Spraying system

Abstract

This application relates to a spraying system, wherein the high-viscosity fluid spraying system for the human body's natural cavities includes an interventional catheter and an infusion device. The interventional catheter includes a tube body with a mixing structure. A microfluidic chip is disposed within the mixing structure. The microfluidic chip has internal channels connecting an outlet and various fluid inlets. These channels include: a main channel, one end connected to a first fluid inlet located proximally, and the other end connected to an outlet; and side channels, one end connected to a second fluid inlet located laterally, and the other end connected to the main channel. A distribution structure capable of acting on at least a portion of the fluid is disposed within the microfluidic chip. This application achieves atomization of the transported fluid through the microfluidic chip, improving the atomization effect.

Description

Technical Field

[0001] This application relates to the field of atomization technology, and in particular to spraying systems. Background Technology

[0002] Nebulizers typically transform liquids into micron-sized liquid particles. In clinical endoscopic treatments, nebulized drug delivery is often necessary to ensure uniform distribution of the injected liquid medication, thereby improving the evenness of binding between the nebulized material and the relevant tissues. The fluid input to the nebulizer can include therapeutic or restorative liquids. Current nebulizers are used to administer medications by inhalation, breaking down the liquid into a mist of tiny particles or droplets, allowing for efficient inhalation and absorption. However, during inhalation, it's difficult for all the medication to reach the lesion, resulting in unnecessary loss. Furthermore, inhalation also presents the risk of potential safety hazards, as the medication may damage organs along its route before reaching the lesion due to its own side effects.

[0003] Existing atomizers have poor atomization effects, their structure needs improvement, and their applicable scenarios are limited. Summary of the Invention

[0004] Based on this, it is necessary to address the above-mentioned technical problems. This application discloses a high-viscosity fluid spraying system for the human body's natural cavities, including an interventional catheter and an infusion device for respectively delivering a first fluid and a second fluid to the interventional catheter.

[0005] The interventional catheter includes a tube body, one end of which is a proximal end and the other end is a distal end that can extend into the bronchus. The tube body has a channel for delivering fluid from the proximal end to the distal end. The distal end of the tube body is provided with a mixing structure, through which the fluid in the channel is mixed and then output.

[0006] The mixing structure has at least a first fluid inlet, a second fluid inlet, and an outlet, with each fluid inlet having an independently configured flow channel within the pipe body;

[0007] The mixing structure contains a microchannel chip. The first fluid inlet is located near the proximal end of the microchannel chip, and the second fluid inlet is located beside the microchannel chip. The interior of the microchannel chip is a chip channel connecting the outlet and each fluid inlet. The chip channel includes:

[0008] The main channel is connected at one end to the first fluid inlet on the proximal side and at the other end to the outlet;

[0009] The side channel is connected at one end to the second fluid inlet located on the side, and at the other end to the main channel;

[0010] The chip channel is provided with a distribution structure that can act on at least a portion of the fluid;

[0011] The atomized droplet size is ≥20 micrometers. One of the first fluid and the second fluid is a liquid phase fluid and the other is a gas phase fluid. The pressure of the liquid phase fluid is 0.2 to 0.76 MPa and the pressure of the gas phase fluid is 0.1 to 0.4 MPa.

[0012] Optionally, the main channel throat width W7 is 0.1 to 0.2 mm.

[0013] Optionally, the droplet outlet width W8 is 0.15 to 0.3 mm.

[0014] Optionally, the etching depth H3 is 0.1 to 0.25 mm.

[0015] Optionally, the thickness H1 of the etched flow channel unit sheet is 0.25 to 0.55 mm.

[0016] Optionally, the atomized droplet size ranges from 20 to 60 micrometers.

[0017] This application also discloses a cell spraying system for natural human cavities, including an interventional catheter and an infusion device for delivering a first fluid and a second fluid to the interventional catheter respectively;

[0018] The interventional catheter includes a tube body, one end of which is a proximal end and the other end is a distal end that can extend into the bronchus. The tube body has a channel for delivering fluid from the proximal end to the distal end. The distal end of the tube body is provided with a mixing structure, through which the fluid in the channel is mixed and then output.

[0019] The mixing structure has at least a first fluid inlet, a second fluid inlet, and an outlet, with each fluid inlet having an independently configured flow channel within the pipe body;

[0020] The mixing structure contains a microchannel chip. The first fluid inlet is located near the proximal end of the microchannel chip, and the second fluid inlet is located beside the microchannel chip. The interior of the microchannel chip is a chip channel connecting the outlet and each fluid inlet. The chip channel includes:

[0021] The main channel is connected at one end to the first fluid inlet on the proximal side and at the other end to the outlet;

[0022] The side channel is connected at one end to the second fluid inlet located on the side, and at the other end to the main channel;

[0023] The chip channel is provided with a distribution structure that can act on at least a portion of the fluid;

[0024] The cells have a particle size of 15-120 micrometers, and one of the first fluid and the second fluid is a liquid phase fluid and the other is a gas phase fluid. The pressure of the liquid phase fluid is 0.2-0.76 MPa, and the pressure of the gas phase fluid is 0.1-0.4 MPa.

[0025] Optionally, the etching depth H3 is 0.08 to 0.12 mm.

[0026] Optionally, the droplet outlet width W8 is 0.1 to 0.2 mm.

[0027] Optionally, the width W1 of the main 130 lane is 0.2 to 0.4 mm.

[0028] Optionally, the droplet size range is 20-50 micrometers.

[0029] This application also discloses a drug spraying system for natural human cavities, including an interventional catheter and an infusion device for delivering a first fluid and a second fluid to the interventional catheter respectively;

[0030] The interventional catheter includes a tube body, one end of which is a proximal end and the other end is a distal end that can extend into the bronchus. The tube body has a channel for delivering fluid from the proximal end to the distal end. The distal end of the tube body is provided with a mixing structure, through which the fluid in the channel is mixed and then output.

[0031] The mixing structure has at least a first fluid inlet, a second fluid inlet, and an outlet, with each fluid inlet having an independently configured flow channel within the pipe body;

[0032] The mixing structure contains a microchannel chip. The first fluid inlet is located near the proximal end of the microchannel chip, and the second fluid inlet is located beside the microchannel chip. The interior of the microchannel chip is a chip channel connecting the outlet and each fluid inlet. The chip channel includes:

[0033] The main channel is connected at one end to the first fluid inlet on the proximal side and at the other end to the outlet;

[0034] The side channel is connected at one end to the second fluid inlet located on the side, and at the other end to the main channel;

[0035] The chip channel is provided with a distribution structure that can act on at least a portion of the fluid;

[0036] One of the first fluid and the second fluid is a liquid phase fluid, and the other is a gas phase fluid. The drug is loaded in the liquid phase fluid, the particle size of the drug is less than 69 micrometers, the pressure of the liquid phase fluid is 0.2 to 0.76 MPa, and the pressure of the gas phase fluid is 0.2 to 0.6 MPa.

[0037] Optionally, the main lane width W1 is 0.2 to 0.5 mm.

[0038] Optionally, the width of the main channel throat W7 is smaller than the width of the main channel 130 W1, and the width of the main channel throat W7 is preferably 0.05 to 0.15 mm.

[0039] Optionally, the droplet outlet width W8 can deviate from the main channel throat width W7 by 5% to 15%.

[0040] Optionally, the atomized droplet size ranges from 8 to 30 micrometers.

[0041] This application also discloses an inactivated virus spraying system for human natural cavities, including an interventional catheter and an infusion device for delivering a first fluid and a second fluid to the interventional catheter respectively;

[0042] The interventional catheter includes a tube body, one end of which is a proximal end and the other end is a distal end that can extend into the bronchus. The tube body has a channel for delivering fluid from the proximal end to the distal end. The distal end of the tube body is provided with a mixing structure, through which the fluid in the channel is mixed and then output.

[0043] The mixing structure has at least a first fluid inlet, a second fluid inlet, and an outlet, with each fluid inlet having an independently configured flow channel within the pipe body;

[0044] The mixing structure contains a microchannel chip. The first fluid inlet is located near the proximal end of the microchannel chip, and the second fluid inlet is located beside the microchannel chip. The interior of the microchannel chip is a chip channel connecting the outlet and each fluid inlet. The chip channel includes:

[0045] The main channel is connected at one end to the first fluid inlet on the proximal side and at the other end to the outlet;

[0046] The side channel is connected at one end to the second fluid inlet located on the side, and at the other end to the main channel;

[0047] The chip channel is provided with a distribution structure that can act on at least a portion of the fluid;

[0048] One of the first fluid and the second fluid is a liquid phase fluid, and the other is a gas phase fluid. The inactivated virus is loaded in the liquid phase fluid, wherein the particle size of the inactivated virus is less than 21 micrometers, the pressure of the liquid phase fluid is 0.2 to 0.76 MPa, and the pressure of the gas phase fluid is 0.2 to 0.6 MPa.

