Ultrahigh-speed jet flow skin drug delivery adjusting device

Abstract

The invention discloses an ultra-high-speed jet flow skin drug delivery adjusting device, and relates to the technical field of needleless skin drug delivery, the ultra-high-speed jet flow skin drug delivery adjusting device comprises a device body, an auxiliary mechanism is arranged on the device body, the auxiliary mechanism comprises a rubber pad with a groove, a plurality of cylindrical holes and a miniature air pump, and a filter plate is installed at the air inlet end of the miniature air pump; a multi-way pipe is installed at the air outlet end of the miniature air pump, a hose is installed at each air outlet end of the multi-way pipe, and a plurality of miniature air bags are arranged in a groove of the rubber pad with the groove. By arranging the auxiliary mechanism, local pressure can be compensated in real time, it is ensured that a gapless uniform sealing face is formed between the rubber pad and the skin, and therefore the situations of jet velocity attenuation and direction deviation caused by airflow leakage are avoided, the medicine penetration depth and the coverage range conform to preset parameters, then the administration dosage error is reduced, and the administration efficiency is improved. And the use effect of the ultra-high-speed jet flow skin drug delivery adjusting device is improved.

Description

Technical Field

[0001] This invention relates to the field of needle-free skin drug delivery technology, specifically to an ultra-high-speed jet skin drug delivery adjustment device. Background Technology

[0002] Ultra-high-speed jet transdermal drug delivery, a breakthrough needle-free drug delivery technology, uses pneumatic drive to transform drugs into micron-sized droplets, which then precisely penetrate the skin's stratum corneum barrier in the form of a supersonic jet, directly reaching the target tissue area. This technology eliminates the need for traditional needle puncture, thus avoiding the pain and cross-infection risks of needle pricks at the source, while maximizing the preservation of drug activity. It also enables precise control of drug dosage and penetration depth. In the current trend of medical technology upgrading towards minimally invasive, intelligent, and personalized approaches, ultra-high-speed jet transdermal drug delivery adjustment devices are used to effectively overcome the many limitations of traditional needle injections and meet the differentiated delivery needs of different drugs and patients.

[0003] In existing technologies, when using ultra-high-speed jet skin drug delivery adjustment devices for needle-free drug delivery, the drug delivery end of the device usually needs to be tightly fitted to the user's skin to create the sealed chamber required for the jet. However, the surface of human skin is not absolutely flat, and the curvature and wrinkles of different parts vary greatly. Traditional rubber pads with fixed hardness are difficult to achieve uniform fit over the entire area, which can easily form local gaps and cause air leakage. Air leakage will directly lead to unstable air pressure in the sealed chamber, causing the ultra-high-speed jet velocity to decrease and the direction to deviate. This makes it impossible to accurately achieve the originally preset drug penetration depth and coverage range, thereby greatly increasing the dosage error and making it difficult to achieve the core goal of accurate drug delivery, thus reducing the effectiveness of the ultra-high-speed jet skin drug delivery adjustment device.

[0004] Therefore, we propose an ultra-high-speed jet skin drug delivery adjustment device to solve the problems mentioned in the background art. Summary of the Invention

[0005] The purpose of this invention is to provide an ultra-high-speed jet skin drug delivery adjustment device. By setting an auxiliary mechanism, it can compensate for local pressure in real time, ensuring that the rubber pad and the skin form a uniform sealing surface without gaps. This avoids the situation where the jet velocity decreases or the direction deviates due to airflow leakage, so that the drug penetration depth and coverage range meet the preset parameters, thereby reducing the drug dosage error and improving the use effect of the ultra-high-speed jet skin drug delivery adjustment device, so as to solve the problems mentioned in the background art.

[0006] To achieve the above objectives, the present invention provides the following technical solution: an ultra-high-speed jet skin drug delivery adjustment device, comprising a device body, wherein an auxiliary mechanism is provided on the device body; The auxiliary mechanism includes a grooved rubber pad, multiple cylindrical holes, and a miniature air pump. A filter plate is installed at the air inlet of the miniature air pump, and a multi-port pipe is installed at the air outlet of the miniature air pump. Each outlet of the multi-port pipe is fitted with a flexible hose. Multiple miniature airbags are disposed inside the grooves of the grooved rubber pad, and multiple auxiliary pressure sensors are installed inside the grooves of the grooved rubber pad. The detection end of each auxiliary pressure sensor movably penetrates the inner wall of the grooved rubber pad. A first electric valve is installed at the air inlet of each miniature airbag, and a second electric valve is installed at the air outlet of each miniature airbag. Each flexible hose is movably sleeved inside each cylindrical hole, and the air outlet of each flexible hose is connected to the air inlet of each first electric valve.

