Ablation system

Abstract

The application provides an ablation system, comprising: a medium storage device for storing liquid medium; a plurality of probes, each of which is provided with an air inlet channel and an air return channel; a liquid inlet module provided with a gas-liquid separation device, the gas-liquid separation device comprising a gas pipeline and a plurality of liquid pipelines, wherein each of the liquid pipelines is respectively in communication or isolation with the air inlet channel of each of the probes; a heat exchange module provided with a heat exchanger, the heat exchanger being in communication with the air return channel to convert the liquid medium conveyed in the air return channel into gaseous medium; and a control module electrically connected with each of the probes and the heat exchange module, the control module acquiring the temperature of each of the probes and controlling the flow Q2 of the gaseous medium flowing out of the heat exchange module. The ablation system of the application greatly reduces the time for the probe temperature to drop to the minimum temperature, and improves the work efficiency.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and more particularly to an ablation system. Background Technology

[0002] The incidence of malignant tumors is increasing year by year, posing a growing threat to human health. Traditional treatment methods such as surgery, radiotherapy, and chemotherapy are becoming increasingly mature, but they inevitably cause varying degrees of damage to normal bodily functions, and the success rate of treatment still needs improvement. With the development of science and technology, especially the advancement of medical imaging technologies such as magnetic resonance imaging and ultrasound imaging, minimally invasive ablation therapy for tumors, particularly cryoablation, has made significant progress and is becoming increasingly popular.

[0003] Currently, cryoablation equipment on the market is mainly based on two principles. One is based on the gas throttling effect, also known as the Joule-Thompson principle: high-pressure, room-temperature gases such as nitrogen and argon expand through throttling, causing a temperature drop and achieving freezing. For this type of refrigeration equipment, the gas flow rate can usually be infinitely adjusted using a proportional valve, thus achieving continuous adjustment of the freezing power. The other type uses a low-temperature refrigerant such as liquid nitrogen, which evaporates and absorbs heat from human tissue. For this type of refrigeration equipment, because it uses a low-temperature freezing medium such as liquid nitrogen, there are currently no proportional valves on the market for use under extremely low temperature conditions, therefore, it is not possible to directly achieve infinitely adjustable freezing power for this type of refrigeration mode.

[0004] Haijiea's authorized patent, "High and Low Temperature Composite Ablation Surgical System" (application number 201922147498.5), discloses a multi-channel refrigeration system based on the principle of cryogenic working fluid refrigeration. In this system, the cryogenic working fluid output from the cold tank is separated into gaseous and liquid working fluids by a phase separator. The gaseous working fluid is discharged outside the system, while the liquid working fluid, after exiting the phase separator, is divided into four paths, each connected to a solenoid valve and then delivered to one of the four cryoablation needle channels. Because the opening and closing of each channel needs to be controlled individually, a cryogenic solenoid valve is installed directly between the phase separator and each probe channel. This means that a large valve block is added between the phase separator and the probe. When the probe is in use, the cryogenic working fluid needs to simultaneously cool the probe, the solenoid valve, and the surrounding pipeline to liquid nitrogen temperature before it can operate. However, the probe volume is much smaller than the cryogenic solenoid valve volume. Therefore, with this structure, the time from system startup to probe cooling to the lowest temperature is greatly extended, reducing working efficiency.

[0005] To address this issue, a precooler was added to the solenoid valve base. The gaseous working fluid flowing from the phase separator is first fed into the precooler before being discharged outside the system, making full use of the cooling capacity of the gaseous working fluid and improving the problem of excessively long cooling time to some extent. However, this improvement also added the precooler structure, which is equivalent to further increasing the volume of the valve block, so it did not fundamentally solve the problem.

[0006] Therefore, there is an urgent need for a multi-channel ablation system with high efficiency. Summary of the Invention

[0007] In view of the above problems, this application provides an ablation system to overcome or at least partially solve the above problems.

[0008] This application provides an ablation system, comprising: a medium storage device for storing a liquid medium; multiple probes, each probe having an inlet channel and a return channel; a liquid inlet module having a gas-liquid separation device, the gas-liquid separation device including a gas pipe and multiple liquid pipes, wherein each liquid pipe is interconnected with or isolated from the inlet channel of each probe; a heat exchange module having a heat exchanger connected to the return channel to convert the liquid medium transported in the return channel into a gas medium; and a control module electrically connected to each probe and the heat exchange module, the control module acquiring the temperature of each probe and controlling the flow rate Q2 of the gas medium flowing out of the heat exchange module.

