CN116035692A - Electrode ablation device based on ganglion cyst - Google Patents

Abstract

The present application discloses an electrode ablation device based on a ganglion cyst, which belongs to the technical field of medical devices. An electrode ablation device based on a ganglion cyst includes: a puncture tube configured with a first channel, one end of which is formed with a puncture segment, and the puncture segment is inserted into the into the cyst; the suction tube constructs the second channel; the support member is constructed with a third channel, the puncture tube and the suction tube are placed into the third channel respectively, and the first channel and the second channel communicate with each other; the electric heating assembly, It is arranged on the puncture section; the power supply device is arranged on the support and is used to supply power to the electric heating assembly; wherein, the electric heating assembly includes a first conductive member and a second conductive member for releasing and receiving electric current, and the puncture tube is placed into In a cyst, the first conductive member and the second conductive member release and receive electric current to heat interstitial fluid of the cyst. The beneficial effect of the present application is to provide a ganglion cyst-based electrode ablation device which has a good therapeutic effect on the ganglion cyst.

Description

Electrode ablation device based on ganglion cyst

technical field

The present application relates to the field of medical devices, in particular, to an electrode ablation device based on a ganglion cyst.

Background technique

Ganglion cyst is a very common disease for long-term exercise personnel. The cyst is usually composed of cyst wall and interstitial fluid in the cyst wall.

At present, there are two commonly used treatment methods. The first is to use a puncture needle to penetrate into the cyst wall, and then suck out the interstitial fluid in the cyst wall by means of negative pressure suction. After the interstitial fluid in the cyst is sucked out, the patient symptoms will be relieved. However, this type of treatment has a high recurrence rate, because the cyst wall is also biologically active, and the cyst wall can also actively transport the tissue fluid outside the cyst wall, and inhale the tissue fluid outside the cyst wall into the cyst wall. After the puncture site is healed, the cyst wall will still actively transport the interstitial fluid outside the cyst wall and introduce the interstitial fluid outside the cyst wall into the cyst wall, resulting in cyst recurrence. The second method is to directly remove the cyst through minimally invasive resection. Compared with the first method, this method can avoid recurrence, but the operation risk is high and it is easy to cause irreversible damage to the patient's joints.

To sum up, there is currently a lack of electrode ablation devices based on ganglion cysts that can reduce surgical risks on the basis of good therapeutic effects and less recurrence of ganglion cysts.

Contents of the invention

The Summary section of this application serves to introduce concepts in a simplified form that are described in detail in the Detailed Description section that follows. The contents of this application are not intended to identify key features or essential features of the claimed technical solution, nor are they intended to be used to limit the scope of the claimed technical solution.

In order to solve the problem of high risk and easy recurrence of ganglion cyst treatment, some embodiments of the present application provide an electrode ablation device based on ganglion cyst, including:

a puncture tube configured with a first channel, one end of which is formed with a puncture section, and the puncture section is inserted into the cyst;

Suction tube, constructing the second channel;

The support, the puncture tube and the suction tube are respectively connected to the support, and the first channel and the second channel communicate with each other;

The electric heating component is arranged on the puncture section;

The power supply device is arranged on the support and is used to supply power to the electric heating component;

Wherein, the electric heating assembly includes a first conductive part and a second conductive part for releasing and receiving electric current, the puncture tube is placed in the cyst, and the first conductive part and the second conductive part release and receive electric current to heat the interstitial fluid of the cyst.

The electrode ablation device for ganglion cyst provided by this application inserts the puncture tube into the cyst wall when treating the ganglion cyst, then the electric heating component is activated, and the first conductive element and the second conductive element are released to the interstitial fluid in the cyst wall The electric current makes the interstitial fluid heat, thus the interstitial fluid is evaporated, the pressure in the cyst wall increases, a positive pressure is formed in the cyst wall, and the interstitial fluid in the cyst wall is discharged through the suction tube; so a part of the interstitial fluid in the cyst wall is evaporated, and a part of the interstitial fluid is discharged from the body , and then play the purpose of treating ganglion cyst; at the same time, the protein denaturation will occur in the cyst wall due to the heating of interstitial fluid, thus the cyst wall will lose its biological activity, and then the cyst wall cannot have the ability of active transport, thus the present application The provided electrode ablation device has good treatment effect, low treatment risk and is not easy to relapse when used.

