Multi-detection dry biochemical assay chip (reagent kit) and its usage instructions

Abstract

This application discloses a multi-detection dry biochemical assay chip (reagent kit) and its usage method, belonging to the field of biochemical detection. The assay chip includes a handle assembly and a chip assembly connected to the handle assembly. This application features an inventive design for obtaining serum through blood pressure filtration and for the microchannels used for serum, ensuring smooth, rapid, and efficient blood pressure filtration and smooth flow of blood into the sequencing sites within the microchannels. In particular, the design of the filter element and the microchannels is noteworthy. The filter element adopts a two-stage structure, first coarse filtration and then fine filtration, improving the filtration effect and achieving the removal of most blood cells without centrifugation, thus obtaining serum and improving the accuracy of subsequent detection. It also facilitates smooth pressure filtration and improves efficiency. In addition, the microchannels take into account the viscosity of the serum, the length of the microchannels, the flow rate, the driving pressure, and the venting, ensuring smooth microflow of the serum, filling the sequencing sites, and fully reacting with the drying reagents, which is beneficial for subsequent optical detection and detection accuracy.

Description

Technical Field

[0001] This application relates to the field of biochemical detection technology, and more specifically, to a multi-detection dry biochemical detection chip (reagent kit) and its usage method. Background Technology

[0002] Existing technologies have problems such as large size of biochemical detection devices, large demand for blood testing, long testing time, high testing cost, and limitations in the location and environment of use of biochemical detection devices;

[0003] Currently, the demand for miniaturization and convenience in blood biochemistry testing is becoming increasingly prominent. The difficulty in miniaturizing and facilitating blood biochemistry testing lies in the high level of integration and innovation in testing methods and equipment. Summary of the Invention

[0004] This application provides a multi-detection dry biochemical detection chip (reagent kit) and its usage method, which can solve the increasingly prominent demand for miniaturization and convenience in blood biochemical detection. The difficulty in miniaturizing and facilitating blood biochemical detection lies in the technical problem of the high difficulty in integrating and innovating detection methods and detection equipment.

[0005] This application discloses a multi-detection dry biochemical detection chip (reagent kit), including a detection chip, the detection chip having a pressure filtration chamber, a sequence point, and a microchannel connecting the pressure filtration chamber to the sequence point; the pressure filtration chamber forms the sample inlet on the upper surface of the detection chip, and a small amount of blood is dripped into the pressure filtration chamber of the detection chip through the sample inlet;

[0006] The pressure filtration chamber within the detection chip contains a pressure filtration filter element for filtering blood cells to obtain serum; the sequence points include multiple detection points for optical transillumination; each detection point forms a detection point cavity within the detection chip; the detection point cavities are connected to the pressure filtration chamber through microchannels; and each sequence point contains a corresponding drying reagent within its corresponding detection point cavity.

[0007] The trace amount of blood is driven by the air pressure to filter and flow through the detection chip to the sequence point, while at the same time gradually squeezing out the air in the microchannels and detection point cavities of the detection chip, until the serum obtained by pressure filtration fills all the detection point cavities of the sequence point.

[0008] The detection chip is positioned in a planar manner that is both water-resistant and air-permeable, corresponding to the microchannels and the detection point cavity.

[0009] Air in the microchannels and detection point cavities of the detection chip is discharged along the plane of the detection chip, while the serum liquid is confined within the microchannels and detection point cavities.

[0010] The detection chip has at least 7 types, each corresponding to one of the 7 detection types: liver function test, kidney function test, viral infection test, glucose and lipid test, pancreatic test, renal glucose and lipid test, and myocardial test. Each detection type has multiple detection items, each detection item has at least one detection point, and each detection item has a corresponding drying reagent.

[0011] Preferably, the detection chip is provided with an identity module and a positioning module that works with the detection host. The identity module corresponds to the ID information of the detection chip. The ID information of the detection chip includes the type of the detection chip and the corresponding drying reagent information. The drying reagent information includes the type of drying reagent and the calibration curve.

[0012] Preferably, the detection chip includes a handle assembly and a chip assembly connected to the handle assembly;

[0013] The pressure filter chamber is disposed on the handle assembly, with the pressure filter chamber forming an inlet on the upper side of the handle assembly and a filter outlet on the lower side of the handle assembly;

[0014] Sequence points and microchannels are set on the chip assembly;

[0015] The chip assembly has a fixed end and a free end along its length;

[0016] The chip assembly is connected to the handle assembly near the fixed end;

[0017] The sequence points are located near the free end of the chip assembly.

