Intervention systems, control methods, computer equipment, software products, and storage media

Abstract

This application relates to interventional systems, control methods, computer equipment, program products, and storage media. The interventional system includes: an infusion device for supplying a fluid containing a therapeutic substance, the fluid comprising a liquid phase fluid and a gas phase fluid, at least one of which contains the therapeutic substance; an interventional catheter connected to the infusion device for receiving the fluid and, after nebulization, outputting it into the bronchus; a sampling device for collecting the fluid's state parameters; and a control device connected to the sampling device for receiving the state parameters and correspondingly controlling the infusion device. This application improves interventional outcomes through optimization of the interventional system.

Description

Technical Field

[0001] This application relates to the field of atomization technology, and in particular to intervention systems, control methods, computer equipment, program products, and storage media. 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 intervention system control method, comprising:

[0005] S1, preset target air pressure and at least two sets of PID parameters, and associate each target air pressure with the corresponding PID parameters;

[0006] S2, the infusion device first provides gaseous fluid to the interventional catheter;

[0007] 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;

[0008] S4, the perfusion device then provides liquid fluid to the interventional catheter so that the interventional catheter outputs atomized fluid;

[0009] 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;

[0010] S6, repeat step S5 at preset intervals.

[0011] Optionally, the first real-time air pressure value is less than the second real-time air pressure value.

[0012] Optionally, at least two voltage values ​​are preset, and each set of PID parameters is associated with a corresponding voltage value. When the control device retrieves the corresponding PID parameter, the control device adjusts the starting voltage value of the infusion device through the voltage value corresponding to the PID parameter.

[0013] Optionally, it also includes: S7, where the perfusion device first stops supplying liquid fluid to the interventional catheter, and then the perfusion device stops supplying gaseous fluid to the interventional catheter.

[0014] Optionally, the target air pressure is a target air pressure value, and the control device determines the magnitude between the second real-time air pressure value and the target air pressure value to select the PID parameters to be retrieved; or the target air pressure is a target air pressure range value, and the control device determines the target air pressure range value in which the second real-time air pressure value is located to select the PID parameters to be retrieved.

[0015] This application also discloses an intervention system control method, including:

[0016] Preset liquid medium transport parameters, and generate a liquid medium transport map based on the preset liquid medium transport parameters;

[0017] A corresponding driving signal is generated based on the liquid medium transport pattern. The driving signal is used to drive the motor, and the motor is used to drive the piston of the syringe to achieve liquid transport.

[0018] The encoder signal set on the motor is collected to obtain the motor's operating position, and the piston's movement position is calculated from the motor's operating position.

[0019] Record the movement position of the piston and calculate the actual delivery pattern based on the movement position information of several pistons;

[0020] The liquid medium transport map and the actual transport map are compared according to a preset period. If the difference is less than the preset value, the original liquid medium transport map is retained. If the difference is greater than or equal to the preset value, the original liquid medium transport map is modified and a new liquid medium transport map is generated according to the preset rules and replaced with the original liquid medium transport map.

[0021] The liquid medium transport map is continuously updated until the liquid medium transport ends or is paused.

[0022] Optionally, the intervention system further includes a limit position detector, which is used to limit the movement limit of the piston.

[0023] This application also discloses an intervention system, including:

[0024] An infusion device for supplying fluids containing therapeutic substances;

[0025] An interventional catheter is used to receive fluids and, after mixing, deliver them into the body's natural cavities.

[0026] A sampling device used to collect the state parameters of a fluid;

[0027] A control device, connected to the acquisition device, is used to receive the status parameters and control the load accordingly. The control device includes a control unit and a switching circuit controlled by the control unit. The switching circuit includes a first switching transistor, which has the following characteristics:

[0028] The first input terminal is electrically connected to an external power supply;

[0029] The first output terminal is electrically connected to the corresponding load.

[0030] The first driving electrode is used to control and adjust the conduction and cutoff of the first input electrode and the first output electrode.

[0031] This application also discloses an intervention system, characterized in that it includes:

[0032] 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;

[0033] An interventional catheter, connected to an infusion device, is used to receive fluid and, after atomization, deliver it into the bronchus;

[0034] A sampling device used to collect the state parameters of a fluid;

[0035] The control device, connected to the acquisition device, is used to receive status parameters and control the injection device accordingly.

[0036] Optionally, the filling device includes a cylinder, a piston, and a drive mechanism; wherein the cylinder is installed to the corresponding position via an adapter, the adapter is provided with an adapter identification tag, and the control device is connected to an adapter identification circuit provided with an adapter identification tag. The adapter identification circuit determines the cylinder parameters by reading the adapter identification tag or uploads a data packet containing the cylinder parameters.

[0037] Optionally, the adapter identification circuit and the adapter identification tag complete the identification without contact; the adapter identification circuit includes an antenna PCB board and an antenna connected to the antenna PCB board, and the adapter identification tag is a passive tag sleeved on the adapter.

[0038] Optionally, it includes an atomizing device, said atomizing device comprising:

[0039] chassis;

[0040] An air pump is located on the housing. The air pump has an air inlet and an air outlet, and the air inlet and the air outlet are respectively connected to the outside of the housing through corresponding pipes.

[0041] The secondary damping device includes:

[0042] Several first buffer blocks are disposed inside the housing;

[0043] The primary shock absorption platform is supported by each first buffer block;

[0044] Several second buffer blocks are set on the primary shock absorption platform and support the air pump.

[0045] Optionally, it includes an atomizing device, said atomizing device comprising:

[0046] Pump room;

[0047] An air pump is located in the pump chamber. The air pump has an air inlet and an air outlet, and the air inlet and the air outlet are respectively connected to the outside of the pump chamber through corresponding pipelines.

[0048] A heat exchanger is located in the pump chamber and thermally coupled to the air pump, with at least a portion of the heat exchanger exposed to the chamber wall of the pump chamber;

[0049] A cooling fan is located outside the pump chamber and is thermally coupled to the heat exchanger.

[0050] Optionally, 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, and the fluid in the channel is output after being mixed by the mixing structure.

[0051] 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.

[0052] This application also discloses a computer device, including a processor, memory, network interface, display screen, and input device connected via a system bus, wherein the processor of the computer device is used to execute programs to implement the intervention system control method described above.

[0053] This application also discloses a program product comprising one or more computer instructions that, when executed by a computer, cause the computer to implement the aforementioned intervention system control method.

[0054] This application also discloses a storage medium storing computer-executable instructions that implement the above-described intervention system control method.

[0055] 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

[0056] Figures 1a to 1c These are structural block diagrams of the intervention system in different embodiments of this application;

[0057] Figure 1d This is a circuit diagram of a switching circuit in one embodiment of this application;

[0058] Figure 1e This is a circuit diagram of an air pump speed control circuit in one embodiment of this application;

[0059] Figure 1f This is a schematic diagram illustrating the working principle of the control unit in one embodiment of this application;

[0060] Figure 1g This is a schematic diagram of the interventional device in one embodiment of this application;

[0061] Figure 1h This is a schematic diagram of the intervention device control process in one embodiment of this application;

[0062] Figure 2 This is a schematic flowchart of a control method for a nebulized drug delivery system in one embodiment of this application;

[0063] Figure 3 This is a structural block diagram of a computer device according to an embodiment of this application;

[0064] Figures 4 to 8 This is a schematic diagram of the interventional device from different perspectives in one embodiment of this application;

[0065] Figures 9 to 10 This is a schematic diagram of the gas phase pipeline connection from different perspectives in one embodiment of this application;

[0066] Figures 11 to 14 This is a schematic diagram of the air pump from different perspectives in one embodiment of this application;

[0067] Figures 15 to 16 This is a schematic diagram showing the relationship between the air pump and the cooling components.

[0068] Figures 17 to 21 These are schematic diagrams of the liquid phase portion of the interventional device from different perspectives in one embodiment of this application;

[0069] Figures 22 to 26 This is a schematic diagram of the adapter identification circuit and the adapter identification tag from different perspectives in one embodiment of this application;

[0070] Figures 27 to 28 These are schematic diagrams of the internal structure of the interventional device from different perspectives in one embodiment of this application;

[0071] Figures 29 to 30 This is a schematic diagram of the movable door structure of the interventional device in one embodiment of this application from different perspectives;

[0072] Figures 31 to 32 This is a schematic diagram of the atomization control method in one embodiment of this application.

[0073] The annotations in the figure are explained as follows:

[0074] 500. Housing; 5001. Third buffer block; 501. Air connection; 5011. Second filter; 502. Liquid connection; 503. Exhaust port; 510. Pump chamber; 511. Main pipe; 512. Pressure relief valve; 5121. Output pipe; 5122. Pressure relief duct; 5123. Four-way connector; 513. Soundproof partition; 514. Secondary vibration damping device; 5141. First buffer block; 5142. Primary vibration damping platform; 5143. Second buffer block; 5144. First mounting slot; 5145. Second mounting slot; 520. Air pump; 521. Air inlet pipe; 5211. First filter; 522. Air pressure transmitter; 523. Gas cylinder; 524. Solenoid valve; 5 25. Pressure regulating valve; 530. Cooling assembly; 531. Cooling fan; 532. Heat dissipation window; 533. Heat exchanger; 534. Airflow slit; 600. Injector; 610. Cylinder; 620. Piston; 630. Adapter; 631. Limiting part; 632. Adaptive identification tag; 700. Drive mechanism; 701. Fixing base; 7011. Adaptive identification circuit; 702. Motor; 703. Slide; 7031. Pressure sensor; 704. Lead screw; 705. Pressure plate; 706. Locking device; 707. Sliding position sensor; 708. Sliding trigger; 709. Limit position sensor; 710. Limit trigger; 800. Operation panel; 801. Shielding cover. Detailed Implementation

[0075] 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.

[0076] 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.

[0077] 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.

[0078] 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.

[0079] In this application, "natural human cavities" refers to cavities within the human body that may develop pathological conditions, such as the lung cavity mentioned below, or other cavities, such as the intestines, kidneys, bladder, blood vessels, mouth and nose cavities, etc.