[0007] Preferably, the device body includes a housing, a cover is installed at the opening of the housing, a protective cover is rotatably connected to one side corner of the housing, and two hand-tightened bolts are threaded through the surface of the protective cover.

[0008] Preferably, a controller is installed inside one of the recesses of the housing, and the operating end of the controller moves through the inner wall of one of the recesses of the housing. An air compressor, a first heat exchanger and an air tank, a slide base, a perforated bracket, a drug storage pipe and a second heat exchanger are installed inside one of the recesses of the housing.

[0009] Preferably, the first heat exchanger is equipped with pressure-resistant pipes at both the inlet and outlet ends, the gas storage tank is equipped with a connecting pipe at the outlet end, a stepper motor is installed on the top of the slide base, a threaded rod is rotatably sleeved inside the through hole of the perforated bracket, and a sliding block is threadedly sleeved on the outer surface of the threaded rod.

[0010] Preferably, a sealing push rod is movably sleeved inside the drug storage tube, a one-way valve is installed at the liquid inlet end of the drug storage tube, a delivery pipe is installed at both the liquid inlet and liquid outlet ends of the second heat exchanger, a main pressure sensor is installed at the top mounting port of the gas storage tank, and a flow sensor is installed at one of the mounting ports of the delivery pipe.

[0011] Preferably, a Laval nozzle is fixedly inserted through another groove in the housing, a gas throttle valve is installed at the air inlet end of the Laval nozzle, an atomizing nozzle is fixedly inserted through the outer surface of the Laval nozzle, and a mounting bracket is fixedly sleeved on the outer surface of the Laval nozzle.

[0012] Preferably, the threaded end of each of the hand-tightening bolts is threaded to one side of the housing, the pressure-resistant pipe is used to connect the air compressor to the first heat exchanger and the first heat exchanger to the gas storage tank, and the outlet end of the connecting pipe is installed with the inlet end of the gas throttle valve.

[0013] Preferably, the infusion tube is used to connect the drug storage tube to the second heat exchanger, and the second heat exchanger to the atomizing nozzle; the output end of the stepper motor is installed with one end of the threaded rod; and the mounting bracket is installed with the inner wall of another groove in the housing.

[0014] Preferably, the bottom end of the sliding block is slidably connected to the inside of the slide table seat, and one side of the sliding block is fixed to the end face of the sealing push rod away from the drug storage tube. The end of the sealing push rod away from the drug storage tube moves through one side of the perforated bracket.

[0015] Preferably, the miniature air pump is installed inside one of the grooves of the housing, and each of the cylindrical holes is opened in the inner wall of another groove of the housing. The grooved rubber pad is fixed to the output end face of the Laval nozzle on the side near the mounting bracket.

[0016] Compared with the prior art, the beneficial effects of the present invention are: 1. In this invention, by setting an auxiliary mechanism, local pressure can be compensated in real time, ensuring that the rubber pad and the skin form a uniform sealing surface without gaps. This avoids the situation where the jet velocity decreases or the direction deviates due to airflow leakage, so that the drug penetration depth and coverage range meet the preset parameters, thereby reducing the dosage error and improving the performance of the ultra-high speed jet skin drug delivery adjustment device. With the cooperation of the activated micro air pump, filter plate, multi-port pipe, hose and activated first electric valve, the filtered air can be delivered to the inside of the micro airbag. With the cooperation of the gas delivered to the corresponding micro airbag, the micro airbag, the first electric valve, the second electric valve and the auxiliary pressure sensor, the grooved rubber pad can fit tightly to the user's skin.

