CN112294426A

CN112294426A - Heat energy tool bit and tissue ablation, cutting and fusion system

Info

Publication number: CN112294426A
Application number: CN201910703211.4A
Authority: CN
Inventors: 周星; 苏文宇; 徐华苹; 罗丽飞; 王玉娥; 张琪
Original assignee: Guangzhou T K Medical Instrument Co ltd
Current assignee: Guangzhou T K Medical Instrument Co ltd
Priority date: 2019-07-31
Filing date: 2019-07-31
Publication date: 2021-02-02

Abstract

The heat energy cutter head comprises a first working part and a second working part which are matched with each other, wherein at least one working surface is arranged on each of the first working part and the second working part, and a heating device is arranged on at least one working surface; and the near end of the first working part or the second working part is connected with a tissue pushing mechanism which can push the tissue to the upper end of the working surface. The tissue ablation, cutting and fusion system of the present invention comprises a handle assembly, a shaft assembly, a working portion, circuitry and a power source. The working part comprises a heat energy cutter head. During clinical use, in the process of closing the working surface, the tissue pushing mechanism can push the tissue to the upper part of the working surface of the first working part and/or the second working part, so that the tissue is prevented from being gathered at the bottom of the first working part and/or the second working part, the operation dead angle of the tissue ablation, cutting or fusion process is avoided, and the efficiency of the tissue ablation, cutting or fusion process is higher in the clinical use process.

Description

Heat energy tool bit and tissue ablation, cutting and fusion system

Technical Field

The present invention relates to an electrosurgical instrument, in particular a surgical instrument for tissue ablation, cutting and fusion for use in surgery.

Background

In surgical operation, ablation, cutting and fusion of tissues are very important tissue treatment processes, and in currently common tissue ablation, cutting and fusion technologies, an electrically heated tissue ablation method is one of important technologies, and the ablation, cutting and fusion processes of tissues are realized by heating the tissues to cause aggregation and modification of proteins. Therefore, in the electrically heated tissue ablation method, the core is how to ensure rapid aggregation of proteins and rapidly raise their temperature. In human tissue, there are, in addition to proteins, a large number of liquid substances, such as blood, interstitial fluid, etc., the presence of which interferes significantly with the aggregation of proteins and the warming of the proteins.

Aiming at the problems that in the prior art, the working surfaces of original work are generally in plane contact due to the fact that a heating device is additionally arranged at the end parts of conventional surgical instruments such as surgical forceps, surgical nickel and the like, and the forceps heads need to be closed by applying large pressure in the temperature rising process so as to ensure that protein in a working area is aggregated and modified, and the operation process is inconvenient, the working part of the conventional tissue ablation, cutting and fusion system is improved by the technical scheme provided by the applicant in the patent application of 'a thermal energy cutter head and a tissue ablation, cutting and fusion system' (application number: 201910263660.1).

However, in practical applications, tissue accumulation occurs at the bottom of the working portion during the closing process of the working portion, so that the tissue ablation, cutting and fusion processes cannot be smoothly performed, and therefore, the prior art tissue ablation, cutting and fusion system needs to be improved, and particularly, the working portion thereof needs to be further improved.

Disclosure of Invention

According to the tissue ablation, cutting and fusion system, the specially designed tissue pushing mechanism can push the tissue to the working surface of the working part when the working part is closed in the tissue ablation, cutting and fusion processes, so that the tissue is prevented from being gathered at the bottom of the working part, no operation dead angle exists in the clinical use process, and the clinical use is safer and more effective.

The invention relates to a heat energy cutter head, which is characterized in that:

A. the thermal energy cutter head 3 comprises a pair of a first working part 301 and a second working part 302 which are matched with each other;

B. the first working part 301 and the second working part 302 are respectively 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 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 cutter head 3 to the working surface 31.

The tissue pushing mechanism 33 is arranged on the thermal energy cutter head 3, when the working parts are closed, the tissue pushing mechanism 33 can push tissues to the upper parts of the working surfaces 31 of the first working part 301 and/or the second working part 302, so that the tissues are prevented from being gathered at the bottoms of the first working part 301 and/or the second working part 302, operation dead corners of tissue ablation, cutting or fusion processes are avoided, and the tissue ablation, cutting or fusion processes are higher in efficiency in the clinical use process.

The tissue pushing mechanism 33 is arranged at the proximal end of the first working part 301 and is connected with the outer rod 21-2 of the shaft assembly 200; the pushing surface 33-1 of the tissue pushing mechanism 33 and the axis of the outer rod 21-2 form an angle beta. When the tissue pushing mechanism 33 is disposed at the proximal end of the first working portion 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 portion 302, and after the closing process, 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, so as to be ablated, cut or fused completely, and the clinical use efficiency is higher. The pushing surface 33-1 may be a plane, or a convex arc surface, or a concave arc surface, but the pushing surface 33-1 and the axial direction of the outer rod 21-2 form a certain angle.

The beta angle is less than 90 deg.. When the tissue pushing mechanism 33 is disposed on the first working portion 301, the β angle is less than 90 °. When the tissue pushing mechanism 33 is disposed on the second working portion 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 portion 302 and the axis of the outer rod 21-2, so as to ensure that the comprehensive stress direction of the tissue is upward, and the tissue can be pushed toward the upper portion of the working surface 31, thereby avoiding the tissue from accumulating at the bottoms of the first working portion 301 and the second working portion 302.

The pushing surface 33-1 is a blunt smooth surface. Due to the design of the blunt smooth surface, the tissue can be effectively prevented from being accidentally cut by the sharp edges and corners of the thrust extrusion surface 33-1 in the closing process, and accidental injury to the tissue is avoided.

The pushing surface 33-1 and the working surface 31 of the first working part 301 form an angle α.

Further, the α angle is less than 180 °.

The tissue pushing mechanism 33 is integrally manufactured with the first working portion 301. The tissue pushing mechanism 33 can be integrally manufactured with the first working portion 301, so that the assembly process is more convenient, the manufacturing process is simple, and the cost is lower. Of course, the tissue pushing mechanism 33 can be separately manufactured and then connected to the first working portion 301 or the second working portion 302, which is not specifically illustrated by the applicant herein, without departing from the scope of the present application.

