Microparticle monodisperse device

Abstract

The application discloses a kind of microparticle monodisperse devices, wherein, chamber and ejection hole are equipped in focused flow channel, ejection hole is connected with chamber and external environment;The inner diameter of the core capillary of liquid flow introduction module is much larger than the particle size of microparticles, the outlet end of the core capillary is inserted into the chamber and is opposite to the ejection hole, and the core capillary is used to transport microparticle suspension;Air flow introduction module is connected with focused flow channel, used to introduce high-pressure gas into the chamber, to form a pressure difference between the chamber and the external environment, and then the microparticle suspension flowing out of the outlet end of the core capillary is pulled into a very thin liquid jet under the wrapping and extrusion of coaxial sheath gas flow at the ejection hole, and breaks into monodisperse particle droplets independently outside the focused flow channel.The application is not easy to block, the efficiency of microparticle monodispersion is high, the flux is high, and it can be compatible with organic mass spectrometer and spectral analyzer.

Description

Technical Field

[0001] This invention relates to the field of micron particle monodispersion technology, and more particularly to a micron particle monodispersion device. Background Technology

[0002] Currently, there are several types of micron-sized particle monodispersion technologies:

[0003] One method utilizes a capillary with an inner diameter close to that of micron-sized particles such as cells to monodisperse these particles. Because the capillary's inner diameter is similar to the particle diameter, only one particle is allowed to enter the capillary at a time under pressure, achieving monodispersity. Hydrofluoric acid is used to etch the capillary outlet section to obtain an outlet tip with a reduced outer diameter while maintaining the inner diameter. This avoids cell aggregation after dispersion and facilitates the final emission of cells into analytical detectors such as mass spectrometers. However, because this method uses a liquid flow with a diameter close to that of cells to introduce the flow channel, it is very prone to clogging.

[0004] Secondly, using Dean flow to monodisperse micron-sized particles such as cells requires a high voltage of several kilovolts to assist particle ejection. This high voltage is incompatible with some ionization methods. The high voltage is typically applied to a connecting tee, and prolonged operation can cause cell debris to accumulate in the dead volume, eventually clogging the conduit.

[0005] Third, flow focusing is used to monodisperse micron-sized particles such as cells. A high-velocity sheath flow is used to focus the cell suspension introduced by the core flow, and a high voltage of several thousand volts is used to assist cell ejection. Because this method requires a high flow rate of sheath flow to focus and disperse micron-sized particles such as cells, it is not suitable for detection methods that use gas chromatography-mass spectrometry or liquid chromatography as detectors. Summary of the Invention

[0006] The present invention aims to at least solve one of the technical problems existing in the prior art. Therefore, one object of the present invention is to provide a micron-particle monodisperse device that is not easily clogged, has high micron-particle monodisperse efficiency, high throughput, and is compatible with organic mass spectrometry and spectroscopic analyzers, etc.

[0007] A micron-particle monodisperse device according to an embodiment of the present invention includes:

[0008] A focusing flow channel is provided with a chamber and an ejection port, the ejection port being connected to the chamber and the external environment;

[0009] A liquid flow introduction module includes a core capillary tube, the inner diameter of which is much larger than the particle size of micron particles. The outlet end of the core capillary tube extends into the chamber and is directly opposite to the ejection orifice. The core capillary tube is used to transport a suspension of micron particles.

[0010] An airflow introduction module, connected to the focusing flow channel, is used to introduce high-pressure gas into the chamber, creating a pressure difference between the chamber and the external environment. This causes the micron-sized particle suspension flowing out of the outlet end of the core capillary to be drawn into an extremely fine liquid jet under the compression of the coaxial sheath gas flow at the ejection orifice, and then autonomously broken into monodisperse droplets outside the focusing flow channel.