[0009] Optionally, the ablation system further includes a first type connector and a second type connector, which can be snapped together or detached. When the first type connector and the second type connector are snapped together, each liquid pipe is connected to the air inlet channel of each probe. When the first type connector and the second type connector are detached, the first type connector automatically closes to prevent the liquid medium in the liquid pipe from flowing out.

[0010] Optionally, the first type of connector includes two first pipes, and the second type of connector includes two second pipes. The two first pipes are respectively connected to the liquid pipe and the heat exchanger, and the two second pipes are respectively connected to the air inlet channel and the air return channel of the probe. When the first type of connector and the second type of connector are interlocked, the two first pipes are respectively connected to the two second pipes.

[0011] Optionally, each of the first pipes includes a first pipe segment, a second pipe segment, and a third pipe segment connected in sequence. The inner diameter of the second pipe segment is larger than the inner diameters of the first and third pipe segments. The inner cavity of the second pipe segment is provided with an elastic element and a ball bearing. The elastic element abuts against the end of the second pipe segment. The inner diameter of the third pipe segment is less than the diameter of the ball bearing, which is less than the inner diameter of the second pipe segment. When the first type connector and the second type connector are disassembled, the ball bearing is engaged between the second and third pipe segments. The outer diameter of the first end of each second pipe is smaller than the inner diameter of the third pipe segment, so that when the first type connector and the second type connector are mated, the first end of each second pipe passes through the third pipe segment and enters the second pipe segment, causing the ball bearing to move away from the end of the third pipe segment.

[0012] Optionally, the second pipe has an extension and a first channel, wherein the extension extends radially outward along a first end of the second pipe, and the first channel is formed between the extension and the body of the second pipe.

[0013] Optionally, the heat exchange module further includes a first proportional valve, which is connected to the heat exchanger, and the control module controls the flow rate Q2 of the gas medium via the first proportional valve.

[0014] Optionally, the control module adjusts the flow rate Q2 of the gas medium based on the difference ΔT between the probe temperature T and the target temperature T2, so that the probe temperature T tends to the target temperature T2.

[0015] Optionally, the relationship between the flow rate Q2 of the gas medium and the target temperature T2 roughly conforms to the empirical formula: T2=a1-a2*a3^Q2, where a1, a2, and a3 are constants.

[0016] Optionally, the heat exchanger is connected to both a second proportional valve and the gas pipeline, the second proportional valve being used to control the flow rate of the gas medium from the gas pipeline.

[0017] Optionally, the liquid inlet module further includes a first solenoid valve, which is connected to the gas-liquid separation device. The control module is electrically connected to the first solenoid valve and is used to control the flow of liquid medium in the medium storage device into the gas-liquid separation device.

[0018] Optionally, a liquid medium usage valve is provided between the first solenoid valve and the medium storage device.

[0019] Optionally, the ablation system further includes a rewarming module, which includes a temperature control device and a second solenoid valve connected to the temperature control device. The temperature control device is connected to the air inlet channel of the probe through a pipeline, and a gas medium usage valve is provided between the second solenoid valve and the medium storage device.

[0020] Optionally, the probe also includes a tube, a tip, and a thermocouple wire. The return gas channel circumferentially surrounds the inlet gas channel, and a vacuum layer is formed between the return gas channel and the tube. The thermocouple wire passes through the return gas channel and enters at least a portion of the tip. The thermocouple wire is electrically connected to the control module for transmitting the current temperature T of the probe to the control module.

[0021] Optionally, the gas-liquid separation device includes an inner sleeve and an outer sleeve, with a channel formed between the inner sleeve and the outer sleeve. Several first through holes are distributed at intervals on the wall of the inner sleeve, and a second through hole is provided at the end of the outer sleeve, which is connected to the heat exchanger pipeline.

[0022] Optionally, the end of the gas-liquid separator is provided with several second channels, each of which is connected to the inner sleeve and each of which is connected to the air inlet channel of the probe, and the channel passes through the end of the gas-liquid separator between the several second channels.

