A rotary cutting electrode assembly and electrode

Abstract

This invention belongs to the field of medical device technology and relates to a rotary cutting electrode assembly and its electrode. It includes an external tube with a distal hemostatic portion. An internal rotary cutting blade is inserted within the external tube. The internal rotary cutting blade includes an inner blade tube and a spiral portion located distal to the inner blade tube. The spiral portion includes a spiral body and a spiral tip located distal to the spiral body. The spiral body has a spiral groove with a cutting edge. The spiral groove communicates with the inner blade tube. A suction tube providing negative pressure is connected to the proximal end of the inner blade tube. The spiral tip protrudes outside the hemostatic portion. This invention solves the technical problem of existing technologies being unable to directly break up tissue and smoothly remove tissue debris from the human body.

Description

Technical Field

[0001] This invention belongs to the field of medical device technology, specifically relating to a rotary cutting electrode assembly and its electrode. Background Technology

[0002] Electrosurgical hemostatic instruments, such as electrocautery knives, electrocoagulation forceps, ultrasonic scalpels, and electrocoagulation tweezers, are frequently used in surgical procedures. Resection surgery is widely used in the treatment of sinus, pharyngeal, and joint lesions. The core instrument used in resection surgery is the razor blade. While razors offer fast cutting speed and high efficiency, they result in significant tissue bleeding during the cutting process. Hemostasis is achieved using hemostatic instruments such as electrocoagulation tweezers, and the repeated changing of instruments significantly delays the operation. To meet clinical needs, hemostatic razor blades with hemostatic functions have been developed, which can greatly shorten the operation time and improve surgical efficiency.

[0003] A hemostatic shaving head needs to possess both shaving and bipolar hemostasis capabilities. The hemostasis principle involves forming electrocoagulation bipolar electrodes on the electrode assembly. A high-frequency current is generated between the bipolar electrodes, accumulating energy to produce a large amount of heat to stop bleeding from the tissue wound. The shaving head works by creating cutting edges through windows on the circumferential sides of both the outer and inner blades. The inner blade rotates relative to the outer blade, and the windowed cutting edges of both blades create a scissor-like shearing effect on the human tissue, removing it. Tissue removal relies entirely on the negative pressure inside the inner blade tube for suction. The windowed structure on the circumferential sides of the shaving head dictates that the hemostatic bipolar electrodes must be positioned to avoid these windowed cutting edges. This results in a very limited area of ​​bipolar hemostasis; 360° complete hemostasis cannot be achieved circumferentially. Multiple rotations of the electrode assembly are required during operation to achieve hemostasis on multiple surfaces. Furthermore, since the shaving head relies entirely on the negative pressure inside the inner tube to suction the cut tissue, the inner tube's inner bore must have a sufficiently large cross-sectional size to ensure adequate negative pressure. This makes the shaving head unsuitable for operation in confined spaces. With the increasing prevalence and development of minimally invasive surgery, the requirements for the operating space of surgical electrode components are constantly increasing. For example, in minimally invasive thyroid nodule removal surgery, the surgical electrode components are required to perform tissue resection and hemostasis within a 3mm inner bore cannula. When the shaving head operates within this specification, the inner tube is typically less than 2mm, making it very prone to blockage. Therefore, there is currently no hemostasis shaving head solution that meets these requirements.

