WO2022000313A1 - 恒电位电路、血糖测量电路及设备 - Google Patents

恒电位电路、血糖测量电路及设备 Download PDF

Info

Publication number
WO2022000313A1
WO2022000313A1 PCT/CN2020/099431 CN2020099431W WO2022000313A1 WO 2022000313 A1 WO2022000313 A1 WO 2022000313A1 CN 2020099431 W CN2020099431 W CN 2020099431W WO 2022000313 A1 WO2022000313 A1 WO 2022000313A1
Authority
WO
WIPO (PCT)
Prior art keywords
circuit
voltage
mcu
inverting input
electrochemical sensor
Prior art date
Application number
PCT/CN2020/099431
Other languages
English (en)
French (fr)
Inventor
赵博
张军
杨宁
唐海
杨长贵
常子怡
李祝昊
吴斌
Original Assignee
浙江大学
Oppo广东移动通信有限公司
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 浙江大学, Oppo广东移动通信有限公司 filed Critical 浙江大学
Priority to PCT/CN2020/099431 priority Critical patent/WO2022000313A1/zh
Priority to CN202080099953.1A priority patent/CN115484868A/zh
Publication of WO2022000313A1 publication Critical patent/WO2022000313A1/zh

Links

Images

Classifications

    • 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
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis

