Hemostatic rotary cutting electrode assembly and electrode thereof

Abstract

The invention belongs to the technical field of medical instruments, and relates to a hemostasis rotary-cut electrode assembly and an electrode thereof.The hemostasis rotary-cut electrode assembly comprises a hemostasis tube, the hemostasis tube is provided with a hemostasis part located at the far end, a rotary-cut inner knife is arranged in the hemostasis tube in a penetrating mode, and the rotary-cut inner knife comprises an inner knife tube and a spiral part arranged at the far end of the inner knife tube; the spiral part comprises a spiral main body and a spiral blade tip located at the far end of the spiral main body, and the spiral main body is provided with a spiral groove with a cutting edge; the spiral groove is communicated with the inner knife tube; the near end of the inner knife tube is communicated with a suction tube for providing negative pressure; the spiral blade tip is exposed out of the hemostasis part. The technical problem that in the prior art, tissue cannot be directly broken, and tissue chippings cannot be smoothly brought out of the human body is solved.

Description

Technical Field

[0001] The present invention belongs to the technical field of medical devices, and in particular relates to a hemostatic rotary cutting electrode assembly and an electrode thereof. Background Art

[0002] Electrosurgical hemostatic devices, such as electrocautery, electrocoagulation forceps, ultrasonic scalpels, and electrocoagulation tweezers, are frequently used in surgical procedures. Planing surgery is widely used to treat diseased tissue in the sinuses, throat, and joints. The core instrument used in planing surgery is the planer. While the planer is fast and efficient, it causes significant bleeding during the cutting process. Hemostatic devices, such as electrocoagulation forceps, are often used during the hemostasis process. Repeated instrument changes significantly delay the operation. To meet clinical needs, hemostatic planing blades with hemostatic functions have emerged, significantly shortening surgical time and improving efficiency.

[0003] A hemostatic shaving blade must possess both shaving and bipolar hemostasis capabilities. The hemostasis mechanism utilizes a bipolar electrode formed on the electrode assembly, generating a high-frequency current between the two electrodes. This energy accumulation generates a large amount of heat to stop bleeding in the tissue wound. The shaving blade operates by creating cutting edges on the circumferential sides of the outer and inner blades. The inner blade rotates relative to the outer blade. These cutting edges create a scissor-like shearing effect on human tissue, excising it. Tissue extraction relies entirely on the negative pressure within the inner blade tube for suction. The circumferential windowing of the shaving blade dictates that the bipolar electrode must be positioned away from the lateral windowing edges. This significantly limits the range of bipolar hemostasis, preventing 360° circumferential hemostasis. Multiple rotations of the electrode assembly are required during operation to achieve multi-faceted hemostasis. Moreover, since the planing head completely relies on the negative pressure inside the inner blade tube to suction the cut tissue, in order to ensure sufficient negative pressure, the inner hole of the inner blade tube must have a sufficiently large cross-sectional size, which makes the planing head unable to meet the requirements of operation in narrow spaces. With the popularization and development of minimally invasive surgery, the requirements for the operating space of surgical electrode assemblies are constantly increasing. For example, in minimally invasive surgery for thyroid nodule resection, the surgical electrode assembly is required to perform tissue resection and hemostasis in a cannula with a 3mm inner hole. When the planing head operates under this specification, the inner blade tube is usually less than 2mm and is very prone to clogging. Therefore, there is currently no hemostatic planing solution that can meet this requirement.

