Efficient cryoablation needle

Abstract

The invention belongs to the technical field of medical instruments, and particularly relates to an efficient cryoablation needle which comprises a handle, a connecting pipe is fixed to one end of the handle, a needle rod is fixed to the end, away from the handle, of the connecting pipe, a needle head is fixed to the end, away from the connecting pipe, of the needle rod, and an expansion cavity is formed in the needle head. A transmission pipe is fixed to the other end of the handle, a connector is fixed to the end, away from the handle, of the transmission pipe, a fluid pipe and a coaxial cable are assembled in the connector, one end of the fluid pipe and one end of the coaxial cable extend into the expansion cavity, and an antenna is fixed to the position, located in the expansion cavity, of one end of the coaxial cable. A cooling working medium is input into the needle through the fluid pipe, so that the needle can perform cryoablation, microwaves are transmitted to the spiral antenna through the coaxial cable 1, so that the antenna can perform microwave ablation, and the device has the advantages of fast temperature rise, large ablation area, low cost and the like.

Description

TECHNICAL FIELD

[0001] The present application belongs to the technical field of medical devices, and particularly relates to a high-efficiency cryoablation needle. BACKGROUND

[0002] In the field of medical clinical treatment, cryoablation as a minimally invasive treatment method has been widely used in the ablation treatment of target regions of patient's anatomical structure. During the cryosurgery, one or more cryoprobe can be deployed by the surgeon to achieve the ablation of the target region by freezing and thawing the tissue. The core refrigeration principle of such cryoprobes is based on the Joule-Thomson effect. Specifically, the cryogenic fluid inside the cryoprobe expands from a higher pressure state to a lower pressure state, which cools the temperature at the top end of the device to a temperature required for tissue cryoablation near the top end or lower. Subsequently, the expanded cryogenic fluid undergoes heat transfer with the outer wall of the cryoprobe, thereby forming an "ice ball" in the tissue around the top end of the probe, and finally achieving the effect of tissue cryoablation. Therefore, the cryoprobe becomes the core device in the implementation process of cryoablation. However, the current traditional cryoablation technology (such as argon-helium knife) still has many defects to be solved, which seriously affects the treatment effect and safety. The traditional cryoablation technology relies on the Joule-Thomson effect for refrigeration, and needs to switch to helium or use resistance heating during the rewarming stage. The specific defects are as follows: Firstly, the rewarming speed is slow, and it takes 3-5 minutes to use helium for rewarming, and the temperature after rewarming can only reach 40℃, which leads to poor hemostasis effect of the needle channel, increases the pain of the patient, and increases the risk of bleeding. At the same time, helium is a strategic material with high price, and the cost of consumables for a single treatment exceeds 1000 yuan, which greatly increases the treatment cost; Secondly, there is a problem of ice ball residue. During the needle withdrawal process, the ice ball does not completely melt, which can easily tear the tissue of the needle channel and cause additional damage to the patient; Thirdly, the refrigeration efficiency is low, and the expanded refrigerant gas in the expansion chamber is not fully utilized, resulting in energy waste; Fourthly, no vacuum insulation structure is provided at the handle, and frost phenomenon may occur at the handle during the operation, which may freeze the operator and pose a safety hazard; Fifthly, although there are attempts to integrate resistance wires in the cryoprobe for rewarming in the prior art, the power density of the resistance wires is low (<50W / cm), and the heat generated will be lost along the metal needle shaft, resulting in insufficient rewarming efficiency. At the same time, the traditional electric heating and gas rewarming methods have low efficiency for tumors larger than 3cm in volume, and the heating energy cannot meet the demand. In summary, the existing cryoablation technology has significant defects in rewarming efficiency, refrigeration utilization rate, operation safety, and adaptability to tumors of different volumes. These problems not only increase the treatment risk and economic burden of patients, but also limit the further application of cryoablation in clinical treatment, especially in the treatment of deep and large-volume tumors. SUMMARY

[0003] The purpose of the present application is to provide an efficient cryoablation needle, which can input cooling working medium into the inside of the needle head through the fluid pipe, so that the needle head can perform cryoablation, and can transmit microwaves to the antenna in a spiral form through the coaxial cable, so that the antenna can perform microwave ablation, so that the device has the advantages of fast warming, large ablation area, low cost, etc.