Definitions

  • Embodiments of the present application relate to the field of circuits, and more particularly, to potentiostatic circuits, blood glucose measurement circuits, and devices.
  • Three-electrode electrochemical sensors are widely used in blood glucose measurement.
  • Three-electrode electrochemical sensors include a working electrode (Work Electrode, WE), a reference electrode (Reference Electrode, RE) and a counter electrode (Counter Electrode, CE).
  • the working principle of the three-electrode electrochemical sensor is: by adding a control voltage between WE and RE.
  • the WE with glucose oxidase undergoes an electrochemical reaction to generate a current proportional to the glucose concentration, and the CE collects and outputs the current signal.
  • the glucose concentration has a certain relationship with the current signal, and the glucose concentration and the blood glucose concentration are also related. There is a certain relationship, based on this, the blood glucose concentration can be calculated by analyzing the current signal.
  • the potentiostatic circuit is a crucial device in the blood glucose measurement process.
  • the embodiments of the present application provide a potentiostatic circuit, a blood glucose measurement circuit, and a device, so that the voltage bias of WE of the three-electrode electrochemical sensor and RE of the three-electrode electrochemical sensor is constant, so that the voltage of the three-electrode electrochemical sensor can be maintained. Chemical stability, so as to output a stable current signal.
  • a constant potential circuit comprising: a first amplifying circuit, a second amplifying circuit and a voltage dividing circuit.
  • the non-inverting input terminal of the first amplifier circuit is connected to the input voltage
  • the non-inverting input terminal of the second amplifier circuit is connected to the input voltage through a voltage divider circuit
  • the inverting input terminal of the first amplifier circuit is connected to the working electrode WE of the three-electrode electrochemical sensor.
  • the inverting input terminal of the second amplifier circuit is connected to the reference electrode RE of the three-electrode electrochemical sensor
  • the output terminal of the second amplifier circuit is connected to the counter electrode CE of the three-electrode electrochemical sensor.
  • a negative feedback circuit is arranged between the inverting input end and the output end of the first amplifying circuit, and the output end of the first amplifying circuit is used for outputting a voltage signal.
  • the potentiostatic circuit further includes: a first compensation circuit. Wherein, the inverting input end of the first amplifier circuit is connected to WE through the first compensation circuit.
  • the first compensation circuit includes: a first resistor.
  • the negative feedback circuit includes: a second resistor.
  • the potentiostatic circuit further includes: a second compensation circuit.
  • the second compensation circuit is connected in parallel with the second resistor.
  • the second compensation circuit includes: a first capacitor.
  • the potentiostatic circuit further includes: a filter circuit connected to the output end of the first amplifying circuit.
  • the filter circuit is a first-order LC filter circuit.
  • the potentiostatic circuit further includes: a third compensation circuit.
  • the third compensation circuit is arranged between the inverting input terminal and the output terminal of the second amplifying circuit.
  • the third compensation circuit includes: a second capacitor.
  • the voltage dividing circuit includes: a third resistor and a fourth resistor connected in series. One end of the third resistor is connected to the input voltage, the other end is connected to the non-inverting input terminal of the second amplifier circuit, one end of the fourth resistor is connected to the non-inverting input terminal of the second amplifier circuit, and the other end is grounded.
  • the input voltage is the voltage produced by the DAC.
  • the DAC is integrated on the MCU.
  • a blood glucose measurement circuit comprising: an MCU and the potentiostatic circuit provided by the first aspect or a possible implementation manner of the first aspect.
  • the MCU is electrically connected to the potentiostatic circuit.
  • a DAC is integrated on the MCU, and the DAC generates the input voltage of the potentiostatic circuit.
  • an ADC is also integrated on the MCU, and the ADC is used to obtain the output voltage of the potentiostatic circuit.
  • a communication unit is further integrated on the MCU, and the communication unit is used to realize communication between the MCU and other devices.
  • the communication unit communicates in an NFC manner.
  • a blood glucose measurement circuit comprising: a three-electrode electrochemical sensor and a potentiostatic circuit as provided in the first aspect or a possible implementation manner of the first aspect.
  • a blood glucose measuring device comprising: a three-electrode electrochemical sensor, a micro-control unit MCU, and the potentiostatic circuit provided as the first aspect or a possible implementation manner of the first aspect.
  • the MCU is electrically connected to the potentiostatic circuit.
  • a DAC is integrated on the MCU, and the DAC generates the input voltage of the potentiostatic circuit.
  • an ADC is also integrated on the MCU, and the ADC is used to obtain the output voltage of the potentiostatic circuit.
  • a communication unit is further integrated on the MCU, and the communication unit is used to realize communication between the MCU and other devices.
  • the communication unit communicates in an NFC manner.
  • the voltage bias of the WE of the three-electrode electrochemical sensor and the RE of the three-electrode electrochemical sensor is made constant, so that the electrochemical stability of the three-electrode electrochemical sensor can be maintained, and a stable current signal can be output, and Since the RE of the three-electrode electrochemical sensor is connected to the inverting input terminal of the second amplifying circuit, the current can be prevented from flowing through the RE, and the polarization of the RE can be prevented and the solution potential will be changed.
  • the potentiostatic circuit, MCU, DAC, ADC, and NFC in the blood glucose measurement device can be partially or fully integrated to achieve miniaturization of the blood glucose measurement device.
  • FIG. 1 is a schematic structural diagram of a constant potential circuit 10 provided by an embodiment of the present application.
  • FIG. 2 is a schematic structural diagram of a constant potential circuit 10 provided by another embodiment of the present application.
  • FIG. 3 is a schematic diagram of a blood glucose detection circuit 30 provided by an embodiment of the present application.
  • FIG. 4 is a schematic diagram of a blood glucose detection circuit 40 provided by an embodiment of the present application.
  • FIG. 5 is a schematic diagram of a blood glucose measuring device 50 provided by an embodiment of the present application.
  • WE also known as the research electrode
  • the material of the working electrode can be either solid or liquid.
  • Commonly used working electrode materials are: glassy carbon electrode, platinum (Pt), gold (Au), silver (Ag), lead (Pb), conductive glass (ITO), mercury (Hg), etc.
  • CE is also called auxiliary electrode.
  • CE and WE form a loop, so that the WE is powered on to ensure that the studied reaction takes place on the working electrode.
  • the gas evolution reaction or the reverse reaction of the WE reaction can be arranged on the CE, so that the composition of the electrolyte remains unchanged.
  • the performance of the counter electrode generally does not affect the reaction on WE.
  • the potential of CE will change with the change of the current. If the current passing through the measurement process is large, the CE itself will be polarized at this time, so it cannot be used as a standard for potential comparison, which will easily cause measurement errors. In order to keep the potential of CE stable, RE must be used, otherwise it will affect the accuracy of the measurement.
  • the potential of RE is not affected by changes in the composition of the electrolyte and has a constant value.
  • the present application provides a potentiostatic circuit, a blood glucose measurement circuit and a device.
  • the potentiostatic circuit, the blood glucose measuring circuit and the device according to the embodiments of the present application will be described in detail below with reference to FIGS. 1 to 5 .
  • FIG. 1 is a schematic structural diagram of a constant potential circuit 10 provided by an embodiment of the present application.
  • the constant potential circuit 10 includes: a first amplifying circuit 11 , a second amplifying circuit 12 and a voltage dividing circuit 13 .
  • the non-inverting input terminal of the first amplifier circuit 11 is connected to the input voltage AN0
  • the non-inverting input terminal of the second amplifier circuit 12 is connected to the input voltage AN0 through the voltage divider circuit 13
  • the inverting input terminal of the first amplifier circuit 11 is connected to the three electrodes.
  • the WE of the electrochemical sensor is connected, the inverting input terminal of the second amplifier circuit 12 is connected to the RE of the three-electrode electrochemical sensor, and the output terminal of the second amplifier circuit 12 is connected to the CE of the three-electrode electrochemical sensor; the first amplifier circuit 11 A negative feedback circuit is arranged between the inverting input terminal and the output terminal of the first amplifier circuit 11 , and the output terminal of the first amplifying circuit 11 is used to output the voltage signal AN1 .
  • the first amplifier circuit 11 is provided with a negative feedback circuit, so that the voltages of the non-inverting input terminal and the inverting input terminal of the first amplifier circuit 11 are the same.
  • the inverting input terminal of 11 is connected to the WE of the three-electrode electrochemical sensor. Therefore, the voltage of the WE of the three-electrode electrochemical sensor and the non-inverting input terminal of the first amplifier circuit 11 can be the same finally.
  • the second amplifier circuit 12 forms a negative feedback circuit through electrodes, so that the voltages of the non-inverting input terminal and the reverse input terminal of the second amplifier circuit 12 are the same, and the inverting input terminal of the second amplifier circuit 12 is connected to the RE of the three-electrode electrochemical sensor. , therefore, the voltage of RE of the three-electrode electrochemical sensor and the non-inverting input terminal of the second amplifying circuit 12 can be the same finally.
  • the non-inverting input terminal of the first amplifier circuit 11 is connected to the input voltage AN0, that is, the voltage of the non-inverting input terminal of the first amplifier circuit 11 is the input voltage AN0.
  • the non-inverting input terminal of the second amplifier circuit 12 is connected to the input voltage AN0 through the voltage divider circuit 13 , so that the voltage of the non-inverting input terminal of the second amplifier circuit 12 is the divided voltage, eg AN0/2.
  • the voltages of WE of the three-electrode electrochemical sensor and the non-inverting input terminal of the first amplifier circuit 11 are the same, and the voltages of RE of the three-electrode electrochemical sensor and the non-inverting input terminal of the second amplifier circuit 12 are the same, that is, the three-electrode electrochemical sensor has the same voltage.
  • the voltage of the WE of the chemical sensor is AN0
  • the voltage of the RE of the three-electrode electrochemical sensor is AN0/2
  • the negative feedback circuit is also used to convert the current signal generated by the three-electrode electrochemical sensor into a voltage signal.
  • the voltage bias of the WE of the three-electrode electrochemical sensor and the RE of the three-electrode electrochemical sensor can be kept constant, so that the electrochemical stability of the three-electrode electrochemical sensor can be maintained, and then the three-electrode electrochemical sensor can be maintained. Output stable current signal.