If the separate first conductive part and the second conductive part can be energized, after the power supply device is started, the current will flow directly from the first conductive part to the second conductive part, and then the current will heat the puncture section of the puncture tube, and then pass through The way of heat conduction is transferred to the interstitial fluid. This way of heating the interstitial fluid through heat transfer, on the one hand, takes a long time to heat, and on the other hand, because the cyst wall is too small, it is difficult for the interstitial fluid to form convection, so the temperature of the puncture section will be too high, which is easy to normal tissue causing burns.

Further, the single first conductive part and the single second conductive part are insulated from each other.

In this application, the first conductive part and the second conductive part are insulated. Therefore, after the power supply component is started, the current released by the first conductive part needs to pass through the interstitial fluid and then enter the second conductive part. It cannot pass through the interstitial fluid. And it goes directly to the second conductive part, so during the whole treatment process, the part that generates heat is the tissue fluid, and the puncture section itself will not generate heat; thus, it ensures that the tissue fluid in the cyst wall is heated evenly and the heating rate is fast , and the temperature of the puncture section will not be very high, and it is not easy to cause burns to normal tissues.

Further, the first conductive part is exposed on the outside of the puncture tube to form the first contact surface; the second conductive part is exposed on the outside of the puncture tube to form the second contact surface, the first contact surface and the second contact surface The area ratio is 1:0.9～1.1.

The area ratio of the first contact surface and the second contact surface is basically equal, which can ensure that the area of the first conductive member and the second conductive member in contact with the interstitial fluid is basically the same, so that the resistance of the current release end and the current output end are approximately equal, avoiding the first A portion of the conductive member or the second conductive member generates excessive heat.

Ganglion cysts generally occur more frequently in athletes who will undergo high-intensity training. Therefore, during the treatment process, it is necessary to avoid damage to the patient's normal tissues as much as possible to avoid increasing the difficulty of the patient's recovery. However, applying an alternating current to a patient can easily cause damage to the normal tissue of the patient, and this problem is aimed at.

Further, the current supplied by the current supply device to the first conductive member and the second conductive member is an alternating current, wherein the frequency of the current is 100kHz˜500kHz.

In the present application, the impedance of the interstitial fluid in the cyst wall is smaller than that of the cyst wall itself, and the frequency of the current is limited within the above range. Therefore, at the frequency of the alternating current, the current can break through the interstitial fluid in the cyst wall and generate a short-circuit current in the interstitial fluid. After the interstitial fluid in the cyst wall is evaporated, because the impedance of the cyst wall is too high, The current current cannot break down the impedance of the capsule wall, so no current will be generated in the normal tissues of the human body, and thus will not cause damage to the normal tissues of the human body. At the same time, the frequency of alternating current is higher than 100kHz, which can make the frequency of alternating current higher than the reciprocal of the reflex arc time of human muscle, so as to avoid the stimulation of muscles due to the low frequency of alternating current. In addition, during the heating of the interstitial fluid, the interstitial fluid can heat the cyst wall, thereby controlling the damage of the cyst wall to 1-1.5 mm.

Further, the puncture tube includes an inner support tube fixedly connected to the support, a puncture head fixedly connected to the inner support tube, an inner insulating tube sleeved on the inner support tube, a conductive tube sleeved on the inner insulating tube, and the conductive tube There is a distance between the puncture head and the inner insulating tube, the inner insulating tube is made of insulating material, the first conductive part is configured as a puncture head or is arranged on the puncture head, and the second conductive part is configured as a conductive tube or is set on the conductive tube.

By setting the inner insulating tube as an insulating material, the insulation between the first conductive part and the second conductive part can be guaranteed only if there is a gap between the first conductive part and the second conductive part, and the puncture of the first conductive part and the second conductive part can be avoided. Excess heat is generated on the tube.

Further, the inner insulating tube is provided with an insulating sleeve, one side of the insulating sleeve is fixedly connected to the puncture head, and the other side of the conductive tube is fixedly connected.

