Multi-virus aerosol parallel detection method and system based on microfluidic impedance

Abstract

The invention discloses a multi-virus aerosol parallel detection method and system based on micro-fluidic impedance. The system comprises a gas conveying unit, a micro-fluidic chip, a sample partitioning unit, a sample detection unit and a data processing and analyzing unit, the gas conveying unit inputs to-be-detected gas into the micro-fluidic chip, the micro-fluidic chip is used for realizing large-particle impurity separation, and the sample partitioning unit and the sample detection unit are used for multi-channel parallel specific detection; and finally, parallel detection and quantitative analysis of various viruses are realized by a virus-impedance quantitative-qualitative model in the data processing and analysis unit. An efficient and automatic real-time detection scheme is provided for an airborne disease and pathogen monitoring system, accurate identification of the airborne diseases of the complex air matrix, which is simple and convenient to operate, is realized, dynamic and high-throughput evaluation on early-stage epidemic diseases is met, and the method can be applied to real-time detection and prevention and control scenes of airborne viruses.

Description

Technical Field

[0001] This invention relates to the field of airborne virus detection, and in particular to a method and system for parallel detection of multiple virus aerosols based on microfluidic impedance. Background Technology

[0002] With the frequent occurrence of global public health emergencies, airborne pathogens have become a significant threat to human health and biosafety. Studies have shown that various pathogens, such as African swine fever virus, influenza virus, and COVID-19, can remain suspended in the air for extended periods and travel long distances via aerosols. Multiple infectious pathogens can also coexist in the same environment, posing serious risks to public health and livestock production. Existing detection technologies for aerosol microorganisms mainly include PCR, ELISA, immunofluorescence, bioluminescence, and light scattering. These methods generally suffer from high equipment dependence, demanding operator skills, and poor real-time performance. Furthermore, traditional aerosol sampling methods often employ filter membrane capture or sedimentation collection, which suffer from low collection efficiency, target particle damage, and insufficient enrichment capacity.

[0003] Therefore, there is an urgent need for a novel, integrated, highly sensitive, real-time-operable aerosol microbial detection technology with intelligent identification capabilities to meet the practical needs of rapid on-site monitoring. Based on this need, this invention provides a rapid and efficient detection solution for monitoring airborne diseases. Summary of the Invention

[0004] To address the shortcomings of existing technologies, this application proposes a parallel detection method and system for multiple virus aerosols based on microfluidic impedance. This system can achieve high-resolution and rapid parallel detection of multiple virus states in complex atmospheric matrix backgrounds. It does not require professional personnel to operate and has the advantages of simple fabrication and low cost. It can solve the problem of the difficulty in real-time sensing of virus floating state in existing technologies.

[0005] The technical solution adopted in this invention is as follows: A parallel detection system for multiple virus aerosols based on microfluidic impedance includes: The gas delivery unit pumps the gas from the environment to be tested into the microfluidic chip. The microfluidic channel on the microfluidic chip includes an air inlet; one end of the air inlet is connected to the gas delivery unit, and the other end is connected to the circular collision separation zone and the separation zone in sequence through the microfluidic channel. The separation zone has three channels on the outlet side. The first channel is connected to the large particle impurity separation outlet, the second channel is connected to the calibration sample outlet through the serpentine buffer, and the third channel is connected to the detection sample outlet through the serpentine buffer 12. The sample partitioning unit is equipped with a detection sample buffer pool, several detection sample pools, and a calibration sample detection pool; the detection sample buffer pool is connected to the detection sample outlet; with the detection sample buffer pool 31 as the center, the detection sample pools are arranged in an array around the detection sample buffer pool and are interconnected; each sample detection unit is equipped with a specific impedance detection sensor. The data processing and analysis unit is signal-connected to the sample detection unit to acquire impedance information of each detection sample detection cell and the calibration sample detection cell. The impedance information Zi of each detection sample detection cell is compensated using the impedance information Z0 of the calibration sample detection cell 306 to obtain the compensated impedance information Zi′ = Zi−Z0. The impedance information Zi′ serves as the input feature of the virus-impedance quantitative-qualitative model. The virus-impedance quantitative-qualitative model is compared and analyzed with a pre-built impedance feature database to output the presence state and concentration range of the target virus in the corresponding detection sample, thereby realizing the parallel detection and quantitative analysis of multiple viruses.