At least one of the working surfaces 31 includes protrusions 30 thereon which are capable of pushing fluid out of the tissue. When the working surface 31 is closed, the protrusion 30 can rapidly extrude 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 starts to heat up, and as the interference of the liquid in the tissue to the working process is reduced, the protein in the working area is rapidly aggregated and modified, and the tissue ablation, cutting and fusion effects are better.

Further, the working surface 31 of the first working portion 301 and the working surface 31 of the second working portion 302 both include protrusions 30 capable of pushing out the liquid in the tissue.

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 are matched with each other. The matching projections 30 provide a better pressing action on the liquid when the working surface 31 is closed.

The pair of protrusions 30 matched with each other is an arc protrusion to an arc protrusion, or a wedge protrusion to a wedge protrusion, or an arc protrusion to a plane, or a wedge protrusion to a plane, or a convex protrusion to a convex protrusion, or a convex protrusion to a plane. The applicant has only listed the above several shapes of the protrusions matching each other, and those skilled in the art can design different shapes as required without departing from the scope of protection of the present application.

The heating means 32 may be at least one of a pair of the protrusions 30 that are matched with each other.

The heating device 32 may be an electric heating device 32-1 or an ultrasonic vibration heating device 32-2. Different heating modes can be selected according to requirements, such as electric heating or ultrasonic heating, or other heating modes. The applicant has only exemplified the two heating devices described above, and those skilled in the art can design the heating devices in different ways as required without departing from the scope of protection of the present application.

The electric heating device 32-1 adopts a direct current pulse mode for heating. The heating mode of the direct current pulse voltage realizes the periodic electrification and the power failure of the electric heating device 32-1 through the periodic interaction change of a high level and a low level, keeps the periodic change of the state of electrifying, heating and moderate temperature reduction of the electric heating device 32-1, ensures that the temperature of the part of the electric heating device 32-1, which is contacted with the tissue or the organ 9, is kept in a stable range and cannot be continuously increased in the process of continuously conducting heat to the deep part of the tissue or the organ 9, effectively avoids the accidental injury of the tissue or the organ 9 caused by overhigh temperature, and is safer and more reliable in the clinical use process.

The tissue pushing mechanism 33 is connected to the proximal end of the first working part 301, 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 an 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 near end of the second working part 302 is connected with an inner rod 21-1 of the shaft assembly 200, a conductive core rod 41-1 serving as a positive electrode is arranged in the inner rod 21-1, and an inner insulating heat-resistant sleeve 21-3 is arranged 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 far end of the conductive core rod 41-1, the electric heating body extends out of the far end of the second working part 302 and then is tightly attached to the inner insulating heat-resistant sleeve 21-3 to be wound back, the other end of the electric heating body 32-10 is connected to the far end of the inner rod 21-1, and the inner rod 21-1 is used as a negative pole and is connected with the power supply 500 to form an electric loop; the convex electric heating body 32-10 arranged on the working surface 31 of the inner insulating heat-resistant sleeve 21-3 of the second working part 302 and the convex arc surface of the inner insulating heat-resistant sleeve 21-3 form 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 mutually matched protrusions 30; a middle insulating heat-resistant sleeve 21-4 is arranged between the middle pipe 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 retraction 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 surfaces 31 is achieved by translating one of the working surfaces 31 towards the other 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, the tissue is not gathered at the lower end of the working surface 31, the two working surfaces 31 can be completely jointed at the same time, and the working efficiency is very high.

To ensure the strength of the second working portion 302, a support bracket 34 may be disposed outside the second working portion 302, and a proximal end of the support bracket 34 may be connected to a distal end of the inner rod 21-1.

Besides the above-mentioned electric heating manner, the heating device 32 may also be an ultrasonic vibration heat-generating device 32-2 that performs ultrasonic heating by using an ultrasonic transducer.

The outer rod 21-2 may also be provided with an insulating heat shrink 21-6 that reduces the coefficient of friction. The insulating heat-shrinkable sleeve 21-6 not only can provide better insulation protection, but also can reduce the friction coefficient of the outer rod 21-2, and has smaller movement resistance when entering and exiting an instrument and smoother movement in the operation process.

The tissue ablation, cutting and fusion system of the present invention comprises said thermal tip 3.

The tissue ablation, cutting and fusion system of the invention is characterized in that:

A. the tissue ablation, cutting and fusion system 900 comprises a handle assembly 100, a shaft assembly 200, a working portion 300, a circuit system 400 and a power supply 500;

B. the handle assembly 100 comprises a trigger assembly 11, a gear adjusting button 12, a shaft connecting mechanism 13 and a shell 14; the trigger assembly 11, the gear adjusting button 12 and the shaft connecting mechanism 13 are arranged on the shell 14;

C. the shaft assembly 200 comprises a shaft 21 and a connecting assembly 22;

D. the working part 300 comprises the thermal energy tool bit 3, and a heating device 32 is arranged on at least one working surface 31 of the thermal energy tool bit 3;

E. the circuitry 400 includes circuitry 41, a controller 42, and electrical interface means 43; the circuitry 400 is connected to the power supply 500 via the electrical interface means 43;

F. the proximal end of the shaft assembly 200 is connected to the handle assembly 100 through the shaft connecting mechanism 13; the distal end of the shaft assembly 200 is connected to the working portion 300; the electric heating device 32-1 is connected to the power supply 500 through the circuit system 400.

According to the tissue ablation, cutting and fusion system, as the tissue pushing mechanism 33 is arranged on the thermal energy cutter head 3, the tissues or organs 9 cannot be stacked on the lower part of the working surface 31 of the thermal energy cutter head 3, no operation dead angle exists, and the efficiency of the tissue or organ 9 cutting, ablation or fusion process is very high.

The controller 42 comprises a trigger switch 42-1; movement of the trigger assembly 11 can turn the trigger switch 42-1 on or off. The trigger switch 42-1 can be switched on only by pulling the trigger assembly 11 to apply working pressure to the working part 300, so that the electric heating device 32-1 is heated, accidental injury or potential safety hazard possibly caused by misoperation are avoided, and the clinical use process is safer and more reliable.

