Interventional catheters, interventional devices, nebulization delivery systems, and nebulization methods

Abstract

The application relates to an interventional catheter, an interventional device, a nebulization administration system and a nebulization method, wherein the interventional catheter comprises a tube body, the inside of the tube body is provided with a microfluidic chip, the microfluidic chip is provided with a first fluid inlet, a second fluid inlet and an outlet, the inside of the microfluidic chip is a chip flow channel which is communicated with the outlet and the fluid inlets, the chip flow channel comprises a main flow channel which is communicated with the first fluid inlet at one end and communicated with the outlet at the other end, a side flow channel which is communicated with the second fluid inlet at one end and communicated with the main flow channel at the other end, and the side flow channel is provided with a branch flow channel and is communicated with the main flow channel through the branch flow channel. The application realizes nebulization of the delivery fluid through the microfluidic chip, and the nebulization effect is improved.

Description

Interventional catheters, interventional devices, nebulized drug delivery systems, and nebulization methods Technical Field

[0001] This application relates to the field of nebulization technology, and in particular to interventional catheters, interventional devices, nebulized drug delivery systems, and nebulization methods. 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 relatively efficient inhalation and absorption. However, during inhalation, it is difficult for all the medication to reach the lesion, resulting in unnecessary losses. Furthermore, before reaching the lesion, the medication itself may cause damage to organs along its route due to its side effects, posing potential safety risks.

[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 aforementioned technical problems. This application discloses an interventional catheter, including a tube body, one end of which is a proximal end and the other end which is a distal end that can extend into the bronchus. The tube body contains a microfluidic chip, which has the following characteristics:

[0005] The first fluid inlet is located on the proximal side of the microchannel chip;

[0006] The second fluid inlet is located beside the microchannel chip;

[0007] The outlet is located on the distal side of the microfluidic chip;

[0008] The interior of the microchannel chip is a chip flow channel connecting the outlet and each fluid inlet, and the chip flow channel includes:

[0009] The main channel is connected to the first fluid inlet at one end and to the outlet at the other end;

[0010] The side channel is connected to the second fluid inlet at one end and to the main channel at the other end; the side channel has branch channels and intersects with the main channel via the branch channels.

[0011] Optionally, the side channel includes:

[0012] The main channel extends distally from the second fluid inlet until it merges with the main flow channel;

[0013] The branch channel has one end connected to the main channel with the connection point adjacent to the second fluid inlet, and the other end extends proximally and branches into multiple sub-channels, the ends of which converge at the middle and upper reaches of the main channel.

[0014] Optionally, the main channel has a bend at the second fluid inlet and extends distally through the bend, with one end of the branch channel connected to the proximal side of the bend.

[0015] Optionally, the branch channels are generally comb-shaped, and the ends of each sub-channel are vertically connected to the main channel.

[0016] Optionally, there are two side channels distributed on both sides of the main channel, and the ends of the sub-channels in the two side channels are staggered.

[0017] Optionally, there are two side channels distributed on both sides of the main channel. The main channels of the two side channels each intersect with the main channel and define a first intersection and a second intersection. The two side channels extend independently from the first intersection and the second intersection to the outlet and intersect near the outlet.

[0018] Optionally, in the main channel, a distribution member is provided near the outlet. Along the width direction of the main channel, the distribution member closes the middle of the main channel and forms narrow openings distributed on both sides between it and the sidewall of the main channel. The first intersection and the second intersection are respectively located at the corresponding narrow openings.

[0019] Optionally, the side channel is provided with a fluid acceleration structure and a sudden expansion section arranged sequentially according to the fluid flow direction, wherein the narrow opening is connected to the sudden expansion section, and the connection part is adjacent to the acceleration structure section.

[0020] Optionally, the distribution element has a triangular cross-sectional shape.

[0021] Optionally, the main flow channel extends in a straight line with a constant cross-section from the first fluid inlet to the distributor.

[0022] Optionally, the angle between the trend lines extending from the first intersection and the second intersection toward the outlet of the two side channels is an obtuse angle.

[0023] Optionally, the outlet has a widening trend, and the widening angle corresponds to the angle between the trend line and the outlet.

[0024] This application also discloses an atomization method based on a microchannel chip, including:

[0025] The microchannel chip receives liquid fluid.

[0026] The microchannel chip receives gaseous fluid, which is divided into two streams and independently guided to merge with the liquid fluid to form two atomized streams.

[0027] The two atomized streams are guided to converge inside the microchannel chip and then output.