[0004] A search revealed that Chinese patent CN202211341983.6 discloses a rotary ablation device and medical equipment, including a rotary ablation needle, the end of which corresponds to the driving part and is connected to the handle part, and the top end located at the top of the needle body part for rotary ablation and suction; and an ablation needle tube, the end of which is connected to the handle part and the main body is fitted with the rotary ablation needle, with a first distance H1 between the needle and the outer surface of the rotary ablation needle, and the top end exposed for radiofrequency ablation. The rotary ablation needle includes a needle head and a needle shaft. The needle head includes a needle tip and a helix, and the needle tip has a triangular pyramidal structure; the top end of the helix is ​​connected to the bottom end of the needle tip and has a helical rotary ablation cutting edge structure; the lesion debris is suctioned out of the patient's body through the gap between the rotary ablation needle and the ablation needle tube, via the three-way tube and the suction tube. In fact, the solution disclosed in the above patent cannot achieve the breaking up of tissue and the transfer of debris to the patient's body. The reason is due to its own structure, that is, its needle tip has a triangular pyramidal structure, the needle tip is connected to the end of the spiral, and there is a clear gap between the rotary cutting needle and the ablation needle tube to discharge the debris tissue. In clinical practice, this approach can only present the following two situations: (1) If the rotary cutting needle does not rotate during the process of entering the tissue, the triangular pyramidal needle tip plays the role of drilling during the process of advancing towards the target tissue. After the target tissue is subjected to force, it spreads outwards. However, the spiral at the end of the needle tip cannot scrape the target tissue at the original position. It will only "completely cut the tissue that has been squeezed and spread to the spiral part into strips" and take it away. It does not have the effect of breaking the tissue. Instead, it may cause the suction channel at the end to be blocked. (2) If the rotary cutting needle has started to rotate during the process of entering the tissue, the triangular pyramidal needle tip plays the role of drilling during the process of advancing towards the target tissue. After the target tissue is subjected to force, it spreads outwards. Since the spiral at the end of the needle tip will hinder the target tissue from entering the spiral body for cutting during the rotation process, the actual effect is that it cannot scrape the target tissue at all, and there is no effect of breaking the tissue. In conclusion, the solution disclosed in this patent text cannot directly break up tissue and remove tissue debris from the body. Utility Model Content

[0005] Therefore, the purpose of this invention is to provide a rotary cutting electrode assembly and its electrode to solve the technical problem that the prior art cannot directly break up tissues and smoothly remove tissue debris from the human body.

[0006] The technical solution provided by this invention is as follows:

[0007] A rotary cutting electrode assembly includes an outer tube, within which a rotary cutting inner blade is inserted. The rotary cutting inner blade includes an inner blade tube and a spiral portion disposed at the distal end of the inner blade tube. The spiral portion communicates with the inner blade tube, and the spiral tip of the spiral portion protrudes from the outer tube. A suction tube providing negative pressure is connected to the proximal end of the inner blade tube. The spiral tip protrudes from the outer tube.

[0008] Furthermore, the spiral portion includes a spiral body, the spiral tip is located at the distal end of the spiral body, and the spiral body is provided with a spiral groove with a cutting edge.

[0009] Furthermore, the length of the spiral blade tip protruding from the hemostatic part is 0.2-2 mm.

[0010] Furthermore, the outer diameter of the spiral portion is the same as the outer diameter of the inner knife tube.

[0011] Furthermore, the spiral section and the inner blade tube are located inside the outer tube and fit snugly against it. Since there is no gap between them, this structural design brings several advantages to the present invention, such as:

[0012] (1) By limiting the position of the spiral part, it provides support to a certain extent, which can help it to accurately break the tissue of the target area;

[0013] (2) By electrifying the inner blade of the rotary cutter, the piercing and punching function will be easier;

[0014] (3) Prevent the broken tissue from entering the gap between the inner blade of the rotary cutter and the outer tube, and contaminating the inside of the outer tube.

[0015] Furthermore, the distal end of the external tube is provided with an opening for the spiral blade tip to protrude, and the opening can be any one of the following: end face opening, side opening, or a combination of end face and side opening.

[0016] Furthermore, the external tubing includes a front electrode tube, an inter-electrode insulating tube, a rear electrode tube, and an outer insulating tube arranged sequentially from the inside to the outside; the distal end of the front electrode tube protrudes from the inter-electrode insulating tube and serves as electrode one, and the distal end of the rear electrode tube protrudes from the outer insulating tube and serves as electrode two, with electrode one and electrode two having opposite polarities.

[0017] Furthermore, the exposed surface area of ​​electrode one is smaller than that of electrode two.

[0018] Furthermore, an outflow channel is provided between the rear electrode tube and the inter-electrode insulating tube, and the outflow channel extends to the distal end so that the fluid flows sequentially through electrode two and electrode one. The advantage of this structural design is that the fluid can be fully utilized to cool electrode one and electrode two, preventing excessive energy accumulation between the two electrodes from causing the bipolar temperature to become too high and burn the tissue, and also preventing the electrode assembly from becoming too hot and sticking to the tissue.

[0019] Furthermore, the end face of the front electrode tube is provided with an opening for the spiral blade tip to protrude. This invention utilizes a rotary cutting inner blade to perform tissue cutting at the distal end face without occupying lateral space, allowing the front and rear electrode tubes to be arranged 360° in the circumferential direction, ensuring bipolar 360° hemostasis. Moreover, because the rotary cutting inner blade is located at the distal end face, the axial distance between the front and rear electrode tubes is not affected by the cutting structure, allowing for arbitrary adjustment of their axial positions to achieve the most ideal hemostatic effect.