By setting the insulating sleeve, the inner conductive tube can be placed on the inner support tube, and the first conductive part and the second conductive part will not be in direct contact because of sliding toward the direction of the puncture head, which further ensures the first conductive part and the second conductive part. The insulation of the second conductive member prevents excess heat from being generated on the puncture tube when the power is applied.

Further, the conductive tube is sheathed with an outer insulating tube, and there is a gap between the outer insulating tube and the end of the conductive tube opposite to the puncture head, so that the conductive tube is partially exposed outside the puncture tube.

The outer insulating tube wraps the conductive tube, thereby limiting the exposed area and exposed position of the conductive tube, ensuring that the area ratio of the first contact surface and the second contact surface designed by the first conductive part and the second conductive part is within a predetermined range .

Further, the power supply device includes a first wire and a second wire, the first wire is connected to the first conductive member, and the second wire is connected to the second conductive member.

Further, the support member is configured with a third channel, and the ends of the puncture tube and the suction tube are put into the third channel.

One end of the inner insulating tube is fixedly connected to the puncture head, the other end is inserted into the third channel, and there is a gap between the inner insulating tube and the suction tube, the first lead is fixedly connected to the inner support tube, and the first lead is connected to the inner support tube. partly located in the gap between the inner insulating tube and the suction tube;

There is a gap between the end of the outer insulating tube inserted into the third channel and the end of the conductive tube, the second wire is fixedly connected to the conductive tube, and the part where the second wire is connected to the conductive tube is located on the exposed surface of the conductive tube in the third channel .

In this application, by constructing a third channel on the support, the lines for supplying power to the first conductive member and the second conductive member can be integrated on the support, ensuring the smoothness of the outer wall of the puncture tube and avoiding adverse effects on the operation At the same time, the circuit is integrated in the support, which can provide certain protection for the circuit.

To sum up, the beneficial effect of the present application is to provide a ganglion cyst-based electrode ablation device that has a good therapeutic effect and is not easy to recur, and reduces surgical risks for ganglion cysts.

Description of drawings

The accompanying drawings, which constitute a part of this application, are included to provide a further understanding of the application and make other features, objects and advantages of the application apparent. The drawings and descriptions of the schematic embodiments of the application are used to explain the application, and do not constitute an improper limitation to the application.

In addition, the same or similar reference numerals denote the same or similar elements throughout the drawings. It should be understood that the drawings are schematic and elements and elements have not necessarily been drawn to scale.

In the attached picture:

Fig. 1 is the plane view of the electrode ablation device based on the ganglion cyst provided by the present application;

Fig. 2 is a cross-sectional view of the supporting part, the puncture tube, and the matching part of the suction tube;

Fig. 3 is a structural schematic diagram of the puncture section of the puncture tube;

Fig. 4 is a structural schematic diagram of the puncture section of the puncture tube, marking marks near the puncture head;

Fig. 5 is a sectional view of the puncture section of the puncture tube;

Figure 6 is an enlarged view of A in Figure 5, showing the structure near the support;

Fig. 7 is a cross-sectional view of one end of the puncture tube connected to the support;

Fig. 8 is a cross-sectional view of the connecting part of the first wire and the second wire;

FIG. 9 is an enlarged view of a local area in FIG. 8 .

Reference signs:

100. Electrode ablation device based on ganglion cyst;

10. Puncture tube; 10a, first channel; 10b, puncture section; 10c, central axis; 10d, projection plane;

11, inner support tube; 111, puncture head; 111a, puncture surface;

12. Inner insulating tube; 13. Conductive tube; 14. Outer insulating tube; 15. Insulating sleeve;

20. Suction tube; 20a, second channel;

30. Support member; 30a, third channel; 31. Handpiece;

40. Electric heating components;

41. The first conductive member; 41a, the first contact surface;

42. The second conductive member; 42a, the second contact surface;

50. Power supply device; 51. Cable; 52. Plug;

53. Current control component; 531. First wire; 532. Second wire; 533. Current control board;

Detailed ways

Embodiments of the present disclosure will be described in more detail below with reference to the accompanying drawings. Although certain embodiments of the disclosure are shown in the drawings, it should be understood that the disclosure may be embodied in various forms and should not be construed as limited to the embodiments set forth herein. Rather, these examples are provided so that the understanding of this disclosure will be thorough and complete. It should be understood that the drawings and embodiments of the present disclosure are for exemplary purposes only, and are not intended to limit the protection scope of the present disclosure.

