CN219984717U - Microfluidic chip with annular reaction channel, microfluidic device and apparatus - Google Patents

Abstract

The present disclosure relates to microfluidic chips with annular reaction channels and microfluidic devices and equipment. The microfluidic chip includes a sampling port, a sampling channel connected to the sampling port, a capillary pump connected to the sampling channel, and a reaction unit. The reaction unit includes: a ring-shaped reaction channel connected to the sampling channel via a sampling channel. The channel includes a photo-induced deformation material so that the microfluid can be driven through the reaction channel under the action of the Laplace pressure difference generated by the asymmetric photo-induced deformation of the reaction channel; a connecting structure is connected to the reaction channel at one end and remains connected to the reaction channel at the other end. The atmosphere is connected, so that the sample microfluid can self-close the connected structure after entering the connected structure, in which the connection point of the sampling channel and the reaction channel and the connection point of the reaction channel and the connected structure are spaced apart from each other, and the cross-sectional area of the sampling channel is larger than the reaction The cross-sectional area of the channel is larger than the cross-sectional area of the connecting structure and the cross-sectional area of the sampling channel, and the depth of the reaction channel is larger than the depth of the sampling channel.

Description

Microfluidic chip with circular reaction channel and microfluidic device and equipment

Technical field

The present disclosure relates to the field of microfluidic technology, and more specifically, to a microfluidic chip, a microfluidic device and a microfluidic device.

Background technique

Microfluidics can integrate complex microfluidic operations such as sample preparation, reaction, separation, and detection in biological, chemical, and medical analysis processes onto a chip of more than ten square centimeters, so that the entire analysis process can be automatically completed, with It has many advantages such as high degree of integration and large processing throughput. In traditional microfluidic chips, in order to achieve the measurement of micro-samples, complex fluid channels need to be designed, and externally powered pump and valve components are also required to drive and control fluid movement. Not only is the structure complex, the operation is cumbersome, and it is difficult to implement Portability is also because the fluid driven by such a pump and valve assembly must be in a continuous state and needs to fill the entire front channel to complete the back-end measurement operation, so the sample loss is large. Therefore, current microfluidic chips based on externally powered pump and valve components cannot yet achieve true measurement of micro-samples.

Utility model content

The following provides a brief summary of the disclosure in order to provide a basic understanding of some aspects of the disclosure. It should be understood, however, that this summary is not an exhaustive overview of the disclosure. It is not intended to identify key or critical portions of the disclosure or to delineate the scope of the disclosure. The purpose is merely to present some concepts about the disclosure in a simplified form as a prelude to the more detailed description that is presented later.

According to an aspect of the present disclosure, a microfluidic chip is provided, the microfluidic chip includes a microfluidic unit, the microfluidic unit includes: a sampling port configured to receive sample microfluid; a channel configured to communicate with the injection port to receive the sample microfluidic from the injection port; a capillary pump configured to communicate with the injection channel to draw the sample microfluidic through and out of the injection channel; and one or more reactions unit, each reaction unit includes: a reaction channel arranged in an annular manner, configured to communicate with the sampling channel between the injection port and the capillary pump via the sampling channel corresponding to the reaction unit to receive the sample from the injection channel. A preset volume of sample microfluid corresponding to the reaction unit, wherein the reaction channel includes a photo-induced deformation material so that the microfluid can be driven through the reaction channel under the action of the Laplace pressure difference generated by asymmetric photo-induced deformation of the reaction channel, The first communication structure is configured to communicate with the reaction channel at one end and maintain communication with the atmosphere at the other end, so that the sample microfluid can self-close the first communication structure after entering the first communication structure from the sample separation channel through the reaction channel, wherein, The first connection point of the sample separation channel and the reaction channel and the second connection point of the reaction channel and the first communication structure are spaced apart from each other along the longitudinal center line of the reaction channel, wherein the cross-sectional area of the sampling channel is larger than the cross-section of the reaction channel area, the cross-sectional area of the reaction channel is greater than the cross-sectional area of the first connecting structure, the cross-sectional area of the reaction channel is greater than the cross-sectional area of the sampling channel, and the depth of the reaction channel is greater than the depth of the sampling channel.

According to another aspect of the present disclosure, a microfluidic device is provided, the microfluidic device comprising a microfluidic chip according to an embodiment of the present disclosure and configured to provide illumination to the microfluidic chip to A light source that controls the movement of microfluidic fluid in the microfluidic chip.

According to yet another aspect of the present disclosure, a microfluidic device is provided, including: a light control module, the light control module including a light source configured to provide illumination to a microfluidic chip to control the microfluidic controlling the movement of the microfluid in the microfluidic chip, the microfluidic in the microfluidic chip being photodriven; and a moving module configured to move the microfluidic chip to adjust the microfluidic The relative position of the control chip and the light source is such that the microfluidic chip is selectively and locally illuminated by the light source, so that the microfluid in the microfluidic chip is photodriven, wherein the light control chip The module is fixed above the mobile module.

Other features and advantages of the present disclosure will become more apparent from the following detailed description of exemplary embodiments of the present disclosure with reference to the accompanying drawings.

Description of the drawings

The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments of the disclosure and, together with the description, serve to explain principles of the disclosure. The embodiments set forth in the drawings are illustrative and exemplary in nature and are not intended to limit the disclosure. The following detailed description of exemplary embodiments may be clearly understood when read in conjunction with the following drawings, in which like structures are designated with like reference numerals, and in which:

1 to 5 are schematic diagrams illustrating microfluidic chips according to some embodiments of the present disclosure;

6 is a schematic diagram illustrating a non-limiting example process of photo-driving microfluidics in a microfluidic chip according to embodiments of the present disclosure;

7-10 are schematic diagrams illustrating microfluidic devices according to some embodiments of the present disclosure;

Figure 11 is a schematic diagram illustrating a microfluidic device according to some embodiments of the present disclosure;

Figure 12 is a schematic diagram showing a mobile module of the microfluidic device shown in Figure 11;

FIG. 13 is a schematic diagram showing the light control module of the microfluidic device shown in FIG. 11 .

Detailed ways

Various exemplary embodiments of the present disclosure will be described in detail below with reference to the accompanying drawings. It should be noted that the relative arrangement of components and steps, numerical expressions, and numerical values set forth in these examples do not limit the scope of the disclosure unless otherwise specifically stated.

The following description of at least one exemplary embodiment is merely illustrative in nature and is in no way intended to limit the disclosure, its application or uses. That is, the structures and methods herein are shown in an exemplary manner to illustrate different embodiments of the structures and methods in the present disclosure. However, those skilled in the art will understand that they are merely illustrative of exemplary ways in which the disclosure may be practiced, and are not exhaustive. Furthermore, the drawings are not necessarily to scale and some features may be exaggerated to illustrate details of particular components.

In addition, techniques, methods and devices known to those of ordinary skill in the relevant art may not be discussed in detail, but where appropriate, such techniques, methods and devices should be considered a part of the specification.

In all examples shown and discussed herein, any specific values are to be construed as illustrative only and not as limiting. Accordingly, other examples of the exemplary embodiments may have different values.

In one aspect, the present disclosure provides a microfluidic chip, which can drive fluid through the Laplace pressure difference (capillary force) generated by a capillary pump, thereby enabling contactless measurement of trace samples. Since the microfluidic chip according to the present disclosure does not require the use of externally powered pump and valve components to drive fluid, it has low requirements on fluid continuity, low sample loss, and the number of components and the overall volume of the microfluidic chip and its supporting equipment are also small. . Microfluidic chips according to various embodiments of the present disclosure will be described in detail below with reference to the accompanying drawings. It should be understood that an actual microfluidic chip may also include other components, but to avoid obscuring the gist of the present disclosure, these other components are not discussed herein and are not shown in the accompanying drawings. It should also be understood that the various embodiments may be combined with each other, but for simplicity of illustration, the drawings illustrate only some combinations of these embodiments.

Figure 1 illustrates a microfluidic chip 100 in accordance with some embodiments of the present disclosure. As shown in FIG. 1 , the microfluidic chip 100 includes a microfluidic unit 100U. The microfluidic unit 100U includes a sampling port 101 , a sampling channel 102 , a capillary pump 103 and reaction units 110A-110B. It should be understood that although FIG. 1 shows two reaction units, this is only illustrative and not limiting, and the microfluidic chip 100 may include one, two, three or more reactions according to specific needs. unit.

Inlet 101 is configured to receive sample microfluidic. The sampling channel 102 is configured to communicate with the sampling port 101 to receive the sample microfluid from the sampling port 101 . For example, the sample microfluid can be dropped at the inlet 101 to fill the inlet 101 and then extend into the inlet channel 102 for a certain distance. In this article, cross-section refers to the plane of width and depth, which is perpendicular to the direction of length. The planes illustrated in Figures 1 to 5 are those in which the widths and lengths lie, but it is noted that these figures are provided for illustrative purposes and are not necessarily drawn to scale. In some embodiments, the cross-sectional area of the injection port 101 may be greater than or equal to the cross-sectional area of the injection channel 102 . This may facilitate the spontaneous entry of the sample microfluid from the injection port 101 into the injection channel 102 . It should be understood that the present disclosure is not limited to dripping sample microfluidics into the inlet 101 . In some embodiments, the inlet 101 can also be connected to other channels, chambers, etc. on the microfluidic chip 100 to receive sample microfluid therefrom. For example, the sample inlet 101 can be connected to the pre-reaction unit to receive the sample microfluid that needs to be further processed after the reaction is completed.

Capillary pump 103 is configured in communication with sampling channel 102 to draw sample microfluidic fluid through and out of sampling channel 102 . The capillary pump 103 can generally be composed of a plurality of capillary channels, in which the cross-sectional area of each section is much smaller than the cross-sectional area of each channel of the microfluidic chip 100, and the ends of these capillary channels are configured to open to the atmosphere. open. Therefore, after the sample microfluid enters the sampling channel 102, it will be driven through the sampling channel 102 under the action of the Laplace pressure difference generated by the capillary pump 103 and is finally sucked away by the capillary pump 103. In some embodiments, for example as shown in FIG. 1 , the capillary pump 103 may include a plurality of microfluidic channels arranged in a tree-like arrangement. On the one hand, such a structure can effectively increase the capillary force generated by the capillary pump, and on the other hand, it can increase the amount of liquid that the capillary pump can accommodate, further improving the utilization rate of the microfluidic chip 100 . It should be understood that the illustrated structure of capillary pump 103 is provided merely to provide an illustrative example and is not intended to limit the present disclosure.