[0018] Preferably, the microchannel includes at least one main channel and multiple branch channels; the branch channels are arranged one-to-one with the detection point cavities, the detection point cavities are connected to the main channel through the branch channels, the main channel is connected to the filter outlet of the filter press cavity, and the other end of the main channel is provided with a loading inlet, which extends to the outside of the chip assembly and abuts against the outlet of the filter press cavity.

[0019] Preferably, the filter element comprises a coarse filter element and a fine filter element arranged in sequence, wherein the average pore size of the coarse filter element is larger than the average pore size of the fine filter element; and the filtration path of the coarse filter element is much larger than that of the fine filter element.

[0020] Preferably, when the detection chip is working, the driving air pressure is set to P0 and the pressure difference is set to... Microfluidic driven differential pressure ;

[0021] ;

[0022] The filtered serum enters the microchannel directly, with a filtration flow rate of [missing information]. With microchannel flow rate 2 equal, set as the flow rate calculation ;

[0023] During micro-blood pressure filtration:

[0024] To calculate the flow rate, A is the cross-sectional area of ​​the filter cartridge. The permeability of the filter cartridge. For blood viscosity, The pressure difference is the pressure difference between the filter and the pressure vessel. The height of the filter element;

[0025] When obtaining serum microfluidics through filtration:

[0026] When the cross-section of the microchannel is circular; the diameter of the main flow section of the microchannel

[0027]

[0028] in, The diameter of the main flow section of the microchannel, 1 represents the viscosity of the serum; The length of the main segment; To calculate the flow rate, Microfluidic driving pressure difference;

[0029]

[0030] in, The diameter of the main flow section of the microchannel, 1 represents the viscosity of the serum; The length of the tributary section; To calculate the flow rate, Microfluidic pressure differential;

[0031] When the cross-section of the microchannel is rectangular;

[0032] The cross-section of the main flow section of the microchannel satisfies:

[0033]

[0034]

[0035] in, To calculate the flow rate, The width of the rectangular cross-section of the main section. The height of the rectangular cross-section of the main section; ≥ ; The width of the rectangular cross-section of the tributary section. The height of the rectangular cross-section of the tributary section; ≥ ; 1 represents the viscosity of the serum; The length of the main segment; This refers to the length of the tributary segment.

[0036] Preferably, the filter press chamber includes a pressure chamber and a filter chamber arranged sequentially from top to bottom;

[0037] The horizontal diameter of the pressure chamber gradually decreases from top to bottom, and a small-diameter filter hole is formed at the bottom of the pressure chamber; the filter hole is located inside the handle assembly near the chip assembly; the filter hole extends to the outside of the handle assembly to form a filter chamber; the pressure filter element is disposed inside the filter chamber;

[0038] The inner wall of the pressure chamber forms a pressure-inflow field pointing towards the filter chamber; the surface of the pressure-inflow field is hydrophobic, and the pressure-inflow field includes a first flow field and a second flow field arranged sequentially from top to bottom; the first flow field is a circular arc groove, and the second flow field is a conical groove; the second flow field is located on the side of the first flow field closer to the chip assembly; the streamline slope of the second flow field is greater than that of the first flow field;

[0039] The upper side of the handle assembly has a pressure-bearing surface; the pressure cavity opening is located in the middle of the pressure-bearing surface, and the pressure-bearing surface forms a stepped tubular interface corresponding to the pressure cavity opening, with an arc transition between the outer side of the tubular interface and the pressure-bearing surface.

[0040] Preferably, the chip assembly has at least a three-layer structure, the three-layer structure including upper and lower sealing layers and a middle microfluidic layer;

[0041] The microfluidic layer is breathable along its planar direction; microfluidic channels are formed on the upper side of the microfluidic layer corresponding to the microfluidic channels; the upper and lower face seals are attached to seal the upper and lower sides of the middle microfluidic layer to form microfluidic channels.

[0042] Preferably, it also includes accessories for packaging the detection chip;

[0043] The accessories include a sealing bag, a sealing sticker, and / or a packaging box; the sealing sticker seals the sample inlet and detection point of the filter press chamber on the detection chip;

[0044] The detection chip is embedded in a sealed bag and packed in a packaging box.

[0045] Another aspect of this application discloses a method for using a multi-detection dry biochemical detection chip (reagent kit), characterized by including step one, obtaining the detection chip, and adding a small amount of blood through the sample inlet of the detection chip;

[0046] Step 2: The detection chip works with the detection host. The detection host identifies the detection chip. After completion, air pressure is generated at the sample inlet of the detection chip to push the small amount of blood added in the filter chamber out of the outlet and into the microchannel. The blood then enters the microchannel and is distributed into the detection point chambers corresponding to multiple detection points, where it can fully react with the drying reagent.

