CN115337093A - Ablation system - Google Patents
Ablation system Download PDFInfo
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- CN115337093A CN115337093A CN202211083012.6A CN202211083012A CN115337093A CN 115337093 A CN115337093 A CN 115337093A CN 202211083012 A CN202211083012 A CN 202211083012A CN 115337093 A CN115337093 A CN 115337093A
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
- A61B2018/00577—Ablation
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00696—Controlled or regulated parameters
- A61B2018/00714—Temperature
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00696—Controlled or regulated parameters
- A61B2018/00744—Fluid flow
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00773—Sensed parameters
- A61B2018/00791—Temperature
- A61B2018/00821—Temperature measured by a thermocouple
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00773—Sensed parameters
- A61B2018/00863—Fluid flow
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
- A61B2018/0231—Characteristics of handpieces or probes
- A61B2018/0262—Characteristics of handpieces or probes using a circulating cryogenic fluid
- A61B2018/0268—Characteristics of handpieces or probes using a circulating cryogenic fluid with restriction of flow
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
- A61B2018/0293—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques using an instrument interstitially inserted into the body, e.g. needle
Abstract
The present application provides an ablation system comprising: a medium storage device for storing a liquid medium; the gas detection device comprises a plurality of probes, a gas detection device and a gas control device, wherein each probe is provided with a gas inlet channel and a gas return channel; the liquid inlet module is provided with a gas-liquid separation device, the gas-liquid separation device comprises a gas pipeline and a plurality of liquid pipelines, and each liquid pipeline can be communicated or isolated with the gas inlet channel of each probe; the heat exchange module is provided with a heat exchanger, and the heat exchanger is communicated with the air return channel so as to convert the liquid medium conveyed in the air return channel into a gas medium; and the control module is electrically connected with each probe and the heat exchange module respectively, acquires the temperature of each probe and controls the flow Q2 of the gas medium flowing out of the heat exchange module. The application of the ablation system greatly reduces the time for the temperature of the probe to be lowered to the lowest temperature, and improves the working efficiency.
Description
Technical Field
The embodiment of the application relates to the technical field of medical equipment, in particular to an ablation system.
Background
The incidence of malignant tumors is increasing year by year, and the threat to human health is increasing, and the traditional treatment methods such as surgical operation, radiotherapy, chemotherapy and other technologies are becoming mature, but all of them inevitably cause different degrees of damage to the normal functions of the organism, and the success rate of treatment still needs to be improved. With the development of scientific technology, especially the progress of medical imaging technology such as magnetic resonance imaging, ultrasonic imaging and the like, the minimally invasive ablation treatment of tumors, especially cryoablation, has been developed greatly and is becoming more and more popular.
Cryoablation devices currently on the market are mainly based on two principles, one being based on the gas throttling effect, the joule thompson principle: high-pressure normal-temperature gas such as nitrogen, argon and the like is frozen by temperature reduction after throttling expansion. For this type of refrigeration plant, a stepless regulation of the gas flow, and thus a continuous regulation of the refrigeration power, can usually be achieved by means of a proportional valve. The other type of the device absorbs heat by evaporating a low-temperature refrigerant such as liquid nitrogen to take away heat of human tissues. For the refrigeration equipment of the type, because a low-temperature refrigeration medium such as liquid nitrogen and the like is conveyed, a proportional valve used under the condition of extremely low temperature is not available in the market, and therefore stepless regulation cannot be directly realized on the refrigeration mode.
In Hajiya's granted patent "high low temperature compound ablation operation system" (application number 201922147498.5), a multichannel refrigeration system based on low temperature working medium refrigeration principle is disclosed, in the system, cold working medium output from a cold tank is divided into gaseous working medium and liquid working medium through a phase separator, the gaseous working medium is discharged out of the system, the liquid working medium is divided into four paths after coming out of the phase separator, and the four paths are respectively connected to four electromagnetic valves and then respectively conveyed to 4 cryoablation needle channels. Because the opening and closing of each channel are required to be controlled independently, a low-temperature electromagnetic valve is directly arranged in each phase separator and each probe channel, a large-size valve block is added between the phase separator and the probe, and when the probe is used, the cold working medium is required to cool the probe, the electromagnetic valve and the surrounding pipelines to the temperature of liquid nitrogen at the same time to work. And the volume of the probe is far smaller than that of the low-temperature electromagnetic valve, so that the time from the opening of the system to the lowering of the probe to the lowest temperature is greatly prolonged under the structure, and the working efficiency is reduced.
In order to improve the problem, a precooler is additionally arranged on a base of the electromagnetic valve, gaseous working medium flowing out of a phase separator is firstly input into the precooler and then discharged out of the system, the cold energy of the gaseous working medium is fully utilized, and the problem of overlong cooling time is improved to a certain extent.