Further, the handle assembly 100 further comprises a fixing mechanism 15; the trigger assembly 11 is fixedly mounted to the housing 14 by the securing mechanism 15. During assembly, the trigger assembly 11 can be embedded or fixed in the mounting groove of the fixing mechanism 5 and is assembled into a whole and then fixed on the shell 14, so that the assembly process is simpler and more convenient, and the fixation is firmer.

The trigger assembly 11 comprises a trigger 11-1, a rocker arm 11-2 and a sliding block 11-3; the trigger 11-1 is provided with a trigger rotating shaft 11-1-1 and a rocker arm driving shaft 11-1-2; the rocker arm 11-2 comprises a rocker arm fulcrum 11-2-1, a moving chute 11-2-2 and a pushing block clamping groove 11-2-3; the sliding 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 rotating shaft 11-1-1 is connected with the fixing mechanism 15 and fixed on the shell 14; one end of the rocker arm driving shaft 11-1-2 is connected to the trigger 11-1, and the other end of the rocker arm driving shaft is embedded in the moving chute 11-2-2; the rocker fulcrum 11-2-1 and the fixing mechanism 15 are connected together, and the rocker 11-2 is movably arranged in the shell 14; the moving push block 11-3-1 is embedded in the push block clamping groove 11-2-3, and the sliding convex step 11-3-2 is embedded in the positioning sliding groove 15-1 of the fixing mechanism 15 and connected with the fixing mechanism 15; pulling the trigger 11-1, wherein the trigger 11-1 rotates around the trigger rotating shaft 11-1-1 to drive the rocker arm driving shaft 11-1-2 to reciprocate along the motion chute 11-2-2, so as to push the rocker arm 11-2 to reciprocate around the rocker arm fulcrum 11-2-1; the reciprocating swing of the rocker arm 11-2 pushes the moving push block 11-3-1 embedded in the push block clamping groove 11-2-3 so as to drive the slide block to linearly move back and forth along the positioning sliding groove 15-1, so that the working surface 31 of the working part 300 is closed and opened.

The trigger 11-1 is provided with a trigger part 11-1-3; when the trigger 11-1 moves towards the grip 14-1 of the housing 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 grip 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.

The gear shift knob 12 is connected to the controller 42 via the line 41. Doctors can select different output powers through the gear adjusting button 12 according to the specific conditions of the operation process, and the clinical operation is more convenient.

The gear adjusting button 12 comprises a cutting gear 12-1 and a fusion gear 12-2; the cutting rail 12-1 and the fusion rail 12-2 are linked together by a lever mechanism 12-3 such that the cutting rail 12-1 and the fusion rail 12-2 cannot be depressed simultaneously. The cutting file 12-1 and the fusion file 12-2 can not be pressed down simultaneously, so that the phenomenon of misoperation can not occur in the clinical use process.

The handle assembly 100 also includes a reset mechanism 16. When the trigger 11-1 is released, the reset mechanism 16 can enable the trigger 11-1 to automatically reset through reset force, so that the safety, the convenience and the comfort in the use process are greatly improved. The reset mechanism 16 may be a torsion spring mechanism, or a spring mechanism, or an elastic body mechanism, etc., and those skilled in the art can design various reset mechanisms as required, and mount 1 or more reset mechanisms 16 at different positions of the apparatus as required without departing from the scope of the present application.

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 is activated, the maximum working pressure applied to the working part 300 after an operator pulls the trigger 11-1 is constant, and the maximum working pressure can be limited below 100N in the processes of ablation, cutting and fusion of soft tissues. Of course, a person skilled in the art can set the limit value of the maximum working pressure defined by the force limiting mechanism 17 as desired without departing from the scope of protection of the present application. The force limiting mechanism 17 may be a spring force limiting mechanism, an elastic body force limiting mechanism, a pressure spring force limiting mechanism, or other various structures, and those skilled in the art may design other various force limiting mechanisms without departing from the scope of the present application.

The trigger 11-1 moves towards the grip 14-1 of the housing 14 until the force limiting mechanism 17 acts, the trigger switch 42-1 can be started, and when the trigger switch 42-1 is turned on, the gear adjusting button 12 can be closed to turn on the circuit system 400, so that the tissue ablation, cutting and fusion system 900 performs tissue ablation, cutting or fusion under a set working pressure. Since the trigger switch 42-1 can be activated only when the force limiting mechanism 17 is activated, it is ensured that the working pressure applied to the tissue by the surgeon during the operation is constant, therefore, the tissue ablation, cutting and fusion system can perform tissue ablation, cutting or fusion only under the set working pressure, the operation effect is more stable, accidental injury possibly caused by misoperation is effectively prevented, and the clinical effect differences of vessel closure, tissue fusion, cutting and the like caused by different clamping forces used by different surgeons are safer and more effective, namely, the tissue ablation, cutting and fusion system can start the ablation, cutting and fusion of tissues only under the constant clamping force, so that the difference of the use effect of an operator caused by different forces is avoided.

The shaft assembly 200 also contains a knob 23; the knob 23 can drive the shaft 21 to perform a rotational movement.

The shaft rod 21 comprises an inner rod 21-1 and an outer rod 21-2; the proximal end of the first working portion 301 is connected to the outer rod 21-2, the proximal end of the second working portion 302 is connected to the inner rod 21-1, and the knob 23 is rotated to drive the inner rod 21-1 and the outer rod 21-2 to rotate, so as to drive the working surfaces 31 of the first working portion 301 and the second working portion 302 to rotate.

In clinical use, the working surface 31 needs to be rotated to a proper position according to different parts of tissues to be treated, the knob 23 can drive the shaft 21 to move, and the working surface 31 is further driven to rotate to a proper direction and position.

The electrical interface means 43 is an elastic electrical interface means 431, the elastic electrical interface means 431 comprises an electrically conductive contact 43-1, an elastic electrically conductive mechanism 43-2 and an electrical interface 43-3; one end of the conductive connector 43-1 is connected with the electric heating device 32-1 through the line 41, and the other end is connected with 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.

The conductive joint 43-1 comprises 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 and the proximal end of the shaft 21 are connected together, and the rotor 43-1-1 can synchronously rotate when the shaft 21 rotates; the proximal end of the stator 43-1-2 is connected to the distal end of the resilient conductive means 43-2.