[0023] As can be seen from the above technical solutions, the ablation system of this application embodiment uses multiple probes and a gas-liquid separation device with multiple liquid pipes. The liquid pipes of the gas-liquid separation device are directly connected to the gas inlet channel of the probe. After the medium enters the heat exchanger through the return gas channel of the probe, each channel is controlled by the first proportional valve. No valve block is added between the gas-liquid separation device and the probe, which greatly reduces the time for the probe temperature to drop to the lowest temperature and improves the working efficiency.

[0024] Furthermore, existing technologies, due to the inability to continuously control the flow rate of the liquid medium, can only form ice balls of fixed sizes at the tumor site during cryoablation of tumors. The ablation system of this application, however, achieves continuous control of the liquid medium flow rate by completely vaporizing the liquid medium flowing through the probe into room-temperature gas, and employs a first proportional valve. This also enables continuous adjustment of the medium's cooling power and precise control of the probe temperature. Therefore, during cryoablation of tumors, ice balls of different sizes can be formed as needed. For tumors of different sizes, the freezing range can be made consistent with the tumor size by adjusting the flow rate of the liquid medium or the temperature of the probe. On the other hand, for tumors near the edges of vital organs, the cryoablation operation can be performed without damaging these organs by adjusting the flow rate of the liquid medium or the temperature of the probe. Attached Figure Description

[0025] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in the embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings.

[0026] Figure 1 This is a schematic diagram of an embodiment of an ablation system according to this application;

[0027] Figure 2A-2B These are cross-sectional views of the insertion and disassembly states of an embodiment of the first type connector and the second type connector of this application, respectively.

[0028] Figure 2C-2D These are enlarged sectional views of the first type of connector in this application in the detached state and the plugged state, respectively.

[0029] Figures 3A-3B These are cross-sectional views of the insertion and disassembly states of another embodiment of the first type connector and the second type connector of this application, respectively.

[0030] Figure 3C-3D These are cross-sectional views of the first type of connector and plug in this application in the detached state and the plugged state, respectively;

[0031] Figure 4A This is a schematic diagram of the piping connection of the gas-liquid separation device of this application in the ablation system;

[0032] Figure 4B This is an enlarged schematic diagram of the portion of this application that includes the gas-liquid separation device;

[0033] Figure 4C This is a front view of an embodiment of the gas-liquid separation device of this application;

[0034] Figure 4D-4E They are along Figure 4C Cross-sectional views along the AA and BB directions;

[0035] Figure 5 This is a front perspective view of an embodiment of the heat exchange module of this application;

[0036] Figure 6 This is a rear perspective view of an embodiment of the heat exchange module of this application;

[0037] Figure 7 This is a cross-sectional view of an embodiment of the probe of this application.

[0038] Component designation

[0039] 10: Ablation system; 101: Medium storage device; 102: Probe; 1021: Gas inlet channel; 1022: Gas return channel; 103: Liquid inlet module; 1031: Gas-liquid separation device; 1032: Gas pipeline; 1033: Liquid pipeline; 104: Heat exchange module; 1041: Heat exchanger; 105: Control module; 1042: Third interface; 1043: Fourth interface; 1034: First interface; 1035: Second interface; 1044: First proportional... Valve; 1045: Second proportional valve; 1036: First solenoid valve; 106: Reheat module; 1061: Temperature control device; 1062: Second solenoid valve; 1023: Tube body; 1024: Needle tip; 1025: Thermocouple wire; 1026: Vacuum layer; 1037: Inner sleeve; 1038: Outer sleeve; 1039: Through hole; 1131: Pressure sensor interface; 1132: Thermocouple interface; 1046: Exhaust port; 1047: Fan; 1048, 10 49: Flow meter; 21: Type I connector; 210, 210a, 210b: First pipe; 2101, 2103: First end of the first pipe; 2102, 2104: Second end of the first pipe; 201: First pipe section; 202: Second pipe section; 203: Third pipe section; 204: Elastic element; 205: Ball bearing; 221: Elastic snap-fit; 206: Groove; 222: Baffle; 2011: First end of the second pipe section; 2012: [Unclear text - possibly related to the second pipe section] Second end; 220, 220a, 220b: Second pipe; 223, 2230: First end of the second pipe; 2231, 2232: Second end of the second pipe; 224: Extension; 225: Body of the second pipe; 226: First channel; 227: Sealing ring; 300: Plug; 401: Second channel; 1039: First through hole; 402: Second through hole; 403: End of gas-liquid separator; 404: Channel; 22: Second type connector. Detailed Implementation

[0040] To enable those skilled in the art to better understand the technical solutions in the embodiments of this application, the technical solutions in 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 should fall within the protection scope of the embodiments of this application.