Therefore, a need exists for a multi-channel ablation system that operates more efficiently.
Disclosure of Invention
In view of the above, the present application provides an ablation system to overcome the above problems or at least partially solve the above problems.
The present application provides an ablation system, comprising: a medium storage device for storing a liquid medium; the gas detection device comprises a plurality of probes, a gas detection device and a gas control device, wherein each probe is provided with a gas inlet channel and a gas return channel; the liquid inlet module is provided with a gas-liquid separation device, the gas-liquid separation device comprises a gas pipeline and a plurality of liquid pipelines, and each liquid pipeline can be mutually communicated or isolated with the gas inlet channel of each probe; the heat exchange module is provided with a heat exchanger, and the heat exchanger is communicated with the air return channel so as to convert the liquid medium conveyed in the air return channel into a gas medium; and the control module is electrically connected with each probe and the heat exchange module respectively, acquires the temperature of each probe and controls the flow Q2 of the gas medium flowing out of the heat exchange module.
Optionally, the ablation system further comprises a first type joint and a second type joint, the first type joint and the second type joint can be mutually clamped or separated, and when the first type joint and the second type joint are mutually clamped, each liquid pipeline is respectively communicated with the air inlet channel of each probe; when the first type joint and the second type joint are mutually detached, the first type joint is automatically closed to prevent the liquid medium in the liquid pipeline from flowing out.
Optionally, the first type of joint includes two first pipelines, the second type of joint includes two second pipelines, the two first pipelines are respectively connected with the liquid pipeline and the heat exchanger, the two second pipelines are respectively connected with the air inlet channel and the air return channel of the probe, and when the first type of joint and the second type of joint are mutually clamped, the two first pipelines are respectively communicated with the two second pipelines.
Optionally, each of the first pipelines respectively includes a first pipe section, a second pipe section and a third pipe section which are sequentially connected, wherein the inner diameter of the second pipe section is larger than the inner diameters of the first pipe section and the third pipe section, an inner cavity of the second pipe section is provided with an elastic member and a ball, the elastic member abuts against the end portion of the second pipe section, the inner diameter of the third pipe section is smaller than the diameter of the ball and smaller than the inner diameter of the second pipe section, and when the first type joint and the second type joint are detached from each other, the ball is clamped between the second pipe section and the third pipe section; the outer diameter of the first end of each second pipeline is smaller than the inner diameter of the third pipe section, so that when the first type joint and the second type joint are mutually butted, the first end of each second pipeline penetrates through the third pipe section to enter the second pipe section, and the ball is far away from the end part of the third pipe section.
Optionally, the second conduit is provided with an extension portion and a first duct, wherein the extension portion extends radially outward along the first end of the second conduit, and the first duct is formed between the extension portion and the body of the second conduit.
Optionally, the heat exchange module further comprises a first proportional valve, the first proportional valve is connected with the heat exchanger, and the control module controls the flow Q2 of the gas medium through the first proportional valve.
Optionally, the control module adjusts the flow rate Q2 of the gaseous medium according to the difference Δ T between the temperature T of the probe and the target temperature T2, so that the temperature T of the probe approaches the target temperature T2.
Alternatively, the relationship between the flow rate Q2 of the gaseous medium and the target temperature T2 substantially conforms to an empirical formula: t2= a1-a 2a 3^ Q2 where a1, a2, a3 are constants.
Optionally, the heat exchanger is connected to a second proportional valve and the gas conduit, respectively, the second proportional valve being adapted to control the flow of the gaseous medium from the gas conduit.
Optionally, the liquid inlet module further includes a first solenoid valve, the first solenoid valve is connected to the gas-liquid separation device, and the control module is electrically connected to the first solenoid valve and configured to control the liquid medium in the medium storage device to flow into the gas-liquid separation device.
Optionally, a liquid medium usage valve is provided between the first solenoid valve and the medium storage device.
Optionally, the ablation system further comprises 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 communicated with the air inlet channel of the probe through a pipeline, and a gas medium use valve is arranged between the second solenoid valve and the medium storage device.
Optionally, the probe is further provided with a tube body, a needle tip and a thermocouple wire, the air return channel circumferentially surrounds the air inlet channel, a vacuum layer is formed between the air return channel and the tube body, the thermocouple wire penetrates through the air return channel and enters at least one part of the needle tip, and the thermocouple wire is electrically connected with the control module and used for transmitting the current temperature T of the probe to the control module.
Optionally, the gas-liquid separation device includes an inner sleeve and an outer sleeve, a channel is formed between the inner sleeve and the outer sleeve, a plurality of first through holes are distributed at intervals on a tube wall of the inner sleeve, a second through hole is arranged at an end of the outer sleeve, and the second through hole is connected with the heat exchanger pipeline.