[0047] Step 3: The testing host performs optical inspection on multiple testing points on the testing chip to obtain optical joint inspection information, and analyzes and calculates the test results based on the optical joint inspection information.

[0048] The beneficial effects of the technical solution provided in this application are:

[0049] This application creatively designs a detection chip for blood biochemistry testing. It achieves multi-stage dry biochemistry testing without centrifugation and filtration. The application designs a handle assembly and a filtration chamber on the handle assembly. Air pressure is generated at the sample inlet of the filtration chamber, propelling a trace amount of blood added to the detection chip through the filtration chamber for filtration. The filtered serum enters the microchannels of the chip assembly connected to the handle assembly, and then flows through the microchannels to the sequence sites, reacting with the drying reagents built into those sites. This application creatively designs the blood filtration process for obtaining serum and the microchannels used for serum filtration, ensuring smooth, rapid, and efficient blood filtration. The design of the filter element and microchannels ensures smooth flow into the sequencing sites. The filter element employs a two-stage structure, first coarse filtration and then fine filtration, improving filtration efficiency and removing most blood cells without centrifugation, resulting in relatively pure serum. This improves the accuracy of subsequent detection and facilitates smooth pressure filtration, increasing efficiency. Furthermore, the microchannel design considers serum viscosity, microchannel length, flow rate, driving pressure, and venting, ensuring smooth microflow of serum, filling the sequencing sites, and fully reacting with the drying reagent, which is beneficial for subsequent optical detection and accuracy. Attached Figure Description

[0050] To more clearly illustrate the technical solutions in the embodiments of this application, the accompanying drawings used in the description of the embodiments of this application will be briefly introduced below. Obviously, the accompanying drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0051] Figure 1 A schematic diagram of a detection chip disclosed in an exemplary embodiment of this application;

[0052] Figure 2 This is a schematic diagram illustrating the operation of the detection chip and the detection host in conjunction with an exemplary embodiment of this application.

[0053] Figure 3This is an exploded view of the detection chip disclosed in an exemplary embodiment of this application;

[0054] Figure 4 This is an exploded view of the handle assembly in the detection chip disclosed in an exemplary embodiment of this application;

[0055] Figure 5 This is a schematic diagram of the internal structure of the handle assembly in the detection chip disclosed in an exemplary embodiment of this application;

[0056] Figure 6 This is a planar schematic diagram of the handle assembly in the detection chip disclosed in an exemplary embodiment of this application;

[0057] Figure 7 This is a schematic diagram of the structure of a filter element disclosed in an exemplary embodiment of this application;

[0058] Figure 8 This is a planar schematic diagram of the chip components in the detection chip disclosed in an exemplary embodiment of this application;

[0059] Figure 9 This is a planar schematic diagram of the microchannels in the detection chip disclosed in an exemplary embodiment of this application;

[0060] Figure 10 This is a cross-sectional schematic diagram of the microchannels in the detection chip disclosed in an exemplary embodiment of this application;

[0061] Figure 11 An exemplary physical front perspective view of the detection chip disclosed in an exemplary embodiment of this application;

[0062] Figure 12 An exemplary physical reverse perspective view of the detection chip disclosed in an exemplary embodiment of this application;

[0063] Figure 13 An exemplary exploded view of the detection chip disclosed in this application as an exemplary embodiment;

[0064] Figure 14 An exemplary physical side view of the detection chip disclosed in an exemplary embodiment of this application;

[0065] Figure 15 An exemplary physical exploded side view of the detection chip disclosed in an exemplary embodiment of this application. Detailed Implementation

[0066] The embodiments of this application are described in detail below. Examples of these embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain this application, and should not be construed as limiting this application.

[0067] Those skilled in the art will understand that, unless specifically stated otherwise, the singular forms “a,” “an,” “the,” and “the” used herein may also include the plural forms. It should be further understood that the term “comprising” as used in this disclosure means the presence of the stated features, integers, steps, operations, elements, and / or components, but does not exclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and / or groups thereof. It should be understood that when we say an element is “connected” or “coupled” to another element, it can be directly connected or coupled to the other element, or there may be intermediate elements. Furthermore, “connected” or “coupled” as used herein can include wireless connections or wireless coupling. The term “and / or” as used herein includes all or any units and all combinations of one or more associated listed items.

