Thermal energy blade and tissue ablation, cutting and fusion system

Abstract

A thermal energy blade head of the present invention comprises a first working part and a second working part that match each other, each of which is provided with at least one working surface, wherein at least one working surface is provided with a heating device; and a tissue pushing mechanism is connected to the proximal end of the first working part or the second working part, and the tissue pushing mechanism can push the tissue toward the upper end of the working surface. The tissue ablation, cutting and fusion system of the present invention comprises a handle assembly, an axis assembly, a working part, a circuit system and a power supply. The working part comprises a thermal energy blade head. During clinical use, during the closing process of the working surface, the tissue pushing mechanism can push the tissue toward the upper part of the working surface of the first working part and / or the second working part, preventing the tissue from gathering at the bottom of the first working part and / or the second working part, avoiding the operation dead angle of the tissue ablation, cutting or fusion process, and during clinical use, the tissue ablation, cutting or fusion process is more efficient.

Description

Technical Field

[0001] The present invention relates to an electrosurgical instrument, in particular to a surgical instrument used for tissue ablation, cutting and fusion in surgical operations. Background Art

[0002] In surgical operations, tissue ablation, cutting and fusion are very important tissue processing processes. Among the commonly used tissue ablation, cutting and fusion technologies, the electric heating tissue ablation method is one of the important technologies. By heating the tissue, the protein is agglutinated and modified, thereby achieving the ablation, cutting and fusion process of the tissue. Therefore, in the electric heating tissue ablation method, the core lies in how to ensure the rapid agglutination of protein and quickly increase its temperature. In human tissues, in addition to protein, there are also a large number of liquid substances, such as blood, tissue fluid, etc. The presence of these liquid substances has obvious interference with protein agglutination and temperature rise.

[0003] In view of the problem that in the prior art, conventional surgical instruments, such as surgical forceps, surgical nickel and other instruments, are equipped with heating devices at the ends, and the original working surfaces are usually in flat contact, and large pressure needs to be applied during the heating process to close the forceps head to ensure that the proteins in the working area are agglutinated and modified, which makes the operation process inconvenient, the applicant proposed a technical solution in the patent application "A Thermal Energy Blade and Tissue Ablation, Cutting and Fusion System" (Application Number: 201910263660.1) to improve the working part of the existing tissue ablation, cutting and fusion system.

[0004] However, in actual applications, tissue will gather at the bottom of the working part during the closing process of the working part, making it impossible to smoothly perform tissue ablation, cutting and fusion processing. Therefore, it is necessary to improve the tissue ablation, cutting and fusion system in the prior art, especially to further improve its working part. Summary of the invention

[0005] The tissue ablation, cutting and fusion system of the present invention has a specially designed tissue pushing mechanism. During the process of tissue ablation, cutting and fusion, when the working part is closed, the tissue pushing mechanism can push the tissue toward the working surface of the working part to prevent the tissue from gathering at the bottom of the working part. There is no blind spot in the operation during clinical use, and clinical use is safer and more effective.

[0006] A thermal energy cutter head of the present invention is characterized by:

[0007] A. The thermal energy cutter head 3 comprises a pair of first working parts 301 and second working parts 302 that match each other;

[0008] B. The first working part 301 and the second working part 302 are each provided with at least one working surface 31, and at least one of the working surfaces 31 is provided with a heating device 32;

[0009] C. The proximal end of the first working part 301 and / or the second working part 302 is connected with a tissue pushing mechanism 33 , and the tissue pushing mechanism 33 can push the tissue at the bottom of the thermal energy blade 3 toward the working surface 31 .

[0010] The thermal energy blade 3 is provided with the tissue pushing mechanism 33. When the working part is closed, the tissue pushing mechanism 33 can push the tissue to the upper part of the working surface 31 of the first working part 301 and / or the second working part 302 to prevent the tissue from gathering at the bottom of the first working part 301 and / or the second working part 302, thereby causing an operational blind spot in the process of tissue ablation, cutting or fusion. During clinical use, the process of tissue ablation, cutting or fusion is more efficient.

[0011] The tissue pushing mechanism 33 is arranged at the proximal end of the first working part 301 and is connected to the outer rod 21-2 of the shaft assembly 200; the pushing surface 33-1 of the tissue pushing mechanism 33 forms an angle β with the axis of the outer rod 21-2. When the tissue pushing mechanism 33 is arranged at the proximal end of the first working part 31, during the closing process, the pushing surface 33-1 pushes the tissue to move toward the upper end of the working surface 31 of the second working part 302. After closing, the tissue to be ablated, cut or fused completely enters between the working surfaces 31 under the pushing action of the pushing surface 33-1, and can be completely ablated, cut or fused, which has higher clinical use efficiency. The pushing surface 33-1 can be a plane, a convex curved surface, a concave curved surface or other structures, but the pushing surface 33-1 forms a certain angle with the axial direction of the outer rod 21-2.

[0012] The β angle is less than 90°. When the tissue pushing mechanism 33 is arranged on the first working part 301, the β angle is less than 90°. When the tissue pushing mechanism 33 is arranged on the second working part 302, the angle between the pushing surface 33-1 and the axis of the outer rod 21-2 needs to be smaller than the angle between the working surface 31 of the second working part 302 and the axis of the outer rod 21-2, so as to ensure that the comprehensive force direction of the tissue is upward, and the tissue can be pushed to the upper part of the working surface 31, thereby avoiding the tissue from gathering at the bottom of the first working part 301 and the second working part 302.

[0013] The pushing surface 33 - 1 is a blunt smooth surface. The design of the blunt smooth surface can effectively prevent the sharp edges of the pushing surface 33 - 1 from accidentally cutting tissues during the closing process, thereby avoiding accidental tissue damage.

[0014] The pushing surface 33 - 1 forms an angle α with the working surface 31 of the first working part 301 .

[0015] Furthermore, the angle α is smaller than 180°.

[0016] The tissue pushing mechanism 33 is integrally manufactured with the first working part 301. The tissue pushing mechanism 33 can be integrally manufactured with the first working part 301, which makes the assembly process more convenient, and the manufacturing process is simple and the cost is lower. Of course, the tissue pushing mechanism 33 can be manufactured separately and then connected to the first working part 301 or the second working part 302. The applicant does not give specific examples here, but they do not deviate from the protection scope of this application.

[0017] At least one of the working surfaces 31 has a protrusion 30 that can squeeze the liquid in the tissue outward. When the working surface 31 is closed, the protrusion 30 can quickly squeeze the liquid in the tissue out of the working area. At this time, under the action of the heating device 32, the working surface 31 begins to heat up. Since the interference of the liquid in the tissue on the working process is reduced, the protein in the working area is quickly coagulated and modified, and the ablation, cutting and fusion effects of the tissue are better.

[0018] Furthermore, the working surface 31 of the first working part 301 and the working surface 31 of the second working part 302 both have protrusions 30 that can squeeze liquid in the tissue outward.

[0019] The protrusions 30 on the working surface 31 of the first working part 301 and the protrusions 30 on the working surface 31 of the second working part 302 match each other. Such matching protrusions 30 have a better squeezing effect on the liquid when the working surfaces 31 are closed.

[0020] The pair of mutually matching protrusions 30 is an arc-shaped protrusion to an arc-shaped protrusion, or a wedge-shaped protrusion to an arc-shaped protrusion, or a wedge-shaped protrusion to a wedge-shaped protrusion, or an arc-shaped protrusion to a plane, or a wedge-shaped protrusion to a plane, or a convex protrusion to a convex protrusion, or a convex protrusion to a plane. The applicant only lists the above-mentioned several mutually matching protrusion shapes, and those skilled in the art can design different shapes according to needs, which do not deviate from the protection scope of this application.

[0021] The heating device 32 may be at least one of a pair of protrusions 30 that match each other.

[0022] The heating device 32 may be an electric heating device 32-1 or an ultrasonic vibration heating device 32-2. Different heating methods may be selected as needed, such as electric heating or ultrasonic heating, or other heating methods. The applicant only lists the above two heating devices here, and those skilled in the art may design different heating devices as needed, which do not deviate from the protection scope of this application.

[0023] The electric heating device 32-1 is heated by a direct current pulse method. The direct current pulse voltage heating method realizes the periodic power-on and power-off of the electric heating device 32-1 through the periodic alternation of high level and low level, and keeps the electric heating device 32-1 powered on for heating and powered off for moderate cooling. In this way, while the heat is continuously conducted to the deep of the tissue or organ 9, the temperature of the part where the electric heating device 32-1 contacts the tissue or organ 9 is kept within a stable range and will not continue to rise, effectively avoiding accidental damage to the tissue or organ 9 caused by excessive temperature, and making the clinical use process safer and more reliable.

[0024] The proximal end of the first working part 301 is connected to the tissue pushing mechanism 33, and the tissue pushing mechanism 33 is connected to the outer rod 21-2 of the shaft assembly 200. The first working part 301 is provided with the protrusion 30 made of insulating and heat-insulating material, and the protrusion 30 is embedded in the first working part 301 to form a first protrusion 30-1; the proximal end of the second working part 302 is connected to the inner rod 21-1 of the shaft assembly 200, and a conductive core rod 41-1 as a positive electrode is provided in the inner rod 21-1. An inner insulating heat-resistant sleeve 21-3 is provided between the conductive core rod 41-1 and the inner rod 21-1; the heating device 32 adopts an electric heating body 32-10, one end of which is connected to the distal end of the conductive core rod 41-1, extends from the distal end of the second working part 302 and then wraps around the inner insulating heat-resistant sleeve 21-3, and the other end of the electric heating body 32-10 is connected to the distal end of the inner rod 21-1, and the inner rod 21-1 is connected to the power supply 500 as a negative electrode to form an electrical circuit; the protruding electric heating body 32-10 installed on the working surface 31 of the inner insulating heat-resistant sleeve 21-3 of the second working part 302 The arc surface protruding from the inner insulating heat-resistant sleeve 21-3 constitutes the second protrusion 30-2 on the second working part 302, and the first protrusion 30-1 and the second protrusion 30-2 form a pair of protrusions 30 that match each other; a middle insulating heat-resistant sleeve 21-4 is provided between the middle tube 21-5 and the inner rod 21-1; the outer rod 21-2 is movably mounted on the inner rod 21-1, and the extension or retreat of the inner rod 21-1 can control the opening or closing between the second working part 302 and the first working part 301. In this translational design, the closing of the working surface 31 is achieved by translating one working surface 31 to another working surface 31. During operation, the pushing surface 33-1 of the tissue pushing mechanism 33 can push the tissue to the upper part of the working surface 31, and the tissue will not gather at the lower end of the working surface 31. The two working surfaces 31 can be fully fitted at the same time, and the working efficiency is very high.

[0025] In order to ensure the strength of the second working part 302, a support frame 34 may be provided on the outer side of the second working part 302, and the proximal end of the support frame 34 may be connected to the distal end of the inner rod 21-1.

[0026] In addition to the above-mentioned electric heating method, the heating device 32 can also be an ultrasonic vibration heating device 32-2 that uses an ultrasonic transducer for ultrasonic heating.

