CN215415184U - Electrochemical sensor detection circuit, device and system - Google Patents
Electrochemical sensor detection circuit, device and system Download PDFInfo
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- CN215415184U CN215415184U CN202120674798.3U CN202120674798U CN215415184U CN 215415184 U CN215415184 U CN 215415184U CN 202120674798 U CN202120674798 U CN 202120674798U CN 215415184 U CN215415184 U CN 215415184U
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Abstract
The utility model discloses a detection circuit, a device and a system of an electrochemical sensor, wherein the detection circuit comprises: the micro-needle type electrode sensor comprises a three-electrode sensor interface, a first micro-needle interface, a second micro-needle interface, a front-end sensor conditioning circuit, a dual-channel DAC driving constant current source circuit, a microcontroller circuit, a power circuit, a communication circuit and a USB interface, wherein the output of the dual-channel DAC driving constant current source circuit is connected with the first micro-needle interface and the second micro-needle interface, the three-electrode sensor interface is connected with the input of the front-end sensor conditioning circuit, and the microcontroller circuit is connected with the front-end sensor conditioning circuit, the dual-channel DAC driving constant current source circuit, the communication circuit and the USB interface. The embodiment of the utility model can realize painless minimally invasive detection of the human tissue fluid and release of the therapeutic drug, has low cost and is convenient to popularize. The embodiment of the utility model can be widely applied to the technical field of biomedical sensor detection.
Description
Technical Field
The utility model relates to the technical field of biomedical sensor detection, in particular to a detection circuit, a detection device and a detection system of an electrochemical sensor.
Background
The sensing detection research in the biomedical field is an important application field of an electrochemical sensor and an electrochemical sensing detection system, the traditional vital signs for detection comprise temperature, electrocardio, heart rate, pulse, blood pressure and the like, and the indexes have important health monitoring values. In addition, biochemical parameters such as blood sugar, cholesterol, uric acid and the like also contain abundant and direct health characterization information, can be used as important references for analyzing health states and diagnosing diseases, but are not widely popularized. At present, methods for detecting physiological markers such as glucose, lactic acid, uric acid and cholesterol mainly comprise methods such as electrochemiluminescence, an electrochemical method, a fluorescence spectroscopy method, a high performance liquid chromatography method, a colorimetric method, an enzyme detection kit and the like. On the one hand, these test methods are not suitable for long-term widespread applications due to the expensive, long-lasting instruments, the need for professional operation, the high cost of a single test, etc. On the other hand, although the currently diagnosed gold standard liquid is blood, these detection methods are generally implemented by extracting human blood, and by extracorporeal detection; however, invasive sampling is a major obstacle, not suitable for long-term continuous use, and the pain during blood sampling puts psychological stress on the patient.
SUMMERY OF THE UTILITY MODEL
In view of this, an object of the embodiments of the present invention is to provide a detection circuit, a device and a system for an electrochemical sensor, in which the device based on the circuit can realize painless minimally invasive detection of human tissue fluid and release of therapeutic drugs, and has low cost and easy popularization.
In a first aspect, an embodiment of the present invention provides an electrochemical sensor detection circuit, including: three electrode sensor interfaces, first micropin interface, second micropin interface, front end sensor modulate circuit, binary channels DAC drive constant current source circuit, microcontroller circuit, power supply circuit, communication circuit and USB interface, binary channels DAC drive constant current source circuit's output connection first micropin interface reaches the second micropin interface, three electrode sensor interface connection front end sensor modulate circuit's input, microcontroller circuit connection front end sensor modulate circuit binary channels DAC drive constant current source circuit communication circuit reaches the USB interface, power supply circuit connects front end sensor modulate circuit binary channels DAC drive constant current source circuit microcontroller circuit reaches communication circuit.
Optionally, the three-electrode sensor interface comprises a metal microneedle array biosensor interface and/or a flexible printed electrode sensor FPC interface.
Optionally, the front-end sensor conditioning circuit comprises a chip LMP 91000.