[0068] To make the objectives, technical solutions, and advantages of this application clearer, the embodiments of this application will be described in further detail below with reference to the accompanying drawings:

[0069] Please refer to 1 to Figure 15 An exemplary embodiment of this application provides a multi-detection dry biochemical detection chip (reagent kit), including a detection chip 200, which cooperates with a detection host 100;

[0070] The detection chip 200 has a pressure filtration chamber 202, a sequence point 203, and a microchannel 204 connecting the pressure filtration chamber 202 to the sequence point 203; the pressure filtration chamber 202 forms the sample inlet 201 on the upper surface of the detection chip 200, and a small amount of blood 300 is dripped into the pressure filtration chamber 202 of the detection chip 200 through the sample inlet 201.

[0071] The pressure filtration chamber 202 has a pressure filtration filter element 400 within the detection chip 200 for filtering blood cells to obtain serum 301; the sequence point 203 includes multiple detection points B for optical transillumination; each detection point B forms a detection point cavity 205 within the detection chip 200; the detection point cavity 205 is connected to the pressure filtration chamber 202 through a microchannel 204; and each sequence point 203 contains a corresponding drying reagent 206 within its corresponding detection point cavity 205.

[0072] The trace blood 300 is pushed by the driving air pressure 1000 generated by the detection host 100 to filter and flow through the detection chip 200 to the sequence point 203, and at the same time, the air 2000 in the microchannel 204 and the detection point cavity 205 in the detection chip 200 is gradually squeezed out until the serum 301 obtained by pressure filtration fills all the detection point cavities 205 of the sequence point 203.

[0073] The detection chip 200 is positioned in a planar location corresponding to the microchannel 204 and the detection point cavity 205, which is water-resistant and air-permeable.

[0074] Air 2000 in the microchannel 204 and detection point cavity 205 of the detection chip 200 is discharged along the plane of the detection chip 200, and the serum 301 liquid is confined in the microchannel 204 and detection point cavity 205.

[0075] In an exemplary embodiment, the detection chip 200 has at least 7 types, each of which corresponds to a different detection type. The 7 detection types are liver function detection, kidney function detection, viral infection detection, glucose and lipid detection, pancreatic detection, renal glucose and lipid detection, and myocardial detection. Each detection type has multiple detection items, and each detection item has at least one detection point B and a corresponding drying reagent 206.

[0076] In an exemplary embodiment, the detection chip 200 is provided with an identity module 20 and a positioning module DW that cooperates with the detection host 100. The identity module 20 corresponds to the ID information of the detection chip 200. The ID information of the detection chip 200 includes the type of the detection chip 200 and the corresponding drying reagent information. The drying reagent information includes the type of drying reagent 206 and the calibration curve.

[0077] In one exemplary embodiment, the detection chip 200 includes a handle assembly 21 and a chip assembly 22 connected to the handle assembly 21;

[0078] In an exemplary embodiment, the handle assembly 21 has a strip-shaped structure and has a handheld end 211 and a working end 212 along its length.

[0079] The handle assembly 21 has a hand-holding part 2111 on the side near the hand-holding end 211; the upper side of the hand-holding part 2111 has a hand-holding anti-slip area 2112, which is circular and has anti-slip texture.

[0080] The handheld part 2111 has an identity module 20 on its lower side; the detection host 300 obtains the detection target information of the detection chip 200 by detecting the identity module 20, which facilitates subsequent matching detection; in an exemplary embodiment, the identity module 20 is a QR code;

[0081] In an exemplary embodiment, the pressure filter chamber 202 is disposed on the handle assembly 21, the pressure filter chamber 202 forms an inlet 201 on the upper side of the handle assembly 21, and the pressure filter chamber 202 forms a filter outlet 2020 on the lower side of the handle assembly 21.

[0082] In an exemplary embodiment, the upper side of the handle assembly 21 has a pressure-bearing surface 210; the sample inlet 201 is located on the pressure-bearing surface 210, and the pressure-bearing surface 210 forms a stepped tubular interface 2011 corresponding to the sample inlet 201, with an arc transition between the outer side of the tubular interface 2011 and the pressure-bearing surface 210.

[0083] In an exemplary embodiment, the elastic pressure cup 600 is connected to the tubular interface 2011. The elastic pressure cup is driven by the detection host 100 to elastically deform and wrap around and squeeze the sample inlet 201 of the filter chamber, generating a driving air pressure 1000.

