Micro-fluidic chip, instant detection system and detection control method

Abstract

The invention relates to a micro-fluidic chip, a real-time detection system and a detection control method. The micro-fluidic chip comprises a chip unit, wherein the chip unit can rotate around a rotation center; the chip unit comprises a sample adding part which is arranged at the position, close to the rotating center, of the chip unit and is used for placing and accommodating a sample to be detected; the detection part is arranged at the position, far away from the rotating center, of the chip unit and is communicated with the sample adding part; wherein the detection part comprises a first detection hole and a second detection hole, the first detection hole is used for accommodating a reaction reagent group, the second detection hole is used for accommodating a photosensitive microsphere, and the first detection hole and the second detection hole are connected through a transition part. According to the scheme provided by the invention, the structural design of the micro-fluidic chip can be simplified, and the detection cost can be reduced.

Description

Technical Field

[0001] The present application relates to the field of in vitro diagnostic technology, and in particular to a microfluidic chip, a point-of-care detection system, and a detection control method. Background Art

[0002] Microfluidics, also known as lab-on-chip, is a technology that enables the manipulation of fluids at the micrometer scale. As an analytical platform with low sample consumption, rapid analysis speed, and high sensitivity, microfluidics holds enormous potential in point-of-care diagnostics (POCT).

[0003] In related technologies, POCT quantitative detection is generally a lateral flow method or a chromatographic flow method, which is affected by the flow time of the sample, that is, it is not affected by slight differences in sample properties such as viscosity, microfluidic channels or NC membrane heterogeneity, and the process of removing free markers needs to be considered, which makes the design of microfluidic chips more difficult, the structure more complex, and the cost higher. Summary of the Invention

[0004] In order to solve or partially solve the problems existing in the related art, the present application provides a microfluidic chip, an instant detection system and a detection control method, which can simplify the structural design of the microfluidic chip and reduce the detection cost.

[0005] The first aspect of the present application provides a microfluidic chip, comprising:

[0006] A chip unit, wherein the chip unit is rotatable around a rotation center;

[0007] The chip unit includes:

[0008] A sample loading portion, provided on the chip unit near the rotation center, for placing and accommodating samples to be tested;

[0009] a detection unit, disposed at a position of the chip unit away from the rotation center and connected to the sample adding unit;

[0010] Among them, the detection part includes a first detection hole (T hole) and a second detection hole (G hole), the first detection hole is used to accommodate the reaction reagent group, the second detection hole is used to accommodate photosensitive microspheres, and the first detection hole and the second detection hole are connected by a transition part.

[0011] In some embodiments, the second detection hole is taller than the first detection hole in the thickness direction of the chip unit.

[0012] In some embodiments, the transition portion is a first inclined structure, the lower end of the first inclined structure is connected to the first detection hole, and the upper end is connected to the first detection hole; and / or

[0013] The bottom of the second detection hole is a second inclined structure, and the lower end of the second inclined structure is connected to the upper end of the first inclined structure.

[0014] In some embodiments, the first detection hole is located on one side of the second detection hole in a clockwise rotation direction of the chip unit.

[0015] In some embodiments, the first detection hole and the second detection hole are located on the same circular track, and the center of the circular track coincides with the rotation axis of the chip unit.

[0016] In some embodiments, the first detection holes and the second detection holes are provided in multiple groups, and the multiple groups of the first detection holes and the second detection holes are arranged in sequence in the rotation direction of the chip unit.

[0017] In some embodiments, a whole blood separation structure is further included, wherein the whole blood separation structure includes a plasma placement tank, a plasma quantitative tank, and a blood cell storage tank sequentially connected by a plasma flow channel; or

[0018] The dilution structure includes a diluent placement tank and a diluent quantitative tank connected by a dilution flow channel; the chip unit is also provided with a mixing tank, which is connected to the blood cell storage tank and the diluent quantitative tank.