[0004] The technical solutions adopted by the present application are as follows: An efficient cryoablation needle, comprising a handle, one end of the handle is fixed with a connecting pipe, the end of the connecting pipe away from the handle is fixed with a needle rod, the end of the needle rod away from the connecting pipe is fixed with a needle head, an expansion cavity is formed in the inside of the needle head, the other end of the handle is fixed with a transmission pipe, the end of the transmission pipe away from the handle is fixed with a connector, the inside of the connector is assembled with a fluid pipe and a coaxial cable, and one end of the fluid pipe and the coaxial cable extends into the inside of the expansion cavity, one end of the coaxial cable and located in the inside of the expansion cavity is fixed with an antenna, the outside of the handle is slidingly connected with a button, further comprising: A heat preservation transmission assembly is assembled in the inside of the handle, the heat preservation transmission assembly and the fluid pipe, the heat preservation transmission assembly and the coaxial cable, and the heat preservation transmission assembly and the button are connected with each other, and the inside of the connecting pipe, the needle rod, the needle head, the transmission pipe, the connector, the heat preservation transmission assembly and the outer wall of the fluid pipe form a backflow passage, which is configured to be able to transport backflow cooling working medium; Wherein, the cooling working medium is input into the inside of the fluid pipe, and the needle head can perform cryoablation; microwaves are transmitted to the coaxial cable, and the antenna can perform rewarming and microwave ablation, and during the cryoablation process, the output end of the fluid pipe is located in the inside of the antenna, and during the rewarming and microwave ablation process, the output end of the fluid pipe is located outside the antenna.

[0005] In a preferred embodiment, the antenna is in a spiral form, wherein, during the cryoablation process, the antenna in a spiral form can throttle the backflow cooling working medium.

[0006] In a preferred embodiment, the pitch of the antenna is , , , wherein, represents the wavelength of microwaves in vacuum.

[0007] In a preferred solution, the heat preservation transmission assembly comprises a heat preservation tube, a first sealing member, a second sealing member and a metal column, the heat preservation tube is arranged inside the handle and outside the connecting tube, the button is fixedly connected with the heat preservation tube, the fluid tube penetrates through the inside of the heat preservation tube, the first sealing member and the second sealing member are arranged at two ends of the heat preservation tube respectively, the first sealing member and the connecting tube and the second sealing member and the transmission tube are in sliding connection respectively, the metal column is fixed between the first sealing member and the second sealing member, the fluid tube is connected with the metal column, and the coaxial cable penetrates through the inside of the metal column, wherein pushing the button can drive the heat preservation tube and the fluid tube to move synchronously.

[0008] In a preferred solution, the inside of the needle rod is fixed with a heat insulation tube, and the inside of the tube wall of the heat insulation tube and the inside of the tube wall of the heat preservation tube are both provided with a vacuum cavity.

[0009] In a preferred solution, the reflux passage is formed by the inner wall of the needle, the inner wall of the needle rod, the inner wall of the connecting tube, the inner wall of the heat preservation tube, the inner wall of the transmission tube and the outer wall of the fluid tube.

[0010] In a preferred solution, the fluid tube is arranged at a heat exchange section of the heat preservation tube, the heat exchange section is spirally wound outside the metal column, and the outer side of the heat exchange section is wound with a heat conducting sheet.

[0011] In a preferred solution, sealing rings are arranged between the first sealing member and the connecting tube, the first sealing member and the heat preservation tube, the second sealing member and the transmission tube and the second sealing member and the heat preservation tube.