[0011] According to the micron-particle monodisperse device of the present invention, on the one hand, since the inner diameter of the core capillary is much larger than the particle size of the micron particles, the micron-particle suspension flows from the input end to the output end of the core capillary, effectively avoiding blockage of the core capillary; on the other hand, the sheath gas drives the micron-particle suspension to form an extremely fine jet and autonomously break it into monodisperse micron-particle droplets. Specifically, high-pressure gas is continuously and stably injected into the chamber through the airflow introduction module, creating a pressure difference between the chamber and the external environment. The high-pressure gas in the chamber then forms a focused sheath gas flow near the ejection orifice. The sheath gas envelops the micron-particle suspension flow flowing from the outlet end of the core capillary. The sheath gas focuses and compresses the micron-particle suspension flow, achieving a suitable focusing flow chamber pressure difference and a suitable liquid flow rate in the core capillary. Under these conditions, the diameter of the ultrafine jet can reach a size close to that of micron particles, thus enabling the micron particles to be arranged in a row to form an ultrafine jet. After the ultrafine jet breaks down autonomously, it forms monodisperse micron particles encapsulated by droplets. Because the frequency at which the focused ultrafine jet breaks down into droplets with monodisperse micron particles is extremely high, between kHz and MHz, the efficiency is high, thus achieving higher throughput. This avoids the problem of high sheath flow rate required to achieve high throughput in existing flow focusing schemes, and also eliminates the need for high-pressure electrospray assisted liquid flow ejection. Therefore, under high throughput conditions, it can be compatible with organic mass spectrometry and spectrometers. That is, after the ultrafine jet breaks down autonomously, the monodisperse micron particles encapsulated by droplets can directly enter the analyzer, including but not limited to organic mass spectrometers and spectrometers. In summary, the micron-particle monodisperse device of the present invention is not prone to clogging and does not require complex liquid flow pipelines to form special liquid flow dynamics to disperse particles in the liquid flow. Instead, it utilizes an extremely fine jet with a size close to the particle diameter and the droplets of the extremely fine jet breaking into monodisperse micron-particles. The micron-particle monodisperse device has high efficiency, high throughput, and is compatible with organic mass spectrometry and spectrometers.

[0012] In some embodiments, the focusing flow channel includes a chamber body and an orifice plate; the orifice plate is provided with the ejection hole, the orifice plate is fixed on the chamber body and forms the chamber between the orifice plate and the chamber body; the core capillary passes through the chamber body, so that the outlet end of the core capillary extends into the chamber; the airflow introduction module is connected to the chamber body.

[0013] In some embodiments, the chamber body includes a base and two protrusions located on the same side of the base and alternating with each other. The perforated plate is opposite to the base and fixed on the two protrusions. The focusing flow channel also includes two side plates, which are correspondingly distributed on opposite sides of the chamber body and fixed to the chamber body and the perforated plate, so that the base, the two protrusions, the perforated plate and the two side plates together form the chamber.

[0014] In some embodiments, the side panel is a transparent panel.

[0015] In some embodiments, the focusing flow channel further includes a support assembly for supporting the segment of the core capillary located in the chamber.

[0016] In some embodiments, the support assembly includes N support plates, which are fixed between the two protrusions and the perforated plate at intervals by pads; the support plates are provided with limiting support holes for the core capillary to pass through, and the tube segment of the core capillary located in the chamber adaptably passes through the N support plates; the support plates are also evenly distributed with a plurality of exhaust holes.

[0017] In some embodiments, the fluid introduction module further includes a sheath, a tee, and a sheath flow injection pump; the sheath is coaxially sleeved outside the core capillary, the outlet end of the sheath extends into the chamber and is close to the outlet end of the core capillary, and the outlet end of the core capillary protrudes beyond the outlet end of the sheath; the tee fixes the sheath and the core capillary; the sheath flow injection pump is connected to the tee and is used to inject sheath fluid into the sheath.

[0018] In some embodiments, the distance between the outlet end of the core capillary and the outlet end of the sheath is 50-500 μm.

[0019] In some embodiments, the distance from the outlet end of the core capillary to the ejection orifice is 0-500 μm.

[0020] In some embodiments, the airflow introduction module includes a high-pressure gas source, an air inlet pipe, and a gas flow controller; the high-pressure gas source is connected to the inlet end of the gas flow controller, the outlet end of the gas flow controller is connected to the inlet end of the air inlet pipe, and the outlet end of the air inlet pipe is connected to the chamber.