[0017] 2. In this invention, by setting the device body, the drug solution can be precisely penetrated through the skin stratum corneum barrier in the form of a supersonic jet based on the drug characteristics, drug administration requirements and human physiological conditions, and directly reach the target tissue area, so as to realize the ultra-high speed jet skin drug administration adjustment operation. With the cooperation of the activated stepper motor, perforated bracket, slide base, threaded rod and sliding block, the sealing push rod can be driven to transport the drug solution inside the drug storage tube to the inside of one of the infusion tubes. With the cooperation of the activated air compressor, pressure-resistant tube and external air filter, the inhaled air can be filtered, pressurized and delivered to the inside of the first heat exchanger. Attached Figure Description

[0018] Figure 1 This is a partial perspective view of an ultra-high-speed jet skin drug delivery adjustment device according to the present invention; Figure 2 This is a perspective view of an ultra-high-speed jet skin drug delivery adjustment device according to the present invention; Figure 3This is a partial perspective view of the side angle of an ultra-high-speed jet skin drug delivery adjustment device of the present invention; Figure 4 This is a three-dimensional structural diagram of the housing and cylindrical hole of the ultra-high-speed jet skin drug delivery adjustment device of the present invention; Figure 5 This is a partial structural schematic diagram of an ultra-high-speed jet skin drug delivery adjustment device according to the present invention; Figure 6 This is a top-view perspective view of a high-speed jet skin drug delivery adjustment device according to the present invention. Figure 7 This is a perspective cross-sectional view of the main body of the ultra-high-speed jet skin drug delivery adjustment device of the present invention; Figure 8 This is a perspective view of another angle of the ultra-high-speed jet skin drug delivery adjustment device of the present invention; Figure 9 This is a perspective view of the auxiliary mechanism of an ultra-high-speed jet skin drug delivery adjustment device according to the present invention.

[0019] In the diagram: 1. Device body; 101. Shell; 102. Shell cover; 103. Protective cover; 104. Hand-tightening bolt; 105. Controller; 106. Air compressor; 107. First heat exchanger; 108. Air tank; 109. Pressure-resistant pipe; 110. Connecting pipe; 111. Slide base; 112. Stepper motor; 113. Perforated bracket; 114. Threaded rod; 115. Sliding block; 116. Drug storage pipe; 117. Sealing push rod; 118. One-way valve; 119. Second heat exchanger Heater; 120, Infusion tube; 121, Main pressure sensor; 122, Laval nozzle; 123, Atomizing nozzle; 124, Gas throttle valve; 125, Mounting bracket; 126, Flow sensor; 2, Auxiliary mechanism; 201, Grooved rubber pad; 202, Miniature air pump; 203, Filter plate; 204, Multi-port pipe; 205, Hose; 206, Auxiliary pressure sensor; 207, Miniature airbag; 208, First electric valve; 209, Second electric valve; 210, Cylindrical hole. Detailed Implementation

[0020] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0021] Example 1: Please refer to Figures 1-6 , Figure 8 and Figure 9As shown, the present invention provides a technical solution: an ultra-high speed jet skin drug delivery adjustment device, including a device body 1, and an auxiliary mechanism 2 is provided on the device body 1; The auxiliary mechanism 2 includes a grooved rubber pad 201, multiple cylindrical holes 210, and a miniature air pump 202. A filter plate 203 is installed at the air inlet of the miniature air pump 202, and a multi-port pipe 204 is installed at the air outlet of the miniature air pump 202. Each air outlet of the multi-port pipe 204 is equipped with a flexible hose 205. Multiple miniature airbags 207 are arranged inside the groove of the grooved rubber pad 201. Multiple auxiliary pressure sensors 206 are installed inside the groove of the grooved rubber pad 201, and the detection end of each auxiliary pressure sensor 206 movably penetrates the inner wall of the grooved rubber pad 201. A first electric valve 208 is installed at the air inlet of each miniature airbag 207, and a second electric valve 208 is installed at the air outlet of each miniature airbag 207. 09. Each hose 205 is movably fitted inside each cylindrical hole 210. The air outlet of each hose 205 is installed with the air inlet of each first electric valve 208. The device body 1 includes a housing 101. A protective cover 103 is rotatably connected to one side corner of the housing 101. Two hand-tightened bolts 104 are threaded through the surface of the protective cover 103. A controller 105 is installed inside one of the grooves of the housing 101. A miniature air pump 202 is installed inside one of the grooves of the housing 101. Each cylindrical hole 210 is opened in the inner wall of another groove of the housing 101. The grooved rubber pad 201 is fixed to the output end face of the Laval nozzle 122 on the side near the mounting bracket 125.