[0006] Furthermore, polymer film microvalves are installed at both the calibration sample outlet and the detection sample outlet to increase particle concentration.

[0007] Furthermore, at least two interconnected circular collision separation zones should be set up.

[0008] Furthermore, let the width of the channel connecting the circular collision separation zone be L, the diameter of the circular collision separation zone be d, and the ratio of the channel width to the diameter of the circular collision separation zone be in the range of 1:1.5 to 1:2.

[0009] Furthermore, the construction process of the quantitative-qualitative model of virus-impedance is as follows: S2.1 Sample preparation: Prepare aerosol samples of various target viruses at different concentration gradients; S2.2 Full-frequency impedance information acquisition: Using the impedance detection unit, impedance detection is performed on virus aerosol samples of different types and concentration gradients to acquire their full-frequency impedance spectrum information within a preset frequency range. S2.3 Feature Frequency Extraction: Based on the impedance spectrum information of the full frequency band, differential analysis is performed on the impedance data of different viral aerosol samples at the same frequency point, and the frequency point with the most significant difference in impedance response is selected as the feature frequency of the target virus. S2.4 Determination of standard characteristic parameters: The impedance information obtained at the characteristic frequency is used as the standard characteristic parameter, and the standard characteristic parameter is associated with and stored with the corresponding virus type and concentration information; S2.5 Database Construction and Model Establishment: The standard feature parameters, corresponding virus types, and concentration information are used together as feature data to construct a virus-impedance feature database, and a quantitative-qualitative model of virus-impedance is established based on the feature database.

[0010] Furthermore, by increasing the number of air intake holes, the air intake is kept stable.

[0011] Furthermore, a lower layer board is added between the microfluidic chip and the sample partitioning unit. The lower layer board is provided with a lower layer calibration sample inlet, a lower layer calibration sample outlet, a lower layer detection sample inlet, and a lower layer detection sample outlet. The lower layer calibration sample inlet and the calibration sample outlet are arranged opposite to each other. The calibration sample outlet is a through hole and is arranged opposite to the calibration sample detection pool. The lower layer calibration sample inlet and the calibration sample outlet are connected. The lower layer detection sample inlet and the detection sample outlet are arranged opposite to each other. The lower layer detection sample outlet is arranged opposite to the detection sample buffer pool. The lower layer detection sample inlet and the lower layer detection sample outlet are connected.

[0012] Furthermore, a rotor flow meter is installed on the pipeline between the gas delivery unit and the microfluidic chip to monitor and regulate the gas flow rate entering the microfluidic chip in real time.

[0013] Furthermore, the system is equipped with a visualization unit to present the results output by the data processing and analysis unit in a visual format.

[0014] A method for parallel detection of multiple virus aerosols based on microfluidic impedance, based on the aforementioned parallel detection system for multiple virus aerosols based on microfluidic impedance, includes the following steps: Step 1: Prepare a specific impedance detection sensor for the area to be detected and the type of target virus; Step 2: Input the airflow to be measured into the microfluidic chip; the microfluidic chip separates the particles in the airflow to be measured. Step 3: Use the output of the blank verification chip to compensate for the output of the detection chip, and calculate the standard reference value; Step 4: Compare the standard reference value with the data in the quantitative-qualitative model of virus-impedance, and output the detection results.

[0015] The beneficial effects of this invention are: 1. Based on the biological characteristics of viruses attaching to aerosols and other particles, this invention obtains differentiated impedance information through the principle of immunological binding. Information processing is performed on different sample control groups to obtain standard virus presence state parameters, which can realize real-time monitoring without sample processing in complex atmospheric matrices. On the other hand, the standardization of characteristic parameter information through the control system improves the effectiveness of the information.