[0021] Additional aspects and advantages of the invention will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of the invention. Attached Figure Description

[0022] The above and / or additional aspects and advantages of the present invention will become apparent and readily understood from the description of the embodiments taken in conjunction with the following drawings, in which:

[0023] Figure 1 This is a schematic diagram of a micron-sized particle monodisperse device according to an embodiment of the present invention;

[0024] Figure 2 for Figure 1 Enlarged view of point A in the middle;

[0025] Figure 3a This is a front view of the chamber body of the focusing flow channel of the micron-particle monodisperse device according to an embodiment of the present invention;

[0026] Figure 3b for Figure 3a Cross-sectional view at BB;

[0027] Figure 3c This is a side view of the chamber body of the focusing flow channel of the micron particle monodisperse device according to an embodiment of the present invention;

[0028] Figure 4 This is a front view of the orifice plate of the focusing flow channel in the micron particle monodisperse device according to an embodiment of the present invention;

[0029] Figure 5 This is a front view of the support plate of the focusing flow channel of the micron particle monodisperse device according to an embodiment of the present invention;

[0030] Figure 6a This is a front view of the pad block of the focusing flow channel in the micron particle monodisperse device according to an embodiment of the present invention;

[0031] Figure 6b for Figure 6a A cross-sectional view at CC;

[0032] Figure 6c This is a side view of the pad block of the focusing flow channel in the micron particle monodisperse device according to an embodiment of the present invention;

[0033] Figure 7a A schematic diagram showing the flow pattern of the micron-sized particle suspension at the outlet end of the core capillary;

[0034] Figure 7b A schematic diagram showing the extremely fine jet outside the orifice of the orifice plate and its process of breaking down into single droplets;

[0035] Figure 7c This diagram shows a microscopic image of monodisperse micron particles encapsulated in droplets after the ultrafine jet spontaneously breaks up;

[0036] Figure 8aA schematic diagram showing the state of microspheres and cells in a suspension of undispersed microspheres and cells is presented.

[0037] Figure 8b A schematic diagram showing the state of microspheres and cells collected after passing through this example device.

[0038] Figure label:

[0039] Micron-sized particle monodisperse device 1000; focusing flow channel 1; chamber 101; chamber body 102; base 1021; protrusion 1022; tube hole 1023; air inlet 1024; perforated plate 103; injection hole 1031; side plate 104; support plate 105; limiting support hole 1051; exhaust hole 1052; pad 106; positioning column 107; threaded part 108; liquid flow introduction module 2; core capillary 201; sample container 202; sample chamber 2021; sample injection gas pump 203; sheath 204; tee 205; sheath flow injection pump 206; air flow introduction module 3; high pressure gas source 301; gas flow controller 302; air inlet pipe 303. Detailed Implementation

[0040] Embodiments of the present invention are described in detail below. Examples of these embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain the present invention, and should not be construed as limiting the present invention.

[0041] The following is combined with Figures 1 to 8b The micron-particle monodispersing device 1000 of the present invention will be described in this embodiment.

[0042] like Figures 1 to 8b As shown, the micron particle monodispersing device 1000 of this embodiment of the invention is used to monodisperse micron particle suspensions such as cells or microplastics, and includes a focusing flow channel 1, a liquid flow introduction module 2 and an air flow introduction module 3.

[0043] Among them, such as Figure 1 and Figure 2 As shown, the focusing flow channel 1 is provided with a chamber 101 and an ejection port 1031, and the ejection port 1031 connects the chamber 101 and the external environment.

[0044] The fluid introduction module 2 includes a core capillary 201, the inner diameter of which is much larger than the particle size of micron particles. The outlet end of the core capillary 201 extends into the chamber 101 and is directly adjacent to the ejection port 1031. The core capillary 201 is used to transport the micron particle suspension. Because the inner diameter of the core capillary 201 is much larger than the particle size of micron particles, the micron particle suspension flows from the input end to the output end of the core capillary 201 without clogging it. Since the outlet end of the core capillary 201 extends into the chamber 101 and is directly adjacent to the ejection port 1031, it facilitates the ejection of the micron particle suspension from the outlet end of the core capillary 201 through the ejection port 1031.

