Microfluidic chip and microfluidic device

Abstract

The present disclosure relates to a microfluidic chip and a microfluidic device. The microfluidic chip comprises: a sample inlet configured to receive a sample microfluid; a sample channel configured to communicate with the sample inlet to receive the sample microfluid from the sample inlet; a capillary pump configured to communicate with the sample channel to draw the sample microfluid through and out of the sample channel; and one or more liquid metering cavities, each of which is configured to communicate with the sample channel between the sample inlet and the capillary pump via a sample splitting channel corresponding to the liquid metering cavity to meter a preset volume of the sample microfluid corresponding to the liquid metering cavity from the sample channel, and is configured to communicate with the atmosphere via a first communication structure corresponding to the liquid metering cavity, wherein a cross-sectional area of the sample channel is greater than a cross-sectional area of the liquid metering cavity, the cross-sectional area of the liquid metering cavity is greater than a cross-sectional area of the sample splitting channel, and a cross-sectional area of the first communication structure corresponding to the liquid metering cavity on a side adjacent to the liquid metering cavity is greater than or equal to the cross-sectional area of the sample channel.

Description

Technical Field

[0001] This disclosure relates to the field of microfluidics, and more specifically, to a microfluidic chip and its operating method, and a microfluidic device. Background Technology

[0002] Microfluidics integrates complex microfluidic operations such as sample preparation, reaction, separation, and detection in biological, chemical, and medical analyses onto a single chip of just over ten square centimeters. This allows for automated completion of the entire analytical process, offering advantages such as high integration and high throughput. In microfluidic chips, the ability to precisely quantify minute samples (e.g., 10 microliters or less) can effectively improve detection accuracy, reduce sample loss, and is particularly beneficial for the precise detection of trace samples. However, traditional microfluidic chips require complex fluid channels and externally powered pump and valve assemblies to drive and control fluid movement to achieve precise quantification of minute samples. This is not only structurally complex and cumbersome to operate, making portability difficult, but also results in significant sample loss because the fluid driven by these pump and valve assemblies must be continuous and fill the entire upstream channel before the final quantification operation can be completed. Therefore, current microfluidic chips based on externally powered pump and valve assemblies cannot achieve truly precise quantification of minute samples. Summary of the Invention

[0003] A brief overview of this disclosure is given below to provide a basic understanding of some aspects of it. However, it should be understood that this overview is not an exhaustive summary of this disclosure. It is not intended to identify key or essential parts of this disclosure, nor is it intended to limit the scope of this disclosure. Its purpose is merely to present certain concepts of this disclosure in a simplified form as a prelude to the more detailed description that follows.

[0004] According to one aspect of this disclosure, a microfluidic chip is provided, comprising: an inlet configured to receive sample microfluidic fluid; an inlet channel configured to communicate with the inlet to receive sample microfluidic fluid from the inlet; a capillary pump configured to communicate with the inlet channel to draw sample microfluidic fluid through and out of the inlet channel; and one or more volumetric chambers, each volumetric chamber being configured to communicate with the inlet channel via a dispensing channel corresponding to the volumetric chamber between the inlet and the capillary pump to measure a preset volume of sample microfluidic fluid corresponding to the volumetric chamber from the inlet channel, and being configured to communicate with the atmosphere via a first communication structure corresponding to the volumetric chamber, wherein the cross-sectional area of ​​the inlet channel is larger than the cross-sectional area of ​​the volumetric chamber, the cross-sectional area of ​​the volumetric chamber is larger than the cross-sectional area of ​​the dispensing channel, and the cross-sectional area of ​​the first communication structure corresponding to the volumetric chamber on the side adjacent to the volumetric chamber is greater than or equal to the cross-sectional area of ​​the inlet channel.

[0005] According to another aspect of this disclosure, a microfluidic device is provided, which includes a microfluidic chip according to embodiments of this disclosure.

[0006] According to another aspect of this disclosure, a microfluidic device is provided, comprising a microfluidic chip as described in embodiments of this disclosure and a light source configured to provide illumination to the microfluidic chip to control the movement of microfluidics within the microfluidic chip.

[0007] Other features and advantages of this disclosure will become clearer from the following detailed description of exemplary embodiments with reference to the accompanying drawings. Attached Figure Description

[0008] The accompanying drawings, which form part of this specification, illustrate embodiments of the present disclosure and, together with the specification, serve to explain the principles of the disclosure. The embodiments set forth in the drawings are illustrative and exemplary in nature and are not intended to limit the scope of the disclosure. The following detailed description of exemplary embodiments will be clearly understood when read in conjunction with the following drawings, wherein similar structures are indicated by similar reference numerals, and wherein:

[0009] Figures 1 to 9 This is a schematic diagram illustrating a microfluidic chip according to some embodiments of the present disclosure;

[0010] Figure 10 This is a schematic diagram illustrating a non-limiting example process of photo-driven microfluidics in a microfluidic chip according to an embodiment of the present disclosure;

[0011] Figure 11 and Figure 12 This is a flowchart illustrating a method of operating a microfluidic chip according to some embodiments of the present disclosure;

[0012] Figures 13 to 17 This is a schematic diagram illustrating a microfluidic device according to some embodiments of the present disclosure. Detailed Implementation

[0013] Various exemplary embodiments of the present disclosure will now be described in detail with reference to the accompanying drawings. It should be noted that, unless otherwise specifically stated, the relative arrangement, numerical expressions, and values ​​of the components and steps set forth in these embodiments do not limit the scope of the present disclosure.

[0014] The following description of at least one exemplary embodiment is merely illustrative and is in no way intended to limit the scope of this disclosure or its application or use. That is, the structures and methods herein are shown in an exemplary manner to illustrate different embodiments of the structures and methods in this disclosure. However, those skilled in the art will understand that they merely illustrate exemplary ways that can be used to implement this disclosure, and not exhaustive ways. Furthermore, the drawings are not necessarily drawn to scale, and some features may be enlarged to show details of specific components.

[0015] In addition, techniques, methods and equipment known to those skilled in the art may not be discussed in detail, but where appropriate, such techniques, methods and equipment should be considered part of the specification.

[0016] In all examples shown and discussed herein, any specific values ​​should be interpreted as merely exemplary and not as limitations. Therefore, other examples of exemplary embodiments may have different values.

[0017] This disclosure provides a microfluidic chip that can drive fluid through a Laplace pressure differential (capillary force) generated by a capillary pump, thereby enabling contactless quantitative measurement of micro-samples. Since the microfluidic chip according to this disclosure does not require an externally powered pump-valve assembly to drive the fluid, it has low requirements for fluid continuity, low sample loss, and a small number of components and overall size for the microfluidic chip and its associated equipment. The microfluidic chip according to various embodiments of this disclosure will now be described in detail with reference to the accompanying drawings. It should be understood that actual microfluidic chips may include other components, but to avoid obscuring the key points of this disclosure, these other components will not be discussed herein and are not shown in the drawings. It should also be understood that various embodiments can be combined with each other, but for the sake of brevity, the drawings only exemplarily illustrate some combinations of these embodiments.

[0018] Figure 1 A microfluidic chip 100 according to some embodiments of the present disclosure is shown. For example... Figure 1 As shown, the microfluidic chip 100 includes an inlet 101, an inlet channel 102, a capillary pump 103, and one or more volumetric chambers 1041-1044. The inlet 101 is configured to receive sample microfluidics. The inlet channel 102 is configured to communicate with the inlet 101 to receive sample microfluidics from the inlet 101. For example, sample microfluidics can be dropped onto the inlet 101 to fill it, and then extend a distance into the inlet channel 102. Additionally, in this document, a cross-section refers to a plane containing the width and depth, perpendicular to the direction of length. Figures 1 to 9The planes shown in the diagrams are the planes containing the width and length, but it should be noted that these diagrams are provided for illustrative purposes and are not necessarily drawn to scale. In some embodiments, the cross-sectional area of ​​the inlet 101 may be greater than or equal to the cross-sectional area of ​​the inlet channel 102. This can facilitate the spontaneous entry of sample microfluidics from the inlet 101 into the inlet channel 102. It should be understood that this disclosure is not limited to adding sample microfluidics to the inlet 101. In some embodiments, the inlet 101 may also be connected to other channels, cavities, etc., on the microfluidic chip 100 to receive sample microfluidics therefrom. For example, the inlet 101 may be connected to a pre-reaction unit to receive sample microfluidics to be detected after the reaction is complete.

[0019] Capillary pump 103 is configured to communicate with sample inlet channel 102 to draw sample microfluidic fluid through and out of sample inlet channel 102. Capillary pump 103 may generally consist of a combination of multiple capillary channels, each with a cross-sectional area much smaller than the cross-sectional area of ​​the individual channels of microfluidic chip 100, and the ends of these capillary channels are configured to be open to the atmosphere. Therefore, after sample microfluidic fluid enters sample inlet channel 102, it is driven through sample inlet channel 102 by the Laplace pressure difference generated by capillary pump 103 and ultimately drawn away by capillary pump 103. In some embodiments, such as... Figure 1 As shown, the capillary pump 103 may include multiple microchannels arranged in a tree-like pattern. This structure can effectively increase the capillary force generated by the capillary pump on the one hand, and increase the amount of liquid that the capillary pump can hold on the other hand, further improving the utilization rate of the microfluidic chip 100. It should be understood that the illustrated structure of the capillary pump 103 is merely for providing an illustrative example and is not intended to limit this disclosure.

[0020] Each volumetric fluid chamber 1041-1044 is configured to communicate with the injection channel 102 between the injection port 101 and the capillary pump 103 via a corresponding dispensing channel 1051-1054 to measure a preset volume of sample microfluidic fluid corresponding to the volumetric fluid chamber from the injection channel 102, and is configured to communicate with the atmosphere via a first communication structure 1061-1064 corresponding to the volumetric fluid chamber. Figure 1As shown, the volumetric fluid chamber 1041 is connected to the sample inlet channel 102 via the sample dispensing channel 1051 to measure a first preset volume of sample microfluidic fluid from the sample inlet channel 102 and is connected to the atmosphere via the first connecting structure 1061. The volumetric fluid chamber 1042 is connected to the sample inlet channel 102 via the sample dispensing channel 1052 to measure a second preset volume of sample microfluidic fluid from the sample inlet channel 102 and is connected to the atmosphere via the first connecting structure 1062. The volumetric fluid chamber 1043 is connected to the sample inlet channel 102 via the sample dispensing channel 1053 to measure a third preset volume of sample microfluidic fluid from the sample inlet channel 102 and is connected to the atmosphere via the first connecting structure 1063. The volumetric fluid chamber 1044 is connected to the sample inlet channel 102 via the sample dispensing channel 1054 to measure a fourth preset volume of sample microfluidic fluid from the sample inlet channel 102 and is connected to the atmosphere via the first connecting structure 1064. The dispensing channels 1051-1054 can be used as liquid bridges between the volumetric liquid chambers 1041-1044 and the injection channel 102.