[0019] In some embodiments, the chip unit is further provided with a sample distribution groove, the sample distribution groove is provided between the mixing groove and the detection portion, and the sample distribution groove extends in the arrangement direction of the multiple groups of first detection holes and the second detection holes;

[0020] The sample distribution slot has a fluid inlet and a plurality of fluid outlets, wherein the fluid inlet is communicated with the mixing slot, and the plurality of fluid outlets are respectively communicated with the first detection holes in each group.

[0021] In some embodiments, the chip unit is provided in plurality, and the plurality of chip units are arranged in sequence in the circumferential direction of the rotation center.

[0022] In some embodiments, the chip unit is made of an opaque material;

[0023] The chip unit is covered with a first film and a second film, wherein the first film is a transparent film and the second film is a non-transparent film; the second film is provided with a light-transmitting hole corresponding to the first detection hole.

[0024] A second aspect of the present application provides an instant detection system, comprising:

[0025] The microfluidic chip as described in the first aspect above; and

[0026] The detection device cooperates with the detection part of the microfluidic chip to detect the sample.

[0027] The third aspect of the present application provides a detection and control method for a microfluidic chip,

[0028] The method comprises:

[0029] Controlling the chip unit to rotate along a first rotation direction with a first rotation parameter so as to separate the substance to be detected from the sample in the sample adding portion;

[0030] controlling the chip unit to rotate along the first rotation direction at a second rotation parameter to mix the substance to be detected with the diluent;

[0031] Controlling the chip unit to rotate along the first rotation direction at a third rotation parameter so that the mixture of the sample to be tested and the diluent is distributed to the first testing hole;

[0032] The chip unit is controlled to rotate along a second rotation direction with a fourth rotation parameter, so that the sample with the reaction reagent set in the first detection hole flows into the second detection hole along the transition portion.

[0033] In one embodiment, controlling the chip unit to rotate along the first rotation direction with a third rotation parameter so that the mixture of the sample to be tested and the diluent is distributed to the first testing hole includes:

[0034] Controlling the rotation speed of the chip unit to gradually decrease until it stops; or,

[0035] After controlling the chip unit to rotate along the second rotation direction with a fourth rotation parameter so that the mixed liquid containing the reaction reagent set in the first detection hole flows along the transition portion into the second detection hole, the method includes:

[0036] The chip unit is controlled to stop rotating, so that the mixed liquid with the photosensitive microspheres in the second detection hole flows along the transition portion into the first detection hole.

[0037] The technical solution provided by this application may have the following beneficial effects:

[0038] The microfluidic control chip provided in the present application includes a chip unit, which can rotate around a rotation center; the chip unit includes: a sample loading part, which is arranged at the chip unit near the rotation center and is used to place and accommodate the sample to be detected; a detection part, which is arranged at the chip unit away from the rotation center and is connected to the sample loading part; wherein, the detection part includes a first detection hole and a second detection hole, the first detection hole is used to accommodate a reaction reagent group, and the second detection hole is used to accommodate photosensitive microspheres, and the first detection hole and the second detection hole are connected by a transition part. In this way, when the chip unit rotates, the sample can be accurately distributed to the first detection hole. At the same time, the sample can circulate between the first detection hole and the second detection hole, and then the sample is mixed with the reaction reagent group and the photosensitive microspheres under the action of inertia, so that the mixed liquid meets the detection conditions, which can simplify the structural design of the microfluidic chip and reduce the detection cost.

[0039] It should be understood that the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the present application. BRIEF DESCRIPTION OF THE DRAWINGS

[0040] The above and other objects, features and advantages of the present application will become more apparent by describing in more detail exemplary embodiments of the present application in conjunction with the accompanying drawings, wherein the same reference numerals generally represent the same components in the exemplary embodiments of the present application.

