Microfluidic liquid mixing experimental device based on high-energy light source and application thereof

Abstract

The application provides a microfluidic liquid mixing experiment device based on a high-energy light source and an application thereof, and the device comprises a microfluidic chip, an injection unit, a driving unit and a control unit, a microfluidic channel structure of the microfluidic chip comprises a sample inlet channel, a primary mixing channel, a secondary mixing channel and a sample outlet channel; the primary mixing channel is arranged in communication with the sample inlet channel, the secondary mixing channel is arranged below the primary mixing channel and is in communication, the main channel and the sub-channel of the secondary mixing channel extend downward and intersect to form a plurality of communicated annular channels; the sample outlet channel is arranged below the secondary mixing channel and is in communication; the injection unit injects liquid samples into the microfluidic channel structure; the driving unit is connected with the microfluidic chip, and the control unit is electrically connected with the injection unit and the driving unit respectively; the application introduces the turbulent mixing principle on the basis of the laminar mixing, improves the fluid mixing efficiency by changing the microfluidic channel structure, integrates the high-energy light source, and realizes the time-resolved soft matter system microstructure characterization.

Description

Technical Field

[0001] This invention belongs to the field of experimental equipment technology, and in particular relates to a microfluidic liquid mixing experimental device based on a high-energy light source and its application. Background Technology

[0002] Microfluidic chip technology has been listed as one of the most important cutting-edge technologies of the 21st century. As a highly interdisciplinary research technology, microfluidic chips, from design and fabrication to application, encompass cutting-edge disciplines such as analytical chemistry, microelectromechanical systems (MEMS), computer science, electronics, materials science, life sciences, and modern medicine. They achieve integration, miniaturization, automation, and portability from sample preparation and processing to sample detection. The emergence and development of microfluidic chip technology has successfully miniaturized and integrated experiments that previously required multiple instruments in conventional laboratories into a single chip system. This not only greatly improves experimental speed and significantly reduces experimental costs, but most importantly, it makes high-throughput, rapid time-resolved sample detection possible. Following the trend of miniaturization, integration, and portability in modern analytical equipment, microfluidic chip technology has significant advantages in high-throughput, low-consumption, and large-scale parallel processing.

[0003] Soft matter science emerged in the mid-to-late 19th century and has now developed into a highly interdisciplinary research field. The fundamental characteristics of soft matter systems include sensitivity to minute environmental variables, nonlinear responses, and self-organizing behavior. Changes in the fluid environment (such as buffer solution type, types of additives and surfactants, different fluid concentration gradients, and different pH values) are crucial environmental variables that trigger the self-assembly of basic soft matter units. Microfluidic chip technology is an important experimental technique for realizing changes in the fluid environment.

[0004] Integrating microfluidic chip technology into synchrotron radiation beamlines is an important experimental method for studying the dynamic reaction processes of soft matter systems at the molecular level. The high brightness of synchrotron X-rays provides a high spatiotemporal resolution detection source for the test system, while microfluidic chips enable rapid and controllable control over the triggering time of environmental variables. The basic principle of current microfluidic chip mixing channel design is to achieve mixing and collision of fluids at the interface. For example, the most common T-channel chip design involves simultaneously pumping two independent fluids from opposite ends horizontally, allowing them to collide at the interface to achieve mixing. The mixed fluid is then pumped out through a liquid passage perpendicular to the inlet channel. This type of T-channel chip is now widely used in the biopharmaceutical field. However, from a fluid dynamics perspective, after the mixed fluid flows a certain distance through the T-channel, the flow pattern in the straight channel becomes a simple laminar flow, significantly reducing the mixing efficiency.

[0005] Therefore, there is a need to provide an improved technical solution that addresses the shortcomings of the existing technology. Summary of the Invention

[0006] In view of the shortcomings of the prior art described above, the purpose of this invention is to provide a microfluidic liquid mixing experimental device based on a high-energy light source and its application. By changing the microchannel structure, the flow state of the liquid sample is changed, thereby improving the mixing efficiency between liquid samples and solving the problem of low fluid mixing efficiency in the prior art.