[0027] The outer rod 21-2 may also be provided with an insulating heat shrinkable sleeve 21-6 that can reduce the friction coefficient. The insulating heat shrinkable sleeve 21-6 can not only provide better insulation protection, but also reduce the friction coefficient of the outer rod 21-2, resulting in less movement resistance when entering and exiting the device, and smoother movement during operation.

[0028] The tissue ablation, cutting and fusion system of the present invention comprises the thermal energy blade 3 .

[0029] The tissue ablation, cutting and fusion system of the present invention is characterized by:

[0030] A. The tissue ablation, cutting and fusion system 900 comprises a handle assembly 100, an axis assembly 200, a working part 300, a circuit system 400 and a power supply 500;

[0031] B. The handle assembly 100 includes a trigger assembly 11, a gear adjustment button 12, an axis connection mechanism 13 and a housing 14; The trigger assembly 11, the gear adjustment button 12 and the axis connection mechanism 13 are arranged on the housing 14;

[0032] C. The shaft assembly 200 includes a shaft rod 21 and a connecting assembly 22;

[0033] D. The working part 300 includes the thermal energy cutter head 3, and at least one working surface 31 of the thermal energy cutter head 3 is provided with a heating device 32;

[0034] E. The circuit system 400 includes a circuit 41, a controller 42 and an electrical interface device 43; the circuit system 400 is connected to the power supply 500 via the electrical interface device 43;

[0035] F. The proximal end of the shaft assembly 200 is connected to the handle assembly 100 via the shaft connection mechanism 13 ; the distal end of the shaft assembly 200 is connected to the working part 300 ; the electric heating device 32 - 1 is connected to the power source 500 via the circuit system 400 .

[0036] Since the tissue ablation, cutting and fusion system of the present invention is provided with a tissue pushing mechanism 33 on the thermal energy blade 3, the tissue or organ 9 will not accumulate under the working surface 31 of the thermal energy blade 3, and there will be no operating dead angle. The cutting, ablation or fusion process of the tissue or organ 9 is very efficient.

[0037] The controller 42 includes a trigger switch 42-1; the movement of the trigger assembly 11 can turn on or off the trigger switch 42-1. Only by pulling the trigger assembly 11 to apply working pressure to the working part 300 can the trigger switch 42-1 be turned on to heat the electric heating device 32-1, thereby avoiding accidental injuries or safety hazards that may be caused by misoperation, and making the clinical use process safer and more reliable.

[0038] Furthermore, the handle assembly 100 also includes a fixing mechanism 15; the trigger assembly 11 is fixedly mounted on the housing 14 through the fixing mechanism 15. During assembly, the trigger assembly 11 can be embedded or fixed in the mounting groove of the fixing mechanism 5, assembled into a whole and then fixed on the housing 14, so that the assembly process is simpler and the fixing is more reliable.

[0039] The trigger assembly 11 comprises a trigger 11-1, a rocker arm 11-2 and a slider 11-3; the trigger 11-1 is provided with a trigger shaft 11-1-1 and a rocker arm drive shaft 11-1-2; the rocker arm 11-2 comprises a rocker arm fulcrum 11-2-1, a motion slide groove 11-2-2 and a push block slot 11-2-3; the slider 11-3 comprises a motion push block 11-3-1, a sliding convex step 11-3-2 and a working boss 11-3-3; The trigger shaft 11-1-1 and the fixing mechanism 15 are connected together and fixed on the housing 14; one end of the rocker arm drive shaft 11-1-2 is connected to the trigger 11-1, and the other end is embedded in the motion slot 11-2-2; the rocker arm fulcrum 11-2-1 and the fixing mechanism 15 are connected together, and the rocker arm 11-2 is movably installed in the housing 14; the motion push block 11-3-1 is embedded in the push block slot 11-2-3, and the sliding convex step 11-3-2 is embedded in the positioning slot 15-1 of the fixing mechanism 15, and is connected to the fixing mechanism 15; pull the trigger 11-1, The trigger 11-1 rotates around the trigger shaft 11-1-1, driving the rocker drive shaft 11-1-2 to reciprocate along the motion slot 11-2-2, thereby pushing the rocker 11-2 to swing back and forth around the rocker fulcrum 11-2-1; the reciprocating swing of the rocker 11-2 pushes the motion push block 11-3-1 embedded in the push block slot 11-2-3, thereby driving the slider to move back and forth in a straight line along the positioning slot 15-1, thereby realizing the closing and opening of the working surface 31 of the working part 300.

[0040] A trigger part 11-1-3 is provided on the trigger 11-1; when the trigger 11-1 moves toward the handle 14-1 of the shell 14, the trigger part 11-1-3 touches the trigger switch 42-1, and the trigger switch 42-1 is turned on; when the trigger 11-1 moves away from the handle 14-1 of the shell 14, the trigger part 11-1-3 disengages from the trigger switch 42-1, and the trigger switch 42-1 is turned off.

[0041] The gear adjustment button 12 is connected to the controller 42 via the line 41. The doctor can select different output powers through the gear adjustment button 12 according to the specific conditions of the surgical process, which makes clinical operation more convenient.

[0042] The gear adjustment button 12 includes a cutting gear 12-1 and a fusion gear 12-2; the cutting gear 12-1 and the fusion gear 12-2 are linked together by a lever mechanism 12-3, so that the cutting gear 12-1 and the fusion gear 12-2 cannot be pressed at the same time. The cutting gear 12-1 and the fusion gear 12-2 cannot be pressed at the same time, which can ensure that there will be no misoperation during clinical use.

[0043] The handle assembly 100 also includes a reset mechanism 16. When the trigger 11-1 is released, the reset mechanism 16 can automatically reset the trigger 11-1 through the reset force, greatly improving the safety, convenience and comfort of the use process. The reset mechanism 16 can be a torsion spring mechanism, a spring mechanism, an elastomer mechanism and other forms. Those skilled in the art can design various reset mechanisms as needed, and install one or more reset mechanisms 16 at different parts of the instrument as needed, which does not deviate from the protection scope of this application.

[0044] The handle assembly 100 also includes a force-limiting mechanism 17. The force-limiting mechanism 17 can limit the working pressure transmitted to the working part 300 through the trigger assembly 11. When the force-limiting mechanism 17 takes effect, the maximum working pressure applied to the working part 300 after the operator pulls the trigger 11-1 is constant. Usually, during the ablation, cutting and fusion of soft tissues, the maximum working pressure can be limited to less than 100N. Of course, those skilled in the art can set the limit value of the maximum working pressure limited by the force-limiting mechanism 17 as needed, which does not deviate from the protection scope of this application. The force-limiting mechanism 17 can be a spring force-limiting mechanism, an elastomeric force-limiting mechanism, a compression spring force-limiting mechanism and other forms of structures. Those skilled in the art can also design other various forms of force-limiting mechanisms, which do not deviate from the protection scope of this application.

[0045] The trigger switch 42-1 can be activated only when the trigger 11-1 moves toward the handle 14-1 of the shell 14 until the force limiting mechanism 17 takes effect. When the trigger switch 42-1 is in the on state, the gear adjustment button 12 can be closed to connect the circuit system 400, so that the tissue ablation, cutting and fusion system 900 can perform tissue ablation, cutting or fusion under the set working pressure. Because the trigger switch 42-1 can be activated only when the force limiting mechanism 17 takes effect, it is ensured that the working pressure applied to the tissue by the doctor during the operation is constant, so that the tissue ablation, cutting and fusion system of the present invention can only perform tissue ablation, cutting or fusion under the set working pressure, the surgical effect is more stable, and it effectively prevents accidental injuries that may be caused by misoperation, as well as clinical effects such as vascular closure, tissue fusion, cutting, etc. caused by different clamping forces used by different surgeons. It is safer and more effective. That is, a tissue ablation, cutting and fusion system of the present invention can only be activated for tissue ablation, cutting and fusion under a constant clamping force, avoiding differences in use effects caused by different forces used by operators.

[0046] The shaft assembly 200 further includes a knob 23 ; the knob 23 can drive the shaft 21 to rotate.

[0047] The shaft 21 includes an inner rod 21-1 and an outer rod 21-2; the proximal end of the first working part 301 is connected to the outer rod 21-2, and the proximal end of the second working part 302 is connected to the inner rod 21-1. Turning the knob 23 can drive the inner rod 21-1 and the outer rod 21-2 to rotate, thereby driving the working surfaces 31 of the first working part 301 and the second working part 302 to rotate.

[0048] During clinical use, the working surface 31 often needs to be rotated to a suitable position according to the different parts of the tissue to be treated. The knob 23 can drive the shaft 21 to move, thereby driving the working surface 31 to rotate to a suitable direction and position.

[0049] The electrical interface device 43 is an elastic electrical interface device 431, which includes a conductive connector 43-1, an elastic conductive mechanism 43-2 and an electrical interface 43-3; one end of the conductive connector 43-1 is connected to the electric heating device 32-1 through the line 41, and the other end is connected to the elastic conductive mechanism 43-2; the other end of the elastic conductive mechanism 43-2 is connected to the electrical interface 43-3, and the electrical interface 43-3 is connected to the power supply 500.

[0050] The conductive joint 43-1 includes a rotor 43-1-1 and a stator 43-1-2; the rotor 43-1-1 can rotate; the distal end of the rotor 43-1-1 is connected to the proximal end of the shaft 21, and when the shaft 21 rotates, the rotor 43-1-1 can rotate synchronously; the proximal end of the stator 43-1-2 is connected to the distal end of the elastic conductive mechanism 43-2.

[0051] Since the rotor 43-1-1 can rotate synchronously with the shaft 21, the line 41 connecting the rotor 43-1-1 and the shaft 21 also rotates synchronously, and the line 41 connecting the conductive connector 43-1 and the rear end of the shaft 21 remain synchronized, thereby avoiding wire breakage or loosening of solder joints caused by twisting of the line 41.

[0052] The elastic conductive mechanism 43-2 is a conductive mechanism that can be elastically deformed under the action of external force while keeping the circuit unobstructed. The elastic conductive mechanism 43-2 can be elastically deformed under the action of external force. Therefore, when the shaft 21 translates toward the proximal end, the shaft 21 applies pressure to the elastic conductive mechanism 43-2, and the elastic conductive mechanism 43-2 is compressed and deformed. When the shaft translates toward the distal end, the pressure applied by the shaft 21 to the elastic conductive mechanism 43-2 is gradually released. Under the action of the elastic restoring force, the connection state between the conductive connector 43-1 and the shaft 21 can be continuously maintained, and the stable power supply of the circuit system 400 can be maintained. In this motion cycle, the elastic conductive mechanism 43-2 is elastically deformed and reciprocates, which overcomes the fatigue fracture or loose solder joint caused by the continuous expansion and contraction of the wires when the current wires are connected. Not only does it maintain good controllability of the instrument, but it also improves the reliability of the circuit.