Each reaction unit includes a reaction channel and a first connecting structure. The reaction channels are arranged in a ring. In this article, the annular shape only requires that the channels are connected end to end, and there is no limit to the channel outline. The outline of the annular channel can be, for example, a polygon such as a triangle, a quadrilateral, a pentagon, a circle, an ellipse, and other suitable shapes. Shapes, such as the outline of annular reaction channels in the figures herein are illustrated without limitation as rectangles. The reaction channel is configured to communicate with the sampling channel between the sampling port and the capillary pump via a sampling channel corresponding to the reaction unit to receive a preset volume of sample microfluid corresponding to the reaction unit from the sampling channel. The reaction channel includes a photo-induced deformation material so that the microfluid can be driven (herein, also referred to as photo-driven) through the reaction channel (later The process of photo-driven microfluidics in this article will be described in detail in conjunction with Figure 6). The first communication structure is configured to communicate with the reaction channel at one end and maintain communication with the atmosphere at the other end, so that the sample microfluid can self-close the first communication structure after entering the first communication structure from the sample separation channel through the reaction channel. The first connection point of the sample separation channel and the reaction channel and the second connection point of the reaction channel and the first communication structure are spaced apart from each other along the longitudinal center line of the reaction channel. The longitudinal centerline of a reaction channel is a line passing through the center of each cross-section of the reaction channel along the length of the reaction channel. It should be understood that in this article, the distance between one point and another point and the symmetry point of one point with respect to another point mentioned later can be considered by hypothetically expanding the annular reaction channel into a straight line.

For example, as shown in FIG. 1 , the reaction unit 110A includes reaction channels 1041 arranged in an annular shape. The reaction channel 1041 is configured to communicate with the sampling channel 102 via the sampling channel 1051 between the sampling port 101 and the capillary pump 103 to receive a first preset volume of sample microfluid from the sampling channel 102 . The reaction channel 1041 includes a photodeformable material so that the microfluid can be driven through the reaction channel 1041 under the action of the Laplace pressure difference generated by the asymmetric photodeformation of the reaction channel 1041 . The reaction unit 110B includes reaction channels 1042 arranged in an annular shape. The reaction channel 1042 is configured to communicate with the sampling channel 102 between the sampling port 101 and the capillary pump 103 via the sampling channel 1052 to receive a second preset volume of sample microfluid from the sampling channel 102 . The reaction channel 1042 includes a photodeformable material such that the microfluid can be driven through the reaction channel 1042 under the action of the Laplace pressure difference generated by the asymmetric photodeformation of the reaction channel 1042 .

The reaction unit 110A also includes a first communication structure 1061, which is configured to communicate with the reaction channel 1041 at one end and maintain communication with the atmosphere at the other end, so that the sample microfluid enters the first communication structure 1061 from the sample separation channel 1051 via the reaction channel 1041. Finally, the first connection structure 1061 can be self-sealed. The reaction unit 110B also includes a first communication structure 1062 that is configured to communicate with the reaction channel 1042 at one end and remain in communication with the atmosphere at the other end, so that the sample microfluid enters the first communication structure 1062 from the sample separation channel 1052 via the reaction channel 1042 Finally, the first connection structure 1062 can be self-sealed.

The first connection point CP11 of the sample separation channel 1051 and the reaction channel 1041 and the second connection point CP21 of the reaction channel 1041 and the first communication structure 1061 are spaced apart from each other along the longitudinal center line of the reaction channel 1041. The first connection point CP12 of the sample separation channel 1052 and the reaction channel 1042 and the second connection point CP22 of the reaction channel 1042 and the first communication structure 1062 are spaced apart from each other along the longitudinal centerline of the reaction channel 1042.

In the microfluidic chip 100, the cross-sectional area of the sampling channel 102 is larger than the cross-sectional area of the reaction channels 1041-1042. In this way, the microfluid can be facilitated to enter the reaction channels 1041-1042 respectively from the sampling channel 102 under the action of the Laplace pressure difference. The cross-sectional area of the reaction channels 1041-1042 is larger than the cross-sectional area of the first communication structure 1061-1062. In this way, the microfluid can enter the first communication structures 1061-1062 from the reaction channels 1041-1042 respectively under the action of the Laplace pressure difference. The cross-sectional area of the reaction channels 1041-1042 is larger than the cross-sectional area of the sampling channels 1051-1052. The sampling channels 1051-1052 can be used as liquid bridges between the reaction channels 1041-1042 and the sampling channel 102.

Therefore, after the sample microfluid enters the sampling channel 102 from the sampling port 101, the sample microfluid will travel through the sampling channel 102 under the action of the Laplace pressure difference generated by the capillary pump 103, and when reaching each The connection point between the sampling channels 1051-1052 and the sampling channel 102 will pass through each channel under the action of the Laplace pressure difference generated because the cross-sectional area of the sampling channel 102 is larger than the cross-sectional area of the reaction channels 1041-1042. The sampling channels 1051-1052 enter the corresponding reaction channels 1041-1042.

When the sample microfluid enters the sampling channel 1051 (1052) and reaches the first connection point CP11 (CP12) of the sampling channel 1051 (1052) and the reaction channel 1041 (1042), the sample microfluid will flow from the first connection point CP11 (CP12) ) flows to both sides along the reaction channel 1041 (1042) (in Figure 1, clockwise and counterclockwise flow at the same time), and the gas originally inside the reaction channel 1041 (1042) can be discharged through the first communication structure 1061 (1062) . When the sample microfluid reaches the second connection point CP21 (CP22) between the reaction channel 1041 (1042) and the first connection structure 1061 (1062), the cross-sectional area of the reaction channel 1041 (1042) is larger than the first connection structure 1061. (1062) enters the first communication structure 1061 (1062) under the action of the Laplace pressure difference generated by the cross-sectional area of (1062). Once the sample microfluid enters the first communication structure 1061 (1062) with a small cross-sectional area, a liquid column will be formed to seal the first communication structure 1061 (1062). When the first communication structure 1061 (1062) is closed, the gas in the reaction channel 1041 (1042) can no longer be discharged from the first communication structure 1061 (1062), and the sample microfluid cannot overcome the reaction channel 1041 (1042). The air pressure continues to move sideways. Therefore, after the sample microfluid enters the reaction channel 1041 (1042) from the first connection point CP11 (CP12), it can move to both sides as far as the reaction between the first connection point CP11 (CP12) and the second connection point CP21 (CP22). The minimum distance of the longitudinal centerline of the channel 1041 (1042) (the minimum distance is the first distance between the first connection point and the second connection point along the first direction (for example, clockwise direction) of the longitudinal centerline of the reaction channel) and The minimum value of the second distance between the first connection point and the second connection point along the longitudinal centerline of the reaction channel in a second direction opposite to the first direction (for example, counterclockwise)), and fails to enter the reaction channel The sample microfluid of 1041 (1042) still remaining in the sampling channel 102 will be sucked away by the capillary pump 103, leaving the reaction channel 1041 between the second connection point CP21 (CP22) and the second connection point CP21 (CP22). A section of the sample microfluid between the symmetry point CP21' (CP22') on the longitudinal center line of (1042) with respect to the first connection point CP11 (CP12). It can be seen that such a measuring process is realized spontaneously under the action of Laplace pressure difference. It does not need to be driven by any externally powered pump valve assembly, nor does it require the sample microfluid to continuously fill the front reaction unit. Channel 110A-110B.

Through the above measuring process, a section of the sample microfluid between the second connection point CP21 and the symmetry point CP21' (via the first connection point CP11) can be maintained in the reaction unit 110A, while a section of the sample microfluid between the second connection point CP21 and the symmetry point CP21' (via the first connection point CP11) can be maintained in the reaction unit 110B. A section of sample microfluid between the second connection point CP22 and the symmetry point CP22' (via the first connection point CP12). The sampling channels 1051-1052 and the first communication structures 1061-1062 may be the thinnest channels in the microfluidic chip 100, and their volumes may be configured to be between CP21 and CP21' compared to the volume of the reaction channel 1041 and Reaction channel 1042 is negligible with respect to the volume between CP22 and CP22'. Therefore, the first preset volume of the sample microfluid measured by the reaction unit 110A may be substantially equal to the volume of the reaction channel 1041 between CP21 and CP21', which is based on the edge between the first connection point CP11 and the second connection point CP21. The second preset volume of the sample microfluid measured by the reaction unit 110B can be substantially equal to the reaction channel 1042 at CP22 and CP22' The volume between them is determined based on twice the minimum distance between the first connection point CP21 and the second connection point CP22 along the longitudinal centerline of the reaction channel 1042 and the cross-sectional area of the reaction channel 1042. In some embodiments, the reaction units 110A-110B are configured to receive the same preset volume of sample microfluidic from the sampling channel 102, for example as shown in Figure 1 (assuming the cross-sectional area of the reaction channels 1041-1042 in Figure 1 same). In other embodiments, the reaction units 110A-110B are configured to receive different preset volumes of sample microfluidics from the sampling channel 102, for example, as shown in Figure 3 (assuming that the cross-section of the reaction channels 1041-1042 in Figure 3 same area).