[0041] The specific implementation of the embodiments of this application will be further described below with reference to the accompanying drawings.

[0042] See Figures 1 to 7In a specific implementation of this application, an ablation system 10 is provided, comprising: a medium storage device 101 for storing a liquid medium; a plurality of probes 102, each having an inlet channel 1021 and an outlet channel 1022; and a liquid inlet module 103, which includes a gas-liquid separation device 1031, the gas-liquid separation device 1031 including a gas pipe 1032 and a plurality of liquid pipes 1033, wherein each liquid pipe 1033 can be interconnected with or isolated from the inlet channel 1021 of each probe 102. The heat exchange module 104 is provided with a heat exchanger 1041, which is connected to the return gas channel 1022 to convert the liquid medium transported in the return gas channel 1022 into a gas medium; the control module 105 is electrically connected to the probe 102 and the heat exchange module 104 respectively. The control module 105 acquires the temperature of the probe 102 and controls the flow rate Q2 of the gas medium flowing out of the heat exchange module 104 so that the temperature T of the probe 102 tends to the target temperature T2.

[0043] like Figures 2A-2D As shown, in one embodiment, the ablation system 10 further includes a first type connector 21 and a second type connector 22. The first type connector 21 and the second type connector 22 can be snapped together or detached. When the first type connector 21 and the second type connector 22 are snapped together, each of the liquid pipes is connected to the air inlet channel of each of the probes. When the first type connector 21 and the second type connector 22 are detached, the first type connector 21 automatically closes to prevent the liquid medium in the liquid pipe from flowing out.

[0044] The first type connector 21 may be provided with a groove 206, and the second type connector 22 may be provided with an elastic buckle 221. When the first type connector 21 and the second type connector 22 are engaged with each other, the elastic buckle 221 is compressed by the downward pressure of the baffle 222 at the end of the first type connector 21. After that, the elastic buckle 221 enters the groove 206 and returns to the state before compression. Thus, the elastic buckle 221 and the groove 206 are engaged with each other. When it is necessary to separate the first type connector 21 and the second type connector 22, pressure can be applied to the elastic buckle 221 through the groove 206, so that the elastic buckle 221 is compressed and pops out of the groove 206.

[0045] In an optional embodiment, the first type connector 21 includes two first pipes 210, and the second type connector 22 includes two second pipes 220. The first end 2101 of the first pipe 210a is connected to the liquid pipe of the gas-liquid separator 1031, and the first end 2103 of the first pipe 210b is connected to the heat exchanger. The second ends 2102 of the first pipe 210a and the second ends 2104 of the first pipe 210b are respectively used to connect to the first ends 223 of the second pipe 220a and the first ends 2230 of the second pipe 220b. The second end 2231 of the second pipe 220a is connected to the air inlet channel 1021 of the probe 102, and the second end 2232 of the second pipe 220b is connected to the air return channel 1022 of the probe 102. When the first type connector 21 and the second type connector 22 are engaged with each other, the first pipe 210a is connected to the second pipe 220a, and the first pipe 210b is connected to the second pipe 220b. The liquid medium flows from the liquid pipe of the gas-liquid separator 1031 through the first pipe 210a and the second pipe 220a in sequence into the inlet channel of the probe. The liquid medium flowing out from the return channel of the probe then flows through the second pipe 220b and the first pipe 210b in sequence before entering the heat exchanger.