[0020] The present invention provides a rotary cutting electrode, including a handle, a cable plug, and the electrode assembly described above; the distal end of the handle is connected to the proximal end of the electrode assembly, and the proximal end of the handle is connected to the cable plug; the cable plug is connected to the external tube through a wire; and it also includes a rotary power system connected to the inner blade tube.

[0021] Furthermore, the handle is provided with a hand control button, which is connected between the wires.

[0022] The present invention also provides a method for tissue fragmentation and transportation, comprising the following steps:

[0023] Step 1: The rotation of the inner blade generates axial and circumferential forces, which are directly applied to the target tissue to break it up and bring the debris tissue in the human body to the proximal end.

[0024] Step 2: During the movement of the debris towards the proximal end, the direction of movement is assisted and limited by the external tubing that is attached to the periphery of the rotary cutting inner blade;

[0025] Step 3: As the debris moves proximally, it is drawn out of the body by a suction tube connected to the proximal end of the rotary cutting inner blade.

[0026] Furthermore, the rotary cutting inner blade includes an inner blade tube and a spiral portion disposed at the distal end of the inner blade tube. The spiral portion includes a spiral body and a spiral tip located at the distal end of the spiral body. The spiral body is provided with a spiral groove with a cutting edge. The spiral groove communicates with the inner blade tube, and the proximal end of the inner blade tube communicates with the suction tube.

[0027] Furthermore, the external tubing includes a front electrode tube, an inter-electrode insulating tube, a rear electrode tube, and an outer insulating tube arranged sequentially from the inside to the outside; the distal end of the front electrode tube protrudes from the inter-electrode insulating tube and serves as electrode one, and the distal end of the rear electrode tube protrudes from the outer insulating tube and serves as electrode two, with electrode one and electrode two having opposite polarities.

[0028] Compared with the prior art, the main beneficial effects of the present invention are:

[0029] This invention achieves tissue resection. Its core lies in the improved structure of the rotary cutting inner blade, enabling it to apply both axial and circumferential forces distally. These two forces work together to directly break up the tissue. This function also includes perforation and pore enlargement (the spiral section pulls and cuts surrounding tissue to enlarge the pore), a significant difference from CN202211341983.6, which only performs perforation. Through the cooperation of the rotary cutting inner blade and the external tubing, an auxiliary force for transferring fragmented tissue is provided, transporting the fragmented tissue proximally. Furthermore, this transport path is the channel inherent in the rotary cutting inner blade itself, rather than the transport path formed between the inner blade and the external tubing. This is also a significant difference from existing technologies, especially CN202211341983.6. In addition, the suction tube, connected to the proximal end of the inner blade tube, forms a debris suction channel composed of the spiral groove, the inner blade tube, and the suction tube. This creates a debris transfer system where the rotary cutting inner blade, the external tube, and the suction channel work together, effectively avoiding the problem of small-sized blades easily clogging due to insufficient suction force. This allows the invention to operate in confined spaces. Therefore, the invention simultaneously solves the technical problem of existing technologies being unable to directly break up tissue and smoothly remove tissue debris from the human body. Attached Figure Description

[0030] To more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the drawings used in the embodiments will be briefly described below. Obviously, the drawings described below are merely some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort. The above and other objects, features, and advantages of the present invention will become clearer through the accompanying drawings. In all the drawings, the same reference numerals indicate the same parts. The drawings are not intentionally drawn to scale to actual dimensions; the focus is on illustrating the main points of the invention.

[0031] Figure 1 This is a schematic diagram of the outer shape of the far end of the external pipe fitting;

[0032] Figure 2 Schematic diagram of the internal rotary cutting blade Figure 1 ;

[0033] Figure 3 Schematic diagram of the internal rotary cutting blade Figure 2 ;

[0034] Figure 4 This is a schematic diagram of the overall structure of the electrode;

[0035] Figure 5 For the appendix Figure 4 Schematic diagram of part A of the middle electrode;

[0036] Figure 6 For the appendix Figure 4 A schematic diagram of section B of the middle electrode.