Optionally, a plurality of second pore passages are formed in the end portion of the gas-liquid separation device, each of the second pore passages is respectively communicated with the inner sleeve, each of the second pore passages is respectively communicated with the gas inlet channel of the probe, and the channel penetrates through the end portion of the gas-liquid separation device between the plurality of second pore passages.
According to the technical scheme, the ablation system of the embodiment of the application adopts the plurality of probes and the gas-liquid separation device with the plurality of liquid pipelines, the liquid pipelines of the gas-liquid separation device are directly communicated to the gas inlet channel of the probes, and after media enter the heat exchanger through the gas return channel of the probes, each channel is controlled through the first proportional valve, any valve block cannot be added between the gas-liquid separation device and the probes, so that the time for reducing the temperature of the probes to the lowest temperature is greatly reduced, and the working efficiency is improved.
In addition, the prior art can only form ice balls with fixed size at the tumor when the patient is subjected to the cryoablation of the tumor because the flow rate of the liquid medium cannot be continuously controlled. The ablation system of the embodiment of the application adopts the first proportional valve to realize continuous control on the flow of the liquid medium after the liquid medium flowing through the probe is completely gasified to be the normal-temperature gas, and simultaneously realizes continuous adjustment of the medium refrigeration power and accurate control on the temperature of the probe, so that ice balls with different sizes can be formed as required when the patient is subjected to cryoablation of tumors, and therefore, for tumors with different sizes, the freezing range can be consistent with the size of the tumors by adjusting the flow of the liquid medium or the temperature of the probe. On the other hand, in some tumors at the periphery of the important organs, the flow rate of the liquid medium or the temperature of the probe can be adjusted so that the important organs are not damaged by the cryoablation operation.
Drawings
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings needed to be used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments described in the embodiments of the present application, and other drawings can be obtained by those skilled in the art according to the drawings.
FIG. 1 is a schematic view of an embodiment of an ablation system of the present application;
FIGS. 2A-2B are cross-sectional views of an embodiment of a first type fitting and a second type fitting of the present application in a plugged and unplugged state, respectively;
FIGS. 2C-2D are enlarged partial cross-sectional views of a first type of fitting of the present application in a detached condition and in an attached condition, respectively;
FIGS. 3A-3B are cross-sectional views of another embodiment of a first type fitting and a second type fitting of the present application in a plugged and unplugged state, respectively;
3C-3D are cross-sectional views of a first type of fitting of the present application with a bulkhead in a detached state and in an attached state, respectively;
FIG. 4A is a schematic view of the tubing connections of the gas-liquid separation device of the present application in an ablation system;
FIG. 4B is an enlarged schematic view of a portion of the present application including a gas-liquid separation device;
FIG. 4C is a front view of an embodiment of the gas-liquid separation device of the present application;
FIGS. 4D-4E are cross-sectional views taken along the A-A and B-B directions of FIG. 4C, respectively;
FIG. 5 is a front perspective view of one embodiment of a heat exchange module of the present application;
FIG. 6 is a rear perspective view of an embodiment of a heat exchange module of the present application;
FIG. 7 is a cross-sectional view of an embodiment of a probe of the present application.
Element number
10: an ablation system; 101: a media storage device; 102: a probe; 1021: an intake passage; 1022: a return air channel; 103: a liquid inlet module; 1031: a gas-liquid separation device; 1032: a gas conduit; 1033: a liquid conduit; 104: a heat exchange module; 1041: a heat exchanger; 105: a control module; 1042: a third interface; 1043: a fourth interface; 1034: a first interface; 1035: a second interface; 1044: a first proportional valve; 1045: a second proportional valve; 1036: a first solenoid valve; 106: a rewarming module; 1061: a temperature control device; 1062: a second solenoid valve; 1023: a tube body; 1024: a needle tip; 1025: a thermocouple wire; 1026: a vacuum layer; 1037: an inner sleeve; 1038: an outer sleeve; 1039: a through hole; 1131: a pressure sensor interface; 1132: a thermocouple interface; 1046: an exhaust port; 1047: a fan; 1048. 1049: a flow meter; 21: a first type of joint; 210. 210a,210 b: a first pipe; 2101. 2103: a first end of a first conduit; 2102. 2104: a second end of the first conduit; 201: a first tube section; 202: a second tube section; 203: a third tube section; 204: an elastic member; 205: a ball bearing; 221: elastic buckle; 206: a groove; 222: a baffle plate; 2011: a first end of a second tube segment; 2012: a second end of a second tube segment; 220. 220a, 220b: a second conduit; 223. 2230: a first end of a second conduit; 2231. 2232: a second end of the second conduit; 224: an extension portion; 225: a body of a second conduit; 226: a first duct; 227: a seal ring; 300: a plug; 401: a second duct; 1039: a first through hole; 402: a second through hole; 403: an end of the gas-liquid separation device; 404: a channel; 22: a second type of joint.