[0041] Figure 1 Schematic diagram of the structure of the microfluidic chip shown in the embodiment of the present application;

[0042] Figure 2 Schematic diagram of the structure of the chip unit of the microfluidic chip shown in the embodiment of the present application;

[0043] Figure 3 Schematic diagram of the coordination of the first detection hole and the second detection hole of the microfluidic chip shown in the embodiment of the present application;

[0044] Figure 4 is a cross-sectional view of a microfluidic chip shown in an embodiment of the present application;

[0045] Figure 5 Schematic diagram of the internal structure of the microfluidic chip shown in the embodiment of the present application;

[0046] Figure 6 This is a top view of the microfluidic chip shown in the embodiment of the present application

[0047] Figure 7 Schematic diagram of the assembly of the microfluidic chip shown in the embodiment of the present application;

[0048] Figure 8It is a flow chart of the detection and control method of the microfluidic chip shown in the embodiment of the present application.

[0049] Figure numerals: 100, chip unit; 101, sample loading part; 111, plasma quantitative tank; 131, blood cell storage tank; 121, first exhaust hole; 102, detection part; 112, first detection hole; 122, second detection hole; 132, transition part; 103, diluent placement tank; 113, diluent quantitative tank; 104, mixing tank; 114, positioning hole; 105, distribution tank; 115, second exhaust hole; 200, first film; 201, sample loading hole; 202, liquid loading hole; 300, second film. DETAILED DESCRIPTION

[0050] The following describes embodiments of the present application in more detail with reference to the accompanying drawings. Although the accompanying drawings illustrate embodiments of the present application, it should be understood that the present application can be implemented in various forms and should not be limited by the embodiments described herein. Rather, these embodiments are provided to make the present application more thorough and complete, and to fully convey the scope of the present application to those skilled in the art.

[0051] The terms used in this application are for the purpose of describing specific embodiments only and are not intended to limit this application. As used in this application and the appended claims, the singular forms "a," "an," "the," and "the" are intended to include the plural forms, unless the context clearly indicates otherwise. It should also be understood that the term "and / or" as used herein refers to and encompasses any and all possible combinations of one or more of the associated listed items.

[0052] It should be understood that although the terms "first", "second", "third", etc. may be used in this application to describe various information, this information should not be limited to these terms. These terms are only used to distinguish information of the same type from each other. For example, without departing from the scope of this application, the first information may also be referred to as the second information, and similarly, the second information may also be referred to as the first information. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of the features. In the description of this application, the meaning of "plurality" is two or more, unless otherwise clearly and specifically defined.

[0053] In the related art, POCT quantitative detection is generally performed using lateral flow or chromatographic flow methods, which are affected by the flow time of the sample, that is, they are not affected by slight differences in sample properties such as viscosity, microfluidic tubing, or NC membrane heterogeneity. In addition, the process of removing free markers must be considered, which increases the difficulty of designing microfluidic chips, makes the structure complex, and increases the cost. To address the above problems, the embodiments of the present application provide a microfluidic chip and its detection control method, which can simplify the structural design of the microfluidic chip and reduce the detection cost.

[0054] Figure 1 Schematic diagram of the structure of the microfluidic chip shown in the embodiment of the present application; Figure 2 Schematic diagram of the structure of the chip unit of the microfluidic chip shown in the embodiment of the present application; Figure 3 Schematic diagram of the coordination of the first detection hole and the second detection hole of the microfluidic chip shown in the embodiment of the present application.

[0055] See also Figure 1-Figure 4 The microfluidic chip provided in the present application includes a chip unit 100, which can rotate around a rotation center. The chip unit 100 includes a sample loading part 101 and a detection part 102: the sample loading part 101 is arranged near the rotation center of the chip unit 100, and is used to accommodate and hold samples to be detected; the detection part 102 is arranged away from the rotation center of the chip unit 100, and is connected to the sample loading part 101; wherein, the detection part 102 includes a first detection hole 112 and a second detection hole 122, the first detection hole 112 is used to accommodate reaction reagent groups A and B, and the second detection hole 122 is used to accommodate photosensitive microspheres C, and the first detection hole 112 and the second detection hole 122 are connected by a transition part 132.

