Detection method of micro-fluidic chip and plasma separation and diversion integrated micro-fluidic chip

Abstract

The invention discloses a detection method of a micro-fluidic chip and a plasma separation and diversion integrated micro-fluidic chip, and relates to the technical field of micro-fluidic chips. The chip comprises a sample inlet, a separation assembly, a flow guide assembly and a chip body, the sample inlet is used for receiving a blood sample, and the separation assembly is communicated with the sample inlet and used for separating plasma from the blood sample; the flow guide assembly is communicated with the separation assembly; the chip main body is communicated with the flow guide assembly, and the flow guide assembly is used for guiding the separated plasma to the chip main body. According to the plasma separation and diversion integrated micro-fluidic chip disclosed by the embodiment of the invention, the separated plasma is rapidly and completely released while the efficient separation of the plasma is ensured, and the plasma can be effectively guided into the micro-fluidic chip for accurate quantitative detection; efficient plasma separation can be achieved on a microfluidic platform, plasma can be rapidly guided to a detection area, plasma enrichment and extraction are supported, the detection speed and sensitivity can be improved, and the operation process can be simplified.

Description

Technical Field

[0001] The present invention relates to the technical field of microfluidic chips, and in particular to a detection method of a microfluidic chip and a plasma separation and diversion integrated microfluidic chip. Background Art

[0002] Plasma separation is a key pre-treatment step in many medical diagnostic and bioanalysis processes, and its efficiency and quality directly affect the accuracy and reliability of subsequent testing. Traditional plasma separation methods usually rely on large equipment such as centrifuges, which are not only complicated to operate, but also difficult to meet the needs of instant testing and portable devices. In recent years, the rapid development of microfluidics has greatly promoted progress in the field of instant testing. However, since clinical samples are usually whole blood, if the whole blood is separated by centrifuges and other equipment and then directed to a microfluidic chip for testing, it is not only cumbersome to operate, but may also cause cross contamination.

[0003] To solve the above problems, in the existing microfluidic chip design, various types of filter membranes or microstructures are usually integrated in the blood sample input part for plasma separation. Although these structures can achieve the initial separation of plasma, they also cause the separated plasma to be easily "locked" in the separation area and difficult to be effectively released to the detection area. This contradiction seriously affects the efficiency of plasma transfer to the chip detection area, thereby prolonging the time of the entire detection process and reducing the sensitivity and accuracy of the detection. Summary of the invention

[0004] The present invention aims to solve at least one of the technical problems existing in the prior art. To this end, the present invention proposes a detection method of a microfluidic chip and a plasma separation and diversion integrated microfluidic chip, which can effectively separate plasma and divert plasma to the detection area of ​​the chip body.

[0005] On the one hand, the detection method of the microfluidic chip according to the embodiment of the present invention is applied to a plasma separation and flow guidance integrated microfluidic chip, wherein the plasma separation and flow guidance integrated microfluidic chip comprises a sample inlet, a separation component, a flow guidance component and a chip body; the detection method comprises the following steps:

[0006] Putting a blood sample into the sample inlet;

[0007] The separation component separates plasma from the blood sample and transports the plasma to the flow guide component;

[0008] The flow guiding component guides the plasma to the chip body;

[0009] The chip body detects the plasma to obtain a detection result.

[0010] According to some embodiments of the present invention, the flow guiding component includes a microarray structure and a plurality of flow guiding channels, and the microarray structure has a plurality of channels; the step of the flow guiding component guiding the plasma to the chip body includes:

[0011] The microarray structure allows the plasma to flow along the pores through capillary action and be enriched in the flow-guiding channel;

[0012] The guide channel guides the plasma in the pore to the chip body.

[0013] According to some embodiments of the present invention, the chip body includes: a first collecting channel and a plurality of first branch flow channels, one end of the first collecting channel is connected to the flow guide component, a first water absorbent pad is provided at the other end of the first collecting channel, each of the first branch flow channels is connected to the first collecting channel, the first branch flow channel is located between the first water absorbent pad and the flow guide component, and the first branch flow channel is vertically arranged below the first collecting channel, a test strip is arranged in each of the first branch flow channels, a first measuring positioning hole is arranged on the side of each of the first branch flow channels, and the first measuring positioning hole is located above the test strip, and a first air pressure balance port is connected to the bottom of a plurality of the first branch flow channels; a first light response film is arranged outside the first branch flow channel;

[0014] The chip body detects the plasma to obtain the test result, comprising:

[0015] The plasma enters the first collecting channel through the flow guiding component;

[0016] When the plasma reaches the junction of the first collecting channel and the first branch flow channel, the plasma flows into the first branch flow channel until it reaches the first measuring positioning hole;

[0017] The plasma in the first collecting channel continues to flow forward to the first absorbent pad and no longer flows into the first branch flow channel, so that independent and quantitative plasma exists in the first branch flow channel;

[0018] The first light-responsive film is irradiated with a preset light, so that the plasma in the first branch flow channel reacts with the test paper to obtain the test result.

[0019] According to some embodiments of the present invention, the chip body includes a second collecting channel and a second branch flow channel, one end of the second collecting channel is connected to the guide component, the other end of the second collecting channel is provided with a second water absorbent pad, the second branch flow channel is connected to the second collecting channel, the second branch flow channel is located between the second water absorbent pad and the guide component, and the second branch flow channel is vertically arranged below the second collecting channel, the reaction chamber is arranged at the bottom of the second branch flow channel and is connected to the second branch flow channel, the reaction flow channel is connected to the reaction chamber, and the reaction flow channel is arranged in parallel with the second collecting channel, a second measuring positioning hole is provided at the bottom of the reaction flow channel, and a second light-responsive film is provided on the outside of the reaction flow channel;

[0020] The chip body detects the plasma to obtain the test result, comprising:

[0021] Printing the detection reagent in the reaction chamber by inkjet printing, and making the detection reagent into powder by freeze drying; or modifying the inner surface of the reaction chamber with antibodies to form the detection reagent;

[0022] The plasma enters the second collecting channel through the flow guiding component;

[0023] When the plasma reaches the junction of the second collecting channel and the second branch flow channel, the plasma flows into the second branch flow channel, fills the reaction chamber, and reaches the second measuring positioning hole;

[0024] The plasma in the second collection channel continues to flow forward to the second water absorbent pad and no longer flows into the second branch flow channel, so that independent and quantitative plasma exists in the reaction chamber;

[0025] The second light-responsive film is irradiated with a preset light, so that the plasma in the reaction chamber reacts with the detection reagent to obtain the detection result.

[0026] According to some embodiments of the present invention, the flow guide component is a primary flow channel, the chip body further includes a plurality of secondary flow channels and a plurality of tertiary flow channels, the secondary flow channels correspond to the tertiary flow channels one by one, one end of the secondary flow channel is connected to the flow guide component, and the other end of the secondary flow channel is connected to the corresponding tertiary flow channel; a sample separation port is provided on the side of the secondary flow channel;

[0027] The chip body detects the plasma to obtain the test result, comprising:

[0028] After the plasma flows into the secondary flow channel through the primary flow channel, it enters the sample separation port;

[0029] After the plasma enters the tertiary flow channel through the secondary flow channel, the tertiary flow channel absorbs all the plasma in the secondary flow channel;

[0030] The plasma reacts with the detection reagent in the tertiary flow channel to obtain the detection result.

[0031] On the other hand, a plasma separation and flow guidance integrated microfluidic chip according to an embodiment of the present invention comprises:

[0032] A sample inlet, the sample inlet is used to receive a blood sample;

[0033] a separation component, connected to the sample inlet, for separating plasma from the blood sample;

[0034] A flow guide component, connected to the separation component;

[0035] The chip body is communicated with the flow guide component, and the flow guide component is used to guide the separated plasma to the chip body.

[0036] According to some embodiments of the present invention, the flow guide assembly comprises:

[0037] A microarray structure, connected to the separation component, the microarray structure having a plurality of pores, and the microarray structure is used to make the plasma flow along the pores by capillary action;

[0038] A plurality of flow guiding channels, each of which is connected to the microarray structure and the chip body respectively, and the flow guiding channel is used to guide the plasma in the pores to the chip body.

[0039] According to some embodiments of the present invention, each of the diversion channels is connected to the microarray structure through a corresponding collection hole, and the plasma enrichment area of ​​the microarray structure is positioned at the collection hole by adjusting the gaps between different areas of the microarray structure.

[0040] According to some embodiments of the present invention, the microarray structure is a tree-like structure, and the channel width of the tree-like structure gradually decreases from the trunk to the branch end close to the collection hole, so that the separated plasma can be diverted to multiple parallel channels with smaller widths before reaching the collection hole.

[0041] According to some embodiments of the present invention, the microarray structure is a concentric ring structure, and the channel width of the concentric ring structure gradually decreases from the outer ring to the inner ring, so that the separated plasma gradually flows from the outer ring to the inner ring toward the collection hole.

[0042] According to some embodiments of the present invention, a plurality of inlets are evenly distributed on the circumference of the outer ring, so that the separated plasma can evenly flow into the outer ring through the plurality of inlets.

[0043] According to some embodiments of the present invention, the hydrophilicity of the material of the outer ring is greater than the hydrophilicity of the material of the inner ring, and the inner wall of the concentric annular structure is provided with a flow-guiding texture.

[0044] According to some embodiments of the present invention, the channel width of the microarray structure in the Z-axis direction gradually narrows from top to bottom.

[0045] According to some embodiments of the present invention, the chip body has a plurality of microchannels, each of which is provided with a microfluidic valve, and the microfluidic valve is used to adjust the flow speed and direction of the plasma so that the plasma flows along the microchannel to the detection area.

[0046] According to some embodiments of the present invention, the chip body includes:

[0047] a first collecting channel, one end of which is in communication with the flow guide assembly, and the other end of which is provided with a first water absorbent pad;

[0048] A plurality of first branch flow channels, each of which is connected to the first collecting channel, the first branch flow channels are located between the first water absorbent pad and the flow guide component, and the first branch flow channels are vertically arranged below the first collecting channel;

[0049] Among them, a test paper is arranged in each of the first branch flow channels, a first measuring positioning hole is arranged on the side of each of the first branch flow channels, and the first measuring positioning hole is located above the test paper, and the bottoms of several of the first branch flow channels are connected to a first air pressure balance port; a first light response film is arranged on the outside of the first branch flow channel.