[0021] In the microfluidic chip 100, the cross-sectional area of ​​the sample inlet channel 102 is larger than the cross-sectional area of ​​the volumetric liquid chambers 1041-1044. This facilitates the entry of the microfluidic fluid from the sample inlet channel 102 into the volumetric liquid chambers 1041-1044 under the influence of the Laplace pressure difference. The cross-sectional area of ​​the first connecting structures 1061-1064 on the side adjacent to the corresponding volumetric liquid chambers 1041-1044 is greater than or equal to the cross-sectional area of ​​the sample inlet channel 102. This prevents the microfluidic fluid from overflowing into the first connecting structures 1061-1064 or even leaking into the atmosphere after filling the volumetric liquid chambers 1041-1044. The cross-sectional area of ​​the volumetric liquid chambers 1041-1044 is larger than the cross-sectional area of ​​the dispensing channels 1051-1054. The dispensing channels 1051-1054 can be the finest channels in the microfluidic chip 100, and their volume can be configured to be negligible compared to the volume of the volumetric chambers 1041-1044. Therefore, the preset volume of the sample microfluidic fluid measured can be approximately equal to the volume of the volumetric chambers 1041-1044. It can be understood that even if the volume of the dispensing channels 1051-1054 is not negligible compared to the volume of the volumetric chambers 1041-1044, it does not affect the quantitative measurement of the microfluidic chip 100; however, the preset volume of the sample microfluidic fluid measured will be equal to the sum of the volumes of the volumetric chambers 1041-1044 and the dispensing channels 1051-1054.

[0022] Thus, after the sample microfluidic enters the injection channel 102 through the inlet 101, it travels through the injection channel 102 under the Laplace pressure difference generated by the capillary pump 103. Upon reaching the connection point between each dispensing channel and the injection channel 102, it enters and fills the corresponding volumetric chamber via the dispensing channel. After each volumetric chamber is filled with sample microfluidic, the sample microfluidic remaining in the injection channel 102 continues to travel through it until it is drawn away by the capillary pump 103. In this way, multiple independent sample microfluidic samples are formed in each volumetric chamber. It can be seen that this measurement process is spontaneously achieved under the action of the Laplace pressure difference, without the need for any externally powered pump or valve assembly, nor requiring the sample microfluidic to continuously fill the channel preceding the volumetric chamber.

[0023] It should be understood that, although Figure 1 Four volumetric cavities 1041-1044 are shown, but this is merely exemplary and not limiting. The microfluidic chip 100 may include one, two, three, four, five, or more volumetric cavities as needed, for example, it may include a dozen or even dozens of volumetric cavities. It should also be understood that different cross-sectional areas of the channels designed above can be achieved by controlling the channel width to be the same while changing the channel depth, or by controlling the channel depth to be the same while changing the channel width, or by simultaneously changing the channel depth and width. In some cases, achieving different cross-sectional areas of the channels by controlling the channel width to be the same while changing the channel depth may be preferred. For example, when forming channels using a high-precision Computerized Numerical Control (CNC) machine tool, controlling the channel width to be the same while changing the channel depth may be more convenient to implement.

[0024] In some embodiments, each of the dispensing channels 1051-1054 may include a first portion connected to the injection channel 102 and a second portion connecting the first portion to the corresponding volumetric chamber 1041-1044. The depth of the first portion is less than the depth of the injection channel 102, and the depth of the second portion varies from a first depth at the location where the second portion connects to the first portion to a second depth at the location where the second portion connects to the volumetric chamber, where the first depth is equal to the depth of the first portion and the second depth is equal to the depth of the volumetric chamber. This facilitates the flow of sample microfluidic from the dispensing channel into the volumetric chamber. In some examples, the bottom surface of the second portion of the dispensing channel may be formed as a slope, which may be, for example, flat or curved. In other embodiments, the bottom surface of the second portion of the dispensing channel may be formed as multiple steps. Additionally, to facilitate the flow of sample microfluidic from the injection channel 102 into the dispensing channel, in some embodiments, a depth transition may be provided in the portions of the dispensing channels 1051-1054 connected to the injection channel 102.

[0025] refer to Figure 2 In some embodiments, the microfluidic chip 100 may further include a buffer tube 107 connected between the sample inlet 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 sample inlet channel 102. In some embodiments, the buffer tube 107 may include one or more interconnected U-shaped tubes. The arrangement of the buffer tube 107 can help prevent the sample microfluidic fluid from being drawn away by the capillary pump before filling the volumetric fluid chamber. In other words, the arrangement of the buffer tube 107 can help ensure that the sample microfluidic fluid is drawn away by the capillary pump only after the volumetric fluid chamber is filled. The arrangement of the buffer tube 107 can also prevent the sample microfluidic fluid from flowing back from the capillary pump 103 to the sample inlet channel 102. Alternatively, instead of providing the buffer tube 107, the end portion of the sample inlet channel 102 near the capillary pump 103 may be formed into multiple interconnected bends and / or the bottom surface of the end portion of the sample inlet channel 102 near the capillary pump 103 may be formed into multiple steps, which can also provide a buffer area for the sample microfluidic fluid.

[0026] In some embodiments, the first connecting structure 1061-1064 may include a balancing cavity communicating with the corresponding volumetric cavities 1041-1044 and having a vertical through-hole for communication with the atmosphere, the cross-sectional area of ​​which is greater than or equal to the cross-sectional area of ​​the injection channel 102. For example, Figure 1 and Figure 2 As shown. In some embodiments, the first connecting structure 1061-1064 may include a balance channel that is connected at one end to the corresponding volumetric chamber 1041-1044 and at the other end to the atmosphere. The cross-sectional area of ​​the balance channel is greater than or equal to the cross-sectional area of ​​the injection channel 102, for example, as shown. Figure 3 As shown. Figure 1 and Figure 2 Compared to the first connected structure Figure 3 The first connecting structure can have a significantly shortened length, which can make the layout of the microfluidic chip 100 more compact and reduce the processing difficulty of the microfluidic chip 100.

[0027] In some embodiments, the communication between the first connecting structures 1061-1064 and the atmosphere is switchable, and when the first connecting structure is not connected to the atmosphere, the measuring chamber corresponding to the first connecting structure stops measuring. The communication between the connecting structures and the atmosphere can be controlled by any suitable switching mechanism. In some examples, a movable baffle or other closing structure can be provided at the opening of the connecting structure that is open to the atmosphere (e.g., a through-hole in the balancing chamber), the baffle being movable between a first position closing the opening and a second position not closing the opening. In some examples, baffles for multiple connecting structures can be integrated onto the same baffle plate, thereby enabling the switching of different connecting structures or combinations thereof by moving the baffle plate as a whole. In some embodiments, the communication between the connecting structure and the atmosphere can be controlled by a photoresponsive switching mechanism. Such a photoresponsive switching mechanism may include a photodeformable material. In some examples, the photodeformable material may not close the opening of the connecting structure when not exposed to light, but may undergo photodeformation (e.g., expansion) to close the opening of the connecting structure when exposed to light. In other examples, the photodeformable material can close the opening of the interconnected structure when not exposed to light, but undergo photodeformation (e.g., shrinkage) when exposed to light to leave the opening open. For example, a chamber containing a photodeformable gel can be provided at the opening of the interconnected structure, or a thin film or plate formed of a photodeformable material can be provided at the opening of the interconnected structure.

[0028] By controlling whether the first connecting structures 1061-1064 are connected to the atmosphere, it is possible to control whether the corresponding volumetric chambers 1041-1044 perform volumetric operations. For example, when the first connecting structures 1061 and 1062 are connected to the atmosphere while the first connecting structures 1063 and 1064 are not connected to the atmosphere, the sample microfluidic fluid in the sample injection channel 102 will only enter and fill the volumetric chambers 1041 and 1042, and will not enter the volumetric chambers 1043 and 1044. Finally, after the sample microfluidic fluid is drawn away by the capillary pump 103, only the volumetric chambers 1041 and 1042 contain sample microfluidic fluid, while the volumetric chambers 1043 and 1044 are empty.

[0029] In some embodiments, the volumetric chamber of the microfluidic chip 100 includes a first volumetric chamber communicating with the injection channel via a first dispensing channel and a second volumetric chamber communicating with the injection channel via a second dispensing channel. In some examples, the first and second volumetric chambers are located on the same side of the injection channel. In some examples, the first and second volumetric chambers are located on different sides of the injection channel, and the first and second dispensing channels are aligned with each other. In some examples, the first and second volumetric chambers are located on different sides of the injection channel, and the first and second dispensing channels are offset from each other. For example, as... Figure 1 As shown, volumetric cavities 1041-1044 are all located on the same side of the sample inlet channel 102; as Figure 2 As shown, volumetric cavities 1041 and 1043 are located above the injection channel 102, while volumetric cavities 1042 and 1044 are located below the injection channel 102. Furthermore, dispensing channels 1051 and 1052 are aligned with each other, and dispensing channels 1053 and 1054 are aligned with each other. Figure 3 As shown, volumetric cavities 1041 and 1043 are located on the upper side of the injection channel 102, while volumetric cavities 1042 and 1044 are located on the lower side of the injection channel 102. Furthermore, dispensing channels 1051 and 1052 are offset from each other, as are dispensing channels 1053 and 1054. In some cases, distributing the volumetric cavities on different sides of the injection channel 102 can facilitate a more compact layout of the microfluidic chip 100.

[0030] In some embodiments, the preset volume corresponding to each volumetric fluid chamber of the microfluidic chip 100 may be the same, for example, Figures 1 to 3 As shown. In some embodiments, the preset volume corresponding to each volumetric cavity of the microfluidic chip 100 may be different from the preset volumes corresponding to other volumetric cavities. In some embodiments, the preset volume corresponding to each volumetric cavity of the microfluidic chip 100 may not be an integer multiple of the preset volumes corresponding to other volumetric cavities. Figure 4 In this configuration, the first preset volume corresponding to volumetric volume 1041 is smaller than the second preset volume corresponding to volumetric volume 1042, smaller than the third preset volume corresponding to volumetric volume 1043, and smaller than the fourth preset volume corresponding to volumetric volume 1044. For example, the volumes of volumetric volumes 1041-1044 can be 50 nanoliters, 100 nanoliters, 150 nanoliters, and 200 nanoliters, or 200 nanoliters, 300 nanoliters, 500 nanoliters, and 700 nanoliters, etc.