[0004] After searching, it was found that Chinese patent CN202211341983.6 discloses a rotary cutting ablation device and medical equipment, including a rotary cutting needle, the end of which corresponds to the driving part, is connected to the handle part, and the top is located at the top of the needle body part, which is used to achieve rotary cutting suction; an ablation needle tube, the end of which is connected to the handle part, and the main body is sleeved with the rotary cutting needle, and there is a first distance H1 between it and the outer surface of the rotary cutting needle, and the top is exposed to achieve radiofrequency ablation. The rotary cutting needle includes a needle head and a needle rod, and the needle head includes a needle tip and a spiral body, and the needle tip has a triangular pyramid structure; the top of the spiral body is connected to the bottom end of the needle tip, and has a spiral rotary cutting edge structure; the lesion debris tissue passes through the gap between the rotary cutting needle and the ablation needle tube, and is attracted and removed from the patient's body through the three-way tube and the suction tube. In fact, the solution disclosed in the above patent cannot achieve the purpose of crushing tissue and transferring the debris tissue outside the patient's body. The reason is caused by its own structure, that is, the needle tip has a triangular pyramid structure, the needle tip is connected to the spiral at the end, and there is a clear gap between the rotary cutting needle and the ablation needle tube to discharge debris tissue. In clinical practice, this scheme 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 pyramid needle tip plays a role of punching during the process of advancing to the target tissue. The target tissue spreads out in all directions after being subjected to force, and the spiral at the end of the needle tip cannot scrape the target tissue at the original position at all. It will only "completely cut into strips" the tissue that is squeezed and spread to the spiral part and take it away, which will not have the effect of breaking the tissue. Instead, it is likely to 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 pyramid needle tip plays a role of punching during the process of advancing to the target tissue. The target tissue spreads out in all directions after being subjected to force. Since the spiral at the end of the needle tip will hinder the target tissue from entering the spiral for cutting during the rotation process, the actual effect is that it cannot scrape the target tissue at all, let alone the effect of breaking the tissue. In summary, the solution disclosed in this patent document cannot directly break up tissue and remove tissue debris from the body. Summary of the Invention

[0005] In view of this, the object of the present invention is to provide a hemostatic rotary cutting electrode assembly and an electrode thereof to solve the technical problem that the prior art cannot directly break up tissue and smoothly remove tissue debris from the human body.

[0006] The technical solutions provided by the present invention are as follows: A hemostatic rotary cutting electrode assembly comprises a vascular stop component, the vascular stop component is provided with a hemostatic portion located at the distal end, a rotary cutting inner knife is passed through the vascular stop component, the rotary cutting inner knife comprises an inner knife tube and a spiral portion arranged at the distal end of the inner knife tube, the spiral portion comprises a spiral body and a spiral blade 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 is connected to the inner knife tube; the proximal end of the inner knife tube is connected to a suction tube that provides negative pressure; the spiral blade tip is exposed outside the hemostatic portion; in a working state, the rotation of the spiral blade tip will apply axial force and circumferential force to the distal end to crush tissue encountered on the path, and the spiral portion cooperates with the vascular stop component to guide the crushed tissue from its distal end into the inner knife tube, and extract the crushed tissue through the suction tube.

[0007] Furthermore, the length of the spiral blade tip exposed from the hemostatic portion is 0.2-2 mm.

[0008] Furthermore, the outer diameter of the spiral portion is the same as the outer diameter of the inner blade tube.

[0009] Furthermore, the spiral body and the inner blade tube are located within the vascular stopper and fit closely to the vascular stopper. Since there is no gap between the two, this structural design brings multiple benefits in the present invention, such as: (1) The position of the spiral part is limited, which provides support to a certain extent and can help it accurately break the tissue at the target site; (2) Make the inner blade of the rotary cutting machine also electrified, so that the puncture and perforation will be easier; (3) Prevent the broken tissue from entering the gap between the rotary cutting blade and the vascular stopper, and contaminating the inside of the vascular stopper.

[0010] Furthermore, the distal end of the vascular stop member is provided with an opening for exposing the spiral blade tip, and the opening can be any one of an end face opening, a side face opening, and an end face and side face opening.

[0011] Furthermore, the blood vessel stopper includes a front electrode tube, an inter-electrode insulating tube, a rear electrode tube and an outer insulating tube arranged in sequence from the inside to the outside; the distal end of the front electrode tube is exposed through the inter-electrode insulating tube and serves as electrode one, and the distal end of the rear electrode tube is exposed through the outer insulating tube and serves as electrode two, and the electrical polarities of electrode one and electrode two are opposite.

[0012] Furthermore, the exposed surface area of ​​the first electrode is smaller than the exposed surface area of ​​the second electrode.