[0012] In a preferred solution, the cooling working medium is any one of argon, nitrogen and carbon dioxide, and the material of the needle rod is any one of 304 stainless steel, 316 stainless steel and titanium alloy.

[0013] The present application has the following technical effects: The present application has the following technical effects: The present application has the following technical effects: The application can exchange heat with the backflow cooling working medium, avoid frost phenomenon on the outside of the needle rod and the handle, and avoid the phenomenon of scalding hands on the outside of the needle rod and the handle during microwave ablation. The heat exchange section and the heat conduction sheet cooperate to cool the normal-temperature cooling working medium in the fluid pipe by the backflow low-temperature cooling working medium, the cooling working medium in the fluid pipe flows into the expansion cavity after being cooled, can absorb more heat in the expansion cavity, further improves the refrigeration efficiency of the cooling working medium, and further improves the efficiency of the cryoablation, and the spiral heat exchange section can effectively increase the heat exchange area and heat exchange time between the heat conduction sheet and the backflow cooling working medium, and improve the cooling effect. BRIEF DESCRIPTION OF DRAWINGS

[0014] Figure 1 is the overall structure schematic diagram of the embodiment one of the application; Figure 2 is the structure schematic of the handle inside the embodiment one of the application; Figure 3 is the structure schematic of the handle inside the embodiment one of the application; Figure 2 is the local enlarged schematic diagram of A in the embodiment one of the application; Figure 4 is the structure sectional view of the handle in the embodiment one of the application; Figure 5 is the local enlarged schematic diagram of B in the embodiment one of the application; Figure 4 Figure 6 is the structure schematic of the coaxial cable and the antenna in the embodiment one of the application; Figure 7 is the structure sectional view of the needle in the embodiment one of the application; Figure 8 is the SAR distribution schematic diagram of the simulation in the embodiment one of the application; Figure 9 is the simulation result diagram of the ablation area in the embodiment one of the application; Figure 10 is the ablation process schematic diagram in the embodiment two of the application.

[0015] In the drawings, the component list represented by each sign is as follows: 100, handle; 101, adapter pipe; 102, needle rod; 103, needle; 104, expansion cavity; 105, transmission pipe; 106, joint; 107, fluid pipe; 108, coaxial cable; 109, antenna; 110, button; 111, heat insulation pipe; 200, heat preservation transmission assembly; ​201, heat preservation tube; 202, first plugging member; 203, second plugging member; 204, metal column; 205, heat conduction sheet; 206, sealing ring. DETAILED DESCRIPTION

[0016] In order to make the above objectives, features and advantages of the present application more apparent, the specific embodiments of the present application will be described in detail below with reference to the accompanying drawings.

[0017] In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present application. However, it will be apparent to one skilled in the art that the present application can be practiced without the specific details given herein, that the present application can be practiced with other different systems, and therefore the scope of the present application is not limited to the details given herein.

[0018] Secondly, the "one embodiment" or "embodiment" referred to herein means that the specific features, structures or characteristics can be included in at least one implementation of the present application. "In a preferred embodiment" appearing in different places in the specification does not mean the same embodiment, nor is it an embodiment that is independent or alternative to other embodiments.

[0019] Thirdly, the present application is described in detail in conjunction with the schematic diagram. In the detailed description of the embodiments of the present application, the cross-sectional view of the device structure is partially enlarged without the general proportion for the convenience of description, and the schematic diagram is only an example, which should not limit the scope of protection of the present application herein. In addition, the three-dimensional spatial dimensions of length, width and depth should be included in actual manufacture.

