A low-temperature high-frequency surgical knife

Abstract

This utility model discloses a low-temperature high-frequency surgical scalpel, comprising: a handheld part; and a scalpel head body mounted on the handheld part. The handheld part is used to connect a power source, enabling the scalpel head body to perform high-frequency cutting. The scalpel head body includes a blade surface and a cutting edge, with the cutting edge surrounding the blade surface and having a beveled structure. The surface of the blade surface is coated with an insulating coating. This allows for low-temperature, high-efficiency cutting, reducing thermal damage to tissues.

Description

Technical Field

[0001] This utility model relates to the field of medical equipment technology, and in particular to a low-temperature high-frequency surgical knife. Background Technology

[0002] High-frequency scalpels, as a common surgical instrument, are widely used for cutting and coagulation procedures on various tissues. Their working principle utilizes the Joule heating effect generated when a high-frequency current passes through human tissue, rapidly heating the local tissue to achieve vaporization, separation, or coagulation for hemostasis. Traditional high-frequency scalpels typically use a metal conductor as the cutting head; when a high-frequency current is applied, the entire surface of the cutting head heats up, with the heat concentrated in the area in contact with the tissue.

[0003] However, existing high-frequency surgical scalpels have significant technical drawbacks. Because traditional scalpel tips are mostly blunt or unsharpened, lacking sharp cutting edges, they rely on high temperatures to soften the tissue and achieve a "pushing" effect during tissue cutting. Therefore, the operating temperature of the scalpel tip often needs to reach above 160℃, or even exceed 200℃, which can easily cause excessive denaturation and carbonization of tissue proteins, as well as thermal damage to surrounding healthy tissue. This thermal damage not only exacerbates postoperative inflammation but may also affect the wound healing speed, increase the risk of scar formation, and hinder the patient's postoperative recovery.

[0004] Furthermore, the entire blade of a traditional high-frequency surgical scalpel is conductive, resulting in a dispersed current distribution and low thermal efficiency, which further exacerbates unnecessary heat dissipation. Although some improved designs attempt to limit the heat-generating area through coatings and other methods, they often fail to balance the mechanical cutting performance of the scalpel with its electrothermal efficiency. Utility Model Content

[0005] This invention aims to solve at least one of the technical problems existing in the prior art. To this end, this invention proposes a low-temperature, high-frequency surgical scalpel that can achieve low-temperature, high-efficiency cutting and reduce thermal damage to tissues.

[0006] A low-temperature high-frequency surgical knife according to a first aspect embodiment of the present invention includes: Handheld part; The cutter head body is mounted on the handheld part, which is used to connect the power supply so that the cutter head body can perform high-frequency cutting. The cutter head body includes a blade surface and a cutting edge. The cutting edge is arranged around the blade surface and has a beveled structure. The surface of the blade surface is provided with an insulating coating.

[0007] A low-temperature high-frequency surgical scalpel according to an embodiment of the present invention has at least the following beneficial effects: By providing a blade with a beveled structure on the scalpel body, the scalpel possesses mechanical sharpness, enabling tissue cutting and separation at lower temperatures, significantly reducing dependence on high-frequency thermal effects, thereby effectively controlling the working temperature and preventing tissue carbonization and excessive thermal damage due to high temperatures; the surface of the blade is provided with an insulating coating, which effectively blocks the diffusion of current and heat in non-cutting areas, allowing the high-frequency current to concentrate energy release at the blade, improving heat utilization efficiency, reducing heat conduction to surrounding healthy tissue, reducing postoperative inflammatory response, and promoting wound healing; the blade... The scalpel is positioned around the periphery of the blade surface, forming a focused energy output structure. Combined with a sharp, beveled cutting edge, it can achieve a sharp cutting effect similar to a traditional scalpel while being energized, improving the precision and controllability of surgical operations. This scalpel integrates the hemostatic function of high-frequency electrocautery with the cutting efficiency of a mechanical blade. It can achieve tissue coagulation and hemostasis during cutting, and reduce pushing resistance through the physical cutting edge, thereby reducing the required heat power and further enabling low-temperature surgical operations. An insulating coating covers the non-working area to prevent leakage and the risk of unexpected electric shock, improving surgical safety. At the same time, its reasonable structural design facilitates manufacturing and sterilization, making it suitable for various surgical scenarios.

