Bipolar high-frequency electric snare

Abstract

The invention discloses a bipolar high-frequency electric snare, which relates to the field of medical equipment and comprises a ferrule assembly and one or more sleeves, and the sleeves are used for fixing the ferrule assembly. By the adoption of the bipolar snare, current can form a loop, instrument short circuit can be avoided, damage to an intestinal wall serosa layer can be reduced, the possibility of complications such as bleeding and perforation can be reduced, and the bipolar snare has the advantages of being easy to maintain, disassemble, assemble and adjust parameters due to the adoption of the modular design. The invention aims to provide the bipolar high-frequency electric snare which has the advantages of cooperative operation, high operation precision and modular design.

Description

TECHNICAL FIELD

[0001] The present application belongs to the field of medical devices, and particularly relates to a bipolar high-frequency electric snare. BACKGROUND

[0002] Currently, monopolar electric snares are used in the market. The positive pole of a high-frequency device is connected with the electrode of the electric snare, and the negative pole is connected with a negative pole plate which is attached to the surface of the human body. When the power supply of the high-frequency device is turned on, the electric current passes through the electric snare, the human body and the negative pole plate to form a current loop to achieve the effect of cutting polyps. During operation, if the negative pole plate is not tightly attached, the electric current passing through the negative pole plate will generate high temperature, which is easy to cause burns on the contact part of the human body.

[0003] The prior art is an invention patent named bipolar electrosurgical snare, and the publication number of the invention patent is US20050171532A1. The invention discloses a bipolar electrosurgical instrument comprising an introducer having a channel therein and an electrically conductive snare slidably positioned within the channel and slidable between an undeployed position in which the electrically conductive snare is substantially retracted within the channel and a deployed position in which a distal portion of the snare extends outwardly from the channel. The electrically conductive snare is substantially insulated along its length but has an active electrode and a return electrode exposed through predetermined exposed portions. The instrument further comprises a retaining element at the distal end of the snare for securing the distal end of the snare to the introducer to form a loop configuration of the snare, and at least one fluid delivery channel extending through the introducer between a fluid inlet and a fluid outlet at the distal end of the introducer and positioned adjacent the exposed portions of the snare. The operation steps of the invention are relatively complicated, and the cutting effect is poor. SUMMARY

[0004] The purpose of the present application is to provide a bipolar high-frequency electric snare which cooperates, has high operation precision and has a modular design.

[0005] The technical scheme adopted by the present application to achieve the above purpose is as follows: A bipolar high-frequency electric snare comprises a snare assembly and a sleeve, and the sleeve is used for fixing the snare assembly. The sleeve is one or more.

[0006] The snare assembly comprises a first wire and a second wire which are not in contact with each other. The free ends of the first wire and the second wire are connected through a structural member. An insulating tube is wrapped on the first wire along the extension direction of the first wire, and the first wire has an exposed section.

[0007] The first wire and the second wire in the structural member have a non-contact spacing distance. The first wire has an exposed section which is not wrapped with the insulating tube on the side of the structural member.

[0008] Snares are commonly used to cut polyps or lesions. In existing technologies, monopolar snares are typically used for this purpose. However, when using a monopolar snare, the negative electrode plate needs to be attached to the patient during the procedure. This is not only cumbersome, but also carries the risk of overheating and burns if the negative electrode plate is not properly attached or falls off, increasing the patient's risk, or even causing a short circuit and instrument failure. This application uses a bipolar snare, where two electrodes are connected via a first and a second cutting wire. During the snare removal of polyps or lesions, both the first and second cutting wires simultaneously contact the tissue. In other words, the current flows either along the first cutting wire, through the tissue, and then through the second cutting wire, or vice versa. This ensures a current loop during lesion removal and prevents short circuits. Furthermore, the bipolar snare reduces damage to the intestinal wall serosa and lowers the likelihood of complications such as bleeding and perforation. This application employs a modular design, facilitating maintenance, disassembly, assembly, and parameter adjustment.

[0009] The first and second filaments have free ends in the direction of extension of the outer sheath, and the free ends of the first and second filaments converge through a structural component for non-contact connection. It should be noted that the structural component is made of insulating material to prevent short circuits between the first and second filaments. A loop is formed between the first and second filaments and the sheath and the structural component; the loop can be elliptical, polygonal, or circular, etc.

[0010] Furthermore, the ends of the structural components furthest from the first and second cutting wires are rounded. When the outer sheath enters the human body through the endoscopic forceps channel, the collar assembly should be in a closed state, with the collar assembly entirely housed within the outer sheath. However, the structural component acts as a limiting element, initially positioned on the outer side of the outer sheath. By rounding the ends of the structural components furthest from the first and second cutting wires, the smoothness of the outer sheath's entry into the human body is facilitated.

[0011] Furthermore, alternating current is used for the first and second cutting wires. Preferably, high-frequency alternating current is used for the first and second cutting wires. High-frequency alternating current is used to cauterize and remove diseased tissue and to stop bleeding from the wound.

[0012] Furthermore, both the first and second filaments are made of metal. Even further, both the first and second filaments are made of conductive metal.