[0050] According to some embodiments of the present invention, the chip body includes:

[0051] a second collecting channel, one end of the second collecting channel being in communication with the flow guide assembly, and the other end of the second collecting channel being provided with a second water absorbent pad;

[0052] a second branch flow channel, the second branch flow channel being in communication with the second collecting channel, the second branch flow channel being located between the second water absorbent pad and the flow guide assembly, and the second branch flow channel being vertically disposed below the second collecting channel;

[0053] a reaction chamber, disposed at the bottom of the second branch flow channel and communicated with the second branch flow channel;

[0054] The reaction channel is communicated with the reaction chamber and is arranged in parallel with the second collecting channel. A second measuring and positioning hole is arranged at the bottom of the reaction channel, and a second light-responsive film is arranged outside the reaction channel.

[0055] According to some embodiments of the present invention, the flow guide component is a primary flow channel, and the chip body also includes a plurality of secondary flow channels and a plurality of tertiary flow channels, the secondary flow channels correspond one-to-one to the tertiary flow channels, one end of the secondary flow channel is connected to the flow guide component, and the other end of the secondary flow channel is connected to the corresponding tertiary flow channel; a sample separation port is provided on the side of the secondary flow channel, and a quantitative measuring port is provided on the side of the tertiary flow channel.

[0056] According to some embodiments of the present invention, the separation component comprises a filter membrane having a pore size ranging from 0.2 μm to 5 μm.

[0057] According to some embodiments of the present invention, the hydrophilicity of the microfluidic chip is improved by the following method:

[0058] Using benzophenone as a photosensitizer, and evenly coating the photosensitizer on the inner wall of the microfluidic chip;

[0059] Filling the microfluidic chip with a methacryloyloxyethyl phosphorylcholine solution;

[0060] Ultraviolet light is used to irradiate the inside of the microfluidic chip, so that the benzophenone and the polymerized monomers of the methacryloyloxyethyl phosphorylcholine solution undergo a bonding reaction, and a hydration layer is formed on the inner wall of the microfluidic chip.

[0061] The detection method of the microfluidic chip and the integrated plasma separation and diversion microfluidic chip according to the embodiments of the present invention have at least the following beneficial effects: plasma is separated from the blood sample by the separation component, and then the plasma is diverted to the chip body for reaction by the diversion component, thereby obtaining the reaction result. While ensuring efficient separation of plasma, this solution realizes rapid and complete release of separated plasma, and can effectively divert plasma to the microfluidic chip for precise quantitative detection. It can realize efficient plasma separation and rapid diversion to the detection area on the microfluidic platform, and support plasma enrichment and extraction, which can not only improve the speed and sensitivity of detection, but also simplify the operation process.

[0062] Additional aspects and advantages of the present invention will be given in part in the following description and in part will be obvious from the following description, or will be learned through practice of the present invention. BRIEF DESCRIPTION OF THE DRAWINGS

[0063] The above and / or additional aspects and advantages of the present invention will become apparent and easily understood from the description of the embodiments in conjunction with the following drawings, in which:

[0064] Figure 1 A top view of the internal structure of the plasma separation and flow guidance integrated microfluidic chip according to an embodiment of the present invention;

[0065] Figure 2 This is a schematic structural diagram of a sample inlet, a separation component, and a flow guiding component of a plasma separation and flow guiding integrated microfluidic chip according to an embodiment of the present invention;

[0066] Figure 3 for Figure 2 An enlarged schematic diagram of the guide assembly is shown;

[0067] Figure 4 A top view of the internal structure of the plasma separation and flow guidance integrated microfluidic chip according to an embodiment of the present invention;

[0068] Figure 5 Schematic diagram of the flow of plasma in the microarray structure;

[0069] Figure 6 It is a schematic diagram of the microarray structure when it is in a tree-like structure;

[0070] Figure 7 A flow chart of steps for improving the hydrophilicity of a microfluidic chip according to an embodiment of the present invention;

[0071] Figure 8 A schematic diagram of a process for improving the hydrophilicity of a microfluidic chip according to an embodiment of the present invention;

[0072] Fig. 9 It is a schematic structural diagram of a chip body according to a first embodiment of the present invention;

[0073] Fig.10 It is a structural schematic diagram of a chip body according to a second embodiment of the present invention;

[0074] Fig.11 A schematic structural diagram of a chip body according to a third embodiment of the present invention;

[0075] Fig.12 A flow chart of the steps of the detection method of the microfluidic chip according to an embodiment of the present invention;

[0076] The sample inlet 100, the separation component 200, the flow guide component 300, the microarray structure 310, the flow guide channel 320, the chip body 400, the first collection channel 410, the first water absorption pad 420, the first branch flow channel 430, the test paper 440, the first measurement positioning hole 450, the first air pressure balance port 460, the first light response film 470, the second collection channel 510, the second water absorption pad 520, the second branch flow channel 530, the reaction chamber 540, the reaction flow channel 550, the second measurement positioning hole 560, the second light response film 570, the primary flow channel 610, the secondary flow channel 620, the tertiary flow channel 630, the sample separation port 640, and the quantitative measurement port 650. DETAILED DESCRIPTION

[0077] Embodiments of the present invention are described in detail below, and examples of the embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals throughout represent the same or similar elements or elements having the same or similar functions. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain the present application, and are not to be construed as limitations on the present application. For the step numbers in the following embodiments, they are only provided for the convenience of explanation, and the order between the steps is not limited in any way, and the execution order of each step in the embodiment can be adaptively adjusted according to the understanding of those skilled in the art.

[0078] In the description of the present invention, it should be understood that descriptions involving orientations, such as up, down, front, back, left, right, etc., and orientations or positional relationships indicated are based on the orientations or positional relationships shown in the accompanying drawings, and are only for the convenience of describing the present invention and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore should not be understood as a limitation on the present invention.

[0079] The terms "first", "second", "third" and "fourth" etc. in the specification and claims of the present invention and the drawings are used to distinguish different objects, rather than to describe a specific order. In addition, the terms "including" and "having" and any variations thereof are intended to cover non-exclusive inclusions. For example, a process, method, system, product or device that includes a series of steps or units is not limited to the listed steps or units, but may optionally include steps or units that are not listed, or may optionally include other steps or units that are inherent to these processes, methods, products or devices.

[0080] Reference to "embodiments" in the present invention means that a particular feature, structure, or characteristic described in conjunction with the embodiments may be included in at least one embodiment of the present invention. The appearance of the phrase in various places in the specification does not necessarily refer to the same embodiment, nor is it an independent or alternative embodiment that is mutually exclusive with other embodiments. It is explicitly and implicitly understood by those skilled in the art that the embodiments described herein may be combined with other embodiments.

[0081] At present, there are two main methods for plasma separation in microfluidic chips, namely multilayer composite structure and microstructure filtration. Multilayer composite structure usually uses filter membrane and paper-based microfluidic chip to form a multilayer composite structure. The filter membrane is used to achieve preliminary plasma separation, and the separated plasma will be absorbed by the test paper in the lower layer. The detection results of this structure are usually semi-quantitative, which is difficult to achieve accurate quantitative requirements; moreover, the structure cannot enrich and extract the filtered plasma, and the plasma can only be retained in the filter membrane and the test paper, which limits the subsequent in-depth analysis; because the plasma is locked in the porous structure, it is difficult to release effectively, which affects the sensitivity and accuracy of the detection. Another common method is to introduce microbeads into the chip or make microstructures by photolithography technology to achieve plasma separation. This method can theoretically achieve more accurate blood cell isolation and plasma separation. However, the microstructure is prone to clogging during the filtration process, resulting in slow filtration speed and affecting the detection efficiency; similar to the multilayer composite structure, the separated plasma is difficult to release and collect effectively. Therefore, whether it is a multilayer composite structure or microstructure filtration, existing plasma separation devices face the challenge of how to quickly and effectively guide the separated plasma into the microfluidic chip for subsequent testing.

[0082] The solution provided by the embodiment of the present invention can ensure efficient separation of plasma while achieving rapid and complete release of separated plasma, and can effectively guide the plasma to the microfluidic chip for precise quantitative detection. It can achieve efficient plasma separation and rapid guidance to the detection area on the microfluidic platform, and support plasma enrichment and extraction, which can not only improve the speed and sensitivity of detection, but also simplify the operating process.

[0083] On the one hand, if Figure 1 and Figure 2 As shown, an embodiment of the present invention proposes a plasma separation and diversion integrated microfluidic chip, including a sample inlet 100, a separation component 200, a diversion component 300 and a chip body 400, wherein the sample inlet 100 is used to receive a blood sample; the separation component 200 is connected to the sample inlet 100, and is used to separate plasma from the blood sample; the diversion component 300 is connected to the separation component 200, and the chip body 400 is connected to the diversion component 300, and the diversion component 300 is used to divert the separated plasma to the chip body 400.

[0084] Specifically, Figure 2As shown, after adding the blood sample to the sample inlet 100, the blood sample will reach the separation component 200 along the sample inlet 100. In this example, the separation component 200 includes a filter membrane, which is located below the sample inlet 100. The blood sample is filtered through the filter membrane to filter out the plasma and remove the solid components in the blood. The pore size of the filter membrane is designed to be able to pass through the plasma, but not the solid components in the blood sample. For example, the pore size of the filter membrane can range from 0.2 to 5 μm. The principle of extracting plasma from the whole blood sample through the filter membrane here mainly relies on the physical separation between cells and liquid components. In the whole blood sample, the liquid component is mainly plasma, and the solid components include red blood cells, white blood cells and platelets. When the whole blood sample passes through the filter membrane, the plasma passes through the filter membrane under the action of pressure difference or gravity, while the solid components are retained above the filter membrane. The purpose of this is to remove cell components and other large particle impurities, thereby obtaining a clean plasma sample. The liquid component after filtration is plasma, which contains various biochemical components, which is convenient for further detection and analysis. After the plasma is filtered out using the filter membrane, the bottom of the filter membrane directly contacts the flow guide component 300, and the separated plasma is guided to the chip body 400 through the flow guide component 300, so that the plasma reaches the predetermined detection area for subsequent biochemical analysis.