[0046] Each first pipe (210a, 210b) includes a first pipe section 201, a second pipe section 202, and a third pipe section 203 connected in sequence. The inner diameter of the second pipe section 202 is larger than the inner diameters of the first pipe section 201 and the third pipe section 203. The inner cavity of the second pipe section 202 is provided with an elastic element 204 and a ball bearing 205. The elastic element 204 abuts against the first end 2011 of the second pipe section 202, and the ball bearing 205 is close to the second end 2012 of the second pipe section 202. The inner diameter of the third pipe section 203 is less than the diameter of the ball bearing 205 and less than the inner diameter of the second pipe section 202. The elastic element 204 can be a spring. The outer diameter of the first end 223 of each second pipe is smaller than the inner diameter of the third pipe section 203, so that when the first type connector 21 and the second type connector 22 are engaged with each other, the first end (223, 2230) of each second pipe passes through the third pipe section 203 and enters the second pipe section 202. The ball 205 engaged between the second pipe section 202 and the third pipe section 203 is squeezed by the first end (223, 2230) of the second pipe and compresses the elastic element 204, so that the ball 205 moves away from the end of the third pipe section 203.

[0047] The first end 223 of the second pipe may also be provided with an extension 224 extending radially outward along the first end 223 of the second pipe, and a first channel 226 is formed between the extension 224 and the body 225 of the second pipe. When the ball 205 abuts against the first end of the second pipe, the medium can enter the third pipe section 203 from the second pipe section 202 through the first channel 226. The inner wall of the third pipe section 203 may be provided with a sealing ring 227, which can increase the sealing between the first end of the second pipe and the first pipe when the first end of the second pipe is inserted, and prevent the medium from leaking out.

[0048] When the first type connector 21 and the second type connector 22 are disconnected, the first end of the second pipe gradually withdraws from the third pipe section 203. The ball bearing 205 and the elastic element 204 then move towards the third pipe section 203 until the ball bearing 205 is engaged between the second pipe section 202 and the third pipe section 203. This prevents the medium in the second pipe section 202 from flowing into the third pipe section 203, and therefore prevents leakage from the first type connector 21. Thus, when a probe is needed, the first type connector 21 and the second type connector 22 of the probe are engaged. The medium enters the probe's air inlet channel from the liquid pipe via the first type connector 21 and the second type connector 22, returns from the probe's air return channel, and then enters the heat exchanger via the first type connector 21 and the second type connector 22 for vaporization. When the probe is no longer needed, the first type connector 21 and the second type connector 22 are disconnected, and the first type connector 21 of the probe automatically closes.

[0049] like Figures 3A-3D As shown, in another embodiment, the first type connector 21 and the second type connector 22 have a simple plug-in relationship. The first type connector 21 does not have an automatic sealing function. The outer diameter of the second ends (2102, 2104) of the two first pipes (210a, 210b) can be smaller than the inner diameter of the first ends (223, 2230) of the second pipes (220a, 220b). When the first type connector 21 is plugged in with the second type connector 22, the second ends (2102, 2104) of the two first pipes (210a, 210b) are inserted into the first ends (223, 2230) of the second pipes (220a, 220b) to form a tight fit. In this embodiment, when a probe is needed, the first type connector 21 and the second type connector 22 of the probe are plugged in; when the probe is not needed, the first type connector 21 and the second type connector 22 are disconnected, and the first type connector 21 is sealed with a plug 300. The plug 300 has two pipes at one end that mates with the first type connector 21, while the other end is a closed structure, thus preventing the medium from flowing out.

[0050] The medium can be nitrogen, argon, etc. Liquid media are liquid nitrogen, liquid argon, etc., and gaseous media are nitrogen gas, argon gas, etc. The medium storage device 101 can store liquid cryogenic media. The temperature of liquid nitrogen is related to the pressure under equilibrium conditions. For example, when the set working pressure is 1.0 MPa, the corresponding liquid nitrogen temperature is about -169°C.

[0051] like Figures 4A-4B As shown, in one embodiment, the gas-liquid separator may also be equipped with a pressure sensor interface 1131 and a thermocouple interface 1132. The pressure sensor interface 1131 is connected to a pressure sensor, which is electrically connected to the control module 105 for real-time monitoring of the pressure inside the ablation system 10. The thermocouple interface 1132 is connected to a thermocouple, which is electrically connected to the control module 105 for detecting the temperature inside the ablation system 10. The gas-liquid separator may also be equipped with a first interface 1034 and a second interface 1035, which are respectively used to connect the air inlet channel 1021 of the probe 102 and the heat exchanger 1041.

