A laser-induced graphene immunoassay platform for rapid, low-cost remote medical testing.

Abstract

The application discloses a kind of laser-induced graphene immune rapid low-cost remote medical detection platform, it is related to biomedical detection technical field, the platform includes following component part: sensor array module: using CO2 laser engraving technology is formed on polyimide substrate and contains 4 graphene working electrode, 1 Ag / AgCl reference electrode and 1 graphene counter electrode patterned structure, through 1-pyrene butyric acid functionalization after specific antibody is fixed and is blocked with bovine serum albumin;The application greatly reduces the detection cost by using laser engraving graphene electrode preparation process, at the same time, by constructing the sensor array module comprising four graphene working electrode, a plurality of antibodies can be specifically fixed, the simultaneous detection of SARS-CoV-2 nucleocapsid protein, spike protein specific IgM / IgG antibody and C-reactive protein and other multiplex biomarkers is realized, sample detection cycle can be controlled within 10 minutes, greatly improve detection efficiency.

Description

Technical Field

[0001] This invention relates to the field of biomedical detection technology, specifically to a laser-induced graphene immunoassay platform for rapid, low-cost, and remote medical detection. Background Technology

[0002] In the field of biomedical testing technology, with the frequent outbreaks of infectious diseases and the increasing demand for health monitoring, rapid, accurate, and convenient medical testing methods are particularly important. Infectious diseases are characterized by rapid spread and wide impact, and early rapid diagnosis is crucial for controlling the spread and developing effective treatment plans. At the same time, the modern medical model is gradually shifting towards telemedicine and home health monitoring. This requires testing technologies to not only have the ability to conduct rapid on-site testing but also to achieve remote data transmission so that doctors can obtain patients' test information in a timely manner and conduct remote diagnosis. However, existing testing technologies still face many challenges in meeting these needs and urgently require new technological breakthroughs and innovations.

[0003] In the field of rapid diagnosis of infectious diseases, existing detection technologies have significant limitations. While real-time quantitative PCR (qPCR) has high sensitivity and specificity, it heavily relies on expensive equipment and professional operators. The testing process is complex and time-consuming, often requiring several hours or even longer to obtain results, making it difficult to meet the needs of rapid on-site diagnosis. Serological methods based on antibody detection, although relatively simple to operate, cannot effectively distinguish between infection and immune status and lack the ability to comprehensively assess disease progression, potentially leading to misdiagnosis or missed diagnosis. Furthermore, most existing point-of-care testing (POCT) devices can only detect a single indicator and cannot perform combined analysis of multiple biomarkers. At the same time, these devices generally lack remote data transmission capabilities, and test results cannot be uploaded to telemedicine platforms in a timely manner, making it difficult to meet the needs of modern telemedicine monitoring. Summary of the Invention

[0004] The purpose of this invention is to overcome the shortcomings of existing technologies and provide a laser-induced graphene immunoassay platform for rapid, low-cost, and remote medical detection. This platform utilizes CO2 laser engraving technology to form patterned electrode structures on polyimide substrates. Traditional preparation methods suffer from high production costs, complex processes, and difficulties in mass production, severely hindering the industrialization of graphene-based biosensors. This results in high costs for traditional graphene-based detection platforms, making it difficult to meet the needs of primary healthcare and large-scale screening. This invention, by employing a laser-induced graphene preparation process, eliminates the high costs and complex processes of traditional chemical vapor deposition and redox methods. Laser engraving technology can directly create patterned electrode structures on polyimide substrates. In-situ generation of graphene on an amine substrate reduces material costs and supports roll-to-roll mass production, meeting the needs of large-scale testing. Furthermore, functionalization immobilizes multiple antibodies, enabling simultaneous detection of multiple biomarkers. Combined with an electrochemical detection module and a wireless transmission and electronic control module, it achieves simultaneous acquisition and wireless transmission of four-channel electrochemical signals. Simultaneously, a standardized sample pretreatment process is established, supporting direct detection of non-invasive samples such as saliva. This invention offers advantages such as low cost, high-throughput mass production, rapid detection, support for non-invasive sample detection, and remote data transmission. It can be widely applied in on-site diagnosis of infectious diseases and home health monitoring scenarios, providing technical support for rapid response to public health emergencies.