[0049] Optionally, the droplet outlet width W8 is 0.1 to 0.2 mm.

[0050] Optionally, the atomized droplet size ranges from 5 to 40 micrometers.

[0051] Optionally, the spraying system further includes:

[0052] A sampling device used to collect fluid state parameters;

[0053] The control device, connected to the acquisition device, is used to receive status parameters and control the injection device accordingly.

[0054] Optionally, the spraying system also includes a housing, on which air and liquid connectors are installed, and a pump chamber is provided at the bottom inside the housing;

[0055] The infusion device includes:

[0056] A first infusion device includes a syringe and a drive mechanism. The syringe includes a barrel installed inside the housing and a piston slidably installed inside the barrel. The barrel has an outlet and communicates with the liquid connection connector. The drive mechanism is linked to the piston.

[0057] The second injection device includes an air pump installed in the pump chamber, wherein multiple air pumps are connected in parallel and are connected to the air circuit connector through a main pipe.

[0058] Optionally, the spraying system may also include a cooling assembly thermally coupled to the air pump.

[0059] The specific beneficial effects of this application will be explained in detail below with reference to the specific structure, and will not be repeated here. Attached Figure Description

[0060] Figures 1a to 1c This is a schematic diagram of the structure of an interventional catheter in one embodiment of this application;

[0061] Figures 2 to 4 This is a schematic diagram of the microchannel chip structure in the first embodiment of this application;

[0062] Figure 5 This is a schematic diagram of the microchannel chip structure in the second embodiment of this application;

[0063] Figures 6 to 7 This is a schematic diagram of the microchannel chip structure in the third embodiment of this application;

[0064] Figures 8a to 8b This is a schematic diagram of the microchannel chip structure in the fourth embodiment of this application;

[0065] Figures 9a to 9c This is a schematic diagram of the microchannel chip structure in the fifth embodiment of this application;

[0066] Figures 10a to 10cThis is a schematic diagram of the microchannel chip structure in the sixth embodiment of this application;

[0067] Figures 11 to 14 This is a schematic diagram of the interventional device in one embodiment of this application.

[0068] The annotations in the figure are explained as follows:

[0069] 900, Tube body; 901, Proximal end; 902, Distal end; 9061, Communication interface; 907, First interface; 908, Second interface;

[0070] 920. Microfluidic chip; 921. First unit chip; 922. Second unit chip;

[0071] 940. Sheath; 941. Balloon; 942. Balloon catheter; 943. Balloon control interface; 944. Heating assembly;

[0072] 130. Main flow channel; 140. Side flow channel;

[0073] 220. Expansion section;

[0074] 300. Branch flow channel;

[0075] 400. Distribution component; 460. Fluid acceleration structure; 461. Narrow opening; 462. Sudden expansion section;

[0076] 500. Housing; 501. Gas connection; 502. Liquid connection;

[0077] 510. Pump room; 511. Main pipe; 512. Pressure relief valve; 5122. Pressure relief duct; 5123. Four-way connector; 513. Soundproof partition; 514. Secondary damping device; 5141. First buffer block; 5142. Primary damping platform; 5143. Second buffer block;

[0078] 520. Air pump; 5211. First filter;

[0079] 530. Cooling components; 531. Cooling fan; 532. Heat dissipation window; 533. Heat exchanger; 534. Airflow slit;

[0080] 600. Syringe; 700. Drive mechanism; 800. Control panel; Detailed Implementation

[0081] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, and not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0082] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the scope of the application. The term "and / or" as used herein includes any and all combinations of one or more of the associated listed items.

[0083] In this application, the terms "first," "second," etc., are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number or order of the indicated technical features. Therefore, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this application, "multiple" means at least two, such as two, three, etc., unless otherwise explicitly specified.

[0084] In this application, the terms “comprising” and “having”, and any variations thereof, are intended to cover non-exclusive inclusion, for example, a system, product, or device that includes a series of units is not necessarily limited to those units that are explicitly listed, but may include other units that are not explicitly listed or that are inherent to such products or devices.

[0085] This application discloses a cell spraying system for natural human cavities, including an interventional catheter and an infusion device for delivering a first fluid and a second fluid to the interventional catheter, respectively.

[0086] The interventional catheter includes a tube body, one end of which is the proximal end and the other end is the distal end that can extend into the bronchus. The inside of the tube body has a channel for delivering fluid from the proximal end to the distal end. The distal end of the tube body is provided with a mixing structure, through which the fluid in the channel is mixed and then output.

[0087] The mixed flow structure has at least a first fluid inlet, a second fluid inlet, and an outlet, with each fluid inlet having an independent flow channel within the pipe body;

[0088] A microchannel chip is disposed within the mixed-flow structure. The first fluid inlet is located on the proximal side of the microchannel chip, and the second fluid inlet is located on the side of the microchannel chip. The interior of the microchannel chip consists of chip channels connecting the outlet and each fluid inlet. The chip channels include:

[0089] The main channel is connected to the first fluid inlet on the proximal side at one end and to the outlet at the other end;

[0090] The side channel is connected at one end to the second fluid inlet located on the side, and at the other end to the main flow channel;

[0091] The chip flow channel is provided with a distribution structure that can act on at least a portion of the fluid;

[0092] The cell size is 15-120 micrometers. One of the first fluid and the second fluid is a liquid fluid and the other is a gaseous fluid. The pressure of the liquid fluid is 0.2-0.76 MPa and the pressure of the gaseous fluid is 0.1-0.4 MPa.

[0093] In the optimal selection of parameters, the cells include one or more of the following: lung stem cells, hematopoietic stem cells, mesenchymal stem cells, neural stem cells, exosomes, and lung progenitor cells. The cell content in the liquid phase fluid is 1*102 6 ~8*10 6 Cells / mL. Liquid phase fluid volume is 10-40 mL, and liquid phase fluid flow rate is less than or equal to 4 mL / min. Cell size is 15-30 μm, and droplet size is 15-40 μm. Gas phase fluid pressure is 0.1-0.35 MPa, and the gas phase fluid medium is one of the following combinations: air, air and hydrogen, or oxygen.

[0094] In terms of parameter optimization, the concentration of the treatment medium in the liquid phase fluid is 2*10. 6 per ml.

[0095] Hematopoietic stem cells are used to treat blood diseases; mesenchymal stem cells are used to treat cardiovascular diseases, cirrhosis, and nervous system diseases; neural stem cells are used to replenish damaged nerve cells; lung progenitor cells are used to treat chronic obstructive pulmonary disease; exosomes, including small molecule bioactive peptides and proteins, can participate in immune responses, antigen presentation, cell migration, cell differentiation, and tumor invasion. For the corresponding microfluidic chip setup, the preferred parameters are: etching depth H3 of 0.08 to 0.12 mm; droplet outlet width W8 of 0.1 to 0.2 mm; main channel width W1 of 0.2 to 0.4 mm; and droplet size ranging from 20 to 50 micrometers.

[0096] This application also discloses an inactivated virus spraying system for human natural cavities, including an interventional catheter and an infusion device for delivering a first fluid and a second fluid to the interventional catheter respectively.

[0097] The interventional catheter includes a tube body, one end of which is the proximal end and the other end is the distal end that can extend into the bronchus. The inside of the tube body has a channel for delivering fluid from the proximal end to the distal end. The distal end of the tube body is provided with a mixing structure, through which the fluid in the channel is mixed and then output.

[0098] The mixed flow structure has at least a first fluid inlet, a second fluid inlet, and an outlet, with each fluid inlet having an independent flow channel within the pipe body;

[0099] A microchannel chip is disposed within the mixed-flow structure. The first fluid inlet is located on the proximal side of the microchannel chip, and the second fluid inlet is located on the side of the microchannel chip. The interior of the microchannel chip consists of chip channels connecting the outlet and each fluid inlet. The chip channels include:

[0100] The main channel is connected to the first fluid inlet on the proximal side at one end and to the outlet at the other end;

[0101] The side channel is connected at one end to the second fluid inlet located on the side, and at the other end to the main flow channel;

[0102] The chip flow channel is provided with a distribution structure that can act on at least a portion of the fluid;

[0103] One of the first fluid and the second fluid is a liquid phase fluid, and the other is a gas phase fluid. The inactivated virus is loaded in the liquid phase fluid, wherein the particle size of the inactivated virus is less than 21 micrometers, the pressure of the liquid phase fluid is 0.2 to 0.76 MPa, and the pressure of the gas phase fluid is 0.2 to 0.6 MPa.

[0104] For optimal parameter selection, the liquid phase fluid volume is 5-10 ml, and the liquid phase fluid flow rate is less than or equal to 4 ml / min. The virus particle size is 50-350 nm, and the droplet particle size is 20-300 μm. Inactivated viruses include inactivated polio vaccine, inactivated Japanese encephalitis vaccine, influenza vaccine, rabies vaccine, inactivated hepatitis A vaccine, EV71 hand-foot-mouth disease vaccine, and inactivated novel coronavirus vaccine. For chip selection, the droplet outlet width W8 is 0.1 to 0.2 mm. The atomized droplet particle size ranges from 5-40 μm.