[0022] In this embodiment, during use, both hand-tightened bolts 104 are removed, then the protective cover 103 is opened. Next, one side of the grooved rubber pad 201 is placed against the user's skin. Then, each auxiliary pressure sensor 206 is activated via the controller 105. Each activated auxiliary pressure sensor 206 then detects the contact pressure data between the corresponding part of the grooved rubber pad 201 and the skin in real time, and transmits the detected pressure data to the controller 105. The controller 105 compares the received pressure data with a first pressure threshold. When all pressure data are within the first pressure threshold range, it indicates that the grooved rubber pad 201 is in close contact with the skin. When any pressure data is below the first pressure threshold, the controller 105 directly activates the micro air pump 202 and the corresponding first electric valve 208. The activated micro air pump 202 then ventilates the environment. Air is drawn in and filtered through filter plate 203. Then, the filtered air is delivered to the interior of the corresponding micro airbag 207 through multi-port pipe 204, corresponding hose 205, corresponding cylindrical hole 210, and corresponding first electric valve 208. When air is drawn into the interior of the micro airbag 207, the micro airbag 207 will cause the corresponding part of the grooved rubber pad 201 and the first auxiliary pressure sensor 206 to fit more closely to the skin. When the pressure data detected by all auxiliary pressure sensors 206 is within the first pressure threshold range, the controller 105 will shut down the micro air pump 202 and the corresponding first electric valve 208. At the same time, the grooved rubber pad 201 is perfectly adapted to the folds and curvature of the skin surface to form a gapless sealed chamber. When the device body 1 is finished in use, the controller 105 will activate the second electric valve 209 on the corresponding micro airbag 207 to discharge the excess gas inside the corresponding micro airbag 207.

[0023] Example 2: According to Figures 1-8As shown, the device body 1 includes a housing 101, a cover 102 installed at the opening of the housing 101, a protective cover 103 rotatably connected to one corner of the housing 101, and two hand-tightening bolts 104 threaded through the surface of the protective cover 103. A controller 105 is installed inside one of the recesses of the housing 101, and the operating end of the controller 105 moves through the inner wall of one of the recesses of the housing 101. An air compressor 106, a first heat exchanger 107, an air tank 108, a slide base 111, a perforated bracket 113, a drug storage pipe 116, and a second heat exchanger 119 are installed inside one of the recesses of the housing 101. Both the inlet and outlet ends of heat exchanger 107 are equipped with pressure-resistant pipes 109. A connecting pipe 110 is installed at the outlet end of gas storage tank 108. A stepper motor 112 is installed on the top of slide base 111. A threaded rod 114 is rotatably sleeved inside the through hole of perforated bracket 113. A sliding block 115 is threadedly sleeved on the outer surface of threaded rod 114. A sealing push rod 117 is movably sleeved inside drug storage tube 116. A one-way valve 118 is installed at the liquid inlet end of drug storage tube 116. Both the liquid inlet and outlet ends of the second heat exchanger 119 are equipped with infusion pipes 120. A main pressure sensor 121 is installed at the top mounting port of gas storage tank 108. A flow sensor 126 is installed at the mounting port of the infusion tube 120. A Laval nozzle 122 is fixedly inserted through another groove in the housing 101. A gas throttle valve 124 is installed at the air inlet end of the Laval nozzle 122. An atomizing nozzle 123 is fixedly inserted through the outer surface of the Laval nozzle 122. A mounting bracket 125 is fixedly sleeved on the outer surface of the Laval nozzle 122. The threaded end of each hand-tightening bolt 104 is threaded to one side of the housing 101. The pressure-resistant pipe 109 is used to connect the air compressor 106 to the first heat exchanger 107, and the first heat exchanger 107 to the air storage tank 108. The outlet of the connecting pipe 110... The gas end is installed with the gas inlet end of the gas throttle valve 124. The infusion pipe 120 is used to connect the drug storage pipe 116 to the second heat exchanger 119 and the second heat exchanger 119 to the atomizing nozzle 123. The output end of the stepper motor 112 is installed with one end of the threaded rod 114. The mounting bracket 125 is installed with the inner wall of another groove of the housing 101. The bottom end of the sliding block 115 is slidably connected to the inside of the slide table 111, and one side of the sliding block 115 is fixed with the end face of the sealing push rod 117 away from the drug storage pipe 116. The end of the sealing push rod 117 away from the drug storage pipe 116 moves through one side of the perforated bracket 113.