[0005] To solve the above-mentioned technical problems, the present invention provides the following technical solution: a laser-induced graphene immunoassay rapid and low-cost remote medical detection platform, the method comprising the following specific steps:

[0006] Sensor array module: A patterned structure containing four graphene working electrodes, one Ag / AgCl reference electrode and one graphene counter electrode is formed on a polyimide substrate using CO2 laser engraving technology. After functionalization with 1-pyrene butyric acid, a specific antibody is fixed and blocked with bovine serum albumin.

[0007] Electrochemical detection module: Based on differential pulse voltammetry and electrochemical impedance spectroscopy, using a double sandwich and indirect immunoassay strategy, diluted blood or saliva samples are incubated, and then combined with enzyme-labeled antibodies and collected in a buffer solution containing hydroquinone and hydrogen peroxide.

[0008] Wireless Transmission and Electronic System Module: Based on the Arm Cortex-M4 microcontroller, it integrates a Bluetooth module and signal processing circuit, is powered by a lithium-ion polymer battery, and controls the detection timing through firmware to realize wireless data transmission.

[0009] Sample processing module: Blood samples are diluted 1:100 with PBS containing 1.0% BSA, and saliva samples are diluted 1:5 with PBS, and then used directly for sensor array detection.

[0010] Furthermore, the sensor array module is patterned on a polyimide substrate using CO2 laser engraving technology, forming a patterned structure comprising four graphene working electrodes, one Ag / AgCl reference electrode, and one graphene counter electrode. The laser engraving power is 8.0%, the speed is 15%, and the number of dots per inch is 1000. This laser engraving process, through precise control of power and speed, directly transforms the PI substrate into a porous graphene structure. The mesoporous design significantly increases the specific surface area, providing more active sites for biomolecule adsorption and improving detection sensitivity. The specific surface area reaches 1200 m². 2 The / g,Ag / AgCl reference electrode was electrodeposited at a current of -0.2mA for 100 seconds in a mixed solution containing 250mM silver nitrate, 750mM sodium thiosulfate and 500mM sodium bisulfite, followed by drop casting of FeCl3 solution for 1 minute.

[0011] Furthermore, in the sensor array module, the electrode surface is modified with π-π stacking using a 5.0 mM 1-pyrene butyric acid (PBA) DMF solution. After activation with 0.4 M EDC and 0.1 M sulfonyl-NHS, 250 μg / mL of S1-IgG, S1-IgM, CRP antibody, or 50-fold diluted NP antibody is fixed by amide bonds, and unreacted sites are blocked with 2.0% bovine serum albumin solution.

[0012] Furthermore, the electrochemical detection module is based on differential pulse voltammetry (DPV) and open-circuit potential electrochemical impedance spectroscopy (EIS). It employs a double sandwich and sandwich detection configuration for SARS-CoV-2 nucleocapsid protein NP and C-reactive protein CRP, and uses an indirect immunoassay method for S1-IgG and S1-IgM.

[0013] Furthermore, in the electrochemical detection module, during detection, blood samples are diluted 100 times with PBS containing 1.0% BSA, and saliva samples are diluted 5 times. 10 μL of each sample is incubated with the functionalized electrode for 1-10 minutes, HRP-labeled detection antibody is added, and the mixture is incubated at room temperature for 5 minutes. Then, 1.0 mM H2O2 is added to 0.05 M sodium phosphate buffer containing 2.0 mM hydroquinone HQ, and the amperometric signal is recorded at a potential of 0.2 V relative to Ag / AgCl.

[0014] Furthermore, in the electrochemical detection module, HRP-labeled detection antibodies are added. For NP detection, the antibody is diluted 250 times. For S1-IgG and S1-IgM, the concentration is 2.0 mg / mL. For NP detection, an additional incubation of 1.0 mg / mL HRP-goat anti-rabbit IgG for 5 minutes is required.