[0028] In this process, at least a portion of each gas phase fluid is pre-diverted and converges with the liquid phase fluid upstream, causing turbulence; the remaining portion converges with the liquid phase fluid downstream and is atomized.

[0029] Optionally, the angle between the flow trend lines of the two atomized streams before they converge is an obtuse angle.

[0030] This application also discloses an atomized drug delivery system, comprising:

[0031] 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;

[0032] An interventional catheter, using the interventional catheter according to the above technical solution, wherein the proximal end of the interventional catheter is connected to the perfusion device for receiving gaseous fluid and liquid fluid respectively;

[0033] A sampling device used to collect fluid state parameters;

[0034] The control device, connected to the acquisition device, is used to receive status parameters and control the injection device accordingly.

[0035] This application also discloses a gas-liquid two-phase interventional device, wherein the interventional device includes:

[0036] The housing is equipped with air and liquid connectors, and a pump chamber is located at the bottom inside the housing.

[0037] 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.

[0038] Cooling components, thermally coupled to the air pump;

[0039] 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.

[0040] The drive mechanism is linked to the piston of the syringe;

[0041] 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.

[0042] 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

[0043] Figures 1a to 1c are schematic diagrams of the structure of an interventional catheter in one embodiment of this application;

[0044] Figures 2a to 2c are schematic diagrams of the microchannel chip structure in the sixth embodiment of this application;

[0045] Figures 3 to 6 are schematic diagrams of an interventional device in one embodiment of this application.

[0046] The annotations in the figure are explained as follows:

[0047] 900, Tube body; 901, Proximal end; 902, Distal end; 9061, Communication interface; 907, First interface; 908, Second interface;

[0048] 920. Microfluidic chip; 921. First unit chip; 922. Second unit chip;

[0049] 940. Sheath; 941. Balloon; 942. Balloon catheter; 943. Balloon control interface; 944. Heating assembly;

[0050] 130. Main flow channel; 140. Side flow channel;

[0051] 300. Branch flow channel;

[0052] 400. Distribution component; 460. Fluid acceleration structure; 461. Narrow opening; 462. Sudden expansion section;

[0053] 500. Housing; 501. Gas connection; 502. Liquid connection;

[0054] 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;

[0055] 520. Air pump; 5211. First filter;

[0056] 530. Cooling components; 531. Cooling fan; 532. Heat dissipation window; 533. Heat exchanger; 534. Airflow slit;

[0057] 600. Syringe; 700. Drive mechanism; 800. Control panel. Detailed Implementation

[0058] 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.

[0059] 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.

[0060] 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.

[0061] 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.

[0062] Referring to the accompanying drawings, 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:

[0063] The first fluid inlet is located on the proximal side 901 of the microchannel chip 920;

[0064] The second fluid inlet is located beside the microchannel chip 920;

[0065] The outlet is located at the distal end 902 of the microfluidic chip 920;

[0066] The interior of the microfluidic chip 920 consists of chip channels connecting the outlet and various fluid inlets. These chip channels include:

[0067] Main channel 130, one end connects to the first fluid inlet, and the other end connects to the outlet;

[0068] 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.

[0069] In this application, premixing of the main flow channel 130 and the side flow channel 140 is achieved through the branch flow channel 300. Specifically, the side flow channel 140 includes:

[0070] The main channel extends from the second fluid inlet to the distal end 902 until it merges with the main channel 130;

[0071] The branch channel 300 is connected to the main channel at one end and the connection point is adjacent to the second fluid inlet. The other end extends to the proximal end 901 and branches into multiple sub-channels. The ends of each sub-channel converge to the middle and upper reaches of the main channel 130.

[0072] As shown in the attached figure, the main channel has a bend at the second fluid inlet and extends to the distal end 902 via the bend. One end of the branch channel 300 is connected to the proximal end 901 side of the bend.

[0073] The branch channel 300 has a comb-like structure, with the ends of each sub-channel vertically connected to the main channel 130. There are two side channels 140 located on either side of the main channel 130, with the ends of the sub-channels in the two side channels 140 staggered. The main channels of the two side channels 140 each intersect with the main channel 130, defining a first and a second intersection point. The two side channels 140 extend independently from the first and second intersection points towards the outlet and converge near the outlet. In the main channel 130, a distribution element 400 is provided near the outlet. This distribution element can be a protrusion formed by the residue after etching the first unit plate 921 or the second unit plate 922. Along the width of the main flow channel 130, the distributor 400 closes the middle of the main flow channel 130 and forms narrow openings 461 on both sides between itself and the sidewall of the main flow channel 130. The first and second confluences are located at the corresponding narrow openings 461. The side flow channel 140 is 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 connecting portion is adjacent to the acceleration structure section. The distributor 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 angle between the trend lines extending from the first and second confluences of the two side flow channels 140 towards the outlet is an obtuse angle. The outlet has a widening tendency, and the widening angle corresponds to the angle between the trend lines.