In addition, the depth of the reaction channels 1041-1042 may be greater than the depth of the sampling channels 1051-1052. Due to the depth difference between the sample separation channels 1051-1052 and the reaction channels 1041-1042, steps may be formed at the first connection points CP11-CP12 of the sample separation channels 1051-1052 and the reaction channels 1041-1042. In some embodiments, the difference between the depth of the sampling channels 1051-1052 and the depth of the reaction channels 1041-1042 may be configured to allow microfluidics in the reaction channels 1041-1042 to span the sampling channels 1051-1052 and the reaction channels 1041-1042. The first connection point CP11-CP12 of 1042 moves. Since the Laplace pressure difference generated by asymmetric photodeformation can advantageously overcome the flow resistance to drive the fluid in a straight-through pipeline with small flow resistance, the depth of the sampling channels 1051-1052 is different from the depth of the reaction channels 1041-1042 There needs to be a clear difference between them. If the depth of the sample separation channels 1051-1052 is close to the depth of the reaction channel 1041-1042, then the pipeline shape of the reaction channel 1041-1042 at the first connection point CP11-CP12 of the sample separation channel 1051-1052 and the reaction channel 1041-1042 (Close to the tee pipe) Compared with the reaction channels 1041-1042, the shape of the pipe (straight-through pipe) in the part other than the first connection point has changed significantly, which will lead to photoinduced distortion of the microfluidic in the reaction channels 1041-1042. The actuation is hindered from moving freely within the reaction channel 1041-1042 from one end across the first connection point to the other end. Further, in some examples, the ratio of the depth of the sampling channels 1051-1052 to the depth of the reaction channels 1041-1042 is less than 1:2. In some examples, the ratio of the depth of sampling channels 1051-1052 to the depth of reaction channels 1041-1042 is less than or equal to 1:4. When the ratio of the depth of the sampling channels 1051-1052 to the depth of the reaction channels 1041-1042 meets such a requirement, the first connection points CP11-CP12 of the sampling channels 1051-1052 and the reaction channels 1041-1042 can be reduced to the reaction channel 1041 Effects of microfluidic photoactuation within -1042. Similarly, in some embodiments, the difference between the depth of the first communication structures 1061 - 1062 and the depth of the reaction channels 1041 - 1042 may be configured to allow microfluidic flow across the first communication structures 1061 - 1042 in the reaction channels 1041 - 1042 The second connection points CP21-CP22 between 1062 and reaction channels 1041-1042 move. In some examples, the ratio of the depth of the first communication structures 1061-1062 to the depth of the reaction channels 1041-1042 is less than 1:2. In some examples, the ratio of the depth of the first communication structures 1061-1062 to the depth of the reaction channels 1041-1042 is less than or equal to 1:4. In some embodiments, the depth of the first communication structures 1061-1062 may be equal to the depth of the sampling channels 1051-1052. In some embodiments, a depth transition may be provided between the sampling channel 1051 (1052) and the reaction channel 1041 (1042) and/or between the first communication structure 1061 (1062) and the reaction channel 1041 (1042). Transition channel.

The dimensions of the depth and width of each channel included in the microfluidic chip 100 herein may be, for example, in the range of 10-10 ³ microns. In some embodiments, the width and depth of each of the sampling channel 102, the sampling channels 1051-1052, the reaction channels 1041-1042, and the first communication structures 1061-1062 are respectively between 10 microns and 2000 microns, For example, it can be between 50 microns and 1000 microns. Within this range, the processing difficulty of the microfluidic chip 100 is moderate, and the performance of the photodriven fluid is also better. In a non-limiting example, the width of the sampling channel 102 can be 300 microns and the depth can be 300 microns, the width of the reaction channels 1041-1042 can be 200 microns and the depth can be 200 microns, the sampling channels 1051-1052 and The width of the first connecting structure 1061-1062 can be 200 microns and the depth can be 50 microns. According to these dimensions, the impact of the fluid volume in the sampling channels 1051-1052 and the first connecting structure 1061-1062 on the measurement accuracy can be determined. Can be ignored. In some examples, the volume of reaction channel 1041 between CP21 and CP21' and the volume of reaction channel 1042 between CP22 and CP22' can be between 50 nanoliters and 1000 nanoliters, or between 100 nanoliters and 700 nanoliters. between liters. Since the volume of the reaction channel 1041 between CP21 and CP21' and the volume of the reaction channel 1042 between CP22 and CP22' can be very small, the measurement of such a preset volume of sample microfluid can be regarded as a simple and accurate trace. Take quantitative samples. However, those skilled in the art can understand that when specifically designing the volume of the reaction channel 1041 between CP21 and CP21' and the volume of the reaction channel 1042 between CP22 and CP22', they can be determined according to the specific usage scenario of the microfluidic chip 100. Sure.

It should be understood that the different cross-sectional areas of the channels designed above can be achieved by controlling the width of the channels to be the same and changing the depth of the channels, or by controlling the depth of the channels to be the same and changing the width of the channels, or by changing the channels at the same time. depth and width to achieve. In some cases, it may be preferable to achieve different cross-sectional areas of the channels by controlling the width of the channels to be the same and varying the depth of the channels. For example, when forming a channel through high-precision computerized numerical control (CNC) processing, it may be more convenient to control the width of the channel to be the same and change the depth of the channel.

1 and 6 , in some embodiments, the microfluidic chip 100 may include a substrate 10 on which an inlet 101 and a groove connected to the inlet 101 are provided, and a light source attached to the substrate 10 Deformation film 20 (for clarity of illustration, only the substrate 10 is shown in FIGS. 1 to 5 , and the photodeformation film 20 is not shown in FIGS. 1 to 5 ), the photodeformation film 20 is at least partially Covering the grooves and forming a closed channel 30 together with the grooves, the microfluid can be driven through the closed channel 30 under the action of the Laplace pressure difference generated by the asymmetric photodeformation of the closed channel 30 . Closed channel 30 may provide at least reaction channels 1041-1042. In some embodiments, the closed channel 30 may also provide other channels of the microfluidic chip 100 such as the sampling channel 102, the sample separation channels 1051-1052, the first communication structures 1061-1062, etc., but even if the upper surfaces of these other channels Formed by photodeformable films 20, when their upper surfaces do not undergo photodeformation, the fluid in them will not be photodriven. For example, grooves can be formed on the substrate 10 as the bottom surface and side surfaces of the closed channel 30 through CNC processing, and after the CNC processing is completed, the photodeformable film 20 is covered on the grooves as the upper surface of the closed channel 30 Thus a complete channel structure is obtained. In some embodiments, in order to reduce the difficulty of CNC machining and improve measurement accuracy, the cross-sectional shape of the channel may be rectangular. However, this is only illustrative and not limiting, and the channels may also have other suitable cross-sectional shapes. In some examples, the substrate 10 may be an acrylic substrate, which not only can meet the material requirements of the microfluidic chip and the material requirements of CNC processing, but also has good transparency, which is more conducive to observing the microfluidic in the microfluidic chip. state. The photodeformable material may be any suitable photodeformable material now known or later disclosed. In some examples, the photodeformable material may include a photodeformable liquid crystal polymer material. For example, a whole film made of a photodeformable liquid crystal polymer material may be used as the photodeformable film 20 . In some examples, the photodeformable liquid crystal polymer material may include a photoresponsive linear liquid crystal polymer material whose main chain is polycyclooctene and whose side chain contains azobenzene. In some embodiments, the substrate 10 and the photodeformable film 20 may be recycled and reused. For example, acrylic substrates that have been used but are not damaged can be recycled as brand new components to produce new microfluidic chips after thorough cleaning and drying, while films made of photodeformable liquid crystal polymer materials can also be used to produce new microfluidic chips. The original material can be obtained by first dissolving and then extracting, and then re-prepared into a thin film for the production of new microfluidic chips.

When certain illumination conditions are met, the photodeformable material (for example, the photodeformable film 20 ) may undergo local photodeformation, thereby causing the cross-sectional area of the local channel to change. Under the action of Laplace pressure difference, the fluid in the channel will move in the direction of decreasing cross-sectional area. In some embodiments, the photodeformable material (eg, photodeformable film 20) is configured to expand in response to exposure to light, such that portions of the reaction channels 1041-1042 have a smaller thickness when illuminated than when not exposed to light. A larger cross-sectional area drives the microfluid in the reaction channel 1041-1042 in the direction of decreasing light intensity. In some embodiments, the photodeformable material (eg, photodeformable film 20 ) is configured to shrink in response to exposure to light, such that portions of reaction channels 1041 - 1042 have a smaller diameter when illuminated than when not exposed to light. A smaller cross-sectional area is used to drive the microfluid in the reaction channel 1041-1042 in the direction of increasing light intensity.

Referring to Figure 6, which shows the plane where the length and depth are located, the case where the photodeformable film 20 is expanded by light is used as a non-limiting example: the microfluid 40 is at position a (taking the position of the left end surface of the microfluid 40 as represents), the cross-sectional area of each part of the closed channel 30 is initially the same; after the photodeformable film 20 is irradiated with light that can cause expansion of the photodeformable film 20 at position a, since the photodeformable film 20 is at position a The part at a is expanded by light, causing the cross-sectional area of the part of the closed channel 30 at the position a to increase, which is larger than the cross-sectional area of the part of the closed channel 30 at the position b. Therefore, the closed channel 30 is at the position a. The asymmetric photoinduced deformation at position b generates a Laplace pressure difference, and under the action of the Laplace pressure difference, the microfluid 40 spontaneously moves from position a with a larger cross-sectional area to a position with a smaller cross-sectional area. The position b is small, thereby realizing the photo-driven driving of the microfluid 40. Utilizing such a principle, the photo-driven driving of the microfluid 40 can be precisely controlled by controlling the position and intensity of light. Such a photo-driven method does not require external driving equipment, and can achieve contactless driving of microfluidics using only light sources that meet the conditions. And the driving accuracy is also high.

In some embodiments, for example, as shown in Figure 1, the first communication structure 1061 (1062) includes a balance channel 10611 (10621) connected to the corresponding reaction channel 1041 (1042) at one end and connected to the atmosphere at the other end. The cross-sectional area of channel 10611 (10621) is smaller than the cross-sectional area of reaction channel 1041 (1042). In some examples, the ends of balancing channels 10611 (10621) are formed to be open to the atmosphere, as shown in Figure 1. In some examples, the end of the balancing channel 10611 (10621) includes a balancing cavity 10612 (10622) having a vertical through hole to communicate with the atmosphere, as shown in Figure 2. Such through holes may vertically penetrate, for example, the substrate 10 and the photodeformable film 20 . In some embodiments, the first communication structure 1061 (1062) includes a balance channel 10611 (10621) or referred to herein as a backbone that communicates with the corresponding reaction channel 1041 (1042) at one end and the atmosphere at the other end. The branched branch 10613 (10623) has a closed end, as shown in Figure 3. The arrangement of the first communication structure shown in Figure 3 can facilitate more accurate and stable measurement of the reaction unit. Because when the sample microfluid enters the trunk and reaches its intersection with the branch, part of the sample microfluid will continue to move forward in the trunk while another part will enter the branch. Since the ends of the branches are closed, the sample microfluidic entering the branch will compress the gas in the branch, which will cause the sample microfluidic in the trunk to fail earlier than the case without branches (such as shown in Figure 1). It continues to move forward against the air pressure, so the first communication structure 1061 (1062) self-closes earlier.

In some embodiments, the first communication structure may be disposed outside the reaction channel. For example, referring to FIGS. 1 and 2 , the first communication structure 1061 is arranged outside the reaction channel 1041 , and the first communication structure 1062 is arranged outside the reaction channel 1042 . In some embodiments, the first communication structure may be disposed inside the reaction channel. For example, referring to FIG. 3 , the first communication structure 1061 is arranged inside the reaction channel 1041 .