[0008] According to some embodiments of this utility model, one end of the scalpel head body is a planar structure, and the other end is provided with the blade surface and the cutting edge. Both the planar structure and the blade surface are covered with the insulating coating. The scalpel combines auxiliary operation functions such as compression, hemostasis, and separation with high-frequency cutting function. The planar structure can be used for light pressure, separation, or simple compression hemostasis of tissues, avoiding frequent instrument changes and improving surgical smoothness and operational efficiency.

[0009] According to some embodiments of this utility model, the insulating coating is silicone resin. Silicone resin has high resistivity and good dielectric strength, which can effectively block the leakage of high-frequency current in non-working areas, ensure that current energy is concentrated and released at the cutting edge, improve energy utilization efficiency, reduce ineffective heat generation, and thus achieve safer and more precise cutting and coagulation operations.

[0010] According to some embodiments of this utility model, the thickness of the silicone resin is 0.05 mm to 0.2 mm. This thickness range achieves an extremely thin design while ensuring sufficient dielectric strength. A thickness greater than 0.05 mm can effectively prevent high-frequency current breakdown and avoid the risk of leakage or short circuit; while a thickness not exceeding 0.2 mm avoids excessive coating thickness that could lead to blade dulling or affect the precision structure of the tool, thus ensuring the accuracy of surgical operations.

[0011] According to some embodiments of this utility model, the cutting edge includes two opposing inclined sidewalls and an arc-shaped cutting tip surface connected between the two inclined sidewalls, with an arc transition connection between the inclined sidewalls and the arc-shaped cutting tip surface. This arc transition connection effectively alleviates stress concentration, improves the mechanical strength, bending resistance, and wear resistance of the cutting edge during use, and extends the service life of the instrument.

[0012] According to some embodiments of this utility model, the thickness of the cutting end of the inclined sidewall is A, satisfying 0.08mm≤A≤0.15mm. A thinner cutting end is beneficial for electric field concentration, enhancing the current density at the cutting edge, allowing energy to act efficiently on the cutting edge and improving electrocutting efficiency; while the lower limit thickness of 0.08mm avoids local overheating or arc discharge caused by excessive thinness, ensuring stable and controllable energy release.

[0013] According to some embodiments of this utility model, the blade body and the handheld part are connected by an arc transition. The arc transition structure can effectively disperse the mechanical stress generated by bending, torsion or collision during use, avoid the formation of stress concentration points at the connection, significantly improve the fatigue resistance and fracture resistance of the overall structure, and extend the service life of the scalpel.

[0014] According to some embodiments of this utility model, the inclination angle of the inclined sidewall is B, and satisfies: 25° ≤ B ≤ 45°. When the inclination angle B is not less than 25°, the blade has sufficient sharpness, which can significantly reduce the force and energy input required for tissue cutting and reduce the "pushing" phenomenon; while the angle does not exceed 45° to avoid insufficient strength caused by an excessively thin blade edge, ensuring stable cutting when cutting dense tissue and improving surgical efficiency.

[0015] According to some embodiments of this utility model, the blade body is made of titanium alloy or medical-grade stainless steel. Both materials have strong corrosion resistance, and can remain stable, especially in physiological environments containing high temperature, high humidity and chloride ions (such as blood and tissue fluid), effectively resisting the erosion and oxidation of body fluids, preventing rust and peeling of the blade surface, and ensuring the reliability and safety of the instrument for long-term use.

[0016] According to some embodiments of this utility model, the insulating coating is attached to the cutting surface by spraying, dipping, or vapor deposition processes. Spraying and dipping processes can form a continuous film layer with uniform thickness, no pinholes, and no missed coating on the surface of the cutting surface using insulating materials such as silicone resin. This is especially suitable for cutting head bodies with complex geometries, ensuring the integrity and reliability of the insulation performance.

[0017] Additional aspects and advantages of this invention will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of the invention. Attached Figure Description

[0018] The present invention will be further described below with reference to the accompanying drawings and embodiments, wherein: Figure 1 This is a front view of a low-temperature high-frequency surgical knife according to an embodiment of the present utility model; Figure 2 This is a schematic diagram of the back of a low-temperature high-frequency surgical knife according to an embodiment of the present invention; Figure 3 for Figure 2 A schematic diagram of point A in the middle.

[0019] Reference numerals: Handle 100; Blade 110; Blade face 120; Planar structure 130; Inclined sidewall 140; Blade tip 150. Detailed Implementation

[0020] The embodiments of this utility model are described in detail below. Examples of these embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain this utility model, and should not be construed as limiting this utility model.