[0052] like Figure 5 and Figure 6 As shown, in one embodiment, the heat exchange module 104 further includes a first proportional valve 1044, which is connected to the heat exchanger 1041. The control module 105 controls the flow rate Q of the gas medium via the first proportional valve 1044. Since the volume ratio of nitrogen to liquid nitrogen is a constant under constant pressure, the flow rate of liquid nitrogen can be continuously adjusted by regulating the flow rate of nitrogen, that is, the flow rate of liquid nitrogen can be continuously adjusted by regulating the flow rate Q of the gas medium via the first proportional valve 1044.

[0053] The heat exchanger 1041 in the heat exchange module 104 is a high-efficiency heat exchanger, which can be a finned heat exchanger, a plate heat exchanger, a shell-and-tube heat exchanger, etc. The heat exchanger 1041 can have at least two independent heat exchange channels, which are respectively connected to the gas pipeline 1032 of the gas-liquid separation device 1031 and the return gas channel 1022 of the probe 102. After sufficient heat exchange in the high-efficiency heat exchanger, the liquid nitrogen flowing out through the return gas channel 1022 of the probe 102 is completely vaporized into room temperature nitrogen gas (>-20℃). Then, the room temperature nitrogen gas flows through the first proportional valve 1044 to control the nitrogen gas flow rate Q2. The first proportional valve 1044 can be a pressure proportional valve or a flow proportional valve.

[0054] In one embodiment, the control module 105 adjusts the flow rate Q2 of the gas medium based on the difference ΔT between the current temperature T of the probe 102 and the target temperature T2 (i.e., ΔT = T - T2), so that the temperature of the probe 102 tends to approach the target temperature T2. In one embodiment, the relationship between the flow rate Q2 of the gas medium and the target temperature T2 roughly conforms to the empirical formula: T2 = a1 - a2 * a3^Q2, where a1, a2, and a3 are constants. An empirical formula refers to a formula summarized based on experience; the relationship between the variables in the formula does not necessarily completely conform to the definition in the formula, but is only an approximate expression. For example, the relationship between Q2 and T2 does not necessarily strictly follow the relationship defined in the above formula.

[0055] One embodiment of this application provides the adjustment process of the ablation system 10:

[0056] First, fully open the first proportional valve 1044 or set it to a higher nitrogen flow rate Q1 until the measured temperature of probe 102 drops to the lowest temperature T1. During this process, the nitrogen flow rate Q1 flowing through the first proportional valve 1044 gradually increases until it stabilizes. Then, adjust the first proportional valve 1044 to a nitrogen flow rate of Q2. According to the empirical formula T2 = a1 - a2 * a3^Q2, if Q2 is kept constant, the temperature T of probe 102 will deviate from T2 and cannot be maintained at a constant T2, i.e., ΔT is not equal to 0℃. Therefore, in order to keep the temperature of probe 102 at T2, i.e., ΔT tends to 0℃, when ΔT is not equal to 0℃, Q2 needs to be controlled so that the temperature T of probe 102 always tends to T2.

[0057] In one embodiment, heat exchanger 1041 is connected to a second proportional valve 1045 and the gas pipeline 1032, respectively. The second proportional valve 1045 is used to control the flow rate of the gas medium from the gas pipeline 1032. After the system pipeline is fully pre-cooled, the nitrogen flow rate output from the gas pipeline 1032 of the gas-liquid separator can be reduced through the second proportional valve 1045, thereby reducing the liquid nitrogen flow rate and minimizing liquid nitrogen waste. Flow meters 1048 and 1049 can be respectively provided on the first proportional valve 1044 and the second proportional valve 1045 to measure the gas flow rate through the first proportional valve 1044 and the second proportional valve 1045, respectively.

[0058] The heat exchanger 1041 may be provided with a third port 1042 and a fourth port 1043, which are used to connect the gas pipe 1032 of the gas-liquid separator 1031 and the return gas channel 1022 of the probe 102, respectively. The heat exchanger 1041 may also be provided with an exhaust port 1046 and a fan 1047, which are used to exhaust the gas medium and dissipate heat, respectively.