[0016] 2. This invention uses only a microfluidic chip and bioelectrodes to form the basic monitoring unit, resulting in very low material costs. The information processing module utilizes algorithms implemented through an STM32 microcontroller and an AD5933 impedance chip, making the platform simple and long-lasting. No additional operations are required during the detection process, resulting in a high degree of automation and enabling continuous, real-time, and visualized detection, eliminating the dependence on professional personnel and complex equipment inherent in traditional methods.

[0017] 3. In the detection experiment targeting African swine fever, compared with the widely used ELISA detection results, the present invention achieved a positive consistency rate of 95.8%, even when the sample was untreated. This shows that the method and system proposed in this invention can be used to determine the aerosol state of multiple viruses, meet the detection needs of multiple harmful pathogens in a single scenario, and provide a rapid and efficient detection solution for monitoring airborne diseases. Attached Figure Description

[0018] Figure 1 This is a schematic diagram of the multilayer structure of the microfluidic chip of the present invention.

[0019] Figure 2 These are equivalent circuit diagrams of aerosol particles in different forms.

[0020] Figure 3 This is a system structure diagram of the present invention used in experiments.

[0021] Figure 4 It is the impedance detection value of the virus sample in Example 3.

[0022] In the diagram: 101, 102. Air inlet; 103, 104. Circular collision separation zone; 105. Large particle impurity separation outlet; 106. Calibration sample outlet; 107. Detection sample outlet; 108, 109. Polymer membrane microvalve; 11. Separation zone; 12. Serpentine buffer zone; 201. Lower layer detection sample inlet; 202. Lower layer calibration sample inlet; 203. Lower layer calibration sample outlet; 204. Lower layer detection sample outlet; 301, 302, 303, 304, 305. Detection sample detection pool; 306. Calibration sample detection pool; 31. Detection sample buffer pool. Detailed Implementation

[0023] To make the objectives, technical solutions, and advantages of this invention clearer, the invention will be further described in detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are for illustrative purposes only and are not intended to limit the invention. Example

[0024] A parallel detection system for multiple virus aerosols based on microfluidic impedance includes: a gas delivery unit, a microfluidic chip, a sample partitioning unit, a sample detection unit, and a data processing and analysis unit.

[0025] A gas delivery unit is used to pump in the ambient air sample to be tested. In this embodiment, an air pump is used.

[0026] A microfluidic chip includes a substrate on which microfluidic channels are formed. The structural layout of the microfluidic channels is as follows: Figure 1 As shown, the system specifically includes an air inlet 101, a circular collision separation zone, a separation zone 11, a large particle impurity separation outlet 105, a serpentine buffer zone 12, a calibration sample outlet 106, and a detection sample outlet 107. At least one air inlet 101 is provided and connected to a gas delivery unit via a pipeline. The air inlet 101 is connected to the circular collision separation zone via a microfluidic channel. The input aerosol particle stream collides in the circular collision separation zone, effectively preventing excessive accumulation of viruses in particle piles or shallow burial within the aerosol. One side of the separation zone 11 is connected to the circular collision separation zone. Because aerosol particles to which airborne viruses attach have a preference, primarily concentrated in the 2-5 μm particle size range, this invention includes a separation zone 11 to separate large-diameter particles. The specific structure of the separation zone 11 is configured such that the side of the separation zone 11 connected to the circular collision separation zone is the inlet side; the opposite side is the outlet side. On the outlet side, there are three channels arranged side by side. The first channel is connected to the large particle impurity separation outlet 105, the second channel is connected to the calibration sample outlet 106 through the serpentine buffer 12, and the third channel is connected to the detection sample outlet 107 through the serpentine buffer 12. The serpentine buffer can stabilize the airflow. The distance between the three channels on the outlet side and the inlet side gradually decreases, thus forming an inverted trapezoidal structure in the separation zone 11. According to the microfluidic aerodynamics principle within this structure, large-diameter particles that flow in from the inlet are discharged through the first channel. The particle size in the separation zone decreases sequentially from the first channel to the third channel, which can reduce the impact of large-diameter particles on detection.