[0085] Furthermore, if Figures 2 to 4 As shown, in some embodiments of the present invention, the flow guide component 300 includes a microarray structure 310 and a plurality of flow guide channels 320. The microarray structure 310 is connected to the separation component 200. The microarray structure 310 has a plurality of pores. The microarray structure 310 is used to make the plasma flow along the pores through capillary action. Each flow guide channel 320 is respectively connected to the microarray structure 310 and the chip body 400. The flow guide channel 320 is used to guide the plasma in the pores to the chip body 400. Specifically, as Figure 3 As shown, the microarray structure 310 includes a plurality of microstructures 311, and through the arrangement of the plurality of microstructures 311, pores are formed in the gaps between the microstructures 311; the microarray structure 310 is in direct contact with the filter membrane of the separation component 200, and when the filter membrane filters out the plasma, the microarray structure 310 introduces the filtered plasma into the pores of the microarray structure 310 through capillary action, so that the extracted plasma flows spontaneously in the tiny pores of the microarray structure 310. This is because the design of the microarray structure 310 usually includes many tiny pores, and the size and shape of these pores can significantly affect the flow of the fluid. First, the pores inside the microarray structure 310 can enhance the contact area of ​​the liquid and produce a capillary effect when the liquid enters. The capillary force will cause the liquid to flow rapidly along the pores and fill these tiny spaces. Secondly, the gaps between the microarray structures 310 can also play an important role. These gaps provide additional channels for the flow of liquid, further facilitating the extraction of the fluid. As shown in FIG. Figure 3 As shown, in the microarray structure 310, there are also multiple collection holes 312, and each guide channel 320 is connected to the microarray structure 310 through the corresponding collection hole 310. By adjusting the gaps between the microstructures 311 in different areas of the microarray structure 310, the plasma enrichment area of ​​the microarray structure 310 is the location of the collection hole 312, thereby further promoting the plasma to flow into each collection hole 312 along the microarray structure 310, and then enter the chip body 400 along the guide channel 320. In this example, the number of collection holes 312 and guide channels 320 are both set to four. It should be noted that the number of collection holes 312 and guide channels 320 can be adjusted according to actual needs, and is not limited to this. Figure 5 As shown in FIG. 4 , the arrow indicates the flow direction of plasma in the microarray structure 310, and the circle indicates the location of the collection hole 312. The closer to the collection hole 312, the denser the distribution of the microstructure 311, and the farther away from the collection hole 312, the sparser the distribution of the microstructure 311, so that the plasma is enriched in the collection hole 312. Finally, the plasma guided through the microarray structure 310 enters the chip body 400 through the guide channel 320. Figure 1 As shown, the chip body 400 has multiple microchannels. Microfluidic valves can be set on the microchannels of the chip body 400. The operator can adjust the flow speed and direction of the plasma by controlling the microfluidic valves, so that the plasma accurately reaches the predetermined detection area for subsequent biochemical analysis.

[0086] In this embodiment, the combination of the microarray structure 310 and the filter membrane ensures efficient separation of plasma while avoiding rapid clogging of the filter membrane. The microarray structure 310 effectively overcomes the adsorption force of the filter membrane and realizes rapid release of plasma. The design of the diversion channel 320 and the microfluidic valve enables the separated plasma to be accurately and quantitatively diverted to the detection area. By adjusting the microfluidic valve, the enrichment of plasma in a specific area can be achieved, which is convenient for subsequent in-depth analysis. The entire process from sample loading to plasma separation to the diversion detection area is automatically completed, which greatly simplifies the operation process. Since the plasma can be quickly and completely released and diverted to the detection area, the retention of plasma in the filter membrane is avoided, thereby improving the sensitivity and accuracy of the detection. Therefore, the plasma separation and diversion channel 320 provided in this embodiment successfully solves the problem of difficult release and diversion of plasma in the prior art through innovative structural design. The device not only realizes efficient plasma separation, but also ensures the rapid release and precise diversion of plasma after separation, and provides a reliable sample pretreatment solution for biochemical analysis on a microfluidic chip.

[0087] Furthermore, in some embodiments of the present invention, in order to further improve the flow efficiency and stability of plasma, this embodiment also proposes an arrangement design of a microarray structure 310 that combines a two-dimensional parallel microchannel tree structure and a three-dimensional conical structure to achieve directional capillary action and gradient capillary action, and optimize the flow path and extraction efficiency of the liquid.

[0088] It should be noted here that the capillary action here is not a pump that relies on external force in the traditional sense, but a figurative description of the movement of plasma under the action of capillary force. The scheme mentioned in the context of the present invention does not involve a physical capillary pump, does not rely on external force, and relies entirely on ingenious design to achieve the spontaneous flow of plasma.

[0089] like Figure 6 As shown, on the XY plane, the arrangement of the microstructure 311 of the microarray structure 310 is designed to be a tree-like structure (which can also be understood as a "tree line structure" in some scenarios), and the extracted plasma is diverted to multiple smaller parallel microchannels. In this way, since the contact area of ​​the entire system increases, it means that more plasma is in contact with the surface of the channel, thereby enhancing the capillary force and evenly distributing the liquid. According to the basic principle of capillary flow, the capillary force is inversely proportional to the diameter of the channel. Therefore, smaller microchannels can more effectively guide the liquid to flow along the channel. By branching into microchannels with small diameters, the capillary pressure and the driving force of the flow are enhanced. In the specific design, the channel width of the tree-like structure can be gradually reduced from 100μm at the trunk to 10μm at the end of the branch to ensure the generation of directional capillary force.

[0090] It is understood that the width and length of the tree structure are not limited and can be adaptively adjusted according to actual capillary force and flow rate requirements. It is also understood that in this embodiment, the angle and channel width can be adjusted at the branching points of the tree structure, and secondary branches can be designed in each branch to further refine and enhance the capillary effect.

[0091] It should be noted that the spontaneous movement of plasma is controlled by capillary phenomena generated by the interaction of liquid surface tension with the chemistry and geometry of the solid interface, and leads to the overall minimization of the free energy between the solid, liquid and vapor interfaces. These capillary phenomena can be used to spontaneously fill the microstructure. The capillary pressure Pc is related to the liquid-gas meniscus in the microchannel and conforms to the following formula:

[0092] Circular microchannel:

[0093]

[0094] Where γ is the surface tension of the liquid, θ is the contact angle, and r is the radius of the capillary.

[0095] The above formula I shows that the smaller the radius of the capillary, the greater the capillary pressure

[0096] Rectangular microchannel:

[0097]

[0098] In the above formula II, γ is the surface tension of the liquid, α b , α t , α l , α τ are the contact angles of the liquid on the bottom, top, left and right walls, respectively, and d and w are the depth and width of the channel, respectively. Each wettable wall of the cross section contributes to the generation of negative pressure in the liquid and draws the liquid into the channel. Therefore, if the cross section changes, a smaller cross section will produce a correspondingly higher capillary pressure difference. The tree-like structure achieves a smooth transition of the fluid by gradually changing the size. The gradual change of the channel reduces the pressure mutation, making the capillary pressure difference of each part smaller. The tree-like structure can evenly distribute the fluid and reduce the pressure fluctuations in the local area. It can also be understood that the flow resistance in the channel is basically constant, resulting in the liquid flowing at a constant rate.

[0099] Regardless of whether the microstructure 311 of the microarray structure 310 is in the shape of a cube, a cylinder, or a circular hexagon, the flow direction of the plasma during the enrichment process is random. By editing the gaps between the microstructures 311 in different regions of the microarray structure 310 in the XY plane, the enrichment direction of the plasma during the lateral flow can be controlled. The area and gap of the required microstructure 311 can be calculated according to the required amount of plasma, that is, the channel with a large collection amount has a larger enrichment area, so that the directional distribution of the extracted plasma in the XY plane can be achieved. In this way, the filtered plasma can be enriched at the collection hole 312 of the diversion channel 320, which is convenient for enriching the plasma.

[0100] Therefore, this embodiment can increase the capillary pressure P by designing smaller parallel microchannels, thereby increasing the extraction and diversion speed, thereby further increasing the mass flow rate. Currently in this embodiment, the spacing between the microarrays is 100 μm, and the entire filtration, extraction and diversion sampling process can be achieved within 3 minutes.

[0101] In some embodiments of the present invention, the tree structure in the above embodiments may also be replaced by a concentric ring structure.

[0102] In this embodiment, the purpose of designing the concentric annular structure is to guide the liquid to gradually flow from the outside to the inside and concentrate to the central position through the clever arrangement of the annular channels. First, the design of the channel adopts the form of multiple layers of concentric rings, in which the annular channels of each layer gradually decrease from the outer ring to the inner ring. This progressive reduction in size ensures that the liquid is gradually guided to the central area during the flow process, effectively avoiding fluid diffusion and achieving gradual concentration. In order to achieve uniform fluid entry, multiple inlets, such as 4 to 6 inlets, are designed around the outer ring and evenly distributed. The uniform distribution of these inlets can ensure that the fluid enters the outer ring evenly, thereby achieving uniform flow distribution in the initial stage and avoiding the phenomenon of biased flow of the liquid when entering. In addition, in order to optimize the flow path of the liquid, the surface of the channel can be specially treated. The outer ring uses hydrophilic materials to promote the liquid to enter the system more smoothly, while the inner ring uses relatively hydrophobic materials to speed up the flow of the liquid. At the same time, introducing microstructures or diversion textures on the surface of the channel helps to further standardize the flow direction of the liquid and reduce the retention and eddy current of the fluid in the channel.

[0103] In the central area of ​​the design, the collection hole 312 is set as the final gathering point of the liquid. The design of this hole not only ensures the effective collection of the liquid, but also combines with the separation function of the filter membrane to achieve effective enrichment and separation of the target components in the liquid. This design realizes an efficient flow path for the liquid to enter from multiple inlets and gradually concentrate to the central collection hole 312 through the optimized combination of the above structure and materials.