[0020] Embodiment one Please refer to the accompanying Figures 1 to 6 As shown in the first embodiment of the present application, the embodiment provides a high-efficiency cryoablation needle, which comprises a handle 100, one end of the handle 100 is fixed with a connecting pipe 101, the end of the connecting pipe 101 away from the handle 100 is fixed with a needle rod 102, the end of the needle rod 102 away from the connecting pipe 101 is fixed with a needle head 103, and the end of the connecting pipe 101 away from the needle rod 102 extends to the inside of the handle 100, the inside of the needle head 103 is provided with an inflation cavity 104, the other end of the handle 100 is fixed with a transmission pipe 105, the end of the transmission pipe 105 away from the handle 100 is fixed with a connector 106, the inside of the connector 106 is assembled with a fluid pipe 107 and a coaxial cable 108, and one end of the fluid pipe 107 and the coaxial cable 108 extends to the inside of the inflation cavity 104 in sequence through the inside of the transmission pipe 105, the handle 100, the connecting pipe 101 and the needle rod 102, one end of the coaxial cable 108 and located in the inside of the inflation cavity 104 is fixed with an antenna 109, the outside of the handle 100 is slidingly connected with a button 110, and further comprising: The heat preservation transmission assembly 200 is assembled in the interior of the handle 100, and is connected with the fluid pipe 107, the coaxial cable 108 and the button 110, and a backflow channel is formed between the adapter pipe 101, the needle rod 102, the needle head 103, the transmission pipe 105, the joint 106, the interior of the heat preservation transmission assembly 200 and the outer wall of the fluid pipe 107, and the backflow channel is configured to be capable of conveying the cooling working medium of backflow, and the fluid pipe 107 and the heat preservation transmission assembly 200 can be synchronously moved by the button 110. In the process of cryoablation, the output end of the fluid pipe 107 is located in the interior of the antenna 109, and in the process of rewarming and microwave ablation, the output end of the fluid pipe 107 is located outside the antenna 109.

[0021] It should be noted that the device is also matched with a control device, and the joint 106 is connected with the control device, and the control device is internally integrated with a medium conveying unit, a microwave unit and a control unit, the medium conveying unit can convey the cooling working medium into the interior of the fluid pipe 107 and collect the cooling working medium of backflow, the microwave unit can convey the microwave to the coaxial cable 108, and the control unit is used for adjusting and inputting the ablation parameters, controlling the microwave power, the input flow rate of the cooling working medium and other control operations.

[0022] Here, the adapter pipe 101 can be a 90° elbow pipe or a straight pipe, and in the embodiment, only the elbow pipe is shown, and is not limited.

[0023] Further, the rewarming and microwave ablation include rewarming and microwave ablation treatment operations, and the common characteristic is temperature rise, and the difference is that the upper limit of the temperature of microwave ablation is higher.

[0024] Specifically, the cooling working medium is any one of the following substances: argon, nitrogen, carbon dioxide or other gases with refrigeration effect; the materials of the adapter pipe 101, the needle rod 102 and the needle head 103 are any one of the following materials: 304 stainless steel, 316 stainless steel, titanium alloy or other biocompatible metal materials, and in the embodiment, the cooling working medium is preferably carbon dioxide, and the materials of the adapter pipe 101, the needle rod 102 and the needle head 103 are 316 stainless steel.

[0025] In this embodiment, when the patient is subjected to cryoablation, the needle 103 is inserted into the lesion site under the guidance of the imaging device. The doctor observes the size and position of the lesion according to the medical image, selects appropriate ablation parameters, pushes the button 110, and synchronously moves the fluid pipe 107 and the heat preservation transmission assembly 200 through the button 110, so that the fluid pipe 107 moves into the antenna 109, high-pressure normal-temperature cooling working medium is input into the fluid pipe 107, the cooling working medium flows into the expansion cavity 104 from the inside of the fluid pipe 107, based on the "Joule-Thomson effect", the high-pressure normal-temperature cooling working medium flowing out from the output end of the fluid pipe 107 expands rapidly in volume and drops rapidly in temperature, heat transfer between the expanded cooling working medium and the outer wall of the needle 103 causes the tissue surrounding the needle 103 to form an "ice ball", realizing cryoablation of the lesion site, and the expanded cooling working medium in the expansion cavity 104 returns through the return passage; after the cryoablation is completed, the button 110 is moved reversely, the fluid pipe 107 and the heat preservation transmission assembly 200 are reversely moved synchronously through the button 110, so that the fluid pipe 107 moves to the outside of the antenna 109, microwaves are transported into the coaxial cable 108, so that an electromagnetic field is formed around the antenna 109 and molecules in the lesion tissue are excited to produce heat by high-speed friction, the temperature of the cryoablation site can quickly reach the temperature required for rewarming and microwave ablation, and the needle channel can be efficiently hemostatic, avoiding the phenomenon of body fluid diffusion in the needle channel. At the same time, the molecules are excited by microwaves to produce high-speed friction, the heating rate is fast (which can reach 100℃ / min), the ice crystal phase change point (0℃) can be quickly broken through, and the operation time is shortened.