In some embodiments, for example, referring to FIGS. 2 to 4 , the microfluidic chip 100 may further include a buffer tube 107 connected between the injection channel 102 and the capillary pump 103 . In some embodiments, the cross-sectional area of the buffer tube 107 is larger than the cross-sectional area of the injection channel 102 . In some embodiments, buffer tube 107 may include one or more connected U-shaped tubes. The arrangement of the buffer tube 107 can help prevent the sample microfluid from being sucked away by the capillary pump before the first communication structures 1061-1062 are self-sealing. In other words, the arrangement of the buffer tube 107 can help ensure that the sample microfluid is sucked away by the capillary pump after the first communication structures 1061-1062 are self-sealed (that is, the reaction units 110A-110B complete the measuring process). The arrangement of the buffer tube 107 can also prevent the sample microfluid from flowing back from the capillary pump 103 to the sampling channel 102 . Alternatively, the buffer tube 107 may not be provided, but the end portion of the sampling channel 102 close to the capillary pump 103 may be formed into a plurality of connected bends and/or the end portion of the sampling channel 102 close to the capillary pump 103 may be formed into a plurality of connected bends. The bottom surface is formed into multiple steps, which can also provide buffer areas for sample microfluidics.

In some embodiments, the sampling channel 102 can be configured as a U-shaped channel, and the sampling channels 1051-1052 can be connected downstream of the elbow section of the U-shaped channel, which can facilitate the improvement of the sampling port 101. The flow rate and flow rate of the sample microfluid in the sampling channel 102 are maintained within a controllable range. The elbow section of the U-shaped channel can also effectively achieve the effects of buffering and storage, and also reduces the need for microfluidic control in the sampling channel 102. The occupied area in the chip 100 makes the arrangement of the sampling channels 102 more reasonable.

In some embodiments, when the microfluidic chip 100 includes multiple reaction units, the reaction units may be located on the same side of the sampling channel 102 or on different sides of the sampling channel 102 . When two reaction units are located on different sides of the sampling channel 102, the sampling channels of the two reaction units can be aligned with each other or offset from each other.

In some embodiments, pre-set reactants are stored at one or more different locations in the reaction channels 1041-1042, and the sample microfluidic can generate Laplacine generated by the asymmetric photodeformation of the reaction channels 1041-1042. Under the action of the pressure difference, it is driven to each of the one or more different positions to contact and mix and/or react with the preset reactant at that position. In some examples, these preset reactants may be added to the reaction channels 1041-1042 in advance during the manufacturing stage of the microfluidic chip 100. For example, after a groove is opened in the substrate 10, the reactant can be pre-placed in a specific position of the groove in the substrate 10 to be used as a reaction channel by freeze-drying, and then the photodeformable film 20 can be covered on the substrate 10. On the substrate 10 , the substrate 10 covered with the photodeformable film 20 is then packaged to obtain the microfluidic chip 100 .

The sample microfluid in the reaction channel and/or its mixture with preset reactants and/or reaction products can be detected directly at the reaction channel, such as fluorescence detection, absorbance detection, etc. A detection channel connected to the reaction channel to receive the microfluid to be detected may also be additionally provided. In some embodiments, each reaction unit in some or all of the reaction units of the microfluidic chip 100 may further include: a second communication structure configured to communicate with the reaction channel at one end and the atmosphere at the other end; detection The channel is configured to communicate with the reaction channel at one end to receive the microfluid to be detected from the reaction channel, and to communicate with the atmosphere via a third communication structure at the other end, wherein the third connection point of the reaction channel and the second communication structure is with The first distance between the first connection points along the first direction (for example, the clockwise direction) of the longitudinal centerline of the reaction channel is greater than the minimum distance between the first connection point and the second connection point along the longitudinal centerline of the reaction channel, The second distance between the third connection point and the first connection point in a second direction opposite to the first direction (eg, counterclockwise) along the longitudinal centerline of the reaction channel is greater than between the first connection point and the second connection point. The minimum distance along the longitudinal centerline of the reaction channel, wherein the communication of each of the second communication structure and the third communication structure with the atmosphere is switchable, and wherein the cross-sectional area of the reaction channel is larger than the cross-sectional area of the detection channel cross-sectional area.

For example, referring to FIG. 4 , the reaction unit 110A includes a second communication structure 1081 connected to the reaction channel 1041 at one end and connected to the atmosphere at the other end. The communication between the second communication structure 1081 and the atmosphere is switchable. The first distance between the third connection point CP31 and the first connection point CP11 of the reaction channel 1041 and the second connection structure 1081 along the first direction (for example, clockwise direction) of the longitudinal centerline of the reaction channel 1041 is greater than the first connection point. The minimum distance between CP11 and the second connection point CP21 along the longitudinal centerline of the reaction channel 1041. The second distance between the third connection point CP31 and the first connection point CP11 along the second direction (for example, the counterclockwise direction) of the longitudinal centerline of the reaction channel 1041 is greater than the second distance between the first connection point CP11 and the second connection point CP21 along the second direction (eg, counterclockwise direction) of the reaction channel 1041 . The minimum distance between the longitudinal center lines of the reaction channel 1041. That is to say, since the sample microfluid enters the reaction channel 1041 from the first connection point CP11, it can move to both sides as far as the minimum distance between the first connection point CP11 and the second connection point CP21 along the longitudinal centerline of the reaction channel 1041. , therefore when the reaction unit 110A completes the measurement process, the sample microfluid will not reach the second connection structure 1081 in the reaction channel 1041 .

In addition, the reaction unit 110B includes a second communication structure 1082 connected to the reaction channel 1042 at one end and connected to the atmosphere at the other end. The communication between the second communication structure 1082 and the atmosphere is switchable. The first distance between the third connection point CP32 and the first connection point CP12 of the reaction channel 1042 and the second connection structure 1082 along the first direction (for example, clockwise direction) of the longitudinal centerline of the reaction channel 1042 is greater than the first connection point. The minimum distance between CP12 and the second connection point CP22 along the longitudinal centerline of the reaction channel 1042. The second distance between the third connection point CP32 and the first connection point CP12 along the second direction (eg, counterclockwise direction) of the longitudinal centerline of the reaction channel 1042 is greater than the second distance between the first connection point CP12 and the second connection point CP22 along the second direction (eg, counterclockwise direction) of the reaction channel 1042 . The minimum distance between the longitudinal center lines of the reaction channel 1042. That is to say, since the sample microfluid enters the reaction channel 1042 from the first connection point CP12, it can move to both sides as far as the minimum distance along the longitudinal centerline of the reaction channel 1042 between the first connection point CP12 and the second connection point CP22. , therefore when the reaction unit 110B completes the measurement process, the sample microfluid will not reach the second communication structure 1082 in the reaction channel 1042 .

Continuing to refer to FIG. 4 , the reaction unit 110A further includes a detection channel 1121 , which is configured to communicate with the reaction channel 1041 at one end to receive the microfluid to be detected from the reaction channel 1041 , and to communicate with the atmosphere via a third communication structure 1131 at the other end. , the connection between the third communication structure 1131 and the atmosphere is switchable. The cross-sectional area of the reaction channel 1041 is larger than the cross-sectional area of the detection channel 1121 . In addition, the reaction unit 110B also includes detection channels 1122-1123, each of which is configured to communicate with the reaction channel 1042 at one end to receive the microfluid to be detected from the reaction channel 1042, and at the other end via the corresponding third communication structure 1132- 1133 is connected to the atmosphere, and the connection between the third connection structure 1132-1133 and the atmosphere is switchable. The cross-sectional area of reaction channel 1042 is larger than the cross-sectional area of detection channels 1122-1123.

When detection is not required (for example, the reaction has not yet ended), the communication between the second communication structure 1081 (1082) and the third communication structure 1131 (1132-1133) and the atmosphere can be closed. At this time, the gas in the detection channel 1121 (1122-1123) prevents the microfluid in the reaction channel 1041 (1042) from entering the detection channel 1121 (1122-1123). When detection is required, the connection between the third communication structure 1131 (1132-1133) and the atmosphere can be opened. At this time, the microfluid in the reaction channel 1041 (1042) is larger than the detection channel because the cross-sectional area of the reaction channel 1041 (1042) is larger than that of the detection channel. The cross-sectional area of 1121 (1122-1123) spontaneously enters the detection channel 1121 (1122-1123) under the action of the Laplace pressure difference. However, in some cases, the microfluid entering the detection channel 1121 (1122-1123) may block the detection channel 1121 (1122-1123) so that the microfluid still remaining in the reaction channel 1041 (1042) cannot continue to enter the detection. Channel 1121 (1122-1123). For example, when the reaction channel 1041 (1042) is not connected to the atmosphere, only opening the connection between the third communication structure 1131 (1132-1133) and the atmosphere will form a negative pressure in the reaction channel 1041 (1042), thereby blocking the reaction channel 1041. The microfluid in (1042) enters the detection channel 1121 (1122-1123). In such a case, the amount of microfluid that has entered detection channel 1121 (1122-1123) may be sufficient to perform detection. However, the amount of microfluid that has entered the detection channel 1121 (1122-1123) may not be sufficient for detection. For example, some detections may require all the microfluidic in the reaction channel 1041 (1042) to enter the detection channel 1121 (1122-1123). . Therefore, the second communication structure 1081 (1082) and the third communication structure 1131 (1132-1133) can be connected to the atmosphere at the same time, so that a negative pressure will not be formed in the reaction channel 1041 (1042), so that the reaction channel 1041 (1042 ) can enter the detection channel 1121 (1122-1123) smoothly.

The detection channels 1121-1123 may have any suitable geometric shape, as long as the cross-sectional area of the detection channels 1121-1123 is smaller than the cross-sectional area of the reaction channels 1041-1042. In some embodiments, detection channels 1121-1123 may be arranged in a spiral. Compared with a linear arrangement, a spirally arranged detection channel can increase the distribution density of the microfluid to be detected on the microfluidic chip 100, thereby improving detection accuracy and efficiency, and can also accommodate more microfluids to be detected. Although FIG. 4 illustrates the outline of each turn of the helix of the detection channels 1121 - 1123 as being substantially square, it may also have other suitable outline shapes, for example, the outline of each turn of the helix of the detection channels 1121 - 1123 may also be It can be basically a polygon such as a triangle, a quadrilateral, or a pentagon, a circle, an ellipse, etc., and is not limited thereto.