[0084] In an exemplary embodiment, the pressure filter chamber 202 includes a pressure chamber 2021 and a filter chamber 2022 arranged sequentially from top to bottom;

[0085] The horizontal diameter r0 of the pressure chamber 2021 gradually decreases from top to bottom, and a small-diameter filter hole GLK is formed at the bottom of the pressure chamber 2021; the filter hole GLK is located inside the handle assembly 21 on the side close to the chip assembly 22; the filter hole GLK extends to the outside of the handle assembly 21 to form a filter chamber GLQ; the pressure filter element 400 is disposed inside the filter chamber GLQ.

[0086] The inner wall of the pressure chamber 2021 forms a pressure-inflow field YLC pointing towards the filter chamber GLQ; the surface of the pressure-inflow field YLC is hydrophobic, and the pressure-inflow field YLC includes a first flow field LC1 and a second flow field LC2 arranged sequentially from top to bottom; the first flow field LC1 is a circular arc groove, and the second flow field LC2 is a conical groove; the second flow field LC2 is located inside the first flow field LC1 on the side closer to the chip assembly 22; the streamline slope of the second flow field LC2 is greater than the streamline slope of the first flow field;

[0087] The pressure flow field YLC has a scraping flange 2022; the scraping flange 2022 is located at the connection between the first flow field LC1 and the second flow field LC2, the scraping flange 2022 is arc-shaped shell, and the arc opening faces the filter cavity GLQ, which facilitates scraping a small amount of blood 300.

[0088] In one exemplary embodiment, the indented flow field YLC is an inner conical surface; the indented flow field YLC can also be an inner spherical surface.

[0089] The filter chamber GLQ forms a filter outlet 2020 at the bottom of the handle assembly 21;

[0090] In one exemplary embodiment, the filter aperture GLK is circular or elliptical; the central axis of the filter cavity GLQ vertically penetrates the handle assembly 21;

[0091] In one exemplary embodiment, the central axis of the filter chamber GLQ can obliquely penetrate the handle assembly 21, and the central axis of the filter chamber GLQ has an angle with the vertical direction; in one exemplary embodiment, the angle is 30 degrees.

[0092] The pore size of the filter chamber GLQ is the same from top to bottom; in some embodiments, the pore size of the filter chamber GLQ can gradually decrease from top to bottom, which is beneficial for concentrated filtration and improves the filtration effect.

[0093] In an exemplary embodiment, the filter element 400 includes a coarse filter element 401 and a fine filter element 402 arranged sequentially. The average pore size of the coarse filter element 401 is larger than the average pore size of the fine filter element 402. The coarse filtration path 4011 of the coarse filter element 401 is much larger than the fine filtration path 4021 of the fine filter element 402.

[0094] In an exemplary embodiment, the coarse filter element 401 has a columnar structure that cooperates with the filter chamber GLQ. The coarse filter element 401 is built into the filter chamber GLQ and is interference-fitted with the filter chamber GLQ.

[0095] In one exemplary embodiment, the filter chamber GLQ is provided with a limiting flange for engaging and fixing the coarse filter element 401; in some embodiments, the limiting flange may be arranged in a spiral shape on the inner wall of the filter chamber GLQ.

[0096] In an exemplary embodiment, the fine filter element 402 is in the shape of a disc, one end of the fine filter element 402 is embedded in the filter chamber GLQ and connected to the coarse filter element 401; the other end of the fine filter element 402 is fixed to the side of the handle assembly 21 corresponding to the filter outlet 2020 by the filter element fixing part 403.

[0097] In an exemplary embodiment, the filter element fixing part 403 is a fixing patch that attaches the fine filter element 402 to the filter outlet 2020;

[0098] In an exemplary embodiment, the pore size of the coarse filter element 401 follows a normal distribution N(d1,σ12), where d1 is the average pore size of the coarse filter element 401 and σ1 is the standard deviation of the pore size of the coarse filter element 401; d1 is 7um-10um; σ1 is 1um-2um.

[0099] The porosity of the coarse filter element 401 is 0.5-0.7;

[0100] The pore size of the fine filter element 402 follows a normal distribution N(d2,σ22), where μ2 is the average pore size of the fine filter element 402, σ2 is the standard deviation of the pore size of the fine filter element 402, and d2 is 5um-7um.

[0101] σ2 is 0.5um-1um; the porosity of the 402 fine filter element is 0.3-0.5;

[0102] Sequence point 203 and microchannel 204 are disposed on chip assembly 22;

[0103] The chip assembly 22 has a fixed end 221 and a free end 222 along its length;

[0104] Chip assembly 22 is connected to handle assembly 21 near fixed end 221;

[0105] The sequence point 203 is located on the chip assembly 22 near the free end 222.