[0007] To achieve the above and other related objectives, the present invention provides a microfluidic liquid mixing experimental device based on a high-energy light source, the microfluidic liquid mixing experimental device comprising:

[0008] A microfluidic chip includes a microchannel structure comprising an inlet channel, a primary mixing channel, a second mixing channel, and an outlet channel. The inlet channel includes a first inlet and a second inlet, located at opposite ends of the inlet channel. The primary mixing channel is connected to the inlet channel, allowing liquid samples injected from the first and second inlets to converge and initially mix, forming a preliminary mixed sample. The second mixing channel is located below and interconnected with the primary mixing channel, comprising a main channel and sub-channels. The main channel and sub-channels extend downwards and intersect to form multiple interconnected annular channels, with adjacent annular channels connected via a mixing confluence port. The outlet channel is located below the second mixing channel and connected to its output end. The preliminary mixed sample undergoes multiple mixing processes in the second mixing channel before entering the outlet channel.

[0009] An injection unit is provided, comprising a first injection pump and a second injection pump. The injection output end of the first injection pump is connected to the first inlet, and the injection output end of the second injection pump is connected to the second inlet. The first injection pump and the second injection pump respectively inject liquid samples into the microchannel structure.

[0010] A driving unit, which is connected to the microfluidic chip, is used to adjust the position of the microfluidic chip;

[0011] The control unit is electrically connected to the injection unit and the drive unit, respectively.

[0012] Preferably, the microfluidic chip includes a substrate layer and a sealing layer, the microchannel structure is formed in the substrate layer, the sealing layer is located on the side of the substrate layer where the microchannel structure is formed, and the sealing layer is configured to match the morphology of the substrate layer.

[0013] Preferably, both the substrate layer and the sealing layer are made of polymethyl methacrylate, and the microfluidic chip is formed by thermo-pressing the substrate layer and the sealing layer.

[0014] Preferably, the total thickness of the microfluidic chip is 2.8–3.2 mm, the thickness of the substrate layer is 1.8–2.2 mm, and the depth of the microchannel structure is 100–200 μm.

[0015] Preferably, the width of the sample outlet channel is not less than the width of the mixing confluence, and the width of the sample outlet channel is 280μm to 330μm.

[0016] Preferably, the annular channel is an asymmetrical annular channel, which includes a first semi-circular channel and a second semi-circular channel. Multiple first semi-circular channels form a connected main channel, and multiple second semi-circular channels form a connected sub-channel.

[0017] Preferably, the number of annular channels is 4 to 8.

[0018] Preferably, the width of the first semi-circular channel is greater than the width of the second semi-circular channel.

[0019] Preferably, the width of the first semi-circular channel is 1.5 to 2 times the width of the second semi-circular channel.

[0020] The present invention also provides an application of the microfluidic liquid mixing experimental device based on the high-energy light source as described above, wherein the microfluidic liquid mixing experimental device is used for time-resolved microstructure characterization of soft matter systems.

[0021] As described above, the microfluidic liquid mixing experimental device based on a high-energy light source and its application of the present invention have the following beneficial effects:

[0022] The microfluidic liquid mixing experimental device of this invention includes a microfluidic chip, an injection unit, a driving unit, and a control unit. The control unit precisely controls the driving unit to achieve rapid alignment of the beam center of the high-energy light source with the optical path of the microfluidic chip. The control unit also precisely controls the flow rate of the first and second injection pumps injecting liquid samples, achieving rapid mixing between liquid samples and millisecond-scale sample mixing. Liquid samples are injected into the injection channels from two independent first and second injection ports. The two liquid samples contact and collide in the initial mixing channel and are initially mixed to form a preliminary mixed sample. The second mixing channel includes a main channel and a sub-channel. The main channel and the sub-channel extend downward and intersect multiple times, forming a connected annular channel each time they intersect. Multiple annular channels form the second mixing channel. The formed preliminary mixed sample flows into the main channel and the sub-channel respectively. Each time it passes through the mixing confluence between two adjacent annular channels, due to the difference in liquid flow rates between the main channel and the sub-channel, an unbalanced collision of the two fluids is formed at the liquid interface. The liquid samples are mixed through the principle of turbulent mixing, thereby improving the mixing efficiency of the fluid.

[0023] The microfluidic liquid mixing experimental device of this invention introduces the principle of turbulent mixing on the basis of laminar mixing. By changing the microchannel structure, the fluid mixing efficiency is improved. The device adopts a modular design, which is suitable for conducting experiments at different experimental terminals. On this basis, the microfluidic chip is integrated with a high-energy light source to achieve rapid time-resolved characterization of the microstructure of soft matter systems. By tracking the dynamic changes of the microstructure of the soft matter system and the interactions between the basic structural unit molecules during the fluid mixing process online, it can provide a powerful research tool for the design and screening of drug targets for major diseases and the study of rapid chemical reaction kinetics. It can also reduce the impact of high-irradiation environment on the radiation damage of soft matter systems. Attached Figure Description

[0024] Figure 1 The diagram shown is a schematic representation of a microfluidic liquid mixing experimental device based on a high-energy light source in a specific embodiment of the present invention.