Detailed Description
In order to make those skilled in the art better understand the technical solutions in the embodiments of the present application, the technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application, and it is obvious that the described embodiments are only a part of the embodiments of the present application, and not all the embodiments. All other embodiments obtained by a person of ordinary skill in the art based on the embodiments in the present application shall fall within the scope of protection of the embodiments in the present application.
The following further describes specific implementations of embodiments of the present application with reference to the drawings of the embodiments of the present application.
Referring to fig. 1-7, in one particular implementation of the present application, an ablation system 10 is provided, comprising: a medium storage device 101 for storing a liquid medium; a plurality of probes 102 provided with an intake passage 1021 and a return passage 1022; a liquid inlet module 103 provided with a gas-liquid separation device 1031, wherein the gas-liquid separation device 1031 comprises a gas pipeline 1032 and a plurality of liquid pipelines 1033, and each liquid pipeline 1033 and the gas inlet passage 1021 of each probe 102 can be communicated or isolated with each other; the heat exchange module 104 is provided with a heat exchanger 1041, and the heat exchanger 1041 is communicated with the air return channel 1022 to convert the liquid medium conveyed in the air return channel 1022 into a gas medium; a control module 105 electrically connected to the probe 102 and the heat exchange module 104, respectively, wherein the control module 105 obtains the temperature of the probe 102 and controls the flow Q2 of the gas medium flowing out from the heat exchange module 104, so that the temperature T of the probe 102 approaches to a target temperature T2.
As shown in fig. 2A-2D, 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 connected or disconnected with each other, and when the first type connector 21 and the second type connector 22 are connected with each other, each liquid conduit is respectively communicated with the air inlet channel of each probe; when the first type joint 21 and the second type joint 22 are detached from each other, the first type joint 21 is automatically closed to prevent the liquid medium in the liquid pipeline from flowing out.
The first type connector 21 may be provided with a groove 206, 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 clamped with each other, the elastic buckle 221 is compressed by a downward pressure of a baffle 222 arranged at an end of the first type connector 21, then the elastic buckle 221 enters the groove 206 and returns to a state before compression, so that the elastic buckle 221 and the groove 206 are clamped with each other, when the first type connector 21 and the second type connector 22 need to be detached from each other, pressure may be applied to the elastic buckle 221 through the groove 206, so that the elastic buckle 221 is compressed and then springs out of the groove 206.
In an alternative embodiment, the first type joint 21 includes two first pipes 210, the second type joint 22 includes two second pipes 220, the first end 2101 of the first pipe 210a communicates with the liquid pipe of the gas-liquid separation device 1031, the first end 2103 of the first pipe 210b communicates with the heat exchanger, the second ends 2102 and 2104 of the first pipe 210a and 210b are respectively used for communicating with the first end 223 and 2230 of the second pipe 220a and 220b, the second end 2231 of the second pipe 220a communicates with the air inlet passage 1021 of the probe 102, and the second end 2232 of the second pipe 220b communicates with the air return passage 1022 of the probe 102. When the first type joint 21 and the second type joint 22 are clamped with each other, the first pipeline 210a is communicated with the second pipeline 220a, the first pipeline 210b is communicated with the second pipeline 220b, and the liquid medium flows from the liquid pipeline of the gas-liquid separation device 1031 through the first pipeline 210a and the second pipeline 220a in sequence and enters the air inlet channel of the probe; the liquid medium flowing out of the return air channel of the probe flows through the second pipe 220b and the first pipe 210b in sequence and then enters the heat exchanger.
Each first pipeline (210a, 210b) comprises a first pipe section 201, a second pipe section 202 and a third pipe section 203 which are connected in sequence, wherein 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 205, the elastic element 204 abuts against a first end 2011 of the second pipe section 202, the ball 205 is close to a second end 2012 of the second pipe section 202, and the inner diameter of the third pipe section 203 < the diameter of the ball 205 < the inner diameter of the second pipe section 202. The elastic member 204 may be a spring, and the outer diameter of the first end 223 of each second pipe is smaller than the inner diameter of the third pipe segment 203, so that when the first type joint 21 and the second type joint 22 are engaged with each other, the first end (223,2230) of each second pipe passes through the third pipe segment 203 and enters the second pipe segment 202, and the balls 205 engaged between the second pipe segment 202 and the third pipe segment 203 are pressed by the first end (223,2230) of the second pipe to compress the elastic member 204, so that the balls 205 are away from the end of the third pipe segment 203.
