阅读说明：本技术 一种微流控芯片及其制备方法与应用 (Microfluidic chip and preparation method and application thereof ) 是由 陈龙胜 许为康 邹丽丽 刘海信 龚尧 于 2021-05-31 设计创作，主要内容包括：本发明公开了一种微流控芯片及其制备方法与应用,该微流控芯片包括基底层；检测层,所述检测层设于所述基底层表面,所述检测层中设有微流通道；进样条,所述进样条设于所述基底层与所述检测层之间,所述进样条与所述微流通道相交,所述进样条的数量至少为1个。本发明的微流控芯片仅用一路液驱控制即实现了至少一个样本的生化检测,简化了微流控芯片并降低了其液驱控制要求。(The invention discloses a micro-fluidic chip and a preparation method and application thereof, wherein the micro-fluidic chip comprises a substrate layer; the detection layer is arranged on the surface of the substrate layer, and a micro-flow channel is arranged in the detection layer; and the sample feeding strips are arranged between the basal layer and the detection layer and are intersected with the microfluidic channel, and the number of the sample feeding strips is at least 1. The micro-fluidic chip of the invention realizes the biochemical detection of at least one sample by only one path of liquid drive control, simplifies the micro-fluidic chip and reduces the liquid drive control requirement.)

1. A microfluidic chip, characterized in that: comprises that

A base layer;

the detection layer is arranged on the surface of the substrate layer, and a micro-flow channel is arranged in the detection layer;

and the sample feeding strips are arranged between the basal layer and the detection layer and are intersected with the microfluidic channel, and the number of the sample feeding strips is at least 1.

2. A microfluidic chip according to claim 1, wherein: the composition materials of the substrate layer and the detection layer are independently selected from the following materials: one of glass, quartz, polycarbonate, cyclic olefin copolymer, cyclic olefin polymer, polyester, PMMA, PS, PEEK, and PDMS; the composition materials of the substrate layer and the detection layer are the same or different.

3. A microfluidic chip according to claim 1, wherein: the combination mode of the substrate layer and the detection layer comprises bonding, adhesion and mechanical combination; preferably, the bonding is thermocompression bonding; preferably, the adhesive is epoxy resin, UV glue or hot melt adhesive; preferably, the substrate layer and the detection layer are provided with screw holes matched with each other, and the substrate layer and the detection layer are mechanically combined through bolts; preferably, the substrate layer and the detection layer are connected by a clamp to achieve the mechanical bonding.

4. A microfluidic chip according to claim 1, wherein: the microfluidic channel is a spiral microfluidic channel or a radial microfluidic channel.

5. A microfluidic chip according to claim 4, wherein: a liquid outlet and a liquid inlet are formed in the detection layer; preferably, the radial microfluidic channel takes the liquid inlet as a focus and is radially formed into a branch outwards; the number of branches is at least 2; more preferably, when the microfluidic channel is a spiral microfluidic channel, one end of the spiral microfluidic channel is a liquid inlet, and the other end of the spiral microfluidic channel is a liquid outlet.

6. A microfluidic chip according to claim 1, wherein: the material of the feed strip is one of nitrocellulose and polyester.

7. A microfluidic chip according to claim 1, wherein: the thickness of the sample entering strip is less than 50 μm; preferably, the thickness of the sample strip is 10 μm to 30 μm.

8. A method of preparing a microfluidic chip according to any of claims 1 to 7, wherein: the method comprises the following steps: and combining the substrate layer, the sample inlet strip and the detection layer to obtain the microfluidic chip.

9. Use of a microfluidic chip according to any of claims 1 to 7 in multi-sample detection.

10. A method of multi-sample detection, comprising: the method comprises the following steps:

s1, contacting the sample with the exposed end of the sample entering bar;

s2, adding a detection reagent from the liquid inlet, wherein the detection reagent reacts with the sample; and detecting after the reaction.

Technical Field

The invention relates to the technical field of chemical analysis, in particular to a micro-fluidic chip and a preparation method and application thereof.

Background

Bio/chemical detection (biochemical detection for short) is mostly based on biochemical reaction of a liquid or gas phase sample with a sensitive substance in a detector, thereby obtaining a signal output correlated to the sample concentration. Biochemical assays generally require the ability to simultaneously detect multiple samples for the purpose of detecting multiple different samples or performing multiple parallel assays on the same sample. With the increasing demand of field instant detection in outdoor, home and the like, the current biochemical detection usually adopts a miniaturized and portable scheme based on a microfluidic chip, and in the related technology, multi-sample detection usually means multi-channel microchannel and multi-channel independent liquid drive (such as a compression bar, a micropump and the like).