The detection channel can be arranged outside or inside the reaction channel. For example, as shown in FIG. 4 , the detection channel 1121 is arranged outside the reaction channel 1041 , and the detection channels 1122 - 1123 are arranged inside the reaction channel 1042 . Each reaction channel can be connected to one or more detection channels, so that one or more identical or different detections can be performed. In some embodiments, each reaction unit may include at least two detection channels spaced apart from each other. For example, as shown in FIG. 4 , reaction unit 110B includes detection channels 1122 and 1123 spaced apart from each other. These detection channels can be located on the same side of the reaction channel or on different sides. When multiple detection channels can be located on the same side of the reaction channel, the connecting portions of these detection channels and the reaction channel can be shared or separated. When multiple detection channels may be located on different sides of the reaction channel, the connecting portions of the detection channels and the reaction channel may be aligned or offset with each other. In some embodiments, the fourth connection point of the detection channel and the reaction channel can be separated from the first connection point of the sampling channel and the reaction channel. For example, as shown in Figure 4, the fourth connection point CP41 (CP42) is connected to the first connection point of the detection channel and the reaction channel. separated by a connection point CP11 (CP12). In some embodiments, the fourth connection point may coincide with the first connection point. For example, as shown in FIG. 5 , the fourth connection point CP4A (CP4B) coincides with the first connection point CP1A (CP1B).

In some embodiments, detection channels 1121-1123 may have a different depth than reaction channels 1041-1042. In such embodiments, transition channels providing depth transitions may be provided between detection channels 1121-1123 and reaction channels 1041-1042. In some embodiments, the depth of detection channels 1121-1123 may be less than the depth of reaction channels 1041-1042.

The communication between the second communication structures 1081-1082 and the third communication structures 1131-1133 and the atmosphere can be controlled by any suitable switching mechanism. In some examples, a closing structure such as a movable baffle can be provided at an opening of the communication structure that can be opened to the atmosphere (for example, a through hole of the balance chamber). The baffle is in the first position of closing the opening and not closing the opening. The opening is moveable between second positions. In some examples, baffles for multiple communication structures can be integrated onto the same baffle card, so that switching of different communication structures or combinations thereof can be implemented by moving the baffle card as a whole. In some embodiments, communication of the communication structure to the atmosphere may be controlled by a light-responsive switching mechanism. Such light-responsive switching mechanisms may include photodeformable materials. In some examples, the photodeformable material may not close the opening of the communication structure when it is not exposed to light, but may undergo photodeformation (eg, expansion) to close the opening of the communication structure when exposed to light. In other examples, the photodeformable material can close the opening of the communication structure when not exposed to light and photodeform (eg shrink) to not close the opening of the communication structure when exposed to light. For example, a chamber containing a photodeformable gel may be provided at the opening of the communication structure, or a film or sheet formed of a photodeformable material may be provided at the opening of the communication structure.

In some embodiments, the microfluidic chip may also include multiple independent microfluidic units. As a non-limiting example, referring to Figure 5, the microfluidic chip 100 includes two mutually independent microfluidic units 100UA and 100UB. Each of the microfluidic units 100UA and 100UB is not limited to the exemplary arrangement shown in FIG. 5 but may have an arrangement of microfluidic units according to any embodiment of the present disclosure. As shown in FIG. 5 , the microfluidic unit 100UA includes a sampling port 101A, a sampling channel 102A, a capillary pump 103A, and a reaction channel 104A. The reaction channel 104A is connected to the sampling channel 105A at the first connection point CP1A and then communicates with the sampling channel 102A. The reaction channel 104A is connected to the first communication structure 106A at the second connection point CP2A and is connected to the second communication structure 108A at the third connection point CP3A. The reaction channel 104A is also connected to the two detection channels 112A spaced apart from each other at a fourth connection point CP4A. The two detection channels 112A provide two detection areas spaced apart from each other. As further shown in FIG. 5 , the microfluidic unit 100UB includes a sampling port 101B, a sampling channel 102B, a capillary pump 103B and a reaction channel 104B. The reaction channel 104B is connected to the sampling channel 105B at the first connection point CP1B and then communicates with the sampling channel 102B. The reaction channel 104B is connected to the first communication structure 106B at the second connection point CP2B and is connected to the second communication structure 108B at the third connection point CP3B. The reaction channel 104B is also connected to the two detection channels 112B spaced apart from each other at a fourth connection point CP4B. The two detection channels 112B provide two detection areas spaced apart from each other. Since the microfluidic units 100UA and 100UB are independent of each other, they can be used to detect microfluidic samples of different samples.

The microfluidic chip 100 provided by the present disclosure can be used for at least one of the following: immune detection, biochemical detection, molecular detection, and polymerase chain reaction (Polymerase chain reaction, PCR) detection. Taking the microfluidic chip 100 shown in FIG. 4 as an example, the reaction units 110A and 110B may correspond to any two of the three dry biochemical detection items: blood creatinine, blood urea, and blood uric acid. These dry type The samples required for biochemical testing projects are all serum. It can be understood that the microfluidic unit 100U of the microfluidic chip 100 can also include a third reaction unit in addition to the reaction units 110A and 110B, so that the three reaction channels can respectively correspond to blood creatinine, blood urea, and blood. These three dry biochemical testing items are uric acid. The reaction unit 110A performs dry biochemical detection of blood creatinine as an example for description. Serum as a sample microfluid is added to the sampling port 101 and enters the sampling channel 102, and then enters the reaction channel 1041 via the sampling channel 1051. The serum is first mixed with the first detection reagent pre-embedded at the inlet of the reaction channel 1041 (ie, the first connection point CP11) by freeze-drying. They do not react when mixed, and then incubated at 37°C for 5 minutes. After the incubation is completed, the mixture of serum and the first detection reagent is driven to another position in the reaction channel 1041 by photo-driven microfluidics to match the second detection pre-embedded in the other position by freeze-drying. The reagents are mixed and reacted, followed by incubation at 37°C for 5 minutes. After the incubation is completed, the mixture of serum and the first detection reagent and the reaction product of the second detection reagent are driven to the fourth connection point CP41 of the detection channel 1121 and the reaction channel 1041 by means of photo-driven microfluidics, and then the second detection reagent is opened. The communication structure 1081 and the third communication structure 1131 are connected with the atmosphere so that the reaction products enter the detection channel 1121 . The reaction product in the detection area provided by the detection channel 1121 is detected by absorbance. Specifically, the absorbance of the reaction product to light with a wavelength of 550 nanometers can be detected at a certain time and the absorbance of the reaction product to light with a wavelength of 550 nanometers can be detected two minutes after this time. Calculate the difference in absorbance detected twice and record it as the result of this dry biochemical test of serum creatinine. Like the reaction unit 110B, which has multiple detection channels to provide multiple detection areas, different detections can also be performed on different detection areas. For example, absorbance detection can be performed on the detection area provided by the detection channel 1122 and the detection area provided by the detection channel 1123. Fluorescence detection is performed in the detection area. This can be set based on specific detection needs. In addition, the microfluidic chip 100 in Figure 5 has multiple microfluidic units and each microfluidic unit has a separate inlet, which can be applied to multiple detection projects where the types of samples used are not exactly the same. situations, or situations where the samples are of the same type but come from different subjects.

In addition, the same microfluidic chip can not only be used to perform testing items with the same methodology (for example, the aforementioned three dry biochemical testing items of blood creatinine, blood urea, and blood uric acid all belong to the same methodology, that is, biochemical testing). Used to carry out testing projects with different methodologies (for example, immunological testing, biochemical testing, molecular testing, PCR testing, etc.). For example, when the microfluidic chip includes three reaction units, the first reaction unit can be used for dry biochemical detection of blood creatinine, and the second reaction unit can be used for immunoturbidimetric detection of C-reactive protein (CRP). The third reaction unit can be used for immunofluorescence detection of thyroid function (immunohomogeneous luminescence detection). The CRP immunoturbidimetric test is similar to the blood creatinine dry biochemical test. The sample is mixed with two detection reagents, and finally the absorbance test is performed. However, the wavelength used in the absorbance test of the CRP immunoturbidimetric test is The wavelength used in the absorbance detection of dry biochemical detection of serum creatinine is different. In addition, the detection process of thyroid function immunofluorescence detection is similar to that of CRP immunoturbidimetric detection. However, thyroid function immunofluorescence detection does not perform absorbance detection but fluorescence detection. The reaction product is emitted after being excited by light of a specific wavelength. The intensity of light (i.e., fluorescence) is detected, and the detected fluorescence intensity is combined with the immunohomogeneous luminescence detection item and recorded as the result of the immunohomogeneous luminescence detection item.

The microfluidic chip of the present disclosure is also particularly suitable for PCR detection. For end-point PCR detection, the detection process is similar to the detection process of other methodologies mentioned above. It is only necessary to allow the final reaction product to enter the detection channel for detection after the PCR reaction is completely completed. For real-time quantitative fluorescence PCR detection, if a variable temperature PCR reaction is performed, temperature control components such as electric heaters need to be used to form multiple different temperature zones at multiple non-adjacent locations in the reaction channel. For example, it can be formed at two non-adjacent locations. High-temperature zone and low-temperature zone (or forming a high-temperature zone, a medium temperature zone and a low-temperature zone in three non-adjacent positions), and then the mixture of sample microfluid and detection reagent is driven in the high-temperature zone in the reaction channel by photo-driven microfluidics. and low-temperature zones to achieve the process of denaturation-annealing-extension. When the mixture moves from the low-temperature area to the high-temperature area, fluorescence detection of the mixture in the reaction channel can be performed and the fluorescence intensity can be recorded. By plotting the measured fluorescence intensity for each cycle as a curve, the results of the real-time quantitative fluorescence PCR detection can be obtained. If a isothermal PCR reaction is performed, the temperature control component can be used to maintain the microfluidic chip at the desired temperature, and other processes are similar to the above.

In another aspect, the present disclosure also provides a microfluidic device including the aforementioned microfluidic chip.

