WO2024082229A1

WO2024082229A1 - Microfluidic chip and microfluidic analysis system

Info

Publication number: WO2024082229A1
Application number: PCT/CN2022/126513
Authority: WO
Inventors: 杨翥翔; 王胜昔
Original assignee: 深圳迈瑞动物医疗科技股份有限公司
Priority date: 2022-10-20
Filing date: 2022-10-20
Publication date: 2024-04-25

Abstract

The present application is applicable to the field of medical apparatuses, and discloses a microfluidic chip and a microfluidic analysis system. The microfluidic chip comprises a non-circular chip body, wherein a sample injection cavity, a first sample quantification cavity, a diluent intake cavity, a diluent quantification cavity, a mixing cavity, a distribution cavity, a reaction detection cavity, a first overflow cavity and a second overflow cavity are formed in the non-circular chip body; the reaction detection cavity is used for a reagent and a mixed liquid to react to form a sample; the first overflow cavity is in communication with both the diluent quantification cavity and the distribution cavity to collect diluent overflowing from the diluent quantification cavity and collect a mixed liquid overflowing from the distribution cavity; and the second overflow cavity is in communication with the first sample quantification cavity to collect a sample overflowing from the first sample quantification cavity. The microfluidic chip is simple and convenient to use and operate, and can reduce the cost of sample rechecking and the unnecessary waste of samples and consumables.

Description

Microfluidic chip and microfluidic analysis system

Technical Field

The present application relates to the field of medical equipment, and in particular to a microfluidic chip and a microfluidic analysis system having the microfluidic chip.

Background technique

Microfluidic analysis technology integrates the basic operating units of the sample analysis process, such as sample addition, separation, dilution, reaction, and detection, into a microfluidic chip with microchannels (with a size of tens to hundreds of microns), automatically completing the entire process of sample analysis.

The microfluidic chip provided by traditional technology is a complete circular sheet, and the microfluidic chip is surrounded by a plurality of reaction detection chambers in a circle along the circumferential direction, and each reaction detection chamber is used to carry the sample to perform a detection item. When the complete circular microfluidic chip is used for sample detection, it only has the package detection function (that is, the detection items of each reaction detection chamber of the microfluidic chip are used as a package for detection). When the medical staff questions the test results of a certain test item in the package, or the test results of a certain test item are biased, the medical staff needs to review. When testing a single or two or three test items, the use of a complete circular microfluidic chip for review will cause most of the reaction detection chambers on the microfluidic chip to be redundant. In this way, on the one hand, the cost of the review will be increased, and on the other hand, it will cause the waste of redundant reaction detection chambers on the microfluidic chip, and on the other hand, more samples will be consumed, resulting in unnecessary waste of samples, diluents and reagents.

In order to solve the above technical problems, the related art provides a fan-shaped microfluidic chip, and multiple fan-shaped microfluidic chips can be spliced into a complete circular microfluidic structure. The fan-shaped microfluidic chip can reduce the waste of unnecessary reaction detection chambers, samples, diluents and reagents to a certain extent. However, due to the unreasonable structural layout, the fan-shaped microfluidic chip still has the following shortcomings in specific applications: (1) The fan-shaped microfluidic chip does not have the function of separating whole blood samples, and does not have the function of quantitative samples and diluents, which makes the operation of using the fan-shaped microfluidic chip to detect whole blood samples more complicated. It is necessary to first centrifuge the whole blood, take out a certain amount of plasma and add it to the diluent tube, invert and mix several times, and then take out a certain amount of the mixed solution and add it to the fan-shaped microfluidic chip. (2) The central angle of the fan-shaped microfluidic chip is 120°, and it is difficult to further miniaturize it with this layout. There are still many reaction detection chambers on it, which will still cause waste of reaction detection chambers, samples, diluents and reagents.

Summary of the invention

The first objective of the present application is to provide a microfluidic chip, which aims to solve the technical problems in the related art that the microfluidic chip is high in cost and has serious waste of samples and consumables when used for review.

To achieve the above-mentioned object, the present application provides a solution: a microfluidic chip, characterized in that: it includes a non-circular chip body, wherein the non-circular chip body is formed with a sample injection cavity, a first sample quantitative cavity, a diluent inlet cavity, a diluent quantitative cavity, a mixing cavity, a distribution cavity, a reaction detection cavity, a first overflow cavity, and a second overflow cavity;

The injection chamber is used to store samples entering the microfluidic chip;

The first sample quantification chamber is in communication with the injection chamber, so as to quantify the sample from the injection chamber when the microfluidic chip is centrifuged;

The diluent inlet chamber is used to store the diluent entering the microfluidic chip;

The diluent quantitative chamber is in communication with the diluent inlet chamber, so as to quantitatively measure the diluent from the diluent inlet chamber when the microfluidic chip is centrifugally rotated;

The mixing chamber is communicated with the first sample quantitative chamber and the diluent quantitative chamber respectively, so as to receive and mix the sample entering from the first sample quantitative chamber and the diluent entering from the diluent quantitative chamber when the microfluidic chip is centrifuged;

The distribution chamber is communicated with the mixing chamber and the reaction detection chamber respectively, so as to receive a mixed solution formed by mixing a sample and a diluent from the mixing chamber when the microfluidic chip is centrifuged, and distribute the mixed solution to the reaction detection chamber;

The reaction detection chamber is used for the reagent to react with the mixed solution to form a sample;

The first overflow chamber is communicated with the diluent quantitative chamber and the distribution chamber respectively, so as to collect the diluent overflowing from the diluent quantitative chamber and the mixed liquid overflowing from the distribution chamber;

The second overflow chamber is communicated with the first sample quantitative chamber to collect the sample overflowing from the first sample quantitative chamber.

As an embodiment, the non-circular chip body is further formed with a sample determination cavity, and the sample determination cavity is communicated with the second overflow cavity, so as to allow the optical detection component to detect whether there is a sample overflowing from the first sample quantitative cavity;

The distance from the sample determination chamber to the central axis of rotation of the microfluidic chip during centrifugal rotation is the same as the distance from the reaction detection chamber to the central axis of rotation of the microfluidic chip during centrifugal rotation.

As an embodiment, the non-circular chip body is further formed with a diluent determination chamber, and the diluent determination chamber is connected with the first overflow chamber, so as to allow the optical detection component to detect whether there is diluent overflowing from the diluent quantitative chamber;

The distance from the diluent judgment chamber to the central axis of rotation of the centrifugal rotation of the microfluidic chip is the same as the distance from the reaction detection chamber to the central axis of rotation of the centrifugal rotation of the microfluidic chip.

As an embodiment, the distance from the diluent judgment chamber to the central axis of rotation of the centrifugal rotation of the microfluidic chip is greater than the distance from the first overflow chamber to the central axis of rotation of the centrifugal rotation of the microfluidic chip.

As an implementation manner, the sample judgment chamber and the diluent judgment chamber are respectively located on both sides of the reaction detection chamber pair along the centrifugal rotation direction of the microfluidic chip.

As an embodiment, the non-circular chip body also forms a first channel and a second channel, the two ends of the first channel are respectively connected to the distribution chamber and the first overflow chamber, the two ends of the second channel are respectively connected to the distribution chamber and the reaction detection chamber, and the width of the first channel in the centrifugal rotation direction of the microfluidic chip is equal to the width of the second channel in the centrifugal rotation direction of the microfluidic chip.

As an embodiment, the non-circular chip body has a first plate surface and a second plate surface disposed opposite to each other, and the sample injection chamber, the first sample quantitative chamber, the diluent inlet chamber, the diluent quantitative chamber, the mixing chamber, the distribution chamber, the reaction detection chamber, the first overflow chamber and the second overflow chamber are all concavely arranged from the first plate surface toward the second plate surface, and are spaced apart from the second plate surface;

The microfluidic chip further comprises a sealing film, which is attached to the first plate surface to at least cover the sample injection chamber, the first sample quantitative chamber, the diluent inlet chamber, the diluent quantitative chamber, the mixing chamber, the distribution chamber, the reaction detection chamber, the first overflow chamber and the second overflow chamber;

The sealing film is provided with a sample injection hole at a position corresponding to the injection cavity, and the sample injection hole is communicated with the injection cavity so as to allow the sample to be injected into the injection cavity.

As an embodiment, the sealing film is provided with a diluent injection hole at a position corresponding to the diluent inlet cavity, and the diluent injection hole is communicated with the diluent inlet cavity for injecting the diluent into the diluent inlet cavity; or,

A diluent bag is placed in the diluent inlet cavity.

As an embodiment, the non-circular chip body is further formed with a diluent overflow channel and a sample overflow channel, the diluent overflow channel is connected between the diluent quantitative chamber and the first overflow chamber, and the sample overflow channel is connected between the first sample quantitative chamber and the second overflow chamber;

The sealing film is also penetrated by a first vent hole, a second vent hole and a third vent hole, the first vent hole is communicated with the diluent overflow channel, the second vent hole is communicated with the sample overflow channel, and the third vent hole is communicated with the mixing chamber.

As an embodiment, the non-circular chip body is further formed with a second sample quantitative cavity, a sample quantitative channel and a sample drainage capillary, and the two ends of the sample quantitative channel are respectively connected to the first sample quantitative cavity and the second sample quantitative cavity;

The distance from the sample quantitative channel to the central axis of rotation of the microfluidic chip is greater than the distance from the first sample quantitative cavity to the central axis of rotation of the microfluidic chip, and less than the distance from the second sample quantitative cavity to the central axis of rotation of the microfluidic chip;

The two ends of the sample drainage capillary are respectively connected to the sample quantitative pipeline and the mixing chamber, and the sample drainage capillary has a first bending portion, and the distance from the first bending portion to the rotation center axis of the centrifugal rotation of the microfluidic chip is smaller than the distance from the first sample quantitative chamber to the rotation center axis of the centrifugal rotation of the microfluidic chip.

As an embodiment, the non-circular chip body is further formed with a mixed liquid drainage capillary and an initial liquid cavity;

The two ends of the mixed liquid drainage capillary are respectively connected to the mixing chamber and the distribution chamber, and the mixed liquid drainage capillary has a second bending portion, and the distance from the second bending portion to the rotation center axis of the centrifugal rotation of the microfluidic chip is smaller than the distance from the mixing chamber to the rotation center axis of the centrifugal rotation of the microfluidic chip;

The initial liquid chamber is in communication with one end of the distribution chamber close to the mixed liquid drainage capillary, so as to at least collect the initial liquid entering the distribution chamber from the mixed liquid drainage capillary;

The distance from the initial liquid chamber to the central axis of rotation of the microfluidic chip during centrifugal rotation is smaller than the distance from the reaction detection chamber to the central axis of rotation of the microfluidic chip during centrifugal rotation.