[0105] This application also discloses a drug spraying system for natural human cavities, including an interventional catheter and an infusion device for delivering a first fluid and a second fluid to the interventional catheter respectively.

[0106] The interventional catheter includes a tube body, one end of which is the proximal end and the other end is the distal end that can extend into the bronchus. The inside of the tube body has a channel for delivering fluid from the proximal end to the distal end. The distal end of the tube body is provided with a mixing structure, through which the fluid in the channel is mixed and then output.

[0107] The mixed flow structure has at least a first fluid inlet, a second fluid inlet, and an outlet, with each fluid inlet having an independent flow channel within the pipe body;

[0108] A microchannel chip is disposed within the mixed-flow structure. The first fluid inlet is located on the proximal side of the microchannel chip, and the second fluid inlet is located on the side of the microchannel chip. The interior of the microchannel chip consists of chip channels connecting the outlet and each fluid inlet. The chip channels include:

[0109] The main channel is connected to the first fluid inlet on the proximal side at one end and to the outlet at the other end;

[0110] The side channel is connected at one end to the second fluid inlet located on the side, and at the other end to the main flow channel;

[0111] The chip flow channel is provided with a distribution structure that can act on at least a portion of the fluid;

[0112] One of the first fluid and the second fluid is a liquid phase fluid, and the other is a gas phase fluid. The drug is loaded in the liquid phase fluid, and the particle size of the drug is less than 69 micrometers. The pressure of the liquid phase fluid is 0.2 to 0.76 MPa, and the pressure of the gas phase fluid is 0.2 to 0.6 MPa.

[0113] For optimal parameter selection, the liquid phase fluid volume is 5-10 ml, and the liquid phase fluid flow rate is less than or equal to 4 ml / min. The nanomedicine particle size is 50-350 nm, and the droplet size is 20-300 μm. Regarding chip parameter selection, the main channel width W1 is 0.2-0.5 mm. The main channel throat width W7 is smaller than the main channel width W1, and is preferably 0.05-0.15 mm. The droplet outlet width W8 deviates from the main channel throat width W7 by 5%-15%. The atomized droplet size ranges from 8-30 μm.

[0114] The drugs include ribavirin, acyclovir, ganciclovir, oseltamivir, vidarabine, amantadine, voriconazole, amphotericin B, radionuclide, dexamethasone, sildenafil citrate, isoniazid, and N-acetylcysteine. Among them, ribavirin is used to treat respiratory syncytial virus, influenza virus, hepatitis A virus, and adenovirus; acyclovir is used to treat herpesvirus and varicella virus; ganciclovir is used to treat cytomegalovirus; oseltamivir is used to treat influenza A and B; vidarabine is used to treat chronic hepatitis B, herpesvirus, and varicella virus; amantadine is used to treat influenza virus; dexamethasone is used to treat pneumonia, asthma, chronic obstructive pulmonary disease, membranous laryngitis, and cerebral edema; sildenafil citrate is used to treat erectile dysfunction; voriconazole is used to treat aspergillosis, Candida, Actinobacter spp., and Fusarium spp.; amphotericin B is used to treat visceral or systemic infections caused by Cryptococcus, Coccidioides, Histoplasma capsulatum, Blastomyces, Sporothrix, Candida, Mucor, Aspergillus, etc.; isoniazid is used to treat Mycobacterium tuberculosis; and N-acetylcysteine ​​is used to treat expectorants.

[0115] In this embodiment, ribavirin, acyclovir, ganciclovir, oseltamivir, vidarabine, and amantadine are used to treat viral infections, while voriconazole, amphotericin B, isoniazid, and N-acetylcysteine ​​are used to treat fungal infections.

[0116] Please refer to the table for details:

[0117]

[0118] The operation of the aforementioned system relies on a fluid containing therapeutic substances being delivered through an infusion device into the interventional catheter and then applied to the lesion site within the body. The infusion device primarily provides fluid dynamics, achieving a specific flow rate that can be adjusted as needed, for example, using a controllable fluid delivery pump. Existing technologies can be employed for the pump's structure and control methods. The infusion device is configured according to the fluid state and type, with control devices installed at controllable locations. The fluid carrying the therapeutic substance can be pre-prepared or mixed in real-time with the fluid's movement. The therapeutic substance itself depends on the treatment objective and the lesion condition; for example, the therapeutic substance may be a fluid, loaded with a gaseous fluid, or loaded with a liquid fluid. The interventional catheter can also deliver multiphase fluids, such as fluids comprising both gaseous and liquid phases. Preferably, the two phases are separately introduced into the interventional catheter and then mixed and atomized at a mixing structure.

[0119] Regarding the setup of the interventional catheter, referring to the attached diagram, the interventional catheter includes a tube body 900, one end of which is a proximal end 901 and the other end is a distal end 902 that can extend into the bronchus. The tube body 900 has a channel inside that can deliver fluid from the proximal end 901 to the distal end 902. The distal end 902 of the tube body 900 is provided with a mixing structure, and the fluid in the channel is output after being mixed by the mixing structure.

[0120] The mixed flow structure has at least a first fluid inlet, a second fluid inlet, and an outlet, with each fluid inlet having an independently configured flow channel within the pipe body 900;

[0121] A microfluidic chip 920 is disposed within the mixing structure. A first fluid inlet is located on the proximal end 901 side of the microfluidic chip 920, and a second fluid inlet is located beside the microfluidic chip 920. The interior of the microfluidic chip 920 is a chip flow channel connecting the outlet and each fluid inlet. The chip flow channel includes:

[0122] Main channel 130, one end is connected to the first fluid inlet located on the proximal side 901, and the other end is connected to the outlet;

[0123] Side flow channel 140, one end of which is connected to the second fluid inlet located on the side, and the other end of which is connected to the main flow channel 130;

[0124] The chip flow channel is provided with a distribution structure that can act on at least a portion of the fluid.

[0125] Similarly, the microchannel chip 920 independently possesses the following characteristics: the distribution structure is located at the intersection of the main channel 130 and the side channel; the side channel 140 has a narrowing section in its width; the side channel 140 has an extending trend line, and the width of the side channel 140 gradually narrows along the direction of the extending trend line; the width of the side channel 140 continuously decreases from upstream to downstream; the intersection of the side channel 140 and the main channel 130 is a junction, and at least one junction is oriented perpendicular to the extending direction of the main channel 130. The main channel or side channel has a throat section, and the size of this section is smaller than that of the sides, through which at least one fluid moves to the droplet outlet.

[0126] Reference Appendix Figure 1a To be continued Figure 1c As shown, this application also provides another interventional catheter, comprising:

[0127] The tube body 900 has a proximal end 901 at one end and a distal end 902 at the other end that can extend into the bronchus.

[0128] The microchannel chip 920 has a chip flow channel inside, which includes a main flow channel 130 and a side flow channel 140. The main flow channel 130 and / or the side flow channel 140 are provided with a fluid acceleration structure 460 and a sudden expansion section 462 arranged in sequence according to the fluid flow direction. The fluids in the main flow channel 130 and the side flow channel 140 interact in the sudden expansion section 462 and output atomized fluid.

[0129] Heating component 944, located inside tube 900 and at the distal end 902 of microchannel chip 920, is used to regulate the temperature of atomized fluid;

[0130] The balloon 941 is deformably configured on the outside of the tube 900.

[0131] The balloon 941 can control its own shape, such as inflating or contracting, under the guidance of the balloon catheter 942, the balloon control interface 943, and the corresponding fluid delivery, thereby achieving occlusion, positioning, and corresponding operations at preset locations. This improves the stability and adaptability of interventional catheter operations.

[0132] In terms of setup details, along the axial direction of the tube body 900, the balloon 941 and the heating component 944 are positioned correspondingly. The distal end 902 of the microfluidic chip 920 has an outlet for atomized fluid output. The heating component 944 is a heating tube, the interior of which is a temperature control channel connected to the outlet. The heating temperature of the heating component 944 is preferably 43-60℃, at which point lesions (cancer cells) can be killed, while normal cells can recover. The interventional catheter also includes a first interface 907 and a second interface 908, which can be connected to an external perfusion device for delivering fluid to each inner tube. The interventional catheter also includes a communication interface 9061, through which signal and energy transmission can be achieved.

