the first analog-to-digital conversion module 40 to be in an off state so that the acquisition device 1 is in a low power consumption state. As a result, the energy storage of the acquisition device 1 can be increased and the service life thereof can be increased.
In some examples, the acquisition device 1 may be saved for up to 12 months. In some examples, the acquisition device 1 may also continue to operate in the human body for 14 days. In some examples, the body surface temperature of the human body may be acquired by temperature acquisition module 60. In some examples, when the temperature acquisition module acquires 60 the body surface temperature of the human body, the relevant data may be transmitted to the micro-processing unit module 50 for processing.
Fig. 2 is a circuit diagram showing part of elements of the acquisition device 1 according to the embodiment of the present disclosure.
In some examples, as described above, the current sensing module 10 may be used to implant into the subcutaneous tissue of a user and generate an electrical current. In some examples, current sensing module 10 may collect current using three electrodes. As shown in fig. 2, 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 current is detected.
In some examples, the working electrode WE may be provided with a glucose enzyme. In this case, the glucose enzyme may be used to react with glucose in tissue fluid/blood and produce ionic changes in tissue/blood. This can generate a weak current between the working electrode WE and the tissue fluid/blood.
In some examples, the current value of working electrode WE may range from 1 to 100nA. Thus, a weak current in the blood glucose reaction can be collected relatively accurately. However, examples of the present disclosure are not limited thereto, and the current value of the working electrode WE may range from about 1 to 100nA. For example, the current value range of the working electrode WE may also have small-amplitude fluctuations.
In some examples, the reference electrode RE may be held at a constant potential difference with the working electrode WE (described later). In this case, a stable reaction between the glucose and the glucose can occur and thus a stable current can be generated. Thus, the glucose concentration information can be reflected by the current information. Generating a stable current is also beneficial to improving the accuracy of the acquisition of glucose concentration information.
In some examples, the counter electrode CE may form a loop with the working electrode WE. This enables the current sensor module 10 to transmit current data.
In some examples, the reference electrode RE may be sequentially connected in series with the third resistor R1 and the inverting input terminal of the first operational amplifier U1, and the non-inverting input terminal of the first operational amplifier U1 may input the first constant voltage.
In some examples, the working electrode WE may be connected to an inverting input terminal of a second operational amplifier U2 (described later), and an non-inverting output terminal of the second operational amplifier U2 may input a second constant voltage.
Fig. 3 is a circuit diagram illustrating an amplifying module 20 according to an embodiment example of the present disclosure.
In some examples, amplification module 20 may be used to convert and amplify the current signal to a larger voltage. In some examples, amplification module 20 may amplify the weak current measured by working electrode WE to a larger voltage. In some examples, the voltage converted and output by the amplifying module 20 may be 0 to 2V.
In some examples, the amplification module 20 may have a second operational amplifier U2 (see fig. 3).
In some examples, the inverting input of the second operational amplifier U2 may be connected to the working electrode WE. In this case, when the circuit is stable, the voltage input to the non-inverting input terminal of the second operational amplifier U2 is the voltage of the inverting input terminal of the second operational amplifier U2 due to the "weak short and weak broken" characteristic of the operational amplifier. In other words, the voltage input at the non-inverting input terminal of the second operational amplifier U2 is equal to the voltage of the working electrode WE of the current sensing module 10.
In some examples, the inverting input of the second operational amplifier U2 may be connected in turn to the resistor R2, the output of the second operational amplifier U2, and the low pass filter module 30.
Fig. 4 is a circuit diagram illustrating the low-pass filtering module 30 according to an embodiment example of the present disclosure.
In some examples, the low pass filter module 30 may connect the output of the second operational amplifier U2 and the first analog to digital conversion module 40. In some examples, the low-pass filtering module 30 may receive the signal output at the output end of the second operational amplifier U2, and transmit the signal to the first analog-to-digital conversion module 40 after the filtering process.