[0025] Figure 2a The diagram shown is a schematic representation of the structure of the substrate layer in a specific embodiment of the present invention.

[0026] Figure 2b The diagram shown is a structural schematic of the sealing layer in a specific embodiment of the present invention.

[0027] Figure 3 The diagram shown is a schematic representation of the microchannel structure in a specific embodiment of the present invention.

[0028] Figure 4 Displayed as Figure 3 Enlarged view of point A in the middle.

[0029] Figure 5 The diagram shows an example of fluid mixing at different flow rates in the microchannel structure of Embodiment 1 of the present invention.

[0030] Component designation explanation

[0031] 1. Microfluidic chip

[0032] 10. Matrix layer

[0033] 100 Microchannel Structure

[0034] 101 Sample Inlet Channel

[0035] 1011 First Inlet

[0036] 1012 Second Inlet

[0037] 102 Initial Mixing Channel

[0038] 103 Second Mixing Channel

[0039] 1031 Main Channel

[0040] 1032 sub-channels

[0041] 1033 Circular Channel

[0042] 10331 First semi-circular channel

[0043] 10332 Second semi-circular channel

[0044] 1034 Mixed Manifold

[0045] 104 Sample outlet channel

[0046] L is the width of the sample outlet channel.

[0047] 20 sealing layers

[0048] 201, 202, 203 standard connectors

[0049] 2 Injection Units

[0050] 21 First Injection Pump

[0051] 22 Second Injection Pump

[0052] 3 drive units

[0053] 4 Control Unit Detailed Implementation

[0054] The following specific embodiments illustrate the implementation of the present invention. Those skilled in the art can easily understand other advantages and effects of the present invention from the content disclosed in this specification.

[0055] The following specific examples illustrate the embodiments of the present invention. Those skilled in the art can easily understand other advantages and effects of the present invention from the content disclosed in this specification. The present invention can also be implemented or applied through other different specific embodiments, and various details in this specification can be modified or changed based on different viewpoints and applications without departing from the spirit of the present invention. For ease of explanation, when detailing the embodiments of the present invention, the cross-sectional views showing the device structure are partially enlarged, not according to the general scale, and the schematic diagrams are merely examples and should not limit the scope of protection of the present invention. Furthermore, in actual manufacturing, the three-dimensional spatial dimensions of length, width, and depth should be included.

[0056] For ease of description, spatial relation terms such as “below,” “under,” “lower than,” “below,” “above,” and “upper” may be used herein to describe the relationship between one element or feature shown in the accompanying drawings and other elements or features. It will be understood that these spatial relation terms are intended to include directions other than those depicted in the drawings for devices in use or operation. Furthermore, when a layer is referred to as being “between” two layers, it may be the only layer between the two layers, or there may be one or more layers in between.

[0057] In the context of this application, the structure described above the first feature may include embodiments in which the first and second features are formed in direct contact, or embodiments in which additional features are formed between the first and second features, such that the first and second features may not be in direct contact.

[0058] It should be noted that the illustrations provided in this embodiment are only schematic representations of the basic concept of the present invention. Therefore, the drawings only show components related to the present invention and are not drawn according to the actual number, shape, and size of the components in the actual implementation. In the actual implementation, the form, quantity, and proportion of each component can be arbitrarily changed, and the layout of the components may also be more complex. To keep the illustrations as concise as possible, not all structures are shown in the figures.