[0074] Based on the above description, this application also discloses an atomization method based on a microfluidic chip 920, including:

[0075] Liquid fluid is received via the microfluidic chip 920;

[0076] 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.

[0077] The two atomized streams are guided to converge inside the microchannel chip 920 before being output.

[0078] In terms of specific implementation, at least a portion of each gaseous fluid is pre-diverted and converges 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 their convergence is obtuse.

[0079] In terms of specific details, the chip's aspect ratio ranges from 2.5 to 5, with a preferred range of 3 to 4. The aspect ratio shown in the attached figure is 2.5:0.9. The width 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 the main channel 130 is 0.3 mm. The width of the main channel throat is smaller than the width of the main channel 130, and the width 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 the main channel throat is 0.1 mm. The droplet outlet width can be the same as the main channel throat width, or it can be set differently, for example, the droplet outlet width can deviate from the main channel throat width by 5% to 15%. In the attached figure, the droplet outlet width W8 is preferably 0.12 mm. The width 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 of the side channel 140 is 0.2 mm. The distance 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 between the side channel 140 and the proximal side of the microchannel chip 920 is 1.3 mm. The width 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 of the branch channel is 0.02 mm. The width of the sub-channel is smaller than the width of the branch channel. The width of the sub-channel 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 the sub-channel is 0.01 mm. Regarding thickness, the thickness of the etched channel unit wafer is preferably 0.2 to 0.5 mm, and in actual products, it is preferably 0.25 to 0.35 mm. In the attached figure, the thickness of the etched channel unit wafer is 0.3 mm. In the attached figure, the etching depth of the etched channel unit wafer is 0.05 mm. The overall thickness 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 figure, the overall thickness of the microchannel chip 920 is 0.6 ± 0.02 mm.

[0080] In this embodiment, gas is transported in the side channel 140, which is provided with 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 sub-channels of the two branch channels 300 are arranged opposite each other and connected to the main channel 130. The sub-channels of the two branch channels 300 are staggered at intervals, which allows the fluid in the side channel to disturb the fluid in the main channel. In the embodiment shown in the accompanying drawings, the main channel 130 and the side channel 140 intersect at least twice along the extension direction of the main channel 130. The first intersection causes turbulence in the middle and upper reaches of the main channel 130, and the second intersection atomizes the fluid near the outlet 120. The first intersection serves as a pre-dispersion mechanism, and the secondary mixing effectively controls the atomized droplet size and its distribution range. The staggered arrangement of multiple sub-channels allows for sequential impact from both sides of the main channel, resulting in better atomization and improved premixing while preventing opposing sub-channels from clogging the main channel. In this embodiment, the fluid transported in the side channels is gas, and the fluid transported in the main channel is liquid. The sub-channels enable the gas to impact the liquid sequentially from both sides, allowing the liquid to be better dispersed and mixed.

[0081] 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 are intersected 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 and corresponds to two sudden expansion sections 462 respectively. As can be seen from the accompanying drawings, a portion of the sidewall of the sudden expansion section 462 is provided by the distributor 400. From another perspective, the distributor 400 divides the main channel into two narrow openings 461 and two sudden expansion sections 462 corresponding to the two narrow openings 461, wherein the two sudden expansion sections 462 correspond to the fluid acceleration structures 460 of the two side channels 140 respectively. The above configuration effectively reduces the fabrication difficulty of microfluidic chips and improves the dimensional accuracy of the flow channels. By controlling the dimensional parameters of the main flow channel and the distribution components, precise dimensional parameters of the orifices and the expansion sections can be obtained, resulting in a compact and stable internal structure. Furthermore, compared to smaller distribution components, the larger distribution components in this embodiment offer superior structural strength and the ability to withstand greater fluid pressure, thus meeting a wider range of design requirements. In terms of convergence, the main flow channel 130 or the side flow channel 140 converges with the other through two orifices 461. The side flow channel 140 has an expansion section 462 downstream of the fluid acceleration structure 460. In the accompanying drawings, it is clearly visible that the expansion section 462 has a larger cavity diameter and a larger internal volume. Proportionally, the internal volume of the expansion section 462 is at least 15% larger than the internal volume of the fluid acceleration structure. The convergence point with the orifices 461 is located at the proximal end of the expansion section 462. The expansion section 462 is positioned abutting against the fluid acceleration structure 460, and the cavity diameter of the expansion section 462 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 principle of differential pressure atomization. Compared with 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 position. The two pressure-differential atomized droplets collide at the outlet position, forming finer droplets while ensuring a relatively high concentration of droplet size distribution. In this embodiment, the atomized droplet size distribution is in the range of 5 to 40 μm, with at least 70% distributed in the range of 5 to 15 μm.