As an embodiment, the volume of the initial liquid chamber is smaller than the volume of the reaction detection chamber; and/or,

The non-circular chip body also forms a second channel and a third channel, the two ends of the second channel are respectively connected to the distribution chamber and the reaction detection chamber, the two ends of the third channel are respectively connected to the distribution chamber and the initial liquid chamber, and the width of the third channel in the centrifugal rotation direction of the microfluidic chip is equal to the width of the second channel in the centrifugal rotation direction of the microfluidic chip.

As an embodiment, the non-circular chip body includes a first edge and a second edge, the first edge and the second edge are arranged opposite to each other at a distance, the first edge is arranged at one end of the microfluidic chip close to the rotation center axis of the centrifugal rotation of the microfluidic chip, and the second edge is arranged at one end of the microfluidic chip away from the rotation center axis of the centrifugal rotation of the microfluidic chip;

The diluent inlet chamber, the diluent quantitative chamber, the mixing chamber, the distribution chamber, and the first overflow chamber are sequentially arranged between the first edge and the second edge;

The injection chamber, the first sample quantitative chamber, the mixing chamber, the distribution chamber, and the second overflow chamber are sequentially arranged between the first edge and the second edge.

As an implementation, the length of the second edge is greater than the length of the first edge.

As an implementation manner, the first edge and the second edge are two arc-shaped edges with the same center; or,

The first edge and the second edge are two straight line edges parallel to each other.

As an embodiment, the non-circular chip body further includes a third edge and a fourth edge;

The third edge is spaced apart from the fourth edge and arranged opposite to each other. The third edge extends from one end of the first edge to one end of the second edge, and the fourth edge extends from the other end of the first edge to the other end of the second edge.

The diluent inlet chamber, the diluent quantitative chamber, one end of the mixing chamber, one end of the distribution chamber, and the first overflow chamber are arranged in sequence along the third edge;

The injection chamber, the first sample quantitative chamber, and the second overflow chamber are arranged in sequence along the fourth edge.

As an implementation manner, the angle formed by the third edge and the fourth edge is greater than 0° and less than or equal to 90°.

As an implementation manner, the angle formed by the third edge and the fourth edge is 60°±15°.

As an embodiment, the number of the reaction detection cavities formed by the non-circular chip body is less than or equal to six.

As an implementation manner, the number of the reaction detection cavities formed by the non-circular chip body is two, three, four or five.

The second object of the present application is to provide a microfluidic chip, which includes a non-circular chip body, wherein the non-circular chip body is formed with a sample injection chamber, a first sample quantitative chamber, a diluent inlet chamber, a diluent quantitative chamber, a mixing chamber, a distribution chamber, a reaction detection chamber, a third overflow chamber, and a fourth overflow chamber;

The third overflow chamber is in communication with the diluent quantitative chamber, so as to collect the diluent overflowing from the diluent quantitative chamber;

The fourth overflow chamber is communicated with the first sample quantitative chamber and the distribution chamber respectively, so as to collect the sample overflowing from the first sample quantitative chamber and the mixed liquid overflowing from the distribution chamber.

The third object of the present application is to provide a microfluidic analysis system, which includes a turntable, an optical detection component, a rotation drive mechanism and the above-mentioned microfluidic chip;

The turntable is formed with a plurality of accommodating positions sequentially distributed along the circumferential direction, each of the accommodating positions is used to accommodate one of the microfluidic chips or a counterweight component having the same outer contour and the same weight as the microfluidic chip;

The optical detection assembly includes a light emitting element and a light receiving element, wherein the light emitting element is disposed above the rotating disk to at least irradiate light toward the sample in the reaction detection chamber;

The light receiving element is disposed below the rotating disk and directly below the light emitting element, so as to receive the light emitted by the light emitting element through the microfluidic chip;

The rotary drive mechanism is used to drive the turntable to drive the microfluidic chip to rotate, so as to respectively achieve: quantification of samples and diluents, mixing of samples and diluents, distribution of mixed solutions, and rotation of the reaction detection chamber to directly below the light receiving element.

The microfluidic chip and microfluidic analysis system provided by the present application realize the loading of samples on the microfluidic chip through the injection chamber, realize the loading of diluent on the microfluidic chip through the diluent inlet chamber, quantify the sample from the injection chamber through the first sample quantification chamber, quantify the diluent from the diluent inlet chamber through the diluent quantification chamber, receive and mix the sample entering from the first sample quantification chamber and the diluent entering from the diluent quantification chamber through the mixing chamber, receive the mixed solution formed by the sample and the diluent entering from the mixing chamber through the distribution chamber and distribute the mixed solution to the reaction detection chamber, and collect and quantify excess diluent and sample through the first overflow chamber and the second overflow chamber, so that after the sample and the diluent are added to the microfluidic chip, the quantification, mixing, distribution and detection of the sample and the diluent can be automatically completed through the rotation of the microfluidic chip, and the operation is simple and the quantification is accurate. Since the sample injection chamber, the first sample quantitative chamber, the diluent inlet chamber, the diluent quantitative chamber, the mixing chamber, the distribution chamber, the reaction detection chamber, the first overflow chamber and the second overflow chamber are all formed in the non-circular chip body, that is, the microfluidic chip is not a completely circular chip, it is beneficial to reduce the number of reaction detection chambers and reduce the waste of samples, diluents and reagents during re-examination. In addition, since the first overflow chamber is used to collect the diluent overflowing from the diluent quantitative chamber and the mixed liquid overflowing from the distribution chamber, it is equivalent to combining the overflow chamber for diluent quantitative and the overflow chamber for mixed liquid into one, which is beneficial to reduce the number of overflow chambers, and then to simplify the structure of the microfluidic chip and improve the compactness of the structure of the microfluidic chip, which can ultimately be beneficial to the miniaturization design of the microfluidic chip, thereby further reducing the material cost of the microfluidic chip, and then reducing the cost of re-examination using the microfluidic chip.

BRIEF DESCRIPTION OF THE DRAWINGS

In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on the structures shown in these drawings without paying any creative work.

FIG1 is a schematic diagram of a top view of a microfluidic chip provided in Example 1 of the present application;

FIG2 is a schematic diagram of a state after a sample and a diluent are added to a microfluidic chip according to Example 1 of the present application;

3 is a schematic diagram of the state of the microfluidic chip provided in Example 1 of the present application after the first centrifugal rotation to complete the dilution and sample quantification;

4 is a schematic diagram of the state of drainage of the sample and the diluent under the capillary action after the first centrifugal rotation of the microfluidic chip provided in Example 1 of the present application is stopped;

5 is a schematic diagram of the state of the microfluidic chip provided in Example 1 of the present application after the second centrifugal rotation to complete the mixing of the diluent and the sample;

6 is a schematic diagram of the state of drainage of the mixed liquid under capillary action after the second centrifugal rotation of the microfluidic chip provided in Example 1 of the present application is stopped;

7 is a schematic diagram of the state of the microfluidic chip provided in Example 1 of the present application after the third centrifugal rotation to complete the distribution of the mixed solution;

FIG8 is a schematic diagram of the front view of the microfluidic chip provided in Example 1 of the present application;

FIG9 is a schematic diagram of the distribution of multiple microfluidic chips on a turntable provided in Example 1 of the present application;

FIG10 is a schematic diagram of the positions of the microfluidic chip and the optical detection component provided in Example 1 of the present application;

FIG11 is a schematic diagram of the composition of a microfluidic analysis system provided in Example 1 of the present application;

FIG12 is a schematic diagram of a top view of the microfluidic chip provided in Example 2 of the present application;

FIG. 13 is a schematic diagram of the top view of the structure of the microfluidic chip provided in Example 3 of the present application.

Description of the accompanying drawings: 100, microfluidic chip; 110, non-circular chip body; 111, sample injection chamber; 112, first sample quantitative chamber; 113, diluent injection chamber; 114, diluent quantitative chamber; 115, mixing chamber; 116, distribution chamber; 117, reaction detection chamber; 118, first overflow chamber; 119, second overflow chamber; 101, sample judgment chamber; 102, diluent judgment chamber; 103, diluent overflow channel; 104, sample overflow channel; 105, second sample quantitative chamber; 106, sample quantitative pipeline; 107, sample drainage capillary; 1071, first bending portion; 108, diluent drainage Flow capillary; 1081, third bend; 109, mixed liquid drainage capillary; 1091, second bend; 1001, initial liquid chamber; 1002, first channel; 1003, second channel; 1004, third channel; 1005, first edge; 1006, second edge; 1007, third edge; 1008, fourth edge; 1009, first plate surface; 1010, second plate surface; 1011, third overflow chamber; 1012, fourth overflow chamber; 120, sealing film; 121, sample injection hole; 122, diluent injection hole; 123, first vent hole; 124, second vent hole; 125, third vent hole; 200, turntable; 300, optical detection component; 310, light emitting element; 320, light receiving element; 400, rotation drive mechanism; 500, controller; MN, rotation center axis.

Detailed ways

The following will be combined with the drawings in the embodiments of the present application to clearly and completely describe the technical solutions in the embodiments of the present application. Obviously, the described embodiments are only part of the embodiments of the present application, not all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of this application.

It should be noted that all directional indications in the embodiments of the present application (such as up, down, left, right, front, back, etc.) are only used to explain the relative position relationship, movement status, etc. between the components in a certain specific posture. If the specific posture changes, the directional indication will also change accordingly.

It should also be noted that when an element is referred to as being "fixed on" or "disposed on" another element, it may be directly on the other element or there may be an intermediate element at the same time. When an element is referred to as being "connected to" another element, it may be directly connected to the other element or may be indirectly connected to the other element through an intermediate element.

In addition, the descriptions of "first", "second", etc. in this application are only for descriptive purposes and cannot be understood as indicating or implying their relative importance or implicitly indicating the number of the indicated technical features. Therefore, the features defined as "first" and "second" may explicitly or implicitly include at least one of the features. In addition, the technical solutions between the various embodiments can be combined with each other, but they must be based on the ability of ordinary technicians in this field to implement them. When the combination of technical solutions is contradictory or cannot be implemented, it should be deemed that such combination of technical solutions does not exist and is not within the scope of protection required by this application.