[0059] like Figures 1-4As shown, this invention provides a microfluidic liquid mixing experimental device based on a high-energy light source. The high-energy light source includes a high-energy synchrotron radiation source, a laboratory X-ray source, and a neutron source. The microfluidic liquid mixing experimental device includes: a microfluidic chip 1, an injection unit 2, a driving unit 3, and a control unit 4. The microfluidic chip 1 includes a microchannel structure 100, which includes an inlet channel 101, a primary mixing channel 102, a second mixing channel 103, and an outlet channel 104. The inlet channel 101 includes a first inlet. 1011 and 1012 are respectively located at the two ends of the injection channel 101; the primary mixing channel 102 is connected to the injection channel 101, and the liquid sample injected from the first injection port 1011 and the second injection port 1012 converges into the primary mixing channel 102 for collision and preliminary mixing to form a preliminary mixed sample; the second mixing channel 103 is located below the primary mixing channel 102 and is interconnected with it, and the second mixing channel 103 includes a main channel 1031 and a sub-channel 103. 2. The main channel 1031 and the sub-channel 1032 extend downwards and intersect to form multiple interconnected annular channels, and adjacent annular channels are connected by a mixing manifold 1034; the sample outlet channel 104 is located below the second mixing channel 103 and is connected to the output end of the second mixing channel 103 (each annular channel has a mixing manifold 1034, and the output end of the second mixing channel 103 is the lowest mixing manifold 1034). The initially mixed sample enters through the second mixing channel 103. After multiple mixing processes, the sample enters the outlet channel 104; the injection unit 2 includes a first injection pump 21 and a second injection pump 22. The injection output end of the first injection pump 21 is connected to the first inlet 1011, and the injection output end of the second injection pump 22 is connected to the second inlet 1012. The first injection pump 21 and the second injection pump 22 respectively inject the liquid sample into the microfluidic structure 100; the drive unit 3 is connected to the microfluidic chip 1 and is used to adjust the position of the microfluidic chip 1; the control unit 4 is electrically connected to the injection unit 2 and the drive unit 3 respectively.

[0060] Specifically, the control unit 4 precisely controls the flow rate of the liquid sample injected by the first injection pump 21 and the second injection pump 22. The mixing time is controlled by adjusting the flow rate. The liquid sample is injected into the injection channel 101 from two independent first inlet ports 1011 and second inlet ports 1012, respectively. The two liquid samples contact and collide in the initial mixing channel 102 and are initially mixed to form a preliminary mixed sample. Then, the preliminary mixed sample enters the main channel 1031 and sub-channel 1032 of the second mixing channel 103. Both the main channel 1031 and sub-channel 1032 extend downwards in a serpentine pattern, and they intersect multiple times to form multiple annular channels. Adjacent annular channels are connected by a mixing confluence port 1034. In a specific embodiment of the present invention, the mixing manifold 1034 is simultaneously connected to the main channel 1031 and the sub-channel 1032 (the mixing manifold 1034 is formed by the intersection of the main channel 1031 and the sub-channel 1032). Each time the initial mixed sample passes through the mixing manifold 1034 between two adjacent annular channels, due to the difference in the liquid flow rate between the main channel 1031 and the sub-channel 1032, an unbalanced collision of the two fluids is formed at the liquid interface. The liquid sample is mixed through the principle of turbulent mixing, thereby improving the mixing efficiency of the fluid. After being mixed multiple times by the second mixing channel 103, the initial mixed sample flows from the lowermost mixing manifold 1034 to the sample outlet channel 104.

[0061] In addition, a standard connector 201 is installed at the first injection port 1011, and a standard connector 202 is installed at the second injection port 1012. The standard connector 201 at the first injection port 1011 is connected to the injection output end of the first injection pump 21 via a pipeline, and the standard connector 202 at the second injection port 1012 is connected to the injection output end of the second injection pump 22 via a pipeline. However, the structure, model, and material of the standard connectors (the standard connector 201 at the first injection port 1011 and the standard connector 202 at the second injection port 1012) are not subject to excessive restrictions. The standard connectors are provided to facilitate the connection between the pipeline and the first injection port 1011 and the second injection port 1012, and should meet the actual usage requirements. In other examples, flow meters can also be installed on both the first injection pump 21 and the second injection pump 22, but there are no excessive restrictions on the specifics.

[0062] In addition, the drive unit 3 includes a two-dimensional moving platform and a two-dimensional drive motor. The two-dimensional moving platform includes a horizontal position adjustment module and a vertical position adjustment module. The two-dimensional drive motor drives the horizontal position adjustment module to adjust the movement of the microfluidic chip 1 in the horizontal direction, and the two-dimensional drive motor drives the vertical position adjustment module to adjust the movement of the microfluidic chip 1 in the vertical direction. This enables rapid calibration of the beam center of the high-energy light source with the optical path of the microfluidic chip 1, thereby determining the observation area and realizing the dynamic characterization of the time-resolved microstructure.

[0063] Preferably, the microfluidic chip 1 is fixed on a two-dimensional moving platform via an adapter plate (not shown in the figure).