[0133] See appendix Figure 2 To be continued Figure 4As shown in the attached figure, a microchannel chip 920 is disclosed, wherein the chip's aspect ratio ranges from 2.5 to 5, preferably from 3 to 4, and the aspect ratio shown in the figure is 2.5:0.9. The width W1 of the main channel 130 is preferably 0.2 to 0.5 mm, and in actual products, it is preferably 0.25 to 0.45 mm. In the attached figure, the width of W1 is 0.3 mm. The width W7 of the main channel throat is smaller than the width W1 of the main channel 130. The width W7 of the main channel throat is preferably 0.05 to 0.15 mm, and in actual products, it is preferably 0.08 to 0.12 mm. In the attached figure, the width of W7 is 0.1 mm. The droplet outlet width W8 can be the same as the width W7 of the main channel throat, or it can be set differently, for example, the droplet outlet width W8 can deviate from the width W7 of the main channel throat by 5% to 15%. The width W2 of the side channel 140 is preferably 0.1 to 0.3 mm, and in actual products, it is preferably 0.15 to 0.25 mm. In the attached drawing, the width W2 is 0.2 mm. The distance W3 between the side channel 140 and the proximal side of the microchannel chip 920 is preferably 0.5 to 1.8 mm, and in actual products, it is preferably 0.8 to 1.5 mm. In the attached drawing, the distance W3 is 1.3 mm. The width W4 of the branch channel is preferably 0.01 to 0.05 mm, and in actual products, it is preferably 0.015 to 0.03 mm. In the attached drawing, the width W4 is 0.02 mm. The setting range of the branch channel width W5 can be the same as that of the branch channel width W4, or it can be set differently. For example, the branch channel width W5 can deviate from the branch channel width W4 by 5% to 15%. The sub-channel width W6 is smaller than the branch channel width W5. The sub-channel width W6 is preferably 0.005 to 0.015 mm, and in actual products, it is preferably 0.008 to 0.012 mm. In the attached drawing, the width of W6 is 0.01 mm. Regarding thickness, the thickness H1 of the etched channel unit is preferably 0.2 to 0.5 mm, and in actual products, it is preferably 0.25 to 0.35 mm. In the attached drawing, H1 is 0.3 mm. In the attached drawing, the etching depth H3 is 0.05 mm. The overall thickness H2 of the microchannel chip 920 is preferably 0.4 to 1.0 mm, and in actual products, it is preferably 0.55 to 0.85 mm. In the attached drawing, H2 is 0.6 ± 0.02 mm. In this embodiment, the microchannel chip 920 is designed based on a dual atomization principle, with the side channel 140 and the main channel 130 intersecting at least twice. A portion of the main channel 130 is a widened expansion section, and the side channel 140 intersects the main channel 130 at least once on the expansion section. Furthermore, the side channel 140 intersects the main channel 130 at least once after the expansion section. In the accompanying drawings, the side channel 140 includes a branch channel, and intersects the main channel twice independently in the expansion section via the branch channel. Two side channels 140 are provided, located on either side of the main channel 130, and each side channel 140 intersects the main channel 130 independently.The atomized droplet size ranges from 10 to 30 μm, and the liquid phase channel size is all above 100 μm. The microfluidic chip in this embodiment allows drug solutions containing particles to pass through, and therefore can be used in the drug spraying system for the natural cavities of the human body mentioned above.

[0134] See appendix Figure 5 As shown in the attached figure, a microchannel chip 920 is disclosed, with an overall size range similar to that of the attached figure. Figure 2 To be continued Figure 4 In the embodiment described above, a portion of the main channel 130 is a widened expansion section 220, and at least a portion of the side channel 140 converges to the expansion section 220. Therefore, the distributor 400 is located within the expansion section 220 and has at least a first distribution surface and a second distribution surface facing the direction of fluid movement within the main channel 130. The distributor can be a protrusion formed by the residue after etching the first unit piece 921 or the second unit piece 922. A fluid acceleration structure 460 is provided on the side channel 140, and the fluid acceleration structure 460 is located upstream of at least one intersection of the main channel 130 and the side channel 140. The fluid acceleration structure 460 is actually a Laval nozzle with a gradually converging and expanding configuration, which can effectively increase the fluid velocity within the side channel 140. In this embodiment, the fluid within the side channel 140 is gas. Compared to the previous embodiment, this embodiment is designed based on the dual atomization principle and the fluid acceleration structure. After passing through the fluid acceleration structure 460, the gas is accelerated, which is beneficial for gas-liquid mixing. This results in smaller atomized particle size; therefore, in this embodiment, the droplet size distribution after atomization is in the range of 8~25μm.

[0135] See appendix Figure 6 To be continued Figure 7 As shown in the attached figure, a microchannel chip 920 is disclosed, with an overall size range similar to that of the attached figure. Figure 2 To be continued Figure 4The embodiments described are similar, wherein the etching depth H3 is 0.08 to 0.12 mm, the droplet outlet width W8 is 0.1 to 0.2 mm, and the main channel width W1 is 0.2 to 0.4 mm. In the accompanying drawings, the etching depth H3 is preferably 0.1 mm, the droplet outlet width W8 is preferably 0.15 mm, and the main channel width W1 is preferably 0.32 mm. This embodiment is designed based on the dual atomization principle. Similarly, the microfluidic chip in this embodiment allows the passage of drug solutions containing particles, and therefore can be used in the drug spraying system for the human body's natural cavities mentioned above. Simultaneously, the liquid phase channel size is larger than in other embodiments, which can effectively reduce the atomization pressure of the liquid phase, thereby meeting specific operating conditions. For example, when the therapeutic substance is cells, the lower atomization pressure and larger channel size can effectively reduce cell damage. The droplet size distribution after atomization in this embodiment is in the range of 20~50 μm, therefore the microfluidic chip in this embodiment can be used in the cell spraying system for the human body's natural cavities mentioned above.

[0136] See appendix Figure 8a To be continued Figure 8b As shown in the attached figure, a microchannel chip 920 is disclosed, with an overall size range similar to that of the attached figure. Figure 2 To be continued Figure 4 In the embodiment shown, the main channel throat width W7 is 0.1 to 0.2 mm. The droplet outlet width W8 is 0.15 to 0.3 mm. The etching depth H3 is 0.1 to 0.25 mm. The thickness H1 of the etched flow channel unit is 0.25 to 0.55 mm. In the accompanying drawings, the main channel throat width W7 is preferably 0.14 mm, the droplet outlet width W8 is preferably 0.24 mm, the etching depth H3 is preferably 0.2 mm, and the thickness H1 of the etched flow channel unit is preferably 0.4 mm. It is easy to see that this embodiment increases the flow channel size compared to other embodiments. Furthermore, a fluid acceleration structure 460 is provided on the side flow channel 140, located upstream of at least one intersection of the main channel 130 and the side flow channel 140. The fluid acceleration structure 460 is actually a Laval nozzle with a tapered and expanding configuration, which can effectively increase the fluid velocity within the side flow channel 140. In this embodiment, the fluid within the side flow channel 140 is gas. Meanwhile, a portion of the main channel 130 is a widened expansion section, and at least a portion of the side channels 140 converges into the expansion section. Therefore, the distributor 400 is located within the expansion section and has at least a first distribution surface and a second distribution surface facing the direction of fluid movement within the main channel 130. This embodiment is designed based on the dual atomization principle and fluid acceleration structure, which greatly increases the channel size, enabling it to atomize liquids with high viscosity, such as hydrogels. The droplet size distribution after atomization in this embodiment is in the range of 20~60μm. Therefore, the microchannel chip in this embodiment can be used in the high-viscosity fluid spraying system of the human body's natural cavities mentioned above.

[0137] See appendix Figure 9a To be continued Figure 9c As shown in the attached figure, a microchannel chip 920 is disclosed, with an overall size range similar to that of the attached figure. Figure 2 To be continued Figure 4 In the embodiments described above, the droplet outlet width W8 is preferably 0.15 mm, and the overall thickness H2 of the microchannel chip 920 is preferably 0.6 ± 0.02 mm. Compared to other embodiments, in this embodiment, the main channel 130 carries gas and is provided with a fluid acceleration structure 460. The fluid acceleration structure 460 is located upstream of at least one intersection of the main channel 130 and the side channel 140, and at least one narrow opening 461 is provided at this intersection. The main channel 130 or the side channel 140 intersects with the other through this narrow opening 461. The side channel 140 carries liquid and is provided with a distribution structure near one end of the main channel 130. The distribution structure consists of an array of distribution members 400, and the cross-sectional size of each distribution member 400 gradually increases in the fluid flow direction. The main channel 130 is provided with a sudden expansion section 462 downstream of the fluid acceleration structure 460. Figure 9c To better illustrate the expansion section 462, the extension trend of the fluid acceleration structure 460 is extended by dashed lines in the attached diagram. Compared to the extension trend of the fluid acceleration structure 460, it is clearly observable that the cavity diameter of the expansion section 462 is larger, indicating a larger internal volume. (The attached diagram is not included in the provided text.) Figure 9c The designations regarding the abrupt expansion section 462 and the fluid acceleration structure 460 are intended to better indicate the boundary between their approximate positions and do not limit their axial length, especially at their mutually distant ends. For example, as shown in the attached... Figure 9a In the embodiment shown, the axial lengths of the sudden expansion section 462 and the fluid acceleration structure 460 are relative to the attached... Figure 9cThe diagram shows a longer section, where the distal end of the expansion segment 462 extends to the distal end of the chip and forms a droplet outlet. Proportionally, the internal volume of the expansion segment 462 is at least 15% larger than the internal volume of the fluid acceleration structure. A junction with a narrow opening 461 is located in the expansion segment 462; in the accompanying drawings, the junction is located on the proximal end of the expansion segment 462. That is, the expansion segment 462 is positioned abutting against the fluid acceleration structure 460, and the cavity diameter of the expansion segment 462 is at least 10% larger than the cavity diameter at the outlet of the fluid acceleration structure 460. In the embodiments of this application, the design is based on the principle of differential pressure atomization. The gas is accelerated through the fluid acceleration structure and interacts with the liquid phase in the expansion segment 462. The sudden expansion of the channel space in the expansion segment 462 and the high-speed airflow work together to form a pressure difference. Through differential pressure atomization, the size of the small droplets is more concentrated, effectively improving the concentration of the droplet size distribution range after atomization. In this embodiment, the atomized droplet size distribution is in the range of 20~60μm, with at least 70% distributed in the range of 20~40μm. The microfluidic chip in this embodiment can be used in the cell spraying system for the natural cavities of the human body mentioned above. In this embodiment, the cells are preferably exosomes.