[0013] Furthermore, an outflow channel is provided between the rear electrode tube and the inter-electrode insulating tube. The outflow channel extends distally to allow fluid to flow sequentially through electrode 2 and electrode 1. This structural design has the advantage of fully utilizing the fluid to cool electrodes 1 and 2, preventing excessive energy accumulation between the two electrodes, which could cause overheating and tissue burns, and also preventing the electrode assembly from overheating and adhering to tissue.

[0014] Furthermore, the end face of the front electrode tube is provided with an opening for exposing the spiral blade tip. The present invention utilizes a rotary cutting blade to perform tissue cutting at the distal end face, eliminating the need for lateral space. This allows the front and rear electrode tubes to be arranged 360° circumferentially, ensuring bipolar 360° hemostasis. Furthermore, because the rotary cutting blade is positioned at the distal end face, the axial distance between the front and rear electrode tubes is unaffected by the cutting structure, allowing for arbitrary adjustment of their axial positions to achieve optimal hemostasis.

[0015] The present invention provides a hemostatic rotary cutting electrode, comprising 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 hemostatic blood vessel component through a wire; and further comprises a rotational power system, which is connected to the inner knife tube.

[0016] Furthermore, the handle is provided with a manual control button, and the manual control button is connected between the wires.

[0017] The present invention also provides a tissue fragmentation and transportation method, comprising the following steps: Step 1: The rotation of the internal rotary cutting blade generates axial and circumferential forces, which directly act on the target tissue to break it up and move the debris in the human body to the proximal end; Step 2: During the movement of the debris tissue toward the proximal end, the vascular stop member attached to the periphery of the rotary cutting inner blade assists in limiting the movement direction; Step 3: During the movement of the debris tissue toward the proximal end, the debris tissue is sucked out of the human body by a suction tube connected to the proximal end of the rotary cutting blade.

[0018] Furthermore, the rotary cutting inner knife includes an inner knife tube and a spiral portion arranged at the distal end of the inner knife tube, the spiral portion includes a spiral body and a spiral blade tip located at the distal end of the spiral body, and the spiral body is provided with a spiral groove with a cutting edge; the spiral groove is connected to the inner knife tube, and the proximal end of the inner knife tube is connected to the suction tube.

[0019] Furthermore, the blood vessel stopper includes a front electrode tube, an inter-electrode insulating tube, a rear electrode tube and an outer insulating tube arranged in sequence from the inside to the outside; the distal end of the front electrode tube is exposed through the inter-electrode insulating tube and serves as electrode one, and the distal end of the rear electrode tube is exposed through the outer insulating tube and serves as electrode two, and the electrical polarities of electrode one and electrode two are opposite.

[0020] Compared with the prior art, the main beneficial effects of the present invention are: 1. The present invention achieves both tissue excision and hemostasis, avoiding the need for instrument replacement to stop bleeding during tissue excision surgery, shortening operative time and improving surgical efficiency. Its core lies in an improved structure of the rotary endobladder, enabling it to apply both axial force distally and circumferential force to the periphery. These two forces cooperate to achieve direct tissue fragmentation. This function also embodies both perforation and reaming (the spiral portion pulls and cuts the surrounding tissue to achieve perforation expansion), significantly different from the perforation-only function of CN202211341983.6. The coordination of the rotary endobladder and the vascular stop element provides an auxiliary tissue transfer force, transporting the comminuted tissue proximally. This transport path is through the rotary endobladder's own channel, rather than the transport path formed between the rotary endobladder and the vascular stop element. This is a significant difference from the prior art, particularly from CN202211341983.6. Combined with a suction tube connected to the proximal end of the inner blade tube, this creates a debris aspiration channel comprised of the spiral groove, inner blade tube, and suction tube. This creates a debris transfer system that integrates the inner blade, the vascular stop, and the suction channel. This effectively avoids the clogging problem of small blades due to insufficient suction, allowing the present invention to operate in confined and narrow areas. Consequently, the present invention solves the technical problem of prior art, which prevents direct tissue fragmentation and smooth removal of tissue fragments from the body.