[0013] The first and second cutting wires are fixed by a sleeve. The sleeve has at least one sleeve hole. When the sleeve has one sleeve hole, both the first and second cutting wires pass through this sleeve hole and are fixed by heat shrinking or bonding. When the sleeve has two sleeve holes, the first and second cutting wires pass through their respective sleeve holes and are fixed by heat shrinking or bonding. When the sleeve has more than two sleeve holes, the first and second cutting wires pass through symmetrically arranged sleeve holes. It should be noted that the first and second cutting wires can pass through the same sleeve hole and be fixed by heat shrinking or bonding. Unused sleeve holes can achieve air pressure balance inside and outside the outer sheath, improve the smoothness of the movement of the ring assembly, improve the smoothness of the ring assembly's unfolding and closing, and thus improve the operating accuracy of the bipolar high-frequency electric ring ring device.

[0014] It should be noted that the cannula is positioned along the outer sheath. When the loop assembly unfolds and closes, the cannula moves along the extension direction of the outer sheath. The outer sheath can be made of a flexible material. When the outer sheath enters the body through the endoscopic forceps channel, it is usually passively bent due to the physiological curvature of the body. Existing technologies typically use a double-lumen tube to achieve the reciprocating movement of the first and second cutting wires. However, due to the bending, the strokes of the first and second cutting wires are inconsistent, resulting in the loop assembly being unable to completely cut the lesion tissue during unfolding and closing. More specifically, when the loop assembly is closed to remove the lesion tissue, the shorter cutting wire preferentially enters the outer sheath, while the longer cutting wire cannot be completely retracted into the outer sheath, thus failing to completely remove the lesion tissue and causing instrument failure. Compared with existing technologies, this application, through the cannula design, achieves synchronous extension and retraction of the first and second cutting wires on both sides within the outer sheath, even when the outer sheath is bent, thereby ensuring complete removal of the lesion tissue.

[0015] Furthermore, the bushing is made of insulating material.

[0016] There are one or more sleeves. The sleeve can further improve the smoothness of the movement of the sleeve inside the outer sheath when it is bent. In addition, the sleeve can also protect the first and second filaments, preventing them from bending, breaking or failing due to excessive bending angle.

[0017] Because the first cutting wire is covered with an insulating tube along its extension direction, the insulating tube prevents the need for additional insulating pads or sleeves to separate the first and second cutting wires during cannulation. This helps reduce the inner diameter of the cannula, resulting in a reduction in the overall diameter and volume of the cannula. This facilitates adaptation to different outer sheaths, enabling the cannula to handle a wider range of surgical environments. Furthermore, as the cannula's weight is reduced, the control of the opening and closing process of the loop assembly can be made more precise, further improving surgical accuracy and success rates.

[0018] The insulating tube covers the first cutting wire and is immobile during normal operation. This ensures that the insulating tube cannot move freely along the length of the first cutting wire during the surgical procedure, preventing a short circuit between the first and second cutting wires. Furthermore, the fixed insulating tube ensures that the length of the exposed section on the first cutting wire remains constant without human intervention, improving cutting precision.

[0019] It should be noted that the part of the insulating tube that comes into contact with the tissue will not cause damage to the tissue and cannot cut the diseased tissue.

[0020] The first cutting wire has an exposed section that is not wrapped with an insulating tube. The first and second cutting wires can only cut tissue through the exposed sections of the second and first cutting wires. This design reduces the effective cutting length of the first cutting wire, thereby achieving more concentrated energy and improving both cutting efficiency and cutting effect.

[0021] Furthermore, it should be noted that the exposed section is located on one side of the structural component. When the sliding component drives the collar assembly to unfold and close in the outer sheath, the exposed section of the first cutting wire and the second cutting wire can cut the polyp or lesion component.

[0022] Furthermore, the length of the exposed segment should be no less than 6mm. It should be noted that, due to the needs of different surgical environments, the length of the exposed segment can be adjusted or replaced to adjust or replace the ringing device to meet the needs of different surgical environments, thereby reducing costs and improving efficiency.

[0023] According to one embodiment of the present invention, it further includes an outer sheath tube and a handle assembly. The outer sheath tube is connected to the handle assembly, and the collar assembly is housed within the outer sheath tube. The handle assembly includes a handle base, and a sliding member that can move along a first direction is slidably mounted on the handle base. The other ends of the first and second slicing wires are both connected to the sliding member. The sliding member is used to drive the collar assembly to unfold and close within the outer sheath tube.

[0024] The outer sheath is used to house the ring assembly. A sliding member drives the ring assembly to unfold and close within the outer sheath, thereby allowing manual control of the unfolding and closing of the ring assembly by manipulating the sliding member. The handle base has a sliding member that can move along a first direction. In this application, the first direction includes, but is not limited to, the length direction of the handle assembly or an extension direction of the handle length direction as a base direction.

[0025] It should be noted that energy is supplied to the first and second filaments via a sliding component. More specifically, high-frequency alternating current is supplied to the first and second filaments via the sliding component to enable normal cutting of the first and second filaments.

[0026] Furthermore, the handle base is provided with a first mating component that engages in the first direction, and the sliding component is provided with a second mating component. The engagement of the first and second mating components allows the sliding body to slide along the first direction. The first mating component includes, but is not limited to, a guide groove and a guide rod, and the second mating component includes, but is not limited to, a guide block and a guide opening.