[0053] The tissue ablation, cutting and fusion system 900 also includes a temperature control component 401; the temperature control component 401 includes a temperature acquisition system 40-1 and a data transmission system 40-2; the temperature data acquired by the temperature acquisition system 40-1 can be transmitted to the controller 42 through the data transmission system 40-2. The temperature acquisition system 40-1 can continuously acquire working temperature data, and transmit the acquired temperature data to the controller 42 through the data transmission system 40-2. The data processing system 42-2 in the controller 42 can monitor the acquired temperature in real time. When the acquired temperature value exceeds the limit temperature value set by the controller 42, the controller 42 cuts off the power supply to the line 41, or adjusts the current or voltage output by the power supply 500 through the data processing system 42-2, etc., so as to achieve the control effect of reducing the working temperature of the working part 300, effectively avoiding accidental tissue damage or accidental damage to components caused by the electric heating device 32-1 being in a high temperature state for a long time, and being safer during long-term continuous operation.

[0054] The power supply 500 is a low-voltage power supply with an output voltage less than 24 V. The output voltage of the power supply 500 is a safe voltage less than 24 V, and even if an unexpected phenomenon such as leakage occurs during use, it will not cause accidental harm to the human body.

[0055] Preferably, the output voltage of the power supply 500 is less than 12V.

[0056] The power supply 500 outputs a DC pulse voltage. The DC pulse voltage output by the power supply 500 realizes the periodic power-on and power-off of the electric heating device 32-1 through the periodic alternation of high level and low level, and keeps the electric heating device 32-1 in the periodic change of power-on heating and power-off to moderate cooling, so that in the process of heat being continuously conducted to the deep of the tissue or organ 9, the temperature of the part where the heating device contacts the tissue or organ 9 is kept within a stable range and will not continue to rise, effectively avoiding accidental damage to the tissue or organ 9 caused by excessive temperature, and the clinical use process is safer and more reliable.

[0057] The frequency of the DC pulse voltage output by the power supply 500 is less than 500 Hz. According to the thermal conductivity of tissues and organs, the power supply 500 is usually a low-frequency DC pulse voltage with a frequency less than 500 Hz. On the one hand, the low-frequency pulse can increase the range of the duration of the high level and the low level, ensuring that the heat conduction time is sufficient while also giving the heating device 32 enough cooling time to ensure that the temperature of the heating device 32 can be controlled within a safe temperature range. At the same time, the low-frequency pulse can better avoid the electromagnetic interference that the electromagnetic pulse may cause to the surrounding equipment during the operation of the instrument, and the electromagnetic compatibility of the instrument is better.

[0058] Preferably, the frequency range of the DC pulse voltage output by the power supply 500 is 3 Hz to 200 Hz.

[0059] The duty cycle of the DC pulse voltage output by the power supply 500 can be adjusted according to the different thermal conductivity of the tissue or organ 9 to be ablated, cut, or fused.

[0060] According to the different thermal conductivity of the tissue to be ablated, cut, or fused, the power output of the heating device 32 is also different, so the duty cycle of the DC pulse power output by the power supply 500 is also different, that is, the heating time and power-off time of the heating device 32 need to be adjusted according to the different operation objects. The duty cycle of the DC pulse power output by the power supply of the tissue ablation, cutting and fusion system of the present invention can be adjusted to meet the thermal conductivity requirements of different tissues or organs 9.

[0061] Typically, the output current of the power supply 500 is less than 10A.

[0062] The power source 500 is a battery module 51, or a battery pack module 52, or a host 53. The battery module 51 or the battery pack module 52 is small in size and light in weight, suitable for carrying outside, has low requirements for the power environment, and low-voltage power supply is safer, while the host 53 can provide stable power supply for a long time, especially suitable for large-scale operations with long operation time; users can choose different power sources 500 according to different use environments and use requirements.

[0063] The tissue ablation, cutting and fusion system 900 also includes a prompt system 600. The prompt system 600 can prompt the operator of the use status of the instrument as needed, such as using different sounds to prompt different working states, using different lights to prompt the power status, and using different patterns to prompt different working parts.

[0064] The prompt system 600 is a sound prompt device 61, or a light prompt device 62, or an image prompt device 63. The applicant only lists the above three prompt devices, and those skilled in the art can design different prompt system structures as needed without departing from the protection scope of this application.

[0065] The tissue ablation, cutting and fusion system 900 also includes a smoke exhaust system 700; the smoke exhaust system 700 includes a smoke outlet 71, a smoke exhaust pipe 72 and a smoke inlet 73. The smoke outlet 71 of the smoke exhaust system 700 can be connected to a medical negative pressure source to timely extract the smoke generated during the operation out of the body, thereby ensuring a clear surgical field of view and making the surgical process safer and more reliable.

[0066] The tissue ablation, cutting and fusion system 900 also includes a water supply / drainage system 800; the water supply / drainage system 800 includes a water outlet 81, a drain pipe 82 and a water inlet 83. The drain pipe 82 of the water supply / drainage system 800 can be either a drain pipe or a water supply pipe. During the operation, the doctor can inject physiological saline or other solvents into the surgical site through the water supply / drainage system 800 according to the needs of the operation, and can also use the water supply / drainage system 800 to promptly discharge blood or sewage from the surgical site to ensure the smooth progress of the operation.

[0067] During clinical use, the power source 500 is connected to the circuit system 400 through the electrical interface 43-3, the power switch is turned on, the trigger 11-1 is pulled to move toward the handle 14-1, and the inner rod 21-1 is driven to move toward the proximal end. Under the action of the tissue pushing mechanism 33, the pushing surface 33-1 pushes the tissue or organ 9 toward the upper end of the working surface 31 until the working surface 31 is closed, the working part 300 clamps the tissue to be processed, and the protrusion 30 on the working surface 31 squeezes out the liquid in the tissue. The trigger 11-1 is continuously pulled until the force limiting mechanism 17 The trigger switch 42-1 is turned on, and the cutting gear 12-1 or the fusion gear 12-2 of the gear adjustment button 12 is pressed according to the surgical situation. The gear adjustment button 12 turns on the controller 42. At this time, the circuit system 400 connects the power supply 500 and the electric heating device 32-1, and the electric heating device 32-1 starts to heat. During this process, the elastic conductive mechanism 43-2 is elastically deformed under the thrust of the inner rod 21 to maintain stable power supply of the circuit system 400. Since the protrusion 30 on the working surface 31 squeezes out the liquid in the tissue, eliminating the interference of the liquid, the protein in the tissue of the working area can be quickly agglutinated and modified under the action of temperature, so as to achieve tissue ablation, cutting and fusion. The tissue pushing mechanism 33 can push the tissue toward the upper part of the working surface 31 of the first working part 301 and / or the second working part 302 to prevent the tissue from gathering at the bottom of the first working part 301 and / or the second working part 302, thereby avoiding operation blind spots in the process of tissue ablation, cutting or fusion. During clinical use, the process of tissue ablation, cutting or fusion is more efficient.

[0068] During operation, since the power supply 500 outputs a DC pulse voltage to the electric heating device 32-1, the electric heating device 32-1 is periodically powered on and off, and the electric heating device 32-1 is powered on for heating, and powered off for moderate cooling, and periodically changes its state. When powered on, the electric heating device 32-1 heats and raises the temperature, and the heat is conducted through the body tissue to the deep part of the tissue or organ 9. After a certain period of high level, the power supply 500 switches to a low level state, and the electric heating device 32-1 is powered off and stops heating. At this time, the heat retained in the electric heating device 32-1 continues to be conducted through the body tissue, and the temperature of the electric heating device 32-1 is moderately reduced. Then the power supply 50 switches to a high level state again, and the electric heating device 32-1 heats and raises the temperature again. This periodic change of heating and moderate cooling can keep the temperature of the part where the electric heating device 32-1 contacts the tissue or organ 9 within a stable range while ensuring that heat is continuously conducted deep into the tissue or organ 9, and will not continue to rise, thereby effectively avoiding accidental damage to the tissue or organ 9 caused by excessive temperature and ensuring the safe and stable ablation, cutting or fusion process of the tissue.

[0069] After the ablation, cutting or fusion process is completed, the trigger 11-1 is released, and the trigger 11-1 is reset under the action of the reset mechanism 16, the trigger switch 42-1 is disconnected, the electric heating device 32-1 stops working and no longer generates heat, the inner rod 21-1 moves toward the distal end, the working surface 32 opens, and a tissue processing process is completed. When the working surface 32 needs to be rotated, it is only necessary to rotate the knob 23, and the knob 23 drives the shaft 21 to rotate, and the working surface 32 connected to the shaft 21 rotates accordingly. During the rotation process, because the rotor 43-1-1 can rotate synchronously with the shaft 21, the connection between the conductive connector 43-1 and the line 41 at the rear end of the shaft 21 is kept synchronous, which can avoid the wire breakage or loosening of the solder joint or heating of the connector caused by the distortion of the line 41. , thereby ensuring the stable power supply of the circuit system 400. Different tissue parts are selected in turn, and the trigger 11-1 is repeatedly pulled and released to complete the surgical operation. The surgical operation is very simple.

[0070] At the same time, during clinical use, since the temperature acquisition system 40-1 can continuously collect working temperature data and transmit the collected temperature data to the controller 42 through the data transmission system 40-2, the data processing system 42-2 in the controller 42 can monitor the collected temperature in real time. When the collected temperature value exceeds the temperature value set by the controller 42, the controller 42 takes measures such as powering off the line 41, or adjusting the current or voltage output by the power supply 500 through the data processing system 42-2, so as to achieve the control effect of lowering the working temperature of the working part 300, effectively avoiding accidental tissue damage or accidental damage to components caused by the electric heating device 32-1 being in a high temperature state for a long time, and being safer during long-term continuous operation.

[0071] When the ultrasonic vibration heating device 32-2 is used to heat tissue, after the power supply 500 is turned on, the ultrasonic vibration rod 32-22 of the ultrasonic vibration heating device 32-2 is started to heat the tissue, thereby performing ablation, cutting or fusion of the tissue.

[0072] A thermal energy blade head of the present invention comprises a first working part 301 and a second working part 302 that match each other, each of which is provided with at least one working surface 31, wherein at least one of the working surfaces 31 is provided with a heating device 32; and a tissue pushing mechanism 33 is connected to the proximal end of the first working part 301 or the second working part 302, and the tissue pushing mechanism 33 can push the tissue toward the upper end of the working surface 31. The tissue ablation, cutting and fusion system of the present invention comprises a handle assembly 100, an axis assembly 200, a working part 300, a circuit system 400 and a power supply 500. The working part 300 comprises the thermal energy blade head 3. During clinical use, when the working surface 31 is closed, the tissue pushing mechanism 33 can push the tissue toward the upper part of the working surface 31 of the first working part 301 and / or the second working part 302, preventing the tissue from gathering at the bottom of the first working part 301 and / or the second working part 302, thereby avoiding operational blind spots in the process of tissue ablation, cutting or fusion. During clinical use, the tissue ablation, cutting or fusion process is more efficient. BRIEF DESCRIPTION OF THE DRAWINGS

[0073] Figure 1 It is a three-dimensional structural schematic diagram of the tissue ablation, cutting and fusion system of the present invention when the working surface is opened.