Optionally, the microcontroller circuit comprises a chip STM32F103RET 6.
Optionally, the dual channel DAC driven constant current source circuit comprises an on-chip DAC 8562.
Optionally, the communication circuit is a bluetooth circuit.
Optionally, the bluetooth circuitry comprises a chip RF-BM-4044B 4.
In a second aspect, an embodiment of the present invention provides an electrochemical sensor detection apparatus, including the detection circuit, the microneedle detection module, the microneedle treatment module, and the three-electrode sensor described in the first aspect, where the three-electrode sensor is connected to the front-end sensor conditioning circuit, the microneedle detection module is connected to the first microneedle interface, and the microneedle treatment module is connected to the second microneedle interface.
Optionally, the three-electrode sensor comprises a metal microneedle array biosensor or a flexible printed electrode sensor.
In a third aspect, an embodiment of the present invention provides an electrochemical sensor detection system, including the detection device according to the second aspect and an electronic device, where the detection device communicates with the electronic device through the communication circuit.
The implementation of the embodiment of the utility model has the following beneficial effects: according to the embodiment of the utility model, the front-end sensor conditioning circuit receives signals input by the three-electrode sensor interface to detect the human tissue fluid, and the dual-channel DAC drives the constant current source circuit to drive the modules of the first microneedle interface and the second microneedle interface to extract the tissue fluid and release the therapeutic drugs, so that the painless minimally invasive detection of the human tissue fluid and the release of the therapeutic drugs are realized, the cost is low, and the popularization is convenient.
Drawings
FIG. 1 is a block diagram of a detection circuit of an electrochemical sensor according to an embodiment of the present invention;
fig. 2 is a connection diagram of a front-end sensor conditioning circuit and a microcontroller according to an embodiment of the present invention;
FIG. 3 is a circuit schematic of a front-end sensor conditioning circuit provided by an embodiment of the present invention;
FIG. 4 is a schematic circuit diagram of a microprocessor according to an embodiment of the present invention;
FIG. 5 is a schematic circuit diagram of a dual-channel DAC driving constant current source circuit according to an embodiment of the present invention;
FIG. 6 is a circuit schematic of a communication circuit provided by an embodiment of the present invention;
FIG. 7 is a schematic diagram of a circuit for converting an input voltage to a voltage of 5V according to an embodiment of the present invention;
FIG. 8 is a schematic diagram of a circuit for converting 5V voltage to 3.3V voltage according to an embodiment of the present invention;
FIG. 9 is a schematic diagram of a circuit for converting a voltage of 5V to a voltage of 20V according to an embodiment of the present invention;
FIG. 10 is a schematic circuit diagram of a USB interface according to an embodiment of the present invention;
FIG. 11 is a block diagram of an electrochemical sensor detection device according to an embodiment of the present invention;
FIG. 12 is a block diagram of an electrochemical sensor detection system according to an embodiment of the present invention;
FIG. 13 is a data diagram illustrating the results of measuring glucose concentration using a metal microneedle array biosensor according to an embodiment of the present invention;
fig. 14 is a data diagram illustrating the results of a cyclic voltammetry test performed on a flexible printed electrode sensor according to an embodiment of the present invention.
Detailed Description
The utility model is described in further detail below with reference to the figures and the specific embodiments.
As shown in fig. 1, an embodiment of the present invention provides an electrochemical sensor detection circuit, including: three electrode sensor interfaces, first micropin interface, second micropin interface, front end sensor modulate circuit, binary channels DAC drive constant current source circuit, microcontroller circuit, power supply circuit, communication circuit and USB interface, binary channels DAC drive constant current source circuit's output connection first micropin interface reaches the second micropin interface, three electrode sensor interface connection front end sensor modulate circuit's input, microcontroller circuit connection front end sensor modulate circuit binary channels DAC drive constant current source circuit communication circuit reaches the USB interface, power supply circuit connects front end sensor modulate circuit binary channels DAC drive constant current source circuit microcontroller circuit reaches communication circuit.
