Bipolar high-frequency electrotome

Abstract

The utility model relates to a bipolar high frequency electric knife, including operation part and being located operation part distal end's main part, the main part includes the insulating outer tube of axial extension, and is located the insulating inner tube inside the insulating outer tube, is connected through the connecting piece and the hollow tubular active electrode in the insulating inner tube distal end and forms the first cavity, transmission wire is located in the first cavity, is used for realizing the electric connection of active electrode, the insulating outer tube distal end still is equipped with the insulating part, and the active electrode passes through the insulating part, and the first inert electrode is set up on the insulating outer tube close to the insulating part, and the second inert electrode is still set up on the first inert electrode, the return wire is located in the third cavity that the insulating outer tube is equipped with, is wound on the first inert electrode, is used for realizing the electric connection of first inert electrode. The utility model discloses the combination installation of two inert electrodes, and the connection mode that return wire is wound on the inert electrode, make the cooperation of return wire and inert electrode firm and reliable, and it is not easy to break down.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, specifically to a bipolar high-frequency electrosurgical unit. Background Technology

[0002] Endoscopic submucosal dissection (ESD) is a minimally invasive endoscopic technique that uses high-frequency instruments to dissect lesions larger than 2 cm from the submucosa. Compared with traditional surgery, ESD can better preserve the physiological function of the digestive tract while radically removing the tumor, significantly improving the patient's postoperative quality of life. It has become the preferred treatment for early-stage cancers and precancerous lesions of the digestive tract, including the esophagus. However, ESD is a complex procedure that is generally time-consuming and requires endoscopic guidance. The endoscope first enters the body to locate the lesion. Instruments are then inserted into the body through the endoscopic channel to mark the lesion. After marking, the instruments are withdrawn, and an injection needle is used to inject into the submucosal layer. After the injection, a suitable electrocautery knife is used to perform the surgery. It takes about 1 to 2 hours to successfully remove an early-stage cancer lesion of about 3 cm and then remove the specimen for pathological analysis.

[0003] The bipolar high-frequency electrosurgical units currently on the market mainly have the following problems: 1. The inert electrode and the guide wire are connected by welding, which is a complicated process with high energy consumption. During assembly, the weld points are prone to detachment; 2. There is no clamping position for the inert electrode assembly. Assembly requires the use of special tooling for fixation, resulting in low production efficiency; 3. The assembly position between the guide wire and the tubular inert electrode is not fixed, making it difficult to control the assembly position of the guide wire. Summary of the Invention

[0004] The purpose of this invention is to provide a bipolar high-frequency electrosurgical unit that simplifies the electrosurgical unit assembly process by redesigning the electrode head structure, thereby solving the aforementioned problems.

[0005] To achieve the above objectives, the technical solution provided by this utility model is: a bipolar high-frequency electrosurgical unit, comprising an operating part and a main body part disposed at the distal end of the operating part;

[0006] The main body includes an axially extending insulating outer tube and an insulating inner tube disposed inside the insulating outer tube. The insulating inner tube is connected to a hollow tubular active electrode at its distal end via a connector, forming a first cavity. A transmission wire is disposed in the first cavity for electrically connecting the active electrode.

[0007] The insulating outer tube is further provided with an insulating component at its distal end. The active electrode passes through the insulating component. A first inert electrode is sleeved on the insulating outer tube adjacent to the insulating component. A second inert electrode is also sleeved on the first inert electrode. The return wire is provided in a third cavity provided on the insulating outer tube and is wound around the first inert electrode to realize the electrical connection of the first inert electrode.

[0008] Furthermore, the outer diameter of the first inert electrode is larger than the inner diameter of the second inert electrode.

[0009] Furthermore, a through-cut is provided on the first inert electrode so that the outer diameter of the first inert electrode can be changed.

[0010] Furthermore, the first inert electrode is an elastic metal component, and the first inert electrode is tightly connected to the second inert electrode through elastic deformation.

[0011] Furthermore, the first inert electrode has a notch.