[0021] In the description of this utility model, it should be understood that the directional descriptions, such as up, down, front, back, left, right, etc., indicate the directional or positional relationship based on the directional or positional relationship shown in the accompanying drawings. They are only for the convenience of describing this utility model and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this utility model.

[0022] In the description of this utility model, "several" means one or more, "multiple" means two or more, "greater than," "less than," and "exceeding" are understood to exclude the stated number, while "above," "below," and "within" are understood to include the stated number. If "first" or "second" is used in the description, it is only for the purpose of distinguishing technical features and should not be construed as indicating or implying relative importance, or implicitly indicating the number of indicated technical features, or implicitly indicating the order of the indicated technical features.

[0023] In the description of this utility model, unless otherwise explicitly defined, terms such as "setting," "installation," and "connection" should be interpreted broadly. Those skilled in the art can reasonably determine the specific meaning of these terms in this utility model based on the specific content of the technical solution. In the description of this utility model, the terms "one embodiment," "some embodiments," "illustrative embodiment," "example," "specific example," or "some examples," etc., refer to specific features, structures, materials, or characteristics described in connection with that embodiment or example, which are included in at least one embodiment or example of this utility model. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described can be combined in any suitable manner in one or more embodiments or examples. In the description of this specification, the terms "one embodiment," "some embodiments," "illustrative embodiment," "example," "specific example," or "some examples," etc., refer to specific features, structures, materials, or characteristics described in connection with that embodiment or example, which are included in at least one embodiment or example of this utility model. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples.

[0024] Reference Figures 1 to 3 A low-temperature high-frequency surgical scalpel, comprising: Handheld part 100; The cutter head body is mounted on the handheld part 100. The handheld part 100 is used to connect the power supply so that the cutter head body can perform high-frequency cutting. The cutter head body includes a cutting surface 120 and a cutting edge 110. The cutting edge 110 is arranged around the periphery of the cutting surface 120 and has a beveled structure. The surface of the cutting surface 120 is provided with an insulating coating.

[0025] By incorporating a beveled blade section 110 on the blade body, the scalpel achieves mechanical sharpness, enabling tissue cutting and separation at lower temperatures. This significantly reduces reliance on high-frequency thermal effects, effectively controlling the operating temperature and preventing tissue carbonization and excessive thermal damage. The blade face section 120 features an insulating coating that effectively blocks the diffusion of current and heat in non-cutting areas, concentrating high-frequency current at the blade section 110 to release energy, improving thermal efficiency, reducing heat conduction to surrounding healthy tissue, minimizing postoperative inflammation, and promoting wound healing. The blade section 110 is arranged around the blade face section 120. The outer periphery forms a focused energy output structure, combined with a sharp beveled blade design, enabling a sharp cutting effect similar to a traditional scalpel while energized, improving the precision and controllability of surgical operations. This scalpel integrates the hemostatic function of high-frequency electrocautery with the cutting efficiency of a mechanical blade, achieving tissue coagulation and hemostasis during cutting while reducing pushing resistance through the physical blade edge, thus lowering the required heat power and further enabling low-temperature surgical operations. An insulating coating covers non-working areas to prevent leakage and unexpected electric shock risks, enhancing surgical safety. At the same time, its rational structural design facilitates manufacturing and sterilization, making it suitable for various surgical scenarios.

[0026] The scalpel body has a planar structure 130 at one end and a blade surface 120 and a cutting edge 110 at the other end. Both the planar structure 130 and the blade surface 120 are covered with an insulating coating. The scalpel combines auxiliary operation functions such as compression, hemostasis, and separation with high-frequency cutting capabilities. The planar structure 130 can be used for light pressure, tissue separation, or simple compression hemostasis, avoiding frequent instrument changes and improving surgical smoothness and operational efficiency.

[0027] The scalpel's handle 100 is connected to the high-frequency electrosurgical unit's power supply, and the system is in standby mode after power-on. An insulating coating covers the non-working area, including the flat end face and the blade face 120, with only the cutting edge 110 exposed and conductive, forming a controllable energy output area. The surgeon uses one end of the cutting edge 110 of the scalpel body to contact the target tissue. Due to the beveled structure and sharp edge of the cutting edge 110, and its exposure to high-frequency current, the current is highly concentrated at the cutting edge, generating a localized thermal effect, while simultaneously providing mechanical sharpness into the tissue, achieving "electromechanical coordinated cutting." The insulating coating effectively blocks current diffusion from the blade face 120, concentrating heat on the cutting edge and preventing large-area burns. When tissue removal, gentle pressure hemostasis, or blunt dissection is required, the surgeon can rotate the scalpel and use the flat end 130 to apply pressure or push against the tissue. Because this end is flat and covered with an insulating coating, it will not conduct high-frequency current even when in contact with tissue, preventing accidental electrocoagulation or electrocution effects, and only providing a mechanical auxiliary function.