[0031] like Figures 1 to 4As shown, each volumetric volumetric cavity in volumetric cavities 1041-1044 (or, when the connection between the first connecting structure 1061-1064 and the atmosphere is switchable, the corresponding volumetric volumetric cavity connected to the atmosphere) can independently measure a corresponding volume of sample microfluidic fluid. The sample microfluidic fluid in the volumetric cavity can be directly detected at the volumetric cavity, for example, by fluorescence detection or absorbance detection. Alternatively, the sample microfluidic fluids measured from each volumetric cavity can be mixed together for reaction. (Reference) Figure 5 In some embodiments, the microfluidic chip 100 may further include a reaction channel 108 configured to communicate with each volumetric cavity via a sample outlet channel 1091-1094 corresponding to each volumetric cavity 1041-1044 to receive a preset volumetric microfluidic sample corresponding to that volumetric cavity. Specifically, the reaction channel 108 includes a photodeformable material such that the microfluidic fluid can be driven (also referred to herein as photodriven) through the reaction channel 108 (to be described later in conjunction with...) by a Laplace pressure difference generated by the asymmetric photodeformation of the reaction channel 108. Figure 10 (The process of photo-driven microfluidics described in this article is described in detail.) The cross-sectional area of ​​the volumetric cavities 1041-1044 is larger than that of the reaction channel 108, and the cross-sectional area of ​​the reaction channel 108 is larger than that of the sample outlet channels 1091-1094. The cross-sectional area of ​​the sample outlet channels 1091-1094 can, for example, be the same as that of the sample dispensing channels 1051-1054. The sample outlet channels 1091-1094 can be used as a liquid bridge between the volumetric cavities 1041-1044 and the reaction channel 108. In such an embodiment, when the sample microfluidic enters the sample dispensing channels 1051-1054, it will not only fill the sample dispensing channels 1051-1054 and the volumetric cavities 1041-1044, but also fill the sample outlet channels 1091-1094. Similar to the dispensing channels 1051-1054, the dispensing channels 1091-1094 can also be the finest channels in the microfluidic chip 100, and their volumes can be configured to be negligible compared to the volumes of the volumetric chambers 1041-1044. Therefore, the preset volume of the measured sample microfluidic fluid can be approximately equal to the volume of the volumetric chambers 1041-1044. It is understood that even if the volumes of the dispensing channels 1051-1054 and the dispensing channels 1091-1094 are not negligible compared to the volumes of the volumetric chambers 1041-1044, it does not affect the quantitative measurement of the microfluidic chip 100; however, the preset volume of the measured sample microfluidic fluid will be equal to the sum of the volumes of the volumetric chambers 1041-1044, the dispensing channels 1051-1054, and the dispensing channels 1091-1094.

[0032] Furthermore, the depth of reaction channel 108 is greater than the depth of sample outlet channels 1091-1094. Due to the depth difference between sample outlet channels 1091-1094 and reaction channel 108, a step is formed at the connection point of sample outlet channels 1091-1094 and reaction channel 108. This step at the connection point of sample outlet channels 1091-1094 and reaction channel 108 prevents the sample microfluidic from spontaneously flowing into reaction channel 108 under the action of surface tension after filling volumetric fluid chambers 1041-1044 and then sample outlet channels 1091-1094. Instead, the sample microfluidic stops at the connection point of sample outlet channels 1091-1094 and reaction channel 108 within sample outlet channels 1091-1094, thus acting as a brake on the sample microfluidic and ensuring that volumetric fluid chambers 1041-1044 can accurately perform quantitative measurement operations. In some embodiments, the difference between the depth of the sample outlet channels 1091-1094 and the depth of the reaction channel 108 can be configured to allow the microfluidic fluid to move across the junction of the sample outlet channels 1091-1094 and the reaction channel 108 within the reaction channel 108. Since the Laplace pressure differential generated by asymmetric photodeformation can only advantageously overcome flow resistance to drive fluid in a straight-through conduit with low flow resistance, a significant difference is required between the depth of the sample outlet channels 1091-1094 and the depth of the reaction channel 108. If the depth of the sample outlet channels 1091-1094 is close to the depth of the reaction channel 108, then the pipe shape of the reaction channel 108 at the connection points between the sample outlet channels 1091-1094 and the reaction channel 108 (approaching a T-junction) changes significantly compared to the pipe shape of the reaction channel 108 outside these connection points (a straight pipe). This hinders the photodynamic actuation of the microfluidics within the reaction channel 108, making it difficult for the microfluidics to move freely from one end of the reaction channel 108 across these connection points. Furthermore, in some examples, the ratio of the depth of the sample outlet channels 1091-1094 to the depth of the reaction channel 108 is less than 1:2. In some examples, the ratio of the depth of the sample outlet channels 1091-1094 to the depth of the reaction channel 108 is less than or equal to 1:4. When the ratio of the depth of the sample outlet channels 1091-1094 to the depth of the reaction channel 108 meets the following requirements, it can effectively prevent the microfluidic from spontaneously entering the reaction channel 108 after filling the volumetric liquid chambers 1041-1044 and then the sample outlet channels 1091-1094. It can also reduce the influence of the connection point between the sample outlet channels 1091-1094 and the reaction channel 108 on the photo-driven microfluidic flow within the reaction channel 108.

[0033] The depth and width dimensions of each channel in the microfluidic chip 100 described in this article can be, for example, 10⁻¹⁰. 3Within the micrometer range. In some embodiments, the width and depth of each of the sample inlet channel 102, sample dispensing channels 1051-1054, volumetric cavities 1041-1044, sample outlet channels 1091-1094, and reaction channel 108 are between 10 micrometers and 2000 micrometers, respectively, for example, between 50 micrometers and 1000 micrometers. Within such a range, the fabrication difficulty of the microfluidic chip 100 is moderate, and the performance of the photo-driven fluid is also good. In a non-limiting example, the width and depth of the injection channel 102 can be 300 micrometers, the width and depth of the volumetric cavities 1041-1044 can be 400 micrometers, the width and depth of the reaction channel 108 can be 200 micrometers, the width and depth of the dispensing channels 1051-1054 and the outlet channels 1091-1094 can be 200 micrometers and the depth can be 50 micrometers, and the volume of the volumetric cavities 1041-1044 can be 400 nanoliters. Based on these dimensions, it can be determined that the fluid volume within the dispensing channels 1051-1054 and the outlet channels 1091-1094 has a negligible impact on measurement accuracy. In some examples, the volume of the volumetric cavities 1041-1044 can be between 50 nanoliters and 1000 nanoliters, or between 100 nanoliters and 700 nanoliters. Since the volume of the volumetric cavities 1041-1044 can be very small, the measurement of such a preset volume of microfluidic sample can be regarded as a simple and accurate quantitative measurement of trace samples. However, those skilled in the art will understand that the volume of the volumetric cavities 1041-1044 can be determined according to the specific application scenario of the microfluidic chip 100 when designing the specific volumetric cavities 1041-1044.

[0034] Reference Figure 1 and Figure 10 In some embodiments, the microfluidic chip 100 may include a substrate 10 having an inlet 101 and a groove communicating with the inlet 101 thereon, and a photodeformation film 20 attached to the substrate 10 (for clarity, in...). Figures 1 to 9 In China only Figure 1 The substrate 10 is shown in the figure, and in Figures 1 to 9(The photodeformation film 20 is not shown in the diagram). The photodeformation film 20 at least partially covers the groove, thus forming a closed channel 30 together with the groove. This allows the microfluidic fluid to be driven through the closed channel 30 under the Laplace pressure difference generated by the asymmetric photodeformation of the closed channel 30. The closed channel 30 may at least provide a reaction channel 108. In some embodiments, the closed channel 30 may also provide other channels of the microfluidic chip 100, such as sample inlet channel 102, sample dispensing channels 1051-1054, volumetric cavities 1041-1044, sample outlet channels 1091-1094, etc. However, even if the upper surface of these other channels is formed by the photodeformation film 20, the fluid in them will not be photodriven when their upper surfaces do not undergo photodeformation. For example, grooves can be formed on the substrate 10 by CNC machining as the bottom and side surfaces of the closed channel 30, and after CNC machining is completed, the photodeformation film 20 is covered on the grooves as the upper surface of the closed channel 30 to obtain a complete channel structure. In some embodiments, to reduce the difficulty of CNC machining and improve measurement accuracy, the cross-sectional shape of the channel can be rectangular. However, this is merely exemplary and not limiting; the channel can also have other suitable cross-sectional shapes. In some examples, the substrate 10 can be an acrylic substrate, which not only meets the material requirements of microfluidic chips and CNC machining but also has good transparency, making it easier to observe the microfluidic state within the microfluidic chip. The photodeformable material can be any suitable photodeformable material known now or to be developed later. In some examples, the photodeformable material can include a photodeformable liquid crystal polymer, for example, a single film made of a photodeformable liquid crystal polymer can be used as the photodeformable film 20. In some examples, the photodeformable liquid crystal polymer can include a photoresponsive linear liquid crystal polymer with a polycyclooctene main chain and azobenzene side chains. In some embodiments, the substrate 10 and the photodeformable film 20 can be recyclable and reusable. For example, used but undamaged acrylic substrates can be recycled as brand-new components to produce new microfluidic chips after thorough cleaning and drying. Similarly, thin films made of photodeformable liquid crystal polymers can be prepared by dissolving and extracting the original material and then re-preparing it into thin films for the production of new microfluidic chips.

[0035] When specific illumination conditions are met, the photodeformable material (e.g., the photodeformable film 20) can undergo localized photodeformation, resulting in a change in the cross-sectional area of ​​the local channel. Under the influence of the Laplace pressure difference, the fluid within the channel will move in the direction of decreasing cross-sectional area. In some embodiments, the photodeformable material (e.g., the photodeformable film 20) is configured to expand in response to illumination, such that a portion of the reaction channel 108 has a larger cross-sectional area when illuminated compared to when not illuminated, thereby driving the microfluidic in the reaction channel 108 in the direction of decreasing light intensity. In some embodiments, the photodeformable material (e.g., the photodeformable film 20) is configured to contract in response to illumination, such that a portion of the reaction channel 108 has a smaller cross-sectional area when illuminated compared to when not illuminated, thereby driving the microfluidic in the reaction channel 108 in the direction of increasing light intensity.

[0036] refer to Figure 10 The diagram illustrates the plane containing the length and depth, using the case of photosensitive expansion of the photodeformation film 20 as a non-limiting example: The microfluidic 40 is at position a (represented by the position of the left end face of the microfluidic 40), and the cross-sectional areas of each part of the closed channel 30 are initially the same. After irradiating the photodeformation film 20 at position a with light capable of causing expansion, the portion of the photodeformation film 20 at position a expands due to light, resulting in an increase in the cross-sectional area of ​​the portion of the closed channel 30 at position a, which is larger than the cross-sectional area of ​​the portion of the closed channel 30 at position b. This asymmetric photodeformation of the closed channel 30 at positions a and b generates a Laplace pressure difference, and under the influence of this Laplace pressure difference, the microfluidic 40 spontaneously moves from position a with a larger cross-sectional area to position b with a smaller cross-sectional area, thus achieving photo-driven microfluidic 40. Using this principle, the photo-driven microfluidic 40 can be precisely controlled by controlling the position and intensity of the light illumination. This photodynamic actuation method requires no external driving device; it can achieve contactless actuation of microfluidics using only a suitable light source. Furthermore, it offers high actuation precision.