[0045] The airflow introduction module 3 is connected to the focusing flow channel 1 and is used to introduce high-pressure gas into the chamber 101, creating a pressure difference between the chamber 101 and the external environment. This, in turn, causes the micron-sized particle suspension flowing out of the outlet end of the core capillary 201 to flow through the coaxial sheath gas at the ejection orifice 1031 (e.g., Figure 2 (As indicated by the arrow near the ejection orifice 1031) Under the enveloping and squeezing action, the liquid is drawn into an extremely fine jet and autonomously breaks into monodisperse droplets outside the focusing flow channel 1. It can be understood that high-pressure gas is continuously and stably injected into the chamber 101 through the airflow introduction module 3, creating a pressure difference between the chamber 101 and the external environment. Consequently, the high-pressure gas in the chamber 101 forms a focused sheath gas flow near the ejection orifice 1031. This sheath gas envelops the micron-particle suspension flowing from the outlet end of the core capillary 201 and simultaneously ejects it from the ejection orifice 1031. During this process, by utilizing the sheath gas to focus and squeeze the micron-particle suspension, under suitable conditions of pressure difference inside and outside the chamber 101 and liquid flow rate in the core capillary 201, the diameter of the stable extremely fine jet can reach a size close to that of micron-particles. This allows the micron-particles to be arranged in a line, and after autonomous breakup of the extremely fine jet, monodisperse micron-particles encapsulated by droplets are formed and enter the analyzer, which includes, but is not limited to, an organic mass spectrometer or spectrometer.

[0046] According to the embodiment of the present invention, the micron-particle monodisperse device 1000 has the following advantages: First, since the inner diameter of the core capillary 201 is much larger than the particle size of the micron particles, the micron-particle suspension flows from the input end to the output end of the core capillary 201, effectively preventing the core capillary 201 from becoming clogged. Second, the sheath gas drives the micron-particle suspension to form an extremely fine jet and autonomously break it into droplets of monodisperse micron particles (e.g., ...). Figure 2As shown), specifically, high-pressure gas is continuously and stably injected into chamber 101 through airflow introduction module 3, creating a pressure difference between chamber 101 and the external environment. This causes the high-pressure gas in chamber 101 to form a focused sheath gas flow near ejection port 1031. The sheath gas envelops the micron-particle suspension liquid flow exiting from the core capillary 201. By focusing and compressing the micron-particle suspension liquid flow using the sheath gas, under suitable conditions of pressure difference between the inside and outside of the focusing flow chamber 101 and liquid flow rate in the core capillary 201, the diameter of the ultrafine jet can reach a size close to that of micron-particles, thus arranging the micron-particles in a line to form an ultrafine jet. After autonomous fragmentation, monodisperse micron-sized particles encapsulated by droplets are formed. Due to the extremely high frequency (between 100 kHz and 1 MHz) of the focused ultrafine jet breaking down into droplets containing monodisperse micron-sized particles, the efficiency is high, thus achieving higher throughput. This avoids the problem of requiring high sheath flow rates to achieve high throughput in existing flow focusing schemes, and also eliminates the need for high-pressure electrospray assisted liquid flow ejection. Therefore, it is compatible with organic mass spectrometry and spectrometers under high-throughput conditions. That is, after the ultrafine jet autonomously fragments, the monodisperse micron-sized particles encapsulated by droplets can directly enter the analyzer, including but not limited to organic mass spectrometers and spectrometers. In summary, the micron-sized particle monodispersing device 1000 of this invention is not prone to clogging, does not require complex liquid flow pipelines to form special liquid flow dynamics to disperse particles in the liquid flow, but instead utilizes an ultrafine jet with a size close to the particle diameter and droplets formed by the ultrafine jet breaking down into monodisperse micron-sized particles. It achieves high micron-sized particle monodispersing efficiency, high throughput, and compatibility with organic mass spectrometry and spectrometers.

[0047] In some embodiments, such as Figures 1 to 6c As shown, the focusing flow channel 1 includes a chamber body 102 and an orifice plate 103; the orifice plate 103 is provided with an ejection hole 1031, and the orifice plate 103 is fixed on the chamber body 102 and forms a chamber 101 between the orifice plate 103 and the chamber body 102; the core capillary 201 passes through the chamber body 102, so that the outlet end of the core capillary 201 extends into the chamber 101. Specifically, the chamber body 102 is provided with a tube hole 1023 for the core capillary 201 to pass through. The tube passes through the orifice 1023, allowing the outlet end of the core capillary 201 to extend into the chamber 101 and be directly opposite and close to the ejection orifice 1031 of the orifice plate 103. The airflow introduction module 3 is connected to the chamber body 102. Specifically, the chamber body 102 is provided with an air inlet 1024 connected to the airflow introduction module 3. The airflow introduction module 3 is connected to the air inlet 1024 and then communicates with the chamber 101 through the air inlet 1024 to input high-pressure gas into the chamber 101.