[0028] Although the planar structure 130 is made of metal, it is non-conductive due to its insulating coating. Even if tissue is accidentally touched during surgery, it will not trigger unexpected electrocoagulation or electroresection, greatly improving surgical safety, and is particularly suitable for operations in delicate anatomical areas (such as near nerves and blood vessels). The insulating coating strictly limits the release of high-frequency current to the blade 110, avoiding ineffective heating and improving energy utilization efficiency. Combined with the mechanical sharpness of the blade, cutting can be completed at a lower temperature (far below the traditional 160°C), significantly reducing tissue thermal damage, carbonization, and postoperative inflammatory reactions.

[0029] The insulating coating is made of silicone resin. Silicone resin has high resistivity and good dielectric strength, which can effectively block the leakage of high-frequency current in non-working areas, ensure that the current energy is concentrated in the blade part 110 for release, improve the energy utilization efficiency, reduce ineffective heat generation, and thus achieve safer and more precise cutting and coagulation operations.

[0030] When the scalpel handle 100 is connected to the high-frequency electrosurgical unit and powered on, high-frequency current is transmitted to the scalpel body through a conductor. Since the blade surface 120 and non-cutting areas (such as the flat end) are covered with a silicone insulating coating, this coating forms an effective electrical insulation barrier under the influence of the electric field, preventing current from conducting or leaking in non-designed areas (such as the blade surface 120). At this time, the high-frequency current is forcibly concentrated on the uncoated cutting edge 110—that is, the sharp edge with a beveled structure.

[0031] During tissue cutting, the current is highly concentrated at the blade tip 110, generating localized Joule heating. This causes the tissue at the contact point to rapidly heat up, vaporize, and separate, achieving the electrocutting effect. Simultaneously, the sharp mechanical cutting edge assists in the cutting and reduces pushing resistance. Throughout the entire process, the silicone resin coating continuously performs its electrical insulation, thermal barrier, and surface protection functions, ensuring that energy is released only in the target area and avoiding unintended electrical burns and heat dissipation.

[0032] Furthermore, during the cleaning, sterilization, and reuse processes after surgery, the silicone coating maintains its chemical stability and adhesion integrity, effectively resisting the erosion of high-temperature steam, chemical disinfectants, and mechanical friction, ensuring the long-term reliable use of the instrument.

[0033] The silicone resin thickness ranges from 0.05mm to 0.2mm. This thickness range allows for an ultra-thin design while ensuring sufficient dielectric strength. A thickness greater than 0.05mm effectively prevents high-frequency current breakdown, avoiding the risk of leakage or short circuits; while a thickness not exceeding 0.2mm avoids excessive coating thickness that could dull the cutting edge or affect the precision structure of the instrument, ensuring the accuracy of surgical procedures.

[0034] The blade portion 110 includes two opposing inclined sidewalls 140 and an arc-shaped blade tip 150 connecting the two inclined sidewalls 140. The inclined sidewalls 140 and the arc-shaped blade tip 150 are connected by an arc transition. The arc transition between the inclined sidewalls 140 and the arc-shaped blade tip 150 effectively alleviates stress concentration, improves the mechanical strength, bending resistance, and wear resistance of the blade portion 110 during use, and extends the service life of the instrument. When the scalpel is connected to a high-frequency power supply and contacts tissue, a high-frequency current is transmitted to the blade portion 110 along the conductive blade body. Due to the geometric structure formed by the two inclined sidewalls 140 and the arc-shaped blade tip 150 at the front end of the blade portion 110, the current is highly concentrated in this sharp edge area, forming a local high electric field intensity region, generating a concentrated thermal effect, causing the tissue to rapidly vaporize and separate with a very small contact area. During the cutting process, the arc-shaped blade tip 150 first contacts the tissue, serving as a guide and stabilizing element for entry. As the cutting progresses, the sharp cutting edges formed by the inclined sidewalls 140 symmetrically cut the tissue, reducing the risk of tearing caused by uneven force on one side. Because the entire cutting edge area is a continuous arc transition without sharp corners or stress concentration points, the cutting process is smooth and even, with uniform force on the tissue, avoiding jamming or skipping.