[0015] Furthermore, in the electrochemical detection module, the DPV detection conditions are: potential range -0.2~0.6V, pulse width 0.2s, incremental potential 4mV, amplitude 50mV; EIS reaction conditions: frequency range 0.1~10 6 Hz, amplitude 5mV.

[0016] Furthermore, the wireless transmission and electronic system module is based on an STM32L432KC microcontroller, integrating an SPBT3.0DP2 Bluetooth 5.0 module, supporting data transmission within a 10-meter range, using the BLE (Bluetooth Low Energy) protocol with a transmission rate of 1Mbps. The signal processing circuit consists of an AD8605 single op-amp and an AD8608 quad op-amp, forming a transimpedance amplifier circuit with a current detection resolution of 1nA. The power system uses a 3.7V / 500mAh lithium-ion polymer battery, paired with an ISL60002 voltage reference chip, achieving low-power control through PWM pulse width modulation, with a standby current of <10μA and a power consumption of 15mW in continuous detection mode. The PCB board uses a 4-layer immersion gold process, with dimensions of 20mm×35mm×7.3mm, and integrates a 4-channel 16-bit ADC with a sampling rate of 10kHz. Data is transmitted to the Bluetooth module via a UART interface, supporting real-time reception by the device's APP.

[0017] Furthermore, the sample processing module: blood samples are stored in blood collection tubes containing EDTA, and diluted 1:100 with 0.01M PBS containing 1.0% BSA before testing. 0.05% sodium azide is added to the diluent. Saliva samples are collected using a sterile funnel, and immediately diluted 1:5 with PBS containing 1.0% BSA after collection. 0.1% Tween-20 is added to the diluent to enhance protein solubility. All diluted samples are tested within 2 hours.

[0018] Compared with existing technologies, this laser-induced graphene immunoassay rapid and low-cost remote medical detection platform has the following advantages:

[0019] I. This invention significantly reduces detection costs by employing a laser-engraved graphene electrode fabrication process. Furthermore, by constructing a sensor array module containing four graphene working electrodes, it can specifically immobilize multiple antibodies, enabling simultaneous detection of multiple biomarkers such as SARS-CoV-2 nucleocapsid protein, spike protein-specific IgM / IgG antibodies, and C-reactive protein. The sample detection cycle can be controlled within 10 minutes, greatly improving detection efficiency and providing strong support for rapid on-site diagnosis of infectious diseases. It can be widely applied in rapid response scenarios for public health emergencies.

[0020] Second, by integrating Bluetooth wireless transmission, this invention enables the real-time uploading of detection data to a remote medical platform, achieving portable remote diagnosis. This allows the detection results to be promptly transmitted to medical personnel, facilitating remote diagnosis and treatment guidance, thus improving the efficiency and accessibility of medical services. Furthermore, this invention supports direct detection of non-invasive samples such as saliva, reducing patient discomfort and further enhancing the user experience, providing convenience for home health monitoring of infectious diseases.

[0021] Third, this invention adopts a laser-induced graphene preparation process, which eliminates the high cost and complex process of traditional chemical vapor deposition, redox and other methods. Laser engraving technology can directly generate graphene in situ on polyimide substrates, reducing material costs and supporting roll-to-roll mass production to meet large-scale testing needs.

[0022] Other advantages, objectives and features of the invention will be set forth in part in the description which follows, and in part will be apparent to those skilled in the art from the following examination or study, or may be learned from the practice of the invention. Attached Figure Description

[0023] To more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the accompanying drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are merely some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without any creative effort.

[0024] Figure 1 This is a schematic diagram of the structure of a laser-induced graphene immune rapid and low-cost remote medical detection platform;

[0025] Figure 2 This is a flowchart of a laser-induced graphene immune rapid and low-cost remote medical testing platform. Detailed Implementation

[0026] To further illustrate the technical means and effects of the present invention in achieving its intended purpose, the following detailed description of the specific implementation methods, structures, features, and effects of the present invention, in conjunction with the accompanying drawings and preferred embodiments, is provided below.