[0064] As an example, the sample outlet end of the sample outlet channel 104 is also connected to a sample collector (not shown in the figure), which is used to collect the mixed sample.

[0065] Specifically, the sample outlet of the sample outlet channel 104 is connected to the sample collector via a standard connector 203, but no excessive restrictions are placed on the structure, model, material, etc. of the standard connector 203.

[0066] As an example, the microfluidic chip 1 includes a substrate layer 10 and a sealing layer 20. The microchannel structure 100 is formed in the substrate layer 10, and the sealing layer 20 is located on the side of the substrate layer 10 where the microchannel structure 100 is formed. The sealing layer 20 is configured to match the shape of the substrate layer 10.

[0067] For details, please refer to Figure 2a , 2b The microfluidic chip 1 consists of two layers, namely a substrate layer 10 and a sealing layer 20. The opening direction of the microchannel structure 100 is adjacent to the sealing layer 20. When the driving unit 3 adjusts the position of the microfluidic chip 1, the center of the high-energy light source beam is aligned with the optical path of the microfluidic chip 1, thereby determining the observation area. At this time, the center of the beam penetrates the sealing layer 20 and irradiates the microchannel structure 100.

[0068] As an example, both the substrate layer 10 and the sealing layer 20 are made of polymethyl methacrylate, and the microfluidic chip 1 is formed by hot-pressing the substrate layer 10 and the sealing layer 20 together.

[0069] Specifically, both the substrate layer 10 and the sealing layer 20 are made of polymethyl methacrylate, which is hard, transparent, easy to observe in experiments, has high X-ray penetration and low absorption of high-energy X-rays, and is also radiation resistant.

[0070] As an example, the total thickness of the microfluidic chip 1 is 2.8–3.2 mm, the thickness of the substrate layer 10 is 1.8–2.2 mm, and the depth of the microchannel structure 100 is 100–200 μm.

[0071] Specifically, the total thickness of the microfluidic chip 1 can be any value within the range of 2.8mm, 2.9mm, 3.0mm, 3.1mm, 3.2mm, etc., and can be adjusted according to actual needs; the thickness of the substrate layer 10 can be any value within the range of 1.8mm, 1.9mm, 2.0mm, 2.1mm, 2.2mm, etc., and can be adjusted according to actual needs; if the total thickness of the microfluidic chip 1 is a fixed value, the thicker the substrate layer 10, the thinner the corresponding sealing layer 20. If the thickness of the sealing layer 20 is too thick, it will affect the penetration of X-rays; if the thickness of the sealing layer 20 is too thin, it will affect the pressure resistance of the overall microfluidic chip 1; the depth of the microchannel structure 100 can be any value within the range of 100μm, 120μm, 140μm, 160μm, 180μm, 200μm, etc., and can be adjusted according to actual needs.

[0072] In a specific embodiment of the present invention, the microchannel structure 100 is milled on the substrate layer 10 by milling. The microchannel structure 100 includes an inlet channel 101, a primary mixing channel 102, a second mixing channel 103 and an outlet channel 104, and the depth of each channel is the same.

[0073] As an example, the width L of the sample outlet channel is not less than the width of the mixing manifold 1034, and the width L of the sample outlet channel is 280μm to 330μm.

[0074] Specifically, the mixed sample, after being mixed in the primary mixing channel 102 and the second mixing channel 103, flows out through the sample outlet channel 104. The sample outlet channel 104 can receive the focused synchrotron X-ray signal, realizing the dynamic characterization of the microstructure of the mixed sample; see reference Figure 3 The schematic diagram of the microchannel structure 100 shows that the width L of the sample outlet channel can be any value within the range of 280μm, 290μm, 300μm, 310μm, 320μm, 330μm, etc., and can be adjusted according to actual needs.

[0075] As an example, the annular channel is an asymmetrical annular channel 1033. The annular channel includes a first semi-circular channel 10331 and a second semi-circular channel 10332. Multiple first semi-circular channels 10331 form a connected main channel 1031, and multiple second semi-circular channels 10332 form a connected sub-channel 1032.

[0076] For details, please refer to Figure 3 , Figure 4 The second mixing channel 103 is composed of multiple annular channels. The main channel 1031 is formed by multiple first semi-circular channels 10331, and the sub-channel 1032 is formed by multiple second semi-circular channels 10332.

[0077] As an example, the number of ring channels is 4 to 8.