  • the RE of the three-electrode electrochemical sensor is connected to the inverting input end of the second amplifying circuit, the current can be prevented from flowing through the RE, and the polarization of the RE can prevent the solution potential from changing.
  • FIG. 2 is a schematic structural diagram of the constant potential circuit 10 provided by another embodiment of the present application. , see Figure 2 for details.
  • the first amplifier circuit 11 includes an amplifier 111 and a negative feedback circuit disposed between an inverting input terminal and an output terminal of the first amplifier circuit 11 .
  • the amplifier 111 is a low-power operational amplifier with ultra-low input bias current, and the model can be LPV812.
  • the negative feedback circuit provided between the inverting input terminal and the output terminal of the first amplifier circuit 11 includes: a second resistor 112 .
  • the second resistor shown in FIG. 2 is only an implementable manner of the negative feedback circuit.
  • the negative feedback circuit may include: a plurality of resistors connected in series or in parallel, and the application does not limit the negative feedback circuit.
  • the relationship between the output voltage AN1 and the input voltage AN0, the resistance value of the second resistor 112 and the output current on WE is as follows:
  • one end of the first amplifying circuit 11 is further connected to a power supply through P3, and the other end is grounded.
  • the second amplifier circuit 12 is an amplifier.
  • the amplifier is a low-power operational amplifier with ultra-low input bias current
  • the model can be LPV812.
  • one end of the second amplifying circuit 12 is connected to the power supply through P3, and the third capacitor 14 is connected to P3 and the ground for power supply filtering.
  • the potentiostatic circuit 10 further includes: a first compensation circuit; wherein, the inverting input end of the first amplifier circuit 11 is connected to WE through the first compensation circuit.
  • the first compensation circuit includes: a first resistor 15 .
  • the first resistor shown in FIG. 2 is only an implementable manner of the first compensation circuit.
  • the first compensation circuit may include: a plurality of resistors connected in series or in parallel. No restrictions apply.
  • the potentiostatic circuit 10 further includes: a second compensation circuit; wherein, the second compensation circuit is connected in parallel with the second resistor 112 .
  • the second compensation circuit includes: a first capacitor 16 .
  • first capacitor shown in FIG. 2 is only an implementable manner of the second compensation circuit, and this application does not limit the second compensation circuit.
  • the potentiostatic circuit 10 further includes: a filter circuit 17 connected to the output end of the first amplifying circuit 11 .
  • the filtering circuit 17 is used for filtering the output voltage signal, and transmitting the filtered voltage signal to an analog-to-digital converter (Analog Digital Converter, ADC).
  • ADC Analog Digital Converter
  • the ADC is integrated on a microcontroller unit (Microcontroller Unit, MCU) or the ADC and the MCU are separately set.
  • MCU Microcontroller Unit
  • the MCU may be an NHS3152 type MCU.
  • the filter circuit is a first-order LC filter circuit.
  • the first-order LC filter circuit includes: a fifth resistor 171 and a fourth capacitor 172, wherein the fifth resistor 171 is connected to the output terminal of the first amplifying circuit 11 and the output voltage AN1 of the constant potential circuit 10, and the first Four capacitors 172 connect AN1 and ground.
  • the potentiostatic circuit 10 further includes: a third compensation circuit; wherein, the third compensation circuit is provided between the inverting input terminal and the output terminal of the second amplifier circuit 12 .
  • the third compensation circuit includes: a second capacitor 18 .
  • the second capacitor shown in FIG. 2 is only an implementable manner of the third compensation circuit, and this application does not limit the third compensation circuit.
  • the voltage dividing circuit includes: a third resistor 131 and a fourth resistor 132 connected in series; wherein, one end of the third resistor 131 is connected to the input voltage, and the other end is connected to the non-inverting input end of the second amplifying circuit 12, and the first One end of the four-resistor 132 is connected to the non-inverting input end of the second amplifier circuit 12 , and the other end is grounded.
  • the input voltage is a voltage generated by a digital-to-analog converter (DAC).
  • DAC digital-to-analog converter
  • the DAC is integrated on the MCU or the DAC and the MCU are set separately.
  • the compensation circuits included in the constant potential circuit provided by the present application can improve the stability of negative feedback, thereby ensuring that the constant potential circuit can output a stable and reliable voltage Signal.
  • the potentiostatic circuit further includes a filter circuit, etc., so that the accuracy of the output voltage signal can be improved.
  • FIG. 3 is a schematic diagram of a blood sugar detection circuit 30 according to an embodiment of the present application.
  • a DAC and an ADC are integrated on the MCU 31 , wherein the DAC is used to generate the input voltage AN0 of the potentiostatic circuit.
  • the ADC is used to obtain the output voltage of the potentiostatic circuit, and perform analog-to-digital conversion on the output voltage signal to obtain a digital signal, and then the MCU can analyze the digital signal.
  • the glucose concentration corresponds to the output of the sensor corresponding to the digital signal.
  • the current signal has a certain relationship, and the glucose concentration and the blood sugar concentration also have a certain relationship. Based on this, the blood sugar concentration can be calculated by analyzing the digital signal.
  • a relational expression between the blood glucose concentration and the voltage value represented by the digital signal is determined, and the blood glucose concentration is determined based on the relational expression.
  • the relationship between the blood glucose concentration and the voltage value represented by the above digital signal is as follows:
  • the value range of the blood glucose concentration c is [50mg/d, 300mg/d], and the value range of f is [1.064V, 1.247V].
  • a communication unit is further integrated on the MCU, and the communication unit is used to implement communication between the MCU and other devices.
  • the MCU sends the blood glucose concentration obtained by analysis to other devices through the communication unit, such as pushing to the terminal device of the designated user.
  • the communication unit communicates in a near field communication (Near Field Communication, NFC) manner.
  • NFC Near Field Communication
  • the MCU 31 includes an NFC module, which is used to implement communication between the MCU and other devices.
  • the MCU and other devices may also use other wireless methods to communicate.
  • the communication unit may also use other wireless communication methods to communicate with other devices.
  • it may be 2.4 GHz, Bluetooth, ZigBee, Wireless-Fidelity (Wi-Fi), the third generation (3th Generation, 3G) mobile communication technology, the fourth generation (4th Generation, 4G) mobile communication technology, the fifth generation (5th generation) Generation, 5G) mobile communication technology, and subsequently evolved wireless communication technologies, etc., may also be some other wireless communication technologies, which are not limited in this application.
  • the constant potential circuit may be the constant potential circuit shown in FIG. 1 or FIG. 2 , and the explanation about the constant potential circuit may refer to the embodiment shown in FIG. 1 or FIG. 2 , which will not be repeated in this application.
  • the potentiostatic circuit, the MCU31, the DAC, the ADC and the NFC can be partially integrated or fully integrated.
  • the potentiostatic circuit, MCU31, DAC, ADC and NFC can be arranged on one chip to realize the miniaturization of the chip.
  • the blood glucose detection circuit includes a potentiostatic circuit and an MCU, and the potentiostatic circuit can make the voltage bias of the WE of the three-electrode electrochemical sensor and the RE of the three-electrode electrochemical sensor constant, thereby maintaining Based on the electrochemical stability of the three-electrode electrochemical sensor, a stable current signal can be output. Based on this, the blood glucose concentration analyzed by the MCU based on the current signal is more accurate. And because the RE of the three-electrode electrochemical sensor is connected to the inverting input end of the second amplifying circuit, the current can be prevented from flowing through the RE, and the polarization of the RE can prevent the solution potential from changing.
  • the compensation circuits included in the potentiostatic circuit can improve the stability of negative feedback, thereby ensuring that the potentiostatic circuit can output stable and reliable voltage signals.
  • the potentiostatic circuit further includes a filter circuit, etc., so that the accuracy of the output voltage signal can be improved, so that the blood sugar concentration obtained by the MCU analysis based on the current signal is more accurate.
  • FIG. 4 is a schematic diagram of a blood sugar detection circuit 40 provided by an embodiment of the present application.
  • the blood sugar detection circuit 40 includes a three-electrode electrochemical sensor 41 and a potentiostatic circuit.
  • the potentiostatic circuit provides a stable voltage bias between WE and RE, that is, the voltage difference, so that the WE with glucose oxidase reacts electrochemically, thereby generating a current proportional to the glucose concentration, CE collects and outputs the current signal,
  • the current signal is stably amplified by the potentiostatic circuit, converts the current signal into a voltage signal, and then transmits the voltage signal to the ADC integrated on the MCU, so that the ADC is used to obtain the output voltage of the potentiostatic circuit, and the output voltage signal is processed. Analog-to-digital conversion to get a digital signal.
  • the constant potential circuit may be the constant potential circuit shown in FIG. 1 or FIG. 2 , and the explanation about the constant potential circuit may refer to the embodiment shown in FIG. 1 or FIG. 2 , which will not be repeated in this application.
  • the blood glucose detection circuit includes a three-electrode electrochemical sensor and a potentiostatic circuit, and the potentiostatic circuit can make the voltage bias of the three-electrode electrochemical sensor WE and the three-electrode electrochemical sensor RE constant. , so that the electrochemical stability of the three-electrode electrochemical sensor can be maintained, and then a stable current signal can be output. And because the RE of the three-electrode electrochemical sensor is connected to the inverting input end of the second amplifying circuit, the current can be prevented from flowing through the RE, and the polarization of the RE can prevent the solution potential from changing.
  • the compensation circuits included in the potentiostatic circuit can improve the stability of negative feedback, thereby ensuring that the potentiostatic circuit can output stable and reliable voltage signals.
  • the potentiostatic circuit further includes a filter circuit, etc., so that the accuracy of the output voltage signal can be improved.
  • FIG. 5 is a schematic diagram of a blood sugar measuring device 50 provided by an embodiment of the present application.
  • the blood sugar measuring device 50 includes a three-electrode electrochemical sensor 41 , a potentiostatic circuit and an MCU 31 .
  • the ADC integrated on the MCU31 can provide the input voltage for the constant potential circuit.