[0021] 2. Because only the helical blade tip is exposed outside the hemostatic portion (i.e., the portion consisting of electrode 1, the interelectrode insulating tube, and electrode 2), the helical blade tip exerts both axial and circumferential forces during operation. This not only directly pulls tissue fragments, enabling the hemostatic device and the suction tube to transport debris out of the body, but also shortens the distance between the hemostatic portion and the target tissue, improving hemostatic accuracy. Compared to existing technologies, especially CN202211341983.6, this structure allows the hemostatic portion to be virtually infinitely close to the distal end of the helical blade tip, yet achieves unmatched hemostatic accuracy. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following is a brief introduction to the drawings required for use in the embodiments. Obviously, the drawings described below are only some embodiments of the present invention. For those of ordinary skill in the art, other drawings can be obtained based on these drawings without creative work. The above and other purposes, features and advantages of the present invention will become clearer through the accompanying drawings. The same reference numerals indicate the same parts throughout the drawings. The present invention does not intentionally scale the drawings to the actual size, and the focus is on illustrating the main purpose of the present invention.

[0023] Figure 1 A schematic diagram of the appearance of the distal end of the vascular stop; Figure 2 Schematic diagram of the structure of the rotary cutting inner knife Figure 1 ; Figure 3 Schematic diagram of the structure of the rotary cutting inner knife Figure 2 ; Figure 4 Schematic diagram of the overall structure of the electrode; Figure 5 For attachment Figure 4 Schematic diagram of the structure of part A of the middle electrode; Figure 6 For attachment Figure 4 Schematic diagram of the structure of part B of the middle electrode.

[0024] Reference numerals: 1. Vascular stop, 2. Endothelial blade, 3. Handle, 4. Cable plug, 6. Rotational power system; 1-1, hemostasis part, 1-2, opening, 1-3, front electrode tube, 1-4, interelectrode insulating tube, 1-5, rear electrode tube, 1-6, outer insulating tube, 1-7, outflow channel, 1-8, liquid inlet assembly, 1-9, liquid inlet port, 1-10, injection tube; 2-1, inner blade tube, 2-2, spiral part, 2-3, suction tube; 3-1, manual control button, 3-2, valve, 3-3, proximal fixing seat, 3-4, distal fixing seat, 3-5, insulating support; 2-2-1, spiral body, 2-2-2, spiral blade tip, 2-2-3, spiral groove, 2-2-4, cutting edge; 6-1, motor, 6-2, motor seat, 6-3, rear bearing, 6-4, front bearing, 6-5, transmission gear set. DETAILED DESCRIPTION

[0025] To make the objectives, technical solutions, and advantages of the embodiments of the present invention more clear, the technical solutions of the embodiments of the present invention will be clearly and completely described below in conjunction with the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Generally, the components of the embodiments of the present invention described and shown in the drawings herein can be arranged and designed in various different configurations.

[0026] Therefore, the following detailed description of the embodiments of the present invention provided in the accompanying drawings is not intended to limit the scope of the invention as claimed, but rather merely represents selected embodiments of the present invention. All other embodiments derived by persons of ordinary skill in the art based on the embodiments of the present invention without creative effort shall fall within the scope of protection of the present invention.

[0027] It should be noted that similar reference numerals and letters denote similar items in the following drawings, and therefore, once an item is defined in one drawing, it does not need to be further defined or explained in subsequent drawings.

[0028] Fluid: The present invention mainly refers to physiological saline and the like.

[0029] Proximal: refers to the end closest to the operator.

[0030] Distal: refers to the end closest to the target tissue.

[0031] Example 1, with reference to Figure 1-6 As shown, the present invention provides a hemostatic rotary cutting electrode assembly, including a vascular stopper 1, wherein the vascular stopper 1 is provided with a hemostatic portion 1-1 at the distal end; a rotary cutting inner blade 2 is inserted into the vascular stopper 1, and the rotary cutting inner blade 2 includes an inner blade tube 2-1 and a spiral portion 2-2 provided at the distal end of the inner blade tube 2-1; the spiral portion 2-2 includes a spiral body 2-2-1 and a spiral blade tip 2-2-2 located at the distal end of the spiral body 2-2-1; the spiral body 2-2-1 is provided with a spiral groove 2-2-3 with a cutting edge 2-2-4; the spiral groove 2-2- 3 is connected to the inner blade tube 2-1; the proximal end of the inner blade tube 2-1 is connected to the suction tube 2-3 for providing 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 force and circumferential force to the distal end to crush the tissue encountered on the path, and the spiral part 2-2 cooperates with the hemostatic part 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.