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, the conductive joint 43-1 and the line 41 at the rear end of the shaft 21 are kept synchronous, and the wire breakage or the weld loosening caused by the twisting of the line 41 can be avoided.

The elastic conductive mechanism 43-2 is a conductive mechanism that can be elastically deformed under an external force while maintaining a circuit in a smooth state. The elastic conductive mechanism 43-2 can be elastically deformed under the action of an external force, so that when the shaft 21 translates proximally, the shaft 21 applies pressure to the elastic conductive mechanism 43-2, the elastic conductive mechanism 43-2 is compressively deformed, when the shaft translates distally, the pressure applied to the elastic conductive mechanism 43-2 by the shaft 21 is gradually released, and under the action of an elastic restoring force, the connection state of the conductive joint 43-1 and the shaft 21 can be continuously maintained, and the stable power supply of the circuit system 400 can be maintained. In the movement period, the elastic conductive mechanism 43-2 generates elastic deformation to perform reciprocating action, so that the fatigue fracture or welding point loosening caused by the continuous expansion and contraction of the electric wire during the current electric wire connection is overcome. Not only keeps the good controllability of the instrument, but also improves the reliability of the circuit.

The tissue ablation, cutting and fusion system 900 further comprises a temperature control assembly 401; the temperature control assembly 401 comprises a temperature acquisition system 40-1 and a data transmission system 40-2; the temperature data collected by the temperature collection system 40-1 can be transmitted to the controller 42 via the data transmission system 40-2. The temperature collecting system 40-1 can continuously collect the 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 limit temperature value set by the controller 42, the controller 42 performs power-off processing on the line 41, or the data processing system 42-2 adjusts the current or voltage output by the power supply 500, so as to achieve the control effect of reducing the working temperature of the working part 300, effectively avoid the accidental tissue damage or the accidental element damage caused by the long-term high-temperature state of the electric heating device 32-1, and ensure that the electric heating device is safer in the long-term continuous working process.

The power supply 500 is a low voltage power supply with an output voltage less than 24V. The output voltage of the power supply 500 is a safe voltage less than 24V, and even if an unexpected phenomenon such as electric leakage occurs in the use process, the human body cannot be accidentally injured.

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

The power supply 500 outputs a dc pulse voltage. The direct current 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 interaction change of the high level and the low level, keeps the periodic change of the states of the electric heating device 32-1 of power-on heating and moderate temperature reduction of power-off, ensures that the temperature of the part of the heating device contacted with the tissue or organ 9 is kept in a stable range and cannot be continuously increased in the process of continuously conducting heat to the deep part of the tissue or organ 9, effectively avoids the accidental injury of the tissue or organ 9 caused by overhigh temperature, and is safer and more reliable in the clinical use process.

The frequency of the direct current pulse voltage output by the power supply 500 is less than 500 Hz. The power supply 500 is typically a low frequency dc pulsed voltage with a frequency less than 500Hz, depending on the thermal conductivity of the tissue and organs. On one hand, the low-frequency pulse can enlarge the range selection of the duration time of the high level and the low level, and the sufficient cooling time is provided for the heating device 32 while the sufficient heat conduction time is ensured, so that the temperature of the heating device 32 can be controlled within the safe temperature range. Meanwhile, the low-frequency pulse can better avoid the electromagnetic interference possibly caused by the electromagnetic pulse to peripheral equipment in the operation process of the instrument, and the electromagnetic compatibility of the instrument is better.

Preferably, the frequency range of the dc pulse voltage output by the power supply 500 is 3Hz to 200 Hz.

The duty cycle of the dc pulse voltage output by the power supply 500 is adjustable according to the thermal conductivity of the tissue or organ 9 to be ablated, cut or fused.

The heating device 32 needs to output different power according to different thermal conductivity coefficients of tissues to be ablated, cut or fused, so that the duty ratio of the dc pulse power output by the power supply 500 is different, that is, the heating time and the power-off time of the heating device 32 need to be adjusted according to different operation objects. The duty cycle of the direct current pulse power supply output by the power supply for the tissue ablation, cutting and fusion system can be adjusted, and the heat conduction requirements of different tissues or organs 9 can be met.

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

The power supply 500 is a battery module 51, a battery pack module 52 or a host 53. The battery module 51 or the battery module 52 has small volume and light weight, is suitable for being carried outdoors, has low requirement on electricity environment, is safer in low-voltage power supply, can stably supply power for a long time, and is particularly suitable for large-scale operations with long operation time; the user can select different power supplies 500 according to different use environments and different use requirements.

The tissue ablation, cutting and fusion system 900 also includes a cue system 600. The prompt system 600 can prompt the operator about the use state of the apparatus according to the requirement, such as prompting different working states with different sounds, prompting the state of the power supply with different lights, prompting different working positions with different patterns, and the like.

The prompting system 600 is a voice prompting device 61, a light prompting device 62 or an image prompting device 63. The applicant only lists the three prompting devices, and those skilled in the art can design different prompting system structures according to the needs without departing from the protection scope of the present application.

The tissue ablation, cutting and fusion system 900 further comprises a smoke evacuation system 700; the fume extraction system 700 includes a fume outlet 71, a fume extraction duct 72, and a fume inlet 73. The smoke outlet 71 of the smoke exhaust system 700 can be connected with a medical negative pressure source, smoke generated in the operation process is timely extracted out of the body, the operation visual field is clear, and the operation process is safer and more reliable.

The tissue ablation, cutting and fusion system 900 further comprises a water supply/drainage system 800; the water supply/drainage system 800 includes a water outlet 81, a water drainage 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 supply pipe. In the operation process, a doctor can inject normal saline or other solvents into the operation position through the water supply/drainage system 800 according to the operation requirement, and can timely discharge blood or sewage at the operation position out of the body through the water supply/drainage system 800, so that the smooth operation of the operation process is ensured.