Embodiment 1:

As shown in Figures 1, 8 and 9, the microfluidic chip 100 provided in the first embodiment of the present application includes a non-circular chip body 110, and the non-circular chip body 110 is specifically a chip structure with a non-complete circumference, that is, the outer edge of the non-circular chip body 110 is not circular. The microfluidic chip 100 is a non-circular structure as a whole, that is, the microfluidic chip 100 is not a full circle. Compared with a full circle chip, the material cost of the microfluidic chip 100 can be reduced. When used for the detection of a small number of detection items (such as the review of some detection items), the cost and the consumption of samples, diluents and reagents can be reduced. When used for the detection of a large number of detection items, more than two microfluidic chips 100 can be used for combined detection to meet the detection requirements of different numbers of detection items, and the flexibility of use is high.

1, 2 and 8, as an embodiment, the non-circular chip body 110 is formed with a sample injection chamber 111, a first sample quantitative chamber 112, a diluent inlet chamber 113, a diluent quantitative chamber 114, a mixing chamber 115, a distribution chamber 116 and a reaction detection chamber 117. The sample injection chamber 111 is used to store the sample entering the microfluidic chip 100; the first sample quantitative chamber 112 is connected to the sample injection chamber 111, so as to quantitatively sample from the sample injection chamber 111 when the microfluidic chip 100 is centrifuged; the diluent inlet chamber 113 ... diluent inlet chamber 114 is used to store the sample entering the microfluidic chip 100; the diluent inlet chamber 115 is used to store the sample entering the microfluidic chip 100; the diluent inlet chamber 116 is used to store the sample entering the microfluidic chip 100; the diluent inlet chamber 113 is used to store the sample entering the microfluidic chip 100; the diluent inlet chamber 113 is used to store the sample entering the microfluidic chip 100; 113 is used to store the diluent entering the microfluidic chip 100; the diluent quantitative chamber 114 is connected with the diluent inlet chamber 113, so as to quantitatively collect the diluent from the diluent inlet chamber 113 when the microfluidic chip 100 is centrifuged; the mixing chamber 115 is respectively connected with the first sample quantitative chamber 112 and the diluent quantitative chamber 114, so as to receive and mix the sample entering from the first sample quantitative chamber 112 and the diluent entering from the diluent quantitative chamber 114 when the microfluidic chip 100 is centrifuged; the distribution chamber 116 is respectively connected with the mixing chamber 115 and the reaction detection chamber 117, so as to receive the mixed solution formed by mixing the sample and the diluent entering from the mixing chamber 115 when the microfluidic chip 100 is centrifuged, and distribute the mixed solution to the reaction detection chamber 117; the reaction detection chamber 117 is used for the reagent to react with the mixed solution to form a sample. In this embodiment, after the sample and the diluent are added to the microfluidic chip 100, the quantification, mixing, distribution and detection of the sample and the diluent can be automatically completed through the rotation of the microfluidic chip 100, and the operation is simple, convenient and accurate. Since the sample injection cavity 111, the first sample quantitative cavity 112, the diluent injection cavity 113, the diluent quantitative cavity 114, the mixing cavity 115, the distribution cavity 116 and the reaction detection cavity 117 are all formed in the non-circular chip body 110, it is beneficial to reduce the number of reaction detection cavities 117 on the microfluidic chip 100, and it is beneficial to reduce the waste of samples, diluents and reagents during re-examination.

1, 3 and 8, as an embodiment, the non-circular chip body 110 is further formed with a first overflow cavity 118, which is communicated with the diluent quantitative cavity 114, respectively, to collect the diluent overflowing from the diluent quantitative cavity 114. The first overflow cavity 118 can be used to collect excess diluent after quantitative measurement, which is conducive to ensuring sufficient diluent and preventing excessive diluent, and effectively ensuring the accuracy of diluent quantitative measurement.

1, 3 and 7, as an embodiment, the first overflow chamber 118 is also connected to the distribution chamber 116 to collect the mixed liquid overflowing from the distribution chamber 116. In this embodiment, the first overflow chamber 118 is used to collect the diluent overflowing from the diluent quantitative chamber 114, and to collect the mixed liquid overflowing from the distribution chamber 116, which is equivalent to combining the overflow chamber for diluent quantitative and the overflow chamber for mixed liquid into one, thereby facilitating the reduction of the number of overflow chambers, and further facilitating the simplification of the structure of the microfluidic chip 100 and improving the compactness of the structure of the microfluidic chip 100, and ultimately facilitating the miniaturization design of the microfluidic chip 100, thereby facilitating the further reduction of the material cost of the microfluidic chip 100, and further facilitating the reduction of the cost of review using the microfluidic chip 100.

1, 3 and 8, as an embodiment, the non-circular chip body 110 is further formed with a second overflow cavity 119, which is communicated with the first sample quantitative cavity 112 to collect the sample overflowing from the first sample quantitative cavity 112. The second overflow cavity 119 is mainly used to collect excess sample after quantification, which is conducive to ensuring sufficient sample and preventing excessive sample, and effectively ensuring the accuracy of sample quantification.

Referring to FIG. 1 , FIG. 3 and FIG. 8 , as an embodiment, the non-circular chip body 110 is further formed with a sample judgment cavity 101, and the sample judgment cavity 101 is connected to the second overflow cavity 119, so as to allow the optical detection component 300 to detect whether there is a sample overflowing from the first sample quantitative cavity 112. When the optical detection component 300 detects that there is a sample in the sample judgment cavity 101, it means that the first sample quantitative cavity 112 is full, so that it can be judged that the sample amount is sufficient, otherwise it is judged that the sample amount is insufficient. The setting of the sample judgment cavity 101 can help to further ensure the accuracy and reliability of sample quantification.

Referring to FIG. 1 , FIG. 3 and FIG. 10 , as an embodiment, the distance from the sample judgment chamber 101 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100 is the same as the distance from the reaction detection chamber 117 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100. In this embodiment, the distance from the sample judgment chamber 101 to the rotation center axis MN of the microfluidic chip 100 is the same as the distance from the reaction detection chamber 117 to the rotation center axis MN of the microfluidic chip 100, so that when the microfluidic chip 100 rotates, the sample judgment chamber 101 and the reaction detection chamber 117 can pass through the same position in sequence, so that the judgment of the presence or absence of the sample in the sample judgment chamber 101 and the detection of the sample in the reaction detection chamber 117 can share the optical detection component 300, thereby simplifying the structure of the microfluidic system. Of course, in specific applications, as an alternative implementation scheme, the presence or absence of the sample in the sample judgment chamber 101 can also be detected by a separate sensor, without sharing the optical detection component 300 with the reaction detection chamber 117. In this way, the distance from the sample judgment chamber 101 to the rotation center axis MN of the microfluidic chip 100 and the distance from the reaction detection chamber 117 to the rotation center axis MN of the microfluidic chip 100 may be different.

Referring to FIG. 1 , FIG. 3 and FIG. 8 , as an embodiment, the non-circular chip body 110 is further formed with a diluent judgment chamber 102, and the diluent judgment chamber 102 is connected to the first overflow chamber 118, so as to allow the optical detection component 300 to detect whether there is diluent overflowing from the diluent quantitative chamber 114. When the optical detection component 300 detects that there is diluent in the diluent judgment chamber 102, it means that the diluent quantitative chamber 114 is full, so that it can be judged that the amount of diluent is sufficient, otherwise it is judged that the amount of diluent is insufficient. The setting of the diluent judgment chamber 102 can help to further ensure the accuracy and reliability of the diluent quantification.

Referring to FIG. 1 , FIG. 3 and FIG. 10 , as an embodiment, the distance from the diluent judgment chamber 102 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100 is the same as the distance from the reaction detection chamber 117 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100. In this embodiment, the distance from the diluent judgment chamber 102 to the rotation center axis MN of the microfluidic chip 100 is the same as the distance from the reaction detection chamber 117 to the rotation center axis MN of the microfluidic chip 100, so that when the microfluidic chip 100 rotates, the diluent judgment chamber 102 and the reaction detection chamber 117 can pass through the same position in sequence, so that the judgment of the presence or absence of the diluent in the diluent judgment chamber 102 and the detection of the sample in the reaction detection chamber 117 can share the optical detection component 300, so as to simplify the structure of the microfluidic system. Of course, in specific applications, as an alternative implementation scheme, the presence or absence of diluent in the diluent judgment chamber 102 can also be detected by a separate sensor, without sharing the optical detection component 300 with the reaction detection chamber 117. In this way, the distance from the diluent judgment chamber 102 to the rotation center axis MN of the microfluidic chip 100 and the distance from the reaction detection chamber 117 to the rotation center axis MN of the microfluidic chip 100 may be different.

As an embodiment, the diluent judgment chamber 102, the reaction detection chamber 117 and the sample judgment chamber 101 are sequentially distributed along the same arc trajectory, so that when the microfluidic chip 100 rotates, the diluent judgment chamber 102, the reaction detection chamber 117 and the sample judgment chamber 101 can sequentially pass through the same position, thereby facilitating the judgment of the presence of diluent in the diluent judgment chamber 102, the judgment of the presence of sample in the sample judgment chamber 101 and the detection of the sample in the reaction detection chamber 117 to share the optical detection component 300.

1, 2 and 10, as an embodiment, the distance from the diluent judgment chamber 102 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100 is greater than the distance from the first overflow chamber 118 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100. This helps to ensure that a quantitative excess of diluent will preferentially enter the diluent judgment chamber 102 under the action of centrifugation, and will enter the first overflow chamber 118 only after the diluent judgment chamber 102 is full.

1, 2 and 10, as an embodiment, the distance from the sample judgment chamber 101 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100 is greater than the distance from the second overflow chamber 119 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100. This helps to ensure that the quantitative excess sample will first enter the sample judgment chamber 101 under the action of centrifugation, and will enter the second overflow chamber 119 only after the diluent judgment chamber 102 is full.