[0104] The above is mainly a special design on the XY plane of the microarray structure 310. After the plasma is filtered, it reaches the collection hole 312 and flows downward under the action of capillary force and gravity. However, in order to optimize the speed and efficiency of the flow diversion, in this embodiment, the design of the microstructure 311 of the microarray structure 310 is mainly optimized in the Z-axis direction, and gravity is used to enhance the capillary flow.

[0105] In the Z-axis direction, the microchannel is designed to be wide to narrow from top to bottom. In some cases, it can also be understood as a tapered channel, for example, it can be designed as a conical channel or a truncated cone channel with an inclination angle. In some other embodiments, it can also be a spiral microchannel, using a spiral path to increase the flow distance, enhance the capillary force, and achieve gradient control by changing the pitch. By gradually expanding the lateral dimension of the channel, the capillary effect and the stability of guiding the vertical flow of the liquid are further enhanced, and gravity and capillary force are used to promote the flow of the liquid in the Z-axis direction to achieve the effect of diversion.

[0106] In the Z-axis direction perpendicular to the XY plane, the microstructure 311 is designed to be a circular hexagon or a cone with a certain inclination angle in the Z direction. The principle is to achieve a more efficient and stable Z-direction top-down extraction process by gradually expanding the lateral dimensions of the capillary pump. By expanding the lateral dimensions of the capillary pump (such as being designed as a circular hexagon or a cone), the channel cross-section of the liquid flow can be increased, thereby reducing the flow resistance of the fluid. This design makes the flow of the fluid in the Z direction smoother, avoiding the local flow velocity and pressure drop caused by the narrow channel. When the lateral dimension of the channel increases, the capillary effect can play a role on a larger surface area, enhancing the driving ability of the liquid when it flows in the Z axis. Especially for smaller channels, the stronger the capillary force, the more significant the propulsion effect of the liquid in the channel. The conical design with an inclination angle can make the flow of the liquid in the Z-axis direction more efficient. The inclined channel can use the combined effect of gravity or capillary force to better guide the liquid to flow downward and reduce the possible stagnation area. In the conical structure, the change in the direction and speed of the liquid flow helps to discharge bubbles, reduce the interference of bubbles on the flow, and ensure the continuity of the liquid. As the lateral size of the capillary pump gradually expands, the liquid can be better extracted during the flow process. This structure can effectively extract the liquid above the filter membrane into the channel below through capillary action, improving the extraction efficiency.

[0107] For example, in the Z-axis direction perpendicular to the XY plane, the channel in the microfluidic chip gradually expands into a circular hexagonal conical structure. The conical channel gradually expands from the smaller diameter at the end of the microchannel to the location of the collection hole, ensuring that the liquid is extracted more efficiently in the vertical direction. The principle of the conical design is to reduce the resistance to liquid flow by increasing the lateral dimension of the channel. The enlarged channel cross-section allows the capillary effect to work on a larger surface, enhancing the liquid propulsion effect in the Z direction.

[0108] During operation, the liquid to be processed (such as blood, sample solution) is introduced into the sample inlet 100 of the microfluidic chip. Due to the design of the tree-like structure, the liquid is first evenly distributed in multiple parallel microchannels on the XY plane. The diameter of each microchannel is small and the capillary action is strong, so the liquid can flow smoothly without an external driving force. When the liquid flows along the microchannel to the tapered structure in the Z direction, the capillary action and gravity work together to push the liquid from top to bottom to be extracted to the collection hole. The gradually expanding design of the tapered structure helps to reduce the resistance during liquid flow, avoid the local pressure drop caused by too fast flow rate, and ensure the continuity and stability of the liquid. The combined design of the tree-like structure and the tapered structure significantly improves the fluid driving efficiency of the capillary pump, so that the liquid can be evenly distributed and stably flow to the collection hole. By optimizing and adjusting the channel width of the tree-like structure and the inclination angle of the tapered structure, the required channel size and gap can be calculated according to actual needs to ensure that liquids of different volumes can be accurately distributed and extracted.

[0109] In summary, this embodiment significantly enhances the capillary force and the driving force of liquid flow by combining the tree-like structure of two-dimensional parallel microchannels and the three-dimensional tapered capillary pump design, and can achieve efficient and stable liquid extraction. By rationally designing the size and structure of the microchannel, it is ensured that the liquid can flow smoothly and continuously in both the XY plane and the Z direction, thereby improving the extraction efficiency and accuracy of the microfluidic chip.

[0110] The above embodiments all improve the microfluidic chip from the perspective of structural design. In this embodiment, the channel of the microarray structure 310 and the channel structure of the chip body 400 are improved from the material direction to enhance the filtration and diversion efficiency. Since the liquid components in plasma are generally water (accounting for about 90%, which is the main component of plasma), protein, electrolytes, nutrients, etc. The channel material of the microfluidic chip in the prior art is mainly polymethyl methacrylate (PMMA). From a chemical structure point of view, the main chain of PMMA is composed of a carbon-carbon chain, and the side chain contains an ester group. Although the ester group has a certain polarity, the polarity of the entire molecular structure is relatively low, resulting in poor hydrophilicity. In addition, the surface energy of PMMA is relatively low, which makes it difficult for liquid to spread on its surface, which is not conducive to interaction with water. Therefore, when the microfluidic chip is used in the prior art to perform biochemical analysis and detection on the plasma of the sample to be tested, the poor hydrophilicity of the microfluidic chip will cause the liquid to flow poorly in the channel, while the microfluidic chip of the embodiment of the present invention mainly relies on the interaction force between the liquid and the channel wall. The poor hydrophilicity means that the capillary force is affected, which in turn leads to an increase in flow resistance, which weakens the capillary effect to a certain extent. Therefore, in order to achieve efficient separation of plasma on the same chip and quickly and effectively guide it to the detection area for subsequent analysis, this embodiment uses a zwitterionic polymer for grafting to improve the hydrophilicity of its channel.

[0111] Specifically, if Figure 7 and Figure 8 As shown in this example, the hydrophilicity of the microfluidic chip is improved by the following methods:

[0112] Step S100: using benzophenone as a photosensitizer, and evenly coating the photosensitizer on the inner wall of the microfluidic chip;

[0113] Step S200: filling the microfluidic chip with a methacryloyloxyethyl phosphorylcholine solution;

[0114] Step S300: using ultraviolet light to irradiate the inside of the microfluidic chip, so that benzophenone and the polymerized monomers of the methacryloyloxyethyl phosphorylcholine solution undergo a bonding reaction, and a hydration layer is formed on the inner wall of the microfluidic chip.

[0115] See also Figure 8 First, benzophenone is used as a photosensitizer, which is evenly coated and pre-adsorbed on the inner wall surface of the PMMA chip channel. Subsequently, a methacryloyloxyethyl phosphorylcholine (pMPC) solution is introduced to fill the entire microfluidic channel. In this step, pMPC, as a zwitterionic polymer, has electrical neutrality and can bind to benzophenone. Next, ultraviolet light is used to irradiate the inside of the PMMA chip channel. Ultraviolet light irradiation triggers the activation of benzophenone and a bonding reaction occurs with the polymerized monomers of pMPC. In this process, the pMPC monomer forms a layer of stable grafted polymer on the inner wall of the microfluidic chip. Due to the zwitterionic structure of pMPC, the polymer chain carries both positive and negative charges, and finally forms a thick hydration layer on the PMMA surface. This hydration layer not only enhances the hydrophilicity of the inner surface of the PMMA chip channel, but also effectively prevents the nonspecific adsorption of biomolecules (such as proteins and peptides) on the inner wall.

[0116] It should be noted that if Figure 8 The PMMA in the formula is polymethyl methacrylate, PMMA-BP refers to polymethyl methacrylate mixed with some additives or modifiers, and PMMA-pMPC refers to the modified product after polymethyl methacrylate and polymethacryloyloxyethyl phosphorylcholine are grafted.

[0117] It can be understood that this embodiment only uses polymethacryloyloxyethyl phosphorylcholine as an example of a zwitterionic polymer, and in some other scenarios, other zwitterionic polymers can also be used.

[0118] The hydrophilicity of the modified microfluidic chip is significantly enhanced due to the introduction of phosphorylcholine groups (pMPC). After actual testing, the contact angle of the pure PMMA microfluidic chip is 67°, and the contact angle after grafting modification becomes 15°. The contact angle after standing for 7 days is only 21°. This is because the long-range electrostatic interaction between pMPC and water molecules forms a high-density hydration layer. This hydration layer not only effectively repels the adsorption of proteins and other biomolecules, significantly reducing the loss of samples, but also reduces the capillary resistance in the channel, thereby improving the detection sensitivity of the microfluidic system in the analysis of biological samples. In addition, the anti-fouling performance of pMPC further enhances the biocompatibility of the chip, reduces the adhesion of substances such as platelets on the surface, and reduces the risk of coagulation. This modification improves the overall performance of the microfluidic chip, making it more reliable and sensitive in the analysis of complex biological samples.

[0119] Figure 1 The design of a chip body 400 is shown. Fig. 9 As shown, the embodiment of the present invention also proposes another design concept of the chip body 400, so that the microfluidic chip can optimize the traditional semi-quantitative detection method into quantitative antigen-antibody detection.

[0120] like Fig. 9 As shown, in this example, the chip body 400 includes a first collecting channel 410 and several first branch flow channels 430, one end of the first collecting channel 410 is connected to the guide component 300, and the other end of the first collecting channel 410 is provided with a first water absorbent pad 420; each first branch flow channel 430 is connected to the first collecting channel 410, the first branch flow channel 430 is located between the first water absorbent pad 420 and the guide component 300, and the first branch flow channel 430 is vertically arranged below the first collecting channel 410; wherein, a detection test paper 440 is arranged in each first branch flow channel 430, a first measuring positioning hole 450 is arranged on the side of each first branch flow channel 430, and the first measuring positioning hole 450 is located above the detection test paper 440, and the bottom of several first branch flow channels 430 is connected to a first air pressure balance port 460; a first light response film 470 is arranged on the outside of the first branch flow channel 430.