It should also be noted that, for the convenience of description, only the parts related to the related invention are shown in the drawings. In the case of no conflict, the embodiments in the present disclosure and the features in the embodiments can be combined with each other.

The present disclosure will be described in detail below with reference to the accompanying drawings and embodiments.

Referring to FIG. 1 and FIG. 2 , an electrode ablation device 100 based on a ganglion cyst includes: a support member 30 , a puncture tube 10 , a suction tube 20 , an electric heating assembly 40 and a power supply device 50 . Wherein, the puncture tube 10 is configured with a first channel 10a, and one end of the puncture tube 10 is formed with a puncture segment 10b, and the puncture segment 10b is inserted into the cyst; It is connected with the puncture tube 10, and the first channel 10a and the second channel 20a communicate with each other; the electric heating assembly 40 is arranged on the puncture section 10b, and the electric heating assembly 40 includes a first conductive member 41 and a second conductive member 42, the first conductive member 41 and the second conductive member 42 are used for releasing and receiving electric current; the power supply device 50 is arranged on the supporting member 30 and is used for supplying power to the electric heating component 40 .

When it is necessary to treat the ganglion cyst, the puncture section 10b of the puncture tube 10 penetrates into the cyst wall and contacts the interstitial fluid in the cyst wall, and then the power supply device 50 supplies power to the electric heating component 40, and then the first conductive member 41 releases the current , the second conductive member 42 receives current, and the current flows from the first conductive member 41 to the interstitial fluid in the cyst wall, and then flows into the second conductive member 42, so that the interstitial fluid in the vesicle is heated, and part of the interstitial fluid in the cyst wall is evaporated , and then the air pressure in the cyst wall rises, a part of the tissue fluid flows out through the puncture tube 10, the support member 30, and the suction tube 20, and a part of the tissue fluid is evaporated, and when all the tissue fluid in the vesicle is processed, the cyst wall will be heated During the process, protein denaturation occurs, which makes the cyst wall lose its biological activity, so that the interstitial fluid outside the cyst wall cannot be transported by the cyst wall to the interior of the cyst wall through active transport, thus avoiding the recurrence of the cyst.

The individual first conductive element 41 and the individual second conductive element 42 are insulated from each other.

In this application, the first conductive part 41 and the second conductive part 42 are insulated, so that the first conductive part 41 and the second conductive part 42 will not start from the first conductive part 41 and not pass through the capsule wall during operation. The internal tissue fluid directly flows to the second conductive member 42, so the puncture section 10b does not actively generate heat, and the part that generates heat is actually the tissue fluid in the vesicle; thus, the degree of damage to the vesicle wall will be more controllable. It can be foreseen that if the application is to heat the puncture section 10b, radiate heat from the puncture section 10b to the interstitial fluid, and then heat the capsule wall by the interstitial fluid, then during use, on the one hand, the puncture section 10b needs to be adjusted due to the difference in the size of the capsule rupture. On the other hand, it is necessary to pay attention to the changes of the interstitial fluid in the vesicle at any time. It is necessary to stop the operation when all the interstitial fluid is discharged, otherwise the hot puncture section will easily cause irreversible damage to the normal tissue when the cyst is extracted. It is very inconvenient in the actual operation, and it is easy to cause damage to normal tissues.

Referring to Fig. 3, the first conductive member 41 is partially exposed on the outside of the puncture tube 10 to form a first contact surface 41a; the second conductive member 42 is partially exposed on the outside of the puncture tube 10 to form a second contact surface 42a, the first The area ratio of the contact surface 41a to the second contact surface 42a is 1:0.9˜1.1.