[0032] The present invention is suitable for a variety of surgical environments, particularly for minimally invasive soft tissue resection surgeries, such as thyroid nodule and thyroid cyst removal, spinal decompression and nucleus pulposus extraction, and uterine fibroid surgery. The dimensions of this embodiment are designed primarily for minimally invasive thyroid nodule removal surgery; other surgical environments can be adjusted accordingly.

[0033] The specific implementation is as follows: According to the above description, it can be concluded that the outer shape of the spiral portion 2-2 can be regarded as a spiral structure extending toward the distal end.

[0034] The length of the spiral blade tip 2-2-2 exposed from the hemostatic part 1-1 is 0.2-2 mm, preferably 0.2 mm, 0.25 mm, 0.28 mm, 0.3 mm, 0.33 mm, 0.35 mm, 0.4 mm, etc.

[0035] The length of the spiral portion 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 portion 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 portion 2-2 is the same as the outer diameter of the inner blade tube 2-1.

[0036] Reference Attachment Figure 1-5 As shown, the spiral body 2-2-1 and the inner blade tube 2-1 are located inside the vascular stopper 1 and fit closely with the vascular stopper 1. Since there is no gap between the two, this structural design brings multiple benefits in the present invention, such as: (1) The position of the spiral part is limited, which provides support to a certain extent and can help it accurately break the tissue at the target site; (2) Make the inner blade of the rotary cutting machine also electrified, so that the puncture and perforation will be easier; (3) Prevent the broken tissue from entering the gap between the rotary cutting blade and the vascular stopper, and contaminating the inside of the vascular stopper.

[0037] The distal end of the helical blade 2-2-2 is provided with an opening 1-2, which is an end opening. This description is a more explicit explanation of the above solution. It is not recommended to use a side opening or a combined end and side opening like a common planer to avoid failure to achieve 360° hemostasis.

[0038] There are many other possible configurations for the vascular stop 1. The preferred configuration is: Reference Attachment Figure 1 、 5As shown, the vascular stopper 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 in sequence from the inside to the outside; the distal end of the front electrode tube 1-3 is exposed from the inter-electrode insulating tube 1-4 and serves as electrode one, and the distal end of the rear electrode tube 1-5 is exposed from the outer insulating tube 1-6 and serves as electrode two, and the electrical polarities of electrode one and electrode two are opposite.

[0039] The exposed surface area of ​​the electrode 1 is smaller than the exposed surface area of ​​the electrode 2. At this time, if the plasma host is connected, it is beneficial for the electrode 1 to excite plasma in a saline environment. Plasma medical devices are widely used in the field of minimally invasive surgery, mainly through low-temperature plasma technology to achieve precise tissue cutting, coagulation and hemostasis and ablation treatment, reducing thermal damage to surrounding tissues (the working temperature is usually 40-70°C). Its core functions include: (1) Precision tissue cutting: using plasma to break the molecular bonds of the target tissue to achieve millimeter-level precision cutting, especially suitable for delicate operations such as meniscus repair and cartilage trimming. (2) Efficient hemostasis and coagulation: using bipolar plasma hemostasis technology to coagulate blood vessels with a diameter of less than 2 mm, significantly reducing surgical bleeding, and suitable for various scenarios in multiple departments such as otolaryngology and orthopedics. (3) Minimally invasive ablation treatment: vaporizing and ablating diseased tissue (such as intervertebral disc herniation, tumor or nucleus pulposus) to preserve healthy structures, such as tumor ablation, turbinate hypertrophy correction, etc. Of course, the above-mentioned exposed area setting relationship of electrode 1 and electrode 2 can also be replaced by using bipolar radiofrequency hemostasis technology to heat the tissue through high-frequency current. The thermal effect of the current causes protein coagulation and blood vessel closure, thereby achieving a hemostatic effect.