In clinical use, the power supply 500 is connected with the circuit system 400 through the electrical interface 43-3, a power switch is turned on, the trigger 11-1 is pulled to move towards the grip 14-1 to drive the inner rod 21-1 to move towards the proximal end, the pushing surface 33-1 pushes the tissue or organ 9 towards the upper end of the working surface 31 under the action of the tissue pushing mechanism 33 until the working surface 31 is closed, the working part 300 clamps the tissue to be treated, the bulge 30 on the working surface 31 pushes out the liquid in the tissue, the trigger 11-1 is continuously pulled until the force limiting mechanism 17 acts to switch on the trigger switch 42-1, the cutting gear 12-1 or the fusion gear 12-2 of the gear adjusting button 12 is selected to be pressed according to the surgical condition, the gear adjustment button 12 is connected to the controller 42, at this time, the circuit system 400 connects the power supply 500 to the electric heating device 32-1, the electric heating device 32-1 starts to generate heat, and in this process, the elastic conductive mechanism 43-2 elastically deforms under the thrust of the inner rod 21, so as to maintain stable power supply of the circuit system 400. As the bulge 30 on the working surface 31 extrudes the liquid in the tissue, the interference of the liquid is eliminated, the protein in the tissue of the working area can be quickly agglutinated and modified under the action of temperature, and the ablation, the cutting and the fusion of the tissue are realized. 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, so as to prevent the tissue from being gathered at the bottom of the first working part 301 and/or the second working part 302, thereby avoiding the operation dead angle of the tissue ablation, cutting or fusion process, and the efficiency of the tissue ablation, cutting or fusion process is higher in the clinical use process.

In the working process, because the power supply 500 outputs direct current pulse voltage to the electric heating device 32-1, the electric heating device 32-1 is periodically powered on and powered off, the electric heating device 32-1 is powered on for heating, the state of the power-off moderate cooling is periodically changed, when the electric heating device is powered on, the electric heating device 32-1 heats and heats, heat is conducted to the deep part of the tissue or organ 9 through the body tissue, after a certain time of high level, the power supply 500 is switched to the low level state, the electric heating device 32-1 is powered off and stops heating, at the moment, the heat remained on the electric heating device 32-1 is continuously conducted through the body tissue, the temperature of the electric heating device 32-1 is moderately reduced, and then the power supply 50 is switched to the high level state again, the electric heating device 32-1 is heated again to raise the temperature. The periodic changes of temperature rise and moderate temperature drop can keep the temperature of the part of the electric heating device 32-1, which is in contact with the tissue or organ 9, in a stable range in the process of ensuring that heat is continuously conducted to the deep part of the tissue or organ 9, and the temperature cannot be continuously raised, thereby effectively avoiding the accidental injury of the tissue or organ 9 caused by overhigh temperature and ensuring the safe and stable operation of the processes of ablation, cutting or fusion of the tissue.

After the ablation, cutting or fusion process is finished, the trigger 11-1 is released, the trigger 11-1 is reset under the action of the reset mechanism 16, the trigger switch 42-1 is switched off, the electric heating device 32-1 stops working and does not continuously generate heat, the inner rod 21-1 moves towards the far end, the working surface 32 is opened, and the tissue treatment process is finished once. When the working surface 32 needs to be rotated, the knob 23 is only required to be rotated, the knob 23 drives the shaft 21 to rotate, and the working surface 32 connected to the shaft 21 rotates accordingly. During the rotation, the rotor 43-1-1 can rotate synchronously with the shaft 21, so that the conductive connector 43-1 and the line 41 at the rear end of the shaft 21 are kept synchronous, and the wire breakage or the loosening of welding points or the heating of the connector, which may be caused by the twisting of the line 41, can be avoided. Thereby ensuring a stable power supply of the circuitry 400. Different tissue parts are sequentially selected, the trigger 11-1 is repeatedly pulled and released, the operation can be finished, and the operation in the operation process is very simple.

Meanwhile, in the clinical use process, because 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 temperature value set by the controller 42, the controller 42 adopts the modes of performing power-off processing on the line 41 or adjusting the current or voltage output by the power supply 500 through the data processing system 42-2, and the like, so as to achieve the control effect of reducing the working temperature of the working part 300, and effectively avoid the tissue accidental damage or the accidental damage of elements possibly caused by the electric heating device 32-1 being in a high-temperature state for a long time, the operation process is safer for a long time.

When the ultrasonic vibration heating device 32-2 is used for heating tissues, after the power supply 500 is switched on, the ultrasonic vibration rod 32-22 of the ultrasonic vibration heating device 32-2 is started to heat the tissues, and then the tissues can be ablated, cut or fused.

The heat energy cutter head comprises a first working part 301 and a second working part 302 which are matched with each other, wherein at least one working surface 31 is arranged on each of the first working part 301 and the second working part 302, and a heating device 32 is arranged on at least one working surface 31; and a tissue pushing mechanism 33 is connected to a 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, a shaft assembly 200, a working portion 300, circuitry 400 and a power source 500. The working portion 300 includes the thermal head 3. During clinical use, in the process of closing the working surface 31, 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, so as to prevent the tissue from being gathered at the bottom of the first working part 301 and/or the second working part 302, thereby avoiding the formation of operation dead corners in the tissue ablation, cutting or fusion process, and improving the efficiency of the tissue ablation, cutting or fusion process in the clinical use process.

Drawings

FIG. 1 is a perspective view of the working surface of the tissue ablation, cutting and fusion system of the present invention when open.

Fig. 1-1 is an enlarged view at a of fig. 1.

Fig. 1-2 is a sectional view B-B of fig. 1-1.

Fig. 1-3 are left side views of the work surface of fig. 1 in a closed position.

Fig. 1-4 are cross-sectional views C-C of fig. 1-3.

Fig. 1-5 are enlarged views at D of fig. 1-4.

Fig. 1-6 are cross-sectional views E-E of fig. 1-4.

FIGS. 1-7 are schematic structural views of the trigger assembly of the tissue ablation, cutting and fusion system of the present invention.

Fig. 1-8 are perspective views of a first working portion with a tissue pushing mechanism.

Fig. 1-9 are cross-sectional views F-F of fig. 1-8.

FIGS. 1-10 are schematic structural views of a tissue ablation, cutting and fusion system of the present invention with a host power supply.

FIGS. 1-11 are schematic views of the operative state of the tissue ablation, cutting and fusion system of the present invention.

Fig. 1-12 are enlarged views at G of fig. 1-11.

FIG. 2 is a schematic view of a wedge-shaped protrusion and a pair of matching protrusions of the wedge-shaped protrusion.