[0056] In this embodiment, the rotation plane of the chip unit 100 is perpendicular to the thickness direction of the chip unit 100, and the first detection hole 112 and the second detection hole 122 are opened along the thickness direction of the chip unit 100, or the depth of the first detection hole 112 is greater than the depth of the second detection hole 122. The first detection hole 112 has a set volume, for example, a volume of at least 250 μl. The reaction reagent groups A and B contained in the first detection hole 112 are respectively luminescent microspheres R1 (such as FG-Ab) and biotin markers R2 (such as Bio-Ab). The photosensitive microspheres C contained in the second detection hole 122 can be, for example, GG-SA. The reaction reagent groups R1 and R2 and the photosensitive microspheres are all in a freeze-dried state.

[0057] The microfluidic control chip provided in the present application has a detection portion 102 and a sample addition portion 101 that are connected, and the first detection hole 112 of the detection portion 102 is used to accommodate a reaction reagent group, and the second detection hole 122 is used to accommodate photosensitive microspheres. The first detection hole 112 and the second detection hole 122 are connected by a transition portion 132. In this way, when the chip unit 100 rotates, the sample can be accurately distributed into the first detection hole 112. At the same time, the sample can flow between the first detection hole 112 and the second detection hole 122, and then the sample is mixed with the reaction reagent group and the photosensitive microspheres under the action of inertia, so that the mixed liquid meets the detection conditions. This can simplify the structural design of the microfluidic chip and reduce the detection cost.

[0058] In this embodiment, the bottom of the second detection hole 122 is higher than the first detection hole 112, and the transition portion 132 connects the side of the first detection hole 112 and the bottom of the second detection hole 122. The first detection hole 112 is located on the side of the second detection hole 122 in the clockwise rotation direction of the chip unit 100. When the chip unit 100 rotates, the mixture of the sample and the reaction reagent set in the first detection hole 112 can reach the second detection hole 122 through the transition portion 132.

[0059] See also Figure 3 In some embodiments, the transition portion 132 is a first inclined structure, and the inclination direction of the first inclined structure is toward the first detection hole 112, that is, the upper end of the first inclined structure is connected to the second detection hole 122, and the lower end is connected to the first detection hole 112.

[0060] See also Figure 4 In some embodiments, the bottom of the second detection hole 122 is a second inclined structure, and the lower end of the second inclined structure is connected to the upper end of the first inclined structure. In this way, the mixed liquid in the first detection hole 112 can flow toward the second detection hole 122 under the action of inertia. At the same time, the mixed liquid in the second detection hole 122 flows into the first detection hole 112 under the action of gravity.

[0061] Both the first inclined structure and the second inclined structure are inclined surfaces. When the chip unit 100 rotates clockwise, the mixed liquid in the first detection hole 112 moves along the inclined surface to the second detection hole 122 under the action of inertia, and dissolves the photosensitive microspheres in the second detection hole 122. When the chip unit 100 stops, the mixed liquid in the second detection hole 122 will return to the first detection hole 112 along the inclined surface under the action of gravity. At this time, the obtained mixed liquid is placed in a warm bath for a set period of time and can be used in conjunction with the detection equipment for excitation detection. The biotin-labeled molecules in the mixed liquid combine with the streptavidin on the surface of the photosensitive microsphere material, bringing the luminescent microspheres and the photosensitive microspheres closer together and meeting the conditions for photoinduced chemiluminescence.

[0062] See also Figure 2In some embodiments, the first detection hole 112 and the second detection hole 122 are located on the same circular trajectory, and the center of the circular trajectory coincides with the rotation axis of the chip unit 100 .