[0121] It should be noted that Fig. 9 The left part in the figure is a combination of the sample inlet 100, the separation component 200 and the flow guide component 300. In this embodiment, the working process of the microfluidic chip is as follows:

[0122] 5-15 μl of blood sample is added to the sample inlet 100 using a pipette, and the blood will spontaneously complete plasma separation through the filter membrane. When plasma seeps out from the lower surface of the filter membrane, the microarray structure 310 will be activated. Due to the additive effect of capillary action, the microarray structure 310 will produce a larger capillary action, quickly absorbing the plasma from the filter membrane into the diversion channel 320, and then flowing into the first collection channel 410 through the diversion channel 320. When the plasma flows through the junction of the first collection channel 410 and the first branch channel 430, due to the different channel scales, it will spontaneously flow into the first branch channel 430 until it stops at the position of the first measuring positioning hole 450. At this time, the plasma in the first collection channel 410 continues to flow forward to the first absorbent pad 420. Since the capillary force of the first absorbent pad 420 is very large, the plasma in the first collection channel 410 will be quickly absorbed to the first absorbent pad 420 and disconnected from the first branch channel 430. At this time, independent and quantitative plasma exists in the first branch channel 430. At this time, the first light-responsive film 470 is irradiated with 470nm blue light, and the plasma will move toward the test paper 440 under the action of the light-induced Laplace pressure difference, and the antigen in the plasma will react and bind with the test paper 440, such as the antigen-antibody binding of the new coronavirus. Since the sample is quantitative and the light-controlled sample can be transported back and forth, the antigen in the sample can fully react with the detection reagent fixed on the test strip. Therefore, a more accurate quantitative detection process can be achieved based on the degree of color change (grayscale) of the test strip than using only a filter membrane + test strip.

[0123] like Fig.10 As shown, in some embodiments of the present invention, another design concept of the chip body 400 is proposed. In this example, the chip body 400 includes a second collection channel 510, a second branch channel 530, a reaction chamber 540 and a reaction channel 550. One end of the second collection channel 510 is connected to the flow guide component 300, and the other end of the second collection channel 510 is provided with a second water absorbent pad 520. The second branch channel 530 is connected to the second collection channel 510, and the second branch channel 530 is located between the second water absorbent pad 520 and the flow guide component 300, and the second branch channel 530 is vertically arranged below the second collection channel 510; the reaction chamber 540 is arranged at the bottom of the second branch channel 530 and is connected to the second branch channel 530; the reaction channel 550 is connected to the reaction chamber 540, and the reaction channel 550 is arranged in parallel with the second collection channel 510, and the bottom of the reaction channel 550 is provided with a second measuring positioning hole 560, and the outside of the reaction channel 550 is provided with a second light response film 570. In this embodiment, the working process of the microfluidic chip is as follows:

[0124] Reagent pre-packaging: First, the detection reagent is printed in the reaction chamber 540 by inkjet printing, and the reagent volume is 0.5-1.5 μl. The microfluidic chip with the quantitative reagent in the reaction chamber 540 is placed in a freeze dryer for processing. The detection reagent becomes powder after freeze drying. At this time, the second light response film 570 is attached to the microfluidic chip loaded with the detection reagent powder. The flow channel structure in the chip is as follows: Fig.10 Alternatively, antibody modification is performed: antibodies are modified on the channel surface of the reaction chamber 540 . The antibody modification method may be to introduce amine groups on the substrate surface and then bind and fix the antibodies to the amine groups. Other methods may also be used.

[0125] Blood pretreatment: Use a pipette to add 5-15 microliters of blood to the sample inlet 100. The blood will spontaneously complete plasma separation through the filter membrane. When plasma seeps out from the lower surface of the filter membrane, the microarray structure 310 at the reaction chamber 540 will be activated. Due to the additive effect of capillary action, the array will produce a large capillary action to quickly absorb plasma from the filter membrane into the second collection channel 510. When the plasma flows through the junction of the second collection channel 510 and the second branch channel 510, due to the different channel sizes, it will spontaneously flow into the second branch channel 510 and further fill the reaction chamber 540 until it stops at the second measuring positioning hole 560. At this time, the plasma in the second collection channel 510 continues to flow forward to the second absorbent pad 520. Since the capillary force of the second absorbent pad 520 is very large, the plasma in the second collection channel 510 will be quickly absorbed to the second absorbent pad 520 and disconnected from the second branch channel 530. At this time, independent and quantitative plasma exists in the reaction chamber 540. At this time, the second photoresponsive film 570 is irradiated with 470nm blue light, and the plasma will realize reciprocating oscillation under the action of the light-induced Laplace pressure difference, and fully mix and react with the freeze-dried reagent powder pre-buried in the reaction chamber 540. The reaction process is that the target protein in the plasma, such as NTpro-BNP (brain natriuretic peptide), will bind to the antibody modified on the surface of the microsphere in the antibody reagent, causing the entire reaction system to emit fluorescence. Since the antibody reagent is excessive, the intensity of the fluorescence signal is positively correlated with the concentration of the protein marker in the plasma, thereby realizing the quantitative immunoassay process of trace blood samples.

[0126] like Fig.11As shown, in some embodiments of the present invention, another design idea of ​​the chip body 400 is also proposed. In this example, the flow guide component 300 is a primary flow channel 610, and the chip body 400 also includes a plurality of secondary flow channels 620 and a plurality of tertiary flow channels 630, the secondary flow channels 620 correspond to the tertiary flow channels 630 one by one, one end of the secondary flow channel 620 is connected to the flow guide component 300, and the other end of the secondary flow channel 620 is connected to the corresponding tertiary flow channel 630; a sample separation port 640 is provided on the side of the secondary flow channel 620, and a quantitative measurement port 650 is provided on the side of the tertiary flow channel 630.

[0127] This embodiment uses a microfluidic chip for sample distribution and quantitative measurement. A complex flow channel system is designed in the microfluidic chip, including branch channels and interception valves (i.e., sample separation ports 640), and the flow of liquid is controlled by capillary force and air pressure, thereby achieving effective sample processing. The working process of the microfluidic chip is as follows:

[0128] First, a blood sample is loaded into the sample inlet 100 of the microfluidic chip. After preliminary filtration, the blood flows into the primary flow channel 610. As the filtration process proceeds, the capillary force in the primary flow channel 610 gradually increases. When it reaches a certain level, the capillary force of the primary flow channel 610 will exceed that of the tertiary flow channel 630, thereby locking the unfiltered blood and the plasma in the filter membrane in the primary flow channel 610 to prevent them from entering the secondary flow channel 620. Next, the air pressure is used to control the interception valve so that the separated plasma is disconnected from the primary flow channel 610 at the secondary flow channel 620. This process ensures that only the plasma that has been preliminarily filtered is stored in the secondary flow channel 620. Subsequently, the plasma is guided into the tertiary flow channel 630 to achieve quantitative measurement. The tertiary flow channel 630 is specially designed to have a precise volume to ensure that a consistent sample volume can be obtained in each operation. After the plasma enters the tertiary flow channel 630, the capillary pump (a non-physical pump) begins to absorb the excess plasma in the secondary flow channel 620. At this stage, since the capillary force of the secondary flow channel 620 is relatively small, the liquid will be drawn from this area first, ensuring that the secondary flow channel 620 is completely emptied. The completion of this step not only achieves the separation of the samples, but also ensures the independence of each sample.

[0129] It should be noted that in the primary flow channel 610, a filtering process from blood to plasma occurs. If the radii of the primary flow channel 610, the secondary flow channel 620, and the tertiary flow channel 630 are r1>r2>r3, then the capillary force is P1<P2<P3, so the fluid can flow from the primary flow channel 610→secondary flow channel 620→tertiary flow channel 630. When the capillary force in the primary flow channel 610 gradually increases and exceeds the tertiary flow channel 630, it is equivalent to that the fluid no longer actively flows to the tertiary flow channel 630, because the capillary force of the tertiary flow channel 630 is smaller than that of the primary flow channel 610, then the liquid will not flow from the secondary flow channel 620 into the tertiary flow channel 630, then the fluid in the secondary flow channel 620 cannot flow and reversely blocks the liquid flowing from the primary flow channel 610, so the plasma will be blocked in the primary flow channel 610. When the air pressure control interception valve (i.e., the sample separation port 640, which is actually an air hole) is opened, the cross-sectional area of ​​the air hole is smaller than the cross-sectional area of ​​the secondary flow channel 620. Therefore, part of the liquid in the secondary flow channel 620 flows to the tertiary flow channel 630, and part of it flows to the sample separation port 640 of the secondary flow channel 620. The atmosphere will block the intersection of the secondary flow channel 620 and the sample separation port 640, so that the fluid in the primary flow channel 610 cannot flow to the secondary flow channel 620, but the secondary flow channel 620 The fluid in the secondary flow channel 620 continues to flow to the tertiary flow channel 630. When the pores in the tertiary flow channel 630 are opened, the fluid in the secondary flow channel 620 is divided into two paths at the intersection with the tertiary flow channel 630, one part flows clockwise and the other part flows counterclockwise. When the pores in the tertiary flow channel 630 are opened, the clockwise and counterclockwise flowing parts of the fluid will squeeze the air inside the tertiary flow channel 630 and discharge it. When the tertiary flow channel 630 is completely filled, a liquid column will be formed and automatically closed, completing the measuring process.

[0130] Through the above steps, the microfluidic chip effectively achieves accurate sample distribution and quantitative measurement. Each processing step uses a combination of physical properties and chip structure to ensure the efficiency and accuracy of sample processing. Subsequently, the distributed and quantified samples can be further analyzed and tested in independent channels. This design solves the problems of sample cross-contamination and inaccurate quantification in traditional methods.

[0131] In summary, the microfluidic chip of the embodiment of the present invention can be applied to a one-step immune reaction, can also be applied to a complex multi-step reaction, and can also be used as a pre-processing structure.