Referring to FIG. 7 , a microfluidic device 300 is provided, which includes the microfluidic chip 100 according to any of the preceding embodiments and is configured to provide illumination to the microfluidic chip 100 to control the microfluidic chip 100 . A light source 310 for microfluidic movement (especially in a reaction channel). The light source 310 may take any suitable form such as a point light source, a line light source, an area light source, an array light source, etc., and may be any suitable light source such as a light emitting diode (LED), a laser, or the like. In some embodiments, the light source 310 can be configured to be movable relative to the microfluidic chip 100 to scan the illumination position on the microfluidic chip 100 to generate asymmetric photoinduced deformation along the channel (especially the reaction channel) to drive fluid. For example, the relative movement of the light source 310 and the microfluidic chip 100 can be achieved by fixing the light source 310 while moving the microfluidic chip 100, or by fixing the microfluidic chip 100 while moving the light source 310. This can be achieved, or it can also be achieved by allowing the light source 310 and the microfluidic chip 100 to move simultaneously at different speeds, which is not particularly limited here. In some embodiments, for example, as shown in FIG. 8 , the light source 310 may include an array of multiple light sources 310_1 , 310_2 , 310_3 , each of the multiple light sources 310_1 , 310_2 , 310_3 on the microfluidic chip 100 (especially on the reaction channel) with different lighting positions. As a result, the illumination position can be switched by switching each light source. Although only three light sources 310_1, 310_2, 310_3 are shown in FIG. 8, this is only illustrative and not limiting. A larger number of light sources can be arranged as needed, and they can be arranged as a one-dimensional array, a two-dimensional array, or a two-dimensional array. dimensional array or any suitable array.

In the embodiment of FIG. 7 , it can be understood that scanning of a normal-phase light spot on the microfluidic chip 100 is provided. In some other embodiments, scanning of an inverted light spot on the microfluidic chip 100 may also be provided. For example, referring to FIG. 9 , the microfluidic device 300 may further include a light shield 320 disposed between the microfluidic chip 100 and the light source 310 and configured to exclude selectable portions of the reaction channels of the microfluidic chip 100 . The remaining parts receive illumination from the light source 310 . For example, the light source 310 can be configured to provide illumination to the entire microfluidic chip 100, and the projection of the light shield 320 on the microfluidic chip 100 provides an inverted light spot, wherein the microfluidic chip 100 and the light source 310 can be stationary. , and the light shield 320 can be movable, so that different selectable parts of the reaction channel of the microfluidic chip 100 can be selected, which is equivalent to providing scanning of an inverted light spot. In other embodiments, the light shield 320 can also be configured such that a selectable portion of the reaction channel of the microfluidic chip 100 receives illumination from the light source 310 while the remaining portion does not receive illumination from the light source 310 . For example, the light source 310 can be configured to provide illumination to the entire microfluidic chip 100, and the light shield 320 can block all illumination except for openings for light leakage. In this case, the microfluidic chip 100 and the light source 310 can is fixed, and the light shield 320 can be movable, so that different selectable parts of the reaction channel of the microfluidic chip 100 can be selected, which is equivalent to providing scanning of a normal phase light spot.

In other embodiments, referring to FIG. 10 , the microfluidic device 300 may alternatively include a light attenuating sheet 330 disposed between the microfluidic chip 100 and the light source 310 and configured to cause the reaction of the microfluidic chip 100 to The selectable portion of the channel receives illumination from the light source 310 with an attenuated intensity compared to the illumination from the light source 310 received by the remainder of the reaction channel. The light source 310 may, for example, be configured to provide illumination to the entire microfluidic chip 100, and the projection of the light attenuating sheet 330 on the microfluidic chip 100 provides an attenuated light spot, wherein the microfluidic chip 100 and the light source 310 may be stationary. , and the light attenuation piece 330 can be movable, so that different selectable parts of the reaction channel of the microfluidic chip 100 can be selected, which is equivalent to providing scanning of the attenuated light spot.

It can be understood that although the light shielding sheet 320 or the light attenuating sheet 320 moves while the light source 310 and the microfluidic chip 100 do not move as described above, this is only illustrative and not restrictive. The relative movement between the above components can be It can be implemented in a variety of ways, as long as the scanning of the normal-phase light spot, the reverse-phase light spot or the attenuated light spot on the microfluidic chip 100 can be realized.

The microfluidic chip and microfluidic device according to the present disclosure effectively utilize the capillary force of the capillary pump and the Laplace pressure difference generated by the asymmetric photodeformation of the channel to achieve microfluidic operation without any external driving equipment. It is contactless and precise driven, and does not need to fill the entire front channel to achieve precise quantitative trace measurement operations at the back end. It has low sample loss, few parts, small overall volume, simple and robust structure, high repeatability, and High degree of portability and automation.

In another aspect, the present disclosure also provides a microfluidic device, which can realize contactless driving of microfluidics in microfluidic chips by using light to drive microfluidics, and can also be used to perform various methods. Scientific detection and analysis. Microfluidic devices according to various embodiments of the present disclosure are described below with reference to the accompanying drawings. It should be understood that actual microfluidic devices may also include other components, but to avoid obscuring the gist of the present disclosure, these other components are not discussed herein and are not shown in the figures.

Referring to Figure 11, a microfluidic device 400 is shown in accordance with some embodiments of the present disclosure. The microfluidic device 400 includes a light control module 410 and a mobile module 420, where the light control module 410 is fixed above the mobile module 420. The light control module 410 includes a light source 411 configured to provide illumination to the microfluidic chip 460 to control the movement of microfluid in the microfluidic chip 460 . The microfluid in the microfluidic chip 460 is photodriven, which may be, for example, but not limited to, the microfluidic chip 100 according to any embodiment of the present disclosure. With reference to FIG. 13 , the light emitted by the light source 411 can be totally reflected by the right-angled prism 412 onto the microfluidic chip 460 . The optical path design shown here is only exemplary and not limiting. More, fewer, or alternative optical elements may be used to design the optical path from the light source 411 to the microfluidic chip 460. The light control module 410 may similarly refer to the various configurations mentioned previously with respect to the microfluidic device 300 . The light source 411 may be an LED, a laser, or any other suitable light source. For example, the light source 411 may include multiple LEDs of different wavelengths, and these LEDs may form a light source group capable of switching wavelengths. The light source 411 can take any suitable form such as point light source, linear light source, surface light source, array light source, etc., and components for changing the illumination form can be provided in the light path from the light source 411 to the microfluidic chip 460 . For example, in Figure 13, when the light source 411 originally provides a point light source on the microfluidic chip 460, a detachable light guide strip can be added under the right-angle prism 412 to convert the point light source into a linear light source, so that Perform batch photoactivation of multiple microfluidic chips.

11 and 13, the movement module 420 is configured to move the microfluidic chip 460 to adjust the relative position of the microfluidic chip 460 and the light source 411, so that the microfluidic chip 460 is selectively and locally illuminated by the light source 411. This causes the microfluid in the microfluidic chip 460 to be driven by light. For example, as shown in FIG. 12 , in some embodiments, the mobile module 420 may include a carrying platform 421 and a motor set for driving the carrying platform 421 to move in a horizontal plane. The upper surface of the carrying platform 421 provides a carrying surface 4211 for placing the microfluidic chip 460 . It should be understood that although FIG. 11 only shows one microfluidic chip placed on the bearing surface 4211, in some embodiments, multiple microfluidic chips can also be placed on the bearing surface 4211. The motor set may include a first motor, or an X-axis motor 4221, for driving the bearing platform 421 to move transversely in the horizontal plane (also referred to as the X-axis direction here), and a first motor, or called an This is also called the second motor that moves in the Y-axis direction or the Y-axis motor 4231. The moving module 420 may also include a first guide portion, or X-axis guide portion 4222, for guiding the carrying platform 421 to move transversely in the horizontal plane, and a second guide portion for guiding the supporting platform 421 to move longitudinally in the horizontal plane. Or called Y-axis guide part 4232. The X-axis guide part 4222 corresponds to the X-axis motor 4221, and the Y-axis guide part 4232 corresponds to the Y-axis motor 4231. In some examples, each guide part may include at least a set of screw nut mechanisms and guide rails parallel to the guiding direction. The nuts in the screw nut mechanism may be directly fixed to the bottom of the bearing platform 421 , while the screw rods may move along the corresponding The guide direction is arranged and connected to the output of the corresponding motor. For example, when the X-axis motor 4221 outputs torque, due to the transmission effect of the screw nut mechanism, the bearing platform 421 can reciprocate along the X-axis direction, and under the guidance of the X-axis guide portion 4222, the bearing platform 421 can move along the X-axis The direction moves more steadily. In addition, the X-axis motor 4221 and the X-axis guide part 4222 and the Y-axis motor 4231 and the Y-axis guide part 4232 work independently with respect to each other without interfering with each other. Therefore, the carrying platform 421 can move in both the X-axis direction and the Y-axis direction at the same time. Movement, so that the combination of movement in two directions can be achieved, such as diagonal or curved movement in the horizontal plane. In addition, in order to improve control accuracy and stability, servo motors can be selected as the X-axis motor 4221 and Y-axis motor 4231, and guide rails 4241 and 4242 can also be arranged on the corresponding sides of the bearing platform 421 to prevent the bearing platform 421 from unilateral side movement. offset to the direction. A device (for example, a clamp, etc.) for fixing the microfluidic chip 460 can also be provided on the bearing surface 4211 of the bearing platform 421 to prevent the microfluidic chip 460 from slipping and deviating from the desired position during the movement of the bearing platform 421 .

Continuing to refer to FIG. 11 , in some embodiments, the microfluidic device 400 may further include a detection module 430 configured to perform detection on the microfluidic chip 460 , wherein the detection module 430 is fixed above the mobile module 420 and is connected with the light control module 430 . Modules 410 are spaced apart. The moving module 420 is also configured to move the microfluidic chip 460 to adjust the relative position of the microfluidic chip 460 and the detection module 430 so that the microfluidic chip 460 is detected by the detection module 430 . For example, in the aforementioned examples of biochemical detection, immune detection, etc., the movement module 420 can be used to move the corresponding detection area of the microfluidic chip 460 into the detection field of view of the detection module 430. Through the staggered arrangement of the detection module 430 and the light control module 410, and by moving the microfluidic chip 460 through the movement module 420, the relative movement of the microfluidic chip 460 and the light control module 410 and the detection of the microfluidic chip 460 and the light control module 410 are realized. The relative movement of the module 430 reduces the number of moving parts of the microfluidic device 400, simplifies the structure of the microfluidic device 400, and reduces manufacturing difficulty and cost.