The first end 223 of the second conduit may further be provided with an extension 224 extending radially outwards of the first end 223 of the second conduit, and a first aperture 226 is formed between the extension 224 and the body 225 of the second conduit, via which first aperture 226 medium may enter the third tube section 203 from the second tube section 202 when the balls 205 abut against the first end of the second conduit. The inner wall of the third pipe segment 203 may be provided with a sealing ring 227 for increasing the sealing property between the first end of the second pipe and the first pipe when the first end of the second pipe is inserted, so as to prevent the medium from leaking out.
When the first type joint 21 and the second type joint 22 are separated from each other, the first end of the second pipeline is gradually withdrawn from the third pipe section 203, the balls 205 and the elastic member 204 move toward the third pipe section 203 until the balls 205 are clamped between the second pipe section 202 and the third pipe section 203, so that the medium in the second pipe section 202 cannot flow into the third pipe section 203, and therefore cannot leak out from the first type joint 21. Therefore, when a certain probe needs to be used, the first type joint 21 and the second type joint 22 of the probe are clamped with each other, a medium enters an air inlet channel of the probe from a liquid pipeline through the first type joint 21 and the second type joint 22, returns from an air return channel of the probe, and enters a heat exchanger through the first type joint 21 and the second type joint 22 to be gasified; when the probe is not required to be used, the first type connector 21 and the second type connector 22 are detached from each other, and the first type connector 21 of the probe is automatically closed.
In another embodiment, as shown in fig. 3A-3D, the first type of fitting 21 and the second type of fitting 22 are in a simple mating relationship, the first type of fitting 21 does not have a self-closing function, the second end (2102, 2104) of the second first tubing (210 a,210 b) can have an outer diameter less than the inner diameter of the first end (223,2230) of the second tubing (220 a, 220 b), and the second end (2102, 2104) of the second first tubing (210 a,210 b) can be inserted into the first end (223,2230) of the second tubing (220 a, 220 b) to form a tight fit when the first type of fitting 21 and the second type of fitting are mated. In this embodiment, when a certain probe needs to be used, the first type connector 21 of the probe is plugged with the second type connector 22; when the probe is not required to be used, the first type connector 21 is detached from the second type connector 22 and the first type connector 21 is closed using the stopper 300. The end of the plug 300, which is in contact with the first type connector 21, has two channels, and the other end is closed, so that the medium can be prevented from flowing out.
The medium can be nitrogen, argon and the like, the liquid medium is correspondingly liquid nitrogen, liquid argon and the like, and the gas medium is correspondingly nitrogen and argon. The medium storage device 101 can store a liquid cryogenic medium, and the liquid nitrogen temperature is related to the pressure in an equilibrium state, for example, when the set working pressure is 1.0Mpa, the corresponding liquid nitrogen temperature is about-169 ℃.
As shown in fig. 4A-4B, in an embodiment, the gas-liquid separator may further include a pressure sensor interface 1131 and a thermocouple interface 1132 disposed thereon, the pressure sensor interface 1131 is connected to a pressure sensor, and the pressure sensor is electrically connected to the control module 105 for monitoring the pressure inside the ablation system 10 in real time; thermocouple interface 1132 connects thermocouples that are electrically connected to control module 105 to detect the temperature inside ablation system 10. The gas-liquid separator may further have a first interface 1034 and a second interface 1035, which are respectively used for communicating the intake passage 1021 of the probe 102 and the heat exchanger 1041.
As shown in fig. 5 and fig. 6, in an embodiment, the heat exchange module 104 further includes a first proportional valve 1044, the first proportional valve 1044 is connected to the heat exchanger 1041, and the control module 105 controls the flow Q of the gas medium through the first proportional valve 1044. Since the volume ratio of the nitrogen gas to the liquid nitrogen is a fixed constant under a constant pressure, the flow rate of the liquid nitrogen can be continuously adjusted by adjusting the flow rate of the nitrogen gas, that is, the flow rate Q of the gas medium can be continuously adjusted by adjusting the first proportional valve 1044.
The heat exchanger 1041 in the heat exchange module 104 is a high-efficiency heat exchanger, and may be a fin heat exchanger, a plate heat exchanger, a shell-and-tube heat exchanger, etc., and the heat exchanger 1041 may be at least provided with two independent heat exchange passages, which are respectively communicated with the gas pipe 1032 of the gas-liquid separation device 1031 and the return gas passage 1022 of the probe 102. After sufficient heat exchange of the high-efficiency heat exchanger, the liquid nitrogen flowing out of the air return channel 1022 of the probe 102 is completely gasified to normal-temperature nitrogen (> -20 ℃), and then the normal-temperature nitrogen flows through the first proportional valve 1044 to control the nitrogen flow Q2, wherein the first proportional valve 1044 can be a pressure proportional valve or a flow proportional valve.