[0063] In some embodiments, the first detection hole 112 is located on the clockwise side of the second detection hole 122 . When the chip unit 100 rotates counterclockwise, the substance to be detected enters the first detection hole 112 and does not enter the second detection hole 122 .

[0064] See also Figure 5 In some embodiments, the sample loading unit 101 includes a whole blood separation structure, which includes a plasma storage tank, a plasma quantification tank 111, and a blood cell storage tank 131, which are sequentially connected by a plasma flow channel. After a whole blood sample is added to the plasma storage tank, when the chip unit 100 rotates, the whole blood is separated into plasma and blood cells under the action of centrifugal force. The plasma enters the plasma quantification tank 111, and the blood cells enter the blood cell storage tank 131.

[0065] In some embodiments, the sample loading section 101 further includes a dilution structure and a mixing tank 104. The dilution structure includes a diluent placement tank 103 and a diluent quantitative tank 113 connected by a dilution flow channel. The mixing tank 104 is connected to the blood cell storage tank 131 and the diluent quantitative tank 113. After the diluent is added to the diluent placement tank 103, when the chip unit 100 rotates, the diluent enters the diluent quantitative tank 113 under the action of centrifugal force. Since the mixing tank 104 is connected to the blood cell storage tank 131 and the diluent quantitative tank 113, the blood cells and the diluent enter the mixing tank 104, thereby achieving mixing of the blood cells and the diluent. The diluent can be physiological saline.

[0066] In some embodiments, there are multiple groups of detection units 102 on each chip unit 100, and the multiple groups of detection units 102 are arranged in sequence in the rotation direction of the chip unit 100. Each group of detection units 102 can be used for the detection of different indicators. In this way, a parallel multi-indicator joint inspection mode can be realized, which can improve the detection efficiency.

[0067] Continue to see Figure 5 The chip unit 100 also includes a sample distribution groove 105, which is located between the mixing groove 104 and the detection section 102 and extends in the direction in which the multiple groups of first detection holes 112 and second detection holes 122 are arranged. The sample distribution groove 105 has a fluid inlet and multiple fluid outlets. The fluid inlet communicates with the mixing groove, and the multiple fluid outlets communicate with each group of first detection holes 112. When the chip unit 100 rotates, the liquid in the mixing groove 104 enters the distribution groove 105 under the action of centrifugal force. The mixed liquid is then distributed to each of the first detection holes 112 through the distribution groove 105 under the action of centrifugal force.

[0068] The microfluidic chip of this embodiment may include multiple chip units 100, each chip unit 100 is fan-shaped, and multiple chip units 100 are arranged circumferentially along the rotation center to form a disc-shaped structure. The fan angle of the chip unit 100, the number of chip units 100, and the number of specimens that can be accommodated can be set according to actual detection requirements. For example, in the thyroid triple test (TSH, FT3, FT4) scenario, the fan angle of the chip unit 100 is 45°. The number of chip units 100 is 8, and 8 test specimens can be detected simultaneously.

[0069] See also Figure 6 and Figure 7 In this embodiment, the chip unit 100 is a plate-like structure with slots of a specific shape defined on its upper side to form the sample loading and detection structures. A cover is provided above the slots, which includes a sample loading hole 201, a liquid loading hole 202, a first exhaust hole 121, a second exhaust hole 115, and a positioning hole 114. The chip unit 100 is made of an opaque material. The cover comprises a first film 200 and a second film 300. The first film 200 is a transparent film, while the second film 300 is a non-transparent film. The first film 200 and the second film 300 overlap, and the second film 300 includes a light-transmitting hole aligned with the first detection hole 112. This light-transmitting hole serves as a passage for excitation and emission light. Because the photosensitive material within the second detection hole 122 is relatively light-sensitive, the area outside the first detection hole 112 is configured to be opaque. This prevents external light from affecting the photosensitive material within the second detection hole 122.