[0027] More specifically, polymer film microvalves are installed at both the calibration sample outlet 106 and the detection sample outlet 107 to increase the particle concentration, as shown by reference numerals 108 and 109 in the figure.

[0028] More specifically, in order to achieve a better separation effect, at least two circular collision separation zones are set up, as shown in the figure, circular collision separation zone 103 and circular collision separation zone 104 connected in series.

[0029] More specifically, the diameter d of the circular collision separation zone is 2mm, and the width L of the main channel in the inlet ranges from 0.8 to 1.2mm; both need to be designed in a certain ratio, with the channel to the diameter of the circle in the range of 1:1.5 to 1:2. This design prevents particles from being trapped in the separation zone due to viscous resistance, while effectively breaking up particle clusters and enhancing the separation effect.

[0030] The sample partition unit includes a detection sample buffer pool 31, several detection sample pools (shown as 301, 302, 303, 304, and 305 in the figure), and a calibration sample detection pool 306. The detection sample buffer pool 31 is connected to the detection sample outlet 107. The detection sample pools are arranged in an array around the detection sample buffer pool 31, and are connected to each other. That is, the airflow to be tested flowing out of the detection sample outlet 107 enters the detection sample buffer pool 31, and is then diverted into each detection sample pool, achieving uniform distribution of the airflow to be tested. The calibration sample detection pool 306 is connected to the calibration sample outlet 106, meaning that the airflow to be tested flowing out of the calibration sample outlet 106 enters the calibration sample detection pool 306.

[0031] The sample detection unit is equipped with several impedance sensors, each corresponding to a detection cell (301, 302, 303, 304, 305) for the test sample and a detection cell (306) for the calibration sample. These sensors are used to acquire impedance information for each detection cell and the calibration sample detection cell (306).

[0032] In this embodiment, to enable parallel detection of multiple virus types, the impedance sensor in each sample detection pool employs a specific impedance detection sensor. The steps for fabricating the specific impedance detection sensor are as follows: S1.1 Design a two-electrode bioelectrode system, with the mass ratio of carbon powder to binder controlled at 85:15 to 95:5, and adjust the solid content of the slurry to 30% to 60% with solvent. Print the mixed slurry onto a glass fiber substrate to form a preliminary conductive electrode.

[0033] S1.2. Graphene material is deposited on the electrode to expand the molecular contact area on the electrode surface and improve the sensitivity of the sensor.

[0034] S1.3. The electrode prepared in S2 undergoes specific treatment. The impedance detection sensor after this specific treatment can achieve specific detection of specific viruses. The specific treatment process is as follows: S1.3.1 First, determine the environment to be tested and the target virus within it. Taking a pigsty as an example, the viruses that need to be tested in this environment typically include African swine fever, classical swine fever, porcine reproductive and respiratory syndrome (PRRS), and pseudorabies. S1.3.2. For the aforementioned target virus, the detection area electrode is specifically modified, as follows: The electrode was immersed in an EDC / NHS coupling system solution at 4°C for 15 minutes to activate the carboxyl groups on the electrode surface. Then, the virus-corresponding antibody was added to the activated electrode surface and incubated at 4°C for 4 hours. Specific antibodies were immobilized on the electrode through a covalent coupling reaction between the amino groups on the antibody surface and the activated carboxyl groups. The modified electrode was then dried at 25°C for 30 minutes and thoroughly washed with PBS buffer to remove unbound antibody molecules. To block non-specific adsorption sites on the electrode surface, 0.01 mol / L bovine serum albumin (BSA) solution was added and incubated at 4°C for 1 hour to complete the blocking process. Finally, the electrode was dried at 37°C for 30 minutes to enhance the stability of the BSA blocking layer, thereby improving the anti-interference ability and signal-to-noise ratio of subsequent detection.