[0026] Secondly, please refer to Figure 5 and Figure 6 again, the antenna 109 is in a spiral shape, wherein, during the cryoablation process, the spiral-shaped antenna 109 can throttle the return cooling working medium.

[0027] Here, the antenna 109 is directly fed through the coaxial cable 108, the inside of the antenna 109 at least includes an inner core and an outer core, an insulating layer is arranged on the outside of the inner core, and the inner core and one end of the antenna 109 are fixedly connected in a welded manner, and the outer core is grounded through a metal ring.

[0028] In this embodiment, during the cryoablation process, the spiral-shaped antenna 109 can throttle the return cooling working medium, prolong the residence time of the cooling working medium in the expansion cavity 104, and the refrigeration efficiency is higher. At the same time, compared with the rewarming method relying on the resistance wire in the prior art, the spiral-shaped antenna 109 is used to perform rewarming and microwave ablation in a microwave manner, which has the advantages of high heating efficiency, simple structure, compactness, low cost and the like. Moreover, simulation software is used for simulation to obtain a SAR distribution map and a thermal field map (please refer to Figure 8 and Figure 9As shown in the figure, the spiral-shaped antenna 109 also has the advantage of a large ablation range, which can meet the clinical needs of ablation of deep or large-volume tumors.

[0029] In a preferred embodiment, the pitch of antenna 109 is denoted as... , ,in, This indicates the wavelength of microwaves in a vacuum.

[0030] It should be noted that the most commonly used frequencies for microwave ablation in clinical practice are 915MHz and 2450MHz, with 2450MHz being the most frequent. 915MHz has a longer microwave wavelength. Microwave wavelength approximately 330mm, 2450MHz The length is approximately 122.45 mm. In this embodiment, the microwave frequency is preferably 2450 MHz.

[0031] In one specific embodiment, antenna 109 is fabricated using high-strength silver-plated copper wire with a diameter of 0.2 mm. Antenna 109 has 8 turns and a diameter of 1.8 mm. When the microwave frequency is 2450 MHz, its microwave wavelength... The pitch of the antenna 109 is approximately 6.12 mm, and the total length of the antenna 109 is approximately 48.96 mm. Increasing the number of turns of the antenna 109 can improve the gain. In this embodiment, the number of turns of the antenna 109 is 8 turns, which is only one implementation method and is not a specific limitation.

[0032] Secondly, please refer to the following as well. Figures 2 to 4 The heat preservation transmission assembly 200 includes a heat preservation pipe 201, a first sealing member 202, a second sealing member 203, and a metal column 204. The heat preservation pipe 201 is assembled inside the handle 100 and located outside the connecting pipe 101. The button 110 is fixedly connected to the heat preservation pipe 201. The fluid pipe 107 passes through the inside of the heat preservation pipe 201. The first sealing member 202 and the second sealing member 203 are clamped to both ends of the heat preservation pipe 201 in an interference fit manner. The first sealing member 202 and the connecting pipe 101, as well as the second sealing member 203 and the transmission pipe 105, are all slidably connected. The metal column 204 is fixed between the first sealing member 202 and the second sealing member 203 and located inside the heat preservation pipe 201. The fluid pipe 107 is connected to the metal column 204, and the coaxial cable 108 passes through the inside of the metal column 204. Pushing the button 110 can drive the heat preservation pipe 201 and the fluid pipe 107 to move synchronously.