[0070] In this embodiment, the microfluidic chip also includes a rotating body, and multiple chip units 100 are arranged on the rotating body. The rotation center of the chip unit 100 is also the axis of the rotating body. The rotating body is installed on a rotating table. The rotating table can drive the rotating body to rotate clockwise or counterclockwise around its axis according to a pre-set program, thereby driving the multiple chip units 100 to rotate together, thereby realizing the immunoassay process of the microfluidic chip.

[0071] The solution provided by this application can simplify the design difficulty of the microfluidic chip. There is no need to consider the process of removing free markers. It only needs to consider how to accurately distribute the sample to be tested into the first detection hole 112. The binding of the molecule to be tested and the corresponding ligand is carried out in the first detection hole 112 and the second detection hole 122. It no longer uses a lateral flow method or a chromatographic flow method and is not affected by the flow time of the sample. In other words, it is not affected by slight differences in sample properties such as viscosity, microfluidic channels, or NC membrane heterogeneity. In addition, the chip unit 100 of this application can achieve the functions of plasma separation and precise sample distribution. The pre-installed reagents in related technologies often follow the principle of excess reagents. The deviation of the pre-installed reagents in this application will not affect the precision, which can ensure that the detection system has good repeatability.

[0072] The present application provides a timely detection system, comprising a microfluidic chip as described in any of the above embodiments; and a detection device, wherein the optical detection device cooperates with the detection of the microfluidic chip to detect the sample.

[0073] In this embodiment, the detection device may be a POCT detection device, which can collect signal light in the detection hole of the microfluidic chip and perform detection on the sample based on the signal light.

[0074] See also Figure 8 The present application also provides a detection and control method for a microfluidic chip, which can be applied to the microfluidic chip of any of the above embodiments, and the method comprises the following steps:

[0075] In step S110 , the chip unit 100 is controlled to rotate along a first rotation direction with a first rotation parameter, so as to separate the sample in the sample loading portion 101 into the sample to be detected.

[0076] Prior to this step, a specific amount of sample, such as 25-50 μl of whole blood, can be added to the sample addition tank. A specific amount of diluent, such as 125-400 μl of distilled water or saline, can be added to the liquid addition tank. In this step, the first rotation parameter can be 1300 RPM, and the first rotation direction can be counterclockwise. This step can achieve separation of plasma and blood cells. The substance to be detected is plasma. Centrifugal force causes the plasma to enter the sample quantification tank, and the blood cells to enter the blood cell storage tank 131.

[0077] Step S120 : Control the chip unit 100 to rotate along the first rotation direction with a second rotation parameter to mix the sample to be detected with the diluent.

[0078] In this step, when the chip unit 100 rotates along the first rotation direction at a second rotation parameter, the substance to be detected and the diluent enter the mixing tank 104, thereby mixing the blood cells and the sample buffer. The second rotation parameter may be 1300 RPM.

[0079] In step S130 , the chip unit 100 is controlled to rotate along the first rotation direction with a third rotation parameter, so that the mixture of the substance to be detected and the diluent is distributed to the first detection hole 112 .

[0080] In this step, the third rotation parameter can be 3000 RPM, which allows the sample to be centrifuged into first test well 112, thereby mixing with the reaction reagent set. When the centrifuge is initiated, the centrifugal force causes the liquid to enter first test well 112 from the distribution chamber. However, since chip unit 100 rotates counterclockwise and second test well 122 is located counterclockwise from first test well 112, the liquid's inertia is in the opposite direction. Therefore, the liquid in first test well 112 does not enter second test well 122.

[0081] In some embodiments, after the liquid enters the first detection hole 112, the control chip unit 100 is controlled to reduce the rotation speed until it stops. That is, when the centrifugation stops, the speed needs to be evenly reduced to make the chip unit 100 stop slowly to ensure that the liquid inside the first detection hole 112 does not flow to the second detection hole 122 due to inertia.