Therefore, it is required to develop a microfluidic chip which has a simple structure and low requirements for liquid driving control.

Disclosure of Invention

In order to solve the problems in the prior art, the invention provides a microfluidic chip which is simple in structure and low in liquid drive control requirement.

The invention also provides a preparation method of the microfluidic chip.

The invention also provides application of the microfluidic chip.

In a first aspect of the invention, there is provided a microfluidic chip comprising

A base layer;

the detection layer is arranged on the surface of the substrate layer, and a micro-flow channel is arranged in the detection layer;

and the sample feeding strips are arranged between the basal layer and the detection layer and are intersected with the microfluidic channel, and the number of the sample feeding strips is at least 1.

The microfluidic chip disclosed by the invention is a single flow channel, does not need a liquid storage and reaction chamber structure, and is simple in structure.

According to some embodiments of the invention, the constituent materials of the substrate layer and the detection layer are each independently selected from the group consisting of: one of glass, quartz, polycarbonate, cyclic olefin copolymer, cyclic olefin polymer, polyester, PMMA (polymethyl methacrylate), PS (polystyrene material), PEEK (polyether ether ketone), and PDMS (polydimethylsiloxane); the composition materials of the substrate layer and the detection layer are the same or different.

According to some embodiments of the invention, the bonding of the substrate layer and the detection layer comprises bonding, adhesion and mechanical bonding.

According to some embodiments of the invention, the bonding is a thermocompression bonding.

According to some embodiments of the invention, the adhesive is epoxy, UV glue or hot melt glue.

According to some embodiments of the invention, the base layer and the detection layer are provided with matching screw holes, and the base layer and the detection layer are mechanically coupled by bolts.

According to some embodiments of the invention, the substrate layer and the detection layer are joined by a collar to achieve the mechanical bond.

According to some embodiments of the invention, the microfluidic channel is a spiral microfluidic channel or a radial microfluidic channel.

According to some embodiments of the invention, the detection layer is provided with a liquid outlet and a liquid inlet.

According to some embodiments of the present invention, when the microfluidic channel is a spiral microfluidic channel, one end of the spiral microfluidic channel is a liquid inlet, and the other end of the spiral microfluidic channel is a liquid outlet.

According to some embodiments of the invention, the spiral microfluidic channel has at least 2 turns.

The parallel test is realized based on the cross dot matrix of the microfluidic channel and the sample inlet strip, so that the contingency of a single test is avoided. One spiral ring and the sample feeding strip are crossed once to carry out one-time detection, and more than 2 spiral rings are crossed with the sample feeding strip to realize multiple parallel tests.

According to some embodiments of the invention, the radial microfluidic channel is focused at the liquid inlet and is radially branched outwards; the number of branches is at least 2.

According to some embodiments of the present invention, when the microfluidic channel is a radial microfluidic channel, the liquid inlet is connected to a focal end of the radial microfluidic channel, and the liquid outlet is connected to a non-focal end of the radial microfluidic channel.

One branch and the sample injection strip are crossed once to carry out one-time detection, and more than 2 branches are crossed with the sample injection strip to realize multiple parallel tests.

According to some embodiments of the invention, the spline is a hydrophilic material.

According to some embodiments of the invention, the hydrophilic material has a water contact angle of less than 90 °.

According to some embodiments of the invention, the hydrophilic material has a water contact angle of 60 ° to 90 °

According to some embodiments of the invention, the constituent material of the sample strip is one of nitrocellulose and polyester.

The sample feeding strip has the requirement on the wettability of the material and is easy to absorb and store the solution.

According to some embodiments of the invention, the number of exit ports is at least 1.

According to some embodiments of the invention, the thickness of the spline is less than 50 μm; preferably, the thickness of the sample strip is 10 μm to 30 μm.

The bonding effect is influenced by the excessively high thickness of the sample inlet strip, so that the solution can leak from the chip; the thickness is too thin, and the amount of absorbed sample liquid is small, so that the signal is weak and difficult to detect.

According to some embodiments of the invention, the intersection of the spline with the microfluidic channel is at least two points.

According to some embodiments of the invention, the intersection angle of the spline with the microfluidic channel is perpendicular or non-perpendicular.

A second aspect of the present invention provides a method for manufacturing a microfluidic chip, including the steps of: and combining the substrate layer, the sample injection strip layer and the detection layer to obtain the microfluidic chip.