[0080] Specifically, this application discloses an interventional system control method, including: S1, preset a target air pressure and at least two sets of PID parameters, and associate each target air pressure with the corresponding PID parameters; S2, the perfusion device first provides gaseous fluid to the interventional catheter; S3, the sampling device collects a 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 gaseous fluid pressure value of the perfusion device; S4, the perfusion device then provides liquid fluid to the interventional catheter so that the interventional catheter outputs atomized fluid; S5, the sampling device collects a 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 gaseous fluid pressure value of the perfusion device; S6, repeating step S5 at preset time intervals.

[0081] 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.

[0082] 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.

[0083] In other embodiments, the interventional system control method further includes: S7, where the perfusion device first stops supplying liquid fluid to the interventional catheter, and then the perfusion device stops supplying gaseous fluid to the interventional catheter. This step is mainly used to clear the liquid fluid inside the interventional catheter.

[0084] In addition, the control method of this application also achieves safety control through multi-dimensional sensors. The intervention system includes a syringe, a position detector, an encoder, and a motor. The encoder is mounted on the motor and records the piston's stroke through the motor. The position detector is used to verify the piston's stroke to ensure that the piston is working normally. The intervention system also includes an extreme position detector, which is used to limit the piston's extreme stroke.

[0085] Therefore, from another perspective, this application also discloses an intervention system control method, including: preset liquid medium delivery parameters; generating a liquid medium delivery map based on the preset liquid medium delivery parameters; generating a corresponding drive signal based on the liquid medium delivery map, wherein the drive signal is used to drive a motor, and the motor is used to drive the piston of the syringe to achieve liquid delivery; acquiring encoder signals set on the motor to obtain the motor's operating position, and calculating the piston's movement position based on the motor's operating position; recording the piston's movement position and calculating an actual delivery map based on the movement position information of several pistons; comparing the liquid medium delivery map and the actual delivery map at a preset period; if the difference is less than a preset value, retaining the original liquid medium delivery map; if the difference is greater than or equal to the preset value, correcting according to a preset rule and generating a new liquid medium delivery map and replacing the original liquid medium delivery map; and continuously updating the liquid medium delivery map until the liquid medium delivery ends or is paused. Similarly, the closed-loop control and dynamic adjustment of liquid medium transportation can be combined with the closed-loop control of gas medium transportation, such as the comparison of gas pressure values ​​and the control method with at least two PID settings mentioned above.

[0086] In terms of the overall circuit logic of the device, referring to the interventional system shown in the attached figure, it includes: an infusion device for supplying fluid containing therapeutic substances; an interventional catheter for receiving the fluid and, after mixing, outputting it into the body's natural cavities; a sampling device for collecting the fluid's state parameters; and a control device connected to the sampling device for receiving the state parameters and correspondingly controlling the load. The control device includes a control unit and a switching circuit controlled by the control unit. The switching circuit includes a first switching transistor, which has: a first input terminal electrically connected to an external power supply; a first output terminal electrically connected to a corresponding load; and a first driving terminal for controlling and adjusting the conduction and cutoff of the first input terminal and the first output terminal.

[0087] In one embodiment, the above-mentioned device is actually disposed within an atomizing drug delivery system, see [link to relevant documentation]. Figure 1a This application provides a nebulized drug delivery system, comprising: 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 connected to the infusion device for receiving the fluid and outputting it into the bronchus after nebulization; a sampling device for collecting the state parameters of the fluid; and a control device connected to the sampling device for receiving the state parameters and controlling the infusion device accordingly.

[0088] The term "drug administration" as used in the embodiments of this application refers to the delivery of a therapeutic substance to the lesion site. Details of the therapeutic substance can be found in the descriptions of other embodiments. The interventional catheter is described in the embodiments of this application. A fluid containing the therapeutic substance enters the interventional catheter through an infusion device until it is applied to the lesion site in the body environment. The infusion device primarily provides fluid dynamics, achieving a certain flow rate that can be adjusted as needed. For example, a controllable fluid delivery pump can be used. Existing technologies can also be employed regarding the pump's structure and control method. The infusion device is configured according to the fluid state and type, and control devices are installed at locations requiring control. The fluid loaded with 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 a fluid including 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. To facilitate the operation of the interventional catheter, in one embodiment, the nebulized drug delivery system further includes an auxiliary device that acts on the interventional catheter to change the relative position of the interventional catheter and the lesion site.

[0089] See Figure 1bThe infusion device includes a first infusion device and a second infusion device. The microfluidic chip has multiple inlets, at least one of which is a gas phase inlet and at least one of which is a liquid phase inlet. The first infusion device includes a cylinder, a piston, and a drive mechanism. The cylinder is used to supply liquid fluid and has an outlet connected to the liquid phase inlet; the piston is slidably mounted on the cylinder; and the drive mechanism pushes the piston.

[0090] The first infusion device can be, for example, an injection pump equipped with a syringe, the barrel can be, for example, the syringe barrel, the piston can be, for example, the plunger of the syringe, and the drive mechanism can be, for example, a stepper motor, which pushes the piston in a linear motion to achieve drug delivery by the first infusion device. During use, the liquid phase fluid flow rate can be maintained at less than or equal to 4 ml / min. The thrust applied to the piston is 80–200 N, and based on the cross-sectional area of ​​the piston, the liquid phase fluid pressure is calculated to be 0.2–0.76 MPa, for example, 0.4 MPa. The second infusion device includes an air compressor and / or an air cylinder, at least one of which is used to supply the gas phase fluid and is connected to the gas phase inlet. When using an air compressor, the air is compressed to 1.5–2 bar, which is the necessary pressure for the gas phase fluid; when using an air cylinder, the pressure inside the air cylinder only needs to be higher than the pressure required for the gas phase fluid. The gas phase fluid pressure is 0.15–0.4 MPa, for example, 0.2 MPa. The first injection device is connected to one of the inner tubes, and the second injection device is connected to the other inner tube. Taking the first inner tube 950 for transporting liquid fluid as an example, the first inner tube 950 of the tube body is connected to the first injection device, and the second inner tube 960 is connected to the second injection device, and vice versa.

[0091] The first injection device, via, as follows Figure 1b The first interface shown connects to the first inner tube 950, and the second filling device connects to the second inner tube 960 via the second interface. A quick-release connector is provided at the interface between the second inner tube 960 and the second filling device. When the second filling device uses an air compressor bottle, connecting it to the air compressor bottle via the quick-release connector enhances portability and facilitates quick replacement. The air compressor bottle can have a capacity of, for example, 500ml to 1L, a pressure of 0.2 MPa, and can be made of, for example, metal. A regulating valve can be installed on the pipeline connected to the second inner tube 960, and the control device regulates the pressure of the gaseous fluid inside the second inner tube 960 via the regulating valve.

[0092] The sampling device can collect relevant parameters as needed for control purposes. The fluid state parameters include at least one of temperature, pressure, and flow rate. To assist operation, the sampling device also collects image signals and / or state signals of the lesion site. Image signals facilitate visualization and can serve as real-time references and comparisons, while state signals of the lesion site can reflect the treatment progress, such as electrical signals like current and impedance, or temperature. To monitor the patient's physiological state during treatment, the sampling device also collects physiological signals, such as at least one of electrocardiogram (ECG) and blood signals.

[0093] As a nebulized drug delivery system, it may involve multiple specific devices. In order to know the status of each device and use it as a basis for monitoring or control, the sampling device also collects the operating status of related devices, such as the operating status of the infusion device and / or the sampling device. Depending on the specific device, this could include speed, operating current, operating temperature, pressure, etc.

[0094] See Figures 1b-1c The sampling device includes a liquid phase sampling device and a gas phase sampling device. The liquid phase sampling device includes a position detector and a thrust detector. The control device receives signals from the liquid phase sampling device and can use them for feedback control of the first infusion device; it also receives signals from the gas phase sampling device and can use them for feedback control of the second infusion device. The position detector detects the piston position; the thrust detector detects the piston's pushing force, or, in other words, the resistance of the syringe during operation; the control device receives signals from the position detector and the thrust detector and controls the drive mechanism accordingly. The detectors can be the sensors mentioned below, and other descriptions are similar.

[0095] Given the varying piston resistance values ​​of different syringes, the first infusion device utilizes several specified types of syringes. A control device identifies the syringe type and accordingly drives the control mechanism. Specifically, after identifying the syringe model and capacity, the control device adjusts and obtains the flow rate of the liquid fluid in the first infusion device through signal feedback from the thrust detector. This flow rate is then used to control the drive mechanism, thereby regulating the liquid fluid flow rate. By obtaining the piston position at different times and detecting the syringe's travel distance, the flow rate delivered by the first infusion device is obtained. The thrust detector can, for example, be fixedly installed between the drive mechanism and the piston.

[0096] The gas phase sampling device includes a pressure detector for detecting the gas phase fluid pressure, and a control device for receiving signals from the pressure detector and controlling the gas phase fluid pressure accordingly. If the second filling device uses an air compressor, the control device detects the state parameters of the gas phase fluid, uses closed-loop feedback to control the speed of the air compressor, and adjusts the pressure of the gas phase fluid delivered by the air compressor. If the second filling device uses an air cylinder, the control device controls the gas phase fluid pressure through a regulating valve. It can be understood that the gas phase fluid pressure is only one aspect, and adjusting the pressure includes adjusting the flow rate of the gas phase fluid. Furthermore, the gas phase sampling device can also be equipped with a flow detector for detecting the output gas phase fluid flow rate.

[0097] The nebulized drug delivery system also includes a protection device, comprising a limit position detector, a temperature detector, and a cooling fan. Each part of the protection device prevents malfunction of the first and second infusion devices. The limit position detector detects the piston's extreme positions within the cylinder. The control device receives signals from the limit position detector and controls the drive mechanism accordingly to prevent damage to the equipment. The temperature detector monitors the air compressor's operating temperature; the cooling fan regulates the air compressor's operating temperature, and the control device receives information from the temperature detector and controls the cooling fan accordingly. The protection device also includes an alarm. If the second infusion device uses an air cylinder, the control device monitors the gas pressure of the gas phase fluid via a pressure detector; if the pressure is insufficient, the control device issues an alarm.