[0027] Furthermore, the outer sheath is made of PTFE and has a single-lumen structure.

[0028] According to one embodiment of the present invention, both the handle base and the slider are provided with at least one gripping ring.

[0029] The gripping ring is used to enable the operator to control the snare. Furthermore, the gripping ring on the handle base is located at the end of the handle base away from the outer sheath, and there are no more than two gripping rings on the handle base. The sliding member has at least one gripping ring, which can be located on the side of the sliding member or surrounding it. Even further, the gripping ring on the sliding member can be either closed or open.

[0030] Furthermore, a flexible ring can be provided on the inner wall of the gripping ring. The flexible ring can reduce the pressure on the operator's fingers during the use of this device, which helps to improve the operator's operating accuracy and prevent fatigue during long-term operation.

[0031] Furthermore, the inner wall of the gripping ring has a curved structure. This curved structure prevents the operator from experiencing reduced accuracy due to fixed pressure on the fingers while moving the gripping ring along the handle base, improves the grip experience, and also provides an anti-slip effect.

[0032] According to one embodiment of the present invention, the sliding member includes a sliding base, and the sliding base is provided with a conductive component that is compatible with the conductive component for supplying power to the collar assembly.

[0033] According to an embodiment of the present invention, a base corresponding to a conductive component is provided on a sliding substrate, and a base hole corresponding to a first filament and a second filament is provided on the base hole, with a drum spring provided inside the base hole.

[0034] It should be noted that the handle base is provided with a sliding groove, which is configured to cooperate with the base. In other words, when the sliding base drives the base to move in the first direction, the base and the sliding groove cooperate to realize the base moving in the first direction. During this process, the base will drive the first and second shredded wires to move in the first direction.

[0035] Furthermore, the base is also equipped with a conduit, which is connected to the base by mechanical embedding or bonding. The conduit is used to control the first and second cutting wires; in other words, the conduit houses the first and second cutting wires and is connected to an outer sheath. It should be noted that when the sliding member moves to a limit distance away from the outer sheath, the conduit and the outer sheath remain in communication. The conduit design prevents the first and second cutting wires from bending or detaching during the movement of the sliding member in the first direction and ensures consistent movement of the first and second cutting wires.

[0036] Furthermore, the conduit is made of a rigid material.

[0037] It should be noted that the base and the sliding base can be snap-fitted together. The sliding base has a base groove corresponding to the base hole. A third mating component is provided on the side of the conductive base, and a fourth mating component is provided on the inner wall of the base groove. The third and fourth mating components achieve a mating connection between the conductive base and the base, ensuring that the conductive base supplies power to the first and second cutting wires, preventing separation or poor contact between the conductive base and the base during operation, which could lead to surgical failure or harm to the patient. More specifically, the third mating component is a snap-fit ​​block, and the fourth mating component is a mating groove; that is, the snap-fit ​​block and the mating groove are fastened and fixed together.

[0038] The first and second dicing wires are respectively provided with base holes, and the conductive components are correspondingly arranged with the base holes to ensure that the conductive components can supply power to the first and second dicing wires. More specifically, the ends of the first and second dicing wires away from the structural components are embedded in the base holes of the base and are respectively connected to drum springs. The two drum springs are configured to cooperate with pins, and the power supply to the first and second dicing wires is realized through the pins of the conductive components.

[0039] The drum springs are embedded into their respective base holes.

[0040] Furthermore, the drum spring has a flared structure on both sides. The drum spring facilitates a firm fit with the pin, thereby improving the stability of power supply to the first and second wire cutters. Moreover, the drum spring is set perpendicular to the first moving direction, which allows the perpendicularity between the pin and the drum spring to be maintained during the movement of the base, thus maintaining the state of the conductive components and reducing the risk of the conductive components falling off.

[0041] According to one embodiment of the present invention, the conductive component includes a conductive substrate, and symmetrically arranged conductive inserts are provided in the conductive substrate. The conductive inserts have slots on the side facing the sliding substrate, and pins protruding from the conductive substrate are fitted in the slots.

[0042] The conductive component is used to connect to an external high-frequency generator and transfer the current from the external high-frequency generator to the first or second filament. The corresponding arrangement of the pins and slots allows for more flexible mating between the pins and conductive inserts. It should be noted that the slot design ensures a contact connection between the pins and the conductive inserts. It should also be noted that the pins are designed to mate with a drum spring.

[0043] It should be noted that, due to the use of high-frequency alternating current, the fit between each pin and each drum spring is interchangeable. In other words, there is no positive or negative distinction between the fit between the conductive components and the base, which facilitates the assembly of the conductive components and the base.

[0044] Furthermore, the pins are replaceable. This allows for a modular design of the conductive connector, enabling the pins to be replaced or manufactured according to different hole sizes, thus saving costs and increasing the ease of replacement.

[0045] Furthermore, the slot is equipped with a buffer section. It should be noted that the buffer section reduces the possibility of damage and bending of the pin during its engagement with the drum spring. Specifically, when the pin is subjected to a large impact force along its length, the buffer section absorbs the impact while controlling the pin's position. This ensures that the length of the pin extending beyond the conductive substrate is controllable and limited. When the pin retracts into the buffer section after being compressed, it has a force that returns it to its original position, allowing the length of the pin extending beyond the conductive substrate to return to its original position. It should be noted that this force includes, but is not limited to, elastic force or pressure.