[0074] Figure 1-1 yes Figure 1 Enlarged view of point A.

[0075] Figure 1-2 yes Figure 1-1 BB cross-sectional view.

[0076] Figure 1-3 yes Figure 1 Left view of the working surface with it closed.

[0077] Figure 1-4 yes Figure 1-3 CC cross-sectional view.

[0078] Figure 1-5 yes Figure 1-4 Enlarged view of point D.

[0079] Figure 1-6 yes Figure 1-4 EE cross-sectional view.

[0080] Figure 1-7 It is a schematic structural diagram of the trigger assembly of the tissue ablation, cutting and fusion system of the present invention.

[0081] Figure 1-8 It is a three-dimensional structural schematic diagram of the first working part with a tissue pushing mechanism.

[0082] Figure 1-9 yes Figure 1-8 FF cross-sectional view.

[0083] Figure 1-1 0 is a schematic diagram of the structure of the tissue ablation, cutting and fusion system of the present invention with a host power supply.

[0084] Figure 1-1 1 is a schematic structural diagram of the working state of the tissue ablation, cutting and fusion system of the present invention.

[0085] Figure 1-1 2 Yes Figure 1-1 Enlarged view of point G in Figure 1.

[0086] Figure 2 It is a schematic structural diagram of a pair of mutually matching protrusions, a wedge-shaped protrusion and a wedge-shaped protrusion.

[0087] Figure 3 It is a structural schematic diagram of a pair of mutually matching protrusions, a wedge-shaped protrusion and an arc-shaped protrusion.

[0088] Figure 4 It is a schematic structural diagram of a pair of mutually matching protrusions, an arc-shaped protrusion and an arc-shaped protrusion.

[0089] Figure 5 It is a structural schematic diagram of a pair of mutually matching protrusions, a convex protrusion and an arc-shaped protrusion.

[0090] Figure 6 It is a schematic diagram of the cutaway structure of the tissue ablation, cutting and fusion system of the present invention with an elastic electrical interface.

[0091] Figure 6-1 yes Figure 6 Enlarged view of point H.

[0092] Figure 7 It is a three-dimensional structural schematic diagram of the tissue ablation, cutting and fusion system of the present invention with a battery and a battery pack.

[0093] Figure 8 It is a schematic structural diagram of an ultrasonic heating type tissue ablation, cutting and fusion system of the present invention with a host power supply.

[0094] Figure 8-1 yes Figure 8 Enlarged view of point I.

[0095] In the above figure:

[0096] 100 is a handle assembly, 200 is an axis assembly, 300 is a working part, 400 is a circuit system, 401 is a temperature control assembly, 500 is a power supply, 600 is a prompt system, 700 is a smoke exhaust system, 800 is a water supply / drainage system, 900 is a tissue ablation, cutting and fusion system of the present invention, 3 is a thermal energy blade of the present invention, and 9 is a tissue or organ.

[0097] α is the angle between the pushing surface and the working surface of the first working part, and β is the angle between the pushing surface and the axis of the outer rod.

[0098] On the handle assembly:

[0099] 11 is a trigger assembly, 12 is a gear adjustment button, 13 is an axis connection mechanism, 14 is a housing, 15 is a fixing mechanism, 16 is a reset mechanism, and 17 is a force limiting mechanism.

[0100] 11-1 is the trigger, 11-2 is the rocker arm, 11-3 is the slider; 11-1-1 is the trigger shaft, 11-1-2 is the rocker arm drive shaft, 11-1-3 is the trigger part, 11-2-1 is the rocker arm fulcrum, 11-2-2 is the motion slide groove, 11-2-3 is the push block slot, 11-3-1 is the motion push block, 11-3-2 is the sliding convex step, and 11-3-3 is the working boss.

[0101] 12-1 is the cutting gear, 12-2 is the fusion gear, and 12-3 is the lever mechanism.

[0102] 14-1 is the handle.

[0103] 15-1 is a positioning slide.

[0104] 17-1 is a spring force limiting mechanism.

[0105] On the shaft assembly:

[0106] 21 is a shaft rod, 22 is a connecting assembly, and 23 is a knob.

[0107] 21-1 is the inner rod, 21-2 is the outer rod, 21-3 is the inner insulating heat-resistant sleeve, and 21-6 is the insulating heat shrinkable sleeve.

[0108] Work Department:

[0109] 30 is a protrusion, 31 is a working surface, 32 is a heating device, 33 is a tissue pushing mechanism, and 34 is a support frame; 3-10 is a rocker, 30-1 is a first protrusion, 30-2 is a second protrusion, 31-1 is an anti-slip pattern, 32-1 is an electric heating device, 32-2 is an ultrasonic vibration heating device, and 33-1 is a pushing surface; 32-10 is an electric heating body, 32-21 is an ultrasonic transducer, 32-22 is an ultrasonic vibration rod, and 32-23 is an ultrasonic fusion cutting system.

[0110] 301 is a first working part, and 302 is a second working part.

[0111] Circuit system:

[0112] 41 is a circuit, 42 is a controller, 43 is an electrical interface device, and 431 is a flexible electrical interface device.

[0113] 41-1 is a conductive core rod, 42-1 is a trigger switch, 42-2 is a data processing system, 43-1 is a conductive connector, 43-2 is an elastic conductive mechanism, 43-3 is an electrical interface; 43-1-1 is a rotor, 43-1-2 is a stator; brush 43-11.

[0114] Temperature control assembly:

[0115] 40-1 is a temperature acquisition system, and 40-2 is a data transmission system.

[0116] On the power supply:

[0117] 51 is a battery module, 52 is a battery pack module, and 53 is a host.

[0118] On the prompt system:

[0119] 61 is a sound prompt device, 62 is a light prompt device, and 63 is an image prompt device.

[0120] On the smoke exhaust system:

[0121] 71 is a smoke outlet, 72 is a smoke exhaust pipe, and 73 is a smoke inlet.

[0122] On water supply / drainage system:

[0123] 81 is the water outlet, 82 is the drain pipe, and 83 is the water inlet. DETAILED DESCRIPTION

[0124] Embodiment 1: A thermal energy cutter head of the present invention

[0125] refer to Figures 1 to 5 A thermal energy blade head in this embodiment comprises a pair of first working parts 301 and second working parts 302 that match each other; each of the first working parts 301 and the second working parts 302 is provided with at least one working surface 31, and at least one of the working surfaces 31 is provided with a heating device 32; the proximal end of the first working part 301 and / or the second working part 302 is connected with a tissue pushing mechanism 33, and the tissue pushing mechanism 33 can push the tissue at the bottom of the thermal energy blade head 3 toward the working surface 31.

[0126] refer to Figure 1-8 and Figure 1-9 In this embodiment, the tissue pushing mechanism 33 is arranged at the proximal end of the first working part 301 and connected to the outer rod 21-2 of the shaft assembly 200; the pushing surface 33-1 of the tissue pushing mechanism 33 forms an angle β with the axis of the outer rod 21-2.

[0127] refer to Figure 1-1 1 and Figure 1-1 2. In this embodiment, the β angle is less than 90° to ensure that the comprehensive force direction of the tissue is upward, so that the tissue can be pushed to the upper part of the working surface 31, thereby avoiding the tissue from gathering at the bottom of the first working part 301 and the second working part 302.

[0128] The tissue pushing mechanism 33 may also be arranged on the second working part 302, and the angle between the pushing surface 33-1 and the axis of the outer rod 21-2 needs to be smaller than the angle between the working surface 31 of the second working part 302 and the axis of the outer rod 21-2, so as to ensure that the comprehensive force direction of the tissue is upward. Alternatively, the tissue pushing mechanism 33 may also be a combined structure respectively arranged on the first working part 301 and the second working part 302, and the applicant does not give specific examples here, but they do not deviate from the protection scope of this application.

[0129] In this embodiment, the pushing surface 33-1 is a blunt smooth surface. The design of the blunt smooth surface can effectively prevent the sharp edges of the pushing surface 33-1 from accidentally cutting tissues during the closing process, thereby avoiding accidental tissue damage. The pushing surface 33-1 can be a flat surface, a convex curved surface, or a concave curved surface, etc., but the pushing surface 33-1 is at a certain angle to the axial direction of the outer rod 21-2, and the applicant will not give examples one by one here.

[0130] The pushing surface 33 - 1 forms an angle α with the working surface 31 of the first working part 301 .

[0131] Furthermore, the angle α is smaller than 180°.

[0132] In this embodiment, the tissue pushing mechanism 33 is integrally manufactured with the first working part 301, which makes the assembly process more convenient, and the manufacturing process is simple and the cost is lower. Of course, the tissue pushing mechanism 33 can be manufactured separately and then connected to the first working part 301 or the second working part 302. The applicant does not give specific examples here, but they do not deviate from the protection scope of this application.

[0133] In this embodiment, the working surface 31 of the first working part 301 and the working surface 31 of the second working part 302 both contain protrusions 30 that can squeeze the liquid in the tissue outward. The protrusions 30 on the working surface 31 of the first working part 301 and the protrusions 30 on the working surface 31 of the second working part 302 match each other. Such mutually matching protrusions 30 have a better effect of squeezing the liquid when the working surface 31 is closed. When the working surface 31 is closed, the protrusions 30 can quickly squeeze the liquid in the tissue out of the working area. At this time, under the action of the heating device 32, the working surface 31 begins to heat up. Since the interference of the liquid in the tissue on the working process is reduced, the protein in the working area is quickly agglutinated and modified, and the ablation, cutting and fusion effects of the tissue are better.

[0134] refer to Figures 2 to 5 In this embodiment, the protrusions 30 are arc-shaped protrusions against arc-shaped protrusions. The protrusions that match each other can also be wedge-shaped protrusions against arc-shaped protrusions, or wedge-shaped protrusions against wedge-shaped protrusions, or arc-shaped protrusions against planes, or wedge-shaped protrusions against planes, or convex protrusions against convex protrusions, or convex protrusions against planes. The applicant only lists the above-mentioned protrusion shapes that match each other. Those skilled in the art can design different shapes as needed without departing from the protection scope of this application.

[0135] In this embodiment, one of the pair of mutually matching protrusions 30 is constituted by the heating device 32 .

[0136] In this embodiment, the heating device 32 is an electric heating device 32-1. In practical applications, different heating methods can be selected as needed, such as ultrasonic heating methods, such as ultrasonic vibration heating devices 32-2 that use ultrasonic vibration rods 32-22 for heating. Figure 8 and Figure 8-1 Alternatively, those skilled in the art may also design different heating devices according to the needs, which do not deviate from the protection scope of the present application.

[0137] The electric heating device 32-1 is heated by a direct current pulse method. The direct current pulse voltage heating method realizes the periodic power-on and power-off of the electric heating device 32-1 through the periodic alternation of high level and low level, and keeps the electric heating device 32-1 powered on for heating and the periodic change of the power-off state for appropriate cooling, so that in the process of continuous heat conduction to the deep of the tissue or organ 9, the temperature of the part where the electric heating device 32-1 contacts the tissue or organ 9 is kept within a stable range and will not continue to rise, effectively avoiding accidental damage to the tissue or organ 9 caused by excessive temperature, and the clinical use process is safer and more reliable.