[0033] In this embodiment, when switching between freezing ablation and microwave ablation, the button 110 is pushed, and the button 110 and the heat preservation tube 201 move synchronously due to the fixed connection between the button 110 and the heat preservation tube 201. Since the heat preservation tube 201 is connected to the first blocking piece 202 and the first blocking piece 202 is connected to the metal column 204, the heat preservation tube 201 drives the metal column 204 to move synchronously. Since the metal column 204 is connected to the fluid pipe 107, the fluid pipe 107 moves synchronously through the metal column 204. In this embodiment, when the button 110 is pushed forward, the heat preservation tube 201 and the fluid pipe 107 move forward synchronously, and the fluid pipe 107 moves into the antenna 109. When the button 110 is pushed backward, the heat preservation tube 201 and the fluid pipe 107 move backward synchronously, and the fluid pipe 107 moves out of the antenna 109.

[0034] Secondly, referring again to Figure 4 and Figure 6 , the inside of the needle rod 102 is fixed with a heat insulation tube 111, and the inside of the wall of the heat insulation tube 111 and the inside of the wall of the heat preservation tube 201 are both provided with a vacuum cavity.

[0035] In this embodiment, the vacuum cavity can exchange heat with the backflow of the cooling working medium, avoid frost phenomenon on the outside of the needle rod 102 and the handle 100, and also avoid the phenomenon of scalding hands on the outside of the needle rod 102 and the handle 100 during microwave ablation.

[0036] Please refer again to Figure 2 and Figure 3 , the backflow passage is formed by the inner wall of the needle 103, the inner wall of the needle rod 102, the inner wall of the connecting pipe 101, the inner wall of the heat preservation tube 201, the inner wall of the transmission pipe 105, and the outer wall of the fluid pipe 107. The part of the fluid pipe 107 in the heat preservation tube 201 is called the heat exchange section, which is spirally wound outside the metal column 204, and the outer side of the heat exchange section is wound with a heat conducting sheet 205.

[0037] In this embodiment, after the high-pressure normal-temperature cooling working medium is input into the fluid pipe 107, the expanded cooling working medium backflows from the inside of the expansion cavity 104 through the backflow passage. When flowing through the inside of the heat preservation tube 201, the backflowing low-temperature cooling working medium exchanges heat with the heat conducting sheet 205 and the wall of the fluid pipe 107, which can cool the normal-temperature cooling working medium in the fluid pipe 107. After the cooled cooling working medium in the fluid pipe 107 flows out from the output end, it can absorb more heat in the expansion cavity 104, further improving the refrigeration efficiency and effectively improving the efficiency of freezing ablation. At the same time, the spiral heat exchange section can effectively increase the heat exchange area and heat exchange time between the heat conducting sheet 205 and the backflowing cooling working medium, and improve the cooling effect.

[0038] Please refer againFigure 2 and Figure 4 As shown, sealing rings 206 are installed between the first sealing component 202 and the connecting pipe 101, the first sealing component 202 and the insulation pipe 201, the second sealing component 203 and the transmission pipe 105, and the second sealing component 203 and the insulation pipe 201.

[0039] In this embodiment, the sealing ring 206 can improve the sealing performance of the internal space of the insulation pipe 201 and prevent leakage of the backflowing cooling medium.