[0106] The sequence point 203 is composed of multiple detection points B; each detection point B in the chip assembly 22 is provided with a detection point cavity 205;

[0107] The arrangement of the detection points is not limited;

[0108] In one exemplary embodiment, the detection points B are arranged in a straight line;

[0109] In one exemplary embodiment, the detection points B are arranged in a straight line at uniform intervals;

[0110] In one exemplary embodiment, the detection points B are arranged in a straight line with non-uniform intervals;

[0111] In one exemplary embodiment, the detection points B are arranged in an arc-shaped curve;

[0112] In an exemplary embodiment, the detection points B are arranged at uniform intervals in an arc-shaped curve;

[0113] In one exemplary embodiment, the detection points B are arranged in an arc-shaped curve with non-uniform intervals;

[0114] Chip assembly 22 is connected to handle assembly 21 near fixed end 221;

[0115] In an exemplary embodiment, the positioning module DW includes a positioning limiting protrusion DW1, which is a triangular protrusion; this facilitates positioning and limiting.

[0116] In an exemplary embodiment, the positioning module DW includes a positioning groove DW2, which is a semi-circular groove disposed on the free end 222 of the chip assembly 22. The detection host has a positioning protrusion that cooperates with the positioning groove on the corresponding detection chip. The positioning protrusion is cylindrical. There are two positioning grooves and two positioning protrusions, which are asymmetrically designed to indicate that the sample inlet of the detection chip is inserted and fitted upwards.

[0117] In an exemplary embodiment, the bottom of the working end 212 of the handle assembly 21 is provided with a stepped opening TJK; the filter outlet 2020 of the filter chamber 202 is located on the stepped opening TJK; the stepped opening TJK facilitates the positioning and installation of the chip assembly 22; the filter element fixing part 403 and the chip assembly 22 are sequentially attached to the stepped opening TJK; the microchannel 204 is provided with a loading inlet ZRK on one side of the chip assembly, and the loading inlet ZRK is connected to the filter outlet 2020; the fixing patch is provided with a filter element through hole 4031, and the filter element through hole 4031 connects the filter outlet 2020 and the loading inlet ZRK; the fine filter element 402 is located between the loading inlet ZRK and the filter outlet 2020;

[0118] In an exemplary embodiment, the chip assembly 22 has at least a three-layer structure, the three-layer structure including upper and lower sealing layers MC and a middle microfluidic layer ZC;

[0119] The microfluidic layer ZC is breathable along its planar direction; a microfluidic channel is formed on the upper side of the microfluidic layer ZC corresponding to the microfluidic channel 204; the two face seal layers MC are bonded together to seal the upper and lower sides of the middle microfluidic layer ZC to form the microfluidic channel 204.

[0120] The microchannel 204 includes at least one main channel 2041 and multiple branch channels 2042; the branch channels 2042 are configured one-to-one with the detection point cavities 205, and the detection point cavities 205 are connected to one end of the main channel 2041 through the branch channels 2042; the loading inlet ZRK is connected to the other end of the main channel 2041.

[0121] In an exemplary embodiment, the detection host 100 has a first detection positioning point B0 corresponding to the sequence point 203 of the detection chip 200, and the detection light in the first detection positioning point B0 can penetrate the chip assembly without obstruction; the sequence point 203 includes M detection points B from B1 to BM; in an exemplary embodiment, M is 9.

[0122] The first detection positioning point B0 is set outside the detection chip 200 or on the detection chip 200;

[0123] In one exemplary embodiment, when the detection chip is operating, the pressure of the driving air pressure is set to... Filter pressure differential Microfluidic driven differential pressure ;

[0124] ;

[0125] The filtered serum enters the microchannel directly, with a filtration flow rate of [missing information]. With microchannel flow rate Equal, set as the calculation flow ;

[0126] During micro-blood pressure filtration:

[0127] To calculate the flow rate, This refers to the cross-sectional area of ​​the filter cartridge. The permeability of the filter cartridge. For blood viscosity, The pressure difference is the pressure difference between the filter and the pressure vessel. The height of the filter element;

[0128] When obtaining serum microfluidics through filtration:

[0129] When the cross-section of the microchannel is circular; the diameter of the main flow section of the microchannel

[0130]

[0131] in, The diameter of the main flow section of the microchannel, The viscosity of the serum; The length of the main segment; To calculate the flow rate, Microfluidic driving pressure difference;

[0132]

[0133] in, The diameter of the main flow section of the microchannel, The viscosity of the serum; The length of the tributary section; To calculate the flow rate, Microfluidic pressure differential;

[0134] When the cross-section of the microchannel is rectangular;

[0135] The cross-section of the main flow section of the microchannel satisfies:

[0136]

[0137]

[0138] in, To calculate the flow rate, The width of the rectangular cross-section of the main section. The height of the rectangular cross-section of the main section; ≥ ; The width of the rectangular cross-section of the tributary section. The height of the rectangular cross-section of the tributary section; ≥ ; The viscosity of the serum; The length of the main segment; This refers to the length of the tributary segment.