Specifically, the first microneedle interface and the second microneedle interface are respectively used for connecting the microneedle detection module and the microneedle treatment module, and the microcontroller controls the output current by controlling the reference voltage of the dual-channel DAC driving constant current source circuit, so that the microneedle detection module is controlled by the output current to extract the human tissue fluid and the microneedle treatment module releases the treatment drug; the three-electrode sensor interface is used for connecting a test electrode, and the test electrode is sampled by the front-end sensor conditioning circuit and is sent to the microcontroller circuit; the microcontroller circuit is communicated with external electronic equipment through the communication circuit; the power supply circuit provides power for the whole circuit; the microcontroller circuit may also provide power and communication through a USB interface.
The implementation of the embodiment of the utility model has the following beneficial effects: according to the embodiment of the utility model, the front-end sensor conditioning circuit receives signals input by the three-electrode sensor interface to detect the human tissue fluid, and the dual-channel DAC drives the constant current source circuit to drive the modules of the first microneedle interface and the second microneedle interface to extract the tissue fluid and release the therapeutic drugs, so that the painless minimally invasive detection of the human tissue fluid and the release of the therapeutic drugs are realized, the cost is low, and the popularization is convenient.
Optionally, the front-end sensor conditioning circuit comprises a chip LMP 91000.
Specifically, the front-end sensor conditioning module builds a signal conditioning circuit of the electrochemical sensor by an electrochemical analog front-end chip LMP91000 of TI (Texas instruments) and peripheral devices. As shown in fig. 2, the core circuit of LMP91000 is a potentiostat circuit, which consists of a differential input amplifier a1, amplifier a1 for comparing the potential between working electrode WE and reference electrode RE with the bias potential required for the electrochemical sensor (chip internal registers are set by the I2C interface). The potentiostat compares the reference electrode RE voltage to the desired bias voltage and adjusts the voltage on the counter electrode CE to maintain a constant voltage difference between the appropriate working electrode WE and the reference electrode RE. In the application, a reference voltage VREF of LMP91000 is newly designed, and an internal DAC of a main control chip is used for flexibly providing an adjustable reference voltage in a large range; the working potentials of different sensors for obtaining the optimal sensitivity are often different, and the design can cover the sensors in a wider working voltage range; in addition, the reference voltage pin VREF can be accessed to triangular wave excitation, so that a volt-ampere detection method is realized; the pins B1 and B2 are connected with a resistor with a wider resistance range by disabling the resistor of the internal trans-impedance amplifier, so that the detection of weak sensor response current with larger upper and lower limits is realized.
It should be noted that LMP91000 is selected as a chip of the front-end sensor conditioning circuit, which is low in cost, 3x5cm in area, wearable, and capable of meeting various measurement requirements.
Optionally, the microcontroller circuit comprises a chip STM32F103RET 6.
Specifically, referring to fig. 4, the controller circuit adopts a chip STM32F103RET6, and further includes a voltage filter circuit of a crystal oscillator circuit X1, 3.3V.
Specifically, referring to fig. 2, 3 and 4, SCL and SDA of LMP91000 are respectively connected to the 58 th pin SCL and the 59 th pin SDA of microcontroller STM32F103RET6, the output voltage pin VREF of LMP91000 is connected to the 20 th pin of microcontroller STM32F103RET6, the output VOUT of LMP91000 is connected to the 22 th pin of microcontroller STM32F103RET6, and the CE, RE and WE pins of LMP91000 are respectively connected to the CE, RE and WE interfaces of the three-electrode interface. It should be noted that the three-electrode interface may include 3 interfaces, such as CE, RE, and WE interfaces, and the three-electrode interface may include 4 interfaces, such as CE, WE, and 2 RE interfaces, which are specifically configured according to the application.
Optionally, the dual channel DAC driven constant current source circuit comprises an on-chip DAC 8562.