[0082] This application also discloses an atomized drug delivery system, comprising:

[0083] 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;

[0084] The interventional catheter, according to the above technical solution, has its proximal end 901 connected to the perfusion device for receiving gaseous fluid and liquid fluid respectively.

[0085] A sampling device used to collect fluid state parameters;

[0086] The control device, connected to the acquisition device, is used to receive status parameters and control the injection device accordingly.

[0087] Other parts of the interventional catheter can adopt designs from the prior art. Referring to Figures 1a to 1c, this application also provides another type of interventional catheter, including:

[0088] 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; the tube body 900 includes a sheath 940, which provides protection and necessary mechanical support for each inner tube.

[0089] 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.

[0090] 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;

[0091] The balloon 941 is deformably configured on the outside of the tube 900.

[0092] 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.

[0093] 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 temperature it can kill lesions (cancer cells) while allowing normal cells to 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.

[0094] This application also discloses a gas-liquid two-phase interventional device, wherein the interventional device includes:

[0095] 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.

[0096] 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.

[0097] Cooling assembly 530 is thermally coupled to air pump 520;

[0098] 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.

[0099] The drive mechanism 700 is linked to the piston of the syringe 600;

[0100] The interventional catheter, using the interventional catheter in the above technical solution, has its proximal end 901 connected to the gas connector 501 and the liquid connector 502 respectively, for receiving gaseous fluid and liquid fluid respectively.

[0101] Regarding the specific configuration of the device, referring to the embodiments shown in Figures 3 to 6, this application also discloses an interventional device, wherein the interventional device includes:

[0102] 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.

[0103] 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.

[0104] Cooling assembly 530 is thermally coupled to air pump 520;

[0105] 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.

[0106] The drive mechanism 700 is linked to the piston of the syringe 600.

[0107] 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.

[0108] The structure of the gas path section is shown in the attached diagram. The interventional device includes:

[0109] The housing 500 has an air connector 501 installed on it, and a pump chamber 510 is located at the bottom inside the housing 500. The operation panel 800 is located on the outside of the housing 500 and is used to input control information and output parameter status.

[0110] 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.

[0111] 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;

[0112] Cooling fan 531 is thermally coupled to air pump 520.

[0113] 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.

[0114] The airflow direction of the cooling fan 531 needs to be adjusted according to the material of the heat exchanger 533.

[0115] 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.

[0116] 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.

[0117] 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:

[0118] 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 rear end and sent to the main pipe 511 to generate the working pressure requirement, which greatly reduces the utilization factor of each unit.

[0119] 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.

[0120] Besides the operational stability of the air pump 520 mentioned above, noise and vibration issues also exist in actual use. Referring to the embodiment shown in Figure 4, 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 it. The sound-absorbing baffle 513 can be made of highly elastic or complex-surfaced sound-absorbing material (e.g., 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 high-density sound-absorbing material, or a high-damping vibration-damping material, or even combined with the side wall of the pump chamber 510 (e.g., the side wall of the pump chamber 510 is layered (double-layered), a vacuum is drawn, and a getter such as a composite getter composed of barium aluminum alloy and zirconium aluminum is added between the two layers to reduce the medium for sound transmission). A first filter 5211 is provided on the air inlet pipe.

[0121] In addition, the above problems can be overcome by setting up a shock absorption device. Referring to the embodiment shown in Figure 5, the air pump 520 is connected to the housing 500 via a secondary shock absorption device 514, which includes:

[0122] Several first buffer blocks 5141 are disposed on the housing 500;

[0123] The primary shock absorption platform 5142 is supported by each first buffer block 5141;

[0124] Several second buffer blocks 5143 are set on the primary shock absorption platform 5142 and connected to the air pump 520.

[0125] 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.

[0126] 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.

[0127] 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.

[0128] 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:

[0129] S1, preset target air pressure and at least two sets of PID parameters, and associate each target air pressure with the corresponding PID parameters;

[0130] S2, the infusion device first provides gaseous fluid to the interventional catheter;

[0131] 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;

[0132] S4, the perfusion device then provides liquid fluid to the interventional catheter so that the interventional catheter outputs atomized fluid;

[0133] 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;

[0134] S6, repeat step S5 at preset intervals.