[0037] Figure label:

[0038] 1. External fittings; 2. Rotary cutting inner blade; 3. Handle; 4. Cable plug; 6. Rotary power system;

[0039] 1-1. Hemostasis section; 1-2. Opening; 1-3. Front electrode tube; 1-4. Inter-electrode insulation tube; 1-5. Rear electrode tube; 1-6. Outer insulation tube; 1-7. Outflow channel; 1-8. Liquid inlet assembly; 1-9. Liquid inlet; 1-10. Injection tube.

[0040] 2-1. Inner blade tube; 2-2. Spiral section; 2-3. Suction tube;

[0041] 3-1. Manual control button; 3-2. Valve; 3-3. Proximal mounting base; 3-4. Distal mounting base; 3-5. Insulating support.

[0042] 2-2-1, Helical body; 2-2-2, Helical cutting tip; 2-2-3, Helical groove; 2-2-4, Cutting edge;

[0043] 6-1. Motor; 6-2. Motor mount; 6-3. Rear bearing; 6-4. Front bearing; 6-5. Transmission gear set. Detailed Implementation

[0044] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. The components of the embodiments of the present invention described and shown in the accompanying drawings can generally be arranged and designed in various different configurations.

[0045] Therefore, the following detailed description of the embodiments of the invention provided in the accompanying drawings is not intended to limit the scope of the claimed invention, but merely to illustrate selected embodiments of the invention. All other embodiments obtained by those skilled in the art based on the embodiments of the invention without inventive effort are within the scope of protection of the invention.

[0046] It should be noted that similar labels and letters in the following figures indicate similar items. Therefore, once an item is defined in one figure, it does not need to be further defined and explained in subsequent figures.

[0047] Fluids: In this invention, fluids mainly refer to physiological saline, etc.

[0048] Proximal end: refers to the end closest to the practitioner.

[0049] Distant end: refers to the end closest to the target tissue.

[0050] Example 1, see attached document Figure 1-6 As shown, the present invention provides a rotary cutting electrode assembly, including an outer tube 1, the outer tube 1 having a hemostatic part 1-1 located at the distal end, and a rotary cutting inner blade 2 passing through the outer tube 1. The rotary cutting inner blade 2 includes an inner blade tube 2-1 and a spiral part 2-2 located at the distal end of the inner blade tube 2-1. The spiral part 2-2 includes a spiral body 2-2-1 and a spiral cutting edge 2-2-2 located at the distal end of the spiral body 2-2-1. The spiral body 2-2-1 has a spiral groove 2-2-3 with a cutting edge 2-2-4; the spiral groove 2-2-3... It is connected to the inner blade tube 2-1; the proximal end of the inner blade tube 2-1 is connected to a suction tube 2-3 that provides negative pressure; the spiral blade tip 2-2-2 is exposed outside the hemostatic part 1-1 (that is, the spiral body 2-2-1 is located inside the hemostatic part 1-1); in the working state, the rotation of the spiral blade tip 2-2-2 will apply axial and circumferential forces to the distal end to crush the tissue encountered in the path, and the spiral part 2-2 cooperates with the external tube 1 to guide the crushed tissue from its distal end into the inner blade tube 2-1, and the crushed tissue is extracted by the negative pressure provided by the suction tube 2-3.

[0051] This invention is applicable to various surgical environments, especially to minimally invasive soft tissue resection surgeries, such as minimally invasive thyroid nodule and thyroid cyst resection, spinal decompression surgery for nucleus pulposus extraction, and minimally invasive uterine fibroid surgery. This embodiment primarily designs the product dimensions for the surgical environment of minimally invasive thyroid nodule resection; adjustments can be made accordingly for other surgical environments.

[0052] The specific implementation method is as follows:

[0053] Based on the above description, it can be concluded that the external structure of the spiral part 2-2 can be regarded as a spiral structure extending towards the distal end.

[0054] The length of the spiral blade tip 2-2-2 exposed above the hemostatic part 1-1 is 0.2-2mm, preferably 0.2mm, 0.25mm, 0.28mm, 0.3mm, 0.33mm, 0.35mm, 0.4mm, etc.

[0055] The length of the spiral section 2-2 is 2-5 mm, preferably 2 mm, 2.5 mm, 2.8 mm, 3 mm, 3.3 mm, 3.5 mm, 4 mm, 4.5 mm, 5 mm, etc. The spacing between the spiral gaps of the spiral section 2-2 is equal, and the spacing can be set to 1 mm, 1.5 mm, 1.8 mm, 2 mm, 2.3 mm, 2.5 mm, etc. The outer diameter of the spiral section 2-2 is the same as the outer diameter of the inner knife tube 2-1.