Referring to fig. 3, in some examples, the non-inverting input voltage of the second operational amplifier U2 may be VDD2 and the measured weak current I may be a current flowing through the resistor R2. In this case, the output voltage U of the second operational amplifier U2 can be obtained by the equation, u=i×r 2 +VDD2。
In some examples, low pass filter module 30 may be a first order low pass filter. In some examples, low pass filter module 30 may be formed from a combination of resistor R3 and capacitor C3. (see FIG. 4)
In some examples, the low pass filter may filter high frequency noise of the signal, thereby improving immunity of the signal and reducing the likelihood of signal oscillations due to high frequency noise doping. And reduces the effect of high frequency noise on the input signal of the first analog-to-digital conversion module 40.
In some examples, the second operational amplifier may be a transimpedance amplifier. The inverting input of the second operational amplifier U2 may be connected to its output via a third resistor R2. As shown in fig. 3, the non-inverting input terminal of the second operational amplifier U2 inputs a voltage VDD2, which can be used as the reference voltage of the second operational amplifier U2. In some examples, the voltage of the working electrode WE may be the input voltage of the non-inverting input terminal of the second operational amplifier U2. That is, the voltage of the working electrode WE may be VDD2. In this case, by amplifying the voltage of the working electrode WE by the second operational amplification module 20, the intensity of the voltage signal output by the second operational amplification module 20 can be increased so that the sensor current can be measured by the first analog-to-digital conversion module 40 later.
In some examples, the first analog-to-digital conversion module 40 may convert an analog signal to a digital signal. Specifically, after receiving the sensing voltage outputted by the amplifying module 20 and subjected to the filtering process via the low-pass filtering module 30, the ADC value of the voltage is collected by the first analog-to-digital conversion module 40, and the value of the sensor current can be obtained according to ohm's law. In this case, the micro processing unit module 50 can receive and process the digital signal output from the first analog-to-digital conversion module 40.
Fig. 5 is a circuit diagram showing a constant voltage chip 80 according to an embodiment example of the present disclosure.
In some examples, the acquisition device 1 may further comprise a power supply module 70. In some examples, the power supply module may be configured with a constant voltage chip 80. In some examples, the power module 70 may provide the battery voltage VDD1 for the constant voltage chip 80. In some examples, the output terminal of the constant voltage chip 80 may be sequentially connected in series with the first resistor R4, the second resistor R5, and the ground terminal (see fig. 5). After the battery voltage VDD1 is input through the input terminal of the constant voltage chip 80, 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, so that a stable voltage, such as VDD2 and VDD3, can be formed across the first resistor R4, and the voltage configuration can range from 10mV to 1000mV.
In some examples, the output voltage of the constant voltage chip 80 may form a first constant voltage at the first resistor R4, and a second constant voltage between the first resistor R4 and the second resistor R5. In this case, the constant voltage chip 80 in the power module can maintain the stability of the circuit voltage to maintain the stable voltage of the three electrodes, thereby reducing the possibility that the unstable voltage interferes with the three-electrode measurement current and improving the measurement accuracy.
In some examples, the first constant voltage may be VDD2 and the second constant voltage may be VDD3. In some examples, the first constant voltage and the second constant voltage may have a constant potential difference. In some examples, the voltage interval of the potential difference may be 10 millivolts to 1000 millivolts
Fig. 6 is a circuit diagram illustrating a temperature acquisition module 60 according to an embodiment example of the present disclosure.
In some examples, the temperature acquisition module 60 may include a temperature sensing module and a second analog-to-digital conversion module 90, and the second analog-to-digital conversion module 90 may be coupled to the temperature sensing module. The temperature sensing module may communicate the voltage VDD2 via a resistor R6.
In some examples, the temperature sensing module may be a thermistor R7.