1, 2 and 3, as an embodiment, the sample judgment chamber 101 and the diluent judgment chamber 102 are respectively located on both sides of the reaction detection chamber 117 along the direction of centrifugal rotation of the microfluidic chip 100, that is, the reaction detection chamber 117 is located between the sample judgment chamber 101 and the diluent along the circumference of the microfluidic chip 100. With this arrangement, the sample-related chambers and the diluent-related chambers can be respectively concentrated on both sides of the circumference of the microfluidic chip 100, thereby improving the structural compactness of the microfluidic chip 100.

1, 3, 4 and 8, as an embodiment, the non-circular chip body 110 is further formed with a first channel 1002 and a second channel 1003, the two ends of the first channel 1002 are respectively connected to the distribution chamber 116 and the first overflow chamber 118, the two ends of the second channel 1003 are respectively connected to the distribution chamber 116 and the reaction detection chamber 117, and the width _L1 of the first channel 1002 in the centrifugal rotation direction of the microfluidic chip 100 is equal to the width _L2 of the second channel 1003 in the centrifugal rotation direction of the microfluidic chip 100. In this embodiment, the first channel 1002 and the second channel 1003 are designed to be equal in width without distinction, which is conducive to reducing the manufacturing difficulty of the microfluidic chip 100.

1, 3 and 8, as an embodiment, the non-circular chip body 110 is further formed with a diluent overflow channel 103, and the diluent overflow channel 103 is connected between the diluent quantitative chamber 114 and the first overflow chamber 118. The diluent overflow channel 103 is also connected to the diluent judgment chamber 102. The diluent overflow channel 103 is mainly used to guide the diluent overflowing from the diluent quantitative chamber 114 to the diluent judgment chamber 102 and the first overflow chamber 118.

As an embodiment, one end of the diluent overflow channel 103 is connected to the end of the diluent quantitative chamber 114 close to the rotation center axis MN of the microfluidic chip 100, so that the diluent will enter the diluent overflow channel 103 under the action of centrifugation only after filling the diluent quantitative chamber 114.

1, 3 and 8, as an embodiment, the non-circular chip body 110 is further formed with a sample overflow channel 104, and the sample overflow channel 104 is connected between the first sample quantitative chamber 112 and the second overflow chamber 119. The sample overflow channel 104 is also connected to the sample judgment chamber 101. The sample overflow channel 104 is mainly used to guide the sample overflowing from the first sample quantitative chamber 112 to the sample judgment chamber 101 and the second overflow chamber 119.

As an embodiment, one end of the sample overflow channel 104 is connected to the end of the first sample quantitative chamber 112 close to the rotation center axis MN of the microfluidic chip 100, so that the sample will enter the sample overflow channel 104 under centrifugal action only after filling the first sample quantitative chamber 112.

Referring to FIG. 1 , FIG. 3 , FIG. 8 and FIG. 10 , as an embodiment, the non-circular chip body 110 is further formed with a second sample quantitative cavity 105 and a sample quantitative channel 106, and the two ends of the sample quantitative channel 106 are connected to the first sample quantitative cavity 112 and the second sample quantitative cavity 105 respectively; the distance from the sample quantitative channel 106 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100 is greater than the distance from the first sample quantitative cavity 112 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100, and is less than the distance from the second sample quantitative cavity 105 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100. The second sample quantitative cavity 105 is provided mainly to meet the requirements of centrifugal stratification of some samples before detection. For example, when the sample is a whole blood sample, after the sample is centrifuged and quantified, the plasma will be concentrated in the first sample quantitative cavity 112, and the red blood cells will be concentrated in the second sample quantitative cavity 105.

3, 4 and 8, as an embodiment, the non-circular chip body 110 is further formed with a sample drainage capillary 107, and the two ends of the sample drainage capillary 107 are respectively connected to the sample quantitative pipeline 106 and the mixing chamber 115. The provision of the sample drainage capillary 107 is mainly used to ensure that the quantification of the sample and the mixing of the sample entering the mixing chamber 115 can be performed separately in the two centrifugal rotations of the microfluidic chip 100, thereby facilitating the guarantee of the accuracy of the sample quantification.

Referring to FIG. 3, FIG. 4, FIG. 8 and FIG. 10, as an embodiment, the sample drainage capillary 107 has a first bending portion 1071, and the distance from the first bending portion 1071 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100 is less than the distance from the first sample quantitative cavity 112 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100. In this embodiment, the distance from the first bending portion 1071 to the rotation center axis MN of the microfluidic chip 100 is less than the distance from the first sample quantitative cavity 112 to the rotation center axis MN of the microfluidic chip 100, which is conducive to ensuring that in the centrifugal rotation stage of the quantitative sample, the sample will not enter the mixing chamber 115 from the sample drainage capillary 107; in the quantitative sample completion stop stage, the sample in the sample drainage capillary 107 fills the sample drainage capillary 107 under capillary action; in the centrifugal rotation stage of the sample and the diluent, the sample in the sample drainage capillary 107 flows into the mixing chamber 115 under the action of siphon.

As an embodiment, one end of the sample drainage capillary 107 is connected to the end of the sample quantitative pipeline 106 close to the first sample quantitative chamber 112, and the other end of the sample drainage capillary 107 is connected to the end of the mixing chamber 115 close to the rotation center axis MN of the microfluidic chip 100.

As an implementation manner, the first bending portion 1071 is bent in an arc shape.

3, 4 and 8, as an embodiment, the non-circular chip body 110 is further formed with a diluent drainage capillary 108, and the two ends of the diluent drainage capillary 108 are respectively connected to the diluent quantitative chamber 114 and the mixing chamber 115. The setting of the diluent drainage capillary 108 is mainly used to ensure that the quantification of the diluent and the mixing of the diluent entering the mixing chamber 115 can be carried out separately in the two centrifugal rotations of the microfluidic chip 100, thereby helping to ensure the quantitative accuracy of the diluent.

Referring to Fig. 3, Fig. 4, Fig. 8 and Fig. 10, as an embodiment, the diluent drainage capillary 108 has a third bend 1081, and the distance from the third bend 1081 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100 is less than the distance from the diluent quantitative chamber 114 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100. In this embodiment, the distance from the third bend 1081 to the rotation center axis MN of the microfluidic chip 100 is less than the distance from the diluent quantitative chamber 114 to the rotation center axis MN of the microfluidic chip 100, which is conducive to ensuring that the diluent will not enter the mixing chamber 115 from the diluent drainage capillary 108 during the centrifugal rotation stage of the quantitative diluent; in the quantitative diluent completion stop stage, the diluent in the diluent drainage capillary 108 fills the diluent drainage capillary 108 under capillary action; in the mixed centrifugal rotation stage, the diluent in the diluent drainage capillary 108 flows into the mixing chamber 115 under the action of siphon. Specifically, the quantification of the diluent and the quantification of the sample are performed in the same centrifugal rotation stage of the microfluidic chip 100 , and the diluent and the sample enter the mixing chamber 115 in the same centrifugal rotation stage of the microfluidic chip 100 .

As an embodiment, one end of the diluent drainage capillary 108 is connected to the end of the diluent quantitative chamber 114 away from the rotation center axis MN of the microfluidic chip 100, and the other end of the diluent drainage capillary 108 is connected to the end of the mixing chamber 115 close to the rotation center axis MN of the microfluidic chip 100.

As an implementation manner, the third bending portion 1081 is bent in an arc shape.

As shown in FIGS. 5 to 8 , as an embodiment, the non-circular chip body 110 is further formed with a mixed liquid drainage capillary 109 and an initial liquid chamber 1001; the two ends of the mixed liquid drainage capillary 109 are respectively connected to the mixing chamber 115 and the distribution chamber 116, and the initial liquid chamber 1001 is connected to the distribution chamber 116 near one end of the mixed liquid drainage capillary 109, so as to at least collect the initial liquid entering the distribution chamber 116 from the mixed liquid drainage capillary 109. The arrangement of the mixed liquid drainage capillary 109 is mainly used to ensure that the diluent and the sample are mixed and the mixed liquid is distributed into the distribution chamber 116 in two centrifugal rotations of the microfluidic chip 100, so as to ensure that the diluent and the sample can be fully mixed before entering the distribution chamber 116, and further to ensure the accuracy of the sample detection in the reaction detection chamber 117. The initial liquid chamber 1001 is used to collect the unmixed liquid from the mixed liquid drainage capillary 109, so as to ensure the accuracy of the sample detection in the reaction detection chamber 117.

7, 8 and 10, as an embodiment, the distance from the initial liquid chamber 1001 to the central axis MN of the centrifugal rotation of the microfluidic chip 100 is less than the distance from the reaction detection chamber 117 to the central axis MN of the centrifugal rotation of the microfluidic chip 100. In this embodiment, the distance from the initial liquid chamber 1001 to the central axis MN of the microfluidic chip 100 is less than the distance from the reaction detection chamber 117 to the central axis MN of the microfluidic chip 100, which can help ensure that when the microfluidic chip 100 is centrifugally rotated, the liquid that enters the distribution chamber 116 from the mixed liquid drainage capillary 109 will preferentially fill the initial liquid chamber 1001, so that the unmixed liquid can preferentially enter the initial liquid chamber 1001.

As an embodiment, the reaction detection chamber 117 is arranged between the initial liquid chamber 1001 and the first overflow chamber 118 along the circumferential direction of the centrifugal rotation of the microfluidic chip 100. In this way, the initial liquid chamber 1001 and the first overflow chamber 118 can be arranged close to the two ends of the distribution chamber 116, respectively, which is beneficial to ensure that the liquid from the mixed liquid drainage capillary 109 enters the distribution chamber 116, first fills the initial liquid chamber 1001, then fills the reaction detection chamber 117, and finally enters the first overflow chamber 118.

As shown in FIG. 5 to FIG. 8 , as an embodiment, the mixed liquid drainage capillary 109 has a second bend 1091, and the distance from the second bend 1091 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100 is less than the distance from the mixing chamber 115 to the rotation center axis MN of the centrifugal rotation of the microfluidic chip 100. In this embodiment, the distance from the second bend 1091 to the rotation center axis MN of the microfluidic chip 100 is less than the distance from the mixing chamber 115 to the rotation center axis MN of the microfluidic chip 100, which is conducive to ensuring that during the centrifugal rotation stage of the diluent and the sample mixing, the sample and the diluent will not enter the distribution chamber 116 from the mixed liquid drainage capillary 109; in the mixing completion stop stage, the mixed liquid in the mixed liquid drainage capillary 109 fills the mixed liquid drainage capillary 109 under capillary action; in the centrifugal rotation stage of the mixed liquid distribution, the mixed liquid in the mixed liquid drainage capillary 109 flows into the distribution chamber 116 under the action of siphon.