[0132] When the microfluidic chip is used for a one-step immune response, all processes are completed directly in the chip. For example, a freeze-dried reagent can be pre-embedded in the channel, and the fluorescence reaction and detection can be directly performed in situ with the sample after measurement. In this embodiment, a one-step immune response is achieved through a microfluidic chip, and sample distribution, reagent dissolution, immune response and fluorescence detection are integrated into one system. Freeze-dried reagents are pre-embedded in specific channels of the microfluidic chip. These reagents have been optimized according to the target analytes during the production process to ensure that they can react with specific antigens or antibodies in the sample after dissolution. The blood sample is loaded into the inlet of the chip. Using capillary force and air pressure control, the sample is preliminarily filtered in the primary flow channel to remove cellular components. The filtered plasma is guided to the tertiary flow channel for precise quantitative measurement to ensure that the sample volume used for the reaction is consistent, thereby improving the repeatability and accuracy of the results. When the sample flows into the channel containing the freeze-dried reagent, the liquid properties of the sample are used to dissolve the freeze-dried reagent to form a uniform reaction mixture. This process is automatically performed inside the chip without additional operation. Then, the target analyte in the sample reacts specifically with the reagent. After the immune reaction is completed, the sample in the channel directly enters the detection area. The fluorescence signal is excited and detected by the optical elements embedded in the chip. The intensity of the fluorescence signal is proportional to the concentration of the target analyte. The content of the target in the sample can be quantitatively analyzed by reading the signal intensity through the detection instrument. The data obtained from the test is transmitted to the computer system for analysis. Combined with the standard curve, the concentration of the target analyte in the sample can be accurately calculated. The entire process is completed inside the microfluidic chip, reducing external operation steps and reducing the risk of contamination.

[0133] When the microfluidic chip is applied to complex multi-step reactions, such as molecular detection, it can be integrated into other functional modules after the structure of measurement to achieve multiple detection of samples. For example, according to several markers corresponding to a class of diseases, such as six hormones, liver function, kidney function, etc., a specific number of sample-dividing and measuring reaction units can be set, and the measuring and detecting function can be realized in the same chip according to the sample amount required for detection. This embodiment aims to integrate multi-step reactions through a microfluidic chip to achieve multiple detection of samples. For multiple markers corresponding to a class of diseases, such as six hormones, liver function, kidney function, etc., the chip is designed to achieve sample-dividing, measuring and multiple detection. Multiple sample-dividing and measuring units are set in the chip, and each unit is optimized for different markers. Each unit is connected to the central sample inlet to ensure that the sample can be equally distributed when it flows in. In each measuring unit, the freeze-dried reagent required for the corresponding marker detection is preset. The module is designed with a specific reaction area and detection area to meet different detection needs. The blood sample is placed at the central inlet of the chip, and the sample is automatically distributed to each measuring unit by capillary force or air pressure. During the flow process, precise control of sample volume is achieved through microfluidic channel design to ensure that each unit obtains the correct sample volume. After the sample flows to each measuring unit, it dissolves the pre-embedded freeze-dried reagent and undergoes a specific chemical or immune reaction. The reagents and reaction conditions of each unit have been pre-set to match its detection target. After the reaction is completed, the sample directly enters the detection area. The signal of each marker is read through the optical or electrochemical detection element integrated on the chip. Through this microfluidic chip, one-step integration of multiple sample detection is achieved, which improves detection efficiency and reduces the operation steps and errors in traditional methods.

[0134] When the microfluidic chip is used as a pre-treatment structure, the micro sample solution after measuring can be matched with other microfluidic chips to achieve immune, biochemical, and molecular detection. In this embodiment, the microfluidic chip is used as a pre-treatment structure, so that the micro sample solution after accurate measurement can be combined with other subsequent microfluidic chips to achieve immune, biochemical, and molecular detection. The chip contains a sample distribution and measurement unit, which can extract a precise volume of micro sample solution from the original sample. Through microfluidic technology, a capillary force-driven or pressure-controlled channel is designed to achieve automatic separation and accurate measurement of samples. The sample is placed in the chip entrance, and unnecessary components such as cells are automatically removed using the channels and filters designed inside the chip. The sample is accurately measured in the chip, distributed to multiple outlet channels, and prepared to be transmitted to the subsequent detection chip. The pre-treatment chip is designed with a standardized fluid interface so that it can be easily connected to the subsequent immune, biochemical or molecular detection chip to achieve seamless transfer of samples. The treated micro sample solution is transmitted to the target detection chip using the Laplace pressure difference. The sample is transferred to a microfluidic chip with integrated antibodies or antigens for specific binding and fluorescence detection. The sample enters a biochemical reaction chip for analysis through enzymatic reactions, etc. It is used for molecular biology detection such as PCR amplification or nucleic acid hybridization. Through this integrated design, a systematic process from sample pre-treatment to multiple detection is realized, providing an efficient and accurate solution for complex sample analysis.

[0135] On the other hand, based on the plasma separation and flow guidance integrated microfluidic chip of the above-mentioned embodiment, the embodiment of the present invention also proposes a detection method of the microfluidic chip, such as Fig.12 As shown, the detection method comprises the following steps:

[0136] Step S1000: inserting a blood sample into the sample inlet 100;

[0137] Step S2000: the separation component 200 separates plasma from the blood sample and transfers the plasma to the flow guide component 300;

[0138] Step S3000: the flow guiding component 300 guides the plasma to the chip body 400;

[0139] Step S4000: The chip body 400 detects the plasma and obtains the test results.

[0140] Specifically, Figure 2As shown, after adding the blood sample to the sample inlet 100, the blood sample will reach the separation component 200 along the sample inlet 100. In this example, the separation component 200 includes a filter membrane, which is located below the sample inlet 100. The blood sample is filtered through the filter membrane to filter out the plasma and remove the solid components in the blood. The pore size of the filter membrane is designed to be able to pass through the plasma, but not the solid components in the blood sample. For example, the pore size of the filter membrane can range from 0.2 to 5 μm. The principle of extracting plasma from the whole blood sample through the filter membrane here mainly relies on the physical separation between cells and liquid components. In the whole blood sample, the liquid component is mainly plasma, and the solid components include red blood cells, white blood cells and platelets. When the whole blood sample passes through the filter membrane, the plasma passes through the filter membrane under the action of pressure difference or gravity, while the solid components are retained above the filter membrane. The purpose of this is to remove cell components and other large particle impurities, thereby obtaining a clean plasma sample. The liquid component after filtration is plasma, which contains various biochemical components, which is convenient for further detection and analysis. After the plasma is filtered out using the filter membrane, the bottom of the filter membrane directly contacts the flow guide component 300, and the separated plasma is guided to the chip body 400 through the flow guide component 300, so that the plasma reaches the predetermined detection area for subsequent biochemical analysis.

[0141] Furthermore, in this example, the flow guide component 300 includes a microarray structure 310 and a plurality of flow guide channels 320, and the microarray structure 310 has a plurality of channels. The above step S3000 specifically includes the following two steps:

[0142] (1) The microarray structure 310 allows plasma to flow along the pores through capillary action and be enriched in the flow channel 320;

[0143] (2) The guide channel 320 guides the plasma in the channel to the chip body 400.

[0144] Specifically, Figure 3As shown, the microarray structure 310 includes a plurality of microstructures 311, and through the arrangement of the plurality of microstructures 311, pores are formed in the gaps between the microstructures 311; the microarray structure 310 is in direct contact with the filter membrane of the separation component 200, and when the filter membrane filters out the plasma, the microarray structure 310 introduces the filtered plasma into the pores of the microarray structure 310 through capillary action, so that the extracted plasma flows spontaneously in the tiny pores of the microarray structure 310. This is because the design of the microarray structure 310 usually includes many tiny pores, and the size and shape of these pores can significantly affect the flow of the fluid. First, the pores inside the microarray structure 310 can enhance the contact area of ​​the liquid and produce a capillary effect when the liquid enters. The capillary force will cause the liquid to flow rapidly along the pores and fill these tiny spaces. Secondly, the gaps between the microarray structures 310 can also play an important role. These gaps provide additional channels for the flow of liquid, further facilitating the extraction of the fluid. As shown in FIG. Figure 3 As shown, in the microarray structure 310, there are also multiple collection holes 312, and each guide channel 320 is connected to the microarray structure 310 through the corresponding collection hole 310. By adjusting the gaps between the microstructures 311 in different areas of the microarray structure 310, the plasma enrichment area of ​​the microarray structure 310 is the location of the collection hole 312, thereby further promoting the plasma to flow into each collection hole 312 along the microarray structure 310, and then enter the chip body 400 along the guide channel 320. In this example, the number of collection holes 312 and guide channels 320 are both set to four. It should be noted that the number of collection holes 312 and guide channels 320 can be adjusted according to actual needs, and is not limited to this. Figure 5 As shown in FIG. 4 , the arrow indicates the flow direction of plasma in the microarray structure 310, and the circle indicates the location of the collection hole 312. The closer to the collection hole 312, the denser the distribution of the microstructure 311, and the farther away from the collection hole 312, the sparser the distribution of the microstructure 311, so that the plasma is enriched in the collection hole 312. Finally, the plasma guided through the microarray structure 310 enters the chip body 400 through the guide channel 320. Figure 1 As shown, the chip body 400 has multiple microchannels. Microfluidic valves can be set on the microchannels of the chip body 400. The operator can adjust the flow speed and direction of the plasma by controlling the microfluidic valves, so that the plasma accurately reaches the predetermined detection area for subsequent biochemical analysis.