[0024] In this embodiment, when drug administration is required, the air compressor 106, the first heat exchanger 107, and the main pressure sensor 121 are activated via the controller 105. The activated air compressor 106 draws in filtered air from the environment through an air filter and pressurizes it. Then, by activating one pressure-resistant pipe 109, the pressurized high-pressure gas is delivered to the interior of the first heat exchanger 107 for cooling. Next, it is delivered to the interior of the gas storage tank 108 for storage through another pressure-resistant pipe 109. Simultaneously, the activated main pressure sensor 121 monitors the gas pressure data inside the gas storage tank 108 in real time and transmits it to the controller. The controller 105 compares the received pressure data with a pre-set second pressure threshold. When the received pressure data is within the second pressure threshold range, the controller 105 shuts down the air compressor 106, and the air tank 108 enters a pressure-stabilized standby state. Subsequently, the controller 105 directly activates the gas throttle valve 124. At this time, the high-pressure gas inside the air tank 108 is delivered to the Laval nozzle 122 at a suitable speed and flow rate through the connecting pipe 110 and the activated gas throttle valve 124. Simultaneously, the controller 105 directly activates the stepper motor 112 and the flow sensor 126. The stepper motor 112 drives the sliding block 115 to move horizontally via the perforated bracket 113, threaded rod 114, and slide base 111. The horizontally moving sliding block 115 then delivers the medicine inside the storage tube 116 to one of the infusion tubes 120 via the sealing push rod 117. The activated flow sensor 126 detects the flow rate of the medicine passing through it in real time and transmits the flow rate data to the controller 105. The controller 105 compares the received flow rate data with the set target flow rate threshold. When the flow rate data is within the target flow rate threshold range, the controller 105 activates the flow sensor. 05 will directly shut down the stepper motor 112 and the flow sensor 126. At the same time, the medicine delivered to one of the infusion tubes 120 will be directly delivered to the activated second heat exchanger 119 for cooling. After cooling, the medicine will be delivered to the Laval nozzle 122 through another infusion tube 120 and the atomizing nozzle 123. When the high-pressure airflow enters the Laval nozzle 122, it will accelerate to form a supersonic jet. The medicine delivered into the Laval nozzle 122 will be atomized into micron-sized droplets under the drive of the supersonic airflow. The droplets will penetrate the stratum corneum of the skin with the jet and be accurately delivered to the preset target tissue area, thus completing the drug delivery operation.