A third aspect of the present invention provides a microfluidic chip for use in multi-sample detection.

A fourth aspect of the present invention provides a method of multi-sample detection, comprising the steps of:

s1, contacting the sample with the exposed end of the sample entering bar;

s2, adding a detection reagent from the liquid inlet, wherein the detection reagent reacts with the sample; and detecting after the reaction.

According to some embodiments of the invention, the reaction in step S2 comprises a color reaction or a luminescence reaction.

The invention has at least the following beneficial effects: the microfluidic chip disclosed by the invention is of a sandwich structure formed by the substrate layer, the sample inlet strip and the detection layer in sequence, sample introduction is realized through the exposed end of the sample inlet strip, and additional structures such as a reagent storage cavity and the like are not needed; meanwhile, the micro-channel and the sample feeding strip form a cross lattice structure, so that the chip has the effect of realizing biochemical detection of at least one sample by one-way liquid drive, the micro-fluidic chip is simplified, and the liquid drive control requirement of the micro-fluidic chip is reduced. In the application, the reagent reaction and the signal detection process are continuous, the detection process is more flexible, and the reflected information is more complete; compared with the prior art (such as a centrifugal driving chip), each link in the related technology needs to be carried out step by step, the obtained detection signal is a terminal signal after a period of reaction, for instantaneous color development or luminescence reaction, a sample is contacted with a reaction liquid to generate a signal immediately, detection is carried out after the chip completely stops rotating, a detection window is easily missed, or information of key nodes such as reaction starting, acceleration, saturation and fading is lost. In the application, a parallel test formed by a plurality of intersection points of the sample inlet strips and the microfluidic channels is provided for each sample, so that the contingency caused by a single test is avoided.

Drawings

FIG. 1 is a flow chart of multi-sample detection according to an embodiment of the present invention;

FIG. 2 is a schematic structural diagram of a microfluidic chip in example 1 of the present invention;

FIG. 3 is a schematic structural diagram of a microfluidic chip in example 2 of the present invention;

FIG. 4 is a schematic structural diagram of a microfluidic chip in example 3 of the present invention;

FIG. 5 shows the result of multi-sample multi-parallel assay in example 1 of the present invention;

FIG. 6 shows the result of multi-sample multi-parallel assay in example 2 of the present invention;

FIG. 7 shows the results of multiple parallel single-sample assays in example 3 of the present invention.

Reference numerals:

1. a base layer; 2. a circular advancing spline; 21. feeding a sample I; 22. feeding a sample strip II; 23. feeding a sample bar III; 3. a detection layer; 31. a sample inlet; 32. a microfluidic channel; 33. a liquid outlet; 34. exposing the holes.

Detailed Description

The concept and technical effects of the present invention will be clearly and completely described below in conjunction with the embodiments to fully understand the objects, features and effects of the present invention. It is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all embodiments, and those skilled in the art can obtain other embodiments without inventive effort based on the embodiments of the present invention, and all embodiments are within the protection scope of the present invention.

The microfluidic chip in an embodiment of the present invention includes:

a base layer;

the detection layer is arranged on the surface of the substrate layer, a micro-flow channel is arranged in the detection layer, one end of the micro-flow channel is connected with the liquid inlet, and the other end of the micro-flow channel is connected with the liquid outlet;

a sample inlet strip provided between the base layer and the detection layer, the sample inlet strip intersecting the microfluidic channel, the number of sample inlet strips being at least 1;

the basal layer, the sample feeding strip and the detection layer are sequentially stacked to form the sealed microfluidic chip with a sandwich structure.

The substrate layer and the detection layer are made of one of the following materials; glass, quartz, Polycarbonate (PC), Cyclic Olefin Copolymer (COC), Cyclic Olefin Polymer (COP), Polyester (PET), Polymethylmethacrylate (PMMA), Polystyrene (PS), Polyetheretherketone (PEEK), and Polydimethylsiloxane (PDMS).

The materials of the substrate layer and the detection layer are the same or different.

The basal layer and the detection layer are tightly combined together, and the self-absorption sample introduction strip is clamped between the basal layer and the detection layer; the combination mode is one of bonding (hot-press bonding), bonding (the adhesive is epoxy resin, UV adhesive and EVA hot melt adhesive) or mechanical locking (screws or clamps).