[0012] Furthermore, the number of the gaps is greater than or equal to 1.

[0013] Furthermore, the return wire is wound around the notch.

[0014] Furthermore, the insulating component includes a first stepped portion, a second stepped portion, and a third stepped portion, wherein the outer diameter of the first stepped portion is larger than the outer diameter of the second stepped portion and the outer diameter of the third stepped portion; the second inert electrode is sleeved on the second stepped portion and the third stepped portion, the first inert electrode is located between the second stepped portion and the second inert electrode, and the insulating outer tube is located between the third stepped portion and the second inert electrode.

[0015] Furthermore, the connector and the insulating member have a preset distance, enabling the operating unit to control the active electrode to switch between a first state and a second state.

[0016] Furthermore, the first cavity provides a first liquid passage.

[0017] Furthermore, the insulating component has a liquid through-hole for liquid to flow out, and the through-hole and the interlayer between the insulating outer tube and the insulating inner tube form a second liquid channel.

[0018] Furthermore, the connector and the outer surface of the insulating inner tube are also covered with a sealing layer.

[0019] Furthermore, the outer surfaces of the active electrode, the insulating component, and the second inert electrode have an anti-stick coating.

[0020] The beneficial effects of this utility model are as follows: This utility model utilizes the combination and installation of two inert electrodes, and the connection method of the return wire being wound around the inert electrodes reduces the production and assembly process, optimizes the disadvantage of easy desoldering of the solder joint, and makes the cooperation between the return wire and the inert electrode firm and reliable, and less prone to open circuit. Attached Figure Description

[0021] Figure 1 This is a schematic diagram of the main structure of the bipolar high-frequency electrosurgical unit of this utility model.

[0022] Figure 2 This is a schematic diagram of the operating part of the bipolar high-frequency electrosurgical unit of this utility model.

[0023] Figure 3 This is a schematic diagram of the main structure of the bipolar high-frequency electrosurgical unit of this utility model.

[0024] Figure 4 This is a schematic diagram of the first inert electrode structure of the bipolar high-frequency electrosurgical unit of this utility model.

[0025] Figure 5 This is a schematic diagram of the active electrode structure of the bipolar high-frequency electrosurgical unit of this utility model.

[0026] Figure 6 This is a schematic diagram of the insulating component of the bipolar high-frequency electrosurgical unit of this utility model.

[0027] 1-Operating part, 2-Main body, 3-Insulating outer tube, 4-Insulating inner tube, 5-First inert electrode, 6-Second inert electrode, 7-Active electrode, 8-Return wire, 9-Transmission wire, 10-Connector, 11-Slide groove, 12-Cable connector, 13-Second liquid injection port, 14-First liquid injection port, 15-Control handle, 16-Third cavity, 17-Core rod, 18-Connecting sheath, 21-Sealing layer, 22-Insulating component, 23-First step, 24-Second step, 25-Third step, 26-First cavity, 27-Second cavity, 28-Through hole, 51-Slit, 52-Notch, 71-Protrusion. Detailed Implementation

[0028] To make the objectives, technical solutions, and advantages of this utility model clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the utility model and are not intended to limit it. The scope of this application is not limited to these embodiments but is determined by the scope of the patent application. To provide a clearer description and enable those skilled in the art to understand the content of this application, the parts in the drawings are not necessarily drawn according to their relative dimensions; some dimensions may be exaggerated to highlight their proportions to other related dimensions, and irrelevant or unimportant details are not fully drawn for the sake of simplicity. Example

[0029] In this utility model, the embodiments are as follows: Figures 1-3 The main body 2, operating part 1, insulating inner tube 4 and insulating outer tube 3 of the bipolar high-frequency electrosurgical unit shown are defined as distal end and proximal end respectively from left to right.

[0030] like Figure 1-6As shown, the bipolar high-frequency electrosurgical unit of this utility model includes an operating part 1 and a main body part 2 disposed at the distal end of the operating part 1.