[0037] In some embodiments, a pre-placed microfluidic fluid (not shown) is stored in the reaction channel 108 at a location separated from the sample outlet channels 1091-1094. This pre-placed microfluidic fluid can be driven to the connection point between the sample outlet channels 1091-1094 and the reaction channel 108 by a Laplace pressure difference generated by the asymmetric photodeformation of the reaction channel 108, so as to contact and mix with the sample microfluidic fluid received from the volumetric cavities 1041-1044 within the reaction channel 108. The pre-placed microfluidic fluid may be added to the reaction channel 108 during the use phase of the microfluidic chip 100 (e.g., via a separate inlet, different from the inlet 101, directly connected to the reaction channel 108), or it may be added to the reaction channel 108 in advance during the manufacturing phase of the microfluidic chip 100.

[0038] For the sake of brevity, the following description assumes that all of the first connecting structures 1061-1064 are connected to the atmosphere. However, those skilled in the art can similarly understand, based on the teachings of this disclosure, the situation where only some of the first connecting structures 1061-1064 are connected to the atmosphere. For example, after the sample microfluidic in the sample inlet channel 102 is separated from the sample microfluidic in the sample outlet channels 1051-1054, the pre-placed microfluidic in the reaction channel 108 is photo-driven to the connection point between the sample outlet channels 1091-1094 and the reaction channel 108. This causes the pre-placed microfluidic in the reaction channel 108 to come into contact with the sample microfluidic in the sample outlet channels 1091-1094. Consequently, the sample microfluidic in the volumetric cavities 1041-1044 spontaneously enters the reaction channel 108 under the influence of the Laplace pressure difference generated by the cross-sectional area of ​​the volumetric cavities 1041-1044 being larger than that of the reaction channel 108, and mixes with the pre-placed microfluidic in the reaction channel 108 to obtain a first mixed microfluidic. The first mixed microfluidic is a mixture of a pre-set microfluidic and a sample microfluidic, the volume of which is equal to the sum of the pre-set volumes corresponding to the volumetric chambers 1041-1044. It can be understood that when a mixture of the pre-set microfluidic and multiple sample microfluidics is needed, a sample microfluidic can be measured again following a process similar to that described above. For example, after obtaining the first mixed microfluidic, it can be photo-driven away from the connection point between the sample outlet channels 1091-1094 and the reaction channel 108 in the reaction channel 108, and then the sample microfluidic is received again through the inlet 101, causing the sample microfluidic to re-enter the dispensing channels 1051-1054 from the inlet channel 102 and fill the dispensing channels 1051-1054, volumetric chambers 1041-1044, and sample outlet channels 1091-1094. Next, the capillary pump 103 extracts the sample microfluidic still remaining in the inlet channel 102, removing it from the inlet channel 102 and the dispensing channel. The connection point of channels 1051-1054 allows the sample microfluidic in the sample inlet channel 102 to be separated from the sample microfluidic in the sample outlet channels 1051-1054. Then, the first mixed microfluidic in the reaction channel 108 is photo-driven to the connection point between the outlet channels 1091-1094 and the reaction channel 108, causing the first mixed microfluidic in the reaction channel 108 to contact the sample microfluidic in the outlet channels 1091-1094. This allows the sample microfluidic in the volumetric chambers 1041-1044 to enter the reaction channel 108 and mix with the first mixed microfluidic in the reaction channel 108 to obtain a second mixed microfluidic. The second mixed microfluidic is a mixture of a pre-placed microfluidic and two sample microfluidics. The structure of the microfluidic chip 100 allows for repeated operation, enabling the multiple measurement of trace samples of the same or different volumes (depending on the on / off state of the first communication structure's connection to the atmosphere).Therefore, by using the microfluidic chip 100 and its photo-driven fluid method, mixtures of pre-placed microfluidics and sample microfluidics of various volumes can be easily prepared.

[0039] To facilitate photodynamic actuation of the microfluidics in the reaction channel 108, in some embodiments, the reaction channel 108 may be configured to remain in communication with the atmosphere; for example, at least one end of the reaction channel 108 may be open to the atmosphere, such as... Figure 5 As shown. In other embodiments, the reaction channels 108 may also be arranged in a ring. The ring only requires that the channels are connected end to end, and there is no limitation on the channel outline. For example, the outline of the ring channel can be various suitable shapes such as polygons such as triangles, quadrilaterals, pentagons, circles, ellipses, etc. In this way, the gas in the reaction channel 108 is less likely to hinder the photo-driven microfluidics in the reaction channel 108.

[0040] It is important to note that during the quantitative measurement process, the fluid in the injection channel 102 and the fluid in the reaction channel 108 must be prevented from being connected to the dispensing channel and the outlet channel at the same time. Otherwise, the fluid will flow continuously from the injection channel 102 through the dispensing channel and the outlet channel into the reaction channel 108 under the action of the Laplace pressure difference, thus losing the function of quantitative measurement.

[0041] In some embodiments, the sample injection channel 102, the volumetric liquid chambers 1041-1044, and the reaction channel 108 can be arranged in parallel with each other, for example... Figure 5 As shown, this allows for a more compact layout and smaller volume of the microfluidic chip 100. In some embodiments, the sample inlet channel 102 can be configured as a U-shaped channel, and the sample dispensing channels 1051-1054 can be connected downstream of the bend in the U-shaped channel. This helps maintain the flow rate and volume of the sample microfluidic at the inlet 101 within the sample inlet channel 102 within a controllable range. The bend in the U-shaped channel also effectively achieves buffering and liquid storage effects, and reduces the footprint of the sample inlet channel 102 in the microfluidic chip 100, making the arrangement of the sample inlet channel 102 more rational. In some embodiments, the sample dispensing channels 1051-1054 and the sample outlet channels 1091-1094 can be aligned with each other. In other embodiments, such as Figure 5 As shown, the sample distribution channels 1051-1054 and the sample outlet channels 1091-1094 can be staggered from each other. For example, the intersection of the virtual extension line of the sample outlet channel 1091-1094 and the sample inlet channel 102 can be located downstream of the connection point between the corresponding sample distribution channel 1051-1054 and the sample inlet channel 102.

[0042] In such Figure 5In the illustrated embodiment, volumetric cavities 1041-1044 are located on the same side of the injection channel 102 and are commonly connected to the same reaction channel 108. When multiple volumetric cavities are located on different sides of the injection channel 102, they can still be arranged to be commonly connected to the same reaction channel 108, but they can also be arranged such that the volumetric cavities located on each side of the injection channel 102 are respectively commonly connected to a corresponding reaction channel (e.g., as shown). Figure 8 (As shown). That is, some or all of the volumetric cavities of the microfluidic chip 100 can be arranged to share a reaction channel. In other words, the volumetric cavities and reaction channels can be configured in a many-to-one ratio. In other embodiments, each volumetric cavity of the microfluidic chip 100 can be connected to a corresponding reaction channel. That is, the volumetric cavities and reaction channels can be configured in a one-to-one ratio.

[0043] Additionally, as previously mentioned, the pre-placed microfluidic in the reaction channel can be added to the reaction channel during the use phase of the microfluidic chip 100. In some embodiments, the reaction channel may be connected to the atmosphere at one end via a second communication structure corresponding to the reaction channel, and to a second injection channel at the other end, the communication between the second communication structure and the atmosphere being switchable. The second injection channel may be connected at one end to a second inlet configured to receive the second sample microfluidic from the second inlet, and at the other end to a second capillary pump configured to draw the second sample microfluidic through and out of the second injection channel. The reaction channel is connected to the second injection channel at a first connection point between the second inlet and the second capillary pump. A third communication structure is connected to the reaction channel at a second connection point between the first connection point and the second communication structure, wherein the reaction channel is not connected to any exit channel between the first connection point and the second connection point. The cross-sectional area of ​​the second injection channel is larger than the cross-sectional area of ​​the reaction channel, and the cross-sectional area of ​​the reaction channel is larger than the cross-sectional area of ​​the third communication structure. The third connecting structure is configured to maintain communication with the atmosphere, allowing the second sample microfluidic to self-close after entering the third connecting structure from the second injection channel via the reaction channel. The volume of the second sample microfluidic received by the reaction channel from the second injection channel is determined based on the distance between the first and second connection points and the cross-sectional area of ​​the reaction channel. The second sample microfluidic received by the reaction channel from the second injection channel can provide the aforementioned pre-placed microfluidic in the reaction channel, thereby being photo-driven along the reaction channel to the connection point between the outlet channel and the reaction channel to contact the sample microfluidic in the outlet channel. This allows the sample microfluidic in the volumetric chamber to spontaneously enter the reaction channel under the action of the Laplace pressure difference and mix with the second sample microfluidic.

[0044] Specifically, refer to Figure 6The reaction channel 108 is connected to the atmosphere at one end via a second communication structure 110 corresponding to the reaction channel 108, and to a second injection channel 202 at the other end. The connection between the second communication structure 110 and the atmosphere is switchable. The second injection channel 202 is connected to a second injection port 201 at one end to receive a second sample microfluidic from the second injection port 201, and to a second capillary pump 203 at the other end. The second injection port 201 is configured to receive the second sample microfluidic. The second capillary pump 203 is configured to draw the second sample microfluidic through and out of the second injection channel 202. The reaction channel 108 is connected to the second injection channel 202 at a first connection point CP1 between the second injection port 201 and the second capillary pump 203. A third communication structure 111 is connected to the reaction channel 108 at a second connection point CP2 between the first connection point CP1 and the second communication structure 110. No exit channel is connected between the first connection point CP1 and the second connection point CP2. The cross-sectional area of ​​the second injection channel 202 is larger than that of the reaction channel 108, and the cross-sectional area of ​​the reaction channel 108 is larger than that of the third connecting structure 111. The configuration of the second injection port 201, the second injection channel 202, and the second capillary pump 203 can be similar to the configuration of the aforementioned injection port 101, injection channel 102, and capillary pump 103. The configuration of the second connecting structure 110 and the third connecting structure 111 can also be similar to the configuration of the aforementioned connecting structures 1061-1064, which will not be elaborated further here.