  • the potentiostatic circuit provides a stable voltage bias between WE and RE, so that WE with glucose oxidase undergoes an electrochemical reaction, thereby generating a current proportional to the glucose concentration.
  • CE collects and outputs the current signal, which passes through
  • the potentiostatic circuit stably amplifies, converts the current signal into a voltage signal, and then transmits the voltage signal to the ADC integrated on the MCU, so that the ADC is used to obtain the output voltage of the potentiostatic circuit and perform analog-to-digital conversion on the output voltage signal.
  • the digital signal is obtained, and the MCU analyzes the digital signal.
  • there is a certain relationship between the glucose concentration and the current signal output by the sensor corresponding to the digital signal and the glucose concentration and the blood sugar concentration also have a certain relationship. By analyzing this digital signal, the blood glucose concentration can be calculated.
  • a relational expression between the blood glucose concentration and the voltage value represented by the digital signal is determined, and the blood glucose concentration is determined based on the relational expression.
  • the relationship between the blood glucose concentration and the voltage value represented by the above digital signal is as follows:
  • the value range of the blood glucose concentration c is [50mg/d, 300mg/d], and the value range of f is [1.064V, 1.247V].
  • a communication unit is further integrated on the MCU, and the communication unit is used to implement communication between the MCU and other devices.
  • the MCU sends the blood glucose concentration obtained by analysis to other devices through the communication unit, such as pushing to the terminal device of the designated user.
  • the communication unit communicates in an NFC manner.
  • the MCU 31 includes an NFC module, which is used to implement communication between the MCU and other devices.
  • the MCU and other devices may also use other wireless methods to communicate.
  • the communication unit may also use other wireless communication methods to communicate with other devices.
  • it may be 2.4 GHz, Bluetooth, ZigBee, Wi-Fi, 3G, 4G or 5G mobile communication technologies, and subsequently evolved wireless communication technologies, etc., may also be some other wireless communication technologies, which are not limited in this application.
  • the constant potential circuit includes: a first amplifying circuit 11 , a second amplifying circuit 12 and a voltage dividing circuit 13 .
  • the non-inverting input terminal of the first amplifier circuit 11 is connected to the input voltage AN0
  • the non-inverting input terminal of the second amplifier circuit 12 is connected to the input voltage AN0 through the voltage divider circuit 13
  • the inverting input terminal of the first amplifier circuit 11 is connected to the three electrodes.
  • the WE of the electrochemical sensor is connected, the inverting input terminal of the second amplifier circuit 12 is connected to the RE of the three-electrode electrochemical sensor, and the output terminal of the second amplifier circuit 12 is connected to the CE of the three-electrode electrochemical sensor; the first amplifier circuit 11 A negative feedback circuit is arranged between the inverting input end and the output end of the first amplifier circuit 11, and the output end of the first amplifying circuit 11 is used for outputting a voltage signal.
  • the first amplifying circuit 11 is provided with a negative feedback circuit, so that the voltages of the non-inverting input terminal and the inverting input terminal of the first amplifying circuit 11 are the same, while the inverting input terminal of the first amplifying circuit 11 and the WE of the three-electrode electrochemical sensor have the same voltage. Therefore, the voltages of the WE of the three-electrode electrochemical sensor and the non-inverting input terminal of the first amplifier circuit 11 can be the same finally.
  • the second amplifier circuit 12 forms a negative feedback circuit through electrodes, so that the voltages of the non-inverting input terminal and the reverse input terminal of the second amplifier circuit 12 are the same, and the inverting input terminal of the second amplifier circuit 12 is connected to the RE of the three-electrode electrochemical sensor. , therefore, the voltage of RE of the three-electrode electrochemical sensor and the non-inverting input terminal of the second amplifying circuit 12 can be the same finally.
  • the non-inverting input terminal of the first amplifier circuit 11 is connected to the input voltage AN0, that is, the voltage of the non-inverting input terminal of the first amplifier circuit 11 is the input voltage AN0.
  • the non-inverting input terminal of the second amplifier circuit 12 is connected to the input voltage AN0 through the voltage divider circuit 13 , so that the voltage of the non-inverting input terminal of the second amplifier circuit 12 is the divided voltage, eg AN0/2.
  • the voltages of WE of the three-electrode electrochemical sensor and the non-inverting input terminal of the first amplifier circuit 11 are the same, and the voltages of RE of the three-electrode electrochemical sensor and the non-inverting input terminal of the second amplifier circuit 12 are the same, that is, the three-electrode electrochemical sensor has the same voltage.
  • the voltage of the WE of the chemical sensor is AN0
  • the voltage of the RE of the three-electrode electrochemical sensor is AN0/2
  • the first amplifier circuit 11 includes an amplifier 111 and a negative feedback circuit disposed between an inverting input terminal and an output terminal of the first amplifier circuit 11 .
  • the amplifier 111 is a low-power operational amplifier with ultra-low input bias current, and the model can be LPV812.
  • the negative feedback circuit provided between the inverting input terminal and the output terminal of the first amplifier circuit 11 includes: a second resistor 112 .
  • the relationship between the output voltage AN1 and the input voltage AN0, the resistance value of the second resistor 112 and the output current on WE is as follows:
  • one end of the first amplifying circuit 11 is further connected to a power supply through P3, and the other end is grounded.
  • the second amplifier circuit 12 is an amplifier.
  • the amplifier is a low-power operational amplifier with ultra-low input bias current
  • the model can be LPV812.
  • one end of the second amplifying circuit 12 is connected to the power supply through P3, and the third capacitor 14 is connected to P3 and the ground for power supply filtering.
  • the potentiostatic circuit further includes: a first compensation circuit; wherein, the inverting input terminal of the first amplifier circuit 11 is connected to WE through the first compensation circuit.
  • the first compensation circuit includes: a first resistor 15 .
  • the potentiostatic circuit further includes: a second compensation circuit; wherein, the second compensation circuit is connected in parallel with the second resistor.
  • the second compensation circuit includes: a first capacitor 16 .
  • the potentiostatic circuit further includes: a filter circuit 17 connected to the output end of the first amplifying circuit 11 .
  • the filtering circuit 17 is used to filter the output voltage signal, and transmit the filtered voltage signal to the ADC.
  • the filter circuit is a first-order LC filter circuit.
  • the first-order LC filter circuit includes: a fifth resistor 171 and a fourth capacitor 172, wherein the fifth resistor 171 is connected to the output terminal of the first amplifying circuit 11 and the output voltage AN1 of the constant potential circuit, and the fourth Capacitor 172 connects AN1 to ground.
  • the potentiostatic circuit further includes: a third compensation circuit; wherein, the third compensation circuit is arranged between the inverting input terminal and the output terminal of the second amplifying circuit 12 .
  • the third compensation circuit includes: a second capacitor 18 .
  • the voltage dividing circuit includes: a third resistor 131 and a fourth resistor 132 connected in series; wherein, one end of the third resistor 131 is connected to the input voltage, and the other end is connected to the non-inverting input end of the second amplifying circuit 12, and the first One end of the four-resistor 132 is connected to the non-inverting input end of the second amplifier circuit 12 , and the other end is grounded.
  • the blood sugar measuring device further includes: an antenna matched with the communication unit.
  • the communication unit is an NFC module
  • the blood sugar measuring device further includes: an NFC antenna.
  • the MCU can transmit the measured blood glucose concentration to other devices, such as terminal devices, through the communication unit.
  • the terminal device can display the blood glucose concentration, and can also process the blood glucose concentration through the processor, for example: to obtain the blood glucose concentration for multiple times.
  • the blood glucose concentration was comprehensively analyzed to obtain the final blood glucose concentration. Or, when the blood glucose concentration is higher than the preset threshold, push alarm information, etc.
  • the terminal device can also store the blood glucose concentration received in a preset time period, such as a day or a week, into the memory, so that the user can check it at any time.
  • the present application provides a blood glucose measurement device, including: a three-electrode electrochemical sensor, a potentiostatic circuit, and an MCU, wherein the MCU is integrated with an ADC, a DAC, and a communication unit.
  • the potentiostatic circuit makes the voltage bias of the WE of the three-electrode electrochemical sensor and the RE of the three-electrode electrochemical sensor constant, so that the electrochemical stability of the three-electrode electrochemical sensor can be maintained, and then a stable current signal can be output. Based on this , the blood glucose concentration analyzed by the MCU based on the current signal is more accurate.
  • the compensation circuits included in the potentiostatic circuit can improve the stability of negative feedback, thereby ensuring that the potentiostatic circuit can output stable and reliable voltage signals.
  • the potentiostatic circuit further includes a filter circuit, etc., so that the accuracy of the output voltage signal can be improved, so that the blood sugar concentration obtained by the MCU analysis based on the current signal is more accurate.
  • the potentiostatic circuit, the MCU, the DAC, the ADC and the NFC can be partially integrated or fully integrated to realize the miniaturization of the chip.
  • the processor in this embodiment of the present application may be an integrated circuit circuit, which has a signal processing capability.
  • the above-mentioned processor can be a general-purpose processor, a digital signal processor (Digital Signal Processor, DSP), an application specific integrated circuit (Application Specific Integrated Circuit, ASIC), a ready-made programmable gate array (Field Programmable Gate Array, FPGA) or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components.
  • DSP Digital Signal Processor
  • ASIC Application Specific Integrated Circuit
  • FPGA Field Programmable Gate Array
  • the memory of the embodiment of the present application may be a volatile memory or a non-volatile memory, or may include both volatile and non-volatile memory.
  • the non-volatile memory may be a read-only memory (Read-Only Memory, ROM), a programmable read-only memory (Programmable ROM, PROM), an erasable programmable read-only memory (Erasable PROM, EPROM), an electrically programmable read-only memory (Erasable PROM, EPROM). Erase programmable read-only memory (Electrically EPROM, EEPROM) or flash memory.
  • Volatile memory may be Random Access Memory (RAM), which acts as an external cache.
  • RAM Static RAM
  • DRAM Dynamic RAM
  • SDRAM Synchronous DRAM
  • SDRAM double data rate synchronous dynamic random access memory
  • Double Data Rate SDRAM DDR SDRAM
  • enhanced SDRAM ESDRAM
  • synchronous link dynamic random access memory Synchlink DRAM, SLDRAM
  • Direct Rambus RAM Direct Rambus RAM