The area ratio of the first contact surface 41a and the second contact surface 42a is substantially equal, which can ensure that the contact areas of the first conductive member 41 and the second conductive member 42 with the interstitial fluid are basically the same, so that the resistances of the current release end and the current output end are approximately equal, Avoid generating excessive heat at the first conductive member 41 or the second conductive member 42 .

Furthermore, the current supplied by the current supply device to the first conductive member 41 and the second conductive member 42 is an alternating current, wherein the frequency of the current is 100k˜500khz.

At this current frequency, it can adapt to most ganglion cysts. When the first conductive member 41 and the second conductive member 42 release the alternating current in the vesicle, it can only damage tissues with a thickness of 1-1.5 mm, so In the case of ensuring that the capsule wall can be destroyed so that the capsule wall cannot actively transport tissue fluid, the impact on surrounding tissue fluid is reduced.

Moreover, at this current frequency, the insulation between the first conductive member 41 and the second conductive member 42 is good, which can prevent the current from flowing from the first conductive member 41 to the second conductive member 42 in addition to the interstitial fluid passing through the vesicle. In addition, the puncture tube 10 also flows from the first conductive element 41 to the second conductive element 42 , thereby causing the puncture tube 10 itself to generate heat.

The reasons for avoiding the above problems are as follows:

(1) At the frequency of the alternating current, the current can break through the interstitial fluid in the cyst wall and generate a short-circuit current in the interstitial fluid. When the interstitial fluid in the cyst wall is evaporated, because the impedance of the cyst wall is too high , the current current cannot break down the impedance of the capsule wall, so no current will be generated in the normal tissues of the human body, and thus will not cause damage to the normal tissues of the human body. At the same time, the frequency of alternating current is higher than 100kHz, which can make the frequency of alternating current higher than the reciprocal of the reflex arc time of human muscle, so as to avoid the stimulation of muscles due to the low frequency of alternating current. In addition, during the heating of the interstitial fluid, the interstitial fluid can heat the cyst wall, thereby controlling the damage of the cyst wall to 1-1.5 mm.

(2) Although there is insulation between the first conductive member 41 and the second conductive member 42, as the current frequency increases, the insulating relationship between the first conductive member 41 and the second conductive member 42 will be broken, and then It will lead to the formation of current from the first conductive member 41 to the second conductive member 42 on the puncture tube 10, so that the puncture tube 10 itself will also generate heat, which will affect the performance of the product on the one hand, and cause unnecessary damage to the treatment on the other hand. Trouble.

Referring to Figures 4-5, the puncture tube 10 includes an inner support tube 11 fixedly connected to the support 30, an inner insulating tube 12 sleeved on the inner support tube 11, a conductive tube 13 sleeved on the inner insulating tube 12, and the inner support One end of the tube 11 is fixedly connected to the support member 30 , and the other end is provided with a piercing head 111 . There is a distance between the conductive tube 13 and the puncture head 111, the inner support tube 11 is a conductive material, the inner insulating tube 12 is an insulating material, the first conductive member 41 is configured as the puncture head 111 or is arranged on the puncture head 111, and the second conductive member 42 is configured as the conducting tube 13 or is arranged on the conducting tube 13 .

Referring to FIG. 5 , an insulating sheath 15 is sheathed on the inner insulating tube 12 , one side of the insulating sheath 15 is fixedly connected to the puncture head 111 , and the other side is fixedly connected to the conductive tube 13 .

Referring to FIG. 6 , the conductive tube 13 is sheathed with an outer insulating tube 14 , and there is a gap between the outer insulating tube 14 and the end of the conductive tube 13 opposite to the puncture head 111 , so that the conductive tube 13 is partially exposed outside the puncture tube 10 .

Referring to FIG. 8 , further, the power supply device 50 includes a first wire 531 and a second wire 532 , the first wire 531 is connected to the first conductive member 41 , and the second wire 532 is connected to the second conductive member 42 .

In the following, a complete embodiment is provided to illustrate the ganglion cyst-based electrode ablation device 100 in combination with a specific manner.

The electrode ablation device 100 based on a ganglion cyst includes a support member 30 , a puncture tube 10 , a suction tube 20 , an electric heating assembly 40 and a power supply device 50 .