As an embodiment, one end of the mixed liquid drainage capillary 109 is connected to the end of the mixing chamber 115 away from the rotation center axis MN of the microfluidic chip 100, and the other end of the mixed liquid drainage capillary 109 is connected to the end of the distribution chamber 116 close to the rotation center axis MN of the microfluidic chip 100.

As an implementation manner, the second bending portion 1091 is bent in an arc shape.

5, 6 and 7, as an embodiment, the volume of the initial liquid chamber 1001 is smaller than the volume of the reaction detection chamber 117. Since the initial liquid chamber 1001 is mainly used to collect a small amount of liquid that has not been mixed in the mixed liquid drainage capillary 109, the initial liquid chamber 1001 is designed to be smaller than the reaction detection chamber 117, which can help prevent excessive mixed liquid from entering the initial liquid chamber 1001 after mixing in the mixing chamber 115, resulting in waste of samples and diluents, so as to ensure that the subsequent reaction detection chamber 117 can collect a sufficient amount of mixed liquid.

3, 4 and 8, as an embodiment, the non-circular chip body 110 is further formed with a second channel 1003 and a third channel 1004, the two ends of the second channel 1003 are respectively connected to the distribution chamber 116 and the reaction detection chamber 117, the two ends of the third channel 1004 are respectively connected to the distribution chamber 116 and the initial liquid chamber 1001, and the width _L3 of the third channel 1004 in the centrifugal rotation direction of the microfluidic chip 100 is equal to the width _L2 of the second channel 1003 in the centrifugal rotation direction of the microfluidic chip 100. The width _L3 of the third channel 1004 in the centrifugal rotation direction of the microfluidic chip 100 is the circumferential width of the third channel 1004. The width _L2 of the second channel 1003 in the centrifugal rotation direction of the microfluidic chip 100 is the circumferential width of the second channel 1003. In this embodiment, the second channel 1003 and the third channel 1004 are designed to be equal in width without distinction, which is conducive to reducing the manufacturing difficulty of the microfluidic chip 100.

As an implementation mode, the reaction detection chamber 117 is loaded with reagents, and after the mixed solution enters the reaction detection chamber 117 , it reacts with the reagents to form a sample.

As an embodiment, the reagent loaded in the reaction detection chamber 117 is a freeze-dried ball reagent, which is a reagent made by freeze-drying method. The freeze-dried ball reagent is small in volume and is conducive to increasing the shelf life of the reagent. The use of a smaller volume of freeze-dried ball reagent can increase the sample carrying capacity in the reaction detection chamber 117 of the same size, thereby helping to improve the sensitivity and efficiency of the detection.

Referring to FIG. 1 , FIG. 3 and FIG. 8 , as an embodiment, the non-circular chip body 110 includes a first edge 1005 and a second edge 1006, the first edge 1005 and the second edge 1006 are arranged opposite to each other at intervals, the first edge 1005 is arranged at one end of the microfluidic chip 100 close to the rotation center axis MN of the microfluidic chip 100 centrifugally rotating, and the second edge 1006 is arranged at one end of the microfluidic chip 100 away from the rotation center axis MN of the microfluidic chip 100 centrifugally rotating. The diluent inlet chamber 113, the diluent quantitative chamber 114, the mixing chamber 115, the distribution chamber 116, and the first overflow chamber 118 are arranged in sequence between the first edge 1005 and the second edge 1006; the sample inlet chamber 111, the first sample quantitative chamber 112, the mixing chamber 115, the distribution chamber 116, and the second overflow chamber 119 are arranged in sequence between the first edge 1005 and the second edge 1006. Specifically, the first edge 1005 is the inner edge of the non-circular chip body 110, and the second edge 1006 is the outer edge of the non-circular chip body 110. The diluent inlet chamber 113, the diluent quantitative chamber 114, the mixing chamber 115, the distribution chamber 116, and the first overflow chamber 118 are arranged in sequence from the inner edge to the outer edge. The sample inlet chamber 111, the first sample quantitative chamber 112, the mixing chamber 115, the distribution chamber 116, and the second overflow chamber 119 are also arranged in sequence from the inner edge to the outer edge. In this way, it is beneficial to ensure that the microfluidic chip When the sheet 100 is centrifugally rotated, the sample in the injection chamber 111 can enter the first sample quantitative chamber 112 and the second overflow chamber 119 under the action of centrifugation, the sample in the diluent chamber 113 can enter the diluent quantitative chamber 114 and the first overflow chamber 118 under the action of centrifugation, the sample in the first sample quantitative chamber 112 can enter the mixing chamber 115 under the action of centrifugation, the diluent in the diluent quantitative chamber 114 can enter the mixing chamber 115 under the action of centrifugation, and the mixed liquid in the mixing chamber 115 enters the distribution chamber 116 under the action of centrifugation.

As an embodiment, the second sample quantitative chamber 105 is arranged on the side of the first sample quantitative chamber 112 facing the second edge 1006, that is, the second sample quantitative chamber 105 is arranged between the first sample quantitative chamber 112 and the second edge 1006 along the direction of the first edge 1005 toward the second edge 1006. In this way, it is beneficial to ensure that the larger mass part of the sample can preferentially enter the second sample quantitative chamber 105 under the action of centrifugation, thereby facilitating the centrifugal stratification of the sample. For example, the red blood cells in the whole blood sample enter the second sample quantitative chamber 105 under the action of centrifugation, and the plasma in the whole blood sample enters the first sample quantitative chamber 112 under the action of centrifugation.

As an embodiment, the reaction detection chamber 117 is arranged on the side of the distribution chamber 116 toward the second edge 1006, that is, the reaction detection chamber 117 is arranged between the distribution chamber 116 and the second edge 1006 along the direction of the first edge 1005 toward the second edge 1006. In this way, it is helpful to ensure that the mixed liquid in the distribution chamber 116 can enter the reaction detection chamber 117 under the action of centrifugation.

1, 3 and 8, as an embodiment, the non-circular chip body 110 further includes a third edge 1007 and a fourth edge 1008; the third edge 1007 and the fourth edge 1008 are arranged opposite to each other at intervals, the third edge 1007 extends from one end of the first edge 1005 to one end of the second edge 1006, and the fourth edge 1008 extends from the other end of the first edge 1005 to the other end of the second edge 1006; the diluent inlet chamber 113, the diluent quantitative chamber 114, one end of the mixing chamber 115, one end of the distribution chamber 116, and the first overflow chamber 118 are arranged in sequence along the third edge 1007; the sample injection chamber 111, the first sample quantitative chamber 112, and the second overflow chamber 119 are arranged in sequence along the fourth edge 1008. The third edge 1007 and the fourth edge 1008 are two side edges of the non-circular chip body 110 in the circumferential direction. In this embodiment, the sample-related cavities are arranged along one side edge of the non-circular chip body 110, and the diluent-related cavities are arranged along the other side edge of the non-circular chip body 110, which is beneficial to optimize the layout of each cavity and improve the structural compactness of the microfluidic chip 100.

As an embodiment, the length of the second edge 1006 is greater than the length of the first edge 1005, that is, the length of the outer edge of the microfluidic chip 100 is greater than the length of the inner edge. The third edge 1007 and the fourth edge 1008 extend from the second edge 1006 to the first edge 1005 with a trend of gradually decreasing spacing. With this arrangement, when multiple microfluidic chips 100 are combined along the circumferential direction, each adjacent two microfluidic chips 100 can be arranged more closely. Of course, in a specific application, as an alternative embodiment, the length of the second edge 1006 can also be equal to the length of the first edge 1005.

As an embodiment, the first edge 1005 and the second edge 1006 are two concentric arc edges. In this embodiment, the microfluidic chip 100 is a fan-shaped structure, the first edge 1005 and the second edge 1006 are both arc-shaped and concentric, and the third edge 1007 and the fourth edge 1008 extend from the second edge 1006 to the first edge 1005 with a gradually decreasing spacing.

1, 3 and 8, as an embodiment, the angle A formed by the third edge 1007 and the fourth edge 1008 is greater than 0° and less than or equal to 90°, that is, the center angle A of the non-circular chip body 110 is between 0° and 90°. By adopting the layout of the cavities on the non-circular chip body 110, the center angle of the non-circular chip body 110 can be designed to be less than or equal to 90°, so that the volume of the non-circular chip body 110 is relatively small, which is conducive to reducing the cost and unnecessary waste of re-inspection using the microfluidic chip 100.

As an implementation manner, the included angle A formed by the third edge 1007 and the fourth edge 1008 is 60°±15°, that is, the central angle A of the non-circular chip body 110 is between 60°±15°.

As an implementation mode, the angle A formed by the third edge 1007 and the fourth edge 1008 is 60°, that is, the central angle A of the non-circular chip body 110 is 60°, so that six non-circular chip bodies 110 can be combined to form a complete circular chip structure.

As an embodiment, the number of reaction detection chambers 117 formed by the non-circular chip body 110 is less than or equal to six, so that the volume of a single microfluidic chip 100 can be relatively small, and the number of reaction detection chambers 117 on a single microfluidic chip 100 is also relatively small. When a single microfluidic chip 100 is used for re-inspection, the cost of the microfluidic chip 100 can be reduced, and the waste of samples, diluents and reagents can be reduced.

As an embodiment, the number of reaction detection chambers 117 formed by the non-circular chip body 110 is three, so that the need for retesting with a single microfluidic chip 100 can be well met, and waste of samples, diluents and reagents can be avoided very well. Of course, in specific applications, the number of reaction detection chambers 117 formed by the non-circular chip body 110 can also be two, three, four, five, etc.

1 , 3 and 8 , as an embodiment, the non-circular chip body 110 has a first plate surface 1009 and a second plate surface 1010 that are arranged opposite to each other, and the injection chamber 111, the first sample quantitative chamber 112, the diluent inlet chamber 113, the diluent quantitative chamber 114, the mixing chamber 115, the distribution chamber 116, the reaction detection chamber 117, the first overflow chamber 118 and the second overflow chamber 119 are all recessed from the first plate surface 1009 toward the second plate surface 1010, and are all spaced apart from the second plate surface 1010, that is, the injection chamber 111, the first sample quantitative chamber 112, the diluent inlet chamber 113, the diluent quantitative chamber 114, the mixing chamber 115, the distribution chamber 116, the reaction detection chamber 117, the first overflow chamber 118 and the second overflow chamber 119 are not arranged to penetrate along the thickness direction of the non-circular chip body 110, that is, these chambers are all concave cavity structures similar to blind holes.