[0035] The data processing and analysis unit is signal-connected to the sample detection unit and is used to acquire the impedance information of each detection sample detection cell and the calibration sample detection cell. The impedance information corresponding to the i-th detection sample detection cell is denoted as Zi, where i = 1, 2, 3, 4, 5, corresponding to detection sample detection cells 301, 302, 303, 304, and 305 respectively. The impedance information corresponding to the calibration sample detection cell 306 is denoted as Z0.

[0036] To eliminate the impact of environmental background interference and non-specific impedance changes introduced by the system itself on the detection results, this application uses the impedance information Z0 of the calibration sample detection cell 306 to compensate the impedance information Zi of each detection sample detection cell, obtaining the compensated impedance information Zi′, calculated as: Zi′ = Zi − Z0. The calibration sample detection cell 306 maintains the same structure, detection conditions, and operating state as the detection sample detection cell, but does not introduce specific recognition elements. It is used to characterize the common background impedance signal generated by aerosol matrix, environmental temperature and humidity changes, electrode baseline drift, and non-specific particle adhesion in real time. By introducing an impedance compensation mechanism, the impact of systematic noise on the consistency of impedance results of each detection channel can be effectively reduced when multiple detection channels are operating in parallel. This improves the comparability and stability of impedance signals between different detection sample detection cells, thereby enhancing the system's reliability in identifying target viruses against a complex atmospheric matrix background.

[0037] The compensated impedance information Zi′ of each detection sample's detection pool is used as the input feature of the virus-impedance quantitative-qualitative model. The virus-impedance quantitative-qualitative model is compared and analyzed with a pre-built impedance feature database to output the presence state and concentration range of the target virus in the corresponding detection sample, thereby realizing the parallel detection and quantitative analysis of multiple viruses.

[0038] In this embodiment, the construction process of the quantitative-qualitative model of virus-impedance is as follows: S2.1 Sample preparation: Aerosol samples of various target viruses at different concentration gradients are prepared. The aerosol samples are generated by an aerosol generator and introduced into the microfluidic detection system sequentially under the same experimental conditions to ensure the comparability of impedance detection results of different samples.

[0039] S2.2 Full-frequency impedance information acquisition: Using the impedance detection unit mentioned above, impedance detection is performed on viral aerosol samples of different types and concentration gradients to acquire their full-frequency impedance spectrum information within a preset frequency range.

[0040] S2.3 Feature Frequency Extraction: Based on the impedance spectrum information of the full frequency band, differential analysis is performed on the impedance data of different viral aerosol samples at the same frequency point, and the frequency point with the most significant difference in impedance response is selected as the feature frequency of the target virus.

[0041] S2.4 Determination of Standard Characteristic Parameters: The impedance information obtained at the characteristic frequency is used as the standard characteristic parameter, and this standard characteristic parameter is associated with and stored in relation to the corresponding virus type and concentration information. The parameter principle satisfies the following equivalent circuit formula:

[0042] in, For the resistance of the solution, The non-ideal double-layer capacitance at the solution-electrode interface is modeled using CPE. For charge transfer resistor, The additional impedance introduced by viral binding. This represents the diffusion impedance of a finite layer.

[0043] S2.5 Database Construction and Model Establishment: The standard feature parameters, corresponding virus types, and concentration information are used together as feature data to construct a virus-impedance feature database, and a quantitative-qualitative model of virus-impedance is established based on the feature database.

[0044] In subsequent detection, the impedance information of the sample to be tested at the characteristic frequency is input into the virus-impedance quantitative-qualitative model. By comparing and analyzing the model with the standard characteristic parameters in the virus-impedance feature database, the identification result of the target virus and its corresponding concentration range are output.