Specifically, referring to fig. 4 and 5, the dual-channel DAC driving constant current source circuit is composed of a dual-channel digital-to-analog converter DAC8562, a low-power-consumption dual-channel operational amplifier AD8607 and a field effect transistor; U1A and U1B are operational amplifiers, and Q1 and Q2 can be IRLML2402 GTRPBF. The dual-channel digital-to-analog converter is used for generating constant voltage, the low-power-consumption dual-channel operational amplifier generates two paths of constant current source circuits after signal conditioning, a current _ out1 and a current _ out2 are provided for the operation of the micro-needle, and the current _ out1 and the current _ out2 are respectively connected with the first micro-needle interface and the second micro-needle interface.
It should be noted that, the dual-channel DAC8562 DAC chip has a resolution of 16 bits, and can generate waveform excitation with high precision. The microcontroller performs chip control and waveform excitation programming and generation through a high-speed SPI interface, the DAC outputs the analog bandwidth of 350KHz, and the DAC outputs the response of 10uS to 0.003 percent FSR. The AD8607 and the IRLML2402GTRPBF field effect transistor form a constant current output module, and the effect of voltage linear control current is realized by adopting the field effect transistor. When the fet operates normally in the saturation region, the drain current Id is controlled by the voltage Ugs, and the relationship Id ═ f (Ugs) holds when Ud is constant, where the value of Id is constant as long as Ugs remains constant. In the circuit module, R3 and R7 are sampling resistors, and high-precision resistors with the resistance of 1k ohm are adopted. The operational amplifier adopts AD8607 as a voltage follower, UI Up Un, because the gate current Is relatively small and negligible, so the fet Id Is, so Io Id Is Un/R3 VOUTA/R3, and when the output voltage Is VOUTB, Io Id Is Un/R7 Is VOUTB/R7. Therefore, the input voltage of the circuit can play a role in controlling the current Io, and the adjustable current I loaded on the micro-needle is as follows: and Io (VOUTA/R3) or Io (VOUTB/R7) meets the design requirements of voltage control and constant current.
Note that, CLR: asynchronously clear the input, the falling edge is valid, after triggering, DAC8562 outputs the lowest voltage value, the 24 th clock falling edge of the user write operation will exit the clear mode, activate the clear mode will terminate the write operation; din: a 24-bit input shift register to which data is written per clock falling edge; LDAC: in synchronous mode, data update occurs at the falling edge of 24 th SCLK period, and then with the falling edge of SYNC, the synchronous update does not need LDAC, and LDAC must be permanently grounded, or the low level is kept when sending command to the device, in asynchronous mode, LDAC is low level trigger for synchronous DAC update, which can be set by multiple single channel commands, and then a falling edge is generated on LDAC pin to synchronously update DAC output register; SCLK: a clock input end supporting 50 MHz; SYNC (chip select): active low, when SYNC goes low, it enables the input shift register and the data sample is on the following clock falling edge, the DAC output is updated after the 24 th clock falling edge, if SYNC goes high before the 23 th clock edge, the rising edge of SYNC will act as an interrupt and the DAC8562 device will ignore the write sequence.
Optionally, the communication circuit is a bluetooth circuit.
Optionally, the bluetooth circuitry comprises a chip RF-BM-4044B 4.
Specifically, referring to fig. 6, the bluetooth circuit employs a bluetooth module RF-BM-4044B, which can be applied to the wireless communication field and has the characteristics of low power consumption, small size, long transmission distance, strong interference rejection, and the like. Can be used to develop APP electrochemistry sensing control system based on the bluetooth through this module, further improve the wearable function and the intelligent experience of system.
Specifically, the voltage values required to be provided by the power circuit include 5V, 3.3V and 20V, referring to fig. 7, the input voltage is a 3.7V lithium battery, and the 3.7V voltage is converted into 5V voltage by the component LM2704 MF-ADJ; referring to fig. 8, 5V is converted into 3.3V by the component LM1117-3V 3; referring to fig. 9, the voltage of 5V is converted to 20V by the component LM2704 MF-ADJ. The voltage of 3.3V supplies power to LMP91000 and the microprocessor, and the voltage of 5V and the voltage of 20V supply power to the dual-channel DAC driving constant current source circuit.