Landscapes

  • Life Sciences & Earth Sciences (AREA)
  • Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Pathology (AREA)
  • General Health & Medical Sciences (AREA)
  • Molecular Biology (AREA)
  • Chemical & Material Sciences (AREA)
  • Biophysics (AREA)
  • Biomedical Technology (AREA)
  • Analytical Chemistry (AREA)
  • General Physics & Mathematics (AREA)
  • Immunology (AREA)
  • Electrochemistry (AREA)
  • Optics & Photonics (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Engineering & Computer Science (AREA)
  • Biochemistry (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

一种恒电位电路、血糖测量电路及设备，恒电位电路包括第一放大电路（11）、第二放大电路（12）和分压电路（13）。第一放大电路（11）的同相输入端和输入电压（AN0）连接，第二放大电路（12）的同相输入端通过分压电路（13）与输入电压（AN0）连接，第一放大电路（11）的反相输入端和三电极电化学传感器的WE连接，第二放大电路（12）的反相输入端和三电极电化学传感器的RE连接，第二放大电路（12）的输出端和三电极电化学传感器的CE连接。第一放大电路（11）的反相输入端和输出端之间设置有负反馈电路，第一放大电路（11）的输出端用于输出电压信号。使得三电极电化学传感器的WE和三电极电化学传感器的RE的电压偏置恒定，从而可以维持三电极电化学传感器的电化学稳定性，进而才能输出稳定的电流信号。