The detection layer comprises a liquid inlet, at least one liquid outlet and a micro-flow channel communicated with the liquid inlet and the liquid outlet, and the micro-flow channel comprises a spiral micro-flow channel or a radial micro-flow channel; the spiral microfluidic channel at least comprises 2 complete spiral rings, and the radial microfluidic channel at least comprises 2 branches radiating outwards from the center.

The parallel test is realized through the cross dot matrix of the microfluidic channel and the sample inlet strip, so that the contingency of a single test is avoided. One spiral ring and the sample feeding strip are crossed once to carry out one-time detection, and more than 2 spiral rings are crossed with the sample feeding strip to realize multiple parallel tests.

One branch and the sample injection strip are crossed once to carry out one-time detection, and more than 2 branches are crossed with the sample injection strip to realize multiple parallel tests. The self-imbibing sample strip is in a thin sheet shape or a ring shape, and the material is a nitrocellulose membrane (NC membrane) or a polyester membrane.

Self-aspirating splines have hydrophilic properties (static water contact angle less than 90 °), and tend to absorb aqueous solutions that would otherwise be difficult to reach the detection zone by self-aspiration.

When the self-sucking sample strip is in a thin and long sheet shape, one end of the self-sucking sample strip is exposed in the air and used for receiving a sample solution to be detected, and the other end of the self-sucking sample strip is clamped between the substrate and the upper cover and intersected with the microfluidic channel and used for guiding the sample to be detected to react with a reagent in the microfluidic channel.

When the self-suction sample strip is annular, the detection layer is also provided with an exposed hole, one end of the self-suction sample strip is exposed in the air by the exposed hole and used for receiving the sample solution to be detected, and the other end of the self-suction sample strip is clamped between the substrate and the upper cover and is intersected with the microfluidic channel and used for guiding the sample to be detected to react with the reagent in the microfluidic channel.

The number of the sample feeding strips is at least one, each self-suction sample feeding strip is intersected with the micro-flow channel by at least two points, and the intersection angle is vertical or not vertical.

The thickness of the self-absorption sample strip is 10-30 μm, the bonding effect is influenced when the thickness is too high, so that the solution leaks from the chip, and the amount of the absorbed sample solution is small when the thickness is too thin, so that the signal is weak and difficult to detect.

The microfluidic chip in the embodiment of the invention is used for multi-sample detection, and the detection process is shown in figure 1 and comprises the following steps:

s1, preparing a sample solution to be detected;

s2, dropwise adding the solution of the sample to be detected to respective suction sample strips;

s3, introducing reaction liquid into the microfluidic channel from the liquid inlet after the sample strips are respectively sucked to absorb the liquid to be detected to saturation;

s4, carrying out color development or luminescence reaction on the reaction liquid and the sample to be detected at the cross dot matrix;

and S5, after the reaction is finished, signal acquisition and processing are carried out, and then the multi-sample detection is finished.

Example 1

The present embodiment is a microfluidic chip, and the structure is shown in fig. 2: the method comprises the following steps:

a base layer 1;

a detection layer 3, wherein the detection layer 3 is arranged on the surface of the substrate layer 1, a microfluidic channel 32 is arranged in the detection layer 3, and the microfluidic channel 32 is a spiral microfluidic channel; one end of the spiral microfluidic channel is connected to the liquid inlet 31, and the other end is connected to the liquid outlet 33.

The microfluidic channel 32 contains 4 spiral rings.

A sample feeding strip I21, a sample feeding strip II 22 and a sample feeding strip III 23 are arranged between the substrate layer 1 and the detection layer 3, and the sample feeding strip I21, the sample feeding strip II 22 and the sample feeding strip III 23 are intersected with the microfluidic channel 32. Wherein the substrate layer 1 is a glass layer; the detection layer 3 is a PDMS layer; the sample inlet strip I21, the sample inlet strip II 22 and the sample inlet strip III 23 are all nitrocellulose membranes (NC membranes), the thickness is 30 mu m, and the static water contact angle is 70 degrees.

The combination mode of the substrate layer 1 and the detection layer 3 is thermal compression bonding after plasma surface treatment: firstly, placing the surfaces of a substrate layer 1 and a detection layer 3 to be bonded in a Plasma cleaner (Harrick Plasma company, USA, model is PDC-002) chamber, vacuumizing for 5 minutes, then starting the Plasma for surface treatment for 2 minutes, taking out, placing a sample injection strip I21, a sample injection strip II 22 and a sample injection strip III 23 between two bonding surfaces of the substrate layer 1 and the detection layer 3, aligning and clamping, and placing at 90 ℃ for pressure maintaining and annealing for 30 minutes to complete bonding.