Referring to Fig. 1 and Fig. 2, the support 30 is configured as a hand-held part 31, so that the medical staff can grab the support 31 through the hand-held part 31 to facilitate the operation of the support 30, and the support 30 is configured with a third channel 30a; The puncture tube 10 is configured with a first channel 10a, and the suction tube 20 is configured with a second channel 20a. The puncture tube 10 and the suction tube 20 are respectively fixedly connected to the two ends of the support member 30. In the technical solution provided by the application, the third The channel 30a is configured as a tubular channel formed in the support member 30, the ends of the suction tube 20 and the piercing tube 10 are both inserted into the third channel 30a, and the piercing tube 10 is inserted into the second channel 20a of the suction tube 20 , and the portion where the puncture tube 10 is inserted into the second channel 20a is sealed so that the puncture tube 10 and the suction tube 20 are in communication with each other and are sealed to each other.

In the remaining embodiments, both the puncture tube 10 and the suction tube 20 can be placed into the third channel 30a, and the puncture tube 10 and the suction tube 20 are respectively sealed with the inner wall of the third channel 30a, so that the third channel 30a serves as a passage through which the first passage 10a communicates with the second passage 20a.

1 and 2, one end of the puncture tube 10 is fixedly connected to the support member 30, and the other end is formed with a puncture section 10b. The electric heating assembly 40 is arranged on the puncture section 10b. The electric heating assembly 40 includes a first conductive member 41 and a second The conductive element 42, the first conductive element 41 and the second conductive element 42 are used to release or receive current.

Referring to Fig. 1 and Fig. 8, the power supply device 50 is arranged on the support member 30, and is used to provide power to the electric heating assembly 40. In this embodiment, the power supply device 50 includes a cable 51, a plug 52 and a current control assembly 53, and the current control The component 53 is integrated on the support member 30 , the cable 51 is connected to the current control component 53 , and the plug 52 is arranged at the end of the cable for accessing the power supply.

In a more specific embodiment:

Referring to Fig. 5, the puncture tube 10 includes an inner support tube 11, an inner insulating tube 12, a conductive tube 13, an outer insulating tube 14, and an insulating sleeve 15, wherein the inner support tube 11 is configured as a tubular structure, and the inner support tube 11 surrounds the formed The columnar space forms the main body of the first channel 10a. One end of the inner support tube 11 is fixedly connected to the suction tube 20, and the other end is configured with a puncture head 111. In this embodiment, the puncture head 111 is a part integrated at the end of the inner support tube 11 , so that the first channel 10a can pass through the puncture head 111 and the inner support tube 11, in the remaining embodiments, the hollow inner support tube 11 and the hollow puncture head 111 can be set separately, and the puncture head 111 and the inner support tube 11 is fixedly connected by welding, bonding, etc., the inner support tube 11 is inserted into the third channel 30a of the support member 30, and partially inserted into the second channel 20a of the suction tube 20, and the inner support tube 11 and the suction tube 20 For sealing fit, so that the suction tube 20 and the inner support tube 11 are fixedly connected.

Referring to FIG. 5 , the puncture head 111 is used to pull the puncture tube 10 into the human tissue, so the puncture head 111 is provided with a puncture surface 111 a. In this embodiment, the piercing surface 111a is configured as an inclined surface, so that the end of the piercing head 111 forms a sharp piercing end. In other structures, the piercing surface 111a can be set as a plurality of inner concave surfaces to form a multi-faceted structure and increase the sharpness of piercing.

The inner support tube 11 is made of metal and has good electrical conductivity. The puncture head 111 is configured as the aforementioned first conductive member 41 , and the outer surface of the puncture head 111 forms the first contact surface 41 a. In other embodiments, the first conductive member 41 can be fixedly connected to the puncture head 111 , and a conductor fixedly connected to the first conductive member 41 can be placed on the inner support tube 11 .

Referring to Figures 6-7, the inner insulating tube 12 is a tubular structure, the inner insulating tube 12 is made of insulating material, the inner insulating tube 12 is sleeved on the inner support tube 11, and one end of the inner insulating tube 12 is fixedly connected to the piercing head 111, The other end is inserted into the third channel 30a, and there is a gap between the inner insulating tube 12 and the suction tube 20, so that the inner support tube 11 is partially exposed in the third channel 30a.