In one embodiment, the control module 105 adjusts the flow rate Q2 of the gaseous medium based on the difference Δ T between the current temperature T of the probe 102 and the target temperature T2 (i.e., Δ T = T-T2) to bring the temperature of the probe 102 toward the target temperature T2. In one embodiment, the relationship between the flow rate Q2 of the gaseous medium and the target temperature T2 is approximately in accordance with the empirical formula: t2= a1-a 2a 3Q 2, wherein a1, a2, a3 are constants. By empirical formula is meant a formula that has been empirically derived, and the relationships between the variables in the formula do not necessarily conform exactly to the definition in the formula, but rather approximate expressions, such as Q2 and T2, do not necessarily conform exactly to the relationship defined in the above formula.
An embodiment of the present application provides for an adjustment process of the ablation system 10:
first, the first proportional valve 1044 is fully opened or under a higher nitrogen flow rate Q1 until the temperature measured by the probe 102 drops to the minimum temperature T1; in this process, the flow rate Q1 of nitrogen gas flowing through the first proportional valve 1044 gradually rises until it stabilizes. Then, the first proportional valve 1044 is adjusted to a nitrogen flow rate of Q2, according to the empirical formula T2= a1-a 2a 3^ Q2, and if Q2 is kept unchanged, the temperature T of the probe 102 deviates from T2, and cannot maintain a constant T2, i.e. Δ T is not equal to 0 ℃. Therefore, in order to maintain the temperature T2 of the probe 102, i.e. Δ T tends to 0 ℃, when Δ T is not equal to 0 ℃, Q2 needs to be controlled so that the temperature T of the probe 102 tends to T2 all the time.
In one embodiment, the heat exchanger 1041 is connected to a second proportional valve 1045 and the gas conduit 1032, respectively, the second proportional valve 1045 being used to control the flow of the gaseous medium from the gas conduit 1032. After the system pipeline is completely precooled, the flow rate of nitrogen output by the gas pipeline 1032 of the gas-liquid separator can be reduced through the second proportional valve 1045, and then the flow rate of liquid nitrogen is reduced, so that waste of liquid nitrogen is reduced. Flow meters 1048, 1049 may be provided on the first proportional valve 1044 and the second proportional valve 1045, respectively, to measure the flow of gas through the first proportional valve 1044 and the second proportional valve 1045, respectively.
The heat exchanger 1041 may be respectively provided with a third interface 1042 and a fourth interface 1043, which are respectively used for communicating a gas conduit 1032 of the gas-liquid separation device 1031 and a return gas passage 1022 of the probe 102. An exhaust outlet 1046 and a fan 1047 may also be provided on the heat exchanger 1041, for exhausting the gaseous medium and dissipating heat, respectively.
In an embodiment, the liquid inlet module 103 further includes a first solenoid valve 1036, the first solenoid valve 1036 is connected to the gas-liquid separation device 1031, and the control module 105 is electrically connected to the first solenoid valve 1036 for controlling the liquid medium in the medium storage device 101 to flow into the gas-liquid separation device 1031. A liquid medium usage valve, for example, a liquid nitrogen usage valve, may be provided between the medium storage device 101 and the first solenoid valve 1036 to control discharge of the liquid medium in the medium storage device 101.
In one embodiment, the ablation system 10 further comprises a rewarming module 106, which includes a temperature control device 1061 and a second solenoid valve 1062 connected to the temperature control device 1061, wherein the temperature control device 1061 is connected to the gas inlet 1021 of the probe 102 through a pipeline, and a gas medium using valve is disposed between the second solenoid valve 1062 and the medium storage device 101. After the probe 102 finishes the cryoablation, the second electromagnetic valve 1062 can be opened, and heated nitrogen is input, so that the probe 102 is quickly restored to the normal temperature.
As shown in fig. 4A to 4E, the gas-liquid separation device 1031 includes an inner tube 1037 and an outer tube 1038, a channel 404 is formed between the inner tube 1037 and the outer tube 1038, a plurality of first through holes 1039 are distributed at intervals on a tube wall of the inner tube 1037, a second through hole 402 is arranged at an end of the outer tube 1038, and the second through hole 402 is connected to a pipeline of the heat exchanger 1041. The inner sleeve 1037 is used for flowing a liquid medium, and the liquid medium turns into a gas after passing through the first through hole 1039, flows in the outer sleeve 1038, flows out through the second through hole 402, and flows into the heat exchanger 1041. The end 403 of the gas-liquid separator 1031 is provided with a plurality of second hole passages 401, each second hole passage 401 is respectively communicated with the inner sleeve 1037, a channel 404 penetrates through the end 403 of the gas-liquid separator 1031 between the plurality of second hole passages 401, and the gas medium flows in the channel of the outer sleeve 1038, passes through the end 403 of the gas-liquid separator 1031, is collected and flows out of the second hole 402.