1, 3 and 8, as an embodiment, the microfluidic chip 100 further includes a sealing film 120, which is attached to the first plate surface 1009 to at least cover the injection chamber 111, the first sample quantitative chamber 112, the diluent inlet chamber 113, the diluent quantitative chamber 114, the mixing chamber 115, the distribution chamber 116, the reaction detection chamber 117, the first overflow chamber 118 and the second overflow chamber 119. The sealing film 120 is mainly used to seal and protect the injection chamber 111, the first sample quantitative chamber 112, the diluent inlet chamber 113, the diluent quantitative chamber 114, the mixing chamber 115, the distribution chamber 116, the reaction detection chamber 117, the first overflow chamber 118 and the second overflow chamber 119.

As an embodiment, the second sample quantitative cavity 105 is also recessed from the first plate surface 1009 toward the second plate surface 1010, and there is a gap between the second plate surface 1010, that is, the second sample quantitative cavity 105 is not set through the thickness direction of the non-circular chip body 110, that is, the second sample quantitative cavity 105 is a concave cavity structure similar to a blind hole. The sealing film 120 also covers the second sample quantitative cavity 105.

1, 2 and 8, as an embodiment, the sealing film 120 is provided with a sample injection hole 121 at a position corresponding to the injection chamber 111, and the sample injection hole 121 is connected to the injection chamber 111 for injecting the sample into the injection chamber 111. The sample to be tested can be injected into the injection chamber 111 from the sample injection hole 121 to achieve sample addition. Of course, the sample injection hole 121 can also be temporarily manufactured after the sample is injected into the injection chamber 111.

1, 2 and 8, as an embodiment, the sealing film 120 is provided with a diluent injection hole 122 at a position corresponding to the diluent inlet cavity 113, and the diluent injection hole 122 is connected to the diluent inlet cavity 113, so as to allow the diluent to be injected into the diluent cavity 113. In this embodiment, the diluent is injected into the diluent cavity 113 from the diluent injection hole 122; of course, in a specific application, as an alternative embodiment, a diluent bag may be placed in the diluent inlet cavity 113, and when the diluent is needed, the diluent in the diluent bag flows into the diluent inlet cavity 113 by pressing or puncturing.

Referring to FIG. 1 , FIG. 2 and FIG. 8 , as an embodiment, the sealing film 120 is also provided with a first vent 123, and the first vent 123 is connected to the diluent overflow channel 103. Since the diluent overflow channel 103 is respectively connected to the diluent quantitative chamber 114 and the first overflow chamber 118 and the diluent judgment chamber 102, and the first overflow chamber 118 is connected to the distribution chamber 116, when the diluent is quantitatively measured, the gas in the diluent quantitative chamber 114 and the gas in the diluent judgment chamber 102 can be discharged from the first vent 123; when the mixed liquid is distributed, the gas in the distribution chamber 116 and the reaction detection chamber 117 can also be discharged from the first vent 123. In this embodiment, the diluent quantitative chamber 114 and the distribution chamber 116 share the vent, which is conducive to reducing the number of vents, thereby simplifying the structure of the microfluidic chip 100.

1, 2 and 8, as an embodiment, the sealing film 120 is further provided with a second vent hole 124, which is in communication with the sample overflow channel 104. Since the sample overflow channel 104 is in communication with the first sample quantitative chamber 112, the second overflow chamber 119 and the sample judgment chamber 101 respectively, and the first sample quantitative chamber 112 is in communication with the second sample quantitative chamber 105, when the sample is quantitatively measured, the gas in the first sample quantitative chamber 112, the gas in the second sample quantitative chamber 105 and the gas in the sample judgment chamber 101 can be discharged from the second vent hole 124.

1 , 5 and 8 , as an embodiment, the sealing film 120 is further provided with a third vent hole 125 , which is in communication with the mixing chamber 115 . When the sample and the diluent are mixed, the gas in the mixing chamber 115 can be discharged from the third vent hole 125 .

As an implementation, the microfluidic chip 100 is used for the detection of blood samples, that is, the sample added to the injection chamber 111 is a blood sample. Of course, in specific applications, the microfluidic chip 100 can also be used for the detection of other samples, such as urine samples.

As an implementation mode, the microfluidic chip 100 is used for the detection of whole blood samples, plasma samples or serum samples, that is, the microfluidic chip 100 can simultaneously meet the detection requirements of whole blood samples, plasma samples and serum samples, and has a wide range of applications.

8, 10 and 11, the present embodiment further provides a microfluidic analysis system, which includes a turntable 200, an optical detection assembly 300, a rotation drive mechanism 400 and the above-mentioned microfluidic chip 100, the turntable 200 is used to load at least one microfluidic chip 100, the rotation drive mechanism 400 is used to drive the turntable 200 to drive the microfluidic chip 100 to rotate, and the optical detection assembly 300 is used to perform optical detection on the sample in the reaction detection chamber 117. Since the microfluidic analysis system adopts the above-mentioned microfluidic chip 100, the number of microfluidic chips 100 loaded can be customized according to the detection requirements, thereby helping to avoid the waste of microfluidic chips 100, samples, reagents and diluents, and during the detection process, the operator only needs to add samples and diluents, and the operation is simple and convenient.

As an embodiment, the turntable 200 is formed with a plurality of accommodating positions distributed in sequence along the circumferential direction, and each accommodating position is used to accommodate a microfluidic chip 100 or a counterweight component with the same outer contour and the same weight as the microfluidic chip 100. The arrangement of the counterweight component is mainly used to ensure the balance of the microfluidic chip 100 after it is installed on the turntable 200. For example, if only one microfluidic chip 100 is needed to meet the detection requirements, a counterweight component can be configured, and the counterweight component and the microfluidic chip 100 are symmetrically arranged on the turntable 200.

9, 10 and 11, as an embodiment, the optical detection assembly 300 includes a light emitting element 310 and a light receiving element 320. The light emitting element 310 is disposed above the turntable 200 to at least irradiate light toward the sample in the reaction detection chamber 117; the light receiving element 320 is disposed below the turntable 200 and is located directly below the light emitting element 310 to receive the light irradiated by the light emitting element 310 through the microfluidic chip 100; the rotation drive mechanism 400 is used to drive the turntable 200 to drive the microfluidic chip 100 to rotate, so as to respectively realize: quantification of the sample and the diluent, mixing of the sample and the diluent, distribution of the mixed liquid, and rotating the reaction detection chamber 117 to directly below the light receiving element 320. Specifically, the rotary drive mechanism 400 first drives the turntable 200 to drive the microfluidic chip 100 to perform the first centrifugal rotation to achieve quantification of the sample and the diluent; then drives the turntable 200 to drive the microfluidic chip 100 to perform the second centrifugal rotation to achieve mixing of the sample and the diluent; then drives the turntable 200 to drive the microfluidic chip 100 to perform the third centrifugal rotation to achieve distribution of the mixed liquid; finally drives the turntable 200 to drive the microfluidic chip 100 to rotate so that each reaction detection chamber 117 rotates in turn to the bottom of the light receiving element 320 for detection.

As an embodiment, the turntable 200 is formed with six accommodating positions distributed in sequence along the circumferential direction, each microfluidic chip 100 is a structure with a central angle of 60°, and the counterweight component is also a structure with a central angle of 60°. The turntable 200 can carry six microfluidic chips 100 for detection at one time, or the turntable 200 can also carry five microfluidic chips 100 and a counterweight component for detection at one time; or the turntable 200 can also carry four symmetrically arranged microfluidic chips 100 for detection at one time; or the turntable 200 can also carry three microfluidic chips 100 and a counterweight component for detection at one time; or the turntable 200 can also carry two symmetrically arranged microfluidic chips 100 for detection at one time; or the turntable 200 can also carry one microfluidic chip 100 and a counterweight component for detection at one time.

As an implementation mode, when the turntable 200 carries two or more microfluidic chips 100 for detection at one time, the samples in the two microfluidic chips 100 can be samples from the same patient or samples from different patients.

As an embodiment, the microfluidic analysis system also includes a controller 500, which is electrically connected to the optical detection component 300 and the rotation drive mechanism 400, respectively. The controller 500 is used to control the rotation drive mechanism 400 to drive the turntable 200 to rotate and stop, and is used to parse the detection data according to the feedback information of the optical detection component 300.

As an embodiment, the time length that the rotary drive mechanism 400 drives the turntable 200 to rotate during the quantification stage of the sample and the diluent is greater than the time length that the rotary drive mechanism 400 drives the turntable 200 to rotate during the mixing stage of the sample and the diluent, and is greater than the time length that the rotary drive mechanism 400 drives the turntable 200 to rotate during the mixed liquid distribution stage.

As an implementation mode, the microfluidic chip 100 and the microfluidic analysis system provided in this embodiment can be applied to the detection of animal samples, and can also be applied to the detection of human samples.

As an implementation method, the workflow of using the microfluidic analysis system provided in this embodiment to perform sample detection is as follows:

(1) First step: As shown in FIG. 2 , a certain amount (e.g., 20 ul to 50 ul) of sample (whole blood sample, plasma sample, or serum sample) is added into the injection chamber 111 from the sample injection hole 121, and a certain amount (e.g., 50 ul to 100 ul) of diluent is added into the diluent chamber 113 from the diluent injection hole 122.

(2) Step 2: Referring to FIG. 2, FIG. 3 and FIG. 9, the rotating disk 200 is driven to rotate at a first preset speed (e.g., a speed between 3000 rpm and 6000 rpm) for a first preset time (e.g., 3 min to 5 min) to make the sample in the injection chamber 111 flow into the first sample quantitative chamber 112 and the second sample quantitative chamber 105, and the excess sample flows into the second overflow chamber 119. At the same time, the gas in the first sample quantitative chamber 112, the second sample quantitative chamber 105 and the second overflow chamber 119 is discharged from the second vent 124. In addition, the optical detection component 300 can be used to determine whether there is liquid in the sample determination chamber 101. If there is liquid, it can be determined that the sample volume is sufficient, otherwise it is determined that the sample volume is insufficient. If the sample is a whole blood sample, in the later stage of the whole blood sample centrifugation process, the plasma will be concentrated in the first sample quantitative chamber 112, and the red blood cells will be concentrated in the second sample quantitative chamber 105.