[0045] The third connecting structure 111 is configured to maintain communication with the atmosphere, allowing the third connecting structure 111 to self-close after the second sample microfluidic enters from the second injection channel 202 via the reaction channel 108. The third connecting structure 111 can be configured to have its communication with the atmosphere permanently closed, or it can be configured to have a switchable communication with the atmosphere but remain normally open. When the second sample microfluidic needs to be added to the microfluidic chip 100, the second connecting structure 110 is first disconnected from the atmosphere, and then the second sample microfluidic is added to the second injection port 201. The second sample microfluidic is drawn by the second capillary pump 203 through the second injection channel 202, and upon reaching the first connection point CP1, it spontaneously enters the reaction channel 108 under the Laplace pressure difference generated by the larger cross-sectional area of ​​the second injection channel 202 compared to the reaction channel 108, and moves forward (i.e., towards the second connecting structure 110) within the reaction channel 108. At this time, the gas originally in the reaction channel 108 can be discharged from the third connecting structure 111. When the second sample microfluidic reaches the second connection point CP2, it will spontaneously enter the third connecting structure 111 due to the Laplace pressure difference generated by the cross-sectional area of ​​the reaction channel 108 being larger than that of the third connecting structure 111. Once the second sample microfluidic enters the third connecting structure 111, which has a very small cross-sectional area, it will form a liquid column that seals the third connecting structure 111. When the third connecting structure 111 is sealed, the gas in the reaction channel 108 can no longer be discharged from the third connecting structure 111, and the second sample microfluidic cannot overcome the gas pressure to continue moving forward in the reaction channel 108. Therefore, the second sample microfluidic can only reach the second connection point CP2 after entering the reaction channel 108, while the second sample microfluidic that fails to enter the reaction channel 108 and remains in the second sample inlet channel 202 will be drawn away by the second capillary pump 203, leaving a section of the second sample microfluidic between the first connection point CP1 and the second connection point CP2 for subsequent mixing and / or reaction with the sample microfluidic measured by the volumetric chamber in the reaction channel 108. The first process of measuring sample microfluidic fluid in the volumetric chambers 1041-1044 and the second process of receiving second sample microfluidic fluid in the reaction channel 108 can be executed serially or in parallel without affecting each other.After the volumetric cavities 1041-1044 are filled with sample microfluidics and the sample microfluidics in the dispensing channels 1051-1054 are separated from the sample microfluidics in the injection channel 102 (end of the first process), and after the second sample microfluidics in the reaction channel 108 are separated from the second sample microfluidics in the second injection channel 202 (end of the second process), the second connecting structure 110 can be connected to the atmosphere. Then, the Laplace pressure difference generated by the asymmetric photoinduced deformation of the reaction channel 108 is used to photo-drive the second sample microfluidics in the reaction channel 108 to the connection point between the outlet channels 1091-1094 and the reaction channel 108 to contact the sample microfluidics in the outlet channels 1091-1094, so that the sample microfluidics in the volumetric cavities 1041-1044 come into contact with the second sample microfluidics and mix and / or react.

[0046] In some embodiments, one or more reaction channels may be commonly connected to the same second injection channel. In other embodiments, each of the one or more reaction channels may be connected to a corresponding second injection channel of the one or more second injection channels, each second injection channel being connected at one end to a corresponding second injection port and at its other end to a corresponding second capillary pump. For example, Figure 6 This illustrates a scenario where multiple volumetric chambers are connected to the same reaction channel, and this reaction channel is connected to a corresponding second injection channel. In contrast, Figure 7 This illustrates a scenario where multiple volumetric chambers are each connected to a corresponding reaction channel, and each reaction channel is connected to a corresponding second injection channel. For example... Figure 7As shown, the volumetric fluid chamber 1041 is connected to the reaction channel 1081 via the sample outlet channel 1091. The reaction channel 1081 is connected to the atmosphere at one end via a second communication structure 1101 and to the second sample inlet channel 2021 at the other end. The connection between the second communication structure 1101 and the atmosphere is switchable. The second sample inlet channel 2021 is connected to the second sample inlet 2011 at one end to receive the first and second sample microfluidics from the second sample inlet 2011 and to the second capillary pump 2031 at the other end. The second sample inlet 2011 is configured to receive the first and second sample microfluidics, and the second capillary pump 2031 is configured to draw the first and second sample microfluidics through and out of the second sample inlet channel 2021. The reaction channel 1081 is connected to the second sample inlet channel 2021 at a first connection point CP11 between the second sample inlet 2011 and the second capillary pump 2031. The third connecting structure 1111 is connected to the reaction channel 1081 at the second connection point CP21 between the first connection point CP11 and the second connecting structure 1101. No sample outlet channel is connected between the first connection point CP11 and the second connection point CP21. The cross-sectional area of ​​the second sample inlet channel 2021 is larger than that of the reaction channel 1081, and the cross-sectional area of ​​the reaction channel 1081 is larger than that of the third connecting structure 1111. The third connecting structure 1111 is configured to maintain communication with the atmosphere, allowing the first and second sample microfluidics to self-close after entering the third connecting structure 1111 from the second sample inlet channel 2021 via the reaction channel 1081. Furthermore... Figure 7As shown, the volumetric fluid chamber 1042 is connected to the reaction channel 1082 via the sample outlet channel 1092. The reaction channel 1082 is connected to the atmosphere at one end via the second communication structure 1102 and to the second sample inlet channel 2022 at the other end. The connection between the second communication structure 1102 and the atmosphere is switchable. The second sample inlet channel 2022 is connected to the second sample inlet 2012 at one end to receive the second sample microfluidic fluid from the second sample inlet 2012 and to the second capillary pump 2032 at the other end. The second sample inlet 2012 is configured to receive the second sample microfluidic fluid, and the second capillary pump 2032 is configured to draw the second sample microfluidic fluid through and out of the second sample inlet channel 2022. The reaction channel 1082 is connected to the second sample inlet channel 2022 at the first connection point CP12 between the second sample inlet 2012 and the second capillary pump 2032. The third connecting structure 1112 connects to the reaction channel 1082 at the second connection point CP22 between the first connection point CP12 and the second connecting structure 1102. No sample outlet channel is connected between the first connection point CP12 and the second connection point CP22 in the reaction channel 1082. The cross-sectional area of ​​the second sample inlet channel 2022 is larger than that of the reaction channel 1082, which is also larger than the cross-sectional area of ​​the third connecting structure 1112. The third connecting structure 1112 is configured to maintain communication with the atmosphere, allowing the second sample microfluidic to self-close after entering the third connecting structure 1112 from the second sample inlet channel 2022 via the reaction channel 1082. Figure 7 As can be seen, the first distance between the first connection point CP11 and the second connection point CP21 can be configured to be different from the second distance between the first connection point CP12 and the second connection point CP22. Thus, when reaction channels 1081 and 1082 have the same cross-sectional area, the volume of the first and second sample microfluidics received by reaction channel 1081 is different from the volume of the second sample microfluidics received by reaction channel 1082, and the ratio is the ratio of the first distance to the second distance. Therefore, assuming that the first and second sample microfluidics are the same second sample microfluidics, and assuming that volumetric chambers 1041 and 1042 have the same volume, then using... Figure 7The microfluidic chip shown can simultaneously mix and / or react a certain volume of sample microfluidic with different volumes of second sample microfluidic. By designing the volumes of volumetric chamber 1041 and 1042, the volume of reaction channel 1081 between the first connection point CP11 and the second connection point CP21, and the volume of reaction channel 1082 between the first connection point CP12 and the second connection point CP22, mixing and / or reacting of sample microfluidic with second sample microfluidic in various desired proportions can be achieved. Furthermore, the second inlet 2011 and the second inlet 2012 can also receive different second sample microfluidics, thereby enabling mixing and / or reacting of sample microfluidics with different second sample microfluidics.

[0047] in addition, Figure 8 This illustrates a scenario where each of multiple volumetric chambers is connected to a corresponding reaction channel, and all reaction channels are collectively connected to a corresponding second injection channel. For example... Figure 8As shown, the volumetric liquid chambers 1041-1046 are connected to the injection channel 102 via the dispensing channels 1051-1056, respectively, and are connected to the atmosphere via the first connecting structure 1061-1066. They are also individually connected to a corresponding reaction channel 1081-1086 via the outlet channels 1091-1096. Each reaction channel 1081-1086 is connected to the atmosphere at one end via a corresponding second connecting structure 1101-1106, wherein the connection between the second connecting structures 1101-1106 and the atmosphere is switchable. The reaction channels 1081, 1083, and 1085 are connected to the second injection channel 2021 at their other ends. The second injection channel 2021 is connected at one end to the second injection port 2011 to receive the first and second sample microfluidics from the second injection port 2011, and at the other end to the second capillary pump 2031. The second injection port 2011 is configured to receive the first and second sample microfluidics, and the second capillary pump 2031 is configured to draw the first and second sample microfluidics through and out of the second injection channel 2021. Reaction channels 1081, 1083, and 1085 are each connected to the second injection channel 2021 at corresponding first connection points CP11, CP13, and CP15 between the second injection port 2011 and the second capillary pump 2031. The third connecting structures 1111, 1113, and 1115 are connected to the corresponding reaction channels 1081, 1083, and 1085 at the corresponding second connecting points CP21, CP23, and CP25 between the corresponding first connecting points CP11, CP13, and CP15 and the corresponding second connecting structures 1101, 1103, and 1105. No sample outlet channels are connected between the corresponding first connecting points CP11, CP13, and CP15 and the corresponding second connecting points CP21, CP23, and CP25 between the reaction channels 1081, 1083, and 1085. The cross-sectional area of ​​the second sample inlet channel 2021 is larger than the cross-sectional area of ​​the reaction channels 1081, 1083, and 1085, and the cross-sectional area of ​​the reaction channels 1081, 1083, and 1085 is larger than the cross-sectional area of ​​the third connecting structures 1111, 1113, and 1115. The third connecting structures 1111, 1113, and 1115 are configured to maintain communication with the atmosphere, allowing the first and second sample microfluidics to self-close after entering the third connecting structures 1111, 1113, and 1115 from the second injection channel 2021 via reaction channels 1081, 1083, and 1085. Furthermore... Figure 8As shown, reaction channels 1082, 1084, and 1086 are collectively connected to a second injection channel 2022 at their other ends. The second injection channel 2022 is connected at one end to a second injection port 2012 to receive a second sample microfluidic from the second injection port 2012, and at the other end to a second capillary pump 2032. The second injection port 2012 is configured to receive the second sample microfluidic, and the second capillary pump 2032 is configured to draw the second sample microfluidic through and out of the second injection channel 2022. Reaction channels 1082, 1084, and 1086 are each connected to the second injection channel 2022 at corresponding first connection points CP12, CP14, and CP16 between the second injection port 2012 and the second capillary pump 2032. The third connecting structures 1112, 1114, and 1116 are connected to the corresponding reaction channels 1082, 1084, and 1086 at the corresponding second connecting points CP22, CP24, and CP26 between the corresponding first connecting points CP12, CP14, and CP16 and the corresponding second connecting structures 1102, 1104, and 1106. No sample outlet channels are connected between the corresponding first connecting points CP12, CP14, and CP16 and the corresponding second connecting points CP22, CP24, and CP26 of the reaction channels 1082, 1084, and 1086. The cross-sectional area of ​​the second sample inlet channel 2022 is larger than the cross-sectional area of ​​the reaction channels 1082, 1084, and 1086, and the cross-sectional area of ​​the reaction channels 1082, 1084, and 1086 is larger than the cross-sectional area of ​​the third connecting structures 1112, 1114, and 1116. The third connecting structures 1112, 1114, and 1116 are configured to maintain communication with the atmosphere, allowing the second sample microfluidic to self-close after entering the third connecting structures 1112, 1114, and 1116 from the second injection channel 2022 via reaction channels 1082, 1084, and 1086. By designing the volumes of the volumetric cavities 1041-1046 and the volumes of each reaction channel between the corresponding first and second connection points, mixing and / or reaction of sample microfluidics with second sample microfluidics in various desired proportions can be achieved. Furthermore, the second injection port 2011 and the second injection port 2012 can also receive different second sample microfluidics, thereby enabling mixing and / or reaction of sample microfluidics with different second sample microfluidics.