[0078] Specifically, the number of ring channels can be any value within a range, such as 4, 5, 6, 7, or 8. Each ring channel corresponds to one mixing manifold 1034. The number of ring channels is consistent with the number of mixing manifolds 1034. (See reference...) Figure 3 The mixing port 1034 located at the bottom is the output end of the second mixing channel 103.

[0079] Preferably, there are 6 annular channels, that is, 6 mixing confluence ports 1034 are formed.

[0080] As an example, the width of the first semi-circular channel 10331 is greater than the width of the second semi-circular channel 10332.

[0081] Specifically, the width of the first semi-circular channel 10331 is the inner diameter of the main channel 1031, and the width of the second semi-circular channel 10332 is the inner diameter of the sub-channel 1032.

[0082] As an example, the width of the first semi-circular channel 10331 is 1.5 to 2 times the width of the second semi-circular channel 10332.

[0083] Specifically, the liquid mass flow rate in the wider main channel 1031 is greater than that in the narrower sub-channel 1032. Therefore, the flow inertia of the fluid in the main channel 1031 is greater than that in the sub-channel 1032. Due to the difference in fluid inertia between the main channel 1031 and the sub-channel 1032, unbalanced collisions occur during liquid mixing. After each collision, the main channel 1031 and the sub-channel 1032 change their positions on the x-axis (the main channel 1031 and the sub-channel 1032 extend downwards and intersect; when the main channel 1031 is on the left, the sub-channel 1032 is on the corresponding right; after the fluid mixing collision, the main channel 1031 is on the right, and the sub-channel 1032 is on the corresponding left; that is, both the main channel 1031 and the sub-channel 1032 change their positions on the x-axis), thereby achieving higher fluid mixing efficiency.

[0084] In a specific embodiment of the present invention, the width of the first semi-circular channel 10331 is 1.5, 1.6, 1.7, 1.8, or 2 times the width of the second semi-circular channel 10332.

[0085] The present invention also provides an application of a microfluidic liquid mixing experimental device based on a high-energy light source, which is used for time-resolved microstructure characterization of soft matter systems.

[0086] Specifically, relying on the Shanghai Synchrotron Radiation Facility, the microfluidic liquid mixing experimental device provided in this invention is integrated with the synchrotron radiation device to conduct time-resolved scientific research on the microstructure characterization of soft matter systems. Based on the microchannel structure 100 creatively designed in this invention, X-ray irradiation labeling of samples can be achieved on a millisecond to microsecond timescale under physiological solution conditions. By tracking the dynamic changes in the microstructure of the soft matter system and the interactions between basic structural unit molecules during the online fluid mixing process, it can provide a powerful research tool for the design and screening of drug targets for major diseases and the study of rapid chemical reaction kinetics, and can reduce the impact of high-irradiation environments on the irradiation damage of soft matter systems.

[0087] To better understand the microfluidic liquid mixing experimental device based on a high-energy light source and its application in this invention, the application of the microfluidic liquid mixing experimental device based on a high-energy light source in this invention will be described below with reference to specific embodiments. It should be noted that these embodiments are merely descriptive and do not limit the invention in any way.

[0088] Example 1

[0089] This embodiment provides a microfluidic liquid mixing experimental device based on a high-energy light source. The microfluidic liquid mixing experimental device includes: a microfluidic chip 1, an injection unit 2, a driving unit 3, and a control unit 4.

[0090] The microfluidic chip 1 includes a microchannel structure 100, which comprises an inlet channel 101, a primary mixing channel 102, a second mixing channel 103, and an outlet channel 104. The inlet channel 101 includes a first inlet 1011 and a second inlet 1012, located at opposite ends of the inlet channel 101. The primary mixing channel 102 is connected to the inlet channel 101. Liquid samples injected from the first inlet 1011 and the second inlet 1012 converge in the primary mixing channel 102 for collision and initial mixing, forming a primary mixed sample. The second mixing channel 103 is located below the primary mixing channel 102 and is interconnected. The second mixing channel 103 includes a main channel 1031 and a sub-channel 1032, which extend downwards and intersect. The system comprises six asymmetrical annular channels 1033, each including six first semi-circular channels 10331 and six second semi-circular channels 10332. The six first semi-circular channels 10331 form a main channel 1031, and the six second semi-circular channels 10332 form sub-channels 1032. The width of the first semi-circular channel 10331 is 1.7 times the width of the second semi-circular channel 10332, and adjacent annular channels 1033 are connected by a mixing manifold 1034. The sample outlet channel 104 is located below the second mixing channel 103 and is connected to the output end of the second mixing channel 103. The width L of the sample outlet channel is 300 μm, which is not less than the width of the mixing manifold 1034. The initially mixed sample enters the sample outlet channel 104 after being mixed multiple times in the second mixing channel 103.