[0045] In this embodiment, a rotor flow meter can also be installed on the pipeline between the gas delivery unit and the microfluidic chip to monitor and regulate the gas flow rate entering the microfluidic chip in real time. The rotor flow meter provides a visual indication of the gas flow rate output by the gas delivery unit, ensuring that the airflow entering the microfluidic chip remains within a preset stable flow range.

[0046] In this embodiment, if the dimensions of the microfluidic chip and the sample partitioning unit are mismatched, making direct communication between the calibration sample detection pool 306 and the calibration sample outlet 106, the detection sample outlet 107, and the detection sample buffer pool 31 impossible, a lower layer plate can be added. (See attached diagram.) Figure 1 The lower plate is provided with a lower layer calibration sample inlet 202, a lower layer calibration sample outlet 203, a lower layer detection sample inlet 201, and a lower layer detection sample outlet 204. The lower layer calibration sample inlet 202 is arranged opposite to the calibration sample outlet 106, and the lower layer calibration sample outlet 203 is a through hole and is arranged opposite to the calibration sample detection pool 306. The lower layer calibration sample inlet 202 and the lower layer calibration sample outlet 203 are connected. Therefore, the gas flowing out of the calibration sample outlet 106 passes through the lower layer calibration sample inlet 202 and the lower layer calibration sample outlet 203 in sequence and enters the calibration sample detection pool 306. Similarly, the lower-level sample inlet 201 and the sample outlet 107 are arranged opposite to each other, and the lower-level sample outlet 204 and the sample buffer pool 31 are arranged opposite to each other. The lower-level sample inlet 201 and the lower-level sample outlet 204 are connected. Therefore, the gas flowing out of the sample outlet 107 passes through the lower-level sample inlet 201 and the lower-level sample outlet 204 in sequence and enters the sample buffer pool 31, and then disperses to multiple sample detection pools.

[0047] In this embodiment, the system may also be equipped with a visualization unit to visualize the results output by the data processing and analysis unit.

[0048] In this embodiment, in order to maintain the stability of air intake, the number of air intake holes 101 can be increased. As shown in the figure, there are two air intake holes 101 and 102 in a Y-shaped structure.

[0049] In this embodiment, the impedance detection module and the impedance information evaluation module are both deployed on the control board. The processor is an STM32H7 with a main frequency of 480MHz and an operating voltage of 3.3-5V. The impedance detection chip is an AD5933, which is connected to the computer via a full-speed USB interface. This experimental example illustrates the chip hardware fabrication method provided in this invention, which includes the following steps: S3.1, as follows Figure 1 The structure shown is fabricated into a film, and a channel mold on a silicon wafer is obtained using soft lithography.

[0050] S3.2. Mix PDMS solution A and solution B thoroughly at a ratio of 10:1, pour the mixture onto a mold, and place it in an oven to dry completely to obtain the upper substrate. Use a hole punch to create channels by punching holes at the designated locations.

[0051] S3.3, according to Figure 1 The sample separation cell structure is perforated, and the calibration sample detection cell (306) is not connected to other cells.

[0052] S3.4 Clean the two substrates with 95% ethanol solution, then rinse with distilled water to remove debris adhering to the material. Then place them in an oven to dry. Align the two substrates and place them in a bonding machine for bonding to bond the two chips together without compromising their biocompatibility.

[0053] S3.5 The sample detection cell is aligned with the detection area of ​​the detection electrode, and the detection electrode is placed on the PCB board.

[0054] This embodiment uses nanospheres as an example and employs the microfluidic chip described in Embodiment 1 to verify chip performance. This embodiment, as an ideal input, can serve as a practical basis for real-world applications and includes the following steps: S4.1 Prepare solutions of 2μm, 3μm, 5μm, and 10μm nanospheres, and generate aerosol particles using an aerosol generator. Conduct experiments according to the system and flow rate parameters provided by this invention, and place formalin at the vent (107) to collect the outflowing particles; S4.2 Calculate the number of nanospheres of different sizes that entered the nanospheres and the number of nanospheres of different sizes on the formalin by microscopic observation.