Description

恒电位电路、血糖测量电路及设备 技术领域
本申请实施例涉及电路领域，并且更具体地，涉及恒电位电路、血糖测量电路及设备。
背景技术
目前三电极电化学传感器广泛应用于血糖测量中，三电极电化学传感器包括工作电极(Work Electrode，WE)、参考电极(Reference Electrode，RE)和对电极(Counter Electrode、CE)。三电极电化学传感器的工作原理是：通过在WE和RE之间加控制电压。带有葡萄糖氧化酶的WE发生电化学反应产生正比于葡萄糖浓度的电流，CE收集并输出该电流信号，其中如上所述，葡萄糖浓度与该电流信号存在一定的关系，而葡萄糖浓度与血糖浓度也具有一定的关系，基于此，通过分析该电流信号就可以算出血糖浓度。
血糖测量过程中，需要在WE和RE之间加一个恒定电位，以维持传感器的电化学稳定性，进而才能输出稳定的电流信号。因此，恒电位电路是血糖测量过程中至关重要的设备。
发明内容
本申请实施例提供了一种恒电位电路、血糖测量电路及设备，使得三电极电化学传感器的WE和三电极电化学传感器的RE的电压偏置恒定，从而可以维持三电极电化学传感器的电化学稳定性，进而才能输出稳定的电流信号。
第一方面，提供了一种恒电位电路，包括：第一放大电路、第二放大电路和分压电路。第一放大电路的同相输入端和输入电压连接，第二放大电路的同相输入端通过分压电路与输入电压连接，第一放大电路的反相输入端和三电极电化学传感器的工作电极WE连接，第二放大电路的反相输入端和三电极电化学传感器的参考电极RE连接，第二放大电路的输出端和三电极电化学传感器的对电极CE连接。第一放大电路的反相输入端和输出端之间设置有负反馈电路，第一放大电路的输出端用于输出电压信号。
在一种可能的实现方式中，恒电位电路还包括：第一补偿电路。其中，第一放大电路的反相输入端通过第一补偿电路与WE连接。
在一种可能的实现方式中，第一补偿电路包括：第一电阻。
在一种可能的实现方式中，负反馈电路包括：第二电阻。
在一种可能的实现方式中，恒电位电路还包括：第二补偿电路。其中，第二补偿电路与第二电阻并联连接。
在一种可能的实现方式中，第二补偿电路包括：第一电容。
在一种可能的实现方式中，恒电位电路还包括：与第一放大电路的输出端连接的滤波电路。
在一种可能的实现方式中，滤波电路是一阶LC滤波电路。
在一种可能的实现方式中，恒电位电路还包括：第三补偿电路。其中，第三补偿电路设置在第二放大电路的反相输入端和输出端之间。
在一种可能的实现方式中，第三补偿电路包括：第二电容。
在一种可能的实现方式中，分压电路包括：串联连接的第三电阻和第四电阻。其中，第三电阻的一端与输入电压连接，另一端与第二放大电路的同相输入端连接，第四电阻的一端与第二放大电路的同相输入端连接，另一端接地。
在一种可能的实现方式中，输入电压是DAC产生的电压。
在一种可能的实现方式中，DAC集成在MCU上。
第二方面，提供了一种血糖测量电路，包括：MCU和如第一方面或第一方面的可 能的实现方式提供的恒电位电路。其中，MCU和恒电位电路电连接。
在一种可能的实现方式中，MCU上集成有DAC，DAC产生恒电位电路的输入电压。
在一种可能的实现方式中，MCU上还集成有ADC，ADC用于获取恒电位电路的输出电压。
在一种可能的实现方式中，MCU上还集成有通信单元，通信单元用于实现MCU与其他设备之间的通信。
在一种可能的实现方式中，通信单元采用NFC方式进行通信。
第三方面，提供了一种血糖测量电路，包括：三电极电化学传感器和如第一方面或第一方面的可能的实现方式提供的恒电位电路。
第四方面，提供了一种血糖测量设备，包括：三电极电化学传感器、微控制单元MCU和如第一方面或第一方面的可能的实现方式提供的恒电位电路。其中，MCU和恒电位电路电连接。
在一种可能的实现方式中，MCU上集成有DAC，DAC产生恒电位电路的输入电压。
在一种可能的实现方式中，MCU上还集成有ADC，ADC用于获取恒电位电路的输出电压。
在一种可能的实现方式中，MCU上还集成有通信单元，通信单元用于实现MCU与其他设备之间的通信。
在一种可能的实现方式中，通信单元采用NFC方式进行通信。
通过上述技术方案，使得三电极电化学传感器的WE和三电极电化学传感器的RE的电压偏置恒定，从而可以维持三电极电化学传感器的电化学稳定性，进而才能输出稳定的电流信号，并且由于三电极电化学传感器的RE与第二放大电路的反相输入端连接，从而可以避免电流流过RE，防止RE发生极化而造成溶液电势发生变化。此外，血糖测量设备中的恒电位电路、MCU以及DAC、ADC和NFC可以部分集成设置或者全部集成设置，以实现血糖测量设备的小型化。
附图说明
图1是本申请一实施例提供的恒电位电路10的示意性结构图；
图2是本申请另一实施例提供的恒电位电路10的示意性结构图；
图3为本申请一实施例提供的血糖检测电路30的示意图；
图4为本申请一实施例提供的血糖检测电路40的示意图；
图5为本申请一实施例提供的血糖测量设备50的示意图。
具体实施方式
下面将结合本申请实施例中的附图，对本申请实施例中的技术方案进行描述，显然，所描述的实施例是本申请一部分实施例，而不是全部的实施例。针对本申请中的实施例，本领域普通技术人员在没有做出创造性劳动前提下所获得的所有其他实施例，都属于本申请保护的范围。
在介绍本申请技术方案之前，下面先对三电极电化学传感器的三电极做以说明：
WE又称为研究电极，是指所研究的反应在该电极上发生，也就是响应的物质在这个电极上发生反应。一般而言，工作电极的材料既可以是固体，又可以是液体。常用的工作电极材料有：玻碳电极、铂(Pt)、金(Au)、银(Ag)、铅(Pb)、导电玻璃(ITO)、汞(Hg)等。
CE又称为辅助电极。CE和WE组成回路，使WE上电流畅通，以保证所研究的反应在工作电极上发生。当WE上发生氧化或还原反应时，CE上可以安排为气体的析出反应，或WE反应的逆反应，从而使得电解液的组成成分不变。对电极的性能一般不影响WE上的反应。CE的电位会随电流的改变而发生变化，若测量的过程中通过的电流较大 时，此时CE本身将会发生极化，因此不能作为电势比较的标准，容易引起测量误差。为使CE的电位保持稳定，则必须使用RE，否则将会影响测量的准确性。
RE的电位不受电解液成分变化的影响，具有恒定的数值。
在血糖测量过程中，如果直接在WE和RE之间加电压，在电压的作用下，WE表面产生化学反应，由于此时WE和RE之间形成回路，反应所产生的电流信号将通过RE输出，随着电流信号的变化，WE和RE之间的电压也会发生变化，无法保持恒定。因此亟需提供一恒电位器，以维持WE和RE之间的恒定电位，从而维持传感器的电化学稳定性，进而才能输出稳定的电流信号。
本申请提供一种恒电位电路、血糖测量电路及设备。下面将结合图1至图5，详细介绍本申请实施例的恒电位电路、血糖测量电路及设备。
需要说明的是，为便于说明，在本申请的实施例中，相同的附图标记表示相同的部件，并且为了简洁，在不同实施例中，省略对相同部件的详细说明。
图1是本申请一实施例提供的恒电位电路10的示意性结构图。如图1所示，该恒电位电路10包括：第一放大电路11、第二放大电路12和分压电路13。其中，第一放大电路11的同相输入端和输入电压AN0连接，第二放大电路12的同相输入端通过分压电路13与输入电压AN0连接，第一放大电路11的反相输入端和三电极电化学传感器的WE连接，第二放大电路12的反相输入端和三电极电化学传感器的RE连接，第二放大电路12的输出端和三电极电化学传感器的CE连接；第一放大电路11的反相输入端和输出端之间设置有负反馈电路，第一放大电路11的输出端用于输出电压信号AN1。
具体地，由图1所示的恒电位电路可知，第一放大电路11设置有负反馈电路，使得第一放大电路11的正相输入端和反向输入端的电压相同，而由于第一放大电路11的反相输入端和三电极电化学传感器的WE连接，因此，最终可以实现三电极电化学传感器的WE和第一放大电路11的正相输入端的电压相同。第二放大电路12通过电极构成负反馈电路，使得第二放大电路12的正相输入端和反向输入端的电压相同，第二放大电路12的反相输入端和三电极电化学传感器的RE连接，因此，最终可以实现三电极电化学传感器的RE和第二放大电路12的正相输入端的电压相同。
进一步地，第一放大电路11的同相输入端和输入电压AN0连接，即第一放大电路11的同相输入端的电压是输入电压AN0。第二放大电路12的同相输入端通过分压电路13与输入电压AN0连接，使得第二放大电路12的同相输入端的电压为经过分压后的电压，例如是AN0/2。如上所述，三电极电化学传感器的WE和第一放大电路11的正相输入端的电压相同，三电极电化学传感器的RE和第二放大电路12的正相输入端的电压相同，即三电极电化学传感器的WE的电压为AN0，三电极电化学传感器的RE的电压为AN0/2，因此三电极电化学传感器的WE和三电极电化学传感器的RE的电压偏置为AN0-AN0/2＝AN0/2。
其中，负反馈电路还用于将三电极电化学传感器所产生的电流信号转换为电压信号。
综上，通过本申请提供的恒电位电路，使得三电极电化学传感器的WE和三电极电化学传感器的RE的电压偏置恒定，从而可以维持三电极电化学传感器的电化学稳定性，进而才能输出稳定的电流信号。并且由于三电极电化学传感器的RE与第二放大电路的反相输入端连接，从而可以避免电流流过RE，防止RE发生极化而造成溶液电势发生变化。
在图1所示的恒电位电路10的基础上，下面将通过其他实施例对本申请技术方案进行进一步地详细说明：图2是本申请另一实施例提供的恒电位电路10的示意性结构图，具体参见图2。
可选地，第一放大电路11包括放大器111和设置在第一放大电路11的反相输入端和输出端之间的负反馈电路。
可选地，该放大器111是超低输入偏置电流的低功耗运算放大器，型号可以是 LPV812。
可选地，如图2所示，第一放大电路11的反相输入端和输出端之间设置的负反馈电路包括：第二电阻112。
需要说明的是，图2所示的第二电阻仅是负反馈电路的一种可实现方式，当然，负反馈电路可以包括：多个串联或者并联的电阻，本申请对负反馈电路不作限制。
可选地，输出电压AN1与输入电压AN0、第二电阻112的电阻值和WE上的输出电流之间的关系如下：
AN1＝AN0+WE上的输出电流*第二电阻的电阻值或AN1＝AN0-WE上的输出电流*第二电阻的电阻值。
可选地，第一放大电路11一端还通过P3连接供电电源，另一端接地。
可选地，第二放大电路12是一个放大器。
可选地，该放大器是超低输入偏置电流的低功耗运算放大器，型号可以是LPV812。
可选地，第二放大电路12的一端通过P3连接供电电源，第三电容14连接P3和地，用于电源滤波。
可选地，恒电位电路10还包括：第一补偿电路；其中，第一放大电路11的反相输入端通过第一补偿电路与WE连接。如图2所示，第一补偿电路包括：第一电阻15。
需要说明的是，图2所示的第一电阻仅是第一补偿电路的一种可实现方式，当然，第一补偿电路可以包括：多个串联或者并联的电阻，本申请对第一补偿电路不作限制。
可选地，恒电位电路10还包括：第二补偿电路；其中，第二补偿电路与第二电阻112并联连接。
可选地，如图2所示，第二补偿电路包括：第一电容16。
需要说明的是，图2所示的第一电容仅是第二补偿电路的一种可实现方式，本申请对第二补偿电路不作限制。
可选地，恒电位电路10还包括：与第一放大电路11的输出端连接的滤波电路17。滤波电路17用于对输出的电压信号进行滤波，并将滤波后的电压信号传输给模数转换器(Analog Digital Converter，ADC)。
可选地，ADC集成在微控制单元(Microcontroller Unit，MCU)上或者ADC与MCU单独设置。
可选地，该MCU可以是NHS3152型号的MCU。
可选地，滤波电路是一阶LC滤波电路。如图2所示，该一阶LC滤波电路包括：第五电阻171和第四电容172，其中，第五电阻171连接第一放大电路11的输出端和恒电位电路10的输出电压AN1，第四电容172连接AN1和地。
可选地，恒电位电路10还包括：第三补偿电路；其中，第三补偿电路设置在第二放大电路12的反相输入端和输出端之间。
可选地，第三补偿电路包括：第二电容18。
需要说明的是，图2所示的第二电容仅是第三补偿电路的一种可实现方式，本申请对第三补偿电路不作限制。
可选地，分压电路包括：串联连接的第三电阻131和第四电阻132；其中，第三电阻131的一端与输入电压连接，另一端与第二放大电路12的同相输入端连接，第四电阻132的一端与第二放大电路12的同相输入端连接，另一端接地。
可选地，输入电压是数模转换器(Digital Analog Converter，DAC)产生的电压。
可选地，DAC集成在MCU上或者DAC与MCU单独设置。
综上，本申请提供的恒电位电路包括的补偿电路，如第一补偿电路、第二补偿电路和第三补偿电路，可以提高负反馈稳定性，进而保证恒电位电路可以输出稳定且可靠的电压信号。如上所述，恒电位电路还包括滤波电路等，从而可以提高输出的电压信号的精确性。
图3为本申请一实施例提供的血糖检测电路30的示意图，如图3所示，MCU31上集成有DAC和ADC，其中，DAC用于产生恒电位电路的输入电压AN0。ADC用于获取恒电位电路的输出电压，并对输出的电压信号进行模数转换，得到数字信号，然后MCU可以对数字信号进行分析，如上所述，葡萄糖浓度与该数字信号对应的传感器输出的电流信号存在一定的关系，而葡萄糖浓度与血糖浓度也具有一定的关系，基于此，通过分析该数字信号就可以计算出血糖浓度。
或者，确定血糖浓度和上述数字信号所表示的电压值的关系式，根据该关系式确定血糖浓度。
可选地，血糖浓度和上述数字信号所表示的电压值的关系式如下：
c＝1.393f-1446
其中，c表示血糖浓度，单位为mg/d；f表示数字信号所表示的电压值，单位为mV。
可选地，血糖浓度c的取值范围是【50mg/d，300mg/d】，f的取值范围是【1.064V，1.247V】。