[0091] The injection unit 2 includes a first injection pump 21 and a second injection pump 22. The injection output end of the first injection pump 21 is connected to the first inlet 1011, and the injection output end of the second injection pump 22 is connected to the second inlet 1012. The first injection pump 21 and the second injection pump 22 respectively inject liquid samples into the microchannel structure 100.

[0092] The drive unit 3 is connected to the microfluidic chip 1 and is used to adjust the position of the microfluidic chip 1;

[0093] The control unit 4 is electrically connected to the injection unit 2 and the drive unit 3 respectively.

[0094] In this embodiment, the microfluidic chip 1 includes a substrate layer 10 and a sealing layer 20, both of which are made of polymethyl methacrylate. The microfluidic chip 1 is formed by hot-pressing the substrate layer 10 and the sealing layer 20. The microchannel structure 100 is formed on the substrate layer 10, and the sealing layer 20 is located on the side of the substrate layer 10 where the microchannel structure 100 is formed. The morphology of the sealing layer 20 matches that of the substrate layer 10. The total thickness of the microfluidic chip 1 is 3 mm, the thickness of the substrate layer 10 is 2 mm, the thickness of the sealing layer 20 is 1 mm, and the depth of the microchannel structure 100 is 150 μm.

[0095] This embodiment also provides an application of a microfluidic liquid mixing experimental device based on a high-energy light source. The microfluidic liquid mixing experimental device in this embodiment is integrated with a synchrotron radiation experimental station. The microfluidic chip 1 is placed perpendicular to the incident light direction, where X and Y are two directions perpendicular to the incident light, with X representing the horizontal direction and Y representing the vertical direction. The control unit 4 controls the drive unit 3 to move the microfluidic chip 1 horizontally and vertically, achieving collimation and correction of the optical path. Then, two liquid samples, ink and ultrapure water, are injected. Ink is injected through the first inlet 1011, and ultrapure water is injected through the second inlet 1012. The control unit 4 precisely controls the flow rate of the liquid injected by the first injection pump 21 and the second injection pump 22, achieving efficient mixing of ink and ultrapure water at different time scales. (See reference...) Figure 5 As shown, ink and ultrapure water were injected at flow rates of 0.2 mL / min, 0.3 mL / min, 0.4 mL / min, 0.5 mL / min, 0.6 mL / min, and 0.7 mL / min, respectively. The mixing state of the two liquids in the second mixing channel 103 was observed. Figure 5 The uniformity of color distribution at the sample outlet channel 104 is shown in the figure. It can be seen that when the flow rate reaches 0.5 mL / min, efficient mixing of the two liquids can be achieved. That is, the microfluidic liquid mixing experimental device in this embodiment can achieve a flow rate of 0.5 mL / min and achieve efficient mixing of fluids.

[0096] In summary, the microfluidic liquid mixing experimental device of this invention includes a microfluidic chip, an injection unit, a driving unit, and a control unit. The control unit precisely controls the driving unit to achieve rapid alignment of the beam center of the high-energy light source with the optical path of the microfluidic chip. The control unit also precisely controls the flow rate of the first and second injection pumps injecting liquid samples, achieving rapid mixing between liquid samples at the millisecond scale. Liquid samples are injected into the injection channel from two independent first and second injection ports. The two liquid samples contact and collide in the initial mixing channel and are initially mixed to form a preliminary mixed sample. The second mixing channel includes a main channel and sub-channels. The main channel and sub-channels extend downward and intersect multiple times, each intersection forming a connected annular channel. Multiple annular channels form the second mixing channel. The formed preliminary mixed sample flows into the main channel and sub-channels respectively. Each time it passes through the mixing confluence between two adjacent annular channels, the sample is mixed with the main channel. Due to the difference in liquid flow rates between the main channel and sub-channels, unbalanced collisions occur at the liquid interface, mixing the liquid sample through the principle of turbulent mixing, thereby improving the mixing efficiency. The microfluidic liquid mixing experimental device in this invention introduces the principle of turbulent mixing on the basis of laminar mixing. By changing the microchannel structure, the fluid mixing efficiency is improved, and the device adopts a modular design, suitable for experiments at different experimental terminals. Furthermore, by integrating a microfluidic chip with a high-energy light source, rapid time-resolved characterization of the microstructure of soft matter systems can be achieved. By tracking the dynamic changes in the microstructure of the soft matter system and the interactions between basic structural unit molecules during fluid mixing, a powerful research tool can be provided for the design and screening of drug targets for major diseases and the study of rapid chemical reaction kinetics, while also reducing the impact of high-irradiation environments on the radiation damage to soft matter systems. Therefore, this invention effectively overcomes the various shortcomings of existing technologies and has high industrial application value.