In addition, referring to fig. 10, the input voltage may also be provided through a USB interface, the USB interface is connected to an external low ripple voltage-stabilized power supply with positive and negative 5V, the USB outputs USB D-and USB D + to the microcontroller, and the USB interface may also provide a voltage of 3.3V.
Optionally, the three-electrode sensor interface comprises a metal microneedle array biosensor interface and/or a flexible printed electrode sensor FPC interface. As shown in fig. 3, the metal microneedle array biosensor interface may employ JP1, and the flexible printed electrode sensor FPC interface may employ JP 5.
It should be noted that the metal microneedle array biosensor interface integrates a three-electrode system, and as a transdermal tool, the metal microneedle array biosensor interface brings the sensing modulus of Pt/rGO into a carrier of an internal environment, and the Pt/rGO nanostructure on the surface of the microneedle is protected by a layer of water-soluble polymer in the transdermal process to prevent from being damaged due to mechanical friction. After the microneedle enters into the subcutaneous part, the polymer layer can be dissolved by interstitial fluid, so that the Pt/rGO microneedle electrode is exposed again to detect the blood glucose concentration in vivo. The FPC interface of the flexible printed electrode sensor can be used for connecting a flexible three-electrode sensing device, and the flexible printed electrode sensor detects the concentration change of an object to be detected in reaction based on the principle that the enzyme is specifically combined with the object to be detected to generate electron migration.
Referring to fig. 11, an embodiment of the present invention provides an electrochemical sensor detection apparatus, including the detection circuit, the microneedle detection module, the microneedle treatment module, and the three-electrode sensor according to the first aspect, where the three-electrode sensor is connected to the front-end sensor conditioning circuit, the microneedle detection module is connected to the first microneedle interface, and the microneedle treatment module is connected to the second microneedle interface.
Specifically, the microneedle detection module can be connected with microneedle ion electrophoresis detection, and the principle of the method is that the tissue fluid is extracted by adding current, and then the related indexes of the tissue fluid are detected by a three-electrode system. The microneedle therapy module can release an electrophoretic drug through microneedle ions, and the principle of the method is that the drug permeates through adding current; the medicine is put in the back of the treatment micro-needle, and because the medicine has electric charge, when direct current is introduced into the solution, the charged medicine can gradually permeate into tissue fluid in an ion electrophoresis mode, then enter the tissue fluid of a human body and participate in the blood circulation of the body, and then the specific treatment effect of the medicine is exerted.
The implementation of the embodiment of the utility model has the following beneficial effects: according to the embodiment of the utility model, the front-end sensor conditioning circuit receives signals input by the three-electrode sensor interface to detect the human tissue fluid, and the dual-channel DAC drives the constant current source circuit to drive the modules of the first microneedle interface and the second microneedle interface to extract the tissue fluid and release the therapeutic drugs, so that the painless minimally invasive detection of the human tissue fluid and the release of the therapeutic drugs are realized, the cost is low, and the popularization is convenient.
Optionally, the three-electrode sensor comprises a metal microneedle array biosensor or a flexible printed electrode sensor.