[0138] Based on the above, this embodiment discloses an interventional catheter, including a tube body 900, one end of which is a proximal end 901, and the other end is a distal end 902 that can extend into the bronchus. The tube body 900 contains a microfluidic chip 920, which has the following characteristics:

[0139] The first fluid inlet is located on the proximal side 901 of the microchannel chip 920;

[0140] There are two second fluid inlets, which are located on the two opposite sides of the microchannel chip 920.

[0141] The outlet is located at the distal end 902 of the microfluidic chip 920;

[0142] The interior of the microfluidic chip 920 consists of chip channels connecting the outlet and various fluid inlets. These chip channels include:

[0143] Main channel 130, one end connects to the first fluid inlet, and the other end connects to the outlet;

[0144] The side flow channel 140 is connected to the second fluid inlet at one end and to the main flow channel 130 at the other end. Multiple distribution components 400 are arranged at intervals inside the side flow channel 140.

[0145] In terms of configuration details, the tube body 900 includes a sheath 940, which provides protection and necessary mechanical support for each inner tube. Two side channels 140 are symmetrically distributed on both sides of the main channel 130, each connecting to the middle and lower reaches of the main channel 130. The side channels 140 have a bend at the second fluid inlet pointing towards the distal end 902, and at the end of the bend, facing the main channel 130, they connect to the main channel via a confluence section. Distribution members 400 are arranged sequentially along the length of the main channel 130 in the connecting section. The main channel 130 is provided with a fluid acceleration structure 460 and a sudden expansion section 462 arranged sequentially according to the fluid flow direction, wherein the confluence section connects to the sudden expansion section 462, and the connecting part is adjacent to the acceleration structure section. The confluence section includes multiple narrowing sections, with the distribution member 400 located between adjacent stages. The narrowing section includes three stages, with the distribution member 400 located between the first two stages. The confluence section extends along the width of the main channel 130. Each narrowing section has two opposing sidewalls, at least one of which is inclined relative to the extension direction, causing the narrowing section to gradually constrict. Of the two sidewalls, one is parallel to the extension direction, and the other is inclined. In the two downstream stages, the inclined sidewalls are located on opposite sides of the flow channel. Before and after each narrowing stage, the flow channel width changes by 20-60%. The distributors 400 are toothed in shape, and their cross-sectional dimensions gradually increase in the fluid flow direction. Downstream of the distributors 400, each distributor 400 occupies 30-70% of the width of its respective flow channel.

[0146] See appendix Figure 10a To be continued Figure 10b As shown in the attached figure, a microchannel chip 920 is disclosed, with an overall size range similar to that of the attached figure. Figure 9a To be continued Figure 9cIn the embodiment described above, the droplet outlet width W8 is preferably 0.12 mm. Compared to the previous embodiment, in this embodiment, the side channel 140 transports gas and has independent branch channels 300. In the accompanying drawings, there are two side channels 140, each located on either side of the main channel 130. Each side channel 140 has an independent branch channel 300, which includes multiple sub-channels arranged in an array. The multiple sub-channels of the two branch channels 300 are arranged opposite each other and connected to the main channel 130. The multiple sub-channels of the two branch channels 300 are staggered at intervals. This arrangement allows the fluid in the side channel to disturb the fluid in the main channel, improving premixing and pre-dispersion, and effectively controlling the atomized droplet size and its distribution range. The staggered arrangement of the sub-channels also prevents the oppositely arranged sub-channels from blocking the main channel. At the outlet position, the fluid acceleration structure and the sudden expansion section are grouped and respectively disposed in the corresponding side channel 140, wherein the two sudden expansion sections converge within the main channel 130. In this embodiment, the side channel 140 is provided with a fluid acceleration structure 460, which is located upstream of at least one intersection of the main channel 130 and the side channel 140. Optionally, the main channel 130 is provided with a distributor 400, which forms at least two narrow openings 461 with the sidewall of the main channel 130, each corresponding to one of the two sudden expansion sections 462. The main channel 130 or the side channel 140 converges with the other through two narrow openings 461. The side channel 140 has a sudden expansion section 462 downstream of the fluid acceleration structure 460. (See attached...) Figure 10c In the figure, it can be clearly observed that the cavity diameter of the expansion section 462 is larger, resulting in a larger internal volume. Proportionally, the internal volume of the expansion section 462 is at least 15% larger than that of the fluid acceleration structure. A junction with a narrow opening 461 is located in the expansion section 462, which, in the attached figure, is located near the proximal end of the expansion section 462. That is, the expansion section 462 is positioned close to the fluid acceleration structure 460, and its cavity diameter is at least 10% larger than the cavity diameter at the outlet of the fluid acceleration structure 460. This embodiment is designed based on the pressure differential atomization principle. Compared to the previous embodiment, the gas phase is transferred to the side channels on both sides, and the main atomization structure is concentrated at the outlet. The two pressure differential atomized droplets collide at the outlet, forming finer droplets while maintaining a relatively high droplet size distribution concentration. In this embodiment, the atomized droplet size distribution is in the range of 5~40μm, with at least 70% distributed in the range of 5~15μm. The microfluidic chip in this embodiment can be used in the cell spraying system for the human body's natural cavities and the inactivated virus spraying system for the human body's natural cavities mentioned above.

[0147] Based on the above-described implementation, this application discloses an interventional catheter, including a tube body 900, one end of which is a proximal end 901, and the other end is a distal end 902 that can extend into the bronchus. The tube body 900 contains a microfluidic chip 920, which has the following characteristics:

[0148] The first fluid inlet is located on the proximal side 901 of the microchannel chip 920;

[0149] The second fluid inlet is located beside the microchannel chip 920;

[0150] The outlet is located at the distal end 902 of the microfluidic chip 920;

[0151] The interior of the microfluidic chip 920 consists of chip channels connecting the outlet and various fluid inlets. These chip channels include:

[0152] Main channel 130, one end connects to the first fluid inlet, and the other end connects to the outlet;

[0153] The side channel 140 is connected to the second fluid inlet at one end and to the main channel 130 at the other end; the side channel 140 has a branch channel 300 and intersects with the main channel 130 via the branch channel 300.

[0154] In terms of design details, the side channel 140 includes:

[0155] The main channel extends from the second fluid inlet to the distal end 902 until it merges with the main channel 130;

[0156] The branch channel 300 connects to the main channel at one end, with the connection point adjacent to the second fluid inlet. The other end extends proximal to 901 and branches into multiple sub-channels, the ends of which converge at the upper-middle section of the main channel 130. The main channel has a bend at the second fluid inlet and extends distally to 902 via the bend. One end of the branch channel 300 connects to the proximal side of the bend at 901. The branch channel 300 has a comb-like structure overall, with the ends of each sub-channel perpendicularly connected to the main channel 130. Two side channels 140 are located on either side of the main channel 130, with the ends of the sub-channels in the two side channels 140 staggered. Two side channels 140 are distributed on both sides of the main channel 130. The main channels of each side channel 140 intersect with the main channel 130, defining a first intersection and a second intersection. The two side channels 140 extend independently from the first and second intersections towards the outlet and converge near the outlet. In the main channel 130, a distribution member 400 is provided near the outlet. Along the width direction of the main channel 130, the distribution member 400 closes the middle of the main channel 130 and forms narrow openings 461 on both sides between itself and the sidewall of the main channel 130. The first and second intersections are located at the corresponding narrow openings 461. The side channels 140 are provided with a fluid acceleration structure 460 and a sudden expansion section 462 arranged sequentially according to the fluid flow direction. The narrow openings 461 connect to the sudden expansion section 462, and the connection point is adjacent to the acceleration structure section. The distribution member 400 has a triangular cross-sectional shape. The main flow channel 130 extends in a straight line with a constant cross-section from the first fluid inlet to the distributor 400. The two side flow channels 140 extend towards the outlet from the first and second confluences at an obtuse angle. The outlet has a widening tendency, and the widening angle corresponds to the angle between the trend lines.