While the sample is quantified, the diluent in the diluent chamber 113 flows into the diluent quantification chamber 114, and the excess diluent flows into the diluent determination chamber 102 and the first overflow chamber 118. At the same time, the gas originally in the diluent quantification chamber 114, the diluent determination chamber 102 and the first overflow chamber 118 is discharged from the first vent 123. The optical detection component 300 can be used to determine whether there is liquid in the diluent determination chamber 102. If there is liquid, it can be determined that the diluent is sufficient, otherwise it is determined that the diluent is insufficient.

In the later stage of the second step of the rotation centrifugation process, the plasma enters the sample drainage capillary 107, and due to the outward centrifugal force, the sample can only stay at position _a1 . Similarly, the diluent enters the diluent drainage capillary 108, and the diluent can only stay at position _b1 .

(3) Step 3: As shown in FIG. 3 , FIG. 4 and FIG. 9 , the rotating disk 200 stops rotating, the centrifugal force disappears, and the plasma in the sample drainage capillary 107 fills the sample drainage capillary 107 under the capillary force, and the plasma moves to the position _a2 of the sample drainage capillary 107. Similarly, the diluent fills the diluent drainage capillary 108, and the diluent moves to the position _b2 of the diluent drainage capillary 108.

(4) In the fourth step, as shown in FIG. 4 , FIG. 5 and FIG. 9 , the turntable 200 is rotated at a second preset speed (e.g., a speed between 3000 rpm and 5000 rpm, the second preset speed may be less than or equal to or greater than the first preset speed) for a second preset time (e.g., 10 sec to 60 sec, the second preset time is preferably less than the first preset time). The plasma in the first sample quantitative chamber 112 flows into the mixing chamber 115 through the sample drainage capillary 107 under the action of siphon. Similarly, the diluent in the diluent quantitative chamber 114 flows into the mixing chamber 115 through the diluent drainage capillary 108, and the gas in the mixing chamber 115 is discharged from the third vent 125. The turntable 200 mixes the diluent and the plasma under the action of fast acceleration and slow deceleration. Due to the outward centrifugal force, the mixed liquid can only stay at the _c1 position of the mixed liquid drainage capillary 109.

(5) Step 5: Referring to FIGS. 5 , 6 and 9 , the turntable 200 stops rotating, the centrifugal force disappears, the mixed liquid in the mixed liquid drainage capillary 109 fills the mixed liquid drainage capillary 109 , and the mixed liquid moves to the c ₂ position of the mixed liquid drainage capillary 109 .

(6) Step 6: As shown in FIG. 6, FIG. 7 and FIG. 9, the turntable 200 is centrifuged at a third preset speed (e.g., 3000 rpm to 5000 rpm, the third preset speed may be less than or equal to or greater than the first preset speed) for a third preset time (e.g., 10 sec to 60 sec, the third preset time is preferably less than the first preset time). The mixed liquid in the mixing chamber 115 flows from the mixed liquid drainage capillary 109 into the distribution chamber 116, and the initial liquid entering the distribution chamber 116 from the mixed liquid drainage capillary 109 will preferentially enter the initial liquid chamber 1001, which is mainly used to load the unmixed liquid in the mixed liquid drainage capillary 109. The mixed liquid then flows into the reaction detection chamber 117, and the excess mixed liquid in the distribution chamber 116 flows into the second overflow chamber 119, while the gas in the original distribution chamber 116 and the reaction detection chamber 117 is discharged from the second vent 124 through the diluent overflow channel 103. The freeze-dried ball reagent contained in the reaction detection chamber 117 can react with the mixed solution, and the detection of different items can be completed by optical signal collection.

The microfluidic chip 100 provided in this embodiment can make it unnecessary to add diluents and samples in a quantitative manner, and the microfluidic chip 100 can simultaneously meet the detection of different types of samples such as whole blood, plasma, and serum. In specific operations, the operator only needs to take samples within a certain range and diluents within a certain range and add them to the microfluidic chip 100 to complete the operation. The operation is very simple and convenient, and the sample amount used is small and the quantitative measurement is accurate. Each microfluidic chip 100 constitutes a sub-disc that can be independently partitioned and independently detected. Multiple microfluidic chips 100 can be freely combined for detection, and the operator can customize the microfluidic chip 100 that needs to be re-tested, which is conducive to reducing the cost of re-testing and the waste of unnecessary consumables.

Embodiment 2:

1 , 8 and 12 , the microfluidic chip 100 and the microfluidic analysis system provided in this embodiment are different from those in Embodiment 1 mainly in that the shape of the microfluidic chip 100 is different, specifically, the microfluidic chip 100 in Embodiment 1 is fan-shaped; whereas the microfluidic chip 100 in this embodiment is trapezoidal.

As an implementation mode, in this embodiment, the first edge 1005 and the second edge 1006 are two parallel linear edges, and the third edge 1007 and the fourth edge 1008 extend from the second edge 1006 to the first edge 1005 with a gradually decreasing spacing. In this implementation mode, the microfluidic chip 100 is a trapezoidal structure.

Of course, in specific applications, the shape of the microfluidic chip 100 is not limited to fan-shaped and trapezoidal. For example, as an alternative embodiment, the microfluidic chip 100 can also be a rectangular structure. In this alternative embodiment, the first edge 1005 and the second edge 1006 are also two parallel straight edges, and the third edge 1007 and the fourth edge 1008 extend from the second edge 1006 to the first edge 1005 with a constant spacing.

Except for the above differences, other parts of the microfluidic chip 100 and the microfluidic analysis system provided in this embodiment can refer to the first embodiment and will not be described in detail here.

Embodiment three:

1 , 8 and 13 , the microfluidic chip 100 and the microfluidic analysis system provided in this embodiment are different from those in the first embodiment mainly in that the overflow chamber is set differently, specifically: in the first embodiment, the overflow of the diluent and the overflow of the mixed liquid share the overflow chamber, and the sample overflow chamber is independently set; whereas in the present embodiment, the overflow of the sample and the overflow of the mixed liquid share the overflow chamber, and the overflow chamber of the diluent is independently set.

As an implementation mode, in this embodiment, the non-circular chip body 110 is formed with a sample injection chamber 111, a first sample quantitative chamber 112, a diluent inlet chamber 113, a diluent quantitative chamber 114, a mixing chamber 115, a distribution chamber 116, a reaction detection chamber 117, a third overflow chamber 1011 and a fourth overflow chamber 1012; the third overflow chamber 1011 is connected to the diluent quantitative chamber 114 to collect the diluent overflowing from the diluent quantitative chamber 114; the fourth overflow chamber 1012 is connected to the first sample quantitative chamber 112 and the distribution chamber 116 respectively to collect the sample overflowing from the first sample quantitative chamber 112 and the mixed solution overflowing from the distribution chamber 116. In this embodiment, the sample injection chamber 111, the first sample quantitative chamber 112, the diluent inlet chamber 113, the diluent quantitative chamber 114, the mixing chamber 115, the distribution chamber 116 and the reaction detection chamber 117 are arranged in the same manner and principle as in the first embodiment, and will not be described in detail here. In the present embodiment, since the fourth overflow chamber 1012 is used for collecting samples overflowing from the first sample quantification chamber 112 and for collecting the mixed liquid overflowing from the distribution chamber 116, it is equivalent to combining the overflow chamber for sample quantification and the overflow chamber for the mixed liquid into one, which can also help to reduce the number of overflow chambers, and further help to simplify the structure of the microfluidic chip 100 and improve the structural compactness of the microfluidic chip 100, which can ultimately facilitate the miniaturized design of the microfluidic chip 100.

Except for the above differences, other parts of the microfluidic chip 100 and the microfluidic analysis system provided in this embodiment can refer to the first embodiment or the second embodiment, and will not be described in detail here.

The above description is only a preferred embodiment of the present application, and does not limit the patent scope of the present application. All equivalent structural changes made by using the contents of the present application specification and drawings under the inventive concept of the present application, or directly/indirectly applied in other related technical fields are included in the patent protection scope of the present application.

Claims

A microfluidic chip, characterized in that: it comprises a non-circular chip body, wherein the non-circular chip body is formed with a sample injection cavity, a first sample quantitative cavity, a diluent inlet cavity, a diluent quantitative cavity, a mixing cavity, a distribution cavity, a reaction detection cavity, a first overflow cavity and a second overflow cavity;

The injection chamber is used to store samples entering the microfluidic chip;

The first sample quantification chamber is in communication with the injection chamber, so as to quantify the sample from the injection chamber when the microfluidic chip is centrifuged;

The diluent inlet chamber is used to store the diluent entering the microfluidic chip;

The diluent quantitative chamber is in communication with the diluent inlet chamber, so as to quantitatively measure the diluent from the diluent inlet chamber when the microfluidic chip is centrifugally rotated;

The mixing chamber is communicated with the first sample quantitative chamber and the diluent quantitative chamber respectively, so as to receive and mix the sample entering from the first sample quantitative chamber and the diluent entering from the diluent quantitative chamber when the microfluidic chip is centrifuged;

The distribution chamber is communicated with the mixing chamber and the reaction detection chamber respectively, so as to receive a mixed solution formed by mixing a sample and a diluent from the mixing chamber when the microfluidic chip is centrifuged, and distribute the mixed solution to the reaction detection chamber;

The reaction detection chamber is used for the reagent to react with the mixed solution to form a sample;

The first overflow chamber is communicated with the diluent quantitative chamber and the distribution chamber respectively, so as to collect the diluent overflowing from the diluent quantitative chamber and the mixed liquid overflowing from the distribution chamber;

The second overflow chamber is communicated with the first sample quantitative chamber to collect the sample overflowing from the first sample quantitative chamber.
The microfluidic chip according to claim 1, characterized in that: the non-circular chip body is further formed with a sample judgment cavity, the sample judgment cavity is connected to the second overflow cavity, so as to allow the optical detection component to detect whether there is a sample overflowing from the first sample quantitative cavity;