[0040] Reference Attachment 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. This outflow channel 1-7 extends distally, allowing fluid to flow sequentially through electrode 2 and electrode 1. This is because both bipolar plasma hemostasis and bipolar radiofrequency hemostasis technologies operate optimally in relatively low-temperature environments (e.g., 40-70°C, though the differences between the two are not considered here). This structural design fully utilizes the fluid to cool electrodes 1 and 2, preventing excessive energy accumulation between the two electrodes, which could cause overheating and tissue burns, and also prevents overheating of the electrode assembly and tissue adhesion.

[0041] The end surface of the front electrode tube 1-3 is provided with an opening 1-2 for exposing the spiral blade tip 2-2-2, which is a further explanation of the above-mentioned solution adopted by the vascular stop member 1.

[0042] Reference Attachment Figure 4-6As shown, the present invention provides a hemostatic 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 hemostatic blood vessel component 1 through a wire; and also includes a rotational power system 6, which is connected to the inner knife tube 2-1.

[0043] The electrodes are further described as follows: The proximal end of the suction tube 2 - 3 can be connected to a negative pressure device (not shown in the drawings). A valve 3 - 2 for controlling the flow rate can be further provided on the suction channel, and the valve 3 - 2 can be preferably provided on the handle 3 .

[0044] The proximal end of the outflow channel 1-7 is provided with a liquid inlet 1-9 at the rear electrode tube 1-5 (regardless of whether it is covered with an outer insulating tube 1-6), and the liquid inlet 1-9 is connected to the liquid inlet component 1-8.

[0045] The handle 3 is provided with a manual control button 3-1, which is connected between the wires. The manual control button 3-1 and the valve 3-2 are typically positioned so as to not interfere with the operator's grip, such as above the handle 3. The handle 3 is typically designed with two symmetrical left and right halves. Therefore, the manual control button 3-1 and the valve 3-2 can be installed at their respective locations at the junction of the left and right halves.

[0046] The proximal end of the electrode assembly located inside the handle 3 can be fixed in the following manner, such as by providing a proximal fixing seat 3 - 3 , a distal fixing seat 3 - 4 and an insulating support 3 - 5 in the handle 3 . Specifically, the rear end of the front electrode tube 1-3 is fixed to the inner hole of the proximal fixing base 3-3, and the rear electrode tube 1-5 is fixed to the inner hole of the distal fixing base 3-4. The proximal fixing base 3-3 is fixed to the rear end of the insulating support 3-5, and the distal fixing base 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 circumference of the front electrode tube 1-3, and the rear electrode tube 1-5 is sleeved outside the inter-electrode insulating tube 1-4. The annular gap between the inner hole of the rear electrode tube 1-5 and the outer circumference 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 connected to 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 circumference of the inter-electrode insulating tube 1-4. The outer insulating tube 24 is heat-shrinkably fixed to the outer circumference of the rear electrode tube 1-5 and provides insulation protection.

[0047] It is worth mentioning that the handle 3 still needs to be equipped with a mounting position for the rotary power system 6 to provide rotational power to the inner blade tube 2-1. Usually, the rotation speed of the rotary power system 6 is 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 the inner blade tube 2-1 and other components can be implemented by referring to the following scheme: Reference Attachment Figure 4-6 As shown, the rotational power system 6 includes a motor 6-1 fixed to a motor base 6-2, and a valve 3-2 fixed to the motor base 6-2. A rear bearing 6-3 and a front bearing 6-4 are mounted at the rear end of the inner blade tube 2-1, which is mounted to the motor base 6-2 via the rear bearings 6-3 and 6-4. A cable plug 4 provides power to the motor 6-1, the front electrode tube 1-3, and the rear electrode tube 1-6. The input gear of the transmission gear set 6-5 is fixed to the output shaft of the motor 6-1, and the output gear of the transmission gear set 6-5 is fixed to the rear end of the inner blade tube 2-1. The motor 6-1 transfers kinetic energy to the inner blade tube 2-1 via the transmission gear set, driving the inner blade tube 2-1 to rotate. The manual control button 3-1 transmits a signal to the main unit by pressing the switch, thereby controlling the hemostatic energy output of the front electrode tube 1-3 and the rear electrode tube 1-5. A conventional foot switch (not shown) can also be used to control the hemostatic energy output, or both methods can be used. Valve 3-2 is used to control the opening and closing of the suction channel established by inner blade tube 2-1 and suction tube 2-3. Other technical details related to the rotary power system 6, such as the description of the sealing ring, can be referred to the existing design of the surgical power system. The description of the technical details related to electrode 1 and electrode 2 is sufficient for those skilled in the art to understand how to implement them, and therefore, they are not repeated in this embodiment.