[0027] Example 1

[0028] Electrode arrays were fabricated on a 125 μm thick polyimide (PI) film using CO2 laser engraving technology. The engraving parameters were 8.0% power, 15% speed, and 1000 dpi resolution. Four 2 mm × 3 mm mesoporous graphene working electrodes (specific surface area 1200 m²) were formed in grating mode. 2A ring-shaped Ag / AgCl reference electrode with an inner diameter of 1 mm and a 5 mm × 5 mm graphene counter electrode were prepared. Laser engraving, through precise control of power and speed, directly transformed the PI substrate into a porous graphene structure. The mesoporous design significantly increased the specific surface area, providing more active sites for biomolecule adsorption and improving detection sensitivity. In the preparation of the Ag / AgCl reference electrode, the Ag electrode was first immersed in a mixed solution containing 250 mM silver nitrate, 750 mM sodium thiosulfate, and 500 mM sodium bisulfite, and electrodeposited at a current of -0.2 mA for 100 seconds, followed by a drop casting of 10 μL of 10% FeCl3 solution for oxidation treatment for 1 minute. This process eliminates the high-temperature environment and complex precursors required for chemical vapor deposition, directly inducing PI carbonization to form porous graphene. This improves material utilization and supports roll-to-roll mass production, significantly increasing production capacity compared to micromechanical exfoliation. Furthermore, the mesoporous structure allows for a specific surface area of ​​1200 m². 2 / g provides abundant active sites for antibody immobilization.

[0029] 10 μL of 5.0 mM 1-pyrenebutyric acid (PBA) in DMF solution was dropped onto the electrode surface and incubated for 2 hours in a controlled environment (RH 50%). The electrode was then rinsed sequentially with DMF, isopropanol, and deionized water. PBA covalently binds to the graphene surface through π-π stacking, avoiding disruption of the graphene's conjugated structure. Simultaneously, carboxyl functional groups are introduced for antibody immobilization. The electrode was then immersed in 0.025 M HCl containing 0.4 M EDC and 0.1 M sulfonyl-NHS. Activate with MES buffer (pH 6.5) for 35 minutes, then drop 5 μL of mouse anti-SARS-CoV-2 nucleocapsid protein (NP) monoclonal antibody, rabbit anti-S1-IgG antibody, goat anti-S1-IgM antibody, and rabbit anti-C-reactive protein (CRP) monoclonal antibody at a concentration of 250 μg / mL. Incubate at room temperature for 3 hours. Activate carboxyl groups with EDC / sulfonyl-NHS to promote antibody fixation via amide bonds, maintaining the active conformation of the antibodies. Finally, block with 0.01M PBS solution containing 2.0% bovine serum albumin (BSA) for 90 minutes. BSA blocks unreacted sites, reduces non-specific adsorption, lowers background signal interference, and improves detection specificity.

[0030] Collect 2 mL of venous blood from the patient into a vacuum blood collection tube containing EDTA. Take 20 μL of blood and dilute it 100 times with 0.01M PBS (pH 7.4) containing 1.0% BSA and 0.05% sodium azide to 2 mL. Take 10 μL of the diluted sample and drop it onto the surface of the functionalized electrode. Incubate at 37°C for 10 minutes. Wash 3 times with PBS. EDTA anticoagulates to prevent blood clotting, BSA maintains protein stability, sodium azide inhibits microbial growth, and incubation at 37°C simulates physiological temperature, accelerates antigen-antibody binding kinetics, and shortens reaction time.

[0031] Add 250-fold diluted HRP-labeled detection antibodies (HRP-labeled rabbit anti-NP polyclonal antibody for NP detection, and HRP-labeled goat anti-CRP polyclonal antibody for CRP detection), incubate for 5 minutes, wash, and then add an additional 1.0 mg / mL of HRP-goat anti-rabbit IgG antibody for NP detection, incubate for 5 minutes. The HRP-labeled antibodies form a signal amplification system through antigen-antibody specific binding, and the enzyme catalyzes the substrate to generate an electrochemical signal. The double antibody sandwich strategy (NP detection) further improves the detection sensitivity and reduces the detection limit to 500 pg / mL.