[0056] Reference Appendix Figure 1-5 As shown, the spiral body 2-2-1 and the inner blade tube 2-1 are located inside the outer tube 1 and are fitted together with the outer tube 1. Since there is no gap between them, this structural design brings several advantages to the present invention, such as:

[0057] (1) By limiting the position of the spiral part, it provides support to a certain extent, which can help it to accurately break the tissue of the target area;

[0058] (2) By electrifying the inner blade of the rotary cutter, the piercing and punching function will be easier;

[0059] (3) Prevent the broken tissue from entering the gap between the inner blade of the rotary cutter and the outer tube, and contaminating the inside of the outer tube.

[0060] The distal end of the external tube 1 is provided with an opening 1-2 for the spiral blade tip 2-2-2 to be exposed, and the opening 1-2 is an end face opening. This description is a more specific explanation of the above solution. It is not recommended to have a side opening or a combined end face and side opening like a regular planer, to avoid the inability to achieve 360° hemostasis.

[0061] The external pipe fitting 1 may have many other configuration options. The preferred option here is:

[0062] Reference Appendix Figure 1 , 5 As shown, the external tube 1 includes a front electrode tube 1-3, an inter-electrode insulating tube 1-4, a rear electrode tube 1-5, and an outer insulating tube 1-6 arranged sequentially from the inside to the outside; the distal end of the front electrode tube 1-3 protrudes from the inter-electrode insulating tube 1-4 and serves as electrode one, and the distal end of the rear electrode tube 1-5 protrudes from the outer insulating tube 1-6 and serves as electrode two, with electrode one and electrode two having opposite polarities.

[0063] The exposed surface area of ​​electrode one is smaller than that of electrode two. At this time, if connected to a plasma host, it can help electrode one to generate plasma in the environment of physiological saline. Plasma medical devices are widely used in the field of minimally invasive surgery. They mainly use low-temperature plasma technology to achieve precise tissue cutting, coagulation hemostasis and ablation treatment, reducing thermal damage to surrounding tissues (the working temperature is usually 40-70℃). Its core functions include: (1) Precise tissue cutting: Plasma breaks the molecular bonds of the target tissue to achieve millimeter-level precision cutting, which is especially suitable for delicate operations such as meniscus repair and cartilage trimming. (2) Efficient hemostasis and coagulation: Bipolar plasma hemostasis technology coagulates blood vessels with a diameter of less than 2 mm, significantly reducing surgical bleeding, and is suitable for various scenarios in multiple departments such as otolaryngology and orthopedics. (3) Minimally invasive ablation treatment: Vaporize and ablate diseased tissue (such as intervertebral disc herniation, tumor or nucleus pulposus) while preserving healthy structures, such as tumor ablation and correction of nasal turbinate hypertrophy. Of course, the above-mentioned relationship between the exposed areas of electrode one and electrode two can also be omitted. Bipolar radiofrequency hemostasis technology can be used, which heats the tissue with high-frequency current. The current thermal effect causes protein coagulation and blood vessel closure, thereby achieving hemostasis.

[0064] Reference Appendix Figure 1-3 As shown, an outflow channel 1-7 is provided between the rear electrode tube 1-5 and the inter-electrode insulating tube 1-4. The outflow channel 1-7 extends distally to allow fluid to flow sequentially through electrode two and electrode one. This is because both bipolar plasma hemostasis and bipolar radiofrequency hemostasis are suitable for operation in relatively low-temperature environments (e.g., 40-70℃, without considering the difference between the two here). This structural design can fully utilize the fluid to cool electrode one and electrode two, preventing excessive energy accumulation between the bipolar electrodes from causing excessively high bipolar temperatures and burning tissue, and also preventing the electrode assembly from overheating and adhering to tissue.

[0065] The end face of the front electrode tube 1-3 is provided with an opening 1-2 for the spiral blade tip 2-2-2 to be exposed. This is a further explanation of the above-mentioned scheme adopted for the external tube 1.

[0066] Because only the spiral blade tip is exposed outside the hemostatic part (i.e., the part consisting of electrode one, the inter-electrode insulating tube, and electrode two), the spiral blade tip exerts axial and circumferential forces during operation. Besides directly generating a traction effect on fragmented tissue and fulfilling its core function of transporting tissue debris outside the body in conjunction with external tubing and aspiration tubes, it also shortens the distance between the hemostatic part and the target tissue. This structure is beneficial for improving hemostatic accuracy. Compared to existing technologies, especially compared to CN202211341983.6, this structure allows the hemostatic part to be almost infinitely close to the farthest point of the spiral blade tip, and the hemostatic accuracy is incomparable.