In some embodiments, the detection module 430 includes a plurality of detection units, and the relative arrangement between the multiple detection units corresponds to the relative arrangement between the multiple detection areas of the microfluidic chip 460 . In some examples, the detection module 430 may include a fluorescence detection unit 431 and an absorbance detection unit 432. The distance between the fluorescence detection unit 431 and the absorbance detection unit 432 may be configured to be between two detection areas of the microfluidic chip 460. distance is the same. For example, assuming that the microfluidic chip 460 is the microfluidic chip 100 shown in FIG. 4 , the distance between the fluorescence detection unit 431 and the absorbance detection unit 432 of the detection module 430 may be configured to be the same as that provided by the detection channel 1122 . The distance between the detection area and the detection area provided by the detection channel 1123 is the same. In addition, especially in real-time quantitative fluorescence PCR detection, for example, in order to facilitate the fluorescence detection unit 431 to accurately capture the position of the liquid to be detected during detection, the detection point of the fluorescence detection unit 431 can be configured to be in line with the light source 411 of the light control module 410 The light spots overlap, which will not affect the reciprocating oscillation cycle of the liquid to be detected. Here, the wavelength of the light source 411 used to drive the microfluid may be different from the fluorescence wavelength detected by the fluorescence detection unit 431. Therefore, only corresponding filters need to be set in the fluorescence detection unit 431 to eliminate light pairs of other wavelengths. impact on test results.

Continuing to refer to FIG. 11 , in some embodiments, the microfluidic device 400 may further include a temperature control module 440 (not explicitly shown in the figure) configured to control the temperature of the microfluidic chip 460 , where the temperature control module 440 is Arranged in the mobile module 420 , in particular in the carrying surface 4211 . In some embodiments, the temperature control module 440 may include an electric heater and a temperature sensor. The electric heater can be arranged in the bearing surface 4211 to transfer heat to the microfluidic chip 460 in a thermal conductive manner. Of course, other heat transfer methods and other forms of heating are possible. In addition, a refrigerator can also be installed according to actual needs. Since the microfluidic chip 460 is fixed on the bearing surface 4211 and there is no relative displacement between the two, the electric heater can be arranged in the bearing surface 4211 at a position corresponding to the reaction unit of the microfluidic chip 460 to ensure the reaction. The temperature during the process is controllable. The temperature sensor can be, for example, a thermocouple or other form of temperature sensing component attached between the microfluidic chip 460 and the carrying surface 4211, which can monitor the temperature in the reaction unit of the microfluidic chip 460 in real time. The temperature can be used to adjust the power of the electric heater to ensure that the temperature of the reaction unit of the microfluidic chip 460 is stably maintained within a required range.

In some embodiments, the temperature control module 440 is configured to provide a plurality of different temperature zones to the microfluidic chip 460, so that corresponding multiple zones of the microfluidic chip 460 are at different temperatures. Such a microfluidic device 400 may be used, for example, for variable temperature PCR detection. In some embodiments, the temperature control module 440 is configured to provide a temperature zone to the microfluidic chip 460 such that each area of the microfluidic chip 460 is at the same temperature. Such a microfluidic device 400 may be used, for example, for isothermal PCR detection.

In some embodiments, in order to improve the temperature control accuracy of the temperature control module 440, the following process can also be performed: obtain the volume V of the sample liquid entering the reaction unit of the microfluidic chip 460, the temperature T required for the reaction, and the sample The type of liquid; adjust the output heating power P of the electric heater of the temperature control module 440 to the output heating power reference value P _ref corresponding to the type of sample liquid at the volume V and temperature T; through the temperature control module 440 The temperature sensor obtains the real-time temperature T _real of the sample. When the difference ΔT between the real-time temperature T _real and the temperature required for the reaction T exceeds the preset value, the output heating power P is adjusted so that the real-time temperature T _real is equal to the temperature T required for the reaction. The difference ΔT does not exceed the preset value until the reaction ends. Temperature control here can be achieved using various appropriate control methods now known or later open such as proportional integration differentiation (PID) control methods. In addition, the volume V of the sample liquid entering the reaction unit of the microfluidic chip 460, the temperature T required for the reaction, and the type of sample liquid are all determined by the specific detection items and the specifications and types of the microfluidic chip, that is to say The above parameters are actually determined before the reaction starts, so the above information can be quickly obtained through code scanning and identification. The output heating power reference value _Pref can be calculated based on the volume V of the sample liquid entering the reaction unit of the microfluidic chip 460, the temperature T required for the reaction, the specific heat capacity C, and the density ρ of the sample liquid. It can also be calculated in the microfluidic The control chip is calibrated through simulated heating experiments during the design and manufacturing process, and can be obtained through table lookup during use. When the difference ΔT between the real-time temperature T _real and the reaction required temperature T exceeds the preset value, the adjustment amplitude of the output heating power P can be determined according to the actual situation, or through simulated heating experiments during the design and manufacturing process of the microfluidic chip. Determine the adjustment range reference value.

Continuing to refer to FIG. 11 , in some embodiments, the microfluidic device 400 may further include a housing 470 , in which the aforementioned light control module 410 , detection module 430 , movement module 420 and temperature control module 440 may be accommodated. A display screen 480 and an operation panel 490 can be provided on the housing 470 for the user to operate the light control module 410, the detection module 430, the movement module 420 and the temperature control module 440. Through the operation panel 490, the user can freely select and adjust the moving path of the carrying platform 421, the start and stop of the light control module 410, the settings of the temperature control module 440, the selection of detection items of the detection module 430, the start and stop of the detection process, etc. The detection result of the detection module 430 can also be displayed on the display screen 480 .

The microfluidic device according to the present disclosure realizes contactless driving of the microfluid in the microfluidic chip by driving the microfluidic light, and can integrate a variety of detection items with different methodologies into a single microfluidic chip. Corresponding testing units are provided for these testing items, so that a variety of testing items with different methodologies can be carried out in a single device. Such microfluidic devices have smaller volumes, lower detection costs, and higher detection accuracy, and can provide portable, automated point-of-care testing (POCT) covering different methodological testing items. ) equipment, which is simple to operate and does not require users to have professional skills, and can meet users' daily testing needs.

What needs special emphasis is that the biggest feature of PCR detection technology is that it can greatly increase the amount of trace DNA, so it is widely used in medical testing and other fields. However, for PCR detection technology, the current conventional PCR detection equipment is large and difficult to meet the needs of the POCT field. In addition, PCR reaction conditions are relatively harsh, and if the control is not accurate, the test results will be affected. Therefore, samples are usually sent to a specialized testing laboratory or laboratory for testing. In contrast, the microfluidic device of the present disclosure can not only reduce the amount of samples and shorten the reaction time by transferring the location of PCR detection to the microfluidic chip, but also does not affect the detection accuracy, and provides a POCT that can perform PCR detection. equipment.

If the words "left", "right", "front", "rear", "top", "bottom", "upper", "lower", "high", "low", etc. in the description and claims, If present, it is used for descriptive purposes and not necessarily to describe a constant relative position. It is to be understood that the words so used are interchangeable under appropriate circumstances such that the embodiments of the disclosure described herein, for example, can be used in other orientations than those illustrated or otherwise described herein. Operate on orientation. For example, if the device in the figures is turned over, features described as "above" other features would now be described as "below" other features. The device may be otherwise oriented (rotated 90 degrees or at other orientations) and the relative spatial relationships will be interpreted accordingly.

In the specification and claims, one element is referred to as being "on", "attached to", "connected to" another element, "coupled to" another element, and "coupled to" another element. An element, or "contacting" another element, etc., can be directly on the other element, directly attached to the other element, directly connected to the other element, directly coupled to the other element, directly coupled to Another element may be in direct contact with another element, or one or more intervening elements may be present. In contrast, one element is said to be "directly on" another element, "directly attached" to another element, "directly connected to" another element, "directly coupled to" another element, "directly connected" to another element, "directly coupled" to another element, "directly connected to" another element When an element is coupled to or in direct contact with another element, there are no intervening elements present. In the specification and claims, a feature being arranged "adjacent" to another feature may mean that one feature has a portion that overlaps the adjacent feature or that is located above or below the adjacent feature.

As used herein, the word "exemplary" means "serving as an example, instance, or illustration" rather than as a "model" that will be accurately reproduced. Any implementation illustratively described herein is not necessarily to be construed as preferred or advantageous over other implementations. Furthermore, the disclosure is not intended to be bound by any expressed or implied theory presented in the technical field, background, brief summary, or detailed description.

As used herein, the word "substantially" is meant to include any minor variations resulting from design or manufacturing defects, device or component tolerances, environmental effects, and/or other factors. The word "substantially" also allows for differences from perfect or ideal conditions due to parasitic effects, noise, and other practical considerations that may be present in actual implementations.

Additionally, "first," "second," and similar terms may also be used herein for reference purposes only and are therefore not intended to be limiting. For example, the words "first," "second," and other such numerical terms referring to structures or elements do not imply a sequence or order unless clearly indicated by the context.

It will also be understood that the word "comprising/comprising" when used herein illustrates the presence of the indicated features, integers, steps, operations, units and/or components, but does not exclude the presence or addition of one or more other features, Integers, steps, operations, units and/or components and/or combinations thereof.

In this disclosure, the term "provide" is used in a broad sense to cover all ways of obtaining an object, so "providing an object" includes but is not limited to "purchasing", "preparing/manufacturing", "arranging/setting up", "installing/ Assembly", and/or "Order" objects, etc.

As used herein, the term "and/or" includes any and all combinations of one or more of the associated listed items. The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the disclosure. As used herein, the singular forms "a", "an" and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise.

Those skilled in the art will appreciate that the boundaries between the operations described above are illustrative only. Multiple operations may be combined into a single operation, a single operation may be distributed among additional operations, and operations may be performed with at least partial overlap in time. Furthermore, alternative embodiments may include multiple instances of a particular operation, and the order of operations may be altered in various other embodiments. However, other modifications, changes and substitutions are also possible. Aspects and elements of all of the embodiments disclosed above may be combined in any manner and/or combination with aspects or elements of other embodiments to provide multiple additional embodiments. Accordingly, the specification and drawings should be regarded as illustrative rather than restrictive.

Although some specific embodiments of the present disclosure have been described in detail through examples, those skilled in the art will understand that the above examples are for illustration only and are not intended to limit the scope of the disclosure. The various embodiments disclosed herein may be combined in any manner without departing from the spirit and scope of the disclosure. Those skilled in the art will further appreciate that various modifications may be made to the embodiments without departing from the scope and spirit of the disclosure. The scope of the disclosure is defined by the appended claims.