Referring to Fig. 6, the conductive pipe 13 is a tubular structure, the conductive pipe 13 is made of stainless steel in this embodiment, has good electrical conductivity, the conductive pipe 13 is sleeved on the inner insulating pipe 12, and the conductive pipe 13 and the inner insulating pipe 12 are fixedly connected One end of the conductive tube 13 extends to the piercing section 10b, and the other end is inserted into the third channel 30a. The conductive tube 13 is configured as the aforementioned second conductive member 42 . In the rest of the embodiments, the second conductive member 42 can also be configured as two parts independent of the conductive pipe 13, and the conductive pipe 13 and the second conductive member 42 are in contact with each other, so that the second conductive member 42 can input current to the conductive tube 13 .

Referring to FIG. 6 , there is a gap between the conductive tube 13 and the puncture head 111 , so the conductive tube 13 and the puncture head 111 are insulated from each other. In order to further increase the insulation strength between the conductive tube 13 and the piercing head 111, an insulating sleeve 15 is sheathed on the inner insulating tube 12. One side of the insulating sleeve 15 is in contact with the conductive tube 13, and the other side is in contact with the piercing head 111. In this way, the degree of insulation between the insulating sleeve 15 and the piercing head 111 will be further improved. In this embodiment, the insulating sleeve 15 is a separate component sleeved on the inner insulating tube 12 , and in other embodiments, the insulating sleeve 15 is a structure based on the inner insulating tube 12 . In this embodiment, the first conductive member 41 and the second conductive member 42 are insulated from each other by arranging the insulating sleeve 15 and the inner insulating tube 12. It can be foreseen that in other embodiments, the two There is no directly connected conductor between the conductive elements 41 and they are insulated.

Referring to Fig. 6 and Fig. 7, the outer insulating tube 14 is a tubular structure, and the outer insulating tube 14 is made of insulating material, and insulating rubber can be selected. The outer insulating tube 14 is wrapped on the outside of the conductive tube 13, and the outer insulating tube 14 and the conductive tube 13 are fixedly connected. There is a gap between the outer insulating tube 14 and the conductive tube 13 and the end opposite to the puncture head 111, so that the conductive tube 13 is partially exposed to the puncture. The outer side of the tube 10, and the exposed area of the conductive tube 13 in the gap is 1:1 with the exposed area of the puncture head 111. One end of the outer insulating tube 14 is opposite to the puncture head 111, and the other end is inserted into the third channel 30a, and the outer wall of the outer insulating tube 14 is in a sealing fit with the inner wall of the third channel 30a, and the outer insulating tube 14 is inserted into the third channel 30a. There is a gap between one end and the end of the conductive tube 13 , so the conductive tube 13 has a partially exposed surface in the third channel 30 a.

8-9, the power supply device 50 includes a cable 51, a plug 52 and a current control assembly 53, the plug 52 is arranged at the end of the cable 51 for external power supply, the current control assembly 53 includes a current regulation board 533, a first wire 531, The second wire 532, the current regulation board 533 is connected with the cable, the cable is connected to the current regulation board 533, the current regulation board 533 is integrated with a control circuit and a control chip, the required current can be modulated through the control chip, the first wire 531 and The second wires 532 are respectively the current output end and the current input end of the current regulation board, the first wire 531 is connected to the first conductive member 41, and the second wire 532 is connected to the second conductive member 42. In this embodiment, the first wire 531 and the second wire 532 are partially placed in the third channel 30a, the first wire 531 is fixedly connected to the inner support tube 11, and the part where the first wire 531 is connected to the inner support tube 11 is located between the inner insulating tube 12 and the suction tube 20 gap between. The second wire 532 is fixedly connected to the conductive tube 13 , and the part where the second wire 532 is connected to the conductive tube 13 is located on the exposed surface of the conductive tube 13 in the third channel 30 a. In this embodiment, the inner insulating sheath 15 and the outer insulating sheath 15 are exposed partly compared to the ends of the inner support pipe 11 and the conductive pipe 13. In other embodiments, the inner insulating sheath 15 can also be exposed. Offer the hole that is used for inserting wire on the outer insulating sheath 15.