[0032] Electrochemical detection was performed on a CHI820 electrochemical workstation. The three-electrode system was placed in 0.05M sodium phosphate buffer (pH 6.0) containing 2.0mM hydroquinone (HQ). After adding 1.0mM H2O2, the signal was acquired by chronoamperometry at a potential of -0.2V (vs Ag / AgCl) with a sampling rate of 10kHz. Hydroquinone acts as an electron mediator to accelerate the electron transfer of H2O2 catalyzed by HRP, generating a quantifiable current signal on the electrode surface. The pH 6.0 buffer optimizes enzyme activity and ensures signal stability. The high sampling rate ensures accurate capture of the current signal, providing a data basis for quantitative analysis.

[0033] The built-in STM32L432KC microcontroller in the test kit synchronously acquires four-channel current data through a 4-channel 16-bit ADC. The data is then transmitted to the hospital information system (HIS) via the SPBT3.0DP2 Bluetooth 5.0 module using the BLE protocol. This multi-channel synchronous acquisition enables parallel detection of NP, IgG, IgM, and CRP, shortening the overall testing time. Bluetooth transmission technology supports real-time data upload, facilitating clinicians to quickly obtain test results and optimizing triage efficiency.

[0034] This protocol enables quantitative analysis of NP (detection limit 500 pg / mL, linear range 0-6000 pg / mL), S1-IgG / IgM (detection limit 250 ng / mL), and CRP (detection limit 50 ng / mL). Testing of 10 RT-PCR-confirmed positive serum samples showed positive detection rates of NP, S1-IgM, and CRP of 92%, 88%, and 95%, respectively, with a correlation coefficient (r) of 0.955 with the ELISA method. The intra-assay repeatability coefficient of variation (CV) was <8.5%, and the entire testing process took 15 minutes.

[0035] Example 2

[0036] Sensors were fabricated on a 125 μm polyimide substrate using CO2 laser engraving technology. The engraving parameters were 8.0% power, 15% speed, and 1000 dpi resolution, forming four 2 mm × 3 mm mesoporous graphene working electrodes (specific surface area 1200 m²). 2A ring-shaped Ag / AgCl reference electrode with an inner diameter of 1 mm and a 5 mm × 5 mm graphene counter electrode are used. The mesoporous graphene electrode is laser-engraved to form a porous structure, increasing the specific surface area and improving the adsorption efficiency of biomolecules, laying the foundation for high-sensitivity detection. This process does not require the high-temperature environment and complex precursors of chemical vapor deposition. It directly induces PI carbonization to form porous graphene, improving material utilization and supporting roll-to-roll mass production. The production capacity is greatly improved compared to the micromechanical exfoliation method, and the mesoporous structure enables a specific surface area of ​​1200 m². 2 / g provides abundant active sites for antibody immobilization.

[0037] The electrode surface was functionalized with π-π stacking using a 5.0 mM 1-pyrene butyric acid (PBA) DMF solution. After activation with 0.4 M EDC and 0.1 M sulfonyl-NHS, 250 μg / mL of SARS-CoV-2 spike protein (S1), NP antigen, and rabbit anti-CRP monoclonal antibody were immobilized. Finally, unreacted sites were blocked with 2.0% bovine serum albumin (BSA). PBA functionalization avoids damage to the graphene conjugated structure and introduces carboxyl groups for antigen / antibody immobilization. EDC / sulfonyl-NHS activation ensures directional coupling of antigen / antibody and maintains biological activity. BSA blocking reduces non-specific adsorption and lowers background signal interference caused by saliva impurities in home testing.

[0038] Users collect 2 mL of saliva using a sterile funnel and immediately dilute it to 10 mL with 0.01 M PBS (pH 7.4) containing 1.0% BSA and 0.1% Tween-20 at a ratio of 1:5. 10 μL of the diluted solution is then dropped onto the surface of the functionalized electrode and incubated at room temperature for 5 minutes. The electrode is then washed twice with PBS (50 μL each time). The sterile funnel method avoids external contamination. Tween-20 acts as a surfactant to dissolve salivary mucins and prevent blockage of the electrode channels. The 1:5 dilution reduces interference from the salivary matrix. Room temperature incubation simplifies the process and is suitable for non-temperature-controlled home environments.