[0082] In some embodiments, the luminescent microspheres R1 and the biotin-labeled R2 can be filled using a conventional liquid nitrogen drying method. After the luminescent microspheres R1 and the biotin-labeled R2 are mixed, they are poured into the first detection well 112. Each first detection well 112 can be filled with a set amount of the mixed reagent of the luminescent microspheres R1 and the biotin-labeled R2, for example, 25 μl, and each second detection well 122 can be filled with a set amount of photosensitive microspheres, for example, 10 μl.

[0083] Step S140 , controlling the chip unit 100 to rotate along the second rotation direction with a fourth rotation parameter, so that the sample with the luminescent microspheres R1 and the reagent biotin label R2 in the first detection hole 112 flows into the second detection hole 122 along the transition portion 132 .

[0084] The second rotation direction may be clockwise, and the fourth rotation parameter may be 3000 RPM. When the centrifuge is started, under the action of inertia, the liquid in the first detection hole 112 moves along the inclined surface of the transition portion 132 to the second detection hole 122, and dissolves the photosensitive particle powder in the second detection hole 122.

[0085] Step S150 , the control chip unit 100 stops rotating, so that the mixed liquid with the second detection material photosensitive microspheres in the second detection hole 122 flows back to the first detection hole 112 along the transition portion 132 .

[0086] In this step, when the chip unit 100 stops rotating, the mixed liquid in the second detection hole 122 flows toward the first detection hole 112 along the inclined surface of the transition portion 132 due to inertia and gravity.

[0087] According to the method provided in the embodiment of the present application, when the chip unit 100 rotates along the second rotation direction with a fourth rotation parameter, the sample flows into the second detection hole 122 along the transition portion 132 due to inertia and dissolves the photosensitive material in the second detection hole 122. When the control chip unit 100 stops rotating, the liquid in the second detection hole 122 will flow into the first detection hole 112 along the transition portion 132 under the action of gravity. After the mixed liquid is allowed to stand in the first detection hole 112 for a set period of time (for example, 5 minutes) in a warm bath, it can be used in conjunction with the detection equipment for excitation detection. The biotin-labeled molecules in the sample bind to the streptavidin on the surface of the photosensitive microspheres, bringing the luminescent microspheres and the photosensitive microspheres closer together and satisfying the conditions for photoinduced chemiluminescence.

[0088] This embodiment provides a solution that combines a photochemiluminescence device with a microfluidic chip for conventional excitation detection and then reads the test results. The detection process is automated via a pre-configured application. This organic fusion of photochemiluminescence analysis and centrifugal microfluidics enables precise quantitative analysis of point-of-care (POCT).

[0089] The microfluidic chip of this application integrates complex operational processes into a single chip format, enabling point-of-care (POCT) testing. Furthermore, photochemiluminescence analysis eliminates separation and wash requirements and enables parallel testing of multiple indicators, such as myocardial injury markers, inflammatory factors, thyroid hormones, and sex hormones. This multi-indicator approach can significantly reduce chip manufacturing costs and expand its application areas.

[0090] The embodiments of the present application have been described above. The above description is exemplary, not exhaustive, and is not limited to the disclosed embodiments. Many modifications and variations will be apparent to those skilled in the art without departing from the scope and spirit of the described embodiments. The terminology used herein is selected to best explain the principles of the embodiments, their practical applications, or improvements to the technology in the market, or to enable other persons skilled in the art to understand the embodiments disclosed herein.

Claims

1. A microfluidic chip, characterized in that: include: A chip unit, wherein the chip unit is rotatable around a rotation center; The chip unit includes: A sample loading portion, provided on the chip unit near the rotation center, for placing and accommodating samples to be tested; a detection unit, disposed at a position of the chip unit away from the rotation center and connected to the sample adding unit; The detection portion includes a first detection hole and a second detection hole. The first detection hole is used to accommodate a reaction reagent group, and the second detection hole is used to accommodate photosensitive microspheres. The first detection hole and the second detection hole are connected by a transition portion.