[0055] S4.3 Calculations show that the proportion of 5μm particles in the test sample vent (107), i.e. the test area, reaches 98.3%. Example

[0056] Based on the above system, this invention also proposes a parallel detection method for multiple virus aerosols based on microfluidic impedance, comprising the following steps: Step 1: Prepare a specific impedance detection sensor for the area to be detected and the type of target virus; Step 2: Start the air pump to input the airflow to be measured into the microfluidic chip; the microfluidic chip separates the particles in the airflow to be measured. Step 3: Use the output of the blank verification chip to compensate for the output of the detection chip, and calculate the standard reference value; Step 4: Compare the standard reference value with the data in the quantitative-qualitative model of virus-impedance, and output the detection results.

[0057] This embodiment uses African swine fever virus (ASFV) as the target detection agent. The system provided by this invention and the experimental procedure described above are used to evaluate the effectiveness and reliability of the method. Specifically, the method uses classical swine fever virus (CSFV), pseudorabies virus (PRV), and a mixture of three viruses as control groups. The volume of each sample within the aerosol generator is controlled consistently in a single experiment. The antibody for the impedance sensor is the African swine fever P30 monoclonal antibody. Figure 4 As shown, the detection values ​​at a characteristic frequency of 10Hz can clearly distinguish the presence of African swine fever virus.

[0058] Comparative experiments were conducted on the same samples using the ELISA method, and the positive consistency between the two methods reached 96.7%. Compared to the ELISA method, this method significantly reduces the sample processing requirements, with the entire process taking less than one minute, achieving minute-level detection.

[0059] The above embodiments are only used to illustrate the design concept and features of the present invention, and their purpose is to enable those skilled in the art to understand the content of the present invention and implement it accordingly. The protection scope of the present invention is not limited to the above embodiments. Therefore, all equivalent changes or modifications made based on the principles and design ideas disclosed in the present invention are within the protection scope of the present invention.

Claims

1. A parallel detection system for multiple virus aerosols based on microfluidic impedance, characterized in that, include: The gas delivery unit pumps the gas from the environment to be tested into the microfluidic chip. The microfluidic channel on the microfluidic chip includes an air inlet (101); one end of the air inlet (101) is connected to the gas delivery unit, and the other end is connected to the circular collision separation zone and the separation zone (11) in sequence through the microfluidic channel. The separation zone (11) has three channels on the outlet side. The first channel is connected to the large particle impurity separation outlet (105), the second channel is connected to the calibration sample outlet (106) through the serpentine buffer (12), and the third channel is connected to the detection sample outlet (107) through the serpentine buffer (12). The sample partition unit is equipped with a detection sample buffer pool (31), several detection sample pools and a calibration sample pool (306); the detection sample buffer pool (31) is connected to the detection sample outlet (107); with the detection sample buffer pool (31) as the center, each detection sample pool is arranged in an array around the detection sample buffer pool (31) and is interconnected; each sample detection unit is equipped with a specific impedance detection sensor. The data processing and analysis unit is signal-connected to the sample detection unit to obtain impedance information of each detection sample detection cell and the calibration sample detection cell; The impedance information Zi of each detection sample detection pool is compensated by using the impedance information Z0 of the calibration sample detection pool (306) to obtain the compensated impedance information Zi′= Zi−Z0; the impedance information Zi′ is used as the input feature of the virus-impedance quantitative-qualitative model. The virus-impedance quantitative-qualitative model is compared and analyzed with the pre-constructed impedance feature database to output the existence state and concentration range of the target virus in the corresponding detection sample, thereby realizing the parallel detection and quantitative analysis of multiple viruses.

2. The multi-virus aerosol parallel detection system based on microfluidic impedance according to claim 1, characterized in that, Polymer film microvalves are installed at both the calibration sample outlet (106) and the detection sample outlet (107) to increase the particle concentration.