[0048] The present invention also provides a tissue fragmentation and transportation method, comprising the following steps: Step 1: The rotation of the rotary cutting blade 2 generates axial force and circumferential force, which directly acts on the target tissue to break it up and move the debris in the human body to the proximal end; Step 2: During the movement of the debris tissue toward the proximal end, the vascular stop 1 attached to the outer periphery of the rotary cutting inner blade 2 assists in limiting the movement direction; Step 3: During the movement of the debris tissue toward the proximal end, the debris tissue is sucked out of the human body by the suction tube 2 - 3 connected to the proximal end of the rotary cutting blade 2 .

[0049] The foregoing description is merely a preferred embodiment of the present invention and is not intended to limit the present invention. Those skilled in the art will readily appreciate that various modifications and variations of the present invention are possible. Any modifications, equivalent substitutions, or improvements made within the spirit and principles of the present invention are intended to be within the scope of protection of the present invention.

Claims

1. A hemostatic rotary cutting electrode assembly, characterized in that: The invention comprises a hemostatic component (1), wherein the hemostatic component (1) is provided with a hemostatic portion (1-1) located at the distal end; a rotary cutting inner knife (2) is provided in the hemostatic component (1), wherein the rotary cutting inner knife (2) comprises an inner knife tube (2-1) and a spiral portion (2-2) arranged at the distal end of the inner knife tube (2-1); the spiral portion (2-2) comprises a spiral body (2-2-1) and a spiral blade tip (2-2-2) located at the distal end of the spiral body (2-2-1); the spiral body (2-2-1) is provided with a spiral groove (2-2-3) with a blade edge (2-2-4); The spiral groove (2-2-3) is connected to the inner knife tube (2-1); the proximal end of the inner knife tube (2-1) is connected to a suction tube (2-3) for providing negative pressure; the spiral blade tip (2-2-2) is exposed outside the hemostasis part (1-1); in a working state, the rotation of the spiral blade tip (2-2-2) applies axial force and circumferential force to the distal end to crush tissue encountered on the path, and the spiral part (2-2) cooperates with the hemostasis part (1) to guide the crushed tissue from its distal end into the inner knife tube (2-1), and extracts the crushed tissue through the suction tube (2-3).

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

3. The hemostatic rotary cutting electrode assembly according to claim 1, characterized in that: The outer diameter of the spiral portion (2-2) is the same as the outer diameter of the inner blade tube (2-1).

4. The hemostatic rotary cutting electrode assembly according to claim 1, characterized in that: The spiral body (2-2-1) and the inner knife tube (2-1) are located inside the blood vessel stopping component (1) and are fitted with the blood vessel stopping component (1).

5. The hemostatic rotary cutting electrode assembly according to claim 1, characterized in that: The distal end of the vascular stop member (1) is provided with an opening (1-2) for exposing the spiral blade tip (2-2-2), and the opening (1-2) is an end face opening.

6. The hemostatic rotary cutting electrode assembly according to claim 1, characterized in that: The blood vessel stopper (1) comprises 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) which are arranged in sequence from the inside to the outside; the distal end of the front electrode tube (1-3) exposes the inter-electrode insulating tube (1-4) and serves as electrode one, and the distal end of the rear electrode tube (1-5) exposes the outer insulating tube (1-6) and serves as electrode two, and the electrical polarities of electrode one and electrode two are opposite.

7. The hemostatic rotary cutting electrode assembly according to claim 6, characterized in that: The exposed surface area of ​​the first electrode is smaller than the exposed surface area of ​​the second electrode.

8. The hemostatic 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 toward the distal end so that fluid flows through electrode two and electrode one in sequence.

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

10. A hemostatic 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 to 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 blood stopper (1) through a wire; and it also includes a rotary power system (6), which is connected to the inner knife tube (2-1).

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