In some examples, the resistance value of the thermistor may change with a change in temperature. The resistance of the temperature sensing module (i.e., the thermistor R7) will also change when the ambient temperature changes. In this case, when the collecting device 1 collects the glucose temperature of the human body, the body surface temperature of the human body may be collected by measuring the resistance value of the temperature sensing module (i.e., the thermistor R7).
In some examples, the accuracy of the resistor R6 in the temperature acquisition module 60 may be up to one thousandth. Therefore, the temperature acquisition module 60 can be accurate in the process of acquiring the ambient temperature, and the accuracy of measuring the glucose concentration information is improved.
In some examples, the analog-to-digital conversion value of the voltage of the thermistor R7 may be collected by the second analog-to-digital conversion module 90, the voltage of the thermistor R7 may be calculated, the resistance value of the thermistor R7 may be calculated through the voltage division relationship between the resistor R6 and the thermistor R7, and finally the temperature value of the thermistor R7 may be obtained by querying a resistance value-temperature relationship table of the thermistor R7.
In some examples, a sensor that collects current may be formed by three electrodes and modules cooperating with each other. The sensor may infer the concentration of glucose at the time of collection from the current collected. In some examples, the temperature of the sensor and the sensitivity of the sensor may be proportional. Therefore, whether the sensitivity of the sensor meets the requirement can be judged by measuring the temperature of the sensor.
In some examples, when the measurement is started by the sensor, since the current sensing module 10 is inserted into subcutaneous tissue of the user, after the body surface temperature of the human body is measured by the temperature sensing module, the sensor temperature implanted subcutaneously can be calculated based on the body surface temperature of the human body, and further, whether the sensitivity of the sensor meets the standard requirement can be judged by the sensor temperature. In this case, the sensitivity of the sensor can be monitored in real time by the temperature sensing module and fine-tuned according to the feedback of the sensitivity so as to meet the standard requirements. Thereby, the accuracy of the sensor measuring the current can be improved.
In some examples, the first analog-to-digital conversion module 40 may have a reference voltage. The first analog to digital conversion module 40 may have different gain coefficients. In some examples, a particular measurement range may be obtained by setting a reference voltage and a particular gain factor, in which case different measurement ranges may be selected based on the reference voltage and different gain factors, thereby enabling accurate sensor current data to be obtained.
In some examples, the sensor current may be measured by a current stepper test. When the current gear (current range) of the measured sensor current is too large or too small, the appropriate gear may be switched to measure a more accurate current. The following is a description of the measurement of sensor current using the step test method.
In some examples, a reference voltage may be set internal to the first analog-to-digital conversion module 40, with the input voltage range being equal to the reference voltage divided by the gain of the first analog-to-digital conversion module 40. In this case, when the reference voltage is fixed, the test gear of the current can be switched by switching the gain of the first analog-to-digital conversion module 40. In some examples, the number of current test steps may be 4. Thus, the sensor current measurement range can be configured as 4 different ranges.
In some examples, when measuring the sensor current, the internal reference voltage of the first analog-to-digital conversion module 40 may be set, and the first analog-to-digital conversion module 40 may be set to have a plurality of gains, where the gains are adjusted to be the first bit, and the current range is the first gear, that is, the initial state is to measure the sensor current through the first range. When the output current of the sensor is smaller than the first measuring range, the current value is directly output. When the output sensor current is greater than the first range, the gain of the first analog-to-digital conversion module 40 is switched to switch the gear of the current measurement range, at this time, the current measurement range is switched to the second range, when the output current is still greater than the range of the second range, the above operation is repeated and switched to the third range again, and so on until the measured sensor current is in the proper range. In this case, by outputting the current value in an appropriate gear, it is possible to reduce the error of measurement and reduce the load of the first analog-to-digital conversion module 40. Thereby, the accuracy of measuring the sensor current can be improved.