[0039] Add 2.0 mg / mL of HRP-labeled anti-human IgG / IgM antibody and HRP-labeled goat anti-CRP polyclonal antibody, incubate at room temperature for 5 minutes, wash with PBS, add 100 μL of 0.05 M sodium phosphate buffer (pH 6.0) containing 2.0 mM hydroquinone (HQ), and then add 1.0 mM H2O2 to start the reaction. The HRP-labeled antibody specifically binds to the antibody / CRP in the sample, and the enzyme catalytic system amplifies the signal, generating a detectable current without the need for professional instruments. Hydroquinone acts as an electron mediator to accelerate electrochemical signal transduction, and the pH 6.0 buffer optimizes enzyme activity, ensuring the stability of home testing.

[0040] The built-in STM32L432KC microcontroller in the detection box acquires current signals at a sampling rate of 10kHz through a 4-channel 16-bit ADC. After being amplified by an AD8608 operational amplifier, the signals are transmitted to a mobile app via a SPBT3.0DP2 Bluetooth 5.0 module using the BLE protocol (transmission distance 10 meters). The high sampling rate ADC ensures accurate capture of the current signal, Bluetooth 5.0 low-power transmission is compatible with smartphones, the 10-meter transmission distance meets the needs of home use, and the integrated operational amplifier enhances the ability to detect weak signals, adapting to the convenient data interaction needs in home scenarios.

[0041] The mobile app has a built-in calibration curve (NP: I=0.12 [NP]+15.6, R). 2 =0.992; CRP: I=22.5 [CRP]+85.3, R 2 =0.987), automatically calculates the concentration and generates a visual report. The test data is encrypted and uploaded to the community medical cloud platform. The calibration curve is embedded in the APP to realize one-click quantitative analysis. The results can be interpreted without professional knowledge. The visual report displays the NP, antibody and CRP levels in the form of charts, which is easy for home users to understand. Encrypted cloud storage supports remote monitoring by community doctors and realizes the interconnection between home testing and medical systems.

[0042] This solution enables the quantitative detection of NP (detection limit 500 pg / mL), S1-IgG / IgM (250 ng / mL), and CRP (50 ng / mL) in saliva. The sample processing time is less than 2 minutes, and the total detection cycle is 10 minutes. The test results of 5 RT-PCR confirmed positive saliva samples showed that the positive detection rates of NP, S1-IgM, and CRP were 88%, 84%, and 92%, respectively, with a correlation of r=0.912 with the serum test results. Through integrated portable design and non-invasive saliva detection, professional medical testing technology is transformed into a home-use tool. The 10-minute rapid response meets the needs of high-frequency self-monitoring and provides an economical and efficient solution for home screening and rehabilitation monitoring in epidemic prevention and control.

[0043] The above description is merely a preferred embodiment of the present invention and is not intended to limit the present invention in any way. Although the present invention has been disclosed above with reference to preferred embodiments, it is not intended to limit the present invention. Any person skilled in the art can make some modifications or alterations to the above-disclosed technical content to create equivalent embodiments without departing from the scope of the present invention. Any simple modifications, equivalent changes and alterations made to the above embodiments based on the technical essence of the present invention without departing from the scope of the present invention shall still fall within the scope of the present invention.

Claims

1. A laser-induced graphene immunological rapid low-cost remote medical detection platform, characterized in that, The platform comprises the following components: Sensor array module: A patterned structure containing 4 graphene working electrodes, 1 Ag / AgCl reference electrode and 1 graphene counter electrode is formed on a polyimide substrate using CO2 laser engraving technology. After functionalization with 1-pyrene butyric acid, specific antibodies are immobilized and blocked with bovine serum albumin. Electrochemical detection module: Based on differential pulse voltammetry (DPV) and open circuit potential electrochemical impedance spectroscopy (EIS), double sandwich and sandwich detection configurations are used for SARS-CoV-2 nucleocapsid protein (NP) and C-reactive protein (CRP), and indirect immunoassay is used for S1-IgG and S1-IgM. After incubation of diluted blood or saliva samples, enzyme-labeled antibodies are combined and electrochemical signals are collected in a buffer containing hydroquinone and hydrogen peroxide. Wireless transmission and electronic system module: Based on an Arm Cortex-M4 microcontroller, a Bluetooth module and a signal processing circuit are integrated, and a lithium ion polymer battery is used for power supply. The firmware program controls the detection timing and realizes wireless data transmission. Sample processing module: Blood samples are diluted 1:100 with PBS containing 1.0% BSA, and saliva samples are diluted 1:5 with PBS, which are directly used for sensor array detection.