[0135] 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.

[0136] 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.

[0137] In other embodiments, the intervention system control method further includes:

[0138] 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.

[0139] 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.

[0140] 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 described above for regulating gaseous fluid pressure), the interventional catheter needs to deliver liquid fluid first, followed by gaseous fluid, to facilitate accurate sampling by the pressure sensor.

[0141] 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.

[0142] 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.

[0143] 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. An interventional catheter, characterized in that, The device includes a tube body, one end of which is a proximal end and the other end of which is a distal end that can extend into the bronchus. The tube body contains a microfluidic chip, which has: a first fluid inlet located on the proximal side of the microfluidic chip; and a second fluid inlet located on the side of the microfluidic chip. The outlet is located on the distal side of the microfluidic chip; The microchannel chip has internal flow channels connecting the outlet and each fluid inlet. These flow channels include: a main flow channel, connected at one end to the first fluid inlet and at the other end to the outlet; and side flow channels, connected at one end to the second fluid inlet and at the other end to the main flow channel. Each side flow channel has branch channels that intersect with the main flow channel. Each side flow channel includes: a trunk flow channel extending distally from the second fluid inlet until it intersects with the main flow channel; and a branch flow channel, one end of which connects to the trunk flow channel with the connection point adjacent to the second fluid inlet, and the other end extending proximally and branching into multiple sub-flow channels. The ends of the sub-channels converge at the middle and upper reaches of the main channel; there are two side channels distributed on both sides of the main channel, and the main channels of the two side channels each converge with the main channel and define a first convergence point and a second convergence point. The two side channels extend independently from the first convergence point and the second convergence point to the outlet and converge near the outlet; in the main channel, a distribution member is provided near the outlet. Along the width direction of the main channel, the distribution member closes the middle of the main channel and forms narrow openings distributed on both sides between it and the sidewall of the main channel. The first convergence point and the second convergence point are respectively located at the corresponding narrow opening positions.

2. The interventional catheter according to claim 1, characterized in that, The main channel has a bend at the second fluid inlet and extends distally through the bend, with one end of the branch channel connected to the proximal side of the bend.

3. The interventional catheter according to claim 1, characterized in that, The branch channels have a comb-like structure, and the ends of each sub-channel are vertically connected to the main channel.

4. The interventional catheter according to claim 3, characterized in that, The side channels are two in number and distributed on both sides of the main channel, with the ends of the sub-channels in the two side channels arranged in a staggered manner.

5. The interventional catheter according to claim 1, characterized in that, The side channel is provided with a fluid acceleration structure and a sudden expansion section arranged sequentially according to the fluid flow direction, wherein the narrow opening is connected to the sudden expansion section, and the connection part is adjacent to the acceleration structure section.

6. The interventional catheter according to claim 1, characterized in that, The distribution component has a triangular cross-sectional shape.

7. The interventional catheter according to claim 1, characterized in that, The main flow channel extends from the first fluid inlet to the distribution member, maintaining a straight line with a constant cross-section.

8. The interventional catheter according to claim 1, characterized in that, The angle between the trend lines extending from the first and second confluences toward the outlet of the two side channels is an obtuse angle.

9. The interventional catheter according to claim 8, characterized in that, The outlet has a widening trend, and the widening angle corresponds to the angle between the trend line and the outlet.

10. Atomized drug delivery system, characterized in that, include: 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; An interventional catheter, using any one of claims 1 to 9, wherein the proximal end of the interventional catheter is connected to an infusion device for receiving gaseous fluid and liquid fluid respectively; a sampling device for collecting fluid state parameters; and a control device connected to the sampling device for receiving state parameters and controlling the infusion device accordingly.

11. A gas-liquid two-phase intervention device, characterized in that, The interventional device includes: a housing, on which a gas connection connector and a liquid connection connector are mounted, and a pump chamber is provided at the bottom inside the housing; a gas pump, installed in the pump chamber, wherein multiple gas pumps are connected in parallel and connected to the gas connection connector via a main pipe; a cooling assembly, thermally coupled to the gas pump; a syringe, including a cylinder installed inside the housing and a piston slidably installed inside the cylinder, the cylinder having an outlet and communicating with the liquid connection connector; a drive mechanism, linked to the piston of the syringe; and an interventional catheter, employing an interventional catheter according to any one of claims 1 to 9, wherein the proximal end of the interventional catheter is connected to the gas connection connector and the liquid connection connector respectively, for receiving gaseous fluid and liquid fluid respectively.

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