[0059] In one embodiment, the liquid inlet module 103 further includes a first solenoid valve 1036, which is connected to the gas-liquid separation device 1031. The control module 105 is electrically connected to the first solenoid valve 1036 and is used to control the flow of liquid medium from the medium storage device 101 into the gas-liquid separation device 1031. A liquid medium usage valve, such as a liquid nitrogen usage valve, may be provided between the medium storage device 101 and the first solenoid valve 1036 to control the release of liquid medium from the medium storage device 101.

[0060] In one embodiment, the ablation system 10 further includes a rewarming module 106, which includes a temperature control device 1061 and a second solenoid valve 1062 connected to the temperature control device 1061. The temperature control device 1061 is connected to the air inlet channel 1021 of the probe 102 via a pipeline. A gas medium usage valve is provided between the second solenoid valve 1062 and the medium storage device 101. After the probe 102 completes cryoablation, the second solenoid valve 1062 can be opened to input heated nitrogen gas, enabling the probe 102 to quickly return to room temperature.

[0061] like Figures 4A-4E As shown, the gas-liquid separation device 1031 includes an inner sleeve 1037 and an outer sleeve 1038, forming a channel 404 between the inner sleeve 1037 and the outer sleeve 1038. Several first through holes 1039 are spaced apart on the wall of the inner sleeve 1037. A second through hole 402 is provided at the end of the outer sleeve 1038, and this second through hole 402 is connected to the piping of the heat exchanger 1041. The inner sleeve 1037 is used to supply the flow of liquid medium. After passing through the first through holes 1039, the liquid medium becomes gas and flows in the outer sleeve 1038, then flows out through the second through hole 402, and finally flows into the heat exchanger 1041. The end 403 of the gas-liquid separator 1031 is provided with several second channels 401. Each second channel 401 is connected to the inner sleeve 1037. The channel 404 passes through the end 403 of the gas-liquid separator 1031 between the several second channels 401. The gas medium flows in the channel of the outer sleeve 1038, passes through the end 403 of the gas-liquid separator 1031, and flows out through the second through hole 402 after being collected.

[0062] like Figure 7As shown, in one embodiment, the probe 102 is further provided with a tube body 1023, a needle tip 1024, and a thermocouple wire 1025. The return gas channel 1022 surrounds the inlet gas channel 1021 circumferentially. A vacuum layer 1026 is formed between the return gas channel 1022 and the tube body 1023. The thermocouple wire 1025 passes through the return gas channel 1022 and enters at least a portion of the needle tip 1024. The thermocouple wire 1025 entering the needle tip 1024 can be covered by a rigid material such as stainless steel. The other end of the thermocouple wire 1025 is electrically connected to the control module for transmitting the current temperature T of the probe 102 to the control module.

[0063] As can be seen from the above technical solutions, the ablation system of this application embodiment uses multiple probes and a gas-liquid separation device with multiple liquid pipes. The liquid pipes of the gas-liquid separation device are directly connected to the gas inlet channel of the probe. After the medium enters the heat exchanger through the return gas channel of the probe, each channel is controlled by the first proportional valve. No valve block is added between the gas-liquid separation device and the probe, which greatly reduces the time for the probe temperature to drop to the lowest temperature and improves the working efficiency.

[0064] Furthermore, existing technologies, due to their inability to continuously control the flow rate of the liquid medium, can only form ice balls of fixed sizes at the tumor site during cryoablation of tumors in patients. However, the ablation system 10 of this application, by completely vaporizing the liquid medium flowing through the probe 102 into room-temperature gas, uses a first proportional valve 1044 to achieve continuous control of the liquid medium flow rate. Simultaneously, it achieves continuous adjustment of the medium's cooling power and precise control of the probe 102's temperature. Therefore, during cryoablation of tumors in patients, ice balls of different sizes can be formed as needed. Thus, for tumors of different sizes, the freezing range can be made consistent with the tumor size by adjusting the flow rate of the liquid medium or the temperature of the probe 102. On the other hand, for tumors near the edges of vital organs, the cryoablation operation can also be performed without damaging vital organs by adjusting the flow rate of the liquid medium or the temperature of the probe 102.

[0065] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the embodiments of this application, and are not intended to limit them; although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the foregoing embodiments, or make equivalent substitutions for some of the technical features; and these modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this application.