可选地，MCU上还集成有通信单元，通信单元用于实现MCU与其他设备之间的通信。例如：MCU通过该通信单元将分析得到的血糖浓度发送给其他设备，如推送给指定用户的终端设备。
可选地，通信单元采用近场通信(Near Field Communication，NFC)方式进行通信。如图3所示，MCU31中包括NFC模块，其用于实现MCU与其他设备之间的通信。
需要说明的是，在一些实施例中，该MCU与其他设备之间也可以采用其他的无线方式进行通信，例如，通信单元还可以采用其他无线通信方式与其他设备进行通信，例如：可以是2.4GHz、蓝牙、ZigBee、无线保真(Wireless-Fidelity，Wi-Fi)、第三代(3th Generation，3G)移动通信技术、第四代(4th Generation，4G)移动通信技术、第五代(5th Generation，5G)移动通信技术、以及后续演进的无线通信技术等，另外也可以是一些其他的无线通信技术，本申请对此并不限定。
其中，恒电位电路可以是图1或图2所示的恒电位电路，关于恒电位电路的解释说明可参考图1或者图2所示的实施例，本申请对此不再赘述。
需要说明的是，恒电位电路、MCU31以及DAC、ADC和NFC可以部分集成设置或者全部集成设置。例如：可以将恒电位电路、MCU31以及DAC、ADC和NFC设置在一个芯片上，以实现芯片的小型化。
综上，通过本申请提供的血糖检测电路，其包括恒电位电路和MCU，该恒电位电路可以使得三电极电化学传感器的WE和三电极电化学传感器的RE的电压偏置恒定，从而可以维持三电极电化学传感器的电化学稳定性，进而才能输出稳定的电流信号，基于此，MCU基于该电流信号所分析得到的血糖浓度更加精确。并且由于三电极电化学传感器的RE与第二放大电路的反相输入端连接，从而可以避免电流流过RE，防止RE发生极化而造成溶液电势发生变化。此外，恒电位电路包括的补偿电路，如第一补偿电路、第二补偿电路和第三补偿电路，可以提高负反馈稳定性，进而保证恒电位电路可以输出稳定且可靠的电压信号。如上所述，恒电位电路还包括滤波电路等，从而可以提高输出的电压信号的精确性，从而使得，MCU基于该电流信号所分析得到的血糖浓度更加精确。
图4为本申请一实施例提供的血糖检测电路40的示意图，如图4所示，该血糖检测电路40包括三电极电化学传感器41和恒电位电路。
恒电位电路为WE和RE之间提供稳定的电压偏置，即电压差，使得带有葡萄糖氧化酶的WE发生电化学反应，从而产生正比于葡萄糖浓度的电流，CE收集并输出该电流信号，该电流信号经过恒电位电路稳定放大，将电流信号转换为电压信号，然后将电压信号传输至集成在MCU上的ADC，使得ADC用于获取恒电位电路的输出电压，并对输出的电压信号进行模数转换，得到数字信号。
其中，恒电位电路可以是图1或图2所示的恒电位电路，关于恒电位电路的解释说 明可参考图1或者图2所示的实施例，本申请对此不再赘述。
综上，通过本申请提供的血糖检测电路，其包括三电极电化学传感器和恒电位电路，该恒电位电路可以使得三电极电化学传感器的WE和三电极电化学传感器的RE的电压偏置恒定，从而可以维持三电极电化学传感器的电化学稳定性，进而才能输出稳定的电流信号。并且由于三电极电化学传感器的RE与第二放大电路的反相输入端连接，从而可以避免电流流过RE，防止RE发生极化而造成溶液电势发生变化。此外，恒电位电路包括的补偿电路，如第一补偿电路、第二补偿电路和第三补偿电路，可以提高负反馈稳定性，进而保证恒电位电路可以输出稳定且可靠的电压信号。如上所述，恒电位电路还包括滤波电路等，从而可以提高输出的电压信号的精确性。
图5为本申请一实施例提供的血糖测量设备50的示意图，如图5所示，该血糖测量设备50包括三电极电化学传感器41、恒电位电路和MCU31。
其中，MCU31上集成的ADC可以为恒电位电路提供输入电压。恒电位电路为WE和RE之间提供稳定的电压偏置，使得带有葡萄糖氧化酶的WE发生电化学反应，从而产生正比于葡萄糖浓度的电流，CE收集并输出该电流信号，该电流信号经过恒电位电路稳定放大，将电流信号转换为电压信号，然后将电压信号传输至集成在MCU上的ADC，使得ADC用于获取恒电位电路的输出电压，并对输出的电压信号进行模数转换，得到数字信号，MCU对该数字信号进行分析，如上所述，葡萄糖浓度与该数字信号对应的传感器输出的电流信号存在一定的关系，而葡萄糖浓度与血糖浓度也具有一定的关系，基于此，通过分析该数字信号就可以计算出血糖浓度。
或者，确定血糖浓度和上述数字信号所表示的电压值的关系式，根据该关系式确定血糖浓度。
可选地，血糖浓度和上述数字信号所表示的电压值的关系式如下：
c＝1.393f-1446
其中，c表示血糖浓度，单位为mg/d；f表示数字信号所表示的电压值，单位为mV。
可选地，血糖浓度c的取值范围是【50mg/d，300mg/d】，f的取值范围是【1.064V，1.247V】。
可选地，MCU上还集成有通信单元，通信单元用于实现MCU与其他设备之间的通信。例如：MCU通过该通信单元将分析得到的血糖浓度发送给其他设备，如推送给指定用户的终端设备。
可选地，通信单元采用NFC方式进行通信。如图5所示，MCU31中包括NFC模块，其用于实现MCU与其他设备之间的通信。
需要说明的是，在一些实施例中，该MCU与其他设备之间也可以采用其他的无线方式进行通信，例如，通信单元还可以采用其他无线通信方式与其他设备进行通信，例如：可以是2.4GHz、蓝牙、ZigBee、Wi-Fi、3G、4G或者5G移动通信技术、以及后续演进的无线通信技术等，另外也可以是一些其他的无线通信技术，本申请对此并不限定。
其中，该恒电位电路包括：第一放大电路11、第二放大电路12和分压电路13。其中，第一放大电路11的同相输入端和输入电压AN0连接，第二放大电路12的同相输入端通过分压电路13与输入电压AN0连接，第一放大电路11的反相输入端和三电极电化学传感器的WE连接，第二放大电路12的反相输入端和三电极电化学传感器的RE连接，第二放大电路12的输出端和三电极电化学传感器的CE连接；第一放大电路11的反相输入端和输出端之间设置有负反馈电路，第一放大电路11的输出端用于输出电压信号。
第一放大电路11设置有负反馈电路，使得第一放大电路11的正相输入端和反向输入端的电压相同，而由于第一放大电路11的反相输入端和三电极电化学传感器的WE连接，因此，最终可以实现三电极电化学传感器的WE和第一放大电路11的正相输入端的电压相同。第二放大电路12通过电极构成负反馈电路，使得第二放大电路12的正相输入端和反向输入端的电压相同，第二放大电路12的反相输入端和三电极电化学传感器的 RE连接，因此，最终可以实现三电极电化学传感器的RE和第二放大电路12的正相输入端的电压相同。
进一步地，第一放大电路11的同相输入端和输入电压AN0连接，即第一放大电路11的同相输入端的电压是输入电压AN0。第二放大电路12的同相输入端通过分压电路13与输入电压AN0连接，使得第二放大电路12的同相输入端的电压为经过分压后的电压，例如是AN0/2。如上所述，三电极电化学传感器的WE和第一放大电路11的正相输入端的电压相同，三电极电化学传感器的RE和第二放大电路12的正相输入端的电压相同，即三电极电化学传感器的WE的电压为AN0，三电极电化学传感器的RE的电压为AN0/2，因此三电极电化学传感器的WE和三电极电化学传感器的RE的电压偏置为AN0-AN0/2＝AN0/2。
可选地，第一放大电路11包括放大器111和设置在第一放大电路11的反相输入端和输出端之间的负反馈电路。
可选地，该放大器111是超低输入偏置电流的低功耗运算放大器，型号可以是LPV812。
可选地，第一放大电路11的反相输入端和输出端之间设置的负反馈电路包括：第二电阻112。
可选地，输出电压AN1与输入电压AN0、第二电阻112的电阻值和WE上的输出电流之间的关系如下：
AN1＝AN0+WE上的输出电流*第二电阻的电阻值或AN1＝AN0-WE上的输出电流*第二电阻的电阻值。
可选地，第一放大电路11一端还通过P3连接供电电源，另一端接地。
可选地，第二放大电路12是一个放大器。
可选地，该放大器是超低输入偏置电流的低功耗运算放大器，型号可以是LPV812。
可选地，第二放大电路12的一端通过P3连接供电电源，第三电容14连接P3和地，用于电源滤波。
可选地，恒电位电路还包括：第一补偿电路；其中，第一放大电路11的反相输入端通过第一补偿电路与WE连接。如图5所示，第一补偿电路包括：第一电阻15。
可选地，恒电位电路还包括：第二补偿电路；其中，第二补偿电路与第二电阻并联连接。
可选地，如图5所示，第二补偿电路包括：第一电容16。
可选地，恒电位电路还包括：与第一放大电路11的输出端连接的滤波电路17。滤波电路17用于对输出的电压信号进行滤波，并将滤波后的电压信号传输给ADC。
可选地，滤波电路是一阶LC滤波电路。如图5所示，该一阶LC滤波电路包括：第五电阻171和第四电容172，其中，第五电阻171连接第一放大电路11的输出端和恒电位电路的输出电压AN1，第四电容172连接AN1和地。
可选地，恒电位电路还包括：第三补偿电路；其中，第三补偿电路设置在第二放大电路12的反相输入端和输出端之间。
可选地，第三补偿电路包括：第二电容18。
可选地，分压电路包括：串联连接的第三电阻131和第四电阻132；其中，第三电阻131的一端与输入电压连接，另一端与第二放大电路12的同相输入端连接，第四电阻132的一端与第二放大电路12的同相输入端连接，另一端接地。
可选地，该血糖测量设备还包括：与通信单元匹配的天线，例如如图5所示，当通信单元是NFC模块时，该血糖测量设备还包括：NFC天线。
如上所述，MCU可以通过通信单元将测量得到的血糖浓度传输给其他设备，如终端设备，终端设备可以显示该血糖浓度，也可以通过处理器对血糖浓度进行处理，例如：将多次获取到的血糖浓度进行综合分析，得到最终的血糖浓度。又或者，当血糖浓度高 于预设阈值时，推送报警信息等。终端设备也可以将预设时间段，如一天或者一周内收到的血糖浓度存储至存储器中，以便于用户随时查看。
综上，本申请提供一种血糖测量设备，包括：三电极电化学传感器、恒电位电路和MCU，其中MCU上集成有ADC、DAC和通信单元。该恒电位电路使得三电极电化学传感器的WE和三电极电化学传感器的RE的电压偏置恒定，从而可以维持三电极电化学传感器的电化学稳定性，进而才能输出稳定的电流信号，基于此，MCU基于该电流信号所分析得到的血糖浓度更加精确。并且由于三电极电化学传感器的RE与第二放大电路的反相输入端连接，从而可以避免电流流过RE，防止RE发生极化而造成溶液电势发生变化。此外，恒电位电路包括的补偿电路，如第一补偿电路、第二补偿电路和第三补偿电路，可以提高负反馈稳定性，进而保证恒电位电路可以输出稳定且可靠的电压信号。如上所述，恒电位电路还包括滤波电路等，从而可以提高输出的电压信号的精确性，从而使得，MCU基于该电流信号所分析得到的血糖浓度更加精确。进一步地，恒电位电路、MCU以及DAC、ADC和NFC可以部分集成设置或者全部集成设置，以实现芯片的小型化。
应理解，本申请实施例中的具体的例子只是为了帮助本领域技术人员更好地理解本申请实施例，而非限制本申请实施例的范围。
应理解，在本申请实施例和所附权利要求书中使用的术语是仅仅出于描述特定实施例的目的，而非旨在限制本申请实施例。例如，在本申请实施例和所附权利要求书中所使用的单数形式的“一种”、“上述”和“该”也旨在包括多数形式，除非上下文清楚地表示其他含义。
应理解，本申请实施例的处理器可以是一种集成电路电路，具有信号的处理能力。在实现过程中，上述的处理器可以是通用处理器、数字信号处理器(Digital Signal Processor，DSP)、专用集成电路(Application Specific Integrated Circuit，ASIC)、现成可编程门阵列(Field Programmable Gate Array，FPGA)或者其他可编程逻辑器件、分立门或者晶体管逻辑器件、分立硬件组件。
可以理解，本申请实施例的存储器可以是易失性存储器或非易失性存储器，或可包括易失性和非易失性存储器两者。其中，非易失性存储器可以是只读存储器(Read-Only Memory，ROM)、可编程只读存储器(Programmable ROM，PROM)、可擦除可编程只读存储器(Erasable PROM，EPROM)、电可擦除可编程只读存储器(Electrically EPROM，EEPROM)或闪存。易失性存储器可以是随机存取存储器(Random Access Memory，RAM)，其用作外部高速缓存。通过示例性但不是限制性说明，许多形式的RAM可用，例如静态随机存取存储器(Static RAM，SRAM)、动态随机存取存储器(Dynamic RAM，DRAM)、同步动态随机存取存储器(Synchronous DRAM，SDRAM)、双倍数据速率同步动态随机存取存储器(Double Data Rate SDRAM，DDR SDRAM)、增强型同步动态随机存取存储器(Enhanced SDRAM，ESDRAM)、同步连接动态随机存取存储器(Synchlink DRAM，SLDRAM)和直接内存总线随机存取存储器(Direct Rambus RAM，DR RAM)。
需要说明的是，在不冲突的前提下，本申请描述的各个实施例和/或各个实施例中的技术特征可以任意的相互组合，组合之后得到的技术方案也应落入本申请的保护范围。
应理解，本申请实施例中的具体的例子只是为了帮助本领域技术人员更好地理解本申请实施例，而非限制本申请实施例的范围，本领域技术人员可以在上述实施例的基础上进行各种改进和变形，而这些改进或者变形均落在本申请的保护范围内。
以上所述，仅为本申请的具体实施方式，但本申请的保护范围并不局限于此，任何熟悉本技术领域的技术人员在本申请揭露的技术范围内，可轻易想到变化或替换，都应涵盖在本申请的保护范围之内。因此，本申请的保护范围应以所述权利要求的保护范围为准。