[0048] The mixture of sample microfluidic and second sample microfluidic and / or reaction products in the reaction channel can be detected directly at the reaction channel, for example, by fluorescence detection, absorbance detection, etc. Alternatively, a detection channel can be additionally provided, connected to the reaction channel to receive the microfluidic to be detected. In some embodiments, the microfluidic chip 100 may further include a detection channel configured to be connected at one end to the reaction channel to receive the microfluidic to be detected, and at the other end to the atmosphere via a fourth connecting structure. The connection between the fourth connecting structure and the atmosphere is switchable, and the cross-sectional area of ​​the reaction channel is larger than that of the detection channel. When detection is not required (e.g., the reaction has not yet ended), the connection between the fourth connecting structure and the atmosphere can be closed. At this time, the gas in the detection channel prevents the microfluidic in the reaction channel from entering the detection channel. When detection is required, the connection between the fourth connecting structure and the atmosphere can be opened, at which time the microfluidic in the reaction channel spontaneously enters the detection channel under the Laplace pressure difference generated by the larger cross-sectional area of ​​the reaction channel compared to the detection channel. However, in some cases, the microfluidic fluid entering the detection channel may seal it off, preventing further entry of microfluidic fluid remaining in the reaction channel. For example, when the reaction channel is not connected to the atmosphere, opening only the fourth connection structure to the atmosphere will create a negative pressure within the reaction channel, thus hindering the entry of microfluidic fluid from the reaction channel into the detection channel. In such cases, the amount of microfluidic fluid already in the detection channel may be sufficient for detection. However, the amount of microfluidic fluid already in the detection channel may not be sufficient for detection; for example, some detections may require all the microfluidic fluid in the reaction channel to enter the detection channel. Therefore, in some embodiments with a detection channel, the reaction channel can be configured to be connected to the atmosphere. In some examples, one end of the reaction channel can be directly formed to be open to the atmosphere, for example... Figure 5 As shown. In other examples, a connectivity structure can also be provided for the reaction channels, such as... Figures 6 to 9The second connecting structure shown allows both the connecting structure of the reaction channel and the fourth connecting structure of the detection channel to be simultaneously connected to the atmosphere when detection is required. The detection channel can have any suitable geometry, as long as the cross-sectional area of ​​the detection channel is smaller than that of the reaction channel. In some embodiments, the detection channels can be arranged in a spiral pattern. Compared to a linear arrangement, a spiral arrangement of detection channels can increase the distribution density of the microfluidic fluid to be detected on the microfluidic chip 100, facilitating improved detection accuracy and efficiency, and also accommodating more microfluidic fluid to be detected. Each reaction channel can be connected to one or more detection channels to perform one or more of the same or different detections. These detection channels can be located on the same side or different sides of the reaction channel. When multiple detection channels can be located on the same side of the reaction channel, the connection portions between these detection channels and the reaction channel can be shared or separate. When multiple detection channels can be located on different sides of the reaction channel, the connection portions between these detection channels and the reaction channel can be aligned or offset from each other.

[0049] refer to Figure 9 The reaction channel 1081 is also connected to detection channels 1121-1123, and the cross-sectional area of ​​the reaction channel 1081 is larger than that of the detection channels 1121-1123. The reaction channel 1082 is also connected to detection channels 1124-1125, and the cross-sectional area of ​​the reaction channel 1082 is larger than that of the detection channels 1124-1125. Each of the detection channels 1121-1125 is connected to the atmosphere at its end via a corresponding switchable fourth connection structure 1131-1135, and the detection channels 1121-1125 are arranged in a spiral shape. Although... Figure 9 The outline of each turn of the spiral of detection channels 1121-1125 is illustrated as substantially square, but it can also have other suitable outline shapes. For example, the outline of each turn of the spiral of detection channels 1121-1125 can also be substantially triangular, quadrilateral, pentagonal, or other polygonal, circular, elliptical, etc., without limitation. In some embodiments, detection channels 1121-1125 may have a different depth than reaction channels 1081-1082. In such embodiments, a transition channel providing a depth transition can be provided between detection channels 1121-1125 and reaction channels 1081-1082. In some embodiments, the depth of detection channels 1121-1125 may be less than the depth of reaction channels 1081-1082.

[0050] In another aspect, this disclosure also provides a method for operating the aforementioned microfluidic chip.

[0051] When the microfluidic chip does not include reaction channels (e.g., as shown in the example) Figures 1 to 4When using the microfluidic chip shown, the operation method may include adding sample microfluidic fluid to the inlet to allow the added sample microfluidic fluid to enter the injection channel. When the first communication structure in such a microfluidic chip is switchable between the inlet and the atmosphere, the operation method may further include selecting a volumetric chamber according to the volume to be measured before adding the sample microfluidic fluid to the inlet, and connecting the first communication structure corresponding to the selected volumetric chamber to the atmosphere while disconnecting the first communication structure corresponding to the remaining volumetric chamber from the atmosphere. Then, the microfluidic chip can autonomously complete the measurement of the sample microfluidic fluid without any manual operation.

[0052] When microfluidic chips include reaction channels (e.g., as Figure 5 When referring to the microfluidic chip shown, refer to Figure 11 The operation method S200 includes: in step S202, adding sample microfluidic fluid to the injection port to allow the added sample microfluidic fluid to enter the injection channel; in step S204, after the sample microfluidic fluid in each volumetric cavity of the microfluidic chip is filled with sample microfluidic fluid and remains in the injection channel, and is separated from the sample microfluidic fluid in each dispensing channel of each volumetric cavity of the microfluidic chip, selectively irradiating the reaction channel locally drives the microfluidic fluid in the reaction channel to the connection point between the dispensing channel and the reaction channel corresponding to each volumetric cavity of the microfluidic chip, so that the microfluidic fluid in the reaction channel contacts the sample microfluidic fluid in each dispensing channel, thereby allowing the sample microfluidic fluid in each volumetric cavity of the microfluidic chip to enter the reaction channel and mix with the microfluidic fluid in the reaction channel. When the communication between the first communication structure in such a microfluidic chip and the atmosphere is switchable, refer to Figure 12The operation method S200' includes: at step S202', according to the volume of the sample microfluidic to be measured, making the first communication structure corresponding to one or more selected volumetric cavities of the microfluidic chip connected to the atmosphere, while making the first communication structure corresponding to the remaining volumetric cavities disconnected from the atmosphere, the sum of the preset volumes corresponding to the selected one or more volumetric cavities equal to the volume of the sample microfluidic to be measured; at step S204', adding sample microfluidic to the injection port so that the added sample microfluidic enters the injection channel; at step S206', each volumetric cavity in the selected one or more volumetric cavities is... After the sample microfluidic fluid, which is filled with and still remains in the injection channel, is separated from the sample microfluidic fluid in the respective dispensing channels corresponding to the one or more selected volumetric cavities, the microfluidic fluid in the reaction channel is selectively and locally illuminated. This drives the microfluidic fluid in the reaction channel to the connection point between the respective outlet channels and the reaction channel corresponding to the one or more selected volumetric cavities, allowing the microfluidic fluid in the reaction channel to come into contact with the sample microfluidic fluid in the respective outlet channels of the one or more selected volumetric cavities. This allows the sample microfluidic fluid in the one or more selected volumetric cavities to enter the reaction channel and mix with the microfluidic fluid in the reaction channel. Based on the preceding description, the microfluidic fluid in the reaction channel can be, for example, a pre-placed microfluidic fluid, or a second sample microfluidic fluid that enters the reaction channel via a second injection port and a second injection channel.

[0053] Other embodiments of the operation method can be found in the descriptions of the microfluidic chip 100 above, and will not be repeated here.

[0054] In another aspect, this disclosure also provides a microfluidic device including the aforementioned microfluidic chip.

[0055] refer to Figure 13A microfluidic device 300 is provided, comprising a microfluidic chip 100 having a reaction channel according to any of the foregoing embodiments, and a light source 310 configured to provide illumination to the microfluidic chip 100 to control the movement of microfluidics within the microfluidic chip 100 (especially in the reaction channel). The light source 310 can take any suitable form, such as a point light source, line light source, area light source, array light source, etc., and can be any suitable light source such as a light-emitting diode (LED), laser, etc. 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 photodeformation along the channel (especially the reaction channel) thereby driving the fluid. For example, the relative movement between the light source 310 and the microfluidic chip 100 can be achieved by fixing the light source 310 and moving the microfluidic chip 100 simultaneously, or by fixing the microfluidic chip 100 and moving the light source 310 simultaneously, or by having the light source 310 and the microfluidic chip 100 move simultaneously at different speeds; no particular limitation is made here. In some embodiments, such as... Figure 14 As shown, the light source 310 may include an array of multiple light sources 310_1, 310_2, and 310_3, each of which has a different illumination position on the microfluidic chip 100 (especially on the reaction channel). Therefore, the illumination position can be switched by turning each light source on and off. Although Figure 14 Only three light sources 310_1, 310_2, and 310_3 are shown in the figure, but this is merely exemplary and not restrictive. More light sources can be arranged as needed, and they can be arranged in any suitable array, such as a one-dimensional array or a two-dimensional array.

[0056] exist Figure 13 In this embodiment, it can be understood as providing a scanning of a positive-phase light spot on the microfluidic chip 100. In some other embodiments, a scanning of an inverted light spot on the microfluidic chip 100 may also be provided. For example, refer to... Figure 15The microfluidic device 300 may further include a light-shielding plate 320 disposed between the microfluidic chip 100 and the light source 310 and configured such that selectable portions of the reaction channel 108 of the microfluidic chip 100 are not illuminated by the light source 310, while the remaining portions are illuminated by the light source 310. The light source 310 may, for example, be configured to provide illumination to the entire microfluidic chip 100, and the projection of the light-shielding plate 320 onto the microfluidic chip 100 provides an inverted light spot. The microfluidic chip 100 and the light source 310 may be fixed, while the light-shielding plate 320 may be movable, allowing selection of different selectable portions of the reaction channel 108 of the microfluidic chip 100, effectively providing a scan of the inverted light spot. In other embodiments, the light-shielding plate 320 may also be configured such that selectable portions of the reaction channel 108 of the microfluidic chip 100 are illuminated by the light source 310, while the remaining portions are not. 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 the illumination except for the openings therein for light leakage. In this case, the microfluidic chip 100 and the light source 310 can be fixed, and the light shield 320 can be movable, so that different selectable portions of the reaction channel 108 of the microfluidic chip 100 can be selected, which is equivalent to providing a scanning of the positive phase light spot.