Claims

1. An ablation system (10), characterized in that, The ablation system (10) includes: Medium storage device (101) for storing liquid medium; Multiple probes (102), each of which is provided with an air inlet channel (1021) and an air return channel (1022). The liquid inlet module (103) is provided with a gas-liquid separation device (1031), which includes a gas pipe (1032) and a plurality of liquid pipes (1033), wherein each of the liquid pipes (1033) can be connected to or isolated from the gas inlet channel (1021) of each probe (102); A heat exchange module (104) is provided with a heat exchanger (1041) which is connected to the return gas channel (1022) to convert the liquid medium transported in the return gas channel (1022) into a gas medium. A control module (105) is electrically connected to each of the probes (102) and the heat exchange module (104). The control module (105) acquires the temperature of each probe (102) and controls the flow rate Q2 of the gas medium flowing out of the heat exchange module (104). The ablation system (10) further includes a first type connector (21) and a second type connector (22). The first type connector (21) and the second type connector (22) can be interlocked or detached. When the first type connector (21) and the second type connector (22) are interlocked, each liquid pipe (1033) is connected to the air inlet channel (1021) of each probe (102). When the first type connector (21) and the second type connector (22) are detached, the first type connector (21) automatically closes to prevent the liquid medium in the liquid pipe (1033) from flowing out. The heat exchange module (104) also includes a first proportional valve (1044), which is connected to the heat exchanger (1041). The control module (105) controls the flow rate Q2 of the gas medium through the first proportional valve (1044).

2. The ablation system according to claim 1, characterized in that, The first type of connector (21) includes two first pipes (210), and the second type of connector (22) includes two second pipes (220). The two first pipes (210) are respectively connected to the liquid pipe (1033) and the heat exchanger (1041), and the two second pipes (220) are respectively connected to the air inlet channel (1021) and the air return channel (1022) of the probe (102). When the first type of connector (21) and the second type of connector (22) are engaged with each other, the two first pipes (210) are respectively connected to the two second pipes (220).

3. The ablation system according to claim 2, characterized in that, Each of the first pipes (210) includes a first pipe segment (201), a second pipe segment (202), and a third pipe segment (203) connected in sequence. The inner diameter of the second pipe segment (202) is larger than the inner diameters of the first pipe segment (201) and the third pipe segment (203). The inner cavity of the second pipe segment (202) is provided with an elastic element (204) and a ball bearing (205). The elastic element (204) abuts against the end of the second pipe segment (202). The inner diameter of the third pipe segment (203) is less than the diameter of the ball bearing (205) and less than the inner diameter of the second pipe segment (202). When the first type connector (21) and the second type connector (22) are disassembled, the ball (205) is engaged between the second pipe section (202) and the third pipe section (203); the outer diameter of the first end of each second pipe (220) is smaller than the inner diameter of the third pipe section (203), so that when the first type connector (21) and the second type connector (22) are connected, the first end of each second pipe (220) passes through the third pipe section (203) and enters the second pipe section (202), so that the ball (205) is away from the end of the third pipe section (203).

4. The ablation system according to claim 2, characterized in that, The second pipe (220) is provided with an extension (224) and a first channel (226), wherein the extension (224) extends radially outward along the first end of the second pipe (220), and the first channel (226) is formed between the extension (224) and the body (225) of the second pipe (220).

5. The ablation system according to claim 1, characterized in that, The control module (105) adjusts the flow rate Q2 of the gas medium according to the difference ΔT between the temperature T of the probe (102) and the target temperature T2, so that the temperature T of the probe (102) tends to the target temperature T2.

6. The ablation system according to claim 4, characterized in that, The gas-liquid separation device (1031) includes an inner sleeve (1037) and an outer sleeve (1038), forming a channel (404) between the inner sleeve (1037) and the outer sleeve (1038). Several first through holes (1039) are distributed at intervals on the wall of the inner sleeve (1037), and a second through hole (402) is provided at the end of the outer sleeve (1038), which is connected to the pipeline of the heat exchanger (1041).

7. The ablation system according to claim 6, characterized in that, The gas-liquid separator (1031) has several second channels (401) at its end. Each second channel (401) is connected to the inner sleeve (1037), and each second channel (401) is connected to the air inlet channel (1021) of the probe (102). The channel (404) passes through the end of the gas-liquid separator (1031) between the several second channels (401).

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