[0040] Example 2 Please see Figure 10 As shown, this embodiment provides a method for using a high-efficiency cryoablation needle, applicable to any of the high-efficiency cryoablation needles in Embodiment 1, including the following steps: St1: Accurately insert the needle 103 into the lesion site and connect the fluid tube 107 to the control device; St2: Determine the size of the ablation area based on medical imaging data, and determine the cryoablation parameters, including the power and time of cryoablation; St3: Push button 110 to move the output end of fluid tube 107 into antenna 109, and start cryoablation through control device; St4: Determine whether cryoablation completely covers the lesion and whether cryoablation is completed based on medical images. If cryoablation fails to achieve the expected results, repeat cryoablation until the lesion site is completely covered. St5: Push button 110 in the opposite direction to move the output end of fluid tube 107 to the outside of antenna 109; St6: Determine the parameters for microwave ablation based on medical imaging data, including the power and time of microwave ablation, adjust the pressure of the cooling medium to a low pressure state, and start microwave ablation through the control equipment; St7: Determine whether the ice ball of the lesion tissue has melted and whether the lesion is completely covered based on medical imaging. If microwave ablation fails to achieve the expected purpose, repeat microwave ablation until the lesion site is completely ablated. St8: After microwave ablation is completed, turn off the control equipment and cooling system, remove needle 103, and the treatment is complete.

[0041] The working principle of this invention is as follows: When the patient is subjected to cryoablation, the needle 103 is inserted into the lesion site under the guidance of the imaging device, the physician observes the size and position of the lesion according to the medical image, selects appropriate ablation parameters, pushes the button 110, and synchronously moves the fluid pipe 107 and the heat preservation pipe 201 through the button 110, so that the fluid pipe 107 moves to the inside of the antenna 109, the high-pressure normal-temperature cooling working medium is input into the fluid pipe 107, the cooling working medium flows into the expansion cavity 104 from the inside of the fluid pipe 107, the high-pressure normal-temperature cooling working medium flows out from the output end of the fluid pipe 107, the volume expands sharply, the temperature drops sharply, and the heat transfer between the expanded cooling working medium and the outer wall of the needle 103 causes the tissue surrounding the needle 103 to form an "ice ball", realizing the cryoablation of the lesion site, the expanded cooling working medium in the expansion cavity 104 is returned through the backflow passage after throttling through the antenna 109, when the expanded cooling working medium flows through the inside of the heat preservation pipe 201, the expanded cooling working medium exchanges heat with the cooling working medium in the inside of the fluid pipe 107, and the normal-temperature cooling working medium in the inside of the fluid pipe 107 is cooled, the cooling effect is better after the cooled cooling working medium flows into the inside of the expansion cavity 104; after the cryoablation is completed, the button 110 is reversely moved, the fluid pipe 107 and the heat preservation pipe 201 are reversely moved synchronously through the button 110, so that the fluid pipe 107 moves to the outside of the antenna 109, the microwave is transported into the coaxial cable 108, so that the electromagnetic field is formed around the antenna 109 and the molecules in the lesion tissue are excited to generate heat by high-speed friction, the ice crystal phase change point can be quickly broken through, the temperature of the cryoablation site can quickly reach the temperature required for rewarming and microwave ablation, and the needle channel can be efficiently hemostatic.

[0042] The above is only the preferred embodiment of the present application, and it should be pointed out that those skilled in the art can make some improvements and refinements without departing from the principles of the present application, and these improvements and refinements should also be regarded as the protection scope of the present application. The structures, devices and operation methods not specifically described and explained in the present application are implemented according to the conventional means in the art, unless otherwise specified and limited.