[0067] Reference Appendix Figure 4-6As shown, the present invention provides a rotary cutting electrode, including a handle 3, a cable plug 4, and the electrode assembly described above; the distal end of the handle 3 is connected to the proximal end of the electrode assembly, and the proximal end of the handle 3 is connected to the cable plug 4; the cable plug 4 is connected to the external tube 1 through a wire; it also includes a rotary power system 6, which is connected to the inner blade tube 2-1.

[0068] The electrodes are further described below:

[0069] The proximal end of the suction tube 2-3 can be connected to a negative pressure device (not shown in the attached diagram). A flow control valve 3-2 can be further added to the suction channel; the valve 3-2 can preferably be located on the handle 3.

[0070] The outflow channel 1-7 is connected to the liquid inlet 1-9 at the rear electrode tube 1-5 (whether or not it is covered by the outer insulating tube 1-6).

[0071] The handle 3 is equipped with a hand control button 3-1, which is connected to the wires. Generally, the hand control button 3-1 and the valve 3-2 are positioned in a location that does not obstruct the operator's grip, such as above the handle 3. The handle 3 is typically designed with symmetrical left and right halves; therefore, the hand control button 3-1 and the valve 3-2 can be installed at the junction of the left and right halves.

[0072] The proximal end of the electrode assembly located inside the handle 3 can be fixed in the following way: by setting a proximal fixing seat 3-3, a distal fixing seat 3-4 and an insulating support 3-5 inside the handle 3. Specifically, the rear end of the front electrode tube 1-3 is fixed to the inner hole of the proximal fixing seat 3-3, and the rear electrode tube 1-5 is fixed to the inner hole of the distal fixing seat 3-4; the proximal fixing seat 3-3 is fixed to the rear end of the insulating support 3-5, and the distal fixing seat 3-4 is fixed to the front end of the insulating support 3-5; the inter-electrode insulating tube 1-4 is heat-shrinkably fixed to the outer circle of the front electrode tube 1-3, and the rear electrode tube 1-5 is fitted onto the outside of the inter-electrode insulating tube 1-4. The annular gap between the inner hole of the rear electrode tube 1-5 and the outer circle of the inter-electrode insulating tube 1-4 forms a water channel, and the front end of the rear electrode tube 1-5 forms an outflow channel 1-7; the injection tube 1-10 is fixed to the insulating support 3-5 and communicates with the liquid inlet assembly 1-8; the liquid inlet 1-9 is formed between the inner hole of the insulating support 3-5 and the outer circle of the inter-electrode insulating tube 1-4. The outer insulating tube 24 is heat-shrinkably fixed to the outer circle of the rear electrode tube 1-5, serving as an insulating protection.

[0073] It is worth mentioning that a mounting position for the rotary power system 6 still needs to be added inside the handle 3 to provide rotational power to the inner blade tube 2-1. Typically, the rotational speed of the rotary power system 6 is primarily controlled by a matching foot switch. This part of the technology is not a core innovation. The composition of the rotary power system 6 and its relationship with components such as the inner blade tube 2-1 can be implemented with reference to the following scheme:

[0074] Reference Appendix Figure 4-6 As shown, the rotary power system 6 includes a motor, with motor 6-1 fixed on motor mount 6-2 and valve 3-2 fixed on motor mount 6-2. A rear bearing 6-3 and a front bearing 6-4 are mounted on the rear end of the inner knife tube 2-1, which is then mounted on motor mount 6-2 via the rear bearing 6-3 and front bearing 6-4. Cable plug 4 provides power to motor 6-1, front electrode tube 1-3, and rear electrode tube 1-6. The input gear of transmission gear set 6-5 is fixed on the output shaft of motor 6-1, and the output gear of transmission gear set 6-5 is fixed on the rear end of inner knife tube 2-1. Motor 6-1 transmits kinetic energy to inner knife tube 2-1 through the transmission gear set, driving inner knife tube 2-1 to rotate. Hand control button 3-1 transmits signals to the main unit via a press switch, thereby controlling the hemostatic energy output of front electrode tube 1-3 and rear electrode tube 1-5. Alternatively, a traditional foot switch (not shown in the attached diagram) can be used to control the hemostatic energy output, or both methods can be used in combination. Valve 3-2 is used to control the opening and closing of the suction channel established by the inner knife tube 2-1 and the suction tube 2-3. Other technical details related to the rotational power system 6, such as the description of the sealing ring, can be found in the existing design of the surgical power system. Alternatively, the descriptions related to the technical details of electrode one, electrode two, etc., are sufficient for those skilled in the art to understand how to implement, and therefore will not be repeated in this embodiment.