[0145] like Fig. 9As shown, in some embodiments of the present invention, the chip body 400 includes a first collecting channel 410 and several first branch flow channels 430, one end of the first collecting channel 410 is connected to the guide component 300, and the other end of the first collecting channel 410 is provided with a first water absorbent pad 420; each first branch flow channel 430 is connected to the first collecting channel 410, the first branch flow channel 430 is located between the first water absorbent pad 420 and the guide component 300, and the first branch flow channel 430 is vertically arranged below the first collecting channel 410; wherein, a detection test paper 440 is arranged in each first branch flow channel 430, a first measuring positioning hole 450 is arranged on the side of each first branch flow channel 430, and the first measuring positioning hole 450 is located above the detection test paper 440, and the bottom of several first branch flow channels 430 is connected to a first air pressure balance port 460; a first light response film 470 is arranged on the outside of the first branch flow channel 430. In this embodiment, the above step S4000 includes the following four steps:

[0146] (1) Plasma enters the first collection channel 410 through the flow guide component 300;

[0147] (2) When the plasma reaches the junction of the first collecting channel 410 and the first branch channel 430, the plasma flows into the first branch channel 430 until it reaches the first measuring positioning hole 450;

[0148] (3) The plasma in the first collecting channel 410 continues to flow forward to the first absorbent pad 420 and no longer flows into the first branch flow channel 430, so that independent and quantitative plasma exists in the first branch flow channel 430;

[0149] (4) The first light-responsive film 470 is irradiated with a preset light, so that the plasma in the first branch flow channel 430 reacts with the test paper 440 to obtain a test result.

[0150] Specifically, in this embodiment, the working process of the microfluidic chip is as follows:

[0151] 5-15 μl of blood sample is added to the sample inlet 100 using a pipette, and the blood will spontaneously complete plasma separation through the filter membrane. When plasma seeps out from the lower surface of the filter membrane, the microarray structure 310 will be activated. Due to the additive effect of capillary action, the microarray structure 310 will produce a larger capillary action, quickly absorbing the plasma from the filter membrane into the diversion channel 320, and then flowing into the first collection channel 410 through the diversion channel 320. When the plasma flows through the junction of the first collection channel 410 and the first branch channel 430, due to the different channel scales, it will spontaneously flow into the first branch channel 430 until it stops at the position of the first measuring positioning hole 450. At this time, the plasma in the first collection channel 410 continues to flow forward to the first absorbent pad 420. Since the capillary force of the first absorbent pad 420 is very large, the plasma in the first collection channel 410 will be quickly absorbed to the first absorbent pad 420 and disconnected from the first branch channel 430. At this time, independent and quantitative plasma exists in the first branch channel 430. At this time, the first light-responsive film 470 is irradiated with 470nm blue light, and the plasma will move toward the test paper 440 under the action of the light-induced Laplace pressure difference, and the antigen in the plasma will react and bind with the test paper 440, such as the antigen-antibody binding of the new coronavirus. Since the sample is quantitative and the light-controlled sample can be transported back and forth, the antigen in the sample can fully react with the detection reagent fixed on the test strip. Therefore, a more accurate quantitative detection process can be achieved based on the degree of color change (grayscale) of the test strip than using only a filter membrane + test strip.

[0152] like Fig.10 As shown, in some embodiments of the present invention, the chip body 400 includes a second collecting channel 510, a second branch flow channel 530, a reaction chamber 540 and a reaction flow channel 550, one end of the second collecting channel 510 is connected to the guide component 300, and the other end of the second collecting channel 510 is provided with a second water absorbent pad 520, the second branch flow channel 530 is connected to the second collecting channel 510, the second branch flow channel 530 is located between the second water absorbent pad 520 and the guide component 300, and the second branch flow channel 530 is vertically arranged below the second collecting channel 510; the reaction chamber 540 is arranged at the bottom of the second branch flow channel 530 and is connected to the second branch flow channel 530; the reaction flow channel 550 is connected to the reaction chamber 540, and the reaction flow channel 550 is arranged parallel to the second collecting channel 510, the bottom of the reaction flow channel 550 is provided with a second measuring positioning hole 560, and the outside of the reaction flow channel 550 is provided with a second light response film 570. In this embodiment, the above step S4000 includes the following five steps:

[0153] (1) Printing the detection reagent in the reaction chamber 540 by inkjet printing, and making the detection reagent into powder by freeze drying; or modifying the inner surface of the reaction chamber 540 with antibodies to form the detection reagent;

[0154] (2) Plasma enters the second collection channel 510 through the flow guide component 300;

[0155] (3) When the plasma reaches the junction of the second collecting channel 510 and the second branch channel 530, the plasma flows into the second branch channel 530, fills the reaction chamber 540, and reaches the second measuring positioning hole 560;

[0156] (4) The plasma in the second collection channel 510 continues to flow forward to the second water absorbent pad 520 and no longer flows into the second branch flow channel 530, so that independent and quantitative plasma exists in the reaction chamber 540;

[0157] (5) Using a preset light to irradiate the second light-responsive film 570, so that the plasma in the reaction chamber 540 reacts with the detection reagent to obtain a detection result.

[0158] Specifically, in this embodiment, the working process of the microfluidic chip is as follows:

[0159] Reagent pre-packaging: First, the detection reagent is printed in the reaction chamber 540 by inkjet printing, and the reagent volume is 0.5-1.5 μl. The microfluidic chip with the quantitative reagent in the reaction chamber 540 is placed in a freeze dryer for processing. The detection reagent becomes powder after freeze drying. At this time, the second light response film 570 is attached to the microfluidic chip loaded with the detection reagent powder. The flow channel structure in the chip is as follows: Fig.10 Alternatively, antibody modification is performed: antibodies are modified on the channel surface of the reaction chamber 540 . The antibody modification method may be to introduce amine groups on the substrate surface and then bind and fix the antibodies to the amine groups. Other methods may also be used.

[0160] Blood pretreatment: Use a pipette to add 5-15 microliters of blood to the sample inlet 100. The blood will spontaneously complete plasma separation through the filter membrane. When plasma seeps out from the lower surface of the filter membrane, the microarray structure 310 at the reaction chamber 540 will be activated. Due to the additive effect of capillary action, the array will produce a large capillary action to quickly absorb plasma from the filter membrane into the second collection channel 510. When the plasma flows through the junction of the second collection channel 510 and the second branch channel 510, due to the different channel sizes, it will spontaneously flow into the second branch channel 510 and further fill the reaction chamber 540 until it stops at the second measuring positioning hole 560. At this time, the plasma in the second collection channel 510 continues to flow forward to the second absorbent pad 520. Since the capillary force of the second absorbent pad 520 is very large, the plasma in the second collection channel 510 will be quickly absorbed to the second absorbent pad 520 and disconnected from the second branch channel 530. At this time, independent and quantitative plasma exists in the reaction chamber 540. At this time, the second photoresponsive film 570 is irradiated with 470nm blue light, and the plasma will realize reciprocating oscillation under the action of the light-induced Laplace pressure difference, and fully mix and react with the freeze-dried reagent powder pre-buried in the reaction chamber 540. The reaction process is that the target protein in the plasma, such as NTpro-BNP (brain natriuretic peptide), will bind to the antibody modified on the surface of the microsphere in the antibody reagent, causing the entire reaction system to emit fluorescence. Since the antibody reagent is excessive, the intensity of the fluorescence signal is positively correlated with the concentration of the protein marker in the plasma, thereby realizing the quantitative immunoassay process of trace blood samples.

[0161] like Fig.11 As shown, in some embodiments of the present invention, the flow guide component 300 is a primary flow channel 610, and the chip body 400 further includes a plurality of secondary flow channels 620 and a plurality of tertiary flow channels 630, the secondary flow channels 620 correspond to the tertiary flow channels 630 one by one, one end of the secondary flow channel 620 is connected to the flow guide component 300, and the other end of the secondary flow channel 620 is connected to the corresponding tertiary flow channel 630; a sample separation port 640 is provided on the side of the secondary flow channel 620, and a quantitative measurement port 650 is provided on the side of the tertiary flow channel 630. In this embodiment, the above step S4000 includes the following three steps:

[0162] (1) After the plasma flows through the primary flow channel 610 into the secondary flow channel 620, it enters the sample separation port 640;

[0163] (2) After the plasma passes through the secondary flow channel 620 and enters the tertiary flow channel 630, the tertiary flow channel 630 absorbs all the plasma in the secondary flow channel 620;

[0164] (3) The plasma reacts with the detection reagent in the tertiary flow channel 630 to obtain the detection result.

[0165] This embodiment uses a microfluidic chip for sample distribution and quantitative measurement. A complex flow channel system is designed in the microfluidic chip, including branch channels and interception valves (i.e., sample separation ports 640), and the flow of liquid is controlled by capillary force and air pressure, thereby achieving effective sample processing. The working process of the microfluidic chip is as follows:

[0166] First, a blood sample is loaded into the sample inlet 100 of the microfluidic chip. After preliminary filtration, the blood flows into the primary flow channel 610. As the filtration process proceeds, the capillary force in the primary flow channel 610 gradually increases. When it reaches a certain level, the capillary force of the primary flow channel 610 will exceed that of the tertiary flow channel 630, thereby locking the unfiltered blood and the plasma in the filter membrane in the primary flow channel 610 to prevent them from entering the secondary flow channel 620. Next, the air pressure is used to control the interception valve so that the separated plasma is disconnected from the primary flow channel 610 at the secondary flow channel 620. This process ensures that only the plasma that has been preliminarily filtered is stored in the secondary flow channel 620. Subsequently, the plasma is guided into the tertiary flow channel 630 to achieve quantitative measurement. The tertiary flow channel 630 is specially designed to have a precise volume to ensure that a consistent sample volume can be obtained in each operation. After the plasma enters the tertiary flow channel 630, the capillary pump (a non-physical pump) begins to absorb the excess plasma in the secondary flow channel 620. At this stage, since the capillary force of the secondary flow channel 620 is relatively small, the liquid will be drawn from this area first, ensuring that the secondary flow channel 620 is completely emptied. The completion of this step not only achieves the separation of the samples, but also ensures the independence of each sample.

[0167] Through the above steps, the microfluidic chip effectively achieves accurate sample distribution and quantitative measurement. Each processing step uses a combination of physical properties and chip structure to ensure the efficiency and accuracy of sample processing. Subsequently, the distributed and quantified samples can be further analyzed and tested in independent channels. This design solves the problems of sample cross-contamination and inaccurate quantification in traditional methods.

[0168] The embodiments of the present invention are described in detail above with reference to the accompanying drawings, but the present invention is not limited to the above embodiments, and various changes can be made within the knowledge scope of ordinary technicians in the relevant technical field without departing from the purpose of the present invention.