A multi-sample multi-time parallel detection method comprises the following steps:

s1, dissolving horseradish peroxidase freeze-dried powder (Shanghai Aladdin Biotechnology Co., Ltd., model P105528) in phosphate buffer (1x PBS, pH 7.4) to prepare 3 parts of horseradish peroxidase solution with the concentration of 10 mu g/mL, and sequentially dripping 10 mu L of horseradish peroxidase solution to exposed ends of a self-priming sample injection strip I21, a self-priming sample injection strip II 22 and a self-priming sample injection strip III 23 through a liquid transfer gun; horseradish peroxidase solution was well absorbed to saturation from the imbibed strip over 10 minutes.

S2, adding undiluted stock solutions of BeyoECL MoonA and BeyoECL MoonB of a chemiluminescence detection reagent (Shanghai Binyun biotech Co., Ltd., model number BeyoECL Moon) with luminol as a substrate according to the volume ratio of 1: 1, pumping the mixture into a spiral flow channel of the microfluidic chip from a liquid inlet 31 through a micro-injection pump, and sequentially flowing through cross nodes of a self-absorption sample introduction strip I21, a self-absorption sample introduction strip II 22 and a self-absorption sample introduction strip III 23 to react.

And S3, collecting a luminescence signal through a CCD detector (charge coupled device detector) under the condition of avoiding light, and finishing detection.

Example 2

The present embodiment is a microfluidic chip, and the structure is shown in fig. 3: the method comprises the following steps:

a base layer 1;

a detection layer 3, wherein the detection layer 3 is arranged on the surface of the substrate layer 1, a microfluidic channel 32 is arranged in the detection layer 3, and the microfluidic channel 32 is a spiral microfluidic channel; one end of the spiral microfluidic channel is connected to the liquid inlet 31, and the other end is connected to the liquid outlet 33.

The spiral microfluidic channel contains 4 spiro rings.

A sample inlet strip I21 and a sample inlet strip II 22 are provided between the base layer 1 and the detection layer 3, and the sample inlet strip I21 and the sample inlet strip II 22 intersect with the spiral microfluidic channel.

Wherein the substrate layer 1 is a quartz glass layer; the detection layer 3 is a PDMS layer; the sample inlet strip I21 and the sample inlet strip II 22 are both nitrocellulose membranes (NC membranes), the thickness is 20 μm, and the static water contact angle is 70 degrees.

The combination mode of the substrate layer 1 and the detection layer 3 is thermal compression bonding after plasma surface treatment: firstly, placing the surfaces of a substrate layer 1 and a detection layer 3 to be bonded in a cavity of a Plasma cleaner (Harrick Plasma company, USA, model is PDC-002) for vacuumizing for 5 minutes, then starting the Plasma for surface treatment for 2 minutes, taking out the sample strip I21 and the sample strip II 22, placing the sample strip I21 and the sample strip II 22 between two bonding surfaces of the substrate layer 1 and the detection layer 3 for aligning and clamping, and placing the substrate layer 1 and the detection layer 3 at 90 ℃ for pressure maintaining and annealing for 30 minutes to complete bonding.

A multi-sample multi-time parallel detection method comprises the following steps:

s1, dissolving horseradish peroxidase freeze-dried powder (Shanghai Aladdin Biotechnology Co., Ltd., model P105528) in common phosphate buffer (1x PBS, pH 7.4) to prepare 2 parts of horseradish peroxidase solution with the concentration of 50 mug/mL, and sequentially dripping 10 mug of horseradish peroxidase solution to the exposed ends of a self-priming sample injection strip I21 and a self-priming sample injection strip II 22 through a pipette gun; horseradish peroxidase solution was well absorbed to saturation from the imbibed strip over 10 minutes.

S2, non-diluted stock solutions of BeyoECL Moon a and BeyoECL Moon b in a luminol-based chemiluminescent assay reagent (model No. BeyoECL Moon, supplied by shanghai bi yunnan biotechnology limited) at a volume ratio of 1: 1, pumping the mixture into a spiral flow channel of the microfluidic chip from a liquid inlet 31 through a micro-injection pump, and sequentially flowing through cross nodes of a self-absorption sample introduction strip I21 and a self-absorption sample introduction strip II 22 to react.

And S3, collecting a luminescence signal through a CCD detector (charge coupled device detector) under the condition of avoiding light, and finishing detection.