[0046] Furthermore, the conductive insert is bent. Bending the conductive insert improves the slot's ability to absorb impact forces and allows it to adapt to external temperature changes, preventing the conductive insert from losing connection with the pin or its input spring after temperature fluctuations. In addition, the precision requirements for bent conductive inserts are lower than those for straight conductive inserts, which helps control production and replacement costs.

[0047] Furthermore, the pins are made of conductive material.

[0048] More specifically, the pins are made of conductive metal. Since the device inevitably involves the pins and conductive substrate interacting with the corresponding receiving device during use, the choice of pin material affects the lifespan of both the pins and the overall device. Using metal can improve the pin's lifespan and reduce the possibility of bending or breaking.

[0049] During the removal of diseased tissue, the high-frequency current sequentially passes through the electrode plug, conductive insert, pin, drum spring, first cutting wire, diseased tissue, second cutting wire, drum spring, pin, conductive insert, and electrode plug, finally returning to the high-frequency generator. The high-frequency current then passes through the diseased tissue, utilizing its thermal effect to complete the removal of the diseased tissue.

[0050] According to one embodiment of the present invention, a plurality of limiting blocks are provided on the handle base, the limiting blocks being used to limit the extreme positions of the sliding member.

[0051] The limit block can control the extreme distance of the sliding part along the first direction, which helps the operator to control the distance and prevents the position of the ring assembly from being over-positioned due to tension or mistakes during the operation of the sliding part.

[0052] Furthermore, the position of the limiting block is adjustable. This allows for control over the unfolding size of the ring assembly to adapt to different surgical environments.

[0053] According to one embodiment of the present invention, a protective sleeve is provided on the outer sheath tube along its extension direction, and the protective sleeve can be connected to the handle base.

[0054] The sheath sleeve is used to protect the outer sheath. The sheath sleeve can be fixed to the handle base by means of snap-fit ​​or threaded connection, not limited to snap-fit ​​or threaded connection.

[0055] It should be noted that a connector is provided on the side of the handle base facing the collar assembly. The connector is used to connect and secure the outer sheath. The connector includes a connecting base. The connecting base is made of metal or rigid plastic. The connecting base has a fixed end and a connecting end, wherein the fixed end connects to the handle base, and the connecting end has a snap-fit ​​protrusion for connecting to the outer sheath. Attached Figure Description

[0056] Figure 1 This is a schematic diagram showing the fit between the ferrule assembly and the bushing. Figure 2 A schematic diagram of a bipolar high-frequency electric ring catcher when the ring catcher assembly is deployed; Figure 3 A schematic diagram of a bipolar high-frequency electric ring catcher when the ring assembly is closed; Figure 4 A schematic diagram of a bipolar high-frequency electric coil device; Figure 5 for Figure 4 Enlarged view of point A in the middle; Figure 6 This is a schematic diagram showing the direction of current flow during the removal of diseased tissue; Figure 7 for Figure 4 Enlarged view of point C in the middle; Figure 8 A schematic diagram of the assembly of the conductive component and the sliding component; Figure 9 This is a schematic diagram of the conductive component structure; Figure 10 This is a three-dimensional schematic diagram of the conductive insert; Figure 11 for Figure 4 Enlarged view of point B in the middle; Figure 12 This is a schematic diagram of the connector.

[0057] Reference numerals: Ring assembly 1, First filament cutter 11, Second filament cutter 12, Structural component 13, Insulating tube 14, Exposed section 15, Sleeve 2, Outer sheath tube 3, Protective sleeve 31, Handle assembly 4, Handle base 41, Gripping ring 42, Limiting block 43, Slide groove 44, Sliding component 5, Sliding base 51, Conductive component 6, Conductive base 61, Conductive insert 62, Slot 63, Pin 64, Third mating component 65, Fourth mating component 66, Base 7, Base hole 71, Drum spring 72, Conduit 73, Base groove 74, Connector 8, Connecting base 81, Fixed end 82, Connecting end 83, Snap-fit ​​protrusion 84. Detailed Implementation

[0058] The technical solution of the present invention will be further described in detail below with reference to specific embodiments and accompanying drawings: Example 1: like Figures 1-12 As shown, a bipolar high-frequency electric coil holder includes a coil assembly 1 and a sleeve 2, the sleeve 2 being used to fix the coil assembly 1, and there may be one or more sleeves 2.

[0059] The ring assembly 1 includes a first cut wire 11 and a second cut wire 12 that do not contact each other. The free ends of the first cut wire 11 and the second cut wire 12 are connected by a structural member 13. The first cut wire 11 is covered with an insulating tube 14 along its extension direction. The first cut wire 11 has an exposed section 15.

[0060] The first filament 11 and the second filament 12 within the structural component 13 have a non-contact interval, and the first filament 11 has an exposed section 15 on the side of the structural component 13 that is not covered by the insulating tube 14.