[0025] The usage method and working principle of this device are as follows: Before use, place the device body 1 in a suitable position and connect the controller 105 to the external power supply. Then, open the cover 102 and deliver an appropriate amount of liquid medicine into the storage tube 116 through the one-way valve 118. Next, connect the external cooling circulation system to the first heat exchanger 107 and the second heat exchanger 119. Then, connect the external air filter to the air compressor 106. Then, return the cover 102 to its original position. Next, open the controller 105 and adjust the target opening threshold, first pressure threshold, second pressure threshold and target flow rate threshold of the gas throttle valve 124 according to the characteristics of the drug, the drug administration requirements and the physiological conditions of the human body. In use, remove both hand-tightened bolts 104, then open the protective cover 103. Next, place one side of the grooved rubber pad 201 against the user's skin. Then, activate each auxiliary pressure sensor 206 via the controller 105. Each activated auxiliary pressure sensor 206 will detect the contact pressure data between the corresponding part of the grooved rubber pad 201 and the skin in real time, and transmit the detected pressure data to the controller 105. The controller 105 will compare the received pressure data with a first pressure threshold. When all pressure data are within the first pressure threshold range, it indicates that the grooved rubber pad 201 is in close contact with the skin. When any pressure data is below the first pressure threshold, the controller 105 will directly activate the micro air pump 202 and the corresponding first electric valve 208. The activated micro air pump 202 will then draw in air from the environment. The air is filtered through a filter plate 203 and then delivered to the interior of the corresponding micro airbag 207 via a multi-port pipe 204, a corresponding hose 205, a corresponding cylindrical hole 210, and a corresponding first electric valve 208. When the micro airbag 207 draws in air, it causes the grooved rubber pad 201 and the first auxiliary pressure sensor 206 to fit more closely to the skin. When the pressure data detected by all auxiliary pressure sensors 206 are within the first pressure threshold range, the controller 105 shuts off the micro air pump 202 and the corresponding first electric valve 208. At the same time, the grooved rubber pad 201 perfectly matches the folds and curvature of the skin surface, forming a gapless sealed chamber. When the device body 1 is finished in use, the controller 105 activates the second electric valve 209 on the corresponding micro airbag 207 to discharge excess gas from inside the corresponding micro airbag 207. During drug administration, the air compressor 106, the first heat exchanger 107, and the main pressure sensor 121 are activated via the controller 105. The activated air compressor 106 draws in filtered air from the environment through an air filter and pressurizes it. Then, through a pressure-resistant pipe 109, the pressurized high-pressure gas is delivered to the interior of the first heat exchanger 107 for cooling. Next, through another pressure-resistant pipe 109, the gas is delivered to the interior of the gas storage tank 108 for storage. Simultaneously, the activated main pressure sensor 121 monitors the gas pressure data inside the gas storage tank 108 in real time and transmits it to the controller 105. The controller 105 compares the received pressure data with a pre-set second pressure threshold. When the received pressure data is within the second pressure threshold range, the controller 105 shuts down the air compressor 106, and the air tank 108 enters a pressure-stabilized standby state. Subsequently, the controller 105 directly activates the gas throttle valve 124. At this time, the high-pressure gas inside the air tank 108 is delivered to the Laval nozzle 122 at an appropriate speed and flow rate through the connecting pipe 110 and the activated gas throttle valve 124. Simultaneously, the controller 105 directly activates the stepper motor 112 and the flow sensor 126. Machine 112 drives sliding block 115 to move horizontally via perforated bracket 113, threaded rod 114, and slide base 111. The horizontally moving sliding block 115 then delivers the medicine from the storage tube 116 to one of the infusion tubes 120 via sealing push rod 117. Activated flow sensor 126 continuously monitors the flow rate of the medicine passing through it and transmits this data to controller 105. Controller 105 compares the received flow rate data with a set target flow rate threshold. When the flow rate is within the target flow rate threshold range, controller 105 will... The stepper motor 112 and flow sensor 126 are directly shut off. At the same time, the medicine delivered to one of the infusion tubes 120 is directly delivered to the activated second heat exchanger 119 for cooling. After cooling, the medicine is delivered to the Laval nozzle 122 through another infusion tube 120 and atomizing nozzle 123. When the high-pressure airflow enters the Laval nozzle 122, it accelerates to form a supersonic jet. The medicine is quantitatively delivered into the Laval nozzle 122 and atomized into micron-sized droplets under the action of the supersonic airflow. The droplets penetrate the stratum corneum of the skin with the jet and are precisely delivered to the preset target tissue area, thus completing the drug delivery operation.

[0026] The wiring diagrams for the controller 105, air compressor 106, first heat exchanger 107, stepper motor 112, second heat exchanger 119, main pressure sensor 121, gas throttle valve 124, flow sensor 126, miniature air pump 202, auxiliary pressure sensor 206, first electric valve 208, and second electric valve 209 in this invention are common knowledge in the field, and their working principles are known technologies. The appropriate model is selected according to actual use. Therefore, the control methods and wiring arrangements for the controller 105, air compressor 106, first heat exchanger 107, stepper motor 112, second heat exchanger 119, main pressure sensor 121, gas throttle valve 124, flow sensor 126, miniature air pump 202, auxiliary pressure sensor 206, first electric valve 208, and second electric valve 209 will not be explained in detail.

[0027] Although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art can still modify the technical solutions described in the foregoing embodiments or make equivalent substitutions for some of the technical features. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the protection scope of the present invention.

Claims

1. A high-speed jet skin drug delivery adjustment device, comprising a device body (1), characterized in that: An auxiliary mechanism (2) is provided on the main body (1) of the device; The auxiliary mechanism (2) includes a grooved rubber pad (201), multiple cylindrical holes (210), and a miniature air pump (202). A filter plate (203) is installed at the air inlet of the miniature air pump (202), and a multi-port pipe (204) is installed at the air outlet of the miniature air pump (202). Each air outlet of the multi-port pipe (204) is equipped with a flexible hose (205). Multiple miniature airbags (207) are disposed inside the groove of the grooved rubber pad (201), and multiple... An auxiliary pressure sensor (206) is provided, and the detection end of each auxiliary pressure sensor (206) is movably inserted through the inner wall of the grooved rubber pad (201). Each micro airbag (207) is equipped with a first electric valve (208) at its air inlet end and a second electric valve (209) at its air outlet end. Each hose (205) is movably sleeved inside each cylindrical hole (210), and the air outlet end of each hose (205) is respectively installed with the air inlet end of each first electric valve (208).