As shown in fig. 7, in an embodiment, the probe 102 further includes a tube 1023, a tip 1024, and a thermocouple wire 1025, the air return channel 1022 circumferentially surrounds the air inlet channel 1021, a vacuum layer 1026 is formed between the air return channel 1022 and the tube 1023, the thermocouple wire 1025 passes through the air return channel 1022 and enters at least a portion of the tip 1024, the thermocouple wire 1025 entering the tip 1024 may be covered by a hard material such as stainless steel, and 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.
According to the technical scheme, the ablation system of the embodiment of the application adopts the plurality of probes and the gas-liquid separation device with the plurality of liquid pipelines, the liquid pipelines of the gas-liquid separation device are directly communicated to the gas inlet channel of the probes, and after media enter the heat exchanger through the gas return channel of the probes, each channel is controlled through the first proportional valve, any valve block cannot be added between the gas-liquid separation device and the probes, so that the time for reducing the temperature of the probes to the lowest temperature is greatly reduced, and the working efficiency is improved.
In addition, in the prior art, because the flow of the liquid medium cannot be continuously controlled, when a patient is subjected to cryoablation of a tumor, only an ice ball with a fixed size can be formed at the tumor, and after the liquid medium flowing through the probe 102 is completely gasified to be a normal-temperature gas, the ablation system 10 in the embodiment of the application realizes continuous control of the flow of the liquid medium by using the first proportional valve 1044, and simultaneously realizes continuous adjustment of the medium refrigeration power and accurate control of the temperature of the probe 102, so that ice balls with different sizes can be formed as required when the patient is subjected to cryoablation of a tumor, and for tumors with different sizes, the freezing range can be made to be consistent with the tumor size by adjusting the flow of the liquid medium or the temperature of the probe 102. On the other hand, in some tumors at the edge of an important organ, the cryoablation operation may be performed without damaging the important organ by adjusting the flow rate of the liquid medium or the temperature of the probe 102.
Finally, it should be noted that: the above embodiments are only used for illustrating the technical solutions of the embodiments of the present application, and are not limited thereto; although the present application has been described in detail with reference to the foregoing embodiments, it should be understood by those of ordinary skill in the art that: the technical solutions described in the foregoing embodiments may still be modified, or some technical features may be equivalently replaced; and such modifications or substitutions do not depart from the spirit and scope of the corresponding technical solutions in the embodiments of the present application.
Claims (10)
1. An ablation system (10), characterized in that the ablation system (10) comprises:
a medium storage device (101) for storing a liquid medium;
a plurality of probes (102), wherein each probe (102) 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), the gas-liquid separation device (1031) comprises a gas pipeline (1032) and a plurality of liquid pipelines (1033), and each liquid pipeline (1033) can be mutually communicated or isolated with a gas inlet channel (1021) of each probe (102);
the heat exchange module (104) is provided with a heat exchanger (1041), the heat exchanger (1041) is communicated with the air return channel (1022) so as to convert the liquid medium conveyed in the air return channel (1022) into a gas medium;
and the control module (105) is respectively electrically connected with each probe (102) and the heat exchange module (104), and the control module (105) acquires the temperature of each probe (102) and controls the flow Q2 of the gas medium flowing out of the heat exchange module (104).
2. The ablation system of claim 1, wherein the ablation system (10) further comprises a first type connector (21) and a second type connector (22), the first type connector (21) and the second type connector (22) are capable of being mutually clamped or separated, when the first type connector (21) and the second type connector (22) are mutually clamped, each liquid conduit (1033) is respectively communicated with the air inlet channel (1021) of each probe (102); when the first type connector (21) and the second type connector (22) are mutually detached, the first type connector (21) is automatically closed to prevent the liquid medium in the liquid pipeline (1033) from flowing out.
3. The ablation system of claim 2, wherein the first type of connection (21) comprises two first conduits (210), the second type of connection (22) comprises two second conduits (220), the two first conduits (210) are respectively connected to the liquid conduit (1033) and the heat exchanger (1041), the two second conduits (220) are respectively connected to the air inlet passage (1021) and the air return passage (1022) of the probe (102), and the two first conduits (210) are respectively in communication with the two second conduits (220) when the first type of connection (21) and the second type of connection (22) are mutually clamped.