[0048] In some embodiments, the chamber body 102 includes a base 1021 and two protrusions 1022 located on the same side of the base 1021 and alternating with each other. An orifice plate 103 is opposite to the base 1021 and fixed to the two protrusions 1022. The focusing flow channel 1 also includes two side plates 104, which are correspondingly distributed on opposite sides of the chamber body 102 and fixed to the chamber body 102 and the orifice plate 103. Thus, the base 1021, the two protrusions 1022, the orifice plate 103, and the two side plates 104 together form the chamber 101. Therefore, the focusing flow channel 1 has a simple structure and is easy to manufacture and assemble.

[0049] In some embodiments, the side panel 104 is a transparent panel for easy observation. Preferably, the transparent panel is made of ultra-clear glass, which has good transparency and is resistant to high pressure.

[0050] In some embodiments, the focusing flow channel 1 further includes a support component for supporting the tube segment of the core capillary 201 located in the chamber 101, so as to stabilize the output end of the core capillary 201 and facilitate the formation of a stable ultrafine jet.

[0051] In some embodiments, the support assembly includes N support plates 105 (N being an integer greater than or equal to 1), and the N support plates 105 are fixed between the two protrusions 1022 and the perforated plate 103 at intervals by spacers 106, for example, Figure 1 The diagram illustrates two support plates 105. One support plate 105 has its opposite ends abutting against two protrusions 1022. The other support plate 105 is separated from the first support plate 105 and the perforated plate 103 by pads 106. The support plate 105 has a limiting support hole 1051 for the core capillary 201 to pass through (e.g., ...). Figure 5 As shown, the core capillary 201, located in the chamber 101, is adapted to pass through N support plates 105, which can stabilize the output end of the core capillary 201 and facilitate the formation of a stable ultrafine jet. Multiple exhaust holes 1052 are also evenly distributed on the support plates 105, which facilitates the uniform flow of high-pressure airflow through the chamber 101 and towards the ejection hole 1031.

[0052] In some embodiments, the perforated plate 103, support plate 105, pad 106, and protrusion 1022 are positioned by positioning pins 107 and fastened by threaded parts 108. Specifically, as shown... Figure 1As shown, the perforated plate 103, support plate 105, pad 106, and protrusion 1022 are provided with positioning holes. The positioning pin 107 passes through the positioning holes on the perforated plate 103, support plate 105, pad 106, and protrusion 1022 to achieve positioning between the perforated plate 103, support plate 105, pad 106, and protrusion 1022. On the one hand, it is convenient for the threaded fasteners to be fixed in the corresponding fixing holes on the perforated plate 103, support plate 105, pad 106, and protrusion 1022. On the other hand, it is beneficial for the output end of the core capillary 201 to be coaxially aligned with the injection hole 1031 of the perforated plate 103.

[0053] In some embodiments, such as Figure 1 As shown, the liquid flow introduction module 2 also includes a sample container 202 and an injection gas pump 203. The sample container 202 is made of metal, plastic, or glass, and has a sample chamber 2021 for holding a suspension of micron-sized particles. The inlet end of the core capillary 201 extends into the sample chamber 2021, and the injection gas pump 203 is connected to the sample chamber 2021. During operation, the injection gas pump 203 introduces air above the surface of the micron-sized particle suspension in the sample chamber 2021, causing the micron-sized particle suspension to enter the core capillary 201 from its inlet end and then flow out of the core capillary 201.