The distance from the sample judgment chamber to the central axis of rotation of the microfluidic chip during centrifugal rotation is the same as the distance from the reaction detection chamber to the central axis of rotation of the microfluidic chip during centrifugal rotation.
The microfluidic chip according to claim 2, characterized in that: the non-circular chip body is further formed with a diluent judgment chamber, the diluent judgment chamber is connected to the first overflow chamber, so as to allow the optical detection component to detect whether there is diluent overflowing from the diluent quantitative chamber;

The distance from the diluent determination chamber to the central axis of rotation of the centrifugal rotation of the microfluidic chip is the same as the distance from the reaction detection chamber to the central axis of rotation of the centrifugal rotation of the microfluidic chip.
The microfluidic chip as described in claim 3 is characterized in that: the distance from the diluent judgment chamber to the central axis of rotation of the microfluidic chip centrifugally rotated is greater than the distance from the first overflow chamber to the central axis of rotation of the microfluidic chip centrifugally rotated.
The microfluidic chip as described in claim 3 or 4 is characterized in that: the sample judgment chamber and the diluent judgment chamber are respectively located on both sides of the reaction detection chamber pair along the direction of centrifugal rotation of the microfluidic chip.
The microfluidic chip according to any one of claims 1 to 4 is characterized in that: the non-circular chip body also forms a first channel and a second channel, the two ends of the first channel are respectively connected to the distribution chamber and the first overflow chamber, the two ends of the second channel are respectively connected to the distribution chamber and the reaction detection chamber, and the width of the first channel in the centrifugal rotation direction of the microfluidic chip is equal to the width of the second channel in the centrifugal rotation direction of the microfluidic chip.
The microfluidic chip according to any one of claims 1 to 4, characterized in that: the non-circular chip body has a first plate surface and a second plate surface arranged opposite to each other, the sample injection chamber, the first sample quantitative chamber, the diluent inlet chamber, the diluent quantitative chamber, the mixing chamber, the distribution chamber, the reaction detection chamber, the first overflow chamber and the second overflow chamber are all recessed from the first plate surface toward the second plate surface, and are spaced apart from the second plate surface;

The microfluidic chip further comprises a sealing film, which is attached to the first plate surface to at least cover the sample injection chamber, the first sample quantitative chamber, the diluent inlet chamber, the diluent quantitative chamber, the mixing chamber, the distribution chamber, the reaction detection chamber, the first overflow chamber and the second overflow chamber;

The sealing film is provided with a sample injection hole at a position corresponding to the injection cavity, and the sample injection hole is communicated with the injection cavity so as to allow the sample to be injected into the injection cavity.
The microfluidic chip according to claim 7, characterized in that: the sealing film is provided with a diluent injection hole at a position corresponding to the diluent inlet cavity, and the diluent injection hole is connected to the diluent inlet cavity for injecting the diluent into the diluent inlet cavity; or,

A diluent bag is placed in the diluent inlet cavity.
The microfluidic chip according to claim 7, characterized in that: the non-circular chip body is further formed with a diluent overflow channel and a sample overflow channel, the diluent overflow channel is connected between the diluent quantitative chamber and the first overflow chamber, and the sample overflow channel is connected between the first sample quantitative chamber and the second overflow chamber;

The sealing film is also penetrated by a first vent hole, a second vent hole and a third vent hole, the first vent hole is communicated with the diluent overflow channel, the second vent hole is communicated with the sample overflow channel, and the third vent hole is communicated with the mixing chamber.
The microfluidic chip according to any one of claims 1 to 4, characterized in that: the non-circular chip body is further formed with a second sample quantitative cavity, a sample quantitative channel and a sample drainage capillary, and the two ends of the sample quantitative channel are respectively connected to the first sample quantitative cavity and the second sample quantitative cavity;

The distance from the sample quantitative channel to the central axis of rotation of the microfluidic chip is greater than the distance from the first sample quantitative cavity to the central axis of rotation of the microfluidic chip, and less than the distance from the second sample quantitative cavity to the central axis of rotation of the microfluidic chip;

The two ends of the sample drainage capillary are respectively connected to the sample quantitative pipeline and the mixing chamber, and the sample drainage capillary has a first bending portion, and the distance from the first bending portion to the rotation center axis of the centrifugal rotation of the microfluidic chip is smaller than the distance from the first sample quantitative chamber to the rotation center axis of the centrifugal rotation of the microfluidic chip.
The microfluidic chip according to any one of claims 1 to 4, characterized in that: the non-circular chip body is further formed with a mixed liquid drainage capillary and an initial liquid cavity;

The two ends of the mixed liquid drainage capillary are respectively connected to the mixing chamber and the distribution chamber, and the mixed liquid drainage capillary has a second bending portion, and the distance from the second bending portion to the rotation center axis of the centrifugal rotation of the microfluidic chip is smaller than the distance from the mixing chamber to the rotation center axis of the centrifugal rotation of the microfluidic chip;

The initial liquid chamber is in communication with one end of the distribution chamber close to the mixed liquid drainage capillary, so as to at least collect the initial liquid entering the distribution chamber from the mixed liquid drainage capillary;

The distance from the initial liquid chamber to the central axis of rotation of the microfluidic chip during centrifugal rotation is smaller than the distance from the reaction detection chamber to the central axis of rotation of the microfluidic chip during centrifugal rotation.
The microfluidic chip according to claim 11, characterized in that: the volume of the initial liquid chamber is smaller than the volume of the reaction detection chamber; and/or,

The non-circular chip body also forms a second channel and a third channel, the two ends of the second channel are respectively connected to the distribution chamber and the reaction detection chamber, the two ends of the third channel are respectively connected to the distribution chamber and the initial liquid chamber, and the width of the third channel in the centrifugal rotation direction of the microfluidic chip is equal to the width of the second channel in the centrifugal rotation direction of the microfluidic chip.
The microfluidic chip according to claim 1, characterized in that: the non-circular chip body comprises a first edge and a second edge, the first edge and the second edge are arranged opposite to each other at a distance, the first edge is arranged at an end of the microfluidic chip close to the central axis of rotation of the microfluidic chip centrifugally, and the second edge is arranged at an end of the microfluidic chip away from the central axis of rotation of the microfluidic chip centrifugally;

The diluent inlet chamber, the diluent quantitative chamber, the mixing chamber, the distribution chamber, and the first overflow chamber are sequentially arranged between the first edge and the second edge;

The injection chamber, the first sample quantitative chamber, the mixing chamber, the distribution chamber, and the second overflow chamber are sequentially arranged between the first edge and the second edge.
The microfluidic chip as described in claim 13 is characterized in that the length of the second edge is greater than the length of the first edge.
The microfluidic chip according to claim 13, wherein: the first edge and the second edge are two concentric arc edges; or

The first edge and the second edge are two straight line edges parallel to each other.
The microfluidic chip according to any one of claims 13 to 15, characterized in that: the non-circular chip body further includes a third edge and a fourth edge;

The third edge is spaced apart from the fourth edge and arranged opposite to each other. The third edge extends from one end of the first edge to one end of the second edge, and the fourth edge extends from the other end of the first edge to the other end of the second edge.

The diluent inlet chamber, the diluent quantitative chamber, one end of the mixing chamber, one end of the distribution chamber, and the first overflow chamber are arranged in sequence along the third edge;

The injection chamber, the first sample quantitative chamber, and the second overflow chamber are arranged in sequence along the fourth edge.
The microfluidic chip according to claim 16, characterized in that: the angle formed by the third edge and the fourth edge is greater than 0° and less than or equal to 90°.
The microfluidic chip as described in claim 17 is characterized in that: the angle formed by the third edge and the fourth edge is 60°±15°.
The microfluidic chip according to any one of claims 1 to 4 or any one of claims 13 to 15 is characterized in that the number of the reaction detection cavities formed by the non-circular chip body is less than or equal to six.
The microfluidic chip as described in claim 19 is characterized in that the number of the reaction detection cavities formed by the non-circular chip body is two, three, four or five.
A microfluidic chip, characterized in that: it comprises a non-circular chip body, wherein the non-circular chip body is formed with a sample injection cavity, a first sample quantitative cavity, a diluent inlet cavity, a diluent quantitative cavity, a mixing cavity, a distribution cavity, a reaction detection cavity, a third overflow cavity and a fourth overflow cavity;

The first sample quantification chamber is in communication with the injection chamber, so as to quantify the sample from the injection chamber when the microfluidic chip is centrifuged;

The diluent quantitative chamber is in communication with the diluent inlet chamber, so as to quantitatively measure the diluent from the diluent inlet chamber when the microfluidic chip is centrifugally rotated;

The mixing chamber is communicated with the first sample quantitative chamber and the diluent quantitative chamber respectively, so as to receive and mix the sample entering from the first sample quantitative chamber and the diluent entering from the diluent quantitative chamber when the microfluidic chip is centrifuged;

The distribution chamber is communicated with the mixing chamber and the reaction detection chamber respectively, so as to receive a mixed solution formed by mixing a sample and a diluent from the mixing chamber when the microfluidic chip is centrifuged, and distribute the mixed solution to the reaction detection chamber;

The reaction detection chamber is used for the reagent to react with the mixed solution to form a sample;

The third overflow chamber is in communication with the diluent quantitative chamber, so as to collect the diluent overflowing from the diluent quantitative chamber;

The fourth overflow chamber is communicated with the first sample quantitative chamber and the distribution chamber respectively, so as to collect the sample overflowing from the first sample quantitative chamber and the mixed liquid overflowing from the distribution chamber.
A microfluidic analysis system, characterized in that it comprises a turntable, an optical detection component, a rotation drive mechanism and the microfluidic chip according to any one of claims 1 to 21;

The turntable is formed with a plurality of accommodating positions distributed in sequence along the circumferential direction, each of the accommodating positions is used to accommodate one of the microfluidic chips or a counterweight component having the same outer contour and the same weight as the microfluidic chip;

The optical detection assembly includes a light emitting element and a light receiving element, wherein the light emitting element is disposed above the rotating disk to at least irradiate light toward the sample in the reaction detection chamber;

The light receiving element is disposed below the rotating disk and directly below the light emitting element, so as to receive the light emitted by the light emitting element through the microfluidic chip;

The rotary drive mechanism is used to drive the turntable to drive the microfluidic chip to rotate, so as to respectively achieve: quantification of samples and diluents, mixing of samples and diluents, distribution of mixed solutions, and rotation of the reaction detection chamber to directly below the light receiving element.