[0157] Similarly, this application can also be understood as disclosing an atomization method based on a microfluidic chip 920, including:

[0158] Liquid fluid is received via the microfluidic chip 920;

[0159] The microfluidic chip 920 receives the gaseous fluid, which is then split into two streams and independently guided to merge with the liquid fluid, forming two atomized streams.

[0160] The two atomized streams are guided to converge inside the microchannel chip 920 before being output.

[0161] In detail, each gaseous fluid stream is pre-diverted at least a portion and merges with the liquid fluid upstream, causing turbulence; the remaining portion merges with the liquid fluid downstream and is atomized. The angle between the flow trend lines of the two atomized streams before they merge is an obtuse angle.

[0162] Each of the above embodiments has its own characteristics, while also sharing certain commonalities. Based on the above description, the following features can be summarized. Regarding the arrangement of the distribution structure, the distribution structure is at least one of the following: Method a: multiple branch channels 300 connected to the side channel 140, the side channel 140 intersecting with the main channel 130 via these multiple branch channels 300; Method b: multiple spaced or individually arranged distribution members 400 located within the main channel 130 and / or the side channel 140.

[0163] Regarding the fluid acceleration structure 460 and the sudden expansion section 462, the sudden expansion section 462 is formed by the expansion of the flow channel it resides in. In terms of transition, the sudden expansion section 462 and the outlet of the fluid acceleration structure 460 have a smooth transition or a stepped transition. It is worth noting that the emphasis here is on a smooth or non-smooth transition based on fluid dynamics design principles, in order to enhance or adjust the influence of the sudden expansion section 460 on fluid motion. For example, burrs, straight edges, steps, etc., formed by process limitations in common industrial products cannot be directly understood as a stepped transition here; similarly, conventionally chosen rounded corners cannot be directly understood as a smooth transition. The focus here is on deliberately manufacturing this shape. In the fluid direction corresponding to the flow channel, the expansion trend of the sudden expansion section 462 relative to the fluid acceleration structure 460 is also designed. Based on the overall size of the expansion section 462, when the size of the expansion section 462 is significantly larger than the opening size of the main channel, its expansion tendency will decrease at the distal end to achieve structural compatibility. When the size of the expansion section 462 is significantly smaller than the size of the droplet outlet, the expansion section 462 can choose to maintain its expansion tendency or further increase it. Besides size, the position of the expansion section 462 on the chip also matters. When the expansion section 462 is close to the droplet outlet, its axial expansion distance is limited. As the axial and radial expansion tendencies of the expansion section 462 change, its morphology will change. For example, in an embodiment with a main channel 130 expansion section and a fluid acceleration structure 460, where the main channel 130 expansion section is positioned close to the outlet of the fluid acceleration structure 460, the expansion section can also achieve a certain working effect similar to the expansion section 462.

[0164] In conjunction with the above embodiments, this application provides an atomized drug delivery system, comprising:

[0165] An infusion device for supplying a fluid containing a therapeutic substance, the fluid including a liquid phase fluid and a gas phase fluid, at least one of the two phase fluids containing the therapeutic substance;

[0166] The interventional catheter, using the interventional catheter in the above technical solution, has its proximal end connected to the perfusion device for receiving gaseous fluid and liquid fluid respectively;

[0167] A sampling device used to collect fluid state parameters;

[0168] The control device, connected to the acquisition device, is used to receive status parameters and control the injection device accordingly.

[0169] In conjunction with the device described below, this application can also be understood as disclosing a gas-liquid two-phase interventional device, wherein the interventional device includes:

[0170] The housing has gas and liquid connectors installed on it. A pump chamber is located at the bottom inside the housing. The operation panel 800 is located on the outside of the housing 500 and is used to input control information and output parameter status.

[0171] The air pump is installed in the pump room. Multiple air pumps are connected in parallel and connected to the air circuit connector through a main pipe.

[0172] Cooling components, thermally coupled to the air pump;

[0173] A syringe, comprising a barrel mounted within a housing and a piston slidably mounted within the barrel, the barrel having an outlet and communicating with a fluid connection.

[0174] The drive mechanism is linked to the piston of the syringe;

[0175] The interventional catheter, using the interventional catheter in the above technical solution, has its proximal end connected to the gas circuit connector and the liquid circuit connector, respectively, for receiving gaseous fluid and liquid fluid.

[0176] For specific equipment settings, please refer to the appendix. Figure 11 To be continued Figure 14 In the illustrated embodiments, this application also discloses an interventional device, wherein the interventional device includes:

[0177] The housing 500 is equipped with a gas connection 501 and a liquid connection 502. A pump chamber 510 is located at the bottom inside the housing 500.

[0178] Air pump 520 is installed in pump room 510. Multiple air pumps 520 are connected in parallel and connected to air line connector 501 through main pipe 511.

[0179] Cooling assembly 530 is thermally coupled to air pump 520;

[0180] The syringe 600 includes a barrel installed within a housing 500 and a piston slidably mounted within the barrel. The barrel has an outlet and communicates with a fluid connector 502.

[0181] The drive mechanism 700 is linked to the piston of the syringe 600.

[0182] The gas-liquid two-phase interventional device in this application can be divided into a gas path section and a liquid path section, which enter the interventional catheter through the gas path connector 501 and the liquid path connector 502, respectively.

[0183] Reference for the structure of the gas path section Figure 13 To be continued Figure 14 Publicly available interventional devices include:

[0184] The housing 500 has an air connector 501 installed on it, and a pump chamber 510 is provided at the bottom inside the housing 500.

[0185] Air pump 520 is installed in pump room 510. Multiple air pumps 520 are connected in parallel and connected to air line connector 501 through main pipe 511.

[0186] Pressure relief valve 512 is installed on main pipe 511, and the outlet of pressure relief valve 512 is connected to pump room 510 through pipeline;

[0187] Cooling fan 531 is thermally coupled to air pump 520.

[0188] In this embodiment, an air pump 520 is used to provide the air source, thereby realizing the function of the air circuit. In actual use, the inventors found that medical pneumatic equipment needs to meet the requirement of being oil-free, which leads to dry friction of the pump body inside the air pump 520, resulting in relatively serious heat generation and affecting its lifespan. At the same time, in order to reduce noise, a shield is generally used, but this setting will lead to the inability to form an effective air duct or the air outlet being too small, causing temperature rise. In addition, under certain special high pressure requirements of consumable instruments, the air pump 520 has excessive temperature rise and excessive load; the combination of these two factors leads to excessive heat generation after long-term operation, affecting the output air pressure of the air pump 520 or significantly affecting the lifespan of the instrument. In order to overcome the above problems, this application has optimized heat dissipation. Referring to the embodiment shown in the accompanying drawings, the cooling fan 531 is located outside the pump chamber 510, and the side wall of the pump chamber 510 has a heat dissipation window 532 through which the cooling airflow of the cooling fan 531 passes. Inside the pump chamber 510, there is a heat exchange component 533 thermally coupled to the air pump 520, and at least a part of the heat exchange component 533 is aligned with the heat dissipation window 532. In the accompanying drawings, heat exchangers 533 are arranged in groups, with at least two heat exchangers 533 in each group, and an airflow slit 534 is provided between them. The airflow slit 534 is aligned with the heat dissipation window 532 and the cooling fan 531. Optionally, each heat exchanger 533 in a group can correspond to a different air pump 520 or a different pump head of a single air pump 520. In the accompanying drawings, the air pump 520 is configured with dual pump heads, and the two heat exchangers 533 correspond to different pump heads, which can improve heat exchange efficiency. The heat exchangers 533 can be made of a material with high thermal conductivity, or the heat exchange efficiency can be improved by increasing the surface area. Alternatively, referring to the embodiment shown in the accompanying drawings, the heat exchanger 533 is a thermoelectric cooler with its cold end thermally coupled to the pump head of the air pump 520, and its hot end exposed to the heat dissipation window 532. The cold end is attached to the heat sink of the air pump 520 body, and the hot end can be cooled by a heat sink or directly by air, and the heat on the thermoelectric cooler is carried away by blowing / suction. Closed-loop control can also be achieved by setting a temperature sensor. For example, a temperature sensor can be installed on the air pump 520. When the temperature is too high, the operating power of the thermoelectric cooler increases, i.e., the current of the thermoelectric cooler increases; conversely, the current decreases when the temperature is low. This forms a closed loop, controlling the temperature of the air pump 520 within an efficient operating temperature range. If the temperature cannot be lowered and exceeds a preset value, an alarm is triggered or an instruction is given to the system to stop the pump.