The microneedle-based biosensor has the characteristics of good skin penetration, low pain, and high sensitivity, and can be easily fabricated into various patterns. Transdermal biosensing by microneedles offers significant opportunities for mobile biosensing technologies and biochips. However, in the detection process, the enzyme modified on the surface of the microneedle array electrode is easy to fall off due to the action of friction force, and in-vivo detection is not easy to realize. In order to prevent a microneedle electrode from easily falling off after entering the skin in the detection process and reduce the pain of a user, a novel microneedle structure is designed. The microneedles were designed in a hook shape, the length of the microneedle electrode was 800 μm, the width of the microneedle electrode was 122 μm, the hook angle of the needles was 45 °, the interval between the needles was 385 μm, and the area of the entire microneedle patch was (5.8mm × 6.0 mm). An electrochemical sensing detection structure of Au-Pt-PB-glucose oxidase-PU is constructed by layer-by-layer assembly on a blank microneedle; the sensor is used as a sensing detection device by combining a porous membrane attached with glucose oxidase and a platinum electrode modified by nano-structure gold and Prussian blue, wherein the GOD can oxidize glucose into gluconic acid and hydrogen peroxide, and the PB membrane has good electrocatalytic reduction property on the hydrogen peroxide. Gold is a good conductor of electricity, electrons can be transferred between the redox center (FAD) of glucose oxidase and an electrode, and the glucose concentration in vivo can be analyzed by detecting the current response by using a sensor so as to diagnose diabetes. According to the difference of the active biological substances modified by the micro-needle, the method can also be applied to the specific detection of physiological markers such as lactic acid, uric acid, cholesterol and the like except glucose, and can be used for diagnosing over-fatigue, hypoxia, heart disease, gout, obesity and the like.
The flexible printed electrode sensor adopts magnetron sputtering nano-gold to form an electrode substrate, and then the prepared bioactive substance is coated on the electrode substrate.
Referring to fig. 12, an embodiment of the present invention provides an electrochemical sensor detection system, including the detection device according to the embodiment of the second aspect and an electronic device, where the detection device communicates with the electronic device through the communication circuit.
It should be noted that the electronic device includes a mobile phone, a tablet computer, a desktop computer, a notebook computer, an electronic watch, and the like, and the electronic device is used for displaying a test result, processing experiment data, configuring test parameters, and the like.
The working process of the system is as follows: at the beginning of the program operation, the peripheral equipment needs to be initialized, for example, peripheral equipment such as a GPIO, a DAC, an ADC, a USB interface, an IIC interface, an SPI interface, a TIM, an LED, and the like used in the system configure the used IO interface; writing NVIC function of software, and determining the interrupt priority and the configuration of priority grouping of each peripheral; the microprocessor circuit generates a reference voltage of LMP91000 through an internally integrated DAC (digital-to-analog converter), controls the LMP91000 front-end sensor conditioning circuit to perform frequency division setting on the reference voltage through an I2C interface configuration to generate a constant voltage suitable for the working of the electrochemical sensor, the constant voltage is input into a constant potential module inside LMP910000, the constant potential module constantly follows an excitation signal to a micro-needle array sensor interface or a flexible electrochemical sensor FPC (flexible printed circuit) interface, and the microprocessor circuit controls the LMP91000 front-end sensor conditioning circuit to perform the configuration of registers such as gain multiples, load resistance, internal zero potential, bias potential, working modes and the like through an I2C interface configuration; the double-channel DAC is controlled by the SPI bus to drive the constant current source circuit to generate constant current to start the microneedle detection module and the microneedle treatment module; the ADC is triggered by timer interruption and DMA interruption of the microprocessor control circuit to complete data acquisition and filtering denoising processing, and the data is sent to a mobile phone or a computer end through the wireless Bluetooth circuit for further processing.
The practical application of the above system is illustrated in two specific embodiments.
The first embodiment is as follows:
in this embodiment, the three-electrode sensor continuously monitors the blood glucose concentration by using a metal microneedle array biosensor. The physical examination test is carried out on the back of a rat, fasting and water prohibition are carried out for 24h before the test, hairs on the back are removed after anesthesia, the detection device is fixed on the skin of the back, an i-t test is carried out under the voltage of 0.7V, after 25min of stabilization, glucose solution is injected into the abdominal cavity, the blood sugar on the tail is measured every 200s, 30s of continuous measurement are carried out every time, and 8 times of measurement are carried out; the measurement results are shown in fig. 13, and the results show that the glucose concentration detected by the above detection device is very close to the actual value, and the conformity degree reaches more than 0.99.