3. The multi-virus aerosol parallel detection system based on microfluidic impedance according to claim 1, characterized in that, At least two interconnected circular collision separation zones should be set up.

4. The multi-virus aerosol parallel detection system based on microfluidic impedance according to claim 1, characterized in that, Let the width of the channel connecting the circular collision separation zone be L, and the diameter of the circular collision separation zone be d. The ratio of the channel width to the diameter of the circular collision separation zone is in the range of 1:1.5 to 1:

2.

5. The multi-virus aerosol parallel detection system based on microfluidic impedance according to claim 1, characterized in that, The construction process of the quantitative-qualitative model of virus-impedance is as follows: S2.1 Sample preparation: Prepare aerosol samples of various target viruses at different concentration gradients; S2.2 Full-frequency impedance information acquisition: Using the impedance detection unit, impedance detection is performed on virus aerosol samples of different types and concentration gradients to acquire their full-frequency impedance spectrum information within a preset frequency range. S2.3 Feature Frequency Extraction: Based on the impedance spectrum information of the full frequency band, differential analysis is performed on the impedance data of different viral aerosol samples at the same frequency point, and the frequency point with the most significant difference in impedance response is selected as the feature frequency of the target virus. S2.4 Determination of standard characteristic parameters: The impedance information obtained at the characteristic frequency is used as the standard characteristic parameter, and the standard characteristic parameter is associated with and stored with the corresponding virus type and concentration information; S2.5 Database Construction and Model Establishment: The standard feature parameters, corresponding virus types, and concentration information are used together as feature data to construct a virus-impedance feature database, and a quantitative-qualitative model of virus-impedance is established based on the feature database.

6. The multi-virus aerosol parallel detection system based on microfluidic impedance according to claim 1, characterized in that, By increasing the number of air intake holes (101), the air intake is kept stable.

7. The multi-virus aerosol parallel detection system based on microfluidic impedance according to claim 1, characterized in that, A lower plate is added between the microfluidic chip and the sample partitioning unit. The lower plate is provided with a lower-layer calibration sample inlet (202), a lower-layer calibration sample outlet (203), a lower-layer detection sample inlet (201), and a lower-layer detection sample outlet (204). The lower-layer calibration sample inlet (202) is arranged opposite to the calibration sample outlet (106), the lower-layer calibration sample outlet (203) is a through hole and is arranged opposite to the calibration sample detection pool (306), and the lower-layer calibration sample inlet (202) and the lower-layer calibration sample outlet (203) are connected. The lower-layer detection sample inlet (201) is arranged opposite to the detection sample outlet (107), the lower-layer detection sample outlet (204) is arranged opposite to the detection sample buffer pool (31), and the lower-layer detection sample inlet (201) and the lower-layer detection sample outlet (204) are connected.

8. The multi-virus aerosol parallel detection system based on microfluidic impedance according to claim 1, characterized in that, A rotor flow meter is installed on the pipeline between the gas delivery unit and the microfluidic chip to monitor and regulate the gas flow rate entering the microfluidic chip in real time.

9. A parallel detection system for multiple virus aerosols based on microfluidic impedance according to claim 1, characterized in that, The system is equipped with a visualization unit to present the results output by the data processing and analysis unit in a visual format.

10. A method for parallel detection of multiple viral aerosols based on microfluidic impedance, characterized in that, Based on the multi-virus aerosol parallel detection system based on microfluidic impedance as described in claim 1, the inspection steps are as follows: Step 1: Prepare a specific impedance detection sensor for the area to be detected and the type of target virus; Step 2: Input the airflow to be measured into the microfluidic chip; the microfluidic chip separates the particles in the airflow to be measured. Step 3: Use the output of the blank verification chip to compensate for the output of the detection chip, and calculate the standard reference value; Step 4: Compare the standard reference value with the data in the quantitative-qualitative model of virus-impedance, and output the detection results.

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