[0031] The main body 2 includes an axially extending insulating outer tube 3 and an insulating inner tube 4 disposed inside it; the insulating inner tube 4 is connected to a hollow tubular active electrode 7 at its distal end via a connector 10, forming a first cavity 26, the connector 10 being made of metal; a transmission wire 9 is disposed in the first cavity 26, one end of which is connected to the connector 10, and the other end is connected to the cable connector 12 on the operation part 1, thereby realizing the electrical connection of the active electrode 7.

[0032] An insulating element 22 is provided at the far end of the insulating outer tube 3. The active electrode 7 passes through the insulating element 22. A first inert electrode 5 is sleeved on the insulating outer tube 3 adjacent to the insulating element 22. A second inert electrode 6 is also sleeved on the first inert electrode 5. The return wire 8 passes through the third cavity 16 provided on the insulating outer tube 3. One end is wrapped around the first inert electrode 5, and the other end is connected to the cable connector 12 on the operation part 1 to realize the electrical connection of the first inert electrode 5.

[0033] like Figure 4 As shown, in this invention, the first inert electrode 5 has a through-hole slit 51. In its free state, the outer diameter of the first inert electrode 5 is larger than the inner diameter of the second inert electrode 6. Due to the presence of the slit 51, the outer diameter of the first inert electrode 5 can be changed, making it smaller than the inner diameter of the second inert electrode 6. The first inert electrode 5 can be an elastic metal part, such as stainless steel. When the outer diameter of the first inert electrode 5 decreases, the second inert electrode 6 can be easily fitted onto the first inert electrode 5. The elastic deformation allows the first inert electrode 5 and the second inert electrode 6 to fit tightly together, and the return wire 8 is tightly squeezed in the middle.

[0034] In this invention, the first inert electrode 5 has one or more notches 52 to fix the position of the return wire 8. The return wire 8 is wound around the notch 52. During installation, as long as the axis of the notch 52 and the first cavity 16 are aligned in the horizontal plane, the position of the return wire 8 and the third cavity 16 can be aligned. The notches 52 are symmetrically provided on both sides of the cut 51. When installing the first inert electrode 5, the notches 52 can be clamped with tools to easily change the outer diameter of the first inert electrode 5, facilitating installation.

[0035] The insulating component 22 includes a first stepped portion 23, a second stepped portion 24, and a third stepped portion 25. The outer diameter of the first stepped portion 23 is larger than that of the second stepped portion 24, which is larger than that of the third stepped portion 25. The second stepped portion 24 and the third stepped portion 25 provide mounting positions for the electric knife insulating outer tube 3, the first inert electrode 5, and the second inert electrode 6. Specifically, the second inert electrode 6 is sleeved on the second stepped portion 24 and the third stepped portion 25, the first inert electrode 5 is located between the second stepped portion 24 and the second inert electrode 6, and the insulating outer tube 3 is located between the third stepped portion 25 and the second inert electrode 6. The first stepped portion 23 ensures mutual insulation between the active electrode 7 and the second inert electrode 6. The inner diameter of the first inert electrode 5 is larger than the outer diameter of the second stepped portion 24 to ensure that the outer diameter of the first inert electrode 5 can have a certain deformation when it is sleeved on the second stepped portion 24.

[0036] The connector 10 and the insulator 22 are spaced at a preset distance, allowing the operating unit 1 to control the active electrode 7 to switch between a first state and a second state. Specifically, the operating unit 1 controls the active electrode 7 to partially expose itself from the insulator 22, at which point the active electrode 7 is in an active state; conversely, the active electrode 7 is not in an active state.

[0037] like Figure 3 , 5 As shown in Figure 6, the active electrode 7 is a hollow tubular structure, which together with the connector 10 and the insulating outer tube 3 forms a first cavity 26 to provide a first liquid channel for liquid to pass through. The interlayer between the insulating outer tube 3 and the insulating inner tube 4 forms a second cavity 27. The insulating component 22 is also provided with a plum blossom-shaped through hole 28. The second cavity 27 and the through hole 28 provide a second liquid channel for liquid to pass through.