2. The laser-induced graphene immunochromatographic rapid low-cost remote medical testing platform according to claim 1, characterized in that, The sensor array module forms a patterned structure containing 4 graphene working electrodes, 1 Ag / AgCl reference electrode and 1 graphene counter electrode on a polyimide substrate by CO2 laser engraving technology, laser engraving power 8.0%, speed 15%, dots per inch 1000, the graphene working electrode adopts a mesoporous structure design, and a porous graphene layer is formed by laser-induced PI carbonization, with a specific surface area of 1200 m 2 / g, the Ag / AgCl reference electrode is treated with FeCl3 solution for 1 minute after being drop-casted for 100 seconds at a current of -0.2 mA in a mixed solution containing 250 mM silver nitrate, 750 mM sodium thiosulfate and 500 mM sodium bisulfite.

3. The laser-induced graphene immunochromatographic rapid low-cost remote medical detection platform according to claim 1, characterized in that, In the sensor array module, the electrode surface is modified with a 5.0 mM 1-pyrene butyric acid (PBA) DMF solution for π-π stacking, and after activation with 0.4 M EDC and 0.1 M sulfo-NHS, 250 μg / mL of S1-IgG, S1-IgM, CRP antibody or 50-fold diluted NP antibody is immobilized through amide bond, and 2.0% bovine serum albumin solution is used to block the unreacted sites.

4. The laser-induced graphene immunochromatographic rapid low-cost remote medical detection platform according to claim 1, characterized in that, In the electrochemical detection module, after the blood sample is diluted 100 times with PBS containing 1.0% BSA and the saliva sample is diluted 5 times, 10 μL is taken and incubated with the functionalized electrode for 1-10 minutes, the HRP-labeled detection antibody is added, and the amperometric signal is recorded at a potential of 0.2 V relative to Ag / AgCl in a 0.05 M sodium phosphate buffer containing 2.0 mM hydroquinone (HQ) and 1.0 mM H2O2.

5. The laser-induced graphene immunochromatographic rapid low-cost remote medical detection platform according to claim 1, characterized in that, In the electrochemical detection module, the HRP-labeled detection antibody is added, the NP detection is 250-fold diluted, the S1-IgG and S1-IgM are 2.0 mg / mL, and the NP detection requires additional incubation of 1.0 mg / mL HRP-goat anti-rabbit IgG for 5 minutes.

6. The laser-induced graphene immunochromatographic rapid low-cost remote medical testing platform according to claim 1, characterized in that, The DPV detection condition in the electrochemical detection module is: potential range -0.2~0.6V, pulse width 0.2s, increment potential 4mV, amplitude 50mV; the EIS reaction condition: frequency range 0.1~10 6 Hz, amplitude 5mV.

7. The laser-induced graphene immunochromatographic rapid low-cost remote medical detection platform according to claim 1, characterized in that, In the wireless transmission and electronic system module, the signal processing circuit: a constant potential circuit is composed of a single operational amplifier AD8605 and a four-channel operational amplifier AD8608, which realizes current signal amplification.

8. The laser-induced graphene immunochromatographic rapid low-cost remote medical detection platform according to claim 1, characterized in that, The sample processing module: the blood sample is preserved by EDTA blood collection tube, and before detection, the blood sample is diluted by 0.01M PBS containing 1.0% BSA at 1:100, 0.05% sodium azide is added to the diluent; the saliva sample is collected by a sterile funnel, and immediately after collection, the saliva sample is diluted by PBS containing 1.0% BSA at 1:5, 0.1% Tween-20 is added to the diluent to enhance the protein solubility, and all the diluted samples are detected within 2 hours.

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