The above descriptions are only some preferred embodiments of the present disclosure and illustrations of the applied technical principles. Those skilled in the art should understand that the scope of the invention involved in the embodiments of the present disclosure is not limited to the technical solution formed by the specific combination of the above-mentioned technical features, but also covers the above-mentioned invention without departing from the above-mentioned inventive concept. Other technical solutions formed by any combination of technical features or equivalent features. For example, a technical solution formed by replacing the above-mentioned features with technical features having similar functions disclosed in (but not limited to) the embodiments of the present disclosure.

Claims (10)

1. An electrode ablation device based on ganglion cyst, characterized in that it comprises: a puncture tube configured with a first channel, one end of which is formed with a puncture section, and the puncture section is inserted into the cyst; Suction tube, constructing the second channel; The support, the puncture tube and the suction tube are respectively connected to the support, and the first channel and the second channel communicate with each other; The electric heating component is arranged on the puncture section; The power supply device is arranged on the support and is used to supply power to the electric heating component; Wherein, the electric heating assembly includes a first conductive element and a second conductive element for releasing and receiving electric current, the puncture tube is placed in the cyst, and the first conductive element and the second conductive element release and receive electric current to heat the interstitial fluid of the cyst. 2 . The ganglion cyst-based electrode ablation device according to claim 1 , characterized in that: the single first conductive element and the single second conductive element are insulated from each other. 3. The electrode ablation device based on ganglion cyst according to claim 1, characterized in that: the first conductive part is exposed on the outside of the puncture tube to form the first contact surface; the second conductive part is exposed on the outside of the puncture tube The outer side is to form the second contact surface, and the area ratio of the first contact surface to the second contact surface is 1:0.9˜1.1. 4. The electrode ablation device based on ganglion cyst according to claim 1, characterized in that: the current delivered by the current supply device to the first conductive member and the second conductive member is an alternating current, wherein the frequency of the current is 100kHz-500kHz . 5. The electrode ablation device based on ganglion cyst according to any one of claims 1 to 4, characterized in that: the puncture tube includes an inner support tube fixedly connected to the support, a puncture head fixedly connected to the inner support tube, The inner insulating tube sleeved on the inner support tube, the conductive tube sleeved on the inner insulating tube, there is a distance between the conductive tube and the puncture head, the inner insulating tube is made of insulating material, and the first conductive part is configured as a puncture head or arranged on the On the puncture head, the second conductive member is configured as a conductive tube or arranged on the conductive tube. 6. The electrode ablation device based on ganglion cyst according to claim 5, characterized in that: the inner insulating tube is provided with an insulating sleeve, one side of the insulating sleeve is fixedly connected with the puncture head, and the other side of the conductive tube is fixedly connected. 7. The electrode ablation device based on ganglion cyst according to claim 6, characterized in that: the conductive tube is sheathed with an outer insulating tube, and there is a gap between the outer insulating tube and the end of the conductive tube opposite to the puncture head, so that the conductive tube Partially exposed on the outside of the puncture tube. 8. The electrode ablation device based on ganglion cyst according to claim 7, characterized in that: the power supply device includes a first wire and a second wire, the first wire is connected to the first conductive member, and the second wire is connected to the second conductive member. pieces. 9. The electrode ablation device based on ganglion cyst according to claim 8, characterized in that: the support member is configured with a third channel, and the ends of the puncture tube and the suction tube are placed into the third channel. 10. The electrode ablation device based on ganglion cyst according to claim 9, characterized in that: One end of the inner insulating tube is fixedly connected to the puncture head, the other end is inserted into the third channel, and there is a gap between the inner insulating tube and the suction tube, the first lead is fixedly connected to the inner support tube, and the first lead is connected to the inner support tube. partly located in the gap between the inner insulating tube and the suction tube; There is a gap between the end of the outer insulating tube inserted into the third channel and the end of the conductive tube, the second wire is fixedly connected to the conductive tube, and the part where the second wire is connected to the conductive tube is located on the exposed surface of the conductive tube in the third channel .

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