[0097] The above embodiments are merely illustrative of the principles and effects of the present invention and are not intended to limit the invention. Any person skilled in the art can modify or alter the above embodiments without departing from the spirit and scope of the present invention. Therefore, all equivalent modifications or alterations made by those skilled in the art without departing from the spirit and technical concept disclosed in the present invention should still be covered by the claims of the present invention.

Claims

1. A high-energy light source based microfluidic liquid mixing experimental device, characterized in that: The microfluidic liquid mixing experimental device includes: A microfluidic chip includes a microchannel structure comprising an inlet channel, a primary mixing channel, a second mixing channel, and an outlet channel. The inlet channel includes a first inlet and a second inlet, located at opposite ends of the inlet channel. The primary mixing channel is connected to the inlet channel, allowing liquid samples injected from the first and second inlets to converge and initially mix, forming a preliminary mixed sample. The second mixing channel is located below and interconnected with the primary mixing channel, comprising a main channel and sub-channels. The main channel and sub-channels extend downwards and intersect to form multiple interconnected annular channels, with adjacent annular channels connected via a mixing confluence. The outlet channel is located below the second mixing channel and connected to its output end. The preliminary mixed sample undergoes multiple mixing processes in the second mixing channel before entering the outlet channel. An injection unit is provided, comprising a first injection pump and a second injection pump. The injection output end of the first injection pump is connected to the first inlet, and the injection output end of the second injection pump is connected to the second inlet. The first injection pump and the second injection pump respectively inject liquid samples into the microchannel structure. A driving unit, which is connected to the microfluidic chip, is used to adjust the position of the microfluidic chip; The control unit is electrically connected to the injection unit and the drive unit, respectively.

2. The high-energy light source based microfluidic liquid mixing experiment device according to claim 1, characterized in that: The microfluidic chip includes a substrate layer and a sealing layer. The microchannel structure is formed in the substrate layer, and the sealing layer is located on the side of the substrate layer where the microchannel structure is formed. The sealing layer is configured to match the morphology of the substrate layer.

3. The high-energy light source based microfluidic liquid mixing experiment device according to claim 2, characterized in that: Both the substrate layer and the sealing layer are made of polymethyl methacrylate, and the microfluidic chip is formed by thermo-pressing the substrate layer and the sealing layer.

4. The high-energy light source based microfluidic liquid mixing experiment device according to claim 2, characterized in that: The total thickness of the microfluidic chip is 2.8–3.2 mm, the thickness of the substrate layer is 1.8–2.2 mm, and the depth of the microchannel structure is 100–200 μm.

5. The microfluidic liquid mixing experimental device based on a high-energy light source according to claim 1, characterized in that: The width of the sample outlet channel is not less than the width of the mixing confluence port, and the width of the sample outlet channel is 280μm to 330μm.

6. The microfluidic liquid mixing experimental device based on a high-energy light source according to claim 1, characterized in that: The annular channel is an asymmetrical annular channel, which includes a first semi-circular channel and a second semi-circular channel. Multiple first semi-circular channels form a connected main channel, and multiple second semi-circular channels form a connected sub-channel.

7. The microfluidic liquid mixing experimental device based on a high-energy light source according to claim 1, characterized in that: The number of annular channels is 4 to 8.

8. The microfluidic liquid mixing experimental device based on a high-energy light source according to claim 6, characterized in that: The width of the first semi-circular channel is greater than the width of the second semi-circular channel.

9. The microfluidic liquid mixing experimental device based on a high-energy light source according to claim 6, characterized in that: The width of the first semi-circular channel is 1.5 to 2 times the width of the second semi-circular channel.

10. An application of the microfluidic liquid mixing experimental device based on a high-energy light source as described in any one of claims 1 to 9, characterized in that: The microfluidic liquid mixing experimental apparatus is used for time-resolved characterization of the microstructure of soft matter systems.

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