[0098] See Figure 1c Each detector can be implemented using a corresponding scheme. For example: the position detector is implemented using a sliding rheostat; the extreme position detector is implemented using an infrared limit sensor; the thrust detector is implemented using a syringe thrust sensor; the air compressor is implemented using an air compression pump; the temperature detector is implemented using a temperature sensor of the air compression pump; and the air pressure detector is implemented using an air pressure sensor. The control device includes a main board and a compressed air pump control main board, wherein the main board detects the data from the above detectors and controls the working status of the stepper motor, compressed air pump, and cooling fan accordingly.

[0099] The control device can also be used to convert the detection results of position detectors, thrust detectors, limit position detectors and pressure detectors into fluid state parameters, such as the flow rate and flow volume of liquid fluids and gaseous fluids, and output video and audio directly or after processing.

[0100] For example, nebulizer delivery systems also include, Figure 1aThe display device shown can also be equipped with touch functionality. The control device receives touch signals from the display device and adjusts the operating mode accordingly, such as adjusting the flow rate of the liquid phase fluid and the gas pressure of the gas phase fluid. The display device can, for example, use a capacitive touchscreen for human-machine interaction, system operating status indication, displaying the current gas phase fluid pressure, the current liquid phase fluid flow rate, and the flow rate of the liquid phase fluid already delivered.

[0101] See Figure 1d The control device includes a control unit and a switching circuit controlled by the control unit. The switching circuit includes a second switching transistor and a first switching transistor. The control unit is equipped with a microprocessor. For example, the control unit can be a single-chip microcomputer (MCU) located inside the motherboard. The high-level signal output by the control unit is the start signal, and the low-level signal output is the stop signal, which plays the role of controlling a large current with a small current.

[0102] The first switching transistor has a first driving electrode, a first input electrode, and a first output electrode, and the first driving electrode controls the first input electrode and the first output electrode to be turned on and off; the second switching transistor has a second driving electrode, a second input electrode, and a second output electrode, and the second driving electrode controls the second input electrode and the second output electrode to be turned on and off.

[0103] The first input electrode is electrically connected to an external power source, such as a 24V power supply obtained through processing. The first output electrode is electrically connected to a corresponding filling device (such as an air compressor) or cooling fan to control the start and stop of the air compressor or cooling fan. The first drive electrode is electrically connected to the control unit to receive start and stop signals from the control unit. The first drive electrode can be directly or indirectly connected to the control unit, for example, through a second switching transistor. The second input electrode is electrically connected to an external power source via a bias resistor R17; the second output electrode is grounded; and the second drive electrode is electrically connected to the control unit.

[0104] Specifically, the second switching transistor can be, for example, a transistor Q4, and the first switching transistor can be, for example, a field-effect transistor Q2. The second driver is the base of transistor Q4, the second input is the collector of transistor Q4, and the second output is the emitter of transistor Q4. The first driver is the gate (G) of field-effect transistor Q2, the first input is the source (S), and the first output is the drain (D). After the second driver receives a start signal, the second input and the second output are turned on, the voltage of the second input drops, triggering the first driver, which in turn turns on the first input and the second output, enabling the external power supply to power the subsequent circuitry.

[0105] The external power supply can handle 24V DC power. The drain (D) is connected to the corresponding air compressor or cooling fan via a board connector (B2B-XH-A). The board connector has an input terminal (pin 2) and an output terminal (pin 1). A resettable fuse F5 is electrically connected between the drain (D) and the injection device, specifically between the drain (D) and the input terminal of the board connector, to prevent risks caused by overload or short circuit. The output terminal (pin 1) is grounded. The air compressor or cooling fan can be configured with an independent switching circuit, and the control unit outputs start / stop signals to the corresponding switching circuit. The field-effect transistor Q2 can be, for example, a P-type MOSFET of model SM4405PPL. When the field-effect transistor Q2 is turned on, the external power supply powers the subsequent circuits.

[0106] For example, the transistor Q4 can be an SS8050 model. It operates in saturation or cutoff state in the circuit and is used to receive high and low level signals from the control unit. After the base of transistor Q4 receives the start signal, the MOSFET is turned on.

[0107] The switching circuit also includes an energy storage device, a first current limiting element, a second current limiting element, and a third current limiting element. The first terminal of the energy storage device is electrically connected between an external power supply and the first input electrode (source). The first current limiting element is connected in parallel with the energy storage device to prevent false triggering due to increased charge accumulation. One end of the second current limiting element is electrically connected to the second terminal of the first current limiting element, and the other end is electrically connected to the first driving electrode (gate). One end of the third current limiting element is electrically connected to the second terminal of the energy storage device, and the other end is electrically connected to the second input electrode (collector).

[0108] Specifically, the energy storage device is the first capacitor C22, which acts as a soft-start capacitor, allowing the current through the MOSFET Q2 to increase linearly and slowly, preventing transient large currents from impacting the load. The first current-limiting element is the first resistor R18, which divides the voltage to keep the MOSFET Q2 operating below 12V. The second current-limiting element is the second resistor R52, and the third current-limiting element is the third resistor R69. The third Zener diode D14 is electrically connected between the source and gate. As a clamping diode, D14 limits the voltage between the source and gate to within 15V to protect the MOSFET Q2 from breakdown.

[0109] Furthermore, a second capacitor C91 is placed between the base and emitter of transistor Q4. The second capacitor C91 filters out instantaneous spike signals from interference, preventing false triggering of transistor Q4. Between the source and drain of MOSFET Q2, a first Zener diode D41, a fourth resistor R71 connected in series with and in parallel with the first Zener diode D41, and a third capacitor C89 are also placed. The first Zener diode D41 clamps the diode, and an RC snubber circuit protects against overvoltage between the drain and source. A second Zener diode D18 is also electrically connected between the drain of MOSFET Q2 and ground, and a capacitor bank connected in parallel with the second Zener diode D18 is also connected. The second Zener diode D18 discharges the reverse electromotive force generated when the load stops. The capacitor bank includes capacitors C24, C25, C26, C27, and C66. A notification device is also electrically connected between the drain of the field-effect transistor Q2 and ground to indicate the operating status of the electronic device controlled by the switching circuit. The notification device can be, for example, a buzzer or an indicator light LED18. Specifically, the connection between the drain and ground includes a fourth Zener diode D16, a fifth resistor R67, and the notification device, which are connected in series between the two terminals.

[0110] See Figures 1c to 1f The control unit via Figure 1d The switching circuit shown is electrically connected to the power interface on the compressed air pump control motherboard, via... Figure 1e The air pump speed control circuit shown is electrically connected to the adjustment interface on the compressed air pump control mainboard. The switching circuit controls the start and stop of the air compressor pump, and the air compressor pump speed is adjusted via the air pump speed control (DAC) circuit. Figure 1e As shown, the air pump speed control circuit is controlled by the control unit. The air pump speed control circuit includes a digital-to-analog converter module and an operational amplifier module coupled in sequence. After receiving the PWM signal output from the control unit, the digital-to-analog converter module generates an analog voltage with a range of 0–3.3V. The operational amplifier module converts the voltage to 0–5V. The 0–5V analog signal is connected to the board via a B2B-XH-A connector. Figure 1c The compressed air pump mainboard is electrically connected to the air compressor pump, adjusting its speed and gas phase fluid pressure. The operational amplifier circuit can be implemented using the integrated operational amplifier OPA333AIDBVR and its peripheral devices. The operational amplifier has five pins, from 1 to 5, with pin 5 being the power supply terminal. The specific connection method will not be described here.

[0111] Control units, switching circuits, or other peripheral circuits can be integrated into one unit or distributed across multiple circuit boards. To accommodate upgrades to hardware or software, the circuit boards may undergo multiple iterations, with each version featuring a unique identification mark. This identification mark can be a simple physical structure or implemented through circuitry. Furthermore, other mechanical components or consumables can also bear identification marks.

[0112] To simplify identification, in one embodiment, a set of circuit elements can be provided, through which the detectable signal serves as the identification identifier. In another embodiment, replaceable components in the interventional device have circuit elements serving as identification identifiers. These circuit elements include multiple resistors forming a circuit topology, with at least one location within the topology serving as a sampling point. Different components are distinguished based on the electrical signals measured at these sampling points.

[0113] In order to match the identification mark and generate the corresponding electrical signal, at least one position in the circuit topology is connected to a power source. The sampling point is connected to the judgment circuit through the sampling circuit. The power source can be the total power source of the intervention device or it can be configured independently. Taking the main board of the control unit as an example, the power supply terminal of the main board can be used to supply power to the circuit topology, or a battery can be configured separately. The judgment circuit can be implemented by the control unit itself or additionally configured with devices with signal processing capabilities.

[0114] For example, a circuit topology can be constructed using 2 to 5 resistors connected in series, with power supplied at one end. Both sides of each resistor can serve as sampling points. The resistance values ​​of each resistor can be the same or independent, as long as the electrical signals at different sampling points are easily distinguishable. Furthermore, while the external resistance value of the circuit topology remains constant, different versions of the circuit board can be used. In each version, the number and / or resistance values ​​of the resistors included in the circuit topology are not entirely the same. The sampling point results within the circuit topology differ in different versions, without affecting the circuit components in the control device other than the circuit topology itself.

[0115] Taking version A and version B circuit boards as examples, sampling points can be set at different locations. Under the same power supply voltage, the voltage values ​​read from different sampling points will be different, thus distinguishing between different versions of the circuit board and determining whether the circuit board is installed correctly. Figure 1f As shown, the circuit topology is electrically connected between the voltage divider VCC and ground, including resistors R1, R2, and R3 connected in series to ground. Resistors R1 and R2 are configured in a specific ratio. The voltage divider VCC provides different voltages to the sampling circuit. Different voltages detected by the control unit's port represent different versions; for example, a detection result of 1V indicates version 1.0, and a detection result of 1.1V indicates version 1.1. The voltage divider VCC can be, for example, 3.3V, and the sampling circuit can be implemented using an ADC sampling circuit, for example.

[0116] The control unit can perform machine self-tests and corresponding processing based on the sampling results from the sampling circuit. If the control unit is compatible with at least two versions, it will automatically select the appropriate control logic. If the control unit is only compatible with a single version, an alarm will be triggered if the versions are incompatible. It is understood that the control logic and various control parameters are not entirely the same across different versions.