[0061] Snares are commonly used to cut polyps or lesions. In existing technologies, monopolar snares are typically used. However, with monopolar snares, the negative electrode plate needs to be attached to the patient during the procedure. This is not only cumbersome, but also carries the risk of overheating and burns if the negative electrode plate is not properly attached or falls off, increasing the patient's risk, or even causing a short circuit and instrument failure. This application uses a bipolar snare, where two electrodes are connected via a first cutting wire 11 and a second cutting wire 12. During the snare removal of polyps or lesions, both the first and second cutting wires 11 and 12 simultaneously contact the tissue. In other words, the current flows either along the first cutting wire 11, through the tissue, and then along the second cutting wire 12, or vice versa. This ensures a current loop during lesion removal and prevents short circuits. Furthermore, the bipolar snare reduces damage to the intestinal wall serosa and lowers the likelihood of complications such as bleeding and perforation. This application employs a modular design, facilitating maintenance, disassembly, assembly, and parameter adjustment.

[0062] The first filament 11 and the second filament 12 have free ends in the extending direction of the outer sheath 3, and the free ends of the first filament 11 and the second filament 12 converge through the structural member 13 for non-contact connection. It should be noted that the structural member 13 is made of insulating material to prevent short circuits between the first filament 11 and the second filament 12. A collar is formed between the first filament 11 and the second filament 12 and the structural member 13. The collar can be elliptical, polygonal, or circular, etc. In this embodiment, an elliptical collar is used as an example.

[0063] Furthermore, the end of the structural component 13 furthest from the first cutting wire 11 and the second cutting wire 12 is rounded. When the outer sheath 3 enters the human body through the endoscopic forceps channel, the collar assembly 1 should be in a closed state. At this time, the collar assembly 1 is entirely housed inside the outer sheath 3, but the structural component 13 will play a limiting role, that is, the limiting is initially located on the outside of the end of the outer sheath 3. By making the end of the structural component 13 furthest from the first cutting wire 11 and the second cutting wire 12 rounded, it is beneficial to achieve a smooth entry of the outer sheath 3 into the human body.

[0064] Furthermore, the current flowing through the first cutting wire 11 and the second cutting wire 12 is alternating current. Preferably, the current flowing through the first cutting wire 11 and the second cutting wire 12 is high-frequency alternating current. High-frequency alternating current is used to cauterize and remove diseased tissue and to stop bleeding from the wound.

[0065] Furthermore, the first filament 11 and the second filament 12 are made of metal. Even further, the first filament 11 and the second filament 12 are made of conductive metal.

[0066] The first slicing wire 11 and the second slicing wire 12 are fixed by the sleeve 2. The sleeve 2 has at least one sleeve hole.

[0067] When the sleeve 2 has one sleeve hole, both the first cutting wire 11 and the second cutting wire 12 pass through this sleeve hole and are fixed by heat shrinking or bonding. When the sleeve 2 has two sleeve holes, the first cutting wire 11 and the second cutting wire 12 pass through the corresponding sleeve holes respectively and are fixed by heat shrinking or bonding. When the sleeve 2 has more than two sleeve holes, the first cutting wire 11 and the second cutting wire 12 pass through symmetrically arranged sleeve holes. It should be noted that the first cutting wire 11 and the second cutting wire 12 can pass through the same sleeve hole and be fixed by heat shrinking or bonding. Unused sleeve holes can achieve air pressure balance inside and outside the outer sheath 3, improve the smoothness of the movement of the ring assembly 1, improve the opening and closing flow of the ring assembly 1, and thus improve the operating accuracy of the bipolar high-frequency electric ring ring device.

[0068] It should be noted that the sleeve 2 is set along the outer sheath 3. When the collar assembly 1 is opened and closed, the sleeve 2 will move along the extension direction of the outer sheath 3. The outer sheath 3 can be made of a flexible material. When the outer sheath 3 enters the human body through the endoscopic forceps channel, it will be passively bent due to the physiological curvature of the human body. Existing technologies typically use a double-lumen tube to achieve the reciprocating movement of the first cutting wire 11 and the second cutting wire 12. However, due to the bending, the stroke of the first cutting wire 11 and the second cutting wire 12 will be inconsistent, which will result in the lasso assembly 1 being unable to completely cut the lesion tissue during the opening and closing process. More specifically, when the lasso assembly is closed to remove the lesion tissue, the shorter cutting wire will preferentially enter the outer sheath 3, while the longer cutting wire will not be able to be completely retracted into the outer sheath 3, which will result in the inability to completely remove the lesion tissue and cause the instrument to fail. Compared with the existing technology, this application achieves synchronous extension and retraction of the first cutting wire 11 and the second cutting wire 12 on both sides in the outer sheath 3 even when the outer sheath 3 is bent, thereby ensuring that the lesion tissue can be completely removed.

[0069] Furthermore, the sleeve is made of insulating material.

[0070] There are one or more sleeves 2. The sleeves 2 can further improve the smoothness of the movement of the sleeve inside the outer sheath when it is bent. The sleeves 2 can also protect the first and second filaments, preventing the first and second filaments from bending, breaking or failing due to excessive bending angle.

[0071] Because the first cutting wire 11 is covered with an insulating tube 14 extending along its direction. The insulating tube 14 can prevent the first cutting wire 11 and the second cutting wire 12 from needing to be separated by an additional insulating pad or insulating tube 14 when the sheath 2 is fixed, which is beneficial to reducing the inner diameter of the sheath 2, and can reduce the overall diameter and volume of the sheath 2. This is beneficial to adapting to different outer sheath tubes 3, and thus can cope with more surgical environments.