FIG. 3 is a schematic view of a mating pair of wedge-shaped protrusions versus arc-shaped protrusions.

FIG. 4 is a schematic view of a mating pair of projections of the arcuate projection pair arcuate projections.

FIG. 5 is a schematic view of a matched pair of protrusions of a convex protrusion pair and an arc protrusion.

FIG. 6 is a schematic cross-sectional view of the tissue ablation, cutting and fusion system of the present invention with an elastomeric electrical interface.

Fig. 6-1 is an enlarged view at H of fig. 6.

Fig. 7 is a perspective view of a tissue ablation, cutting and fusion system of the present invention with a battery and battery pack.

FIG. 8 is a schematic structural view of an ultrasonic heating tissue ablation, cutting and fusion system of the present invention with a host power supply.

Fig. 8-1 is an enlarged view at I of fig. 8.

In the above figures:

100 is a handle assembly, 200 is a shaft 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 prompting system, 700 is a smoke evacuation system, 800 is a water supply/drainage system, 900 is a tissue ablation, cutting and fusion system of the invention, 3 is a thermal energy cutter head of the invention, and 9 is a tissue or organ.

Alpha is the included angle between the pushing surface and the working surface of the first working part, and beta is the included angle between the pushing surface and the axis of the outer rod.

On the handle assembly:

the device comprises a trigger assembly 11, a gear adjusting button 12, a shaft connecting mechanism 13, a shell 14, a fixing mechanism 15, a resetting mechanism 16 and a force limiting mechanism 17.

11-1 is a trigger, 11-2 is a rocker arm, and 11-3 is a sliding block; 11-1-1 is a trigger rotating shaft, 11-1-2 is a rocker driving shaft, 11-1-3 is a trigger part, 11-2-1 is a rocker fulcrum, 11-2-2 is a moving chute, 11-2-3 is a push block clamping groove, 11-3-1 is a moving push block, 11-3-2 is a sliding convex step, and 11-3-3 is a working boss.

12-1 is a cutting gear, 12-2 is a fusion gear, and 12-3 is a lever mechanism.

14-1 is a handle.

15-1 is a positioning chute.

And 17-1 is a spring force limiting mechanism.

On the shaft assembly:

21 is a shaft, 22 is a connecting component, and 23 is a knob.

21-1 is an inner rod, 21-2 is an outer rod, 21-3 is an inner insulating heat-resistant sleeve, and 21-6 is an insulating heat-shrinkable sleeve.

The working part is provided with:

30 is a bulge, 31 is a working surface, 32 is a heating device, 33 is a tissue pushing and extruding mechanism, and 34 is a support frame; 3-10 is a rocker, 30-1 is a first bulge, 30-2 is a second bulge, 31-1 is an anti-skid 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 vibrating rod, and 32-23 is an ultrasonic fusion cutting system.

Reference numeral 301 denotes a first working unit, and 302 denotes a second working unit.

On the circuit system:

41 is a line, 42 is a controller, 43 is an electrical interface device, and 431 is an elastic electrical interface device.

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, and 43-3 is an electrical interface; 43-1-1 is rotor, 43-1-2 is stator; brushes 43-11.

On the temperature control assembly:

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

On the power supply:

the numeral 51 denotes a battery module, numeral 52 denotes a battery pack module, and numeral 53 denotes a main unit.

On the prompt system:

numeral 61 denotes a sound indicator, numeral 62 denotes a light indicator, and numeral 63 denotes an image indicator.

On the system of discharging fume:

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

On the water supply/drainage system:

81 is a water outlet, 82 is a water outlet pipe, and 83 is a water inlet.

Detailed Description

Example 1: the invention relates to a heat energy cutter head

Referring to fig. 1 to 5, a thermal energy tool bit of the present embodiment includes a pair of first and second working

portions

301 and 302 matched with each other; the first working part 301 and the second working part 302 are respectively 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 cutter head 3 to the working surface 31.

Referring to FIGS. 1-8 and 1-9, in this embodiment, the tissue pushing mechanism 33 is disposed at the proximal end of the first working portion 301 and is connected to the outer shaft 21-2 of the shaft assembly 200; the pushing surface 33-1 of the tissue pushing mechanism 33 and the axis of the outer rod 21-2 form an angle beta.

Referring to fig. 1-11 and 1-12, in this embodiment, the angle β is smaller than 90 ° to ensure that the combined force direction of the tissue is upward, so that the tissue can be pushed toward the upper portion of the working surface 31, thereby avoiding the tissue from accumulating at the bottom of the first and second working

portions

301 and 302.

The tissue pushing mechanism 33 may also be disposed on the second working portion 302, so that 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 portion 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 be a combined structure disposed on the first working portion 301 and the second working portion 302, which is not specifically illustrated herein by the applicant, without departing from the scope of the present application.

In this embodiment, the pushing surface 33-1 is a blunt smooth surface. Due to the design of the blunt smooth surface, the tissue can be effectively prevented from being accidentally cut by the sharp edges and corners of the thrust extrusion surface 33-1 in the closing process, and accidental injury to the tissue is avoided. The pushing surface 33-1 may be a plane, or a convex arc surface, or a concave arc surface, but the pushing surface 33-1 is at an angle with the axial direction of the outer rod 21-2, which is not illustrated herein by the applicant.

Further, the α angle is less than 180 °.

In this embodiment, the tissue pushing mechanism 33 and the first working portion 301 are integrally manufactured, so that the assembling process is more convenient, the manufacturing process is simple, and the cost is lower. Of course, the tissue pushing mechanism 33 can be separately manufactured and then connected to the first working portion 301 or the second working portion 302, which is not specifically illustrated by the applicant herein, without departing from the scope of the present application.

In this embodiment, the working surface 31 of the first working portion 301 and the working surface 31 of the second working portion 302 both include protrusions 30 capable of pushing out the liquid in the tissue. 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 are matched with each other. The matching projections 30 provide a better pressing action on the liquid when the working surface 31 is closed. When the working surface 31 is closed, the protrusion 30 can rapidly extrude 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 starts to heat up, and as the interference of the liquid in the tissue to the working process is reduced, the protein in the working area is rapidly aggregated and modified, and the tissue ablation, cutting and fusion effects are better.