Claims (31)

1. A microfluidic chip, characterized in that the microfluidic chip includes a microfluidic unit, and the microfluidic unit includes: a sample inlet configured to receive the sample microfluidic; a sampling channel configured to communicate with the sampling port to receive the sample microfluid from the sampling port; a capillary pump configured to communicate with the sampling channel to draw the sample microfluid through and out of the sampling channel; and One or more reaction units, each reaction unit includes: The annularly arranged reaction channel is configured to communicate with the injection channel between the injection port and the capillary pump via the sampling channel corresponding to the reaction unit to receive from the injection channel a preset volume corresponding to the reaction unit. Sample microfluidic, wherein the reaction channel includes a photo-induced deformation material so that the microfluid can be driven through the reaction channel under the action of a Laplace pressure difference generated by asymmetric photo-induced deformation of the reaction channel, The first communication structure is configured to communicate with the reaction channel at one end and maintain communication with the atmosphere at the other end, so that the sample microfluid can self-close the first communication structure after entering the first communication structure from the sample separation channel through the reaction channel, wherein, The first connection point of the sample separation channel and the reaction channel and the second connection point of the reaction channel and the first communication structure are spaced apart from each other along the longitudinal centerline of the reaction channel, Wherein, the cross-sectional area of the sampling channel is larger than the cross-sectional area of the reaction channel, the cross-sectional area of the reaction channel is larger than the cross-sectional area of the first connecting structure, the cross-sectional area of the reaction channel is larger than the cross-sectional area of the sampling channel, and the cross-sectional area of the reaction channel is larger than the cross-sectional area of the first connecting structure. The depth is greater than the depth of the sampling channel. 2. The microfluidic chip according to claim 1, characterized in that the microfluidic unit further includes a buffer tube connected between the sampling channel and the capillary pump, wherein the cross-sectional area of the buffer tube is larger than the inlet channel. cross-sectional area of the sample channel. 3. The microfluidic chip according to claim 1, characterized in that, The first communication structure includes a balance channel connected to the corresponding reaction channel at one end and connected to the atmosphere at the other end. The cross-sectional area of the balance channel is smaller than the cross-sectional area of the reaction channel, where: The ends of the equilibrium channels are formed to be open to the atmosphere; or The end of the balancing channel includes a balancing cavity with a vertical through hole for communicating with the atmosphere. 4. The microfluidic chip according to claim 1, characterized in that the first communication structure includes a backbone connected to the corresponding reaction channel at one end and connected to the atmosphere at the other end, and a closed end branched from the backbone. branch. 5. The microfluidic chip of claim 1, wherein the one or more reaction units are configured to receive different preset volumes of sample microfluid from the sampling channel. 6. The microfluidic chip according to claim 1, wherein the difference between the depth of the sampling channel and the depth of the reaction channel is configured to allow the microfluid to cross the first step of the sampling channel and the reaction channel in the reaction channel. The connection point moves. 7. The microfluidic chip according to claim 1, characterized in that the ratio of the depth of the sampling channel to the depth of the reaction channel is less than 1:2. 8. The microfluidic chip according to claim 1, wherein the ratio of the depth of the sampling channel to the depth of the reaction channel is less than or equal to 1:4. 9. The microfluidic chip according to claim 1, characterized in that, The photodeformable material is configured to expand in response to exposure to light, such that a portion of the reaction channel has a larger cross-sectional area when exposed to light than when not exposed to light, thereby increasing the intensity of the light in the reaction channel. Decreasing direction driven microfluidics; or The photodeformable material is configured to shrink in response to exposure to light, such that a portion of the reaction channel has a smaller cross-sectional area when exposed to light than when not exposed to light, and thereby changes in the reaction channel toward the intensity of the light. Increasing direction drives microfluidics. 10. The microfluidic chip according to claim 1, characterized in that preset reactants are stored at one or more different positions in the reaction channel, and the sample microfluid can be activated by asymmetric light in the reaction channel. Under the action of the Laplace pressure difference generated by the deformation, it is driven to each of the one or more different positions to contact and mix and/or react with the preset reactant at that position. 11. The microfluidic chip according to claim 1, wherein each reaction unit in some or all of the one or more reaction units further includes: a second communication structure configured to communicate with the reaction channel at one end and with the atmosphere at the other end; a detection channel configured to communicate with the reaction channel at one end to receive the microfluid to be detected from the reaction channel, and to communicate with the atmosphere via a third communication structure at the other end, Wherein, the first distance between the third connection point and the first connection point of the reaction channel and the second connection structure along the first direction of the longitudinal centerline of the reaction channel is greater than the first distance between the first connection point and the second connection point along the reaction channel. The minimum distance between the longitudinal centerline of the channel and the second distance between the third connection point and the first connection point in the second direction opposite to the first direction along the longitudinal centerline of the reaction channel is greater than the first connection point and the second connection point. The minimum distance between points along the longitudinal centerline of the reaction channel, wherein the connection of each of the second connection structure and the third connection structure to the atmosphere is switchable, and Wherein, the cross-sectional area of the reaction channel is larger than the cross-sectional area of the detection channel. 12. The microfluidic chip according to claim 11, wherein the detection channel is arranged in a spiral shape. 13. The microfluidic chip according to claim 11, wherein each reaction unit includes at least two detection channels spaced apart from each other. 14. The microfluidic chip according to claim 11, wherein the detection channel is arranged inside the reaction channel. 15. The microfluidic chip according to claim 11, wherein the fourth connection point of the detection channel and the reaction channel coincides with the first connection point. 16. The microfluidic chip of claim 11, wherein each of the second communication structure and the third communication structure includes an opening open to the atmosphere, and wherein: A baffle is provided at the opening, and the baffle is movable between a first position that closes the opening and a second position that does not close the opening; or A photodeformable material is provided at the opening. The photodeformable material is configured not to close the opening when it is not exposed to light, but to photodeform to close the opening when it is exposed to light, or is configured to not close the opening when it is not exposed to light. When exposed to light, the opening will be closed and photo-induced deformation will occur so as not to close the opening. 17. The microfluidic chip according to any one of claims 1 to 16, characterized in that the microfluidic chip includes: a base plate having a sample inlet and a groove communicating with the sample inlet; and A photodeformable film attached to the substrate, the photodeformable film at least partially covers the groove to form a closed channel together with the groove, so that the microfluid can be pulled by the asymmetric photodeformation of the closed channel. It is driven through the closed channel under the action of Plath pressure difference, which closed channel provides at least the reaction channel. 18. The microfluidic chip according to any one of claims 1 to 16, characterized in that the microfluidic chip further includes a plurality of mutually independent microfluidic units. 19. The microfluidic chip according to any one of claims 1 to 16, characterized in that the microfluidic chip is used for at least one of the following: immune detection, biochemical detection, molecular detection, polymerase chain detection Reaction detection. 20. A microfluidic device, characterized in that the microfluidic device includes the microfluidic chip according to any one of claims 1 to 19 and is configured to provide illumination to the microfluidic chip to control Light source for microfluidic movement in microfluidic chips. 21. The microfluidic device according to claim 20, characterized in that, The light source is configured to be movable relative to the microfluidic chip to scan the illumination position on the microfluidic chip; or The light source includes an array of multiple light sources, each of the multiple light sources having a different illumination position on the microfluidic chip. 22. The microfluidic device according to claim 20, wherein the microfluidic device further includes one of the following: A light-shielding sheet is disposed between the microfluidic chip and the light source and is configured to allow a selectable portion of the reaction channel of the microfluidic chip to receive illumination from the light source while the remaining portion does not receive illumination from the light source, or is configured to allow the microfluidic chip to Selectable portions of the reaction channels of the chip are not illuminated by the light source while the remaining portions are illuminated by the light source; or A light attenuation sheet disposed between the microfluidic chip and the light source and configured such that the illumination of the light source received by a selectable portion of the reaction channel of the microfluidic chip is compared to the illumination of the light source received by the remaining portion of the reaction channel. Has attenuated intensity. 23. The microfluidic device according to claim 22, characterized in that, The microfluidic chip and light source are stationary, and The light shield or light attenuating plate is removable, enabling selection of different selectable portions of the reaction channels of the microfluidic chip. 24. A microfluidic device, characterized in that the microfluidic device includes: A light control module, the light control module includes a light source, the light source is configured to provide illumination to the microfluidic chip to control the movement of the microfluid in the microfluidic chip, the microfluid in the microfluidic chip is photodriven; and A moving module configured to move the microfluidic chip to adjust the relative position of the microfluidic chip and the light source, so that the microfluidic chip is selectively and locally illuminated by the light source. Thus, the microfluid in the microfluidic chip is driven by light, Wherein, the light control module is fixed above the mobile module. 25. The microfluidic device according to claim 24, wherein the microfluidic device further comprises: a detection module configured to perform detection on the microfluidic chip, Wherein, the moving module is further configured to move the microfluidic chip to adjust the relative position of the microfluidic chip and the detection module, so that the microfluidic chip is detected by the detection module, Wherein, the detection module is fixed above the mobile module and spaced apart from the light control module. 26. The microfluidic device according to claim 25, wherein the detection module includes a plurality of detection units, and the relative arrangement between the plurality of detection units corresponds to the plurality of detection units of the microfluidic chip. Relative arrangement between detection areas. 27. The microfluidic device according to claim 26, wherein the plurality of detection units include a fluorescence detection unit and an absorbance detection unit, and the detection point of the fluorescence detection unit is configured to be connected to the light control module. The light spots of the light sources coincide with each other, and the distance between the absorbance detection unit and the fluorescence detection unit is configured to be the same as the distance between the two detection areas of the microfluidic chip. 28. The microfluidic device according to claim 25, wherein the microfluidic device further comprises: A temperature control module configured to control the temperature of the microfluidic chip, wherein the temperature control module is arranged in the mobile module. 29. The microfluidic device according to claim 28, wherein the temperature control module is configured to provide a plurality of different temperature zones to the microfluidic chip, so that the corresponding multiple temperature zones of the microfluidic chip are The regions are at different temperatures, and the microfluidic device is used for temperature-variable polymerase chain reaction detection. 30. The microfluidic device according to claim 28, wherein the temperature control module is configured to provide a temperature zone to the microfluidic chip, so that each area of the microfluidic chip is at the same temperature. temperature, and wherein the microfluidic device is used for isothermal polymerase chain reaction detection. 31. The microfluidic device according to claim 24, characterized in that the microfluidic device is used for the microfluidic chip according to any one of claims 1 to 19.