[0189] The airflow direction of the cooling fan 531 needs to be adjusted according to the material of the heat exchanger 533.

[0190] For example, when the heat exchanger 533 is made of a material with high thermal conductivity, the cooling fan 531 can be selected to blow air to deliver cold air into the pump chamber 510, where it exchanges heat with the heat exchanger 533 and / or the pump head cooling fins of the air pump 520 and is then discharged through the exhaust port at the bottom of the pump chamber 510.

[0191] In this embodiment, the pressure relief duct 5122 receives the gas flowing from the four-way interface 5123 and enters the pump chamber 510, forming a positive pressure in the pump chamber 510. The cooling fan 531 assists in the airflow by drawing air out.

[0192] In addition to enhanced heat dissipation, this embodiment improves working efficiency and stability by using multiple air pumps 520 operating in tandem. Various combinations are possible in actual operation. For example:

[0193] The dual pumps operate at low pressure simultaneously to provide the final output high pressure: Since the parameters of the consumables (interventional catheter) at the front end are variable, it is sometimes necessary to increase the upper limit pressure of the air pump 520, that is, close to the full load operation of 0.2mPa. The dual pumps in parallel input mode each provide a certain low flow rate, which is collected by the three-way check valve at the back end and sent to the main pipe 511 to generate the working pressure requirement, which greatly reduces the utilization factor of each unit.

[0194] Dual pumps working separately extend service life: When the working pressure is low, one air pump is used for each operation, which will not cause the temperature to rise continuously and affect the equipment. In addition, if one pump fails, the other can be used as a backup to prevent downtime, and an alarm will be triggered.

[0195] Besides the operational stability issues mentioned above, the noise and vibration of the air pump 520 also present problems in actual use. (See attached reference.) Figure 12 In the illustrated embodiment, a sound-absorbing baffle 513 is provided on the inner wall of the pump chamber 510. The baffle is attached to the side wall of the pump chamber 510 or spaced apart from the side wall of the pump chamber 510. The sound-absorbing baffle 513 can be made of a highly elastic or complex surface sound-absorbing material (such as environmentally friendly sponge, made of various porous sound-absorbing materials, such as rock wool, plant fiber spraying, etc., to absorb noise), or it can be made of a high-density sound-absorbing material, or a high-damping shock-absorbing material, or it can even be combined with the side wall of the pump chamber 510 (for example, the side wall of the pump chamber 510 is treated with a double layer, a vacuum is drawn, and a getter such as a composite getter composed of barium aluminum alloy and zirconium aluminum is added between the double layers to reduce the medium for sound transmission). A first filter 5211 is provided on the air inlet pipe.

[0196] In addition, the above problems can be overcome by installing shock absorption devices. (See attached reference) Figure 13 In the illustrated embodiment, the air pump 520 is connected to the housing 500 via a secondary vibration damping device 514, which includes:

[0197] Several first buffer blocks 5141 are disposed on the housing 500;

[0198] The primary shock absorption platform 5142 is supported by each first buffer block 5141;

[0199] Several second buffer blocks 5143 are set on the primary shock absorption platform 5142 and connected to the air pump 520.

[0200] The second buffer block 5143 has a lower hardness than the first buffer block 5141, effectively blocking vibration transmission between the air pump 520 and the housing 500. Structurally, the second buffer block 5143 is a thin-walled cylindrical structure with first and second mounting slots at the top and bottom for the mounting feet of the primary damping platform 5142 and the air pump 520 to engage. In terms of overall dimensions, the outer diameter of the first buffer block 5141 is approximately 11 mm, the buffer distance between the first and second mounting slots is approximately 8 mm, and the wall thickness of the cylindrical portion between the first and second mounting slots is approximately 1 mm. Overall, the second buffer block 5143 is a long cylindrical shape, meaning its axial length is slightly greater than its radial length, thus providing greater deformation space to absorb vibration.

[0201] In the attached diagram, the second buffer block 5143 can be tilted relative to a shock-absorbing platform 5142. In principle, the line connecting the center of the upper surface and the middle of the lower surface of the second buffer block 5143 is the working line. When the second buffer block 5143 is tilted, the working line will form an angle with the direction of gravity. In the above configuration, this angle can reach 20 degrees or even 30 degrees, thereby effectively releasing the vibration energy of the air pump 520.

[0202] However, excessive tilting of the second buffer block 5143 may reduce the installation stability of the air pump 520. Therefore, this problem can be avoided by adjusting the structural parameters of the second buffer block 5143. For example, each second buffer block 5143 can have directional characteristics, thereby ensuring the spatial stability of the air pump through force coupling in different directions. Ideally, the second buffer block 5143 should only receive its own axial load. To avoid unexpected situations and improve robustness, a buffer zone can be set between the air pump 520 and surrounding components to prevent component interference caused by the tilting of the second buffer block 5143. Especially when using dual air pumps arranged side by side, the spacing between the air pumps should be ensured to avoid interference.

[0203] In addition to structural optimization, optimization can also be achieved through control methods. For example, this application also discloses an interventional device control method, which specifically includes:

[0204] S1, preset target air pressure and at least two sets of PID parameters, and associate each target air pressure with the corresponding PID parameters;

[0205] S2, the infusion device first provides gaseous fluid to the interventional catheter;

[0206] S3, the sampling device collects the first real-time air pressure value, compares the first real-time air pressure value with the target air pressure, the control device retrieves the corresponding PID parameters, and uses the PID parameters to adjust the gas phase fluid pressure value of the infusion device;

[0207] S4, the perfusion device then provides liquid fluid to the interventional catheter so that the interventional catheter outputs atomized fluid;

[0208] S5, the sampling device collects the second real-time air pressure value, compares the second real-time air pressure value with the target air pressure, the control device retrieves the corresponding PID parameters, and uses the PID parameters to adjust the gas phase fluid pressure value of the infusion device;

[0209] S6, repeat step S5 at preset intervals.

[0210] By controlling the interventional system's operation using at least two sets of PID parameters, operational stability can be effectively improved. For example, if the target pressure is a target pressure value, the control device determines the relationship between the second real-time pressure value and the target pressure value to select the necessary PID parameters. Alternatively, if the target pressure is a target pressure range, the control device determines the target pressure range within which the second real-time pressure value falls to select the necessary PID parameters. In detail, using corresponding PID parameters to adjust the gas phase fluid pressure of the perfusion device can prevent liquid phase fluid from entering the gas path of the interventional catheter, thus improving safety.

[0211] Furthermore, the first real-time air pressure value is less than the second real-time air pressure value. This setting prevents excessively high air pressure from cutting off the fluid path within the interventional catheter. At least two voltage values ​​are preset, with each set of PID parameters associated with a corresponding voltage value. When the control device retrieves the corresponding PID parameter, it adjusts the starting voltage value of the infusion device based on the voltage value corresponding to that PID parameter. This setting can shorten the start-up time of the air pump.

[0212] In other embodiments, the intervention system control method further includes:

[0213] S7, the perfusion device first stops supplying liquid fluid to the interventional catheter, and then stops supplying gaseous fluid to the interventional catheter. This step is mainly used to clear the liquid fluid inside the interventional catheter.

[0214] This embodiment provides a method for segmented adjustment of gas phase fluid pressure: the target pressure of the gas phase fluid is divided into at least two segments, and each segment is adjusted using independent PID control parameters. Control parameters may include, for example, an initial voltage value.

[0215] In this embodiment, the threshold values ​​for each segment are preset in the control unit, for example, 120 kPa or 130 kPa. By dividing the PID control parameters into multiple segments, stable and rapid pressure regulation with small overshoot can be achieved in each segment, resulting in stable atomization with minimal fluctuations and more precise control. For example, the target gaseous fluid pressure can be divided into a low-pressure segment of 50 kPa to 130 kPa and a high-pressure segment of 130 kPa to 200 kPa. The range of adjustment for each PID control segment is typically between 20 and 80 kPa. Based on the segmented PID control strategy (i.e., the method for regulating gaseous fluid pressure described above), the interventional catheter needs to deliver liquid fluid first, followed by gaseous fluid, to facilitate accurate sampling by the pressure sensor.

[0216] The interventional device includes a display unit, which may also be equipped with a touch screen for human-machine interaction with the control unit located on the control panel. During use, the user inputs the target pressure range via the display unit, for example, 70 kPa to 200 kPa, and then activates the interventional device via the control unit.

[0217] The technical features of the embodiments described above can be combined arbitrarily. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as the combination of these technical features does not contradict each other, it should be considered to be within the scope of this specification. When technical features of different embodiments are embodied in the same drawing, it can be regarded as the drawing also disclosing examples of combinations of the various embodiments involved.

[0218] The embodiments described above are merely examples of several implementation methods of this application, and while the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the patent application. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these modifications and improvements all fall within the protection scope of this application.