[0075] The present invention also provides a method for tissue fragmentation and transportation, comprising the following steps:

[0076] Step 1: The rotation of the inner blade 2 generates axial and circumferential forces, which are directly applied to the target tissue to break it up and bring the debris tissue in the human body to the proximal end.

[0077] Step 2: During the movement of the debris towards the proximal end, the direction of movement is assisted and limited by the external tube 1 that is attached to the periphery of the inner rotary cutter 2;

[0078] Step 3: As the debris moves proximally, it is drawn out of the body by the suction tube 2-3, which is connected to the proximal end of the rotary cutting inner blade 2.

[0079] The above description is merely a preferred embodiment of the present invention and is not intended to limit the invention. Various modifications and variations can be made to the present invention by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the scope of protection of the present invention.

Claims

1. A rotary cutting electrode assembly, characterized in that, The device includes an external tube (1), and a rotary cutting inner blade (2) is inserted inside the external tube (1). The rotary cutting inner blade (2) includes an inner blade tube (2-1) and a spiral part (2-2) located at the distal end of the inner blade tube (2-1). The spiral part (2-2) is connected to the inner blade tube (2-1), and the spiral tip (2-2-2) of the spiral part (2-2) protrudes from the external tube (1). A suction tube (2-3) that provides negative pressure is connected to the proximal end of the inner blade tube (2-1). The spiral tip (2-2-2) protrudes from the external tube (1).

2. The rotary cutting electrode assembly according to claim 1, characterized in that, The spiral part (2-2) includes a spiral body (2-2-1), the spiral tip (2-2-2) is located at the far end of the spiral body (2-2-1), and the spiral body (2-2-1) is provided with a spiral groove (2-2-3) with a cutting edge (2-2-4).

3. The rotary cutting electrode assembly according to claim 1, characterized in that, The length of the spiral blade tip (2-2-2) exposed above the hemostatic part (1-1) is 0.2-2 mm.

4. The rotary cutting electrode assembly according to claim 1, characterized in that, The outer diameter of the spiral section (2-2) is the same as the outer diameter of the inner knife tube (2-1).

5. A rotary cutting electrode assembly according to claim 1, characterized in that, The spiral part (2-2) and the inner knife tube (2-1) are located inside the outer tube (1) and are in contact with the outer tube (1).

6. The rotary cutting electrode assembly according to claim 1, characterized in that, The external tube (1) includes a front electrode tube (1-3), an inter-electrode insulating tube (1-4), a rear electrode tube (1-5), and an outer insulating tube (1-6) arranged sequentially from the inside to the outside; the distal end of the front electrode tube (1-3) protrudes from the inter-electrode insulating tube (1-4) and serves as electrode one, and the distal end of the rear electrode tube (1-5) protrudes from the outer insulating tube (1-6) and serves as electrode two, with electrode one and electrode two having opposite polarities.

7. A rotary cutting electrode assembly according to claim 6, characterized in that, The exposed surface area of ​​electrode one is smaller than that of electrode two.

8. A rotary cutting electrode assembly according to claim 6, characterized in that, An outflow channel (1-7) is provided between the rear electrode tube (1-5) and the inter-electrode insulating tube (1-4), and the outflow channel (1-7) extends to the distal end so that the fluid flows through the second electrode and the first electrode in sequence.

9. A rotary cutting electrode assembly according to claim 6, characterized in that, The end face of the front electrode tube (1-3) is provided with an opening (1-2) for the spiral blade tip (2-2-2) to be exposed.

10. A rotary cutting electrode, comprising a handle (3) and a cable plug (4), characterized in that, It also includes an electrode assembly according to any one of claims 1-9; the distal end of the handle (3) is connected to the proximal end of the electrode assembly, and the proximal end of the handle (3) is connected to the cable plug (4); the cable plug (4) is connected to the external tube (1) via a wire; it also includes a rotary power system (6) connected to the inner knife tube (2-1).

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