Claims

1. A high efficiency cryoablation needle, characterized by: The utility model provides an improved cryoablation and microwave ablation device, which comprises a handle (100), one end of the handle (100) is fixed with a connecting pipe (101), one end of the connecting pipe (101) away from the handle (100) is fixed with a needle rod (102), one end of the needle rod (102) away from the connecting pipe (101) is fixed with a needle head (103), the inside of the needle head (103) is provided with an expansion cavity (104), the other end of the handle (100) is fixed with a transmission pipe (105), one end of the transmission pipe (105) away from the handle (100) is fixed with a connector (106), the inside of the connector (106) is assembled with a fluid pipe (107) and a coaxial cable (108), one end of the fluid pipe (107) and the coaxial cable (108) extends to the inside of the expansion cavity (104), one end of the coaxial cable (108) in the inside of the expansion cavity (104) is fixed with an antenna (109), the outside of the handle (100) is slidably connected with a button (110), further comprising: a heat preservation transmission assembly (200) is assembled in the inside of the handle (100), the heat preservation transmission assembly (200) and the fluid pipe (107), the heat preservation transmission assembly (200) and the coaxial cable (108) and the heat preservation transmission assembly (200) and the button (110) are connected with each other, the inside of the connecting pipe (101), the needle rod (102), the needle head (103), the transmission pipe (105), the connector (106), the heat preservation transmission assembly (200) and the outer wall of the fluid pipe (107) form a backflow passage, the backflow passage is configured to be able to transport backflow cooling working medium; wherein, the inside of the fluid pipe (107) is inputted with cooling working medium, the needle head (103) can be used for cryoablation, the coaxial cable (108) is transported with microwave, the antenna (109) can be used for rewarming and microwave ablation, and the output end of the fluid pipe (107) is located in the inside of the antenna (109) in the cryoablation process, the output end of the fluid pipe (107) is located outside the antenna (109) in the rewarming and microwave ablation process.

2. The high efficiency cryoablation needle of claim 1, wherein: The antenna (109) is in a spiral form, wherein, the antenna (109) in the spiral form can throttle the backflow cooling working medium in the cryoablation process.

3. The high efficiency cryoablation needle of claim 2, wherein: The pitch of the antenna (109) is denoted by , where denotes the wavelength of the microwave in vacuum.

4. The high efficiency cryoablation needle of claim 1, wherein: The heat preservation transmission assembly (200) comprises a heat preservation pipe (201), a first blocking piece (202), a second blocking piece (203) and a metal column (204), the heat preservation pipe (201) is assembled in the inside of the handle (100) and located outside the adapter pipe (101), the button (110) and the heat preservation pipe (201) are fixedly connected, the fluid pipe (107) penetrates the inside of the heat preservation pipe (201), the first blocking piece (202) and the second blocking piece (203) are assembled at two ends of the heat preservation pipe (201) respectively, the first blocking piece (202) and the adapter pipe (101) and the second blocking piece (203) and the transmission pipe (105) are slidably connected, the metal column (204) is fixed between the first blocking piece (202) and the second blocking piece (203), the fluid pipe (107) is connected with the metal column (204), and the coaxial cable (108) penetrates the inside of the metal column (204), wherein the button (110) can drive the heat preservation pipe (201) and the fluid pipe (107) to move synchronously.

5. The high efficiency cryoablation needle of claim 4, wherein: The inside of the needle rod (102) is fixed with a heat insulation pipe (111), and the inside of the pipe wall of the heat insulation pipe (111) and the inside of the pipe wall of the heat preservation pipe (201) are both provided with a vacuum cavity.

6. The high efficiency cryoablation needle of claim 4, wherein: The reflux passage is formed by the inner wall of the needle (103), the inner wall of the needle rod (102), the inner wall of the adapter pipe (101), the inner wall of the heat preservation pipe (201), the inner wall of the transmission pipe (105) and the outer wall of the fluid pipe (107).

7. The high efficiency cryoablation needle of claim 4, wherein: The fluid pipe (107) located in the heat preservation pipe (201) is a heat exchange section, the heat exchange section is spirally wound outside the metal column (204), and the outer side of the heat exchange section is wound with a heat conducting sheet (205).

8. The high efficiency cryoablation needle of claim 4, wherein: The first blocking piece (202) and the adapter pipe (101), the first blocking piece (202) and the heat preservation pipe (201), the second blocking piece (203) and the transmission pipe (105) and the second blocking piece (203) and the heat preservation pipe (201) are all provided with a sealing ring (206).

9. The high efficiency cryoablation needle of claim 1, wherein: The cooling working medium is any one of the following substances: argon, nitrogen and carbon dioxide, and the material of the needle rod (102) is any one of the following materials: 304 stainless steel, 316 stainless steel and titanium alloy.

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