[0117] See Figure 1g and Figure 1h The interventional device simultaneously outputs liquid and gaseous fluids, which are mixed in a certain proportion to produce droplets with diameters of tens of micrometers. During mixing, the output air pressure needs to be kept stable. However, fluctuations in the air pump itself, the air path, and the load can lead to unstable air pressure, caused by factors such as motor overload. This is particularly noticeable when the air pressure output range is wide. The typical air pressure output range is 50 kPa to 200 kPa, specifically 70 kPa to 200 kPa. The control unit controls the air pump speed to regulate the air pressure. A pressure sensor collects the air pressure at the outlet, calculates it against the target air pressure value, and controls the air pump output.

[0118] like Figure 1g As shown, the control unit is located within the control board. It obtains the sampling results from the pressure sensor via an ADC sampling circuit. The pressure sensor is located at the outlet of the air pump. The air pump and the outlet are connected via an air path. The pressure sensor obtains the pressure detection results through this air path connection. The outlet is connected to the consumable via an extension tube. The pressure sensor should be close to the consumable to obtain a more accurate pressure value. The consumable can be understood as an atomizing chip or an interventional catheter.

[0119] In one embodiment, a method for segmented adjustment of gas phase fluid pressure is provided, comprising: dividing the target adjustment of the gas phase fluid pressure into at least two segments, each segment being adjusted using independent PID control parameters. The control parameters may, for example, include an initial voltage value.

[0120] 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.

[0121] See Figure 1h The control process of the interventional device is described in detail. The device includes a display unit, which may also have touch functionality for human-machine interaction with the control unit located on the control panel. During use, the user inputs the target pressure range (e.g., 70 kPa to 200 kPa) through the display unit, and the control unit then activates the interventional device.

[0122] The control unit calls the corresponding control parameters based on a preset threshold. If the threshold is greater than or equal to the threshold, the control unit calls the high-pressure segment PID control parameters, such as the high-pressure segment PID starting voltage value. If the threshold is less than the threshold, the control unit adjusts the low-pressure segment PID control parameters, such as the low-pressure segment starting voltage value. The air pressure sensor periodically samples the data, performs PID calculations based on the corresponding segmented PID control parameters, and adjusts the air pump output through the air pump speed control circuit (output DAC). Periodic sampling is performed, for example, every 100ms. Throughout the control process, a cyclical control flow of "periodic air pressure sensor sampling – PID calculation – air pump output adjustment" is executed.

[0123] In one embodiment, a method for administering medication to treat natural body cavities is provided. An interventional catheter, as described in the embodiments above, is inserted into the lesion site within the bronchus. A fluid containing a therapeutic substance is nebulized through the interventional catheter and delivered to the lesion site. Lesion sites in natural body cavities include the bronchi, lungs, intestines, kidneys, bladder, and blood vessels. Taking lung diseases as an example, lung diseases include sputum buildup, tuberculosis, fungal infections, and tumors. The therapeutic substance can be at least one of expectorants, anti-tuberculosis drugs, anti-fungal infection drugs, or anti-tumor drugs. In specific applications, it can be used, for example, for ICU patients to inhale nebulized expectorants, for tuberculosis patients to inhale nebulized tuberculosis drugs, for inhaled nebulized anti-fungal infection drugs, or for inhaled nebulized anti-tumor drugs, etc. Specifically, for viral pneumonia, which is an inflammation of the respiratory tract or lungs caused by viral infection, several classes of antiviral drugs have been proven effective, with different drugs selected depending on the virus. For example, ribavirin is a broad-spectrum antiviral drug, effective against respiratory syncytial virus, adenovirus, parainfluenza virus, and influenza virus. Acyclovir is also characterized by its broad-spectrum, potent, and rapid onset of action. It is clinically used for herpesvirus and varicella virus, and should be used as early as possible, especially for people with immunodeficiency or those using immunosuppressants.

[0124] Ganciclovir is an acyclovir drug that inhibits DNA synthesis and is mainly used to treat macrophage viruses. Oseltamivir is a neuraminidase inhibitor and is very effective against influenza A and B. Vidarabine adenosine is a purine glycoside compound with broad-spectrum antiviral activity and is mainly used to treat herpesvirus and varicella-zoster virus infections in immunocompromised patients.

[0125] Amantadine also has the effect of preventing viruses from entering human cells and reducing fever; it is mainly used for influenza virus infections. Many other antiviral drugs are still unknown, especially since viruses mutate rapidly. Therefore, whenever a viral respiratory illness occurs, it is crucial to actively identify the pathogen and select the appropriate medication.

[0126] See Figure 2 This application also provides a control method for a nebulized drug delivery system. The nebulized drug delivery system is used to atomize a fluid containing a therapeutic substance and deliver it into the bronchi. The control method includes: acquiring the state parameters of the fluid; generating a corresponding control signal based on the state parameters; and driving the perfusion device through the control signal to adjust the fluid supply. When the nebulized drug delivery system is in use, the fluid in the interventional catheter is filled until it reaches the distal end, and then the mixed-flow structure follows the endoscope to deliver it to the lesion. When the system is started, the gas phase fluid flows first, followed by the liquid phase fluid; when the system is shut down, the liquid phase fluid is stopped first, followed by the gas phase fluid, to minimize fluid residue in the interventional catheter.

[0127] Fluids include micron-sized liquid particles, and the state parameters of fluids include the state parameters of micron-sized liquid particles;

[0128] Based on the state parameters of the micron-sized liquid particles, a corresponding control signal is generated. The control signal controls the gas pressure and liquid flow rate input into the interventional catheter by the perfusion device. The sampling device collects the current gas pressure information and liquid flow rate information and feeds it back to the control device. Based on the current gas pressure information and liquid flow rate information, the control device determines whether it is necessary to adjust the gas pressure and / or liquid flow rate input into the interventional catheter by the perfusion device.

[0129] It should be understood that, although Figure 2 The steps in the flowchart are shown sequentially as indicated by the arrows, but these steps are not necessarily executed in the order indicated by the arrows. Unless otherwise specified herein, there is no strict order in which these steps are executed, and they can be performed in other orders. Figure 2 At least some of the steps in the process may include multiple sub-steps or multiple stages. These sub-steps or stages are not necessarily completed at the same time, but can be executed at different times. The execution order of these sub-steps or stages is not necessarily sequential, but can be executed in turn or alternately with other steps or at least some of the sub-steps or stages of other steps.

[0130] In one embodiment, a computer device is provided, which may be a terminal, and its internal structure diagram may be as follows: Figure 3As shown, the computer device includes a processor, memory, network interface, display screen, and input devices connected via a system bus. The processor provides computing and control capabilities. The memory includes non-volatile storage media and internal memory. Non-volatile storage may include read-only memory (ROM), magnetic tape, floppy disk, flash memory, optical storage, high-density embedded non-volatile memory, resistive random access memory (ReRAM), magnetic random access memory (MRAM), ferroelectric random access memory (FRAM), phase change memory (PCM), graphene memory, etc. The non-volatile storage media stores the operating system and computer programs. The internal memory provides an environment for the operation of the operating system and computer programs in the non-volatile storage media. The network interface of the computer device is used for communication with external terminals via a network connection. When the computer program is executed by the processor, it implements a control method for a nebulized drug delivery system. The display screen of the computer device can be an LCD screen or an e-ink screen. The input device of the computer device can be a touch layer covering the display screen, or buttons, trackballs or touchpads set on the casing of the computer device, or external keyboards, touchpads or mice, etc.

[0131] Similarly, this application also discloses a program product and a corresponding storage medium. The program product includes one or more computer instructions that, when executed by a computer, cause the computer to implement a method for controlling a nebulized drug delivery system. When the computer program instructions are loaded and executed on the computer, all or part of the process described in the embodiments of this application is generated. The computer may be a general-purpose computer, a special-purpose computer, a computer network, or other programmable device.

[0132] The aforementioned computer device can be configured in a nebulizer drug delivery system, which is used to atomize a fluid containing a therapeutic substance and output it into the bronchi. The computer device includes a memory and a processor. The memory stores a computer program, and the processor, when executing the computer program, performs the following steps: acquiring fluid state parameters; generating corresponding control signals based on the state parameters; and driving an infusion device through the control signals to adjust the fluid supply. The specific limitations of the steps implemented when the computer program is executed can be found in the above description of the control method for the nebulizer drug delivery system, and will not be repeated here. Those skilled in the art will understand that… Figure 3The structure shown is merely a block diagram of a portion of the structure related to the present application and does not constitute a limitation on the computer device to which the present application is applied. Specific computer devices may include more or fewer components than those shown in the figure, or combine certain components, or have different component arrangements.

[0133] Based on the above description, please refer to the appendix. Figure 4 To be continued Figure 30 In the illustrated embodiment, this application also discloses a gas-liquid two-phase interventional device, which includes: a housing 500, on which a gas connector 501 and a liquid connector 502 are mounted, and a pump chamber 510 is provided at the bottom inside the housing 500; a gas pump 520, installed in the pump chamber 510, wherein multiple gas pumps 520 are connected in parallel and are connected to the gas connector 501 through a main pipe 511; a cooling assembly 530, thermally coupled to the gas pump 520; a syringe 600, including a cylinder 610 installed in the housing 500 and a piston 620 slidably installed in the cylinder 610, the cylinder 610 having an outlet and communicating with the liquid connector 502; and a drive mechanism 700, which is linked to the piston 620 of the syringe 600. The gas-liquid two-phase interventional device of this application can be divided into a gas circuit part and a liquid circuit part, which enter the interventional catheter through the gas connector 501 and the liquid connector 502, respectively. For better understanding of the technical solution of this application, the two parts will be explained separately below.

[0134] First, the structure of the air passage will be explained, please refer to the appendix. Figure 4 To be continued Figure 16 Publicly available interventional devices include:

[0135] 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.

[0136] 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.

[0137] 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;

[0138] Cooling fan 531 is thermally coupled to air pump 520.

[0139] 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.