[0057] In other embodiments, reference is made to Figure 16 The microfluidic device 300 may alternatively include an optical attenuator 330 disposed between the microfluidic chip 100 and the light source 310 and configured to attenuate the intensity of the illumination from the light source 310 received by a selectable portion of the reaction channel 108 of the microfluidic chip 100 compared to the illumination received by the light source 310 received by the remaining portion of the reaction channel 108. The light source 310 may, for example, be configured to provide illumination to the entire microfluidic chip 100, while the projection of the optical attenuator 330 onto the microfluidic chip 100 provides an attenuated light spot. The microfluidic chip 100 and the light source 310 may be fixed, and the optical attenuator 330 may be movable, allowing selection of different selectable portions of the reaction channel 108 of the microfluidic chip 100, effectively providing a scan of the attenuated light spot.

[0058] It is understood that although the above description shows that the light-shielding plate 320 or the light-attenuating plate 320 moves while the light source 310 and the microfluidic chip 100 remain stationary, this is merely exemplary and not restrictive. The relative movement between the above components can be achieved in various ways, as long as it is possible to scan the positive phase spot, the negative phase spot, or the attenuated spot on the microfluidic chip 100.

[0059] To provide a higher degree of automation for the microfluidic device 300, in some embodiments, reference is made to... Figure 17The microfluidic device 300 may further include a controller 340. The controller 340 may be configured to perform the operating method of the microfluidic chip according to any of the foregoing embodiments. For example, the controller 340 may be configured to: after the sample microfluidic fluid remaining in the injection channel and the sample microfluidic fluid corresponding to the dispensing channel in each volumetric fluid chamber of the microfluidic chip 100 is filled with sample microfluidic fluid, and then separates from the sample microfluidic fluid corresponding to the dispensing channel, control the light source 310 to selectively illuminate the reaction channel locally, driving the microfluidic fluid in the reaction channel to the connection point corresponding to the dispensing channel and the reaction channel, so that the microfluidic fluid in the reaction channel contacts the sample microfluidic fluid in the dispensing channel, thereby allowing the sample microfluidic fluid in each volumetric fluid chamber to enter the reaction channel and mix with the microfluidic fluid in the reaction channel. In some embodiments, when the first communication structure corresponding to each volumetric cavity of the microfluidic chip 100 is switchable from the atmosphere, the controller 340 can be configured to: before adding sample microfluidic fluid to the inlet, based on the volume of the sample microfluidic fluid to be measured, execute control to connect the first communication structure corresponding to one or more selected volumetric cavities of the microfluidic chip 100 to the atmosphere while disconnecting the first communication structure corresponding to the remaining volumetric cavities from the atmosphere, wherein the sum of the preset volumes corresponding to the selected one or more volumetric cavities is equal to the volume of the sample microfluidic fluid to be measured; and in each volumetric cavity of the selected one or more volumetric cavities... After the sample microfluidic fluid in the inlet channel is separated from the sample microfluidic fluid in the respective dispensing channels corresponding to the selected one or more volumetric fluid chambers, the control light source selectively illuminates the reaction channel, driving the microfluidic fluid in the reaction channel to the connection point between the respective outlet channels and the reaction channel corresponding to the selected one or more volumetric fluid chambers. This allows the microfluidic fluid in the reaction channel to contact the sample microfluidic fluid in the respective outlet channels of the selected one or more volumetric fluid chambers, thereby allowing the sample microfluidic fluid in the selected one or more volumetric fluid chambers to enter the reaction channel and mix with the microfluidic fluid in the reaction channel. Other operational embodiments of the controller 340 can be referred to those described above regarding the microfluidic chip 100, and will not be repeated here.

[0060] The microfluidic chip and microfluidic device disclosed herein effectively utilize the capillary force of the capillary pump and the Laplace pressure difference generated by the asymmetric photoinduced deformation of the channel to achieve contactless and precise microfluidic actuation without any external driving device. Furthermore, it can achieve precise quantitative trace measurement operations at the back end without filling the entire front channel. It has low sample loss, few components, small overall size, simple and robust structure, high repeatability, and a high degree of portability and automation.

[0061] The terms “left,” “right,” “front,” “back,” “top,” “bottom,” “upper,” “lower,” “high,” “lower,” etc., used in the specification and claims, if present, are for descriptive purposes and not necessarily for describing unchanging relative positions. It should be understood that such terms are interchangeable where appropriate, enabling the embodiments of this disclosure described herein to operate, for example, in orientations different from those shown or otherwise described herein. For example, when the device in the drawings is reversed, a feature previously described as “above” other features may now be described as “below” other features. The device may also be oriented in other ways (rotated 90 degrees or in other orientations), in which case the relative spatial relationships will be interpreted accordingly.

[0062] In the specification and claims, when an element is described as being "on top of," "attached" to, "connected" to, "coupled" to, "coupled to," or "in contact with" another element, the element may be directly located on top of, directly attached to, directly connected to, directly coupled to, directly coupled to, or directly in contact with the other element, or one or more intermediate elements may be present. Conversely, when an element is described as being "directly" located on top of, directly attached to, directly connected to, directly coupled to, directly coupled to, or directly in contact with another element, no intermediate elements are present. In the specification and claims, when a feature is arranged "adjacent" to another feature, it may mean that a feature has a portion overlapping with the adjacent feature or a portion located above or below the adjacent feature.

[0063] As used herein, the term "exemplary" means "serving as an example, instance, or illustration," and not as a "model" to be precisely copied. Any implementation described herein by example is not necessarily to be construed as preferred or advantageous over other implementations. Furthermore, this disclosure is not limited to any theory expressed or implied as given in the art, background, summary of the invention, or detailed description.

[0064] As used herein, the term "substantially" means any minor variation resulting from design or manufacturing defects, device or component tolerances, environmental influences, and / or other factors. The term "substantially" also allows for differences from the perfect or ideal situation due to parasitic effects, noise, and other practical considerations that may exist in the actual implementation.

[0065] Additionally, terms such as “first,” “second,” etc., may be used in this document for reference purposes only and are not intended to be limiting. For example, unless the context clearly indicates otherwise, the words “first,” “second,” and other such numerical terms relating to structures or elements do not imply order or sequence.

[0066] It should also be understood that when the term “including / contains” is used herein, it indicates the presence of the indicated feature, whole, step, operation, unit and / or component, but does not preclude the presence or addition of one or more other features, wholes, steps, operations, units and / or components and / or combinations thereof.

[0067] In this disclosure, the term “provide” is used broadly to cover all ways of obtaining an object, and therefore “provide an object” includes, but is not limited to, “purchasing,” “preparing / manufacturing,” “arranging / setting up,” “installing / assembling,” and / or “ordering” an object.

[0068] As used herein, the term “and / or” includes any and all combinations of one or more of the listed items in association. The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of this disclosure. As used herein, the singular forms “a,” “an,” and “the” are also intended to include the plural forms unless the context clearly indicates otherwise.

[0069] Those skilled in the art will recognize that the boundaries between the above operations are merely illustrative. 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. Moreover, alternative embodiments may include multiple instances of a particular operation, and the order of operations may be changed in various other embodiments. However, other modifications, variations, and substitutions are equally possible. Aspects and elements of all the embodiments disclosed above may be combined in any way and / or in combination with aspects or elements of other embodiments to provide multiple additional embodiments. Therefore, this specification and the accompanying drawings should be considered illustrative rather than restrictive.

[0070] While specific embodiments of this disclosure have been described in detail by way of example, those skilled in the art should understand that the examples are for illustrative purposes only and not intended to limit the scope of this disclosure. The various embodiments disclosed herein can be combined in any way without departing from the spirit and scope of this disclosure. Those skilled in the art should also understand that various modifications can be made to the embodiments without departing from the scope and spirit of this disclosure. The scope of this disclosure is defined by the appended claims.

Claims

1. A microfluidic chip, comprising: The inlet is configured to receive sample microfluids; The sample inlet channel is configured to communicate with the sample inlet to receive sample microfluids from the sample inlet. A capillary pump is configured to communicate with the injection channel to draw sample microfluids through and out of the injection channel; as well as One or more volumetric fluid chambers, each configured to communicate with an inlet and a capillary pump via a corresponding dispensing channel to measure a preset volume of sample microfluidic fluid from the inlet channel, and configured to communicate with the atmosphere via a corresponding first communication structure. The cross-sectional area of ​​the injection channel is larger than that of the volumetric liquid chamber, the cross-sectional area of ​​the volumetric liquid chamber is larger than that of the dispensing channel, and the cross-sectional area of ​​the first connecting structure corresponding to the volumetric liquid chamber on the side adjacent to the volumetric liquid chamber is greater than or equal to the cross-sectional area of ​​the injection channel. The microfluidic chip further includes: The reaction channel is configured to communicate with each of the one or more volumetric fluid chambers via a sample outlet channel corresponding to that volumetric fluid chamber to receive a preset volume of sample microfluidic fluid corresponding to that volumetric fluid chamber. The reaction channel includes a photodeformable material that allows the microfluidic fluid to be driven through the reaction channel by the Laplace pressure difference generated by the asymmetric photodeformation of the reaction channel, and Among them, the cross-sectional area of ​​the liquid measuring chamber is larger than that of the reaction channel, the cross-sectional area of ​​the reaction channel is larger than that of the sample outlet channel, and the depth of the reaction channel is greater than that of the sample outlet channel.

2. The microfluidic chip according to claim 1, wherein, The sample dispensing channel includes a first part connected to the sample inlet channel and a second part connected between the first part and the corresponding volumetric chamber. The depth of the first part is less than the depth of the sample inlet channel. The depth of the second part changes from a first depth at the location where the second part connects to the first part to a second depth at the location where the second part connects to the volumetric chamber. The first depth is equal to the depth of the first part, and the second depth is equal to the depth of the volumetric chamber.

3. The microfluidic chip according to claim 1 further includes a buffer tube connected between the sample inlet channel and the capillary pump, wherein, The cross-sectional area of ​​the buffer tube is larger than that of the sample inlet channel.

4. The microfluidic chip according to claim 3, wherein, The buffer tube consists of one or more connected U-shaped tubes.

5. The microfluidic chip according to claim 1, wherein, The first connecting structure includes a balance channel that is connected to the corresponding volumetric liquid chamber at one end and to the atmosphere at the other end, wherein the cross-sectional area of ​​the balance channel is greater than or equal to the cross-sectional area of ​​the injection channel. or The first connecting structure includes a balance chamber that is connected to the corresponding volumetric fluid chamber and has a vertical through-hole for communication with the atmosphere. The cross-sectional area of ​​the balance chamber is greater than or equal to the cross-sectional area of ​​the injection channel.

6. The microfluidic chip according to claim 1, wherein, The preset volume corresponding to each of the one or more volumetric cavities is different from the preset volume corresponding to the other volumetric cavities in the one or more volumetric cavities.