Example two:
in the embodiment, the three-electrode sensor adopts a flexible printed electrode sensor, and adopts cyclic voltammetry to perform electrochemical analysis, so as to be used for detecting the concentration of biomarkers such as glucose, lactic acid or uric acid in sweat. The method comprises the steps of modifying a specific active substance containing a specific substance to be detected on a flexible screen printing electrode sensor, connecting the flexible screen printing electrode sensor to an FPC electrode interface clamp, dropwise adding 1 mu L of a solution to be detected (glucose solution) into the center of an electrode of the sensor by using a liquid-transferring gun, enabling a marker to be detected to react with the active substance on the sensor to generate electronic migration, enabling a wireless flexible electrochemical sensing device to sensitively acquire the change of current response, sending the change to a mobile phone APP through wireless Bluetooth for real-time monitoring, storing data for curve drawing and secondary processing, and displaying the result in a graph 14.
The implementation of the embodiment of the utility model has the following beneficial effects: according to the embodiment of the utility model, the front-end sensor conditioning circuit receives signals input by the three-electrode sensor interface to detect the human tissue fluid, and the dual-channel DAC drives the constant current source circuit to drive the modules of the first microneedle interface and the second microneedle interface to extract the tissue fluid and release the therapeutic drugs, so that the painless minimally invasive detection of the human tissue fluid and the release of the therapeutic drugs are realized, the cost is low, and the popularization is convenient.
While the preferred embodiments of the present invention have been illustrated and described, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the utility model as defined by the appended claims.
Claims (10)
1. An electrochemical sensor detection circuit, comprising: three electrode sensor interfaces, first micropin interface, second micropin interface, front end sensor modulate circuit, binary channels DAC drive constant current source circuit, microcontroller circuit, power supply circuit, communication circuit and USB interface, binary channels DAC drive constant current source circuit's output connection first micropin interface reaches the second micropin interface, three electrode sensor interface connection front end sensor modulate circuit's input, microcontroller circuit connection front end sensor modulate circuit binary channels DAC drive constant current source circuit communication circuit reaches the USB interface, power supply circuit connects front end sensor modulate circuit binary channels DAC drive constant current source circuit microcontroller circuit reaches communication circuit.
2. The electrochemical sensor detection circuit of claim 1, wherein the three-electrode sensor interface comprises a metal microneedle array biosensor interface and/or a flexible printed electrode sensor (FPC) interface.
3. The electrochemical sensor detection circuit of claim 1, wherein the front-end sensor conditioning circuit comprises a chip LMP 91000.
4. The electrochemical sensor detection circuit of claim 1, wherein the microcontroller circuit comprises a chip STM32F103RET 6.
5. The electrochemical sensor detection circuit of claim 1, wherein the dual channel DAC driven constant current source circuit comprises an on-chip DAC 8562.
6. The electrochemical sensor detection circuit of claim 1, wherein the communication circuit is a bluetooth circuit.
7. The electrochemical sensor detection circuit of claim 6, wherein the bluetooth circuit comprises a chip RF-BM-4044B 4.
8. An electrochemical sensor detection device, comprising the detection circuit, the microneedle detection module, the microneedle treatment module and the three-electrode sensor according to any one of claims 1 to 7, wherein the three-electrode sensor is connected to the front-end sensor conditioning circuit, the microneedle detection module is connected to the first microneedle interface, and the microneedle treatment module is connected to the second microneedle interface.
9. The electrochemical sensor detection device according to claim 8, wherein the three-electrode sensor comprises a metal micro-needle array biosensor or a flexible printed electrode sensor.
10. An electrochemical sensor detection system comprising a detection device according to any one of claims 8 to 9 and an electronic device, said detection device communicating with said electronic device via said communication circuit.
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| CN110974251A (en) * | 2019-12-17 | 2020-04-10 | 中山大学·深圳 | Micro-needle pressing type electrochemical sensor based on mobile phone platform |
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