[0140] The airflow direction of the cooling fan 531 needs to be combined with the airflow duct inside the pump chamber 510. For example, when the heat exchanger 533 is made of a material with a high thermal conductivity, the cooling fan 531 can be selected to blow air to deliver cool 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 then is discharged through the exhaust port 503 at the bottom of the pump chamber 510.

[0141] For example, when the heat exchanger 533 is a thermoelectric cooler, if the cooling fan 531 continues to blow air, it may transfer the heat from the hot end of the thermoelectric cooler to the cold end, resulting in low heat exchange efficiency. In this case, the cooling fan 531 can choose to draw air to remove the hot air from the pump chamber 510. The exhaust port 503 at the bottom of the pump chamber 510 acts as an air inlet. Cold air enters the pump chamber 510 through the negative pressure inside the pump chamber 510 (generated by the suction of the cooling fan 531), exchanges heat with the heat exchanger 533 and / or the pump head heat sink fins of the air pump 520, and is then discharged by the cooling fan 531.

[0142] In addition to using a cooling fan, the air duct can also be established via a pressure relief duct, as described in the embodiments below. In the field of medical devices, the amount of gas used is generally small, but maintaining a high pressure requires the air pump 520 to remain operational, causing inconvenience. In this embodiment, the output airflow of the air pump 520 enters the pressure relief valve 512 via the main pipe 511. The pressure relief valve 512 is connected to at least an output pipe 5121 leading to the air passage connector 501 and a pressure relief duct 5122 leading to the pump chamber 510. Excess gas is discharged through the pressure relief valve 512 using a waste gas bypass method, utilizing the waste gas to cool the air pump 520 without requiring power, thus improving the miniaturization of the device. The airflow from the pressure relief duct 5122 enters the pump chamber 510, creating positive pressure. The hot air inside the pump chamber is discharged through the exhaust port 503 at the bottom of the device and / or the cooling fan 531, carrying away heat. In this embodiment, the cooling fan 531 can either blow air into the pump chamber 510 to help create a positive pressure environment, or it can draw air from the pump chamber 510 to help the gas flow out. The specific choice can be set according to the operating power of the cooling fan 531 and the air delivery volume of the pressure relief duct 5122.

[0143] In this embodiment, a positive pressure is created using a pressure relief duct 5122, and a cooling fan 531 draws in air. The main consideration for this design is that medical pumps used in this field are very small in size and are often treated with sound insulation materials, resulting in a small internal space and narrow air duct within the air pump 520's isolation enclosure. Using an air duct under the axial fan creates a small cross-sectional area air duct with a high flow rate, meeting practical usage requirements and satisfying heat dissipation needs. Furthermore, the airflow strength is related to the pump's operating power, which is related to the pump's heat generation, and therefore exhibits a relatively linear relationship. In actual control, pressure can be detected by the air pressure transmitter 522 to determine whether the output pressure of the air pump 520 meets the standard. Based on the pressure signal, the speed of the motor 702 is adjusted to perform closed-loop control of the pressure. The gas flows through the pressure relief valve 512, and the excess gas is discharged after being silenced at the outlet. A corresponding hose is connected here, and the gas flows into the pressure relief air pipe 5122 through the four-way interface 5123 (or it can be diverted to multiple points depending on the matching degree of the air pump 520 and consumables) and connected to the pump room 510.

[0144] In terms of specific structure, the pressure relief valve 512 can be controlled by elastic elements, such as by using a spring to press the valve, and releasing pressure when the pressure is too high, thus achieving automatic over-control. Alternatively, it can be controlled by an electrically controlled valve to achieve precise control.

[0145] 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:

[0146] 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.

[0147] Dual pumps working separately extend service life: When the working pressure is low, using one pump per operation 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.

[0148] The air pump 520 can be controlled by the air pressure transmitter 522. By controlling the speed of the brushless motor 702 of each air pump 520, the pressure generated by the pump body movement is controlled within a required temperature range, thus extending the service life.

[0149] In this embodiment, the stability of the air circuit operation is effectively improved by optimizing the heat dissipation settings and the control logic optimization of multiple air pumps 520 operating in tandem.

[0150] 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 7 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 fiber 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 even 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).

[0151] In addition, the above problems can be overcome by installing shock absorption devices. (See attached reference) Figure 11 To be continued Figure 15 In the illustrated embodiment, the air pump 520 is connected to the housing 500 via a secondary vibration damping device 514, which includes:

[0152] Several first buffer blocks 5141 are disposed on the housing 500;

[0153] The primary shock absorption platform 5142 is supported by each first buffer block 5141;

[0154] Several second buffer blocks 5143 are set on the primary shock absorption platform 5142 and connected to the air pump 520.

[0155] The second buffer block 5143 has a lower hardness than the first buffer block 5141, effectively blocking the transmission of vibration between the air pump 520 and the housing 500. For specific structural details, please refer to the attached diagram. Figure 13a The second buffer block 5143 is a thin-walled cylindrical structure, with a first mounting groove 5144 and a second mounting groove 5145 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 spacing between the first mounting groove 5144 and the second mounting groove 5145 is approximately 8 mm, and the wall thickness of the cylindrical portion between the first mounting groove 5144 and the second mounting groove 5145 is approximately 1 mm. In terms of overall shape, 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 vibrations.

[0156] 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.

[0157] 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.

[0158] In the actual product, the first buffer block 5141 can be a cylindrical rubber pad, made of NR, SBR, or CR. Due to the viscoelastic properties of rubber, it has good shock absorption, sound insulation, and cushioning performance. According to tests, it can effectively reduce the vibration transmitted to the housing 500 by 60%. A relatively thick, high-density rubber material is used to fix and support the primary shock absorption platform 5142 and the second buffer block 5143. The second buffer block 5143 adopts a hollow rubber column structure with a wall thickness of approximately 2mm under no-load. In one embodiment, the hardness of the second buffer block 5143 is less than that of the first buffer block 5141, and the spatial movement freedom of the second buffer block 5143 is greater than that of the first buffer block 5141. A softer rubber material is also used to increase flexibility. It is fixed by a slip-fitting method on both sides, with no restriction on the degree of freedom, and can eliminate 80% of the vibration.

[0159] After actual testing, the vibration reduction effect of the secondary damping device 514 in this embodiment can be reduced to 8% of the original effect (40%*20%=8%), and the noise can also be largely eliminated.

[0160] Furthermore, a third buffer block 5001 can be installed at the bottom of the casing 500 to further reduce noise and vibration.

[0161] Reference Appendix Figure 27 To be continued Figure 28As can be seen, in this embodiment, a gas cylinder 523 can also be used to provide a gas source. Compared to the air pump 520 solution, the gas source in this embodiment has less noise and lower energy consumption. The control device can control the air pressure and airflow through a solenoid valve 524. The gas cylinder 523 can be connected to a pressure regulating valve 525 to achieve pressure regulation. At the same time, the control device can detect the amount of gas in the gas cylinder 523, thereby reminding to replace the gas cylinder 523 when the gas content is insufficient. Other settings can refer to the atomizing device with an air pump mentioned above, and will not be repeated here.

[0162] The structural optimization of the air pump 520 and pump chamber 510 is to provide a good working foundation for the operation of the air circuit section. The function of the air circuit section is to provide a stable and reliable air source to work in conjunction with the liquid circuit section. Referring to the embodiment shown in the attached drawings, the housing 500 is also equipped with a liquid circuit connector 502 and a fixing base 701; an adapter 630 is detachably connected to the fixing base 701; the adapter 630 is used to movably insert the barrel 610 of the syringe 600, the syringe 600 includes a barrel 610 and a piston 620 slidably installed in the barrel 610, the barrel 610 has an outlet and communicates with the liquid circuit connector 502; the piston 620 of the syringe 600 is linked to a drive mechanism 700, the liquid fluid output from the liquid circuit connector 502 and the gaseous fluid output from the air circuit connector 501 mix to form a gas-liquid two-phase flow, and the gas-liquid two-phase flow is atomized to achieve drug delivery.

[0163] As described above, this application discloses an interventional device, comprising: a housing 500, on which a gas connector 501 and a liquid connector 502 are mounted, and a pump chamber 510 is provided at the bottom inside the housing 500; a gas pump 520, installed in the pump chamber 510, wherein multiple gas pumps 520 are connected in parallel and are connected to the gas connector 501 through a main pipe 511; a pressure relief valve 512, installed in the main pipe 511, the outlet of the pressure relief valve 512 being connected to the pump chamber 510 through a pipeline; a cooling fan 531, thermally coupled to the gas pump 520; a syringe 600, comprising a cylinder 610 installed in the housing 500 and a piston 620 slidably installed in the cylinder 610, the cylinder 610 having an outlet and being connected to the liquid connector 502; and a drive mechanism 700, which is linked to the piston 620 of the syringe 600.

[0164] Similarly, this application discloses an intervention system, including:

[0165] The device comprises: a housing 500, on which an air connector 501 is mounted; a pump chamber 510 is located at the bottom inside the housing 500; multiple air pumps 520 are installed in the pump chamber 510, and are connected in parallel to the air connector 501 via a main pipe 511; a pressure relief valve 512 is installed on the main pipe 511, and its outlet is connected to the pump chamber 510 via a pipeline; a cooling fan 531 is thermally coupled to the air pumps 520; a syringe 600 includes a cylinder 610 installed inside the housing 500 and a piston 620 slidably installed inside the cylinder 610, the cylinder 610 having an outlet and communicating with a liquid connector 502; and a drive mechanism 700, which is linked to the piston 620 of the syringe 600.

[0166] An 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 proximal end is connected to the gas connection connector and the fluid connection structure. 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, and a microfluidic chip is disposed within the mixing structure. The fluid in the channel is atomized and output after being passed through the microfluidic chip.

[0167] Referring to the embodiment shown in the accompanying drawings, the gas-liquid two-phase flow is used to deliver fluid to the interventional catheter. 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. A mixing structure is provided at the distal end of the tube body. A microfluidic chip is disposed in the mixing structure. The fluid in the channel is atomized by the microfluidic chip and then output.

[0168] The microchannel chip has a distribution structure inside that can act on at least a portion of the fluid.