7. The microfluidic chip according to claim 1, wherein, The one or more volumetric liquid chambers include a first volumetric liquid chamber connected to the injection channel via a first dispensing channel and a second volumetric liquid chamber connected to the injection channel via a second dispensing channel, wherein: The first and second volumetric liquid chambers are located on the same side of the injection channel; or The first and second volumetric liquid chambers are located on different sides of the injection channel, and the first and second dispensing channels are aligned with each other; or The first and second volumetric liquid chambers are located on different sides of the injection channel, and the first and second dispensing channels are offset from each other.

8. The microfluidic chip according to claim 1, wherein, The connection between the first connecting structure and the atmosphere is switchable, and when the first connecting structure is not connected to the atmosphere, the measuring chamber corresponding to the first connecting structure stops measuring.

9. The microfluidic chip according to claim 8, wherein, The first connecting structure includes an opening that can be opened to the atmosphere, and wherein: A baffle is provided at the opening of the first communicating structure, 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 of the first connecting structure. The photodeformable material is configured to not close the opening when not exposed to light, but to undergo photodeformation to close the opening when exposed to light, or to close the opening when not exposed to light, but to undergo photodeformation to not close the opening when exposed to light.

10. The microfluidic chip according to claim 1, wherein, The difference between the depth of the sample outlet channel and the depth of the reaction channel is configured to allow the microfluidic fluid to move across the junction of the sample outlet channel and the reaction channel within the reaction channel.

11. The microfluidic chip according to claim 1, wherein, The ratio of the depth of the sample outlet channel to the depth of the reaction channel is less than 1:

2.

12. The microfluidic chip according to claim 1, wherein, The ratio of the depth of the sample outlet channel to the depth of the reaction channel is less than or equal to 1:

4.

13. The microfluidic chip according to claim 1, wherein, The photodeformable material is configured to expand in response to light, such that portions of the reaction channel have a larger cross-sectional area when illuminated compared to when not illuminated, thereby driving the microfluidic flow in the reaction channel in the direction of decreasing light intensity; or The photodeformable material is configured to contract in response to light, such that portions of the reaction channel have a smaller cross-sectional area when illuminated compared to when not illuminated, thereby driving the microfluidic in the reaction channel in the direction of increasing light intensity.

14. The microfluidic chip according to claim 1, wherein, The photodeformable material includes a photodeformable liquid crystal polymer material, which includes a photoresponsive linear liquid crystal polymer material with a polycyclooctene main chain and azobenzene side chains.

15. The microfluidic chip according to claim 1, wherein, A pre-placed microfluidic is stored in the reaction channel at a location separated from the sample outlet channel. The pre-placed microfluidic is driven to the connection point between the sample outlet channel and the reaction channel by the Laplace pressure difference generated by the asymmetric photodeformation of the reaction channel, so as to contact and mix with the sample microfluidic received from the volumetric fluid chamber in the reaction channel.

16. The microfluidic chip according to claim 15, wherein, Pre-filled microfluidics are added to the reaction channels either during the use phase of the microfluidic chip or during the manufacturing phase of the microfluidic chip.

17. The microfluidic chip according to claim 1, wherein: The one or more volumetric cavities are commonly connected to the same reaction channel; or Each of the one or more volumetric cavities is connected to a corresponding reaction channel in one or more reaction channels.

18. The microfluidic chip according to claim 17, wherein, The reaction channel is connected to the atmosphere at one end via a corresponding second communication structure, and to a second sample injection channel at the other end. The connection between the second communication structure and the atmosphere is switchable. The second injection channel is connected at one end to a second injection port configured to receive the second sample microfluidic fluid, and at the other end to a second capillary pump configured to draw the second sample microfluidic fluid through and out of the second injection channel. The reaction channel is connected to the second injection channel at a first connection point between the second injection port and the second capillary pump. The third connecting structure is connected to the reaction channel at the second connecting point between the first connecting point and the second connecting structure. No sample outlet channel is connected between the first connecting point and the second connecting point in the reaction channel. The cross-sectional area of ​​the second injection channel is larger than that of the reaction channel, and the cross-sectional area of ​​the reaction channel is larger than that of the third connecting structure. The third connecting structure is configured to maintain communication with the atmosphere, so that the second sample microfluidic can self-close the third connecting structure after entering the third connecting structure from the second injection channel through the reaction channel.

19. The microfluidic chip according to claim 18, wherein: The one or more reaction channels are commonly connected to the same second injection channel; or Each of the one or more reaction channels is connected to a corresponding second injection channel of one or more second injection channels, and each second injection channel is connected at one end to a corresponding second injection port and at the other end to a corresponding second capillary pump.

20. The microfluidic chip according to claim 1, further comprising: The detection channel is configured to communicate with the reaction channel at one end to receive the microfluidic sample to be detected from the reaction channel, and to communicate with the atmosphere at the other end via a fourth communication structure, the communication between the fourth communication structure and the atmosphere being switchable. The cross-sectional area of ​​the reaction channel is larger than that of the detection channel.

21. The microfluidic chip according to claim 20, wherein, The detection channels are arranged in a spiral shape.

22. The microfluidic chip according to any one of claims 1 to 21, comprising: A substrate having an inlet and a groove communicating with the inlet; as well as A photodeformable film attached to a substrate, the photodeformable film at least partially covering the groove to form a closed channel together with the groove, such that the microfluidic fluid can be driven through the closed channel under the Laplace pressure difference generated by the asymmetric photodeformation of the closed channel, the closed channel at least providing the reaction channel.

23. A method for operating a microfluidic chip according to any one of claims 1 to 22, comprising: Add sample microfluidic fluid to the injection port to allow the added sample microfluidic fluid to enter the injection channel; After the sample microfluids in each of the one or more volumetric cavities are filled with sample microfluidics and remain in the injection channel, and are separated from the sample microfluidics in the dispensing channels corresponding to the one or more volumetric cavities, the microfluidics in the reaction channel are driven to the connection point between the dispensing channels and the reaction channel corresponding to the one or more volumetric cavities by selectively illuminating the reaction channel locally. This allows the microfluidics in the reaction channel to come into contact with the sample microfluidics in the dispensing channels, thereby allowing the sample microfluidics in the one or more volumetric cavities to enter the reaction channel and mix with the microfluidics in the reaction channel.

24. The method according to claim 23, wherein, The first communication structure corresponding to each volumetric cavity of the microfluidic chip is switchable between communication with the atmosphere and the atmosphere. When the first communication structure is not connected to the atmosphere, the volumetric cavity corresponding to that first communication structure stops measuring. The method includes: Based on the volume of the sample microfluid to be measured, the first communication structure corresponding to one or more selected volumetric cavities in the one or more volumetric cavities is connected to the atmosphere, while the first communication structure corresponding to the remaining volumetric cavities in the one or more volumetric cavities is not connected to the atmosphere. The sum of the preset volumes corresponding to the selected one or more volumetric cavities is equal to the volume of the sample microfluid to be measured. Add sample microfluidic fluid to the injection port to allow the added sample microfluidic fluid to enter the injection channel; After the sample microfluids in each of the selected one or more volumetric cavities are filled with sample microfluidics and remain in the injection channel, and are separated from the sample microfluidics in the dispensing channels corresponding to the selected one or more volumetric cavities, the microfluidics in the reaction channel are driven to the connection point between the sample outlet channels and the reaction channel corresponding to the selected one or more volumetric cavities by selectively illuminating the reaction channel. This allows the microfluidics in the reaction channel to come into contact with the sample microfluidics in the sample outlet channels corresponding to the selected one or more volumetric cavities, thereby allowing the sample microfluidics in the selected one or more volumetric cavities to enter the reaction channel and mix with the microfluidics in the reaction channel.

25. A microfluidic device comprising a microfluidic chip according to any one of claims 1 to 22 and a light source configured to provide illumination to the microfluidic chip to control the movement of microfluidics in the microfluidic chip.

26. The microfluidic device according to claim 25, wherein, The light source is configured to move relative to the microfluidic chip to scan the illumination position on the microfluidic chip; or The light source comprises an array of multiple light sources, each of which has a different illumination position on the microfluidic chip.

27. The microfluidic device according to claim 25, further comprising one of the following: A light-shielding plate is disposed between the microfluidic chip and the light source and configured to allow selective portions of the microfluidic chip's reaction channels to receive light from the light source while the remaining portions do not, or to allow selective portions of the microfluidic chip's reaction channels to not receive light from the light source while the remaining portions do; or An attenuator is disposed between the microfluidic chip and the light source and configured to attenuate the intensity of the light received by a selectable portion of the reaction channel of the microfluidic chip compared to the light received by the remaining portion of the reaction channel.

28. The microfluidic device according to claim 27, wherein, The microfluidic chip and the light source are fixed in place, and The light-shielding plate or light-attenuating plate is movable, allowing for the selection of different selectable portions of the reaction channels of the microfluidic chip.

29. The microfluidic device of claim 25, further comprising a controller, the controller being configured to: After the sample microfluidic fluid in each of the one or more volumetric cavities of the microfluidic chip is filled with sample microfluidic fluid and remains in the injection channel, and is separated from the sample microfluidic fluid in the dispensing channels corresponding to the one or more volumetric cavities, the control light source selectively illuminates the reaction channel locally, driving the microfluidic fluid in the reaction channel to the connection point between the dispensing channel and the reaction channel corresponding to the one or more volumetric cavities. This allows the microfluidic fluid in the reaction channel to contact the sample microfluidic fluid in the dispensing channels, thereby allowing the sample microfluidic fluid in the one or more volumetric cavities to enter the reaction channel and mix with the microfluidic fluid in the reaction channel.

30. The microfluidic device according to claim 29, wherein, The first communication structure corresponding to each volumetric fluid chamber of the microfluidic chip is switchable between communication with the atmosphere and the atmosphere. When the first communication structure is not connected to the atmosphere, the volumetric fluid chamber corresponding to that first communication structure stops measuring. The controller is configured to: Before adding sample microfluidic fluid to the injection port, control is executed according to the volume of sample microfluidic fluid to be measured, so that the first communication structure corresponding to one or more selected volumetric fluid chambers is connected to the atmosphere, while the first communication structure corresponding to the remaining volumetric fluid chambers is not connected to the atmosphere, and the sum of the preset volumes corresponding to the selected one or more volumetric fluid chambers is equal to the volume of sample microfluidic fluid to be measured. After the sample microfluids in each of the selected one or more volumetric cavities are filled with sample microfluidics and remain in the injection channel, and are separated from the sample microfluidics in the dispensing channels corresponding to the selected one or more volumetric cavities, the control light source selectively illuminates the reaction channel locally, driving the microfluidics in the reaction channel to the connection point between the sample outlet channels and the reaction channel corresponding to the selected one or more volumetric cavities. This allows the microfluidics in the reaction channel to contact the sample microfluidics in the sample outlet channels corresponding to the selected one or more volumetric cavities, thereby allowing the sample microfluidics in the selected one or more volumetric cavities to enter the reaction channel and mix with the microfluidics in the reaction channel.

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