[0138] The closing method of the working surface 31 can be a translational closing method. Figure 1-1 to Figure 1-6The proximal end of the first working part 301 is connected to the tissue pushing mechanism 33, and the tissue pushing mechanism 33 is connected to the outer rod 21-2 of the shaft assembly 200, and is usually connected and fixed together by inlaying and welding. The protrusion 30 made of insulating and heat-insulating material is provided on it, and the protrusion 30 is embedded in the first working part 301 to form a first protrusion 30-1; the proximal end of the second working part 302 is connected to the inner rod 21-1 of the shaft assembly 200, and is usually connected and fixed together by embedding and welding. A conductive core rod 41-1 as a positive pole is provided in the inner rod 21-1, and an inner insulating heat-resistant sleeve 21-3 is provided between the conductive core rod 41-1 and the inner rod 21-1; the heating device 32 adopts an electric heating body 32-10, one end of the electric heating body 32-10 is connected to the distal end of the conductive core rod 41-1, extends from the distal end of the second working part 302, and then wraps around the inner insulating heat-resistant sleeve 21-3, and the other end of the electric heating body 32-10 is connected to the distal end of the inner rod 21-1, and the inner rod 21-1 is connected to the power supply 500 as a negative pole to form an electrical circuit. The connection is usually fixed together by embedding or welding; the raised electric heating body 32-10 installed on the working surface 31 of the inner insulating heat-resistant sleeve 21-3 of the second working part 302 and the raised arc surface of the inner insulating heat-resistant sleeve 21-3 constitute the second protrusion 30-2 on the second working part 302, and the first protrusion 30-1 and the second protrusion 30-2 form a pair of mutually matching protrusions 30; a middle insulating heat-resistant sleeve 21-4 is provided between the middle tube 21-5 and the inner rod 21-1; the outer rod 21-2 is movably installed on the inner rod 21-1, and the extension or retreat of the inner rod 21-1 can control the opening or closing between the second working part 302 and the first working part 301. In this translation design, the closing of the working surface 31 is achieved by translating one working surface 31 to another working surface 31. During operation, the pushing surface 33 - 1 of the tissue pushing mechanism 33 can push the tissue toward the upper part of the working surface 31 , and the tissue will not gather at the lower end of the working surface 31 . The two working surfaces 31 can be fully fitted at the same time, and the working efficiency is very high.

[0139] In this translational design, the closing of the working surface 31 is achieved by translation of one working surface 31 toward another working surface 31. During operation, the two working surfaces 31 can be completely fitted at the same time, and the working efficiency is very high.

[0140] refer to Figure 1-1In this embodiment, in order to ensure the strength of the second working part 302, the support frame 34 is provided on the outside of the second working part 302. The support frame 34 is L-shaped, with the distal end fixed to the outside of the inner insulating heat-resistant sleeve 21-3 and the proximal end connected to the distal end of the inner rod 21-1.

[0141] The outer rod 21-2 may also be provided with an insulating heat shrinkable sleeve 21-6 that can reduce the friction coefficient. The insulating heat shrinkable sleeve 21-6 can not only provide better insulation protection, but also reduce the friction coefficient of the outer rod 21-2, so that the movement resistance is smaller when entering and exiting the device, and the movement is smoother during operation.

[0142] In this embodiment, when the tissue pushing mechanism 33 is arranged at the proximal end of the first working part 31, during the closing process, the pushing surface 33-1 pushes the tissue to move toward the upper end of the working surface 31 of the second working part 302. After closing, the tissue to be ablated, cut or fused completely enters between the working surfaces 31 under the pushing action of the pushing surface 33-1, and can be completely ablated, cut or fused, which has higher clinical use efficiency.

[0143] Example 2: Electrically heated tissue ablation, cutting and fusion system of the present invention

[0144] refer to Figures 1 to 6 The tissue ablation, cutting and fusion system of this embodiment includes the thermal energy blade 3 described in Example 1.

[0145] The tissue ablation, cutting and fusion system 900 of this embodiment includes a handle assembly 100 , an axis assembly 200 , a working portion 300 , a circuit system 400 , a power source 500 , a prompt system 600 and a smoke exhaust system 700 .

[0146] refer to Figure 1-7 The handle assembly 100 includes a trigger assembly 11, a gear adjustment button 12, an axis connection mechanism 13 and a housing 14, a fixing mechanism 15, a reset mechanism 16 and a force limiting mechanism 17. The trigger assembly 11 is fixedly mounted on the housing 14 through the fixing mechanism 15, and the gear adjustment button 12 and the axis connection mechanism 13 are arranged on the housing 14.

[0147] The shaft assembly 200 includes a shaft rod 21 , a connecting assembly 22 and a knob 23 .

[0148] The working part 300 includes the thermal blade head 3, and a heating device 32 is provided on at least one working surface 31 of the thermal blade head 3. In this embodiment, the heating device 32 is an electric heating device 32-1 that uses the electric heating body 32-10 for heating. Figure 1-1 to Figure 1-6 .

[0149] refer to Figure 1-4 The circuit system 400 includes a circuit 41, a controller 42 and an electrical interface device 43. The circuit system 400 is connected to the power source 500 via the electrical interface device 43.

[0150] In this embodiment, the controller 42 includes a trigger switch 42 - 1 ; the movement of the trigger assembly 11 can connect or disconnect the trigger switch 42 - 1 .

[0151] The proximal end of the shaft assembly 200 is connected to the handle assembly 100 via the shaft connection mechanism 13 ; the distal end of the shaft assembly 200 is connected to the working part 300 ; and the electric heating device 32 - 1 is connected to the power source 500 via the circuit system 400 .

[0152] refer to Figure 1-7 The trigger assembly 11 comprises a trigger 11-1, a rocker arm 11-2 and a slider 11-3; the trigger 11-1 is provided with a trigger shaft 11-1-1 and a rocker arm drive shaft 11-1-2; the rocker arm 11-2 comprises a rocker arm fulcrum 11-2-1, a motion slide groove 11-2-2 and a push block slot 11-2-3; the slider 11-3 comprises a motion push block 11-3-1, a sliding convex step 11-3-2 and a working boss 11-3-3; the trigger shaft 11-1-1 and the fixing mechanism 15 are connected together and fixed on the housing 14; one end of the rocker arm drive shaft 11-1-2 is connected to the trigger 11-1, and the other end is embedded in the motion slide groove 11-2-2 The rocker arm fulcrum 11-2-1 is connected to the fixing mechanism 15, and the rocker arm 11-2 is movably mounted in the housing 14; the moving push block 11-3-1 is embedded in the push block slot 11-2-3, and the sliding convex step 11-3-2 is embedded in the positioning slot 15-1 of the fixing mechanism 15 and connected to the fixing mechanism 15; the trigger 11-1 is pulled, and the trigger 11-1 rotates around the trigger shaft 11-1-1, driving the rocker arm drive shaft 11-1-2 It reciprocates along the motion groove 11-2-2, thereby pushing the rocker arm 11-2 to swing back and forth around the rocker arm fulcrum 11-2-1; the reciprocating swing of the rocker arm 11-2 pushes the motion push block 11-3-1 embedded in the push block slot 11-2-3, thereby driving the slider to move back and forth in a straight line along the positioning groove 15-1, thereby realizing the closing and opening of the working surface 31 of the working part 300.

[0153] A trigger part 11-1-3 is provided on the trigger 11-1; when the trigger 11-1 moves toward the handle 14-1 of the shell 14, the trigger part 11-1-3 touches the trigger switch 42-1, and the trigger switch 42-1 is turned on; when the trigger 11-1 moves away from the handle 14-1 of the shell 14, the trigger part 11-1-3 disengages from the trigger switch 42-1, and the trigger switch 42-1 is turned off.

[0154] The gear adjustment button 12 is connected to the controller 42 via the line 41. The doctor can select different output powers through the gear adjustment button 12 according to the specific conditions of the surgical process, which makes clinical operation more convenient.

[0155] In this embodiment, the gear adjustment button 12 includes a cutting gear 12-1 and a fusion gear 12-2; the cutting gear 12-1 and the fusion gear 12-2 are linked together by a lever mechanism 12-3, so that the cutting gear 12-1 and the fusion gear 12-2 cannot be pressed at the same time. The cutting gear 12-1 and the fusion gear 12-2 cannot be pressed at the same time, which can ensure that there will be no misoperation during clinical use.

[0156] In this embodiment, the handle assembly 100 includes a reset mechanism 16. In this embodiment, the reset mechanism 16 is a combination of a torsion spring mechanism 16-1 and a spring mechanism 16-2. The torsion spring mechanism 16-1 is arranged at the trigger shaft 11-1-1, and the spring mechanism 16-2 is arranged at the proximal end of the positioning slot 15-1 of the fixing mechanism 15. When the trigger 11-1 is pulled, the torsion spring mechanism 16-1 is compressed, the inner rod 21-1 moves toward the proximal end, and the spring mechanism 16-2 is compressed and deformed. When the trigger 11-1 is released, under the action of the torsion spring mechanism 16-1 and the spring mechanism 16-2, the inner rod 21-1 moves toward the distal end, and the trigger 11-1 is automatically reset.

[0157] Those skilled in the art may also design various reset mechanisms as needed, and install one or more reset mechanisms 16 at different locations of the instrument as needed, without departing from the protection scope of the present application.

[0158] refer to Figure 1-4In this embodiment, the handle assembly 100 includes a force limiting mechanism 17. The force limiting mechanism 17 can limit the working pressure transmitted to the working part 300 through the trigger assembly 11. When the force limiting mechanism 17 takes effect, the maximum working pressure applied to the working part 300 after the operator pulls the trigger 11-1 is constant. Usually, during the ablation, cutting and fusion of soft tissues, the maximum working pressure can be limited to less than 100N. Of course, those skilled in the art can set the limit value of the maximum working pressure limited by the force limiting mechanism 17 as needed, which does not deviate from the protection scope of this application.

[0159] In this embodiment, the trigger 11-1 moves toward the handle 14-1 of the housing 14 until the force limiting mechanism 17 takes effect, and then the trigger switch 42-1 can be activated. When the trigger switch 42-1 is turned on, the gear adjustment button 12 can be closed, and the circuit system 400 can be turned on to achieve the tissue ablation, cutting or fusion of the tissue ablation, cutting and fusion system 900 under the set working pressure. Since the trigger switch 42-1 can be activated only when the force limiting mechanism 17 takes effect, it is ensured that the working pressure applied to the tissue by the doctor during the operation is constant, thereby avoiding the difference in surgical effects caused by different operating personnel due to different working pressures applied to the tissue, and the surgical effect during the operation is more stable. At the same time, the safety hazards caused by the continuous heating of the electric heating device 32-1 in the non-working state are effectively avoided, and the use process is safer and more reliable. Of course, those skilled in the art can also design the connection of the trigger switch 42-1 into different states as needed, but they do not deviate from the protection scope of this application.