[0169] The structure of the hydraulic system will be described next, please refer to the appendix. Figure 17 To be continued Figure 26 The disclosed interventional device includes: a housing 500, on which a fluid inlet connector 502 is mounted; a mounting base 701 fixed to the housing 500; an adapter 630 detachably connected to the mounting base 701, wherein an electronic identification component is provided between the adapter 630 and the mounting base 701; a syringe 600, including a barrel 610 movably inserted into the adapter 630 and a piston 620 slidably installed within the barrel 610, the barrel 610 having an outlet and communicating with the fluid inlet connector 502; and a drive mechanism 700 linked to the piston 620 of the syringe 600.

[0170] In this embodiment, the movement of the piston 620 of the syringe 600 is achieved by the movement of the drive mechanism 700, thereby realizing the output of the liquid medium from the liquid circuit connector 502 and realizing the function of the liquid circuit section. Specifically, referring to the embodiment shown in the accompanying drawings, the drive mechanism 700 includes: a motor 702; and a slide 703, which is slidably mounted within the housing 500 driven by the motor 702. The slide 703 interacts with the piston 620 of the syringe 600. The slide 703 improves its own movement accuracy, thereby accurately outputting a preset quantity of liquid medium. Specifically, the motor 702 is linked to a lead screw 704, and the slide 703 is threadedly engaged with the lead screw 704. To further improve the accuracy of the output, the slide 703 abuts against the piston 620 of the syringe 600, and a pressure sensor 7031 for detecting the interaction force is arranged at the abutment location.

[0171] In addition to the pressure sensor 7031, the drive mechanism 700 can also be controlled through stroke detection. (See attached document) Figure 19 To be continued Figure 21 In the illustrated embodiment, a sliding position sensor 707 is provided on one of the slide block 703 and the housing 500, and a sliding trigger 708 adapted to the sliding position sensor 707 is fixed on the other. The control device uses the sliding position sensor 707 to read the position information of the slide block 703. An extreme position sensor 709 is provided on one of the slide block 703 and the housing 500, and an extreme trigger 710 adapted to the extreme position sensor 709 is fixed on the other. The drive mechanism 700 is controlled by the extreme position sensor 709. In a specific product, the slide block 703, the housing 500, and the lead screw 704 constitute a linear module. The sliding position sensor 707 takes the form of a sliding potentiometer and is simultaneously linked to the slide block 703. The stroke of the sliding potentiometer is greater than the maximum working stroke adapted to the nebulizer. Through the information from different sensors, the control device can accurately obtain the relative / absolute position of the slide block 703, thereby calculating the delivery volume of the liquid medium. The specific control logic will be described in detail in the method section below.

[0172] It is not difficult to see that the driving effect of the drive mechanism 700 on the piston 620 depends on the stable installation of the cylinder 610. For the specific installation method, please refer to the appendix. Figure 19 To be continued Figure 21 In the illustrated embodiment, the fixing base 701 is provided with a hinged pressure plate 705, which has an operating state in which it surrounds the fixing base 701 to clamp the adapter 630 and / or the syringe 600 (see attached figure). Figure 21 ) and the corresponding release status (see attached) Figure 20The syringe 600 can be easily installed and removed by the movement of the pressure plate 705. A locking device 706 is provided between the fixed base 701 and the pressure plate 705, which is used to keep the pressure plate 705 in the working state.

[0173] To accommodate syringes 600 of different volumes and dimensions, the syringe 600 is coupled to the fixing base 701 and the pressure plate 705 via an adapter 630. Referring to the embodiment shown in the accompanying drawings, the adapter 630 is sleeve-shaped with a radially protruding limiting part 631 at one end. The limiting part 631 cooperates with the barrel 610 of the syringe 600 to restrict the circumferential movement of the barrel 610. Specifically, the limiting part 631 is an axially protruding protrusion that mates with commonly used clamping parts of the syringe 600, offering high adaptability and accommodating syringes 600 of different sizes. In terms of specific form, referring to the embodiment shown in the accompanying drawings, the adapter 630 has a cylindrical structure, similar to the opening shape adapted to the fixing base 701. In specific products, the adapter 630 can also be a multi-layered structure with inner and outer nesting or upper and lower nesting.

[0174] In addition to adapting to different syringe sizes, adapter 630 can also serve an identification and marking function. (See attached document) Figure 20 To be continued Figure 26 In the illustrated embodiment, the adapter 630 is provided with an adapter identification tag 632, and the mounting base 701 is provided with an adapter identification circuit 7011 adapted to the adapter identification tag 632. The adapter identification circuit 7011 determines the parameters of the syringe 600 or uploads a data packet containing the parameters of the syringe 600 by reading the adapter identification tag 632. Referring to the embodiment shown in the accompanying drawings, the adapter identification circuit 7011 is disposed inside the mounting base 701, and the adapter identification circuit 7011 and the adapter identification tag 632 complete the identification without contact through the mounting base 701. Therefore, the installation of the cylinder to the corresponding position via the adapter in this embodiment refers to the relative position of the adapter identification circuit 7011 and the adapter identification tag 632 being aligned. In a specific product, the adapter identification circuit 7011 is an antenna and antenna PCB board disposed on the side of the mounting base 701 facing away from the adapter 630, and the adapter identification tag 632 is a ring-shaped circuit sleeved on the adapter 630. During the assembly of the aforementioned adapter identification circuit 7011 and adapter identification tag 632, the adapter identification tag 632 and the adapter 630 are in a transitional fit, forming a single unit. When the adapter 630 is engaged with the mounting base 701, especially when the pressure plate 705 and the mounting base 701 enclose the adapter 630, elastic materials such as EVA or rubber and plastic can be used to ensure that the pressure plate 705 does not damage the adapter 630 after closing. The locking mechanism can be implemented using a mechanical structure or an electronic control structure, or it can be simply locked and closed using bolts or other methods.

[0175] During the identification process of the above-mentioned adapter identification circuit 7011 and adapter identification tag 632, there are several methods: 1) If the power is off, the adapter identification tag 632 will be automatically detected at the beginning, and the parameters will be adjusted accordingly; 2) If the power is on, the adapter identification tag 632 can be identified by directly operating the screen 800; 3) If the parameters have been set, press the start button to perform an automatic check, adjust the corresponding parameters, and then automatically run the subsequent operations. After identifying syringe 600, the parameters need to be adjusted, and the corresponding parameters are provided by the corresponding components in a closed-loop feedback: 1) Liquid pressure is measured and monitored by pressure sensor 7031; 2) Speed ​​is monitored by sliding potentiometer; 3) Gas pressure is measured by pressure transmitter at the back end and adjusted by air pump 520 through speed, etc. Electronic tags RFID or photoelectric switches can identify different syringes 600. The following is a brief description of the electronic tag identification principle: 1) The electronic tag stores the corresponding information through the circuit board and software; 2) The reader or reader runs on the PCB and the antenna sends a radio frequency signal of a certain frequency; 3) When the electronic tag is within the radio frequency signal range and the antenna sends a radio frequency signal of a certain frequency, it generates an induced current to obtain energy and sends its corresponding information to the reader, thus identifying the corresponding syringe 600; 4) After identifying syringe 600, the corresponding parameters are adjusted and corresponding adjustments are made in the application software.

[0176] Similarly, in addition to the automatic identification of the adapter 630, the technical solution disclosed in this application can also achieve multi-dimensional self-control through the setting of other identification tags. (See attached document.) Figure 9 and attached Figure 16 In the illustrated embodiment, the air pump 520 is provided with an air inlet pipe 521 connecting to the outside of the pump chamber 510. A first filter 5211 is provided on the air inlet pipe 521, and a first filter identification tag is provided on the first filter 5211. The intervention device is provided with a control device, which determines the parameters of the first filter 5211 by reading the first filter identification tag. Referring to the embodiment shown in the accompanying drawings, a second filter 5011 is provided on the air connector 501, and a second filter identification tag is provided on the second filter 5011. The intervention device is provided with a control device, which determines the parameters of the second filter 5011 by reading the second filter identification tag. Through the corresponding identification tag, the control device can identify the status of the filter and record the usage time, thereby controlling the overall replacement cycle of consumables. The specific identification process can be found in the description above and will not be repeated here.

[0177] The optimized design of the liquid circuit section is to provide a good working foundation for its operation. Referring to the embodiment shown in the attached drawings, a gas connection connector 501 is installed on the housing 500, and a pump chamber 510 is located at the bottom inside the housing 500. Multiple air pumps 520 are installed in parallel within the pump chamber 510 and are connected to the gas connection connector 501 via a main pipe 511. A pressure relief valve 512 is installed on the main pipe 511, and the outlet of the pressure relief valve 512 is connected to the pump chamber 510 via a pipeline. A cooling fan 531, thermally coupled to the air pumps 520, is installed on the pump chamber 510. The liquid fluid output from the liquid connection connector 502 and the gas fluid output from the gas connection connector 501 mix to form a gas-liquid two-phase flow, which is then atomized to achieve drug delivery.

[0178] As described above, this application discloses an interventional device, comprising: a housing 500, on which a liquid connector 502 and a gas connector 501 are mounted, and a pump chamber 510 is provided at the bottom inside the housing 500; a mounting base 701 fixed to the housing 500; an adapter 630 detachably connected to the mounting base 701, with mutually cooperating electronic identification components between the adapter 630 and the mounting base 701; a syringe 600, including a barrel 610 movably inserted into the adapter 630 and a piston 620 slidably installed inside the barrel 610, the barrel 610 having an outlet and communicating with the liquid connector 502; a drive mechanism 700 linked with the piston 620 of the syringe 600; a gas pump 520 installed in the pump chamber 510, wherein multiple gas pumps 520 are connected in parallel and are connected to the gas connector 501 through a main pipe 511; and a cooling assembly 530 thermally coupled to the gas pumps 520.