In some examples, the internal reference voltage of the channel chip of the first analog-to-digital conversion module 40 may be 0.6V, and the gains of the first analog-to-digital conversion module 40 may be set to 4, 2, 1, and 1/2. In some examples, the input voltage range may be equal to the reference voltage divided by the first analog-to-digital conversion module 40 gain, and the input voltage range may be 0-0.15V, 0-0.3V, 0-0.6V, and 0-1.2V. The resistance value of R2 is set to be 10MΩ, and the input voltage is divided by the resistance value of R2, so as to obtain the corresponding current range. In this case, it can be known that the current measurement ranges of the first analog-to-digital conversion module 40 are 0 to 15nA, 0 to 30nA, 0 to 60nA, and 0 to 120nA, respectively.
When the current test is started, the software may configure the first analog-to-digital conversion module 40 to select 0.6V as the reference voltage, and select the gain of the first analog-to-digital conversion module 40 to select 4, so as to obtain the current measurement range of the first analog-to-digital conversion module 40 in the first gear test: 0 to 15nA. After the first analog-to-digital conversion module 40 completes current collection, the magnitude of the current is determined, for example, whether the sensor current is smaller than the measurement range of the first-gear current by 0-15 nA is determined, and if the sensor current is smaller than 15nA, the current value is normally output. If the sensor current is greater than 15nA, the second gear retest current is switched. In the second-gear test, the software may configure the first analog-to-digital conversion module 40 to select 0.6V as the reference voltage, and switch the gain of the first analog-to-digital conversion module 40 to 2, so that the current measurement range of the first analog-to-digital conversion module 40 in the second-gear test may be obtained: 0 to 30nA. After the second gear is switched, the current is measured again and whether the sensor current is smaller than the measuring range of the second gear current is judged. Similarly, when the sensor current does not exceed the current measurement range of the first analog-to-digital conversion module 40, a current value is output, otherwise, the sensor current needs to be measured by switching a larger range again.
However, examples of the present disclosure are not limited thereto, and in other examples, a relatively large range may be used to measure the sensor current first, and when the measurement of the current of the sensor is significantly smaller than the range of the range, the range may be switched to one gear smaller range. And the like until a proper measuring range is selected.
In some examples, the micro-processing unit module 50 may also include a serial port communication module. In some examples, the acquisition device 1 may be programmed at the time of production through a serial communication module. In some examples, the current measurement accuracy and the temperature measurement accuracy of the acquisition device 1 may also be calibrated by the serial communication module. Thus, the accuracy of collecting glucose concentration data can be improved.
In some examples, the micro-processing unit module 50 may also include a bluetooth communication module. In some examples, the bluetooth communication module may transmit the collected data information. In this case, after the bluetooth communication module and the data analysis module such as a mobile phone or a computer are matched, the collected data information may be wirelessly received through the bluetooth communication module and transmitted to the data analysis module. Thus, the concentration information of glucose can be checked by the data analysis module.
While the disclosure has been described in detail in connection with the drawings and examples, it is to be understood that the foregoing description is not intended to limit the disclosure in any way. Modifications and variations of the present disclosure may be made as desired by those skilled in the art without departing from the true spirit and scope of the disclosure, and such modifications and variations fall within the scope of the disclosure.