Claims (24)

  1. 一种恒电位电路，包括：第一放大电路、第二放大电路和分压电路；
    所述第一放大电路的同相输入端和输入电压连接，所述第二放大电路的同相输入端通过所述分压电路与所述输入电压连接，所述第一放大电路的反相输入端和三电极电化学传感器的工作电极WE连接，所述第二放大电路的反相输入端和所述三电极电化学传感器的参考电极RE连接，所述第二放大电路的输出端和所述三电极电化学传感器的对电极CE连接；
    所述第一放大电路的反相输入端和输出端之间设置有负反馈电路，所述第一放大电路的输出端用于输出电压信号。
  2. 根据权利要求1所述的电路，其特征在于，还包括：第一补偿电路；
    其中，所述第一放大电路的反相输入端通过所述第一补偿电路与所述WE连接。
  3. 根据权利要求2所述的电路，其特征在于，所述第一补偿电路包括：第一电阻。
  4. 根据权利要求1-3任一项所述的电路，其特征在于，所述负反馈电路包括：第二电阻。
  5. 根据权利要求4所述的电路，其特征在于，还包括：第二补偿电路；
    其中，所述第二补偿电路与所述第二电阻并联连接。
  6. 根据权利要求5所述的电路，其特征在于，所述第二补偿电路包括：第一电容。
  7. 根据权利要求1-6任一项所述的电路，其特征在于，还包括：与所述第一放大电路的输出端连接的滤波电路。
  8. 根据权利要求7所述的电路，其特征在于，所述滤波电路是一阶LC滤波电路。
  9. 根据权利要求1-8任一项所述的电路，其特征在于，还包括：第三补偿电路；
    其中，所述第三补偿电路设置在所述第二放大电路的反相输入端和输出端之间。
  10. 根据权利要求9所述的电路，其特征在于，所述第三补偿电路包括：第二电容。
  11. 根据权利要求1-10任一项所述的电路，其特征在于，所述分压电路包括：串联连接的第三电阻和第四电阻；
    其中，所述第三电阻的一端与所述输入电压连接，另一端与所述第二放大电路的同相输入端连接，所述第四电阻的一端与所述第二放大电路的同相输入端连接，另一端接地。
  12. 根据权利要求1-11任一项所述的电路，其特征在于，所述输入电压是数模转换器DAC产生的电压。
  13. 根据权利要求12所述的电路，其特征在于，所述DAC集成在微控制单元MCU上。
  14. 一种血糖测量电路，其特征在于，包括：微控制单元MCU和如权利要求1-13任一项所述的恒电位电路；
    其中，所述MCU和所述恒电位电路电连接。
  15. 根据权利要求14所述的电路，其特征在于，所述MCU上集成有数模转换器DAC，所述DAC产生所述恒电位电路的输入电压。
  16. 根据权利要求14或15所述的电路，其特征在于，所述MCU上还集成有模数转换器ADC，所述ADC用于获取所述恒电位电路的输出电压。
  17. 根据权利要求14-16任一项所述的电路，其特征在于，所述MCU上还集成有通信单元，所述通信单元用于实现所述MCU与其他设备之间的通信。
  18. 根据权利要求17所述的电路，其特征在于，所述通信单元采用近场通信NFC方式进行通信。
  19. 一种血糖测量电路，其特征在于，包括：三电极电化学传感器和如权利要求1-13任一项所述的恒电位电路。
  20. 一种血糖测量设备，其特征在于，包括：三电极电化学传感器、微控制单元MCU 和如权利要求1-13任一项所述的恒电位电路；
    其中，所述MCU和所述恒电位电路电连接。
  21. 根据权利要求20所述的设备，其特征在于，所述MCU上集成有数模转换器DAC，所述DAC产生所述恒电位电路的输入电压。
  22. 根据权利要求20或21所述的设备，其特征在于，所述MCU上还集成有模数转换器ADC，所述ADC用于获取所述恒电位电路的输出电压。
  23. 根据权利要求20-22任一项所述的设备，其特征在于，所述MCU上还集成有通信单元，所述通信单元用于实现所述MCU与其他设备之间的通信。
  24. 根据权利要求23所述的设备，其特征在于，所述通信单元采用近场通信NFC方式进行通信。
PCT/CN2020/099431 2020-06-30 2020-06-30 恒电位电路、血糖测量电路及设备 WO2022000313A1 (zh)

Priority Applications (2)

Application Number Priority Date Filing Date Title
PCT/CN2020/099431 WO2022000313A1 (zh) 2020-06-30 2020-06-30 恒电位电路、血糖测量电路及设备
CN202080099953.1A CN115484868A (zh) 2020-06-30 2020-06-30 恒电位电路、血糖测量电路及设备

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/CN2020/099431 WO2022000313A1 (zh) 2020-06-30 2020-06-30 恒电位电路、血糖测量电路及设备

Publications (1)

Publication Number Publication Date
WO2022000313A1 true WO2022000313A1 (zh) 2022-01-06

Family

ID=79317325

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2020/099431 WO2022000313A1 (zh) 2020-06-30 2020-06-30 恒电位电路、血糖测量电路及设备

Country Status (2)

Country Link
CN (1) CN115484868A (zh)
WO (1) WO2022000313A1 (zh)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN114778626A (zh) * 2022-04-28 2022-07-22 深圳可孚生物科技有限公司 一种葡萄糖传感器信号调理电路
CN114778642A (zh) * 2022-03-23 2022-07-22 深圳硅基传感科技有限公司 具有三个电极的葡萄糖浓度信息采集装置

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101661015A (zh) * 2009-09-09 2010-03-03 上海睿兴实业有限公司 电化学生物传感器通用便携式检测仪
CN102706931A (zh) * 2012-05-31 2012-10-03 成都安可信电子股份有限公司 电化学气体传感器偏压与非偏压工作电路及偏压配置电路
US20130116524A1 (en) * 2011-11-07 2013-05-09 Abbott Diabetes Care Inc. Analyte Monitoring Device and Methods
WO2019166964A1 (en) * 2018-03-02 2019-09-06 Distretto Tecnologico Sicilia Micro E Nano Sistemi S.C.A.R.L. Interface electronic device for reading an output signal and for controlling and conditioning a three-electrodes amperometric sensor
CN110368000A (zh) * 2019-07-17 2019-10-25 河北科技大学 一种基于nfc的连续血糖检测仪及检测方法
CN110609072A (zh) * 2019-10-17 2019-12-24 南京工业大学 一种普鲁士蓝膜生物电极的微弱信号检测电路
CN110646494A (zh) * 2018-06-27 2020-01-03 英飞凌科技股份有限公司 用于运行电化学电池的电路装置和相应的方法
CN110741248A (zh) * 2017-06-11 2020-01-31 彼得·斯特兹 基于芯片的多通道电化学转换器及其使用方法

Patent Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101661015A (zh) * 2009-09-09 2010-03-03 上海睿兴实业有限公司 电化学生物传感器通用便携式检测仪
US20130116524A1 (en) * 2011-11-07 2013-05-09 Abbott Diabetes Care Inc. Analyte Monitoring Device and Methods
CN102706931A (zh) * 2012-05-31 2012-10-03 成都安可信电子股份有限公司 电化学气体传感器偏压与非偏压工作电路及偏压配置电路
CN110741248A (zh) * 2017-06-11 2020-01-31 彼得·斯特兹 基于芯片的多通道电化学转换器及其使用方法
WO2019166964A1 (en) * 2018-03-02 2019-09-06 Distretto Tecnologico Sicilia Micro E Nano Sistemi S.C.A.R.L. Interface electronic device for reading an output signal and for controlling and conditioning a three-electrodes amperometric sensor
CN110646494A (zh) * 2018-06-27 2020-01-03 英飞凌科技股份有限公司 用于运行电化学电池的电路装置和相应的方法
CN110368000A (zh) * 2019-07-17 2019-10-25 河北科技大学 一种基于nfc的连续血糖检测仪及检测方法
CN110609072A (zh) * 2019-10-17 2019-12-24 南京工业大学 一种普鲁士蓝膜生物电极的微弱信号检测电路

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN114778642A (zh) * 2022-03-23 2022-07-22 深圳硅基传感科技有限公司 具有三个电极的葡萄糖浓度信息采集装置
CN114778642B (zh) * 2022-03-23 2023-12-05 深圳硅基传感科技有限公司 具有三个电极的葡萄糖浓度信息采集装置
CN114778626A (zh) * 2022-04-28 2022-07-22 深圳可孚生物科技有限公司 一种葡萄糖传感器信号调理电路
CN114778626B (zh) * 2022-04-28 2024-03-22 深圳可孚生物科技有限公司 一种葡萄糖传感器信号调理电路

Also Published As

Publication number Publication date
CN115484868A (zh) 2022-12-16

Similar Documents

Publication Publication Date Title
WO2022000313A1 (zh) 恒电位电路、血糖测量电路及设备
Turner et al. A CMOS potentiostat for amperometric chemical sensors
US20100066378A1 (en) Current Mirror Potentiostat
Jalal et al. Multimodal technique to eliminate humidity interference for specific detection of ethanol
Chen et al. A microwatt dual-mode electrochemical sensing current readout with current-reducer ramp waveform generation
Al Mamun et al. A glucose biosensor using CMOS potentiostat and vertically aligned carbon nanofibers
Machini et al. Electrochemical investigation of the voltammetric determination of hydrochlorothiazide using a nickel hydroxide modified nickel electrode
Hanitra et al. Multichannel front-end for electrochemical sensing of metabolites, drugs, and electrolytes
US7663357B2 (en) Signal readout circuit for amperometric sensor
Chen et al. A portable signal-on self-powered aptasensor for ultrasensitive detection of sulfadimethoxine based on dual amplification of a capacitor and biphotoelectrodes
Umasankar et al. Wearable alcohol monitoring device with auto-calibration ability for high chemical specificity
Mahato et al. Low-noise potentiostat circuit for electrochemical detection of heavy metals or metalloids
Punjiya et al. Low-cost paper-based electrochemical sensors with CMOS readout IC
Boutet et al. Low power CMOS potentiostat for three electrodes amperometric chemical sensor
Lin et al. A Multichannel Electrochemical Sensor Interface IC for Bioreactor Monitoring
Ma et al. A review of electrochemical electrodes and readout interface designs for biosensors
Roknsharifi et al. A low power, highly stabilized three electrode potentiostat for biomedical implantable systems
Ahmad et al. Programmable Readout with Integrated Bandgap Reference Potentiostat for Glucose Sensing
Ghoreishizadeh et al. Sub-mW reconfigurable interface IC for electrochemical sensing
Ma et al. Design of a wireless compact implantable electrochemical biosensor system for health monitoring application
Xie et al. Design of a 68 dB input dynamic range Potentiostat for electrochemical biosensing
US9097655B2 (en) Programmable gain amplifier with multi-range operation for use in body sensor interface applications
Chen et al. Power-efficient cyclic voltammetric electrochemical sensing readout circuitry with current-reducer ramp waveform generation
US20240180458A1 (en) Continuous electrochemical monitoring
CN117805209B (zh) 一种基于尿酸、肌酐和pH的电化学检测装置及系统

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 20942932

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 20942932

Country of ref document: EP

Kind code of ref document: A1