[0072] The insulating tube 14 covers the first cutting wire 11 and cannot move during normal operation. This ensures that the insulating tube 14 cannot move freely along the length of the first cutting wire 11 during the surgical procedure, preventing a short circuit between the first and second cutting wires 11 and 12. Furthermore, the fixed insulating tube 14 ensures that the length of the exposed section 15 on the first cutting wire 11 remains constant without human intervention, thus improving cutting accuracy.

[0073] It should be noted that the part of the insulating tube 14 that comes into contact with the tissue will not cause damage to the tissue and cannot cut the diseased tissue.

[0074] The first cutting wire 11 has an exposed section 15 that is not wrapped with the insulating tube 14. The first cutting wire 11 and the second cutting wire 12 can only cut tissue through the exposed section 15 of the second cutting wire 12 and the first cutting wire 11. This setting can reduce the effective cutting length of the first cutting wire 11, thereby achieving more concentrated energy and improving both cutting efficiency and cutting effect.

[0075] Furthermore, it should be noted that the exposed section 15 is located on one side of the structural member 13. When the sliding member 5 drives the collar assembly 1 to unfold and close in the outer sheath tube 3, the exposed section 15 of the first cutting wire 11 and the second cutting wire 12 can cut the polyp or lesion component.

[0076] Furthermore, the length of the exposed section 15 is not less than 6 mm. It should be noted that, due to the needs of different surgical environments, the length of the exposed section 15 can be adjusted or replaced to adjust or replace the ringing assembly 1, so that the ringing device can meet the needs of different surgical environments, thereby reducing costs and improving efficiency.

[0077] It also includes an outer sheath tube 3 and a handle assembly 4. The outer sheath tube 3 is connected to the handle assembly 4. The collar assembly 1 is housed inside the outer sheath tube 3. The handle assembly 4 includes a handle base 41. The handle base 41 is slidably fitted with a sliding member 5 that can move along a first direction. The other ends of the first shredded wire 11 and the second shredded wire 12 are both connected to the sliding member 5. The sliding member 5 is used to drive the collar assembly 1 to unfold and close in the outer sheath tube 3.

[0078] The outer sheath 3 is used to house the ring assembly 1. The ring assembly 1 is opened and closed within the outer sheath 3 by means of a slider 5, thereby allowing manual control of the opening and closing of the ring assembly by manipulating the slider 5. The handle base 41 has a slider 5 that can move along a first direction. In this application, the first direction includes, but is not limited to, the length direction of the handle assembly 4 or an extension direction of the length direction of the handle assembly 4 as the base direction.

[0079] It should be noted that the sliding member 5 provides energy to the first shredded wire 11 and the second shredded wire 12. More specifically, the sliding member 5 provides high-frequency alternating current to the first shredded wire 11 and the second shredded wire 12 to achieve normal cutting of the first shredded wire 11 and the second shredded wire 12.

[0080] Furthermore, the handle base 41 is provided with a first mating component that engages in the first direction, and the sliding member 5 is provided with a second mating component. The engagement of the first and second mating components allows the sliding member 5 to slide along the first direction. The first mating component includes, but is not limited to, a guide groove and a guide rod, and the second mating component includes, but is not limited to, a guide block and a guide opening.

[0081] Furthermore, the outer sheath 3 is made of PTFE and has a single-lumen structure. The single-lumen outer sheath 3, combined with the dual electrodes, avoids instrument failure caused by the inability to fully retract the shredder into the outer sheath 3.

[0082] Both the handle base 41 and the slider 5 are provided with at least one gripping ring 42.

[0083] The gripping ring 42 is used to enable the operator to control the snare. Furthermore, the gripping ring 42 on the handle base 41 is located at the end of the handle base 41 away from the outer sheath 3, and there are no more than two gripping rings 42 on the handle base 41. The sliding member 5 is provided with at least one gripping ring 42, which can be located on the side of the sliding member or surrounding it. Furthermore, the gripping ring on the sliding member can be either closed or open.

[0084] Furthermore, a flexible ring may be provided on the inner wall of the gripping ring 42. The flexible ring can reduce the pressure on the operator's fingers during the use of this device, which helps to improve the operator's operating accuracy and prevent fatigue during long-term operation.

[0085] Furthermore, the inner wall of the gripping ring 42 has a curved structure. This curved structure prevents the operator from experiencing reduced accuracy due to fixed pressure on the fingers while moving the gripping ring 42 along the handle base 41, improves the gripping experience, and also provides an anti-slip effect.

[0086] The sliding component 5 includes a sliding base 51, which is equipped with a conductive component 6 that can be used to supply power to the collar assembly 1.

[0087] The sliding base 51 is provided with a base 7 corresponding to the conductive component 6. The base 7 is provided with a base hole 71 corresponding to the collar component 1, and a drum spring 72 is provided in the base hole 71. Among them, the base 7 is provided with a base hole 71 corresponding to the first cutting wire 11 and the second cutting wire 12.

[0088] It should be noted that the handle base 41 is provided with a sliding groove 44, which is configured to cooperate with the base 7. In other words, when the sliding base 51 drives the base 7 to move along the first direction, the base 7 and the sliding groove 44 cooperate to realize the movement of the base 7 along the first direction. During this process, the base 7 will drive the first shredder 11 and the second shredder 12 to move along the first direction.