Claims

1. A detection method based on a microfluidic chip, characterized in that: The invention is applied to a plasma separation and flow guiding integrated microfluidic chip, wherein the plasma separation and flow guiding integrated microfluidic chip comprises a sample inlet, a separation component, a flow guiding component and a chip body; the detection method comprises the following steps: Putting a blood sample into the sample inlet; The separation component separates plasma from the blood sample and transports the plasma to the flow guide component; The flow guiding component guides the plasma to the chip body; The chip body detects the plasma to obtain a detection result.

2. The detection method of the microfluidic chip according to claim 1, characterized in that: The flow guiding component comprises a microarray structure and a plurality of flow guiding channels, wherein the microarray structure has a plurality of channels; The step of the flow guiding component guiding the plasma to the chip body comprises: The microarray structure allows the plasma to flow along the pores through capillary action and be enriched in the flow-guiding channel; The guide channel guides the plasma in the pore to the chip body.

3. The detection method of the microfluidic chip according to claim 1, characterized in that: The chip body comprises: a first collecting channel and a plurality of first branch flow channels, one end of the first collecting channel is connected to the flow guide component, a first water absorbent pad is arranged at the other end of the first collecting channel, each of the first branch flow channels is connected to the first collecting channel, the first branch flow channel is located between the first water absorbent pad and the flow guide component, and the first branch flow channel is vertically arranged below the first collecting channel, a detection test paper is arranged in each of the first branch flow channels, a first measuring positioning hole is arranged on the side of each of the first branch flow channels, and the first measuring positioning hole is located above the detection test paper, and the bottoms of the plurality of the first branch flow channels are connected to a first air pressure balance port; a first light response film is arranged outside the first branch flow channel; The chip body detects the plasma to obtain the test result, comprising: The plasma enters the first collecting channel through the flow guiding component; When the plasma reaches the junction of the first collecting channel and the first branch flow channel, the plasma flows into the first branch flow channel until it reaches the first measuring positioning hole; The plasma in the first collecting channel continues to flow forward to the first absorbent pad and no longer flows into the first branch flow channel, so that independent and quantitative plasma exists in the first branch flow channel; The first light-responsive film is irradiated with a preset light, so that the plasma in the first branch flow channel reacts with the test paper to obtain the test result.

4. The detection method of the microfluidic chip according to claim 1, characterized in that: The chip body includes a second collecting channel and a second branch channel, one end of the second collecting channel is connected to the flow guide component, the other end of the second collecting channel is provided with a second water absorbent pad, the second branch channel is connected to the second collecting channel, the second branch channel is located between the second water absorbent pad and the flow guide component, and the second branch channel is vertically arranged below the second collecting channel, the reaction chamber is arranged at the bottom of the second branch channel and is connected to the second branch channel, the reaction channel is connected to the reaction chamber, and the reaction channel is arranged in parallel with the second collecting channel, the bottom of the reaction channel is provided with a second measuring positioning hole, and the outside of the reaction channel is provided with a second light-responsive film; The chip body detects the plasma to obtain the test result, comprising: Printing the detection reagent in the reaction chamber by inkjet printing, and making the detection reagent into powder by freeze drying; or modifying the inner surface of the reaction chamber with antibodies to form the detection reagent; The plasma enters the second collecting channel through the flow guiding component; When the plasma reaches the junction of the second collecting channel and the second branch flow channel, the plasma flows into the second branch flow channel, fills the reaction chamber, and reaches the second measuring positioning hole; The plasma in the second collection channel continues to flow forward to the second water absorbent pad and no longer flows into the second branch flow channel, so that independent and quantitative plasma exists in the reaction chamber; The second light-responsive film is irradiated with a preset light, so that the plasma in the reaction chamber reacts with the detection reagent to obtain the detection result.

5. The detection method of the microfluidic chip according to claim 1, characterized in that: The flow guide component is a primary flow channel, and the chip body further includes a plurality of secondary flow channels and a plurality of tertiary flow channels, wherein the secondary flow channels correspond to the tertiary flow channels one by one, one end of the secondary flow channel is connected to the flow guide component, and the other end of the secondary flow channel is connected to the corresponding tertiary flow channel; a sample separation port is provided on the side of the secondary flow channel; The chip body detects the plasma to obtain the test result, comprising: After the plasma flows into the secondary flow channel through the primary flow channel, it enters the sample separation port; After the plasma enters the tertiary flow channel through the secondary flow channel, the tertiary flow channel absorbs all the plasma in the secondary flow channel; The plasma reacts with the detection reagent in the tertiary flow channel to obtain the detection result.

6. A plasma separation and flow guidance integrated microfluidic chip, characterized in that: include: A sample inlet, the sample inlet is used to receive a blood sample; a separation component, connected to the sample inlet, for separating plasma from the blood sample; A flow guide component, connected to the separation component; The chip body is communicated with the flow guide component, and the flow guide component is used to guide the separated plasma to the chip body.

7. The plasma separation and flow guidance integrated microfluidic chip according to claim 6, characterized in that: The flow guide assembly comprises: A microarray structure, connected to the separation component, the microarray structure having a plurality of pores, and the microarray structure is used to make the plasma flow along the pores by capillary action; A plurality of flow guiding channels, each of which is connected to the microarray structure and the chip body respectively, and the flow guiding channel is used to guide the plasma in the pores to the chip body.

8. The plasma separation and flow guidance integrated microfluidic chip according to claim 7, characterized in that: Each of the diversion channels is connected to the microarray structure through a corresponding collection hole, and the plasma enrichment area of ​​the microarray structure is made to be the location of the collection hole by adjusting the gaps between different areas of the microarray structure.

9. The plasma separation and flow guidance integrated microfluidic chip according to claim 8, characterized in that: The microarray structure is a tree-like structure, and the channel width of the tree-like structure gradually decreases from the trunk to the branch end close to the collection hole, so that the separated plasma is diverted to multiple parallel channels with smaller widths before reaching the collection hole.

10. The plasma separation and flow guidance integrated microfluidic chip according to claim 8, characterized in that: The microarray structure is a concentric ring structure, and the channel width of the concentric ring structure gradually decreases from the outer ring to the inner ring, so that the separated plasma gradually flows from the outer ring to the inner ring toward the collection hole.

11. The plasma separation and flow guiding integrated microfluidic chip according to claim 10, characterized in that: A plurality of inlets are evenly distributed on the circumference of the outer ring, so that the separated plasma can evenly flow into the outer ring through the plurality of inlets.

12. The plasma separation and flow guidance integrated microfluidic chip according to claim 10, characterized in that: The hydrophilicity of the material of the outer ring is greater than that of the material of the inner ring, and the inner wall of the concentric annular structure is provided with a flow-guiding texture.

13. The plasma separation and flow guidance integrated microfluidic chip according to claim 7, characterized in that: The channel width of the microarray structure in the Z-axis direction gradually narrows from top to bottom.

14. The plasma separation and flow guidance integrated microfluidic chip according to claim 6, characterized in that: The chip body has a plurality of microchannels, each of which is provided with a microfluidic valve, and the microfluidic valve is used to adjust the flow speed and direction of the plasma so that the plasma flows along the microchannel to the detection area.

15. The plasma separation and flow guidance integrated microfluidic chip according to claim 6, characterized in that: The chip body comprises: a first collecting channel, one end of which is in communication with the flow guide assembly, and the other end of which is provided with a first water absorbent pad; A plurality of first branch flow channels, each of which is connected to the first collecting channel, the first branch flow channels are located between the first water absorbent pad and the flow guide component, and the first branch flow channels are vertically arranged below the first collecting channel; Among them, a test paper is arranged in each of the first branch flow channels, a first measuring positioning hole is arranged on the side of each of the first branch flow channels, and the first measuring positioning hole is located above the test paper, and the bottoms of several of the first branch flow channels are connected to a first air pressure balance port; a first light response film is arranged on the outside of the first branch flow channel.

16. The plasma separation and flow guidance integrated microfluidic chip according to claim 6, characterized in that: The chip body comprises: a second collecting channel, one end of the second collecting channel being in communication with the flow guide assembly, and the other end of the second collecting channel being provided with a second water absorbent pad; a second branch flow channel, the second branch flow channel being in communication with the second collecting channel, the second branch flow channel being located between the second water absorbent pad and the flow guide assembly, and the second branch flow channel being vertically disposed below the second collecting channel; a reaction chamber, disposed at the bottom of the second branch flow channel and communicated with the second branch flow channel; The reaction channel is communicated with the reaction chamber and is arranged in parallel with the second collecting channel. A second measuring and positioning hole is arranged at the bottom of the reaction channel, and a second light-responsive film is arranged outside the reaction channel.

17. The plasma separation and flow guidance integrated microfluidic chip according to claim 6, characterized in that: The flow guide component is a primary flow channel, and the chip body also includes a plurality of secondary flow channels and a plurality of tertiary flow channels. The secondary flow channels correspond to the tertiary flow channels one by one, one end of the secondary flow channel is connected to the flow guide component, and the other end of the secondary flow channel is connected to the corresponding tertiary flow channel; a sample separation port is provided on the side of the secondary flow channel, and a quantitative measuring port is provided on the side of the tertiary flow channel.

18. The plasma separation and flow guidance integrated microfluidic chip according to claim 6, characterized in that: The separation component comprises a filter membrane, and the pore size of the filter membrane ranges from 0.2 μm to 5 μm.

19. The plasma separation and flow guidance integrated microfluidic chip according to claim 6, characterized in that: The microfluidic chip improves hydrophilicity by the following methods: Using benzophenone as a photosensitizer, and evenly coating the photosensitizer on the inner wall of the microfluidic chip; Filling the microfluidic chip with a methacryloyloxyethyl phosphorylcholine solution; Ultraviolet light is used to irradiate the inside of the microfluidic chip, so that the benzophenone and the polymerized monomers of the methacryloyloxyethyl phosphorylcholine solution undergo a bonding reaction, and a hydration layer is formed on the inner wall of the microfluidic chip.

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