[0054] In some embodiments, such as Figure 1 As shown, the liquid flow introduction module 2 also includes a sheath 204, a three-way connector 205, and a sheath flow injection pump 206. The sheath 204 is coaxially sleeved outside the core capillary 201. The outlet end of the sheath 204 extends into the chamber 101 and is close to the outlet end of the core capillary 201. The outlet end of the core capillary 201 protrudes beyond the outlet end of the sheath 204, which is beneficial for forming a stable jet at a lower liquid flow rate. The three-way connector 205 fixes the sheath 204 and the core capillary 201, which is convenient and reliable. The sheath flow injection pump 206 is connected to the three-way connector 205 and is used to inject sheath fluid into the sheath 204, that is, to inject sheath fluid into the annular liquid flow channel between the sheath 204 and the core capillary 201. The sheath fluid flows out from the output end of the sheath 204 and can coaxially encapsulate the micron particle suspension, which is beneficial for improving the ionization effect of the monodisperse micron particles broken into the ultrafine liquid flow. For applications where ionization of monodisperse micron-sized particles is not required, the sheath 204, tee 205, and sheath flow injection pump 206 can be omitted. The sheath 204 and core capillary 201 are made of metal, plastic, or glass such as quartz glass.

[0055] In some embodiments, the distance between the outlet end of the core capillary 201 and the outlet end of the sheath 204 is 50-500 μm, which is beneficial for forming a stable jet at a lower liquid flow rate.

[0056] In some embodiments, the distance from the outlet end of the core capillary 201 to the ejection orifice 1031 is 0-500 μm. Since the core working principle of this embodiment is to use the air pressure distribution near the airflow ejection orifice 1031 to compress the droplet into a cone shape, ultimately forming an extremely fine jet at the front end of the droplet cone, appropriately adjusting the distance from the outlet end of the core capillary 201 to the ejection orifice 1031 is beneficial for forming a stable jet under different liquid flow rates.

[0057] In some embodiments, the inner diameter of the core capillary 201 is 25-500 μm, and the core capillary 201 is not easily blocked.

[0058] In some embodiments, such as Figure 1 As shown, the airflow introduction module 3 includes a high-pressure gas source 301, a gas flow controller 302, and an inlet pipe 303. The high-pressure gas source 301 can be a high-pressure gas cylinder or an air compressor, etc. The high-pressure gas source 301 is connected to the inlet end of the gas flow controller 302, the outlet end of the gas flow controller 302 is connected to the inlet end of the inlet pipe 303, and the outlet end of the inlet pipe 303 is connected to the chamber 101. The gas flow controller 302 can be controlled by volumetric flow rate, mass flow rate, or pipeline pressure. Regardless of the control method, it can simultaneously monitor volumetric flow rate, mass flow rate, or pipeline pressure.

[0059] The following is a specific example of monodispersing micron-sized particles using a micron-sized particle suspension. In this suspension, the cells are MCF7, and the polystyrene microspheres have a diameter of 10 μm. The cells require an isotonic solution, while the polystyrene microspheres have no specific requirements regarding solution properties. Therefore, to accommodate the cell requirements, the cells and polystyrene microspheres are dissolved in an isotonic ammonium formate solution, forming a mixed suspension, i.e., the micron-sized particle suspension. The liquid flow path employs a double-layer structure of a core capillary 201 and a sheath 204. By adjusting the appropriate pressure difference between the inside and outside of the focusing flow channel 1 and the liquid sample supply rate—with a sheath gas flow rate of 190 ml / min, an internal and external pressure difference of 7.3 kPa, a liquid flow rate of 2 μl / min in the core capillary 201, and a liquid flow rate of 20 μl / min in the sheath 204—the ultrafine jet diameter can be approximately 10 μm. Therefore, by utilizing the ultrafine jet and its self-breaking into single droplets, monodisperse of micron-sized particles can be achieved. Figure 7a The flow pattern of the micron-sized particle suspension at the outlet end of the core capillary 201 is shown. Figure 7b The extremely fine jet outside the ejection orifice 1031 and its process of breaking down into single droplets are demonstrated. Figure 7c The diagram shows a microscopic image of monodisperse micron particles encapsulated in droplets after the ultrafine jet spontaneously breaks up. Figure 8a The state of microspheres and cells in a mixed suspension of undispersed microspheres and cells is shown; Figure 8bThe state of the microspheres and cells collected after passing through this example device is shown. It can be seen that the microspheres and cells are effectively monodispersed, and if connected to an analyzer, online single-cell measurement can be further realized.

[0060] In the description of this specification, the references to terms such as "one embodiment," "some embodiments," "illustrative embodiment," "example," "specific example," or "some examples," etc., indicate that a specific feature, structure, material, or characteristic described in connection with that embodiment or example is included in at least one embodiment or example of the invention. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples.