Claims (9)
1. A glucose concentration information acquisition device with three electrodes, which is characterized in that:
the blood glucose sensor comprises a current sensing module, an amplifying module, a low-pass filtering module, a first analog-to-digital conversion module, a micro-processing unit module and a temperature acquisition module, wherein the current sensing module is configured to be implanted into subcutaneous tissue of a user and generate current in tissue fluid or blood in the subcutaneous tissue, the current sensing module comprises a working electrode, a reference electrode and a counter electrode, the working electrode is provided with a glucose enzyme, the glucose enzyme reacts with glucose in the tissue fluid or blood to generate weak current, a constant potential difference is kept between the reference electrode and the working electrode to promote the glucose enzyme to react with the glucose, and the counter electrode is configured to form a loop with the working electrode; the amplifying module is connected with the working electrode and is configured to receive an analog signal of weak current from the working electrode and perform operational amplification processing on the analog signal; the low-pass filtering module is connected with the amplifying module and is configured to filter high-frequency noise in the analog signal; the first analog-to-digital conversion module is connected with the low-pass filtering module and converts an analog signal which passes through the low-pass filtering module and is in a measuring range into a digital signal based on a gain coefficient; the temperature acquisition module comprises a temperature sensing module and a second analog-to-digital conversion module connected with the temperature sensing module, wherein the temperature sensing module is configured to measure the body surface temperature of a user and obtain the temperature of the working electrode based on the body surface temperature, judge whether the sensitivity of the working electrode meets the standard requirement or not through the temperature of the working electrode and perform fine adjustment according to the feedback of the sensitivity so that the sensitivity meets the standard requirement; when the measurement is started through the sensor, as the current sensing module is inserted into subcutaneous tissue of a user, after the temperature of the body surface of a human body is measured through the temperature sensing module, the temperature of the sensor implanted under the skin is calculated based on the temperature of the body surface of the human body, whether the sensitivity of the sensor meets the standard requirement is judged through the temperature of the sensor, the sensitivity of the sensor is monitored in real time through the temperature sensing module, and fine adjustment is carried out according to feedback of the sensitivity so that the sensitivity meets the standard requirement; the micro-processing unit module is configured to control the acquisition frequency of the current acquisition device, the micro-processing unit module is configured to enable the current acquisition device to be in a low-power consumption state by closing the first analog-to-digital conversion module, and the micro-processing unit module is configured to control the gain coefficient of the first analog-to-digital conversion module based on the magnitude of the analog signal so as to adjust the measuring range of the first analog-to-digital conversion module.
2. The glucose concentration information collection device according to claim 1, wherein:
the power supply module is configured to provide battery voltage, the input end of the constant voltage chip is connected with the battery voltage, the output end of the constant voltage chip is sequentially connected with a first resistor, a second resistor and a ground end in series, a first constant voltage is formed between the output end of the constant voltage chip and the first resistor, and a second constant voltage is formed between the first resistor and the second resistor.
3. The glucose concentration information collection device according to claim 2, wherein:
the reference electrode is sequentially connected with the third resistor and the inverting input end of the first operational amplifier in series, and the non-inverting input end of the first operational amplifier inputs the first constant voltage.
4. The glucose concentration information collection device according to claim 2, wherein:
the working electrode is connected with the inverting input end of the second operational amplifier, and the non-inverting output end of the second operational amplifier inputs the second constant voltage.
5. The glucose concentration information collection device according to claim 2, wherein:
the first constant voltage and the second constant voltage have a constant potential difference, and the voltage interval of the potential difference is 10 millivolts to 1000 millivolts.
6. The glucose concentration information collection device according to claim 1, wherein:
the temperature sensing module is a thermistor.
7. The glucose concentration information collection device according to claim 1, wherein:
the low-pass filter module is a first-order low-pass filter; the micro-processing unit module comprises a serial communication module, and the serial communication module is configured to burn a program for the acquisition device and calibrate the current measurement precision and the temperature measurement precision of the acquisition device during production.
8. The glucose concentration information collection device according to claim 1 or 7, wherein:
the micro-processing unit module further comprises a Bluetooth communication module, and the Bluetooth communication module is configured to transmit collected data information.
9. The glucose concentration information collection device according to claim 1, wherein:
the first analog-to-digital conversion module has a reference voltage.
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| CN202210286393.1A CN114778642B (en) | 2022-03-23 | 2022-03-23 | Glucose concentration information acquisition device with three electrodes |
| CN202410082763.9A CN117770808A (en) | 2022-03-23 | 2022-03-23 | Low-power consumption glucose concentration information acquisition device |
| CN202410083402.6A CN117898719A (en) | 2022-03-23 | 2022-03-23 | Glucose concentration information acquisition device |
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| CN117770808A (en) | 2024-03-29 |
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