[0160] In this embodiment, the force limiting mechanism 17 is a spring force limiting mechanism 17-1, and the spring force limiting mechanism 17-1 is arranged at the proximal end of the working boss 11-3-3 of the slider 11-3. When the inner rod 21-1 moves toward the proximal end, the working boss 11-3-3 presses the spring force limiting mechanism 17-1, and the spring force limiting mechanism 17-1 undergoes elastic deformation, thereby achieving the effect of limiting the working pressure.

[0161] Those skilled in the art may also design various other forms of force limiting mechanisms such as an elastic force limiting mechanism or a compression spring force limiting mechanism, which do not depart from the protection scope of the present application.

[0162] During clinical use, the working surface 31 often needs to be rotated to a suitable position according to the different parts of the tissue to be treated. Therefore, in this embodiment, the shaft assembly 200 includes a knob 23, and the knob 23 can drive the shaft 21 to rotate.

[0163] The shaft 21 includes an inner rod 21-1 and an outer rod 21-2; the proximal end of the first working part 301 is connected to the outer rod 21-2, and the proximal end of the second working part 302 is connected to the inner rod 21-1. Turning the knob 23 can drive the inner rod 21-1 and the outer rod 21-2 to rotate, thereby driving the working surfaces 31 of the first working part 301 and the second working part 302 to rotate.

[0164] refer to Figure 6 and Figure 6-1 In this embodiment, the electrical interface device 43 is an elastic electrical interface device 431, and the elastic electrical interface device 431 includes a conductive connector 43-1, an elastic conductive mechanism 43-2, and an electrical interface 43-3. One end of the conductive connector 43-1 is connected to the electric heating device 32-1 through the line 41, and the other end is connected to the elastic conductive mechanism 43-2; the other end of the elastic conductive mechanism 43-2 is connected to the electrical interface 43-3, and the electrical interface 43-3 is connected to the power source 500.

[0165] The conductive joint 43-1 includes a rotor 43-1-1 and a stator 43-1-2; the rotor 43-1-1 can rotate; the distal end of the rotor 43-1-1 is connected to the proximal end of the shaft 21, and when the shaft 21 rotates, the rotor 43-1-1 can rotate synchronously; the proximal end of the stator 43-1-2 is connected to the distal end of the elastic conductive mechanism 43-2.

[0166] Since the rotor 43-1-1 can rotate synchronously with the shaft 21, the line 41 connecting the rotor 43-1-1 and the shaft 21 also rotates synchronously, and the line 41 connecting the conductive connector 43-1 and the rear end of the shaft 21 remain synchronized, thereby avoiding the possible breakage of the wires, loosening of the solder joints, or heating of the connectors caused by the twisting of the line 41.

[0167] The elastic conductive mechanism 43-2 is a conductive mechanism that can be elastically deformed under the action of external force while keeping the circuit unobstructed. The elastic conductive mechanism 43-2 can be elastically deformed under the action of external force. Therefore, when the shaft 21 translates toward the proximal end, the shaft 21 applies pressure to the elastic conductive mechanism 43-2, and the elastic conductive mechanism 43-2 is compressed and deformed. When the shaft translates toward the distal end, the pressure applied by the shaft 21 to the elastic conductive mechanism 43-2 is gradually released. Under the action of the elastic restoring force, the connection state between the conductive connector 43-1 and the shaft 21 can be continuously maintained, and the stable power supply of the circuit system 400 can be maintained. In this movement cycle, the elastic conductive mechanism 43-2 is elastically deformed and reciprocates, which overcomes the fatigue fracture or loose solder joint or heating of the connector caused by the continuous expansion and contraction of the wires during the current wire connection. Not only does it maintain good controllability of the instrument, but it also improves the reliability of the circuit.

[0168] In this embodiment, the elastic conductive mechanism 43-2 is a coil spring mechanism. The elastic conductive mechanism 43-2 can also be a tower spring mechanism, a compression spring mechanism, or other spring mechanisms, which the applicant does not list here. Those skilled in the art can also design the elastic conductive mechanism 43-2 into other elastic structures such as an elastomer structure as needed, which does not deviate from the protection scope of the art.

[0169] In this embodiment, the power supply 500 is a low-frequency, low-voltage DC pulse voltage with an output voltage less than 24V and a frequency less than 500Hz.

[0170] The output voltage of the power supply 500 is a safe voltage less than 24V, and even if an unexpected phenomenon such as leakage occurs during use, it will not cause accidental harm to the human body.

[0171] Preferably, the output voltage of the power supply 500 may be less than 12V.

[0172] The DC pulse voltage output by the power supply 500 realizes the periodic power-on and power-off of the electric heating device 32-1 through the periodic alternating changes between high level and low level, and keeps the electric heating device 32-1 powered on for heating and powered off for moderate cooling. In this way, while the heat is continuously conducted deep into the tissue or organ 9, the temperature of the part where the heating device contacts the tissue or organ 9 is maintained within a stable range and will not continue to rise, thereby effectively avoiding accidental damage to the tissue or organ 9 caused by excessive temperature, and making the clinical use process safer and more reliable.

[0173] According to the thermal conductivity of tissues and organs, the power supply 500 is usually a low-frequency DC pulse voltage with a frequency of less than 500 Hz. Low-frequency pulses can increase the range of high-level and low-level durations, ensuring sufficient heat conduction time while also giving the heating device 32 enough cooling time to ensure that the temperature of the heating device 32 can be controlled within a safe temperature range. At the same time, low-frequency pulses can better avoid electromagnetic interference that electromagnetic pulses may cause to peripheral equipment during the operation of the instrument, and the electromagnetic compatibility of the instrument is better.

[0174] Preferably, the frequency range of the DC pulse voltage output by the power supply 500 is 3 Hz to 200 Hz.

[0175] In this embodiment, the duty cycle of the DC pulse voltage output by the power supply 500 can be adjusted according to the different thermal conductivity of the tissue or organ 9 that needs to be ablated, cut, or fused.

[0176] According to the different thermal conductivity of the tissue to be ablated, cut, or fused, the power output of the heating device 32 is also different, so the duty cycle of the DC pulse power output by the power supply 500 is also different, that is, the heating time and power-off time of the heating device 32 need to be adjusted according to the different operation objects. The duty cycle of the DC pulse power output by the power supply of the tissue ablation, cutting and fusion system of the present invention can be adjusted to meet the thermal conductivity requirements of different tissues or organs 9.

[0177] In this embodiment, the output current of the power supply 500 is less than 10A.

[0178] refer to Figure 1-8 In this embodiment, the power source 500 is a host 53 that can provide long-term stable power supply, which is particularly suitable for large-scale operations with long operation time.

[0179] refer to Figure 7 The power source 500 may also be a battery module 51 or a battery pack module 52. The battery module 51 or the battery pack module 52 is small in size and light in weight, suitable for carrying outside, has low requirements for the power environment, and low voltage power supply is also safer. Users can choose different power sources 500 according to different usage environments and usage requirements.

[0180] In this embodiment, the specific circuit connection method is as follows:

[0181] Positive electrode circuit: The positive electrode of the electric heating device 32-1 is connected to the circuit 41 set in the rod core of the inner rod 21-1. In order to enhance the strength of the inner rod 21-1 during translation and clamping, this part of the circuit 41 is set as a rigid conductive core rod 41-1. An inner insulating heat-resistant sleeve 21-3 is provided between the conductive core rod 41-1 and the inner rod 21-1. One end of the conductive core rod 41-1 is connected to the positive electrode of the electric heating device 32-1, and the other end is connected to the positive electrode of the rotor 43-1-1. The other end of the positive electrode of the rotor 43-1-1 is connected to the positive electrode of the stator 43-1-2 by means of a brush. The other end of the positive electrode of the stator 43-1-2 is connected to the positive electrode of the elastic conductive mechanism 43-2. ​​The other end of the positive electrode of the elastic conductive mechanism 43-2 is connected to the positive electrode of the electrical interface 43-3, and is connected to the positive electrode of the power supply 500 through the electrical interface 43-3.

[0182] Negative pole circuit: the negative pole of the electric heating device 32-1 is connected to the distal end of the conductive inner rod 21-1, the proximal end of the inner rod 21-1 is connected to the negative pole of the rotor 43-1-1 via the circuit 41, the other end of the negative pole of the rotor 43-1-1 is connected to the negative pole of the stator 43-1-2 by means of a brush, the other end of the negative pole of the stator 43-1-2 is connected to the negative pole of the elastic conductive mechanism 43-2, the other end of the negative pole of the elastic conductive mechanism 43-2 is connected to the negative pole of the electrical interface 43-3, and is connected to the negative pole of the power supply 500 via the electrical interface 43-3.

[0183] In this embodiment, the working current flows in through the positive electrode of the electrical interface 43-3, flows into the stator 43-1-2 through the positive electrode of the stator 43-1-2 after passing through the elastic conductive mechanism 42, flows out of the stator 43-1-2 and then flows into the rotor 43-1-1 through the positive electrode of the rotor 43-1-1, flows out of the rotor 43-1-1 and then flows into the conductive core rod 41-1 from the proximal end of the conductive core rod 41-1, flows through the conductive core rod 41-1 and then enters the electric heating device 32-1 from the positive electrode of the electric hot water 32-10 of the electric heating device 32-1, driving the electric heating device 32 -1 generates heat, and the current then flows out from the negative pole of the electric heating device 32-1 and enters the distal end of the inner rod 21-1, flows through the inner rod 21-1 and flows out from the proximal end of the inner rod 21-1, and enters the negative pole of the rotor 43-1-1, flows out from the negative pole of the rotor 43-1-1 and enters the negative pole of the stator 43-1-2, enters the elastic conductive mechanism 43-2 after passing through the stator 43-1-2, flows through the elastic conductive mechanism 43-2 and flows into the electrical interface 43-3 from the distal end of the elastic conductive mechanism 43-2, and flows into the negative pole of the power supply 500 after passing through the electrical interface 43-3.

[0184] In this embodiment, the tissue ablation, cutting and fusion system 900 further includes a temperature control component 401; the temperature control component 401 includes a temperature acquisition system 40-1 and a data transmission system 40-2; the temperature data acquired by the temperature acquisition system 40-1 can be transmitted to the controller 42 through the data transmission system 40-2. The temperature acquisition system 40-1 can continuously acquire working temperature data, and transmit the acquired temperature data to the controller 42 through the data transmission system 40-2. The data processing system 42-2 in the controller 42 can monitor the acquired temperature in real time. When the acquired temperature value exceeds the limit temperature value set by the controller 42, the controller 42 cuts off the power supply to the line 41, or adjusts the current or voltage output by the power supply 500 through the data processing system 42-2, etc., so as to achieve the control effect of reducing the working temperature of the working part 300, effectively avoiding accidental tissue damage or accidental damage of components caused by the electric heating device 32-1 being in a high temperature state for a long time, and making it safer during long-term continuous operation.

[0185] refer to Figure 1-1 0 and Figure 1-1 1. The tissue ablation, cutting and fusion system of this embodiment includes a prompt system 600. The prompt system 600 can prompt the operator of the use status of the instrument as needed, such as using different sounds to prompt different working states, using different lights to prompt the power status, using different patterns to prompt different working parts, etc.