[0035] The thickness of the cutting end of the inclined sidewall 140° is A, which satisfies 0.08mm≤A≤0.15mm. A thinner cutting end is conducive to electric field concentration, enhances the current density at the cutting edge, and allows energy to act efficiently on the cutting edge, thereby improving the electrocutting efficiency; while the lower limit thickness of 0.08mm avoids local overheating or arc discharge caused by excessive thinness, ensuring stable and controllable energy release.

[0036] The blade body and the handheld part 100 are connected by a rounded transition. The rounded transition structure can effectively disperse the mechanical stress generated by bending, torsion or collision during use, avoid the formation of stress concentration points at the connection, significantly improve the fatigue resistance and fracture resistance of the overall structure, and extend the service life of the scalpel.

[0037] When a surgeon holds the handle 100 to cut, separate, or manipulate tissue, the scalpel often needs to enter the surgical area at different angles and slide, turn, or apply pressure between tissues. During this process, the connection area between the scalpel head and the handle 100 may come into contact with surrounding non-target tissue. Due to the use of a rounded transition connection, this area has no sharp edges or right-angle steps, resulting in low resistance and smooth movement of the instrument in the tissue, making it less likely to snag, tear, or accidentally damage nearby blood vessels, nerves, or other important structures.

[0038] The inclination angle of the inclined sidewall 140° is B, and satisfies: 25° ≤ B ≤ 45°. When the inclination angle B is not less than 25°, the blade has sufficient sharpness, which can significantly reduce the force and energy input required for tissue cutting and reduce the "pushing" phenomenon; while the angle does not exceed 45° to avoid insufficient strength caused by an excessively thin blade edge, ensuring stable cutting when cutting dense tissue and improving surgical efficiency.

[0039] When a surgeon uses a scalpel to cut into tissue, the arc-shaped tip 150 of the blade 110 first contacts the tissue, followed by the sidewalls with specific tilt angles B advancing along the cutting direction. Because the tilt angle is controlled between 25° and 45°, a sharp and stable cutting edge structure is formed, effectively concentrating pressure during mechanical advancement for smooth entry. Simultaneously, a high-frequency current is transmitted to the blade 110 through a conductive metal. Due to the skin effect and tip concentration characteristics of the current, a high current density area is formed at the edge region where the tilted sidewalls 140 contact the tissue, generating a localized thermal effect that rapidly vaporizes and separates the tissue. This tilt angle range ensures uniform current distribution and concentrated heat release, preventing energy diffusion to non-cutting areas.

[0040] The blade body is made of titanium alloy or medical-grade stainless steel. Both materials have strong corrosion resistance, and remain stable, especially in physiological environments containing high temperature, high humidity and chloride ions (such as blood and tissue fluid). They effectively resist the erosion and oxidation of body fluids, prevent the blade surface from rusting and peeling, and ensure the reliability and safety of the instrument for long-term use.

[0041] Because the blade body is made of medical metal materials with good conductivity, such as titanium alloy or medical stainless steel, the current can be efficiently and stably conducted to the blade 110, and the energy is concentrated and released in the exposed blade area to generate a local thermal effect to achieve tissue cutting and coagulation.

[0042] The insulating coating is applied to the cutting edge 120 via spraying, dipping, or vapor deposition. Spraying and dipping processes allow insulating materials such as silicone resin to form a continuous film of uniform thickness, free of pinholes and missed areas on the cutting edge 120 surface, which is particularly suitable for cutting head bodies with complex geometries, ensuring the integrity and reliability of insulation performance. All three processes allow for precise control of the coating thickness within the ideal range of 0.05mm to 0.2mm. Too thin a coating results in insufficient insulation, while too thick a coating dulls the cutting edge; this range balances electrical safety and mechanical sharpness, and is a key parameter for achieving "low-temperature cutting." Plasma cleaning or sandblasting can be performed before spraying to enhance the adhesion between the metal substrate and the coating; vapor deposition can achieve molecular-level bonding, preventing blistering, peeling, or delamination during high-temperature, friction, or sterilization processes.

[0043] This embodiment provides a low-temperature high-frequency surgical scalpel, including a handle 100 and a scalpel head body. The handle 100 is used to connect to the power supply of the high-frequency electrosurgical host, realizing stable input and transmission of electrical energy. The scalpel head body is fixedly installed at the front end of the handle 100, and is made entirely of medical-grade stainless steel (grade 316L), possessing good conductivity, mechanical strength, corrosion resistance, and biocompatibility, and can withstand high-temperature and high-pressure sterilization and repeated use.