2. The microfluidic chip according to claim 1, wherein: The height of the second detection hole in the thickness direction of the chip unit is greater than that of the first detection hole.

3. The microfluidic chip according to claim 2, wherein: The transition portion is a first inclined structure, the lower end of the first inclined structure is connected to the first detection hole, and the upper end is connected to the first detection hole; and / or The bottom of the second detection hole is a second inclined structure, and the lower end of the second inclined structure is connected to the upper end of the first inclined structure.

4. The microfluidic chip according to claim 1, wherein: The first detection hole is located on one side of the second detection hole in the clockwise rotation direction of the chip unit.

5. The microfluidic chip according to claim 1, wherein: The first detection hole and the second detection hole are located on the same circular track, and the center of the circular track coincides with the rotation axis of the chip unit.

6. The microfluidic chip according to claim 1, characterized in that: There are multiple groups of the first detection holes and the second detection holes, and the multiple groups of the first detection holes and the second detection holes are arranged in sequence in the rotation direction of the chip unit.

7. The microfluidic chip according to claim 1, characterized in that The sample adding part comprises: A whole blood separation structure, comprising a plasma placement tank, a plasma quantitative tank, and a blood cell storage tank sequentially connected by a plasma flow channel; A dilution structure, comprising a dilution liquid placement tank and a dilution liquid quantitative tank connected by a dilution flow channel; The chip unit is further provided with a mixing tank, which is communicated with the blood cell storage tank and the diluent quantitative tank.

8. The microfluidic chip according to claim 7, characterized in that: The chip unit is further provided with a sample distribution groove, which is provided between the mixing groove and the detection part, and the sample distribution groove extends in the arrangement direction of the multiple groups of first detection holes and the second detection holes; The sample distribution groove is provided with a fluid inlet and a plurality of fluid outlets. The fluid inlet is communicated with the mixing groove, and the plurality of fluid outlets are respectively communicated with the first detection holes in each group.

9. The microfluidic chip according to claim 1, characterized in that: There are a plurality of chip units, and the plurality of chip units are arranged in sequence in the circumferential direction of the rotation center.

10. The microfluidic chip according to claim 1, characterized in that: The chip unit is made of opaque material; The chip unit is covered with a first film and a second film, wherein the first film is a transparent film and the second film is a non-transparent film; the second film is provided with a light-transmitting hole corresponding to the first detection hole.

11. An instant detection system, characterized in that: include: The microfluidic chip according to any one of claims 1 to 10; as well as The detection device cooperates with the detection part of the microfluidic chip to detect the sample.

12. A detection and control method for a microfluidic chip, characterized in that ； The method comprises: Controlling the chip unit to rotate along a first rotation direction with a first rotation parameter so as to separate the substance to be detected from the sample in the sample adding portion; controlling the chip unit to rotate along the first rotation direction at a second rotation parameter to mix the substance to be detected with the diluent; Controlling the chip unit to rotate along the first rotation direction at a third rotation parameter so that the mixture of the sample to be tested and the diluent is distributed to the first testing hole; The chip unit is controlled to rotate along a second rotation direction with a fourth rotation parameter, so that the sample with the reaction reagent set in the first detection hole flows into the second detection hole along the transition portion.

13. The method according to claim 12, characterized in that The step of controlling the chip unit to rotate along the first rotation direction with a third rotation parameter so as to distribute the mixture of the sample to be detected and the diluent to the first detection hole includes: Controlling the rotation speed of the chip unit to gradually decrease until it stops; or, After controlling the chip unit to rotate along the second rotation direction with a fourth rotation parameter so that the mixed liquid containing the reaction reagent set in the first detection hole flows along the transition portion into the second detection hole, the method includes: The chip unit is controlled to stop rotating, so that the mixed liquid with the photosensitive microspheres in the second detection hole flows along the transition portion into the first detection hole.

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