[0186] In this embodiment, the applicant shows three prompting devices of the prompting system 600, namely, a sound prompting device 61, a light prompting device 62, and an image prompting device 63. Those skilled in the art can design different prompting system structures as needed, which do not deviate from the protection scope of this application.

[0187] refer to Figure 1-4 In this embodiment, the tissue ablation, cutting and fusion system 900 includes a smoke exhaust system 700. The smoke exhaust system 700 includes a smoke outlet 71, a smoke exhaust pipe 72 and a smoke inlet 73. The smoke outlet 71 of the smoke exhaust system 700 can be connected to a medical negative pressure source to timely extract the smoke generated during the operation from the body, thereby ensuring a clear surgical field of view and making the surgical process safer and more reliable.

[0188] refer to Figure 6 The tissue ablation, cutting and fusion system of the present invention may also include a water supply / drainage system 800. The water supply / drainage system 800 includes a water outlet 81, a drain pipe 82 and a water inlet 83. The drain pipe 82 of the water supply / drainage system 800 may be either a drain pipe or a water supply pipe. During the operation, the doctor may inject physiological saline or other solvents into the surgical site through the water supply / drainage system 800 according to the needs of the operation, or may promptly discharge blood or sewage from the surgical site through the water supply / drainage system 800 to ensure a smooth operation. At the same time, the water supply / drainage system 800 may also be used as the smoke exhaust system 700 to promptly discharge the smoke generated during the operation to ensure a clear surgical field of view.

[0189] During clinical use, the power source 500 is connected to the circuit system 400 through the electrical interface 43-3, the power switch is turned on, the trigger 11-1 is pulled to move toward the handle 14-1, and the inner rod 21-1 is driven to move toward the proximal end. Under the action of the tissue pushing mechanism 33, the pushing surface 33-1 pushes the tissue or organ 9 toward the upper end of the working surface 31 until the working surface 31 is closed, the working part 300 clamps the tissue to be processed, and the protrusion 30 on the working surface 31 squeezes out the liquid in the tissue, and the trigger 11-1 is continuously pulled until the force limiting mechanism 17 The trigger switch 42-1 is turned on, and the cutting gear 12-1 or the fusion gear 12-2 of the gear adjustment button 12 is pressed according to the surgical situation. The gear adjustment button 12 turns on the controller 42. At this time, the circuit system 400 connects the power supply 500 and the electric heating device 32-1, and the electric heating device 32-1 starts to heat. During this process, the elastic conductive mechanism 43-2 is elastically deformed under the thrust of the inner rod 21 to maintain stable power supply of the circuit system 400. Since the protrusion 30 on the working surface 31 squeezes out the liquid in the tissue and eliminates the interference of the liquid, the protein in the tissue of the working area can be quickly agglutinated and modified under the action of temperature, so as to achieve ablation, cutting and fusion of the tissue. During the closing process of the working surface 31, the tissue pushing mechanism 33 can push the tissue toward the upper part of the working surface 31 of the first working part 301 and / or the second working part 302, preventing the tissue from gathering at the bottom of the first working part 301 and / or the second working part 302, thereby avoiding operational blind spots in the process of tissue ablation, cutting or fusion. During clinical use, the tissue ablation, cutting or fusion process is more efficient.

[0190] During operation, since the power supply 500 outputs a DC pulse voltage to the electric heating device 32-1, the electric heating device 32-1 is periodically powered on and off, and the electric heating device 32-1 is powered on for heating, and powered off for moderate cooling, and periodically changes its state. When powered on, the electric heating device 32-1 heats and raises the temperature, and the heat is conducted through the body tissue to the deep part of the tissue or organ 9. After a certain period of high level, the power supply 500 switches to a low level state, and the electric heating device 32-1 is powered off and stops heating. At this time, the heat retained in the electric heating device 32-1 continues to be conducted through the body tissue, and the temperature of the electric heating device 32-1 is moderately reduced. Then the power supply 50 switches to a high level state again, and the electric heating device 32-1 heats and raises the temperature again. This periodic change of heating and moderate cooling can keep the temperature of the part where the electric heating device 32-1 contacts the tissue or organ 9 within a stable range while ensuring that heat is continuously conducted deep into the tissue or organ 9, and will not continue to rise, thereby effectively avoiding accidental damage to the tissue or organ 9 caused by excessive temperature and ensuring the safe and stable ablation, cutting or fusion process of the tissue.

[0191] After the ablation, cutting or fusion process is completed, the trigger 11-1 is released, and the trigger 11-1 is reset under the action of the reset mechanism 16, the trigger switch 42-1 is disconnected, the electric heating device 32-1 stops working and no longer generates heat, the inner rod 21-1 moves toward the distal end, the working surface 32 opens, and a tissue processing process is completed. When the working surface 32 needs to be rotated, it is only necessary to rotate the knob 23, and the knob 23 drives the shaft 21 to rotate, and the working surface 32 connected to the shaft 21 rotates accordingly. During the rotation process, because the rotor 43-1-1 can rotate synchronously with the shaft 21, the connection between the conductive connector 43-1 and the line 41 at the rear end of the shaft 21 is kept synchronous, which can avoid the wire breakage or loosening of the solder joint or heating of the connector caused by the distortion of the line 41. , thereby ensuring the stable power supply of the circuit system 400. Different tissue parts are selected in turn, and the trigger 11-1 is repeatedly pulled and released to complete the surgical operation. The surgical operation is very simple.

[0192] At the same time, during clinical use, since the temperature acquisition system 40-1 can continuously collect working temperature data and transmit the collected temperature data to the controller 42 through the data transmission system 40-2, the data processing system 42-2 in the controller 42 can monitor the collected temperature in real time. When the collected temperature value exceeds the temperature value set by the controller 42, the controller 42 takes measures such as powering off the line 41, or adjusting the current or voltage output by the power supply 500 through the data processing system 42-2, so as to achieve the control effect of lowering the working temperature of the working part 300, effectively avoiding accidental tissue damage or accidental damage to components caused by the electric heating device 32-1 being in a high temperature state for a long time, and being safer during long-term continuous operation.

[0193] In this embodiment, the trigger 11-1 moves toward the handle 14-1 of the shell 14 until the force limiting mechanism 17 takes effect, and then the trigger part 11-1-3 touches the trigger switch 42-1, and the trigger switch 42-1 is turned on; when the trigger 11-1 moves away from the handle 14-1 of the shell 14, the trigger part 11-1-3 disengages from the trigger switch 42-1, and the trigger switch 42-1 is turned off. Because the trigger switch 42-1 can be activated only when the force limiting mechanism 17 takes effect, the tissue ablation, cutting and fusion system of the present invention can only perform tissue ablation, cutting or fusion under the set working pressure, and the surgical effect is more stable, which effectively prevents accidental injuries that may be caused by misoperation, as well as differences in clinical effects such as vascular closure, tissue fusion, cutting, etc. caused by different clamping forces used by different surgeons. It is safer and more effective, that is, a tissue ablation, cutting and fusion system of the present invention can only be activated to perform tissue ablation, cutting and fusion under a constant clamping force, thereby avoiding differences in use effects caused by different forces used by operators.

[0194] In this embodiment, since the blade 3 of the tissue ablation, cutting and fusion system 900 contains the tissue pushing mechanism 33, during clinical use, during the closing process of the working surface 31, the tissue pushing mechanism 33 can push the tissue toward the upper part of the working surface 31 of the first working part 301 and / or the second working part 302, preventing the tissue from gathering at the bottom of the first working part 301 and / or the second working part 302, avoiding operational blind spots in the tissue ablation, cutting or fusion process, and making the tissue ablation, cutting or fusion process more efficient during clinical use.

[0195] Example 3: Ultrasonic heating type tissue ablation, cutting and fusion system of the present invention

[0196] refer to Figure 8 and Figure 8-1 The difference between this embodiment and embodiment 2 is that, in this embodiment, the heating device 32 is an ultrasonic vibration heating device 32-2.

[0197] The tissue ablation, cutting and fusion system 900 of this embodiment includes a handle assembly 100, an axis assembly 200, a working part 300, a circuit system 400, a power supply 500, a prompt system 600 and a smoke exhaust system 700. The working part 300 includes a first working part 301 and a second working part 302.

[0198] The second working part 302 is provided with a heating device 32. In this embodiment, the heating device 32 is the ultrasonic vibration heating device 32-2. The ultrasonic vibration heating device 32-2 includes an ultrasonic transducer 32-21, an ultrasonic vibration rod 32-22 and an ultrasonic fusion cutting system 32-23. The ultrasonic transducer 32-21 is arranged in the housing 14, the proximal end of the ultrasonic vibration rod 32-22 is connected to the ultrasonic transducer 32-21, and the distal end constitutes the second working part 302.

[0199] The ultrasonic transducer 32-21 is connected to the ultrasonic fusion cutting system 32-23 through the line 41. In this embodiment, the ultrasonic fusion cutting system 32-23 is installed together with the host 53 of the power supply 500. In practical applications, the ultrasonic fusion cutting system 32-23 can also be set separately.

[0200] During clinical use, after the power supply 500 is turned on, the ultrasonic fusion and cutting system 32-23 works, and the ultrasonic transducer 32-21 generates ultrasonic vibrations. The vibration waves generated by the ultrasonic transducer 32-21 are transmitted to the ultrasonic vibration rod 32-22, and the ultrasonic vibration rod 32-22 generates vibrations to heat the tissue, thereby performing ablation, cutting or fusion of the tissue.

[0201] It should be noted that the structures disclosed and described herein can be replaced by other structures with the same effect, and the embodiments introduced in the present invention are not the only structures for implementing the present invention. Although the preferred embodiments of the present invention have been introduced and described herein, it is clear to those skilled in the art that these embodiments are only for illustration, and those skilled in the art can make numerous changes, improvements and substitutions without departing from the present invention. Therefore, the protection scope of the present invention should be defined in accordance with the spirit and scope of the claims attached to the present invention.

Claims

1. A thermal energy cutter head, characterized in that: A. The thermal energy blade (3) comprises a pair of first working parts (301) and second working parts (302) that match each other; B. The first working part (301) and the second working part (302) are each provided with at least one working surface (31), and at least one of the working surfaces (31) is provided with a heating device (32); C. The proximal end of the first working part (301) is connected to a tissue pushing mechanism (33), and the tissue pushing mechanism (33) can push the tissue at the bottom of the thermal energy blade (3) toward the working surface (31); The tissue pushing mechanism (33) is connected to the outer rod (21-2) of the shaft assembly (200); the pushing surface (33-1) of the tissue pushing mechanism (33) forms an angle β with the axis of the outer rod (21-2); The angle β is smaller than 90°; an angle α is formed between the pushing surface (33-1) and the working surface (31) of the first working part (301); and the angle α is smaller than 180°.

2. The thermal energy cutter head according to claim 1, characterized in that: The pushing surface (33-1) is a blunt smooth surface.

3. The thermal energy cutter head according to claim 1, characterized in that: The tissue pushing mechanism (33) and the first working part (301) are manufactured integrally.