[0089] Furthermore, the base 7 is also provided with a conduit 73, which is connected to the base 7 by mechanical embedding or bonding. The conduit 73 is used to control the first shredder 11 and the second shredder 12. In other words, the conduit 73 houses the first shredder 11 and the second shredder 12, and the conduit 73 is connected to the outer sheath 3. It should be noted that when the sliding member 5 moves to a limit distance away from the outer sheath 3, the conduit 73 and the outer sheath 3 are still in a connected state. The conduit 73 can prevent the first shredder 11 and the second shredder 12 from bending or detaching during the movement of the sliding member 5 in the first direction, and can achieve consistency in the movement of the first shredder 11 and the second shredder 12.

[0090] Furthermore, conduit 73 is made of rigid material.

[0091] It should be noted that the base 7 and the sliding base 51 can be snap-fitted together. The sliding base 51 has a base groove 74 corresponding to the base hole 71. A third mating part 65 is provided on the side of the conductive base 61, and a fourth mating part 66 is provided on the inner wall of the base groove 74. The third mating part 65 and the fourth mating part 66 achieve the mating connection between the conductive base 61 and the base 7, ensuring that the conductive base 61 supplies power to the first cutting wire 11 and the second cutting wire 12, preventing separation or poor contact between the conductive base 61 and the base 7 during operation, which could lead to surgical failure or harm to the patient. More specifically, the third mating part 65 is a snap-fit ​​block, and the fourth mating part 66 is a mating groove; that is, the snap-fit ​​block and the mating groove are fastened and fixed together.

[0092] The first slicing wire 11 and the second slicing wire 12 are respectively provided with base holes 71, and the conductive component 6 is correspondingly arranged with the base holes 71, thus ensuring that the conductive component 6 supplies power to the first slicing wire 11 and the second slicing wire 12. More specifically, the ends of the first slicing wire 11 and the second slicing wire 12 away from the structural member 13 are embedded in the base holes 71 of the base 7 and are respectively connected to the drum springs 72. The two drum springs 72 are arranged to cooperate with the pins 64, and the power supply to the first slicing wire 11 and the second slicing wire 12 is realized through the pins 64 of the conductive component 6.

[0093] Among them, the drum springs 72 are respectively embedded in the corresponding base holes 71.

[0094] Furthermore, the drum spring 72 has a flared structure on both sides. The drum spring 72 facilitates a firm fit with the pin 64, thereby improving the stability of the power supply from the pin 64 to the first filament 11 and the second filament 12. Moreover, the drum spring 72 is set perpendicular to the first moving direction, which allows the damping effect of the drum spring 72 to maintain the perpendicularity between the pin 64 and the drum spring 72 during the movement of the base 7, thereby maintaining the state of the conductive component 6 and reducing the risk of the conductive component 6 falling off.

[0095] The conductive component 6 includes a conductive substrate 61, and symmetrically arranged conductive inserts 62 are provided in the conductive substrate 61. The conductive inserts 62 have slots 63 on the side facing the sliding substrate 51, and pins 64 protruding from the conductive substrate 61 are fitted in the slots 63.

[0096] The conductive component 6 is used to connect to an external high-frequency generator and transmit the current from the external high-frequency generator to the first filament 11 or the second filament 12. The corresponding arrangement of the pin 64 and the slot 63 allows for more flexible engagement between the pin 64 and the conductive insert 62. It should be noted that the slot 63 ensures a contact connection between the pin 64 and the conductive insert 62. The pin 64 is also configured to engage with the drum spring 72. Furthermore, the conductive component 6 connects to the external high-frequency generator via the conductive insert 62, which has an exposed section for connection to the external high-frequency generator.

[0097] It should be noted that, due to the use of high-frequency alternating current, the fit between each pin 64 and each drum spring 72 is interchangeable. In other words, there is no positive or negative distinction between the fit between the conductive component 6 and the base 7, which facilitates the assembly of the conductive component 6 and the base 7.

[0098] Furthermore, the pin 64 is replaceable. This allows the conductive component 6 to adopt a modular design, and the pin 64 can be replaced or manufactured according to different hole sizes 71, thereby saving costs and improving the ease of replacement.

[0099] Furthermore, the slot 63 is provided with a buffer section. It should be noted that the buffer section reduces the possibility of damage and bending of the pin 64 during its engagement with the drum spring 72. Specifically, when the pin 64 is subjected to a large impact force along its length, the buffer section absorbs the impact while controlling the position of the pin 64. This ensures that the length of the pin 64 extending beyond the conductive substrate 61 is controllable and limited. When the pin 64 retracts into the buffer section after being compressed, it will have a force to return to its original position, thus restoring the length of the pin 64 extending beyond the conductive substrate 61. It should be noted that this force includes, but is not limited to, elastic force or pressure.

[0100] Furthermore, the conductive insert 62 is bent. This bending design improves the impact absorption capacity of the slot 63 and allows for better adaptability to external temperature changes, preventing the conductive insert 62 from disconnecting from the pin 64 or its input spring 72 after temperature fluctuations. Additionally, the bending design allows for lower precision requirements compared to a straight conductive insert 62, which is beneficial for controlling production and replacement costs.