Referring to fig. 2 to 5, in the present embodiment, the protrusion 30 is an arc protrusion to an arc protrusion. The mutually matched bulges can also be either wedge-shaped bulges to arc-shaped bulges, or wedge-shaped bulges to wedge-shaped bulges, or arc-shaped bulges to planes, or wedge-shaped bulges to planes, or convex-shaped bulges to convex-shaped bulges, or convex-shaped bulges to planes. The applicant only lists the above several mutually matching convex shapes, and those skilled in the art can design different shapes as required without departing from the scope of the present application.

In this embodiment, one of a pair of the protrusions 30 that match each other is constituted by the heating device 32.

In this embodiment, the heating device 32 is an electric heating device 32-1. In practical application, different heating modes can be selected according to requirements, for example, an ultrasonic heating mode can also be selected, for example, an ultrasonic vibration heating device 32-2 which heats by adopting the ultrasonic vibration rod 32-22 is adopted, and refer to fig. 8 and 8-1. Or those skilled in the art can design the heating device in different ways according to the needs without departing from the scope of the present application.

The closing mode of the working surface 31 can adopt a translational closing mode. Referring to fig. 1-1 to fig. 1-6, the tissue pushing mechanism 33 is connected to the proximal end of the first working portion 301, the tissue pushing mechanism 33 is connected to the outer rod 21-2 of the shaft assembly 200, and is fixed together by means of usually embedding and welding, the first working portion 301 is provided with the protrusion 30 made of insulating material, and the protrusion 30 is embedded in the first working portion 301 to form a first protrusion 30-1; the proximal end of the second working part 302 is connected with an inner rod 21-1 of the shaft assembly 200, and is usually connected and fixed together in an embedding and welding manner, a conductive core rod 41-1 serving as a positive electrode is arranged in the inner rod 21-1, and an inner insulating heat-resistant sleeve 21-3 is arranged 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 far end of the conductive core rod 41-1, the electric heating body extends out of the far end of the second working part 302 and then is tightly attached to the inner insulating heat-resistant sleeve 21-3 to be wound back, the other end of the electric heating body 32-10 is connected to the far end of the inner rod 21-1, the inner rod 21-1 is used as a negative pole and is connected with the power supply 500 to form an electric loop, and the connection mode is usually connected and fixed together in an embedding or welding mode; the convex electric heating body 32-10 arranged on the working surface 31 of the inner insulating heat-resistant sleeve 21-3 of the second working part 302 and the convex arc surface of the inner insulating heat-resistant sleeve 21-3 form a second bulge 30-2 on the second working part 302, and the first bulge 30-1 and the second bulge 30-2 form a pair of mutually matched bulges 30; a middle insulating heat-resistant sleeve 21-4 is arranged between the middle pipe 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 retraction 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 working surfaces 31 are closed by translating one of the working surfaces 31 towards the other 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, the tissue is not gathered at the lower end of the working surface 31, the two working surfaces 31 can be completely jointed at the same time, and the working efficiency is very high.

In this translational design, the working surfaces 31 are closed by translating one of the working surfaces 31 towards the other working surface 31. During operation, two working faces 31 can be completely attached at the same time, and the working efficiency is very high.

Referring to fig. 1-1, in this embodiment, in order to ensure the strength of the second working portion 302, the support frame 34 is disposed on the outer side of the second working portion 302, the support frame 34 is L-shaped, the distal end of the support frame is fixed on the outer side of the inner insulating heat-resistant sleeve 21-3, and the proximal end of the support frame is connected to the distal end of the inner rod 21-1.

The outer rod 21-2 can be also provided with an insulating heat-shrinkable sleeve 21-6 capable of reducing the friction coefficient. The insulating heat-shrinkable sleeve 21-6 not only can provide better insulation protection, but also can reduce the friction coefficient of the outer rod 21-2, so that the movement resistance is smaller when the outer rod enters or exits the instrument, and the movement is smoother in the operation process.

In this embodiment, when the tissue pushing mechanism 33 is disposed at the proximal end of the first working portion 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 portion 302, and after the closing process, 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, so as to be ablated, cut or fused completely, and the clinical use efficiency is higher.

Example 2: electrical heating type tissue ablation, cutting and fusion system of the present invention

Referring to fig. 1-6, the tissue ablation, cutting and fusion system of this embodiment includes a thermal blade 3 as described in embodiment 1.

The tissue ablation, cutting and fusion system 900 of this embodiment includes a handle assembly 100, a shaft assembly 200, a working portion 300, a circuit system 400, a power source 500, a reminder system 600, and a smoke evacuation system 700.

Referring to fig. 1-7, the handle assembly 100 includes a trigger assembly 11, a shift position adjustment button 12, a shaft connecting 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 adjusting button 12 and the shaft connecting mechanism 13 are arranged on the housing 14.

The shaft assembly 200 includes a shaft 21, a coupling assembly 22, and a knob 23.

The working part 300 comprises the thermal energy tool bit 3, and a heating device 32 is arranged on at least one working surface 31 of the thermal energy tool bit 3. In this embodiment, the heating device 32 is an electric heating device 32-1 that is heated by the electric heating element 32-10, and refer to fig. 1-1 to fig. 1-6.

Referring to fig. 1-4, the circuitry 400 includes circuitry 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.

In this embodiment, the controller 42 includes a trigger switch 42-1; movement of the trigger assembly 11 can turn the trigger development 42-1 on or off.

The proximal end of the shaft assembly 200 is connected to the handle assembly 100 through the shaft connecting mechanism 13; the distal end of the shaft assembly 200 is connected to the working portion 300; the electric heating device 32-1 is connected to the power supply 500 through the circuit system 400.