[0139] Exemplary embodiments disclosed in this application also include an accessory for packaging the detection chip 200;

[0140] The accessories include a sealing bag, a sealing sticker, and / or a packaging box; the sealing sticker seals the sample inlet 201 and the detection point B on the detection chip 200.

[0141] The detection chip 200 is embedded in a sealed bag and packed in a packaging box.

[0142] An exemplary embodiment of this application discloses a method for using a multi-detection dry biochemical detection chip (reagent kit), characterized by including step one: obtaining the detection chip and adding a small amount of blood through the sample inlet of the detection chip;

[0143] Step 2: The detection chip works with the detection host. The detection host identifies the detection chip. After completion, air pressure is generated at the sample inlet of the detection chip to push the small amount of blood added in the filter chamber out of the outlet and into the microchannel. The blood then enters the microchannel and is distributed into the detection point chambers corresponding to multiple detection points, where it can fully react with the drying reagent.

[0144] Step 3: The testing host performs optical inspection on multiple testing points on the testing chip to obtain optical joint inspection information, and analyzes and calculates the test results based on the optical joint inspection information.

Claims

1. A multi-detector dry biochemical detection chip, characterized in that, The detection chip has a pressure filtration chamber, a sequence point, and a microchannel connecting the pressure filtration chamber to the sequence point; the pressure filtration chamber forms an inlet on the upper surface of the detection chip, and a small amount of blood is dripped into the pressure filtration chamber of the detection chip through the inlet; The pressure filtration chamber within the detection chip contains a pressure filtration filter element for filtering blood cells to obtain serum; the sequence points include multiple detection points for optical transillumination; The detection point is formed in the detection chip by a detection point cavity; The detection point cavities are connected to the pressure filtration cavities one-to-one via microchannels; each sequence point is equipped with a corresponding drying reagent in its corresponding detection point cavity. The trace amount of blood is driven by the air pressure to filter and flow through the detection chip to the sequence point, while at the same time gradually squeezing out the air in the microchannels and detection point cavities of the detection chip, until the serum obtained by pressure filtration fills all the detection point cavities of the sequence point. The microchannel includes at least one main channel and multiple tributary channels. When the detection chip is working, the driving air pressure is set to P0, the pressure difference of the filter press is P1, and the microflow driving pressure difference is P2. P1+P2=P0 (1); The filtered serum is directly fed into the microchannel. The flow rate of the filter press, Q1, is equal to the flow rate of the microchannel, Q2, and is set as the calculated flow rate Q. During micro-blood pressure filtration: Q is the calculated flow rate, A is the cross-sectional area of ​​the filter cartridge, k is the permeability of the filter cartridge, μ0 is the blood viscosity, P1 is the pressure difference of the filter cartridge, and H is the height of the filter cartridge. When obtaining serum microfluidics through filtration: When the cross-section of the microchannel is circular, the diameter of the main flow section of the microchannel is... Where R1 is the diameter of the main flow section of the microchannel, μ1 is the viscosity of the serum, L1 is the length of the main flow section, Q is the calculated flow rate, and P2 is the microfluidic driving pressure difference. Where R2 is the diameter of the microfluidic tributary, μ1 is the viscosity of the serum, L2 is the length of the tributary, Q is the calculated flow rate, and P2 is the microfluidic driving pressure difference. When the cross-section of the microchannel is rectangular, The cross-section of the main flow section of the microchannel satisfies: Where Q is the calculated flow rate, w1 is the width of the rectangular cross-section of the main stream, h1 is the height of the rectangular cross-section of the main stream (w1≥h1), w2 is the width of the rectangular cross-section of the tributary (w2≥h2), μ1 is the viscosity of the serum, L1 is the length of the main stream, and L2 is the length of the tributary.