[0101] Furthermore, pin 64 is made of a conductive material.

[0102] More specifically, the pin 64 is made of a conductive metal material. Since the device inevitably involves the pin 64 and the conductive substrate 61 interacting with the corresponding receiving device during use, the choice of material for the pin 64 affects the lifespan of the pin 64 and the overall device. Using a metal material can improve the lifespan of the pin 64 and reduce the possibility of bending or breaking the pin 64.

[0103] During the removal of diseased tissue, the high-frequency current sequentially passes through the electrode plug, conductive insert 62, pin 64, drum spring 72, first cutting wire 11, diseased tissue, second cutting wire 12, drum spring 72, pin 64, conductive insert 62, electrode plug, and finally returns to the high-frequency generator. The high-frequency current, passing through the diseased tissue, utilizes its thermal effect to complete the removal of the diseased tissue.

[0104] The handle base 41 is provided with a plurality of limiting blocks 43, which are used to limit the extreme positions of the sliding member 5.

[0105] The limit block 43 can control the limit distance of the sliding member 5 along the first direction, which is beneficial for the operator to control the distance and prevents the position of the ring assembly 1 from being over-positioned due to tension or mistakes during the operation of the sliding member 5.

[0106] Furthermore, the position of the limiting block 43 is adjustable. This allows for control over the unfolding size of the ring assembly 1 in different surgical environments.

[0107] The outer sheath tube 3 is fitted with a protective sleeve 31 along its extension direction, and the protective sleeve 31 can be connected to the handle base 41.

[0108] The sheath sleeve 31 is used to protect the outer sheath tube 3. The sheath sleeve 31 and the handle base 41 can be fixed by means of snap-fit ​​or threaded connection.

[0109] It should be noted that a connector 8 is provided on the side of the handle base 41 facing the collar assembly 1. The connector 8 is used to connect and fix the outer sheath tube 3. The connector 8 includes a connecting base 81. The connecting base 81 is made of metal or rigid plastic. The connecting base 81 has a fixed end 82 and a connecting end 83, wherein the fixed end 82 is connected to the handle base 41, and the connecting end 83 is provided with a snap-fit ​​protrusion 84 for connecting with the outer sheath tube 3.

[0110] The embodiments described above provide a detailed explanation of the technical solution of the present invention. It should be understood that the above descriptions are merely specific embodiments of the present invention and are not intended to limit the present invention. Any modifications, additions, or similar substitutions made within the scope of the principles of the present invention should be included within the protection scope of the present invention.

Claims

1. A bipolar high-frequency electric coil holder, comprising a coil assembly (1) and a sleeve (2), wherein the sleeve (2) is used to fix the coil assembly (1), characterized in that, The sleeve (2) may be one or more.

2. The bipolar high-frequency electric coil device according to claim 1, characterized in that, The ring assembly (1) includes a first cut wire (11) and a second cut wire (12) that do not contact each other. The free ends of the first cut wire (11) and the second cut wire (12) are connected by a structural member (13). The first cut wire (11) is covered with an insulating tube (14) along its extension direction. The first cut wire (11) has an exposed section (15).

3. The bipolar high-frequency electric coil device according to claim 2, characterized in that, The first filament (11) and the second filament (12) in the structural member (13) have a non-contact interval, and the first filament (11) has an exposed section (15) on the side of the structural member (13) that is not wrapped with an insulating tube (14).

4. The bipolar high-frequency electric coil device according to claim 1, characterized in that, It also includes an outer sheath (3) and a handle assembly (4), the outer sheath (3) being connected to the handle assembly (4), the collar assembly (1) being housed within the outer sheath (3), and the handle assembly (4) including a handle base (41), the handle base (41) being slidably fitted with a sliding member (5) movable in a first direction, the sliding member (5) being used to drive the collar assembly (1) to unfold and close within the outer sheath (3).

5. The bipolar high-frequency electric coil device according to claim 4, characterized in that, The sliding member (5) includes a sliding base (51), and the sliding base (51) is provided with a conductive component (6), which is used to supply power to the ring assembly (1).

6. The bipolar high-frequency electric coil device according to claim 5, characterized in that, The sliding base (51) is provided with a base (7) corresponding to the conductive component (6), and the base (7) is provided with a base hole (71) corresponding to the collar component (1), and a drum spring (72) is provided in the base hole (71).

7. The bipolar high-frequency electric coil device according to claim 5, characterized in that, The conductive component (6) includes a conductive substrate (61), and symmetrically arranged conductive inserts (62) are provided in the conductive substrate (61). The conductive inserts (62) have a slot (63) on the side facing the sliding substrate (51), and a pin (64) protruding from the conductive substrate (61) is provided in the slot (63).

8. The bipolar high-frequency electric coil device according to claim 4, characterized in that, Both the handle base (41) and the slider (5) are provided with at least one gripping ring (42).

9. The bipolar high-frequency electric coil device according to claim 4, characterized in that, The handle base (41) is provided with a plurality of limiting blocks (43), which are used to limit the extreme positions of the sliding member (5).

10. The bipolar high-frequency electric coil device according to claim 4, characterized in that, The outer sheath (3) is fitted with a protective sleeve (31) along its extension direction, and the protective sleeve (31) can be connected to the handle base (41).

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