[0038] In this utility model, the outer surfaces of the connector 10 and the insulating inner tube 4 may also be covered with a sealing layer 21.

[0039] In this invention, the outer surfaces of the active electrode 7, the insulating component 22, and the second inert electrode 6 are covered with an anti-stick coating. The material of this coating may include, but is not limited to, titanium nitride (TiN), chromium nitride (CrN), titanium aluminum carbon (TiAlCN), titanium aluminum nitride (TiAlN), diamond-like carbon (DLC), and polytetrafluoroethylene (PTFE).

[0040] In this utility model, the active electrode 7 is as follows: Figure 5 The diagram shows a hollow tubular structure with a protrusion 71 at the front end, providing a large surface area and creating a large contact surface when in contact with tissue. As can be seen from this invention, the shape of the protrusion 71 is not unique; it can be any shape that provides a large contact surface with tissue, such as triangular, cylindrical, or hemispherical.

[0041] The connector 10 is conductive, has a hollow tubular structure, and its outer surface can be configured with an uneven surface. One end of the connector 10 is connected to the insulating inner tube 4, and the other end is connected to the active electrode 7. In this invention, the outer surfaces of the connector 10 and the insulating inner tube 4 are also covered with a sealing layer 21, which also provides insulation. The sealing layer 21 is made of a polymer material. The connector 10 is connected to the transmission wire 9, thereby enabling the active electrode 7 to conduct electricity.

[0042] The sealing layer 21 is applied to the outer surfaces of the connector 10 and the insulating inner tube 4 using methods such as heat shrinking, welding, or bonding. Because the outer surface of the connector 10 has a textured surface, the sealing layer 21 can better cover the surface, resulting in a better seal. Additionally, a protective tube can be applied to the distal outer surface of the insulating outer tube 3 for electrical safety protection.

[0043] like Figure 1 and 2 As shown, the operating part 1 is located near the main body 2, allowing the active electrode 7 to be extended or retracted, and providing a lumen for injecting liquid. The operating part 1 includes a slide 11, a cable connector 12, a second liquid injection port 13, a first liquid injection port 14, a control handle 15, a core rod 17, and a connecting sheath 18. The slide 11 is located on the core rod 17 and is used for the back-and-forth sliding of the handle 15. The control handle 15 is connected to the insulating inner tube 4, thereby controlling the switching of the active electrode 7 between a first state and a second state. In this invention, the near end of the insulating inner tube 4 and the control handle 15 can be connected by a rigid steel pipe, and the transmission wire 9 is directly electrically connected to the rigid steel pipe.

[0044] The first liquid injection port 14 is equipped with a Luer connector for liquid injection. A connecting sheath 18 is connected to the second liquid injection port 13 for liquid injection. During use, the inert electrode 6 is placed inside the target mucosal tissue, and the injection pump is connected to the first liquid injection port 14 to inject saline or indigo carmine, thereby raising the mucosal tissue and forming a liquid buffer layer, or "water cushion," under the mucosa. This "water cushion" effectively isolates the muscle layer and the lesion, while also effectively preventing heat conduction, resulting in a clearer surgical field. Blood vessels are compressed and sealed by the water cushion, significantly reducing the risk of bleeding. This liquid channel can also be used to clean bleeding sites. Furthermore, frequent changes of parts are unnecessary during the surgical procedure, greatly reducing surgical time and improving surgical safety.

[0045] During use, if charred tissue adheres to the cutting tip, sparks may be generated or the cutting may not be effective when electricity is applied. Timely cleaning of the cutting tip can effectively prevent these situations. When mucous tissue adheres to the active electrode 7 and the insulating component 22, a liquid injection pump or syringe can be connected to the second liquid injection port 13 for injection, such as injecting physiological saline. The liquid cleans the mucous tissue on the active electrode 7 and the insulating component 22 through the second cavity 27. If tissue bleeding occurs during electrode cutting, physiological saline can also be injected through the first liquid injection port 14 to clean the bleeding site.