4. The thermal energy cutter head according to claim 1, characterized in that: At least one of the working surfaces (31) comprises a protrusion (30) capable of squeezing liquid out of the tissue.

5. The thermal energy cutter head according to claim 4, characterized in that: The working surface (31) of the first working part (301) and the working surface (31) of the second working part (302) both contain protrusions (30) capable of squeezing liquid in the tissue outwards.

6. The thermal energy cutter head according to claim 5, characterized in that: The protrusion (30) on the working surface (31) of the first working part (301) and the protrusion (30) on the working surface (31) of the second working part (302) match each other.

7. The thermal energy cutter head according to claim 4, characterized in that: The heating device (32) is at least one of a pair of mutually matching protrusions (30).

8. The thermal energy cutter head according to claim 1, characterized in that: The heating device (32) is an electric heating device (32-1) or an ultrasonic vibration heating device (32-2).

9. The thermal energy cutter head according to claim 8, characterized in that: The electric heating device (32-1) adopts a direct current pulse heating method.

10. The thermal energy cutter head according to claim 1, characterized in that: The first working part (301) is provided with a protrusion (30) made of insulating and heat-insulating material, and the protrusion (30) is embedded in the first working part (301) to form a first protrusion (30-1); the proximal end of the second working part (302) is connected to the inner rod (21-1) of the shaft assembly (200), and a conductive core rod (41-1) as a positive electrode is provided in the inner rod (21-1), and an inner insulating heat-resistant sleeve (21-3) is provided between the conductive core rod (41-1) and the inner rod (21-1); the heating device (32) adopts an electric heating body (32-10), one end of the electric heating body (32-10) is connected to the distal end of the conductive core rod (41-1), extends from the distal end of the second working part (302) and then wraps around the inner insulating heat-resistant sleeve (21-3), and the electric heating body (32-10) is connected to the distal end of the conductive core rod (41-1), extends from the distal end of the second working part (302), and then wraps around the inner insulating heat-resistant sleeve (21-3), and the electric heating body (32-10) is connected to the distal end of the conductive core rod (41-1). 0) is connected to the distal end of the inner rod (21-1), and the inner rod (21-1) is connected to the power supply (500) as a negative pole to form an electrical circuit; the raised electric heating body (32-10) mounted on the working surface (31) of the inner insulating heat-resistant sleeve (21-3) of the second working part (302) and the raised arc surface of the inner insulating heat-resistant sleeve (21-3) constitute a second protrusion (30-2) on the second working part (302), and the first protrusion (30-1) and the second protrusion (30-2) form a pair of protrusions (30) that match each other; the outer rod (21-2) is movably mounted on the inner rod (21-1), and the forward extension or backward extension of the inner rod (21-1) can control the opening or closing between the second working part (302) and the first working part (301).

11. The thermal energy cutter head according to claim 1, characterized in that: The outer rod (21-2) is also provided with an insulating heat shrinkable sleeve (21-6) capable of reducing the friction coefficient.

12. A tissue ablation, cutting and fusion system, characterized in that: The tissue ablation, cutting and fusion system (900) comprises the thermal energy blade (3) as claimed in claim 1.

13. The tissue ablation, cutting and fusion system according to claim 12, characterized in that: A. The tissue ablation, cutting and fusion system (900) comprises a handle assembly (100), an axis assembly (200), a working part (300), a circuit system (400) and a power source (500): B. The handle assembly (100) comprises a trigger assembly (11), a gear adjustment button (12), an axis connection mechanism (13) and a housing (14); the trigger assembly (11), the gear adjustment button (12) and the axis connection mechanism (13) are arranged on the housing (14); C. The shaft assembly (200) comprises a shaft rod (21) and a connecting assembly (22); D. The working part (300) includes the thermal energy blade (3), and a heating device (32) is provided on at least one working surface (31) of the thermal energy blade (3); E. The circuit system (400) comprises a circuit (41), a controller (42) and an electrical interface device (43); the circuit system (400) is connected to the power source (500) via the electrical interface device (43); F. The proximal end of the shaft assembly (200) is connected to the handle assembly (100) via the shaft connection mechanism (13); the distal end of the shaft assembly (200) is connected to the working part (300); and the heating device (32) is connected to the power source (500) via the circuit system (400).

14. The tissue ablation, cutting and fusion system according to claim 13, characterized in that: The controller (42) includes a trigger switch (42-1); movement of the trigger assembly (11) turns the trigger switch (42-1) on or off.

15. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The handle assembly (100) further comprises a fixing mechanism (15); the trigger assembly (11) is fixedly mounted on the housing (14) via the fixing mechanism (15).

16. The tissue ablation, cutting and fusion system according to claim 15, characterized in that: The trigger assembly (11) comprises a trigger (11-1), a rocker arm (11-2) and a slide block (11-3); the trigger (11-1) is provided with a trigger shaft (11-1-1) and a rocker arm drive shaft (11-1-2); the rocker arm (11-2) comprises a rocker arm fulcrum (11-2-1), a motion slide groove (11-2-2) and a push block slot (11-2-3); the slide block (11-3) comprises a motion push block (11-3-1), a sliding convex step (11- 3-2) and a working boss (11-3-3); the trigger shaft (11-1-1) and the fixing mechanism (15) are connected together and fixed on the housing (14); one end of the rocker arm drive shaft (11-1-2) is connected to the trigger (11-1), and the other end is embedded in the motion slide groove (11-2-2); the rocker arm fulcrum (11-2-1) and the fixing mechanism (15) are connected together to enable the rocker arm (11-2) to move The movable push block (11-3-1) is embedded in the push block slot (11-2-3), and the sliding convex step (11-3-2) is embedded in the positioning slot (15-1) of the fixing mechanism (15) and connected to the fixing mechanism (15); the trigger (11-1) is pulled, and the trigger (11-1) rotates around the trigger shaft (11-1-1), driving the rocker arm drive shaft (11-1 -2) reciprocates along the motion slide groove (11-2-2), thereby pushing the rocker arm (11-2) to swing back and forth around the rocker arm fulcrum (11-2-1); the reciprocating swing of the rocker arm (11-2) pushes the motion push block (11-3-1) embedded in the push block slot (11-2-3), thereby driving the slider to move back and forth in a straight line along the positioning slide groove (15-1), thereby realizing the closing and opening of the working surface (31) of the working part (300).

17. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The trigger (11-1) is provided with a trigger portion (11-1-3); when the trigger (11-1) moves toward the handle (14-1) of the housing (14), the trigger portion (11-1-3) touches the trigger switch (42-1), and the trigger switch (42-1) is turned on; when the trigger (11-1) moves away from the handle (14-1) of the housing (14), the trigger portion (11-1-3) is disengaged from the trigger switch (42-1), and the trigger switch (42-1) is turned off.

18. The tissue ablation, cutting and fusion system according to claim 13, characterized in that: The gear adjustment button (12) is connected to the controller (42) via the line (41).

19. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The gear adjustment button (12) comprises a cutting gear (12-1) and a fusion gear (12-2); the cutting gear (12-1) and the fusion gear (12-2) are linked together via a lever mechanism (12-3), so that the cutting gear (12-1) and the fusion gear (12-2) cannot be pressed at the same time.

20. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The handle assembly (100) also includes a reset mechanism (16).

21. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The handle assembly (100) further comprises a force limiting mechanism (17).

22. The tissue ablation, cutting and fusion system according to claim 21, characterized in that: The trigger switch (42-1) can only be activated when the trigger (11-1) moves toward the handle (14-1) of the housing (14) until the force limiting mechanism (17) takes effect. When the trigger switch (42-1) is turned on, the gear adjustment button (12) can be closed to connect the circuit system (400), thereby enabling the tissue ablation, cutting or fusion system (900) to perform tissue ablation, cutting or fusion under the set working pressure.

23. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The shaft assembly (200) further comprises a knob (23); the knob (23) drives the shaft rod (21) to perform rotational movement.

24. The tissue ablation, cutting and fusion system according to claim 23, characterized in that: The shaft rod (21) comprises an inner rod (21-1) and an outer rod (21-2); the proximal end of the first working part (301) is connected to the outer rod (21-2), and the proximal end of the second working part (302) is connected to the inner rod (21-1); the inner rod (21-1) and the outer rod (21-2) are driven to rotate by rotating the knob (23), thereby driving the working surfaces (31) of the first working part (301) and the second working part (302) to rotate.

25. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The electrical interface device (43) is an elastic electrical interface device (431), and the elastic electrical interface device (431) comprises a conductive joint (43-1), an elastic conductive mechanism (43-2) and an electrical interface (43-3); one end of the conductive joint (43-1) is connected to the electric heating device (32-1) via the line (41), and the other end is connected to the elastic conductive mechanism (43-2); the other end of the elastic conductive mechanism (43-2) is connected to the electrical interface (43-3), and the electrical interface (43-3) is connected to the power source (500).

26. The tissue ablation, cutting and fusion system according to claim 25, characterized in that: The conductive joint (43-1) comprises a rotor (43-1-1) and a stator (43-1-2); the rotor (43-1-1) is capable of rotating; the distal end of the rotor (43-1-1) is connected to the proximal end of the shaft (21); when the shaft (21) rotates, the rotor (43-1-1) rotates synchronously; the proximal end of the stator (43-1-2) is connected to the distal end of the elastic conductive mechanism (43-2).

27. The tissue ablation, cutting and fusion system according to claim 25, characterized in that: The elastic conductive mechanism (43-2) is a conductive mechanism that undergoes elastic deformation under the action of external force while maintaining a smooth circuit.

28. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The tissue ablation, cutting and fusion system (900) further comprises a temperature control component (401); the temperature control component (401) comprises a temperature acquisition system (40-1) and a data transmission system (40-2); the temperature data acquired by the temperature acquisition system (40-1) can be transmitted to the controller (42) via the data transmission system (40-2).

29. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The power supply (500) is a low-voltage power supply with an output voltage less than 24V.

30. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The power supply (500) outputs a DC pulse voltage.

31. The tissue ablation, cutting and fusion system according to claim 30, characterized in that: The frequency of the DC pulse voltage output by the power supply (500) is less than 500 Hz.

32. The tissue ablation, cutting and fusion system according to claim 30, characterized in that: The duty cycle of the DC pulse voltage output by the power source (500) is adjustable according to the thermal conductivity of the tissue or organ (9) to be ablated, cut or fused.

33. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The power source (500) is a battery module (51) or a host (53).

34. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The tissue ablation, cutting and fusion system (900) also includes a prompt system (600).

35. The tissue ablation, cutting and fusion system according to claim 34, characterized in that: The prompting system (600) is a sound prompting device (61), or a light prompting device (62), or an image prompting device (63).

36. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The tissue ablation, cutting and fusion system (900) also includes a smoke exhaust system (700); the smoke exhaust system (700) includes a smoke outlet (71), a smoke exhaust pipe (72) and a smoke inlet (73).

37. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The tissue ablation, cutting and fusion system (900) also includes a water supply / drainage system (800); the water supply / drainage system (800) includes a water outlet (81), a drainage pipe (82) and a water inlet (83).

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