Claims

1. A high-viscosity fluid spraying system for natural human cavities, characterized in that, It includes an interventional catheter and an infusion device for delivering a first fluid and a second fluid to the interventional catheter, respectively; The interventional catheter includes a tube body, one end of which is a proximal end and the other end is a distal end that can extend into the bronchus. The tube body has a channel for delivering fluid from the proximal end to the distal end. The distal end of the tube body is provided with a mixing structure, through which the fluid in the channel is mixed and then output. The mixing structure has at least a first fluid inlet, a second fluid inlet, and an outlet, with each fluid inlet having an independently configured flow channel within the pipe body; The mixing structure contains a microchannel chip. The first fluid inlet is located near the proximal end of the microchannel chip, and the second fluid inlet is located beside the microchannel chip. The interior of the microchannel chip is a chip channel connecting the outlet and each fluid inlet. The chip channel includes: The main channel is connected at one end to the first fluid inlet on the proximal side and at the other end to the outlet; The side channel is connected at one end to the second fluid inlet located on the side, and at the other end to the main channel; The chip channel is provided with a distribution structure that can act on at least a portion of the fluid.

2. The high-viscosity fluid spraying system according to claim 1, characterized in that, After the fluid enters the interventional catheter, it is mixed and atomized at the mixing structure, wherein the atomized droplet size is ≥20 micrometers, one of the first fluid and the second fluid is a liquid phase fluid and the other is a gas phase fluid, the pressure of the liquid phase fluid is 0.2 to 0.76 MPa and the pressure of the gas phase fluid is 0.1 to 0.4 MPa.

3. The high-viscosity fluid spraying system according to claim 1, characterized in that, The side channel is equipped with a fluid acceleration structure, which is located upstream of at least one intersection of the main channel and the side channel.

4. The high-viscosity fluid spraying system according to claim 3, characterized in that, The fluid in the side channel is gas, and the fluid acceleration structure is a Laval nozzle with a gradually converging and expanding configuration.

5. The high-viscosity fluid spraying system according to claim 4, characterized in that, One part of the main channel is a widened expansion section, at least a part of the side channel converges to the expansion section, and the expansion section is provided with a distribution member, the distribution member having at least a first distribution surface and a second distribution surface facing the direction of fluid movement in the main channel.

6. A cell spraying system for natural human cavities, characterized in that, It includes an interventional catheter and an infusion device for delivering a first fluid and a second fluid to the interventional catheter, respectively; The interventional catheter includes a tube body, one end of which is a proximal end and the other end is a distal end that can extend into the bronchus. The tube body has a channel for delivering fluid from the proximal end to the distal end. The distal end of the tube body is provided with a mixing structure, through which the fluid in the channel is mixed and then output. The mixing structure has at least a first fluid inlet, a second fluid inlet, and an outlet, with each fluid inlet having an independently configured flow channel within the pipe body; The mixing structure contains a microchannel chip. The first fluid inlet is located near the proximal end of the microchannel chip, and the second fluid inlet is located beside the microchannel chip. The interior of the microchannel chip is a chip channel connecting the outlet and each fluid inlet. The chip channel includes: The main channel is connected at one end to the first fluid inlet on the proximal side and at the other end to the outlet; The side channel is connected at one end to the second fluid inlet located on the side, and at the other end to the main channel; The chip channel is provided with a distribution structure that can act on at least a portion of the fluid.

7. The cell spraying system according to claim 6, characterized in that, The cells have a particle size of 15-120 micrometers, and one of the first fluid and the second fluid is a liquid phase fluid and the other is a gas phase fluid. The pressure of the liquid phase fluid is 0.2-0.76 MPa, and the pressure of the gas phase fluid is 0.1-0.4 MPa.

8. The cell spraying system according to claim 6, characterized in that, The main flow channel and / or the side flow channel are provided with a fluid acceleration structure and a sudden expansion section arranged sequentially according to the fluid flow direction. The internal volume of the sudden expansion section is at least 15% larger than the internal volume of the fluid acceleration structure. The fluid in the main flow channel and the side flow channel meet and atomize in the sudden expansion section.

9. The cell spraying system according to claim 8, characterized in that, The side channel carries liquid and has a distribution structure at one end near the main channel. The distribution structure is an array of distribution components, and the cross-sectional size of each distribution component gradually increases in the direction of fluid flow.

10. A drug spraying system for natural human cavities, characterized in that, It includes an interventional catheter and an infusion device for delivering a first fluid and a second fluid to the interventional catheter, respectively; The interventional catheter includes a tube body, one end of which is a proximal end and the other end is a distal end that can extend into the bronchus. The tube body has a channel for delivering fluid from the proximal end to the distal end. The distal end of the tube body is provided with a mixing structure, through which the fluid in the channel is mixed and then output. The mixing structure has at least a first fluid inlet, a second fluid inlet, and an outlet, with each fluid inlet having an independently configured flow channel within the pipe body; The mixing structure contains a microchannel chip. The first fluid inlet is located near the proximal end of the microchannel chip, and the second fluid inlet is located beside the microchannel chip. The interior of the microchannel chip is a chip channel connecting the outlet and each fluid inlet. The chip channel includes: The main channel is connected at one end to the first fluid inlet on the proximal side and at the other end to the outlet; The side channel is connected at one end to the second fluid inlet located on the side, and at the other end to the main channel; The chip channel is provided with a distribution structure that can act on at least a portion of the fluid.

11. The drug spraying system according to claim 10, characterized in that, One of the first fluid and the second fluid is a liquid phase fluid, and the other is a gas phase fluid. The drug is loaded in the liquid phase fluid, the particle size of the drug is less than 69 micrometers, the pressure of the liquid phase fluid is 0.2 to 0.76 MPa, and the pressure of the gas phase fluid is 0.2 to 0.6 MPa.

12. The drug spraying system according to claim 10, characterized in that, The side channel and the main channel intersect at least twice.

13. The drug spraying system according to claim 12, characterized in that, One part of the main channel is a widened expansion section, and the side channel intersects the main channel at least once on the expansion section and at least once after the expansion section.

14. A virus inactivation spraying system for natural human cavities, characterized in that, It includes an interventional catheter and an infusion device for delivering a first fluid and a second fluid to the interventional catheter, respectively; The interventional catheter includes a tube body, one end of which is a proximal end and the other end is a distal end that can extend into the bronchus. The tube body has a channel for delivering fluid from the proximal end to the distal end. The distal end of the tube body is provided with a mixing structure, through which the fluid in the channel is mixed and then output. The mixing structure has at least a first fluid inlet, a second fluid inlet, and an outlet, with each fluid inlet having an independently configured flow channel within the pipe body; The mixing structure contains a microchannel chip. The first fluid inlet is located near the proximal end of the microchannel chip, and the second fluid inlet is located beside the microchannel chip. The interior of the microchannel chip is a chip channel connecting the outlet and each fluid inlet. The chip channel includes: The main channel is connected at one end to the first fluid inlet on the proximal side and at the other end to the outlet; The side channel is connected at one end to the second fluid inlet located on the side, and at the other end to the main channel; The chip channel is provided with a distribution structure that can act on at least a portion of the fluid.

15. The virus inactivation spraying system according to claim 14, characterized in that, One of the first fluid and the second fluid is a liquid phase fluid, and the other is a gas phase fluid. The inactivated virus is loaded in the liquid phase fluid, wherein the particle size of the inactivated virus is less than 21 micrometers, the pressure of the liquid phase fluid is 0.2 to 0.76 MPa, and the pressure of the gas phase fluid is 0.2 to 0.6 MPa.

16. The virus inactivation spraying system according to claim 14, characterized in that, The side flow channel has two channels, which are respectively located on both sides of the main flow channel. Each side flow channel has an independent branch flow channel. The independent branch flow channel includes multiple sub-flow channels arranged in an array. The multiple sub-flow channels of the two branch flow channels are arranged opposite to each other and connected to the main flow channel. The multiple sub-flow channels of the two branch flow channels are staggered at intervals.

17. The spraying system according to any one of claim 1, claim 6, claim 10, or claim 14, characterized in that, Also includes: A sampling device used to collect fluid state parameters; The control device, connected to the acquisition device, is used to receive status parameters and control the injection device accordingly.

18. The spraying system according to claim 17, characterized in that, The spraying system also includes a housing, on which air and liquid connectors are installed, and a pump chamber is located at the bottom inside the housing. The infusion device includes: A first infusion device includes a syringe and a drive mechanism. The syringe includes a barrel installed inside the housing and a piston slidably installed inside the barrel. The barrel has an outlet and communicates with the liquid connection connector. The drive mechanism is linked to the piston. The second injection device includes an air pump installed in the pump chamber, wherein multiple air pumps are connected in parallel and are connected to the air circuit connector through a main pipe.

19. The spraying system according to claim 18, characterized in that, The spraying system also includes a cooling component that is thermally coupled to the air pump.

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