2. The ultra-high-speed jet skin drug delivery adjustment device according to claim 1, characterized in that: The device body (1) includes a housing (101), a cover (102) is installed at the opening of the housing (101), and a protective cover (103) is rotatably connected to one side corner of the housing (101). Two hand-tightened bolts (104) are threaded through the surface of the protective cover (103).

3. The ultra-high-speed jet skin drug delivery adjustment device according to claim 2, characterized in that: A controller (105) is installed inside one of the grooves of the housing (101), and the operating end of the controller (105) moves through the inner wall of one of the grooves of the housing (101). An air compressor (106), a first heat exchanger (107), an air tank (108), a slide base (111), a perforated bracket (113), a medicine storage pipe (116), and a second heat exchanger (119) are installed inside one of the grooves of the housing (101).

4. The ultra-high-speed jet skin drug delivery adjustment device according to claim 3, characterized in that: The first heat exchanger (107) is equipped with pressure-resistant pipes (109) at both the inlet and outlet ends. The gas storage tank (108) is equipped with a connecting pipe (110) at the outlet end. The slide base (111) is equipped with a stepper motor (112) at the top. The perforated bracket (113) has a threaded rod (114) rotatably sleeved inside the through hole. The outer surface of the threaded rod (114) is threaded with a sliding block (115).

5. The ultra-high-speed jet skin drug delivery adjustment device according to claim 4, characterized in that: The inside of the drug storage tube (116) is fitted with a sealing push rod (117). A one-way valve (118) is installed at the liquid inlet end of the drug storage tube (116). Both the liquid inlet and outlet ends of the second heat exchanger (119) are fitted with infusion pipes (120). A main pressure sensor (121) is installed at the top of the gas storage tank (108). A flow sensor (126) is installed at the installation port of one of the infusion pipes (120).

6. The ultra-high-speed jet skin drug delivery adjustment device according to claim 5, characterized in that: A Laval nozzle (122) is fixedly inserted through another groove in the housing (101). A gas throttle valve (124) is installed at the air inlet end of the Laval nozzle (122). An atomizing nozzle (123) is fixedly inserted through the outer surface of the Laval nozzle (122). A mounting bracket (125) is fixedly sleeved on the outer surface of the Laval nozzle (122).

7. The ultra-high-speed jet skin drug delivery adjustment device according to claim 6, characterized in that: The threaded end of each of the hand-tightening bolts (104) is threaded to one side of the housing (101). The pressure-resistant pipe (109) is used to connect the air compressor (106) to the first heat exchanger (107) and the first heat exchanger (107) to the air tank (108). The outlet end of the connecting pipe (110) is installed with the inlet end of the gas throttle valve (124).

8. The ultra-high-speed jet skin drug delivery adjustment device according to claim 6, characterized in that: The infusion tube (120) is used to connect the drug storage tube (116) to the second heat exchanger (119) and the second heat exchanger (119) to the atomizing nozzle (123). The output end of the stepper motor (112) is installed with one end of the threaded rod (114). The mounting bracket (125) is installed with the inner wall of another groove of the housing (101).

9. The ultra-high-speed jet skin drug delivery adjustment device according to claim 5, characterized in that: The bottom end of the sliding block (115) is slidably connected to the inside of the slide base (111), and one side of the sliding block (115) is fixed to the end face of the sealing push rod (117) away from the drug storage tube (116). The end of the sealing push rod (117) away from the drug storage tube (116) moves through one side of the perforated bracket (113).

10. The ultra-high-speed jet skin drug delivery adjustment device according to claim 6, characterized in that: The micro air pump (202) is installed inside one of the grooves of the housing (101), and each of the cylindrical holes (210) is opened on the inner wall of another groove of the housing (101). The grooved rubber pad (201) is fixed to the output end face of the Laval nozzle (122) on the side near the mounting bracket (125).

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