[0061] Although embodiments of the invention have been shown and described, those skilled in the art will understand that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the invention, the scope of which is defined by the claims and their equivalents.

Claims

1. A device for monodispersing micron-sized particles, characterized in that, Suitable for compatibility with organic mass spectrometry and spectroscopic analyzers, including: A focusing flow channel is provided with a chamber and an ejection port, the ejection port being connected to the chamber and the external environment; A liquid flow introduction module includes a core capillary tube, the inner diameter of which is much larger than the particle size of micron particles. The outlet end of the core capillary tube extends into the chamber and is directly opposite to the ejection orifice. The core capillary tube is used to transport a suspension of micron particles. An airflow introduction module, connected to the focusing flow channel, is used to introduce high-pressure gas into the chamber, creating a pressure difference between the chamber and the external environment. This causes the micron-particle suspension flowing out of the outlet end of the core capillary to be drawn into an extremely fine liquid jet with micron particles arranged in a row and a diameter close to the particle size under the compression and enveloping action of the coaxial sheath gas flow at the ejection orifice. The jet then autonomously breaks into droplets containing monodisperse particles outside the focusing flow channel. The fluid inlet module also includes a sheath; the sheath is coaxially sleeved outside the core capillary, the outlet end of the sheath extends into the chamber and is close to the outlet end of the core capillary, and the outlet end of the core capillary protrudes beyond the outlet end of the sheath. The distance between the outlet end of the core capillary and the outlet end of the sheath is 50-500 μm. The distance from the outlet end of the core capillary to the ejection orifice is 0-500 μm; The inner diameter of the core capillary is 25-500 μm; Adjust the pressure difference between the inside and outside of the focusing flow channel and the liquid sample supply. The flow rate of the sheath gas is 190 ml / min, the pressure difference between the inside and outside of the focusing flow channel is 7.3 kPa, the liquid flow rate of the core capillary is 2 μl / min, and the liquid flow rate of the sheath is 20 μl / min.

2. The micron-particle monodisperse device according to claim 1, characterized in that, The focusing flow channel includes a chamber body and an orifice plate; the orifice plate is provided with the ejection hole, and the orifice plate is fixed on the chamber body and forms the chamber between the orifice plate and the chamber body; the core capillary passes through the chamber body, so that the outlet end of the core capillary extends into the chamber; the airflow introduction module is connected to the chamber body.

3. The micron-particle monodisperse device according to claim 2, characterized in that, The chamber body includes a base and two protrusions located on the same side of the base, which are alternately spaced. The perforated plate is opposite to the base and fixed on the two protrusions. The focusing flow channel also includes two side plates, which are distributed on opposite sides of the chamber body and fixed to the chamber body and the perforated plate. Thus, the base, the two protrusions, the perforated plate and the two side plates together form the chamber.

4. The micron-particle monodisperse device according to claim 3, characterized in that, The side panel is a transparent panel.

5. The micron-particle monodisperse device according to claim 3, characterized in that, The focusing flow channel also includes a support assembly for supporting the core capillary segment located in the chamber.

6. The micron-particle monodisperse device according to claim 5, characterized in that, The support assembly includes N support plates, which are fixed between the two protrusions and the perforated plate at intervals by pads; the support plates are provided with limiting support holes for the core capillary to pass through, and the tube segment of the core capillary located in the chamber fits through the N support plates; the support plates are also evenly distributed with multiple exhaust holes.

7. The micron-particle monodisperse device according to any one of claims 1-6, characterized in that, The fluid introduction module also includes a three-way connector and a sheath flow injection pump; the three-way connector fixes the sheath tube and the core capillary tube; the sheath flow injection pump is connected to the three-way connector and is used to inject sheath fluid into the sheath tube.

8. The micron-particle monodisperse device according to any one of claims 1-6, characterized in that, The airflow introduction module includes a high-pressure gas source, an air inlet pipe, and a gas flow controller; the high-pressure gas source is connected to the inlet end of the gas flow controller, the outlet end of the gas flow controller is connected to the inlet end of the air inlet pipe, and the outlet end of the air inlet pipe is connected to the chamber.

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