Example 3

The present embodiment is a microfluidic chip, and the structure is shown in fig. 4:

the method comprises the following steps:

a base layer 1;

a detection layer 3, wherein the detection layer 3 is arranged on the surface of the substrate layer 1, a microfluidic channel 32 is arranged in the detection layer 3, and the microfluidic channel 32 is an emission microfluidic channel; the radiation microfluidic channel has one end connected to the liquid inlet 31 and the other end connected to the liquid outlet 33.

The radiation microfluidic channel consists of 3 branches.

The circular advancing spline 2 is provided between the base layer 1 and the detection layer 3, and the circular advancing spline 2 intersects with the microfluidic channel 32.

The detection layer 3 is further provided with an exposure hole 34.

The exposed holes 34 provide exposed ends for the looped entry splines 2. Wherein the substrate layer 1 is a glass layer of polymethyl methacrylate (PMMA); the detection layer 3 is a PDMS layer; the self-imbibing specimens were polyester films with a thickness of 25 μm and a static water contact angle of 75 °.

The substrate layer 1 and the detection layer 3 are bonded by epoxy resin.

A single-sample multi-time parallel detection method comprises the following steps:

s1, dissolving horseradish peroxidase freeze-dried powder (provided by Shanghai Aladdin Biotechnology Co., Ltd., model P105528) in common phosphate buffer (1x PBS, pH 7.4), preparing a horseradish peroxidase solution with the concentration of 100 mu g/mL, and dripping 10 mu L of horseradish peroxidase solution through a liquid transfer gun to an exposed hole of the detection layer to be contacted with the annular self-priming sample injection strip; horseradish peroxidase solution was well absorbed to saturation from the imbibed strip over 10 minutes.

S2, non-diluted stock solutions of BeyoECL Moon a and BeyoECL Moon b in a luminol-based chemiluminescent assay reagent (model No. BeyoECL Moon, supplied by shanghai bi yunnan biotechnology limited) at a volume ratio of 1: 1, pumping the mixture into a radial flow channel of the microfluidic chip from a liquid inlet through a micro-injection pump, and respectively flowing through cross nodes of the sample strips which are annularly and automatically sucked to react.

And S3, collecting a luminescence signal through a CCD detector (charge coupled device detector) under the condition of avoiding light, and finishing detection.

The detection results in the embodiments 1 to 3 of the present invention are shown in fig. 5 to 7, and it can be seen from fig. 5 to 6 that: in the embodiment 1 and the embodiment 2 of the invention, multiple parallel biochemical detections of multiple samples are realized only by one-way liquid drive control; from fig. 7 it can be seen that: in the embodiment 3 of the invention, multiple parallel biochemical detections of a single sample are realized by only one path of liquid drive control, and the test results of the embodiments 1 to 3 show that the invention realizes multiple parallel biochemical detections of at least one sample by only one path of liquid drive control, simplifies the microfluidic chip and reduces the liquid drive control requirements of the microfluidic chip.

In conclusion, the micro-fluidic chip disclosed by the invention has the advantages that the sandwich structure is formed by the substrate layer, the sample inlet strip and the detection layer in sequence, the sample introduction is realized through the exposed end of the sample inlet strip, and additional structures such as a reagent storage cavity and the like are not needed; meanwhile, the micro-channel and the sample inlet strip form a cross lattice structure, so that the chip has the effect of realizing multi-sample biochemical detection by one-way liquid drive, the micro-fluidic chip is simplified, and the liquid drive control requirement of the micro-fluidic chip is reduced. According to the invention, the reagent reaction and the signal detection process are continuous, the detection process is more flexible, and the reflected information is more complete; compared with the prior art that each link is required to be carried out step by step (such as a centrifugal drive chip), the obtained detection signal is a terminal signal after a period of reaction, for instantaneous color development or luminescence reaction, a sample is contacted with a reaction liquid to generate a signal immediately, detection is carried out after the chip completely stops rotating, a detection window is easily missed, or information of key nodes such as reaction starting, acceleration, saturation, fading and the like is lost. In the invention, for each sample, a parallel test formed by a plurality of intersection points of the strip and the flow channel is provided, so that the contingency caused by a single test is avoided.

While the embodiments of the present invention have been described in detail with reference to the description and the drawings, the present invention is not limited to the embodiments, and various changes can be made without departing from the gist of the present invention within the knowledge of those skilled in the art. Furthermore, the embodiments of the present invention and the features of the embodiments may be combined with each other without conflict.