[0046] When both the active electrode 7 and the inert electrode 6 come into contact with the diseased tissue, their outer surfaces are in close contact. The contact area between the active electrode 7 and the diseased tissue is smaller than that between the inert electrode 6 and the diseased tissue, and the resistance at the contact point between the active electrode 7 and the diseased tissue is lower than that at the contact point between the inert electrode 6 and the diseased tissue. Upon contact with the tissue, the current density at the active electrode 7 is greater than that at the inert electrode 6, converting electrical energy into heat energy and generating a higher surface temperature at the active electrode 7. This allows the active electrode 7 to cut the tissue.

[0047] The operation procedure of the bipolar high-frequency electrosurgical unit of this invention is as follows: During surgery, the bipolar high-frequency electrosurgical unit is inserted near the lesion tissue through the endoscopic cavity. During this process, the active electrode 7 must be kept in the retracted state, within the insulating outer tube 3, to protect both the active electrode 7 and the endoscope from damage. After the bipolar high-frequency electrosurgical unit reaches the lesion tissue, both the active electrode 7 and the inert electrode 6 simultaneously come into contact with the tissue. The cable connector 12 of the bipolar high-frequency electrosurgical unit is then connected to an external high-frequency generator, which includes, but is not limited to, CONMED's 60-8200-230, ERBE's VIO300S, 300D, etc. A high-frequency current is then supplied to the active electrode 7 and the inert electrode 6, cutting around the lesion tissue. After completion, the high-frequency current is stopped.

[0048] This utility model provides a method for installing a bipolar high-frequency electrosurgical electrode tip, using the attachment provided in Embodiment 1. Figure 1-6 The method specifically includes the following steps:

[0049] The installation method for the inner tube assembly is as follows:

[0050] One end of the active electrode 7 passes through the insulating component 22;

[0051] The active electrode 7 and the connector 10 are welded together.

[0052] After the transmission wire 9 passes through the insulating inner tube 4, it is connected to the connector 10. The connector 10 is made of metal. Then, the insulating inner tube 4 is installed on the connector 10 to complete the installation of the inner tube assembly.

[0053] The return conductor 8 passes through the third cavity 16 on the insulating outer tube 3 and extends out of the third cavity 16;

[0054] The second inert electrode 6 is partially mounted on the insulating outer tube 3, leaving another portion at a preset mounting distance. This mounting distance can perfectly match the second step portion 24 of the insulating component 22, so that the inner tube assembly is installed inside the insulating outer tube 3.

[0055] The return wire 8 is wound around the first inert electrode 5, and the first inert electrode 5 is mounted on the second step portion 24 of the insulating member 22;

[0056] Move the second inert electrode 6 so that the other part of the second inert electrode 6 is completely fitted onto the first inert electrode 5. At this time, the insulating outer tube 3 is installed on the third step 25 of the insulating component 22.

[0057] The first inert electrode 5 in this invention has multiple notches 52, and the return wire 8 is wound around the notches 52 on the first inert electrode 5.

[0058] The first inert electrode 5 in this invention is also provided with a through-hole slit 51, which can change the outer diameter of the first inert electrode 5. When the second inert electrode 6 is fitted onto the first inert electrode 5, the outer diameter of the first inert electrode 5 is changed by clamping the notch 52 with a tool, so that the second inert electrode 6 can be easily fitted onto the first inert electrode 5. The first inert electrode 5 is an elastic metal part. After returning to its original state, the first inert electrode 5 and the second inert electrode 6 fit tightly together, clamping the return wire 8 in the middle position.