4. The ablation system according to claim 3, characterized in that each first conduit (210) comprises a first pipe section (201), a second pipe section (202) and a third pipe section (203) which are connected in sequence, wherein 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 member (204) and a ball (205), the elastic member (204) abuts against the end part of the second pipe section (202), the inner diameter of the third pipe section (203) is smaller than the diameter of the ball (205) and smaller than the inner diameter of the second pipe section (202), and the ball (205) is clamped between the second pipe section (202) and the third pipe section (203) when the first type joint (21) and the second type joint (22) are mutually detached; 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 joint (21) and the second type joint (22) are butted together, the first end of each second pipe (220) penetrates through the third pipe section (203) and enters the second pipe section (202), and the balls (205) are far away from the end part of the third pipe section (203).
5. The ablation system of claim 3, wherein the second conduit (220) is provided with an extension (224) and a first aperture (226), wherein the extension (224) extends radially outward along the first end of the second conduit (220), and the first aperture (226) is formed between the extension (224) and the body (225) of the second conduit (220).
6. The ablation system of claim 1, wherein the heat exchange module (104) further comprises a first proportional valve (1044), the first proportional valve (1044) being connected to the heat exchanger (1041), the control module (105) controlling the flow Q2 of the gaseous medium via the first proportional valve (1044).
7. The ablation system of claim 1, wherein the control module (105) adjusts the flow rate Q2 of the gaseous medium based on a difference Δ T between the temperature T of the probe (102) and a target temperature T2 such that the temperature T of the probe (102) approaches the target temperature T2.
8. The ablation system of claim 7, wherein the relationship between the flow rate Q2 of the gaseous medium and the target temperature T2 is substantially in accordance with an empirical formula: t2= a1-a 2a 3Q 2, wherein a1, a2, a3 are constants.
9. The ablation system of claim 5, wherein the gas-liquid separation device (1031) comprises an inner sleeve (1037) and an outer sleeve (1038), a channel (404) is formed between the inner sleeve (1037) and the outer sleeve (1038), a plurality of first through holes (1039) are distributed at intervals on the wall of the inner sleeve (1037), a second through hole (402) is formed at the end of the outer sleeve (1038), and the second through hole (402) is connected with the heat exchanger (1041) in a pipeline manner.
10. The ablation system of claim 9, wherein the gas-liquid separator (1031) has a plurality of second holes (401) at an end thereof, each of the second holes (401) is respectively connected to the inner tube (1037), each of the second holes (401) is respectively connected to the gas inlet passage (1021) of the probe (102), and the passage (404) extends through the end of the gas-liquid separator (1031) between the second holes (401).
Priority Applications (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202211083012.6A CN115337093A (en) | 2022-09-06 | 2022-09-06 | Ablation system |
| PCT/CN2022/132350 WO2024050967A1 (en) | 2022-09-06 | 2022-11-16 | Ablation system |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202211083012.6A CN115337093A (en) | 2022-09-06 | 2022-09-06 | Ablation system |
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| CN115337093A true CN115337093A (en) | 2022-11-15 |
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| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202211083012.6A Pending CN115337093A (en) | 2022-09-06 | 2022-09-06 | Ablation system |
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| Country | Link |
|---|---|
| CN (1) | CN115337093A (en) |
| WO (1) | WO2024050967A1 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2024050967A1 (en) * | 2022-09-06 | 2024-03-14 | 上海美杰医疗科技有限公司 | Ablation system |
Family Cites Families (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2009009398A1 (en) * | 2007-07-06 | 2009-01-15 | Tsunami Medtech, Llc | Medical system and method of use |
| CN107822705B (en) * | 2017-11-27 | 2024-04-19 | 海杰亚（北京）医疗器械有限公司 | Joint, cryoablation needle and cryoablation treatment device |
| CN109620392B (en) * | 2018-12-11 | 2021-01-01 | 海杰亚（北京）医疗器械有限公司 | Working medium distribution equipment and system for high-low temperature treatment |
| CN109405327B (en) * | 2018-12-26 | 2024-02-13 | 上海导向医疗系统有限公司 | Precooling device for cryotherapy and cryotherapy system |
| CN111839713B (en) * | 2019-04-24 | 2023-03-24 | 上海美杰医疗科技有限公司 | Multi-modal tumor ablation probe system and control method thereof |
| CN115337093A (en) * | 2022-09-06 | 2022-11-15 | 上海美杰医疗科技有限公司 | Ablation system |
-
2022
- 2022-09-06 CN CN202211083012.6A patent/CN115337093A/en active Pending
- 2022-11-16 WO PCT/CN2022/132350 patent/WO2024050967A1/en unknown
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2024050967A1 (en) * | 2022-09-06 | 2024-03-14 | 上海美杰医疗科技有限公司 | Ablation system |
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| WO2024050967A1 (en) | 2024-03-14 |
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