2. The multi-detection dry biochemical detection chip according to claim 1, characterized in that, The detection chip is water-resistant and air-permeable in the planar position corresponding to the microchannels and detection point cavities. Air in the microchannels and detection point cavities of the detection chip is discharged along the planar direction of the detection chip, and the serum fluid is confined within the microchannels and detection point cavities. The detection chip has at least 7 types, each corresponding to a different detection type. The 7 detection types are liver function detection, kidney function detection, viral infection detection, glucose and lipid detection, pancreatic detection, renal glucose and lipid detection, and myocardial detection. Each detection type has multiple detection items, and each detection item has at least one detection point and a corresponding drying reagent. The detection chip is equipped with an identity module and a positioning module that works with the detection host. The identity module corresponds to the ID information of the detection chip, which includes the type of detection chip and the corresponding drying reagent information, including the type of drying reagent.

3. The multi-detection dry biochemical detection chip according to claim 2, characterized in that, The detection chip includes a handle assembly and a chip assembly connected to the handle assembly; the pressure filtration chamber is disposed on the handle assembly, forming an inlet on the upper side of the handle assembly and a outlet on the lower side of the handle assembly; sequence points and microchannels are disposed on the chip assembly; the chip assembly has a fixed end and a free end along its length; the handle assembly is connected to the chip assembly near the fixed end; the sequence points are disposed on the chip assembly near the free end.

4. The multi-detection dry biochemical detection chip according to claim 3, characterized in that, The tributary section is set up one-to-one with the detection point cavity. The detection point cavity is connected to the main flow section one-to-one through the tributary section. The main flow section is connected to the filter outlet of the filter press cavity. The other end of the main flow section in the microchannel is provided with a loading inlet. The loading inlet extends to the outside of the chip assembly and abuts against the filter outlet.

5. The multi-detection dry biochemical detection chip according to claim 3, characterized in that, The filter cartridge includes a coarse filter cartridge and a fine filter cartridge arranged in sequence. The average pore size of the coarse filter cartridge is larger than that of the fine filter cartridge. The filtration path of the coarse filter cartridge is much larger than that of the fine filter cartridge.

6. The multi-detection dry biochemical detection chip according to claim 3, characterized in that, The pressure filter chamber includes a pressure chamber and a filter chamber arranged sequentially from top to bottom; the horizontal diameter of the pressure chamber gradually decreases from top to bottom, and a small-diameter filter hole is formed at the bottom of the pressure chamber; the filter hole is located inside the handle assembly near the chip assembly; the filter hole extends to the outside of the handle assembly to form a filter chamber; the pressure filter element is disposed inside the filter chamber; the inner wall of the pressure chamber forms a pressure-inflow field pointing towards the filter chamber; the surface of the pressure-inflow field is hydrophobic, and the pressure-inflow field includes a first flow field and a second flow field arranged sequentially from top to bottom; the first flow field is a circular arc groove, and the second flow field is a conical groove; the second flow field is located inside the first flow field near the chip assembly; the streamline slope of the second flow field is greater than the streamline slope of the first flow field; the upper side of the handle assembly has a pressure-bearing surface; the pressure chamber opening of the pressure chamber is located in the middle of the pressure-bearing surface, and the pressure-bearing surface forms a stepped tubular interface corresponding to the pressure chamber opening, with an arc transition between the outer side of the tubular interface and the pressure-bearing surface.

7. The multi-detection dry biochemical detection chip according to claim 3, characterized in that, The chip assembly has at least three layers, including upper and lower sealing layers and a middle microfluidic layer; the microfluidic layer is breathable along its planar direction; microfluidic channels are formed on the upper side of the microfluidic layer corresponding to the microfluidic channels; the upper and lower sealing layers are bonded to seal the upper and lower sides of the middle microfluidic layer to form microfluidic channels.

8. A multi-detection dry biochemical assay kit, the kit comprising the multi-detection dry biochemical assay chip according to any one of claims 1-7, characterized in that, The kit also includes accessories for packaging the detection chip; the accessories include a sealing bag, a sealing sticker, and a packaging box; the sealing sticker seals the inlet of the filter chamber and the detection point on the detection chip; the detection chip is housed in the sealing bag and packed in the packaging box.

9. A method of using the multi-detection dry biochemical detection chip according to any one of claims 1-7, characterized in that, The process includes: Step 1, acquiring the detection chip and adding a small amount of blood through the sample inlet of the detection chip; Step 2, the detection chip and the detection host cooperate, the detection host identifies the detection chip, and after completion, air pressure is generated at the sample inlet of the detection chip to push the small amount of blood added in the pressure filtration chamber to be filtered out from the outlet and enter the microchannel, and then enter the detection point chambers corresponding to multiple detection points through the microchannel, so as to fully react with the drying reagent; Step 3: The testing host performs optical inspection on multiple testing points on the testing chip to obtain optical joint inspection information, and analyzes and calculates the test results based on the optical joint inspection information.

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