[0044] The blade body has a planar structure 130 at one end and a cutting surface 120 and a cutting edge 110 at the other end, forming a dual-function end design. The surface of the planar structure 130 is polished and covered with an insulating coating, which can be used for gentle pressure, dissection, or blunt dissection of tissues during surgery, avoiding frequent instrument changes and improving surgical efficiency. The cutting surface 120 is a rectangular platform area, and its surface is also covered with an insulating coating, with only the cutting edge 110 exposed for conductivity, enabling energy focusing.

[0045] The cutting edge 110 consists of two opposing inclined sidewalls 140 and an arc-shaped cutting tip 150 connecting them. The inclined sidewalls 140 and the arc-shaped cutting tip 150 are connected by a smooth arc transition, without sharp corners or stress concentration points. Measurements show that the thickness A of the inclined sidewalls 140 at the cutting end is 0.12 mm, falling within the preferred range of 0.08 mm to 0.15 mm, ensuring both sharpness and sufficient structural strength to prevent chipping or breakage. The inclination angle B of the inclined sidewalls 140 is 35°, within the optimized range of 25° to 45°, achieving an optimal balance between low cutting resistance and high mechanical stability.

[0046] Both the blade face 120 and the planar structure 130 are covered with an insulating coating made of medical-grade silicone resin. The thickness of this coating is precisely controlled to 0.1 mm, fully meeting the technical requirements of 0.05 mm to 0.2 mm. The silicone resin coating is applied to the blade face 120 via a spraying process: before spraying, the metal surface undergoes plasma cleaning and activation treatment, followed by uniform spraying of the silicone resin solution using an automatic spray gun, and then low-temperature curing to form a film. This process ensures a continuous, dense, and complete coating with no gaps, and a smooth transition at the cutting edge, without affecting cutting performance.

[0047] The connection area between the blade body and the handheld part 100 adopts an arc transition with a transition radius of approximately 0.8 mm. This design effectively alleviates stress concentration, improves the fatigue resistance of the overall structure, and makes the instrument's shape smooth, facilitating sliding between tissues and reducing the risk of snagging.

[0048] The embodiments of the present utility model have been described in detail above with reference to the accompanying drawings. However, the present utility model is not limited to the above embodiments. Within the scope of knowledge possessed by those skilled in the art, various changes can be made without departing from the spirit of the present utility model.

Claims

1. A low-temperature high-frequency surgical scalpel, characterized in that, include: Handheld part; The cutter head body is mounted on the handheld part, which is used to connect the power supply so that the cutter head body can perform high-frequency cutting. The cutter head body includes a blade surface and a cutting edge. The cutting edge is arranged around the blade surface and has a beveled structure. The surface of the blade surface is provided with an insulating coating.

2. The low-temperature high-frequency surgical scalpel according to claim 1, wherein one end of the scalpel head body is a planar structure, and the other end is provided with the blade surface and the cutting edge, wherein both the planar structure and the blade surface are covered with the insulating coating.

3. A low-temperature high-frequency surgical scalpel according to claim 1 or 2, characterized in that, The insulating coating is made of silicone resin.

4. The low-temperature high-frequency surgical scalpel according to claim 3, characterized in that, The thickness of the silicone resin is 0.05 mm to 0.2 mm.

5. A low-temperature high-frequency surgical scalpel according to claim 1, characterized in that, The blade portion includes two opposing inclined sidewalls and an arc-shaped blade tip surface connected between the two inclined sidewalls, with an arc transition connection between the inclined sidewalls and the arc-shaped blade tip surface.

6. A low-temperature high-frequency surgical scalpel according to claim 5, characterized in that, The thickness of the cut end of the inclined sidewall is A, which satisfies 0.08mm≤A≤0.15mm.

7. A low-temperature high-frequency surgical scalpel according to claim 5, characterized in that, The blade body and the handheld part are connected by an arc transition.

8. A low-temperature high-frequency surgical scalpel according to claim 5, characterized in that, The inclination angle of the inclined sidewall is B, and satisfies: 25° ≤ B ≤ 45°.

9. A low-temperature high-frequency surgical scalpel according to claim 1, characterized in that, The blade body is made of titanium alloy or medical stainless steel.

10. A low-temperature high-frequency surgical scalpel according to claim 1, characterized in that, The insulating coating is applied to the blade surface by spraying, dipping, or vapor deposition processes.

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