[0179] Similarly, this application discloses an intervention system, including:

[0180] The device comprises: a housing 500, on which a liquid connector 502 and a gas connector 501 are mounted; a pump chamber 510 located at the bottom of the housing 500; a mounting base 701 fixed to the housing 500; an adapter 630 detachably connected to the mounting base 701, with an electronic identification component cooperating between the adapter 630 and the mounting base 701; a syringe 600, including a barrel 610 movably inserted into the adapter 630 and a piston 620 slidably mounted within the barrel 610, the barrel 610 having an outlet and communicating with the liquid connector 502; a drive mechanism 700 linked to the piston 620 of the syringe 600; a gas pump 520 installed within the pump chamber 510, multiple gas pumps 520 connected in parallel and connected to the gas connector 501 via a main pipe 511; and a cooling assembly 530 thermally coupled to the gas pumps 520.

[0181] Interventional catheter, which 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 proximal end is connected to the gas and fluid pathways. The tube body has a channel inside that can deliver fluid from the proximal end to the distal end. The distal end of the tube body is equipped with a mixing structure, and a microfluidic chip is configured inside the mixing structure. The fluid in the channel is atomized by the microfluidic chip and then output.

[0182] Referring to the embodiment shown in the accompanying drawings, the gas-liquid two-phase flow is used to deliver fluid to the interventional catheter. 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. A mixing structure is provided at the distal end of the tube body. A microfluidic chip is disposed in the mixing structure. The fluid in the channel is atomized by the microfluidic chip and then output.

[0183] The microchannel chip has a distribution structure inside that can act on at least a portion of the fluid.

[0184] As can be seen from the above, the gas path and fluid path components of the interventional device disclosed in this application can be implemented separately or in combination, effectively improving the treatment effect. In other aspects, referring to Figure 1, in the embodiment shown in the figure, the interventional device is provided with a control device connected to the drive mechanism 700. The control device is connected to an operation screen 800, which is located on the outside of the housing 500 and is used to input control information and output parameter status.

[0185] Reference Appendix Figure 29 To be continued Figure 30 In the embodiment shown, a shield 801 is installed on the housing 500. The shield 801 can shield the drive mechanism and provide a mounting base for the movable door. The movable door has a closed state that closes the syringe 600 and / or the drive mechanism 700 and a corresponding open state. The intervention device is equipped with a control device connected to the drive mechanism 700. The control device reads the different states of the movable door through sensors and responds according to preset rules.

[0186] The replaceable components in the interventional device are equipped with a set of circuit elements. The signals detected by these circuit elements serve as identification markers. The control device reads the identification markers and responds according to preset rules. The replaceable components in the interventional device have circuit elements that serve as identification markers. These circuit elements include multiple resistors, which form a circuit topology. At least one location in the circuit topology serves as a sampling point. The control device distinguishes different components based on the electrical signals measured at the sampling points.

[0187] Referring to the embodiment shown in the attached drawings, the drive mechanism, except for the motor portion located on the front panel of the housing, is entirely situated on one side of the control panel. This arrangement facilitates syringe installation and observation. The motor of the drive mechanism is located inside the housing, which is advantageous for noise and vibration control. The gas phase components are also located inside the housing, facilitating noise control and tubing arrangement. Overall, the drive mechanism has a figure-7 layout, with the electrodes located at the bottom of the housing. Correspondingly, the gas path is situated within the blank space of the figure-7 layout of the drive mechanism, with the air pump positioned near the electrodes. This arrangement helps lower the center of gravity, increase layout density, and thus control product volume. The gas and liquid connection connectors are close to each other and positioned below the control panel, allowing for centralized operation of the control area and facilitating medical personnel's work.

[0188] As can be easily understood from the above, this application also discloses an interventional system control method, including: step S100, resetting the drive mechanism 700; step S200, pre-perfusing liquid fluid into the interventional catheter under the condition that the syringe 600 is correctly installed; step S300, pre-perfusing gaseous fluid into the interventional catheter; and step S400, driving the liquid fluid and gaseous fluid through the interventional catheter for atomization output according to preset parameters.

[0189] Referring to the embodiments shown in the accompanying drawings, the preset parameters include at least one of the following: liquid fluid type, liquid fluid volume, liquid fluid flow rate, gas fluid type, gas fluid pressure, syringe 600 model, atomization operation time; temperature threshold, pressure threshold, flow rate threshold, and flow velocity threshold for each fluid; and the force threshold between the drive mechanism 700 and the piston 620.

[0190] In one embodiment, the intervention system control method further includes:

[0191] Step S000, hardware fault self-check; determine whether the information of each identification mark and / or sensor is consistent with the input information received by the control device, and if they are inconsistent, issue an alarm or pause the current step.

[0192] Step S000 is performed before step S100. In step S000, it is determined whether the parameters of the syringe 600 in the input information received by the adapter identification mark and the control device are consistent. The slide 703 has a first limit position away from the syringe 600 and a second limit position close to the syringe 600 along its own direction of movement. When the reset drive mechanism 700 is activated, the slide 703 moves towards the first limit position. The movement result can either approach the first limit position or reach the limit position. It is necessary to ensure that there is enough space to install the corresponding model of syringe.

[0193] Liquid-phase fluid pre-perfusion and gas-phase fluid pre-perfusion can be performed simultaneously, or their start times can be slightly different, but the order is not strictly limited. For example, gas-phase fluid can be introduced into the interventional catheter first, and liquid-phase fluid can be introduced during this period. Liquid-phase fluid pre-perfusion includes: driving piston 620 and monitoring the force between drive mechanism 700 and piston 620 in real time until the force reaches a threshold. The threshold force is 200N. In the initial stage of movement, drive mechanism 700 (slide 703) has not yet made contact with piston 620 or does not have sufficient pre-tightening force, so the force value obtained by the thrust detector is zero or in a low value range.

[0194] When the drive mechanism 700 and piston 620 start to work, the force value increases. During this process, the liquid fluid is gradually injected into the corresponding flow channel in the interventional catheter. However, due to the resistance changes at different positions in the flow channel, the force value is not stable. When the injection is complete, the resistance is basically stable and the force value no longer changes significantly. At this time, it can be regarded as the pre-injection is completed. The monitoring of this change process can be applied to gaseous fluid pre-injection.

[0195] Of course, since the space inside the interventional catheter is limited, the duration of pre-perfusion can be used to determine whether the procedure is complete, or the duration of pre-perfusion can be combined with changes in fluid pressure for mutual verification.

[0196] Liquid-phase fluids allow for more precise measurement, thus the completion of pre-injection can be determined solely by or in conjunction with the amount of liquid consumed. Gas-phase fluid pre-injection includes: activating the air pump 520 to input gas-phase fluid until the time and / or pressure meet preset values. The preset time value is preferably 1 to 5 minutes, and the preset pressure value can refer to the gas-phase fluid pressure values ​​mentioned below, or is preferably 0.1 MPa to 0.7 MPa.

[0197] Step S400 initiates atomization. To stabilize output and ensure atomization effect, closed-loop control can be employed. For example, step S400 further includes: step S410, acquiring the current state parameters of the fluid; step S420, generating corresponding control signals based on the state parameters; and step S430, driving the injection device through the control signals to regulate the fluid supply (e.g., adjusting pressure, flow rate, etc.). The liquid-phase fluid carries micron-sized particles, with particle sizes ranging from 20 to 100 micrometers.

[0198] Referring to the embodiment shown in the accompanying drawings, the current state parameters of the fluid in step S410 may include:

[0199] Liquid flow rate or pressure (e.g., the flow rate threshold is set to 3 ml / min, and the pressure threshold is set to 0.4 MPa; the threshold can also be a numerical range).

[0200] Gas phase fluid pressure (e.g., a threshold of 0.2 MPa, or a numerical range).

[0201] In step S420, the control unit acquires the status parameters and compares them with the threshold. If they match or the error is within the permissible range, a corresponding control signal is generated to maintain the status. When any status parameter to be monitored does not match the threshold or deviates from the threshold range, a corresponding control signal is generated for adjustment.

[0202] For liquid fluids, the thrust applied to piston 620 can be changed to increase or decrease the flow rate and pressure accordingly. For gaseous fluids, they can be adjusted by pipeline devices such as pressure reducing valves and regulating valves, or by directly controlling air pump 520. For example, the output of air pump 520 motor 702 can be adjusted by using PWM to increase or decrease the air pressure.

[0203] In specific applications where micron-sized particles are loaded onto liquid-phase fluids, ideal atomization effects can be achieved when the liquid-phase fluid pressure is 0.2–0.76 MPa and the gas-phase fluid pressure is 0.2–0.6 MPa, while also considering both drug delivery efficiency and efficacy.

[0204] In step S400, in order to monitor the progress as a whole, the amount of liquid fluid used can be detected in real time (it can be determined by the stroke of the piston 620 and the model of the syringe 600, for example, the product of the cross-section of the cylinder 610 and the stroke of the piston 620). When the amount used reaches the preset value, step S400 ends.

[0205] In one embodiment, when step S400 ends, the drive mechanism 700 stops running first, and after a delay (e.g., 3 to 10 seconds), the air pump 520 stops running, which can minimize the residue of fluid in the interventional catheter and reduce the waste of therapeutic substances in the liquid phase.

[0206] Similarly, in one embodiment, a nebulization method is provided, comprising: introducing a fluid into an interventional catheter and nebulizing it through the interventional catheter before outputting it, wherein the fluid includes a liquid phase fluid and a gas phase fluid, and at least one of the liquid phase fluid and the gas phase fluid carries a therapeutic substance; during the nebulization process, acquiring the current state parameters of the fluid and generating a corresponding control signal based on the state parameters; and adjusting the fluid supply accordingly through the control signal.

[0207] In another embodiment, a method for administering medication to a natural body cavity is provided, comprising: providing an interventional catheter having a distal end and a proximal end; extending the distal end of the interventional catheter to a lesion site; introducing fluid into the proximal end of the interventional catheter, the fluid being atomized through the interventional catheter and output to the lesion site, the fluid comprising a liquid phase fluid and a gas phase fluid, and at least one of the liquid phase fluid and the gas phase fluid carrying a therapeutic substance; during atomization, generating a control signal to regulate the fluid supply accordingly; the control signal may be generated by one or more of the following methods in combination: method a, acquiring the current state parameters of the fluid and generating a corresponding control signal based on the state parameters; method b, observing the atomization and medication effects using an endoscope and generating a corresponding control signal. The state parameters mentioned above include at least the pressure of the liquid phase fluid and the pressure of the gas phase fluid. Unless otherwise specified, the pressure in this application refers to a physical quantity related to pressure or having a conversion relationship, and is strictly limited to the physical definition of pressure.