[0059] Because the second inert electrode 6 at the high-frequency electrosurgical electrode tip is very small, with an outer diameter of only 2.7 mm, an inner diameter of 2.5 mm, and a length of 4 mm, using traditional welding processes, the weld point is located on the inner wall of the second inert electrode 6. When welding the return lead 8 onto the second inert electrode 6, two problems arise: firstly, welding is difficult; secondly, during installation, the second inert electrode 6 needs to be slidably fitted onto the insulating component 22, making it prone to detachment from the weld. Furthermore, after installation, the position of the second inert electrode 6 cannot be adjusted to ensure that the return lead 8 and the third cavity 16 on the insulating outer tube 3 are collinear. This invention adds a first inert electrode 5, and the guide wire is wound around the first inert electrode 5, eliminating the need for welding. This solves the above problems during installation, and the position of the first inert electrode 5 can be adjusted freely to ensure that the return lead 8 and the third cavity 16 on the insulating outer tube 3 are collinear.

[0060] The above description is merely a preferred embodiment of this utility model and is not intended to limit the scope of this utility model. Various modifications and variations can be made to this utility model by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this utility model should be included within the protection scope of this utility model.

Claims

1. A bipolar high-frequency electrosurgical unit, characterized in that: It includes an operating section and a main body section located at the far end of the operating section; The main body includes an axially extending insulating outer tube and an insulating inner tube disposed inside the insulating outer tube. The insulating inner tube is connected to a hollow tubular active electrode at its distal end via a connector, forming a first cavity. A transmission wire is disposed in the first cavity for electrically connecting the active electrode. The insulating outer tube is further provided with an insulating component at its distal end. The active electrode passes through the insulating component. A first inert electrode is sleeved on the insulating outer tube adjacent to the insulating component. A second inert electrode is also sleeved on the first inert electrode. The return wire is provided in a third cavity provided on the insulating outer tube and is wound around the first inert electrode to realize the electrical connection of the first inert electrode.

2. The bipolar high-frequency electrosurgical unit according to claim 1, characterized in that: The outer diameter of the first inert electrode is larger than the inner diameter of the second inert electrode.

3. The bipolar high-frequency electrosurgical unit according to claim 2, characterized in that: A through-cut is provided on the first inert electrode so that the outer diameter of the first inert electrode can be changed.

4. The bipolar high-frequency electrosurgical unit according to claim 3, characterized in that: The first inert electrode is an elastic metal part, and the first inert electrode is tightly connected to the second inert electrode through elastic deformation.

5. A bipolar high-frequency electrosurgical unit according to any one of claims 1-4, characterized in that: The first inert electrode has a notch.

6. The bipolar high-frequency electrosurgical unit according to claim 5, characterized in that: The number of gaps is greater than or equal to 1.

7. The bipolar high-frequency electrosurgical unit according to claim 5, characterized in that: The return wire is wound around the notch.

8. The bipolar high-frequency electrosurgical unit according to claim 1, characterized in that: The insulating component includes a first stepped portion, a second stepped portion, and a third stepped portion, wherein the outer diameter of the first stepped portion is larger than the outer diameter of the second stepped portion and the outer diameter of the third stepped portion; the second inert electrode is sleeved on the second stepped portion and the third stepped portion, the first inert electrode is located between the second stepped portion and the second inert electrode, and the insulating outer tube is located between the third stepped portion and the second inert electrode.

9. The bipolar high-frequency electrosurgical unit according to claim 1, characterized in that: The connector and the insulating member are at a preset distance, so that the operating unit can control the active electrode to switch between a first state and a second state.

10. The bipolar high-frequency electrosurgical unit according to claim 1, characterized in that: The first cavity provides a first liquid passage.

11. The bipolar high-frequency electrosurgical unit according to claim 1, characterized in that: The insulating component has a liquid through hole for liquid to flow out, and the through hole and the interlayer between the insulating outer tube and the insulating inner tube form a second liquid channel.

12. A bipolar high-frequency electrosurgical unit according to any one of claims 1, 9, or 11, characterized in that: The connector and the outer surface of the insulating inner tube are also covered with a sealing layer.

13. The bipolar high-frequency electrosurgical unit according to claim 1, characterized in that: The outer surfaces of the active electrode, the insulating component, and the second inert electrode have an anti-stick coating.

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