[0208] In another embodiment, a cell spraying method is provided, comprising: providing an interventional catheter having a distal end and a proximal end; extending the distal end of the interventional catheter to a lesion site; introducing a cell-loaded fluid into the proximal end of the interventional catheter, the fluid being atomized via the interventional catheter and output to the lesion site; wherein the cell particle size is 15–120 micrometers, 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. Preferably, the cells are lung pluripotent stem cells and / or mesenchymal stem cells, and the cell content in the liquid phase fluid is 2*102 6 Cells / mL. The volume of liquid fluid used is 10 to 40 mL, and the flow rate of liquid fluid is less than or equal to 4 mL / min. The cell size is 15 to 30 μm, and the droplet size is 15 to 40 μm. The pressure of the gaseous fluid is 0.1 to 0.35 MPa, and the medium of the gaseous fluid is one of the following combinations: air, air and hydrogen, or oxygen.

[0209] In another embodiment, a virus spraying method is provided, comprising: providing an interventional catheter having a distal end and a proximal end; extending the distal end of the interventional catheter to a lesion site; introducing a virus-loaded fluid into the proximal end of the interventional catheter, the fluid being atomized via the interventional catheter and output to the lesion site; wherein the virus particle size is less than 600 nanometers, the pressure of the liquid phase fluid is 0.2–0.76 MPa, and the pressure of the gas phase fluid is 0.2–0.6 MPa. Preferably, 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 mostly 50–350 nanometers, and the droplet size is 20–300 micrometers. In one embodiment, the interventional catheter extends along an endoscopic channel.

[0210] In another embodiment, a method for spraying nanomedicine is provided, comprising: providing an interventional catheter having a distal end and a proximal end; extending the distal end of the interventional catheter to a lesion site; introducing a fluid loaded with nanomedicine into the proximal end of the interventional catheter, the fluid being atomized via the interventional catheter and output to the lesion site; wherein the nanomedicine has a particle size of less than 600 nanometers, the pressure of the liquid phase fluid is 0.2–0.76 MPa, and the pressure of the gas phase fluid is 0.2–0.6 MPa. Preferably, 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 has a particle size of 50–350 nanometers, and the droplet size is 20–300 micrometers. In one embodiment, the interventional catheter extends along an endoscopic channel.

[0211] In the above embodiments, the parameters will be adjusted accordingly depending on the different treatment media. For example, in the treatment of lung cancer, asthma, and chronic obstructive pulmonary disease, specific parameter selections can be found in the table below:

[0212]

[0213]

[0214] The embodiments disclosed in this application also include how to monitor and process abnormal information in real time. In one embodiment, in at least one step of steps S100 to S400, abnormal signals are monitored in real time, and an alarm is triggered or the current step is paused when an abnormal signal occurs.

[0215] Abnormal signals include at least one of the following: the movable door on the housing 500 is open; consumables are not correctly assembled; the number of times or time of consumable use exceeds the threshold, where consumables include at least each filter and interventional catheter; the syringe 600 model does not match the preset parameters; the pressure or temperature of the air pump 520 exceeds the threshold; the resistance of the drive mechanism 700 exceeds the threshold; the piston 620 reaches the limit position; the position of the piston 620 is abnormal, that is, the encoder signal of the motor 702 and the position sensor signal have a large deviation, for example, the position deviation of the piston 620 corresponding to the two reaches 5mm.

[0216] Based on the above functions, the embodiments of this application may also be configured as follows: In one embodiment, an operation screen 800 and / or physical keys are installed on the housing 500, respectively used to send control commands, the control commands including at least:

[0217] A first signal is used to trigger step S100; a second signal is used to trigger step S200; a third signal is used to trigger step S300; a fourth signal is used to trigger step S400; a fifth signal is used to pause step S200 and / or step S300 and / or step S400; a sixth signal is used to resume step S200 and / or step S300 and / or step S400; and a seventh signal is used to terminate any of the above steps.

[0218] In one embodiment, a display screen (or the operation screen 800 mentioned above) is mounted on the housing 500. During the execution of step S400, the display screen virtually displays the progress of step 400. A progress bar or a percentage display can be used.

[0219] Referring to the embodiment shown in the attached figure, the piston 620 stroke L1 is collected in real time, and the piston 620 stroke L2 corresponding to the preset total amount of liquid fluid is calculated. The ratio of L1 to L2 is then converted into the progress of step 400.

[0220] In one embodiment, the interventional device includes a control unit and stores a log file of device operation. A data interface connected to the control unit is mounted on the housing 500 for transmitting the log file. The log file records at least the number of times consumables are used and / or the usage time. The control unit has an independently configured clock circuit that provides clock signals to relevant circuit components. One or more indicator lights are mounted on the housing 500 to indicate the device status in different ways, at least indicating abnormal signals. The indication methods include flashing frequency, color change, brightness, or a combination of these.

[0221] 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 as being within the scope of this specification. When technical features from different embodiments are embodied in the same drawing, it can be considered that the drawing also discloses examples of combinations of the various embodiments involved. The embodiments described above only illustrate several implementation methods of this application, and their descriptions are relatively specific and detailed, but they should not be construed as limiting the scope of the patent application. It should be noted that for those skilled in the art, several modifications and improvements can be made without departing from the concept of this application, and these all fall within the protection scope of this application.

Claims

1. A computer device, characterized in that, The computer device includes a processor, memory, network interface, display screen, and input device connected via a system bus, wherein the processor executes programs to implement the following intervention system control methods: S1, preset target air pressure and at least two sets of PID parameters, and associate each target air pressure with the corresponding PID parameters; S2, the infusion device first provides gaseous fluid to the interventional catheter; 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; S4, the perfusion device then provides liquid fluid to the interventional catheter so that the interventional catheter outputs atomized fluid; 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; S6, repeat step S5 at preset intervals.

2. The computer device according to claim 1, characterized in that, The first real-time air pressure value is less than the second real-time air pressure value.

3. The computer device according to claim 1, characterized in that, At least two voltage values ​​are preset, and each set of PID parameters is associated with the corresponding voltage value. When the control device retrieves the corresponding PID parameter, the control device adjusts the starting voltage value of the infusion device through the voltage value corresponding to the PID parameter.

4. The computer device according to claim 1, characterized in that, Also includes: S7, the perfusion device first stops supplying liquid fluid to the interventional catheter, and then the perfusion device stops supplying gaseous fluid to the interventional catheter.

5. The computer device according to claim 1, characterized in that, The target air pressure is a target air pressure value. The control device determines the magnitude between the second real-time air pressure value and the target air pressure value to select the PID parameters to be retrieved. The target air pressure is a target air pressure range value. The control device determines the target air pressure range value in which the second real-time air pressure value is located to select the PID parameters to be retrieved.

6. An intervention 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, connected to an infusion device, is used to receive fluid and, after atomization, deliver it into the bronchus; A sampling device used to collect fluid state parameters; A control device, connected to the acquisition device, is used to receive status parameters and control the injection device accordingly; The intervention system is used to implement the following intervention system control methods: S1, preset target air pressure and at least two sets of PID parameters, and associate each target air pressure with the corresponding PID parameters; S2, the infusion device first provides gaseous fluid to the interventional catheter; 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; S4, the perfusion device then provides liquid fluid to the interventional catheter so that the interventional catheter outputs atomized fluid; 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; S6, repeat step S5 at preset intervals.

7. The intervention system according to claim 6, characterized in that, The filling device includes a cylinder, a piston, and a drive mechanism; wherein the cylinder is installed in the corresponding position via an adapter, the adapter is provided with an adapter identification tag, and the control device is connected to an adapter identification circuit provided with the adapter identification tag. The adapter identification circuit determines the cylinder parameters by reading the adapter identification tag or uploads a data packet containing the cylinder parameters.

8. The intervention system according to claim 7, characterized in that, The adapter identification circuit and the adapter identification tag complete the identification without contact; the adapter identification circuit includes an antenna PCB board and an antenna connected to the antenna PCB board, and the adapter identification tag is a passive tag sleeved on the adapter.

9. The intervention system according to claim 6, characterized in that, Includes an atomizing device, said atomizing device comprising: chassis; An air pump is located on the housing. The air pump has an air inlet and an air outlet, and the air inlet and the air outlet are respectively connected to the outside of the housing through corresponding pipes. The secondary damping device includes: Several first buffer blocks are disposed inside the housing; The primary shock absorption platform is supported by each first buffer block; Several second buffer blocks are set on the primary shock absorption platform and support the air pump.

10. The intervention system according to claim 6, characterized in that, Includes an atomizing device, said atomizing device comprising: Pump room; An air pump is located in the pump chamber. The air pump has an air inlet and an air outlet, and the air inlet and the air outlet are respectively connected to the outside of the pump chamber through corresponding pipelines. A heat exchanger is located in the pump chamber and thermally coupled to the air pump, with at least a portion of the heat exchanger exposed to the chamber wall of the pump chamber; A cooling fan is located outside the pump chamber and is thermally coupled to the heat exchanger.

11. The intervention system according to claim 6, characterized in that, 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.

12. A program product, characterized in that, The program product contains one or more computer instructions that, when executed by a computer, cause the computer to perform the following intervention system control methods: S1, preset target air pressure and at least two sets of PID parameters, and associate each target air pressure with the corresponding PID parameters; S2, the infusion device first provides gaseous fluid to the interventional catheter; 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; S4, the perfusion device then provides liquid fluid to the interventional catheter so that the interventional catheter outputs atomized fluid; 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; S6, repeat step S5 at preset intervals.

13. A storage medium, characterized in that, The storage medium stores computer-executable instructions, which implement the following intervention system control method: S1, preset target air pressure and at least two sets of PID parameters, and associate each target air pressure with the corresponding PID parameters; S2, the infusion device first provides gaseous fluid to the interventional catheter; 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; S4, the perfusion device then provides liquid fluid to the interventional catheter so that the interventional catheter outputs atomized fluid; 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; S6, repeat step S5 at preset intervals.

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