Referring to FIGS. 1-7, the trigger assembly 11 includes a trigger 11-1, a rocker arm 11-2, and a slide 11-3; the trigger 11-1 is provided with a trigger rotating shaft 11-1-1 and a rocker arm driving shaft 11-1-2; the rocker arm 11-2 comprises a rocker arm fulcrum 11-2-1, a moving sliding groove 11-2-2 and a push block clamping groove 11-2-3; the sliding 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 rotating shaft 11-1-1 is connected with the fixing mechanism 15 and fixed on the shell 14; one end of the rocker arm driving shaft 11-1-2 is connected to the trigger 11-1, and the other end of the rocker arm driving shaft is embedded in the motion chute 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 shell 14; the moving push block 11-3-1 is embedded in the push block clamping groove 11-2-3, and the sliding convex step 11-3-2 is embedded in the positioning sliding groove 15-1 of the fixing mechanism 15 and connected with the fixing mechanism 15; pulling the trigger 11-1, wherein the trigger 11-1 rotates around the trigger rotating shaft 11-1-1 to drive the rocker arm driving shaft 11-1-2 to reciprocate along the movement chute 11-2-2, so as to push the rocker arm 11-2 to reciprocally swing around the rocker arm fulcrum 11-2-1; the reciprocating swing of the rocker arm 11-2 pushes the moving push block 11-3-1 embedded in the push block slot 11-2-3 so as to drive the slide block to linearly move back and forth along the positioning chute 15-1, thereby realizing the closing and opening of the working surface 31 of the working part 300.

In this embodiment, the gear adjusting button 12 includes a cutting gear 12-1 and a fusion gear 12-2; the cutting rail 12-1 and the fusion rail 12-2 are linked together by a lever mechanism 12-3 such that the cutting rail 12-1 and the fusion rail 12-2 cannot be depressed simultaneously. The cutting gear 12-1 and the fusion gear 12-2 can not be pressed down simultaneously, so that the phenomenon of misoperation can not occur in the clinical use process.

In this embodiment, handle assembly 100 includes a reset mechanism 16. In this embodiment, the return 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 rotating shaft 11-1-1, the spring mechanism 16-2 is arranged at the near end of the positioning sliding groove 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 towards the near end, the spring mechanism 16-2 is compressed and deformed, when the trigger 11-1 is loosened, the inner rod 21-1 moves towards the far end under the action of the torsion spring mechanism 16-1 and the spring mechanism 16-2, and the trigger 11-1 automatically resets.

Those skilled in the art may design various reducing mechanisms as desired, and install 1 or more reducing mechanisms 16 at different locations of the instrument as desired without departing from the scope of the present application.

Referring to fig. 1-4, in 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 is activated, the maximum working pressure applied to the working part 300 after an operator pulls the trigger 11-1 is constant, and the maximum working pressure can be limited below 100N in the processes of ablation, cutting and fusion of soft tissues. Of course, the person skilled in the art can set the limit value of the maximum working pressure defined by the force-limiting mechanism 17 as desired without departing from the scope of protection of the present application.

In this embodiment, the trigger 11-1 moves towards the handle 14-1 of the housing 14 until the force limiting mechanism 17 acts, the trigger switch 42-1 cannot be activated, and when the trigger switch 42-1 is turned on, the gear adjusting button 12 cannot be closed, so as to turn on the circuit system 400, and thus the tissue ablation, cutting and fusion system 900 performs tissue ablation, cutting or fusion under a set working pressure. Because only when the force limiting mechanism 17 acts, the trigger switch 42-1 can be started, so that the working pressure applied to the tissue in the operation process of a doctor is ensured to be constant, the difference of the operation effect caused by different working pressures applied to the tissue by different operators is avoided, the operation effect in the operation process is more stable, meanwhile, the potential safety hazard possibly caused by continuous heating of the electric heating device 32-1 in a non-working state is effectively avoided, and the use process is safer and more reliable. Of course, those skilled in the art can design the on state of the trigger switch 42-1 to be different according to the requirement without departing from the scope of the present application.

In this embodiment, the force limiting mechanism 17 is a spring force limiting mechanism 17-1, the spring force limiting mechanism 17-1 is disposed at a proximal end of a working boss 11-3-3 of the slider 11-3, when the inner rod 21-1 moves towards 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 elastically deforms to limit the magnitude of the working pressure.

Those skilled in the art can also design various other types of force limiting mechanisms, such as an elastic body force limiting mechanism, a pressure spring force limiting mechanism, etc., without departing from the scope of the present application.

In clinical use, it is often necessary to rotate the working surface 31 to a proper position according to the location of the tissue to be treated, and therefore, in this embodiment, the shaft assembly 200 includes the knob 23, and the knob 23 can drive the shaft 21 to rotate.

Referring to fig. 6 and 6-1, in the present embodiment, the electrical interface device 43 is an elastic electrical interface device 431, and the elastic electrical interface device 431 includes a conductive contact 43-1, an elastic conductive mechanism 43-2 and an electrical interface 43-3. One end of the conductive joint 43-1 is connected with the electric heating device 32-1 through the line 41, and the other end is connected with 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.

Because 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, the conductive joint 43-1 and the line 41 at the rear end of the shaft 21 are kept synchronous, and the wire breakage or the loosening of welding points or the heating of joints, which may be caused by the twisting of the line 41, can be avoided.

The elastic conductive mechanism 43-2 is a conductive mechanism that can be elastically deformed under an external force while maintaining a circuit in a smooth state. The elastic conductive mechanism 43-2 can be elastically deformed under the action of an external force, so that when the shaft 21 translates proximally, the shaft 21 applies pressure to the elastic conductive mechanism 43-2, the elastic conductive mechanism 43-2 is compressively deformed, when the shaft translates distally, the pressure applied to the elastic conductive mechanism 43-2 by the shaft 21 is gradually released, and under the action of an elastic restoring force, the connection state of the conductive joint 43-1 and the shaft 21 can be continuously maintained, and the stable power supply of the circuit system 400 can be maintained. In the movement period, the elastic conductive mechanism 43-2 is elastically deformed to perform reciprocating action, so that the problem of fatigue fracture or welding point loosening or joint heating caused by continuous expansion and contraction of the electric wire in the conventional electric wire connection process is solved. Not only keeps the good controllability of the instrument, but also improves the reliability of the circuit.

In this embodiment, the elastic conductive mechanism 43-2 is a coil spring mechanism. The elastic conductive mechanism 43-2 may be a tower spring mechanism or a spring mechanism, which is not specifically mentioned herein. Those skilled in the art will also design the elastic conductive mechanism 43-2 to be an elastic structure such as an elastomer structure as required without departing from the scope of the present invention.

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 500 Hz.

The output voltage of the power supply 500 is a safe voltage less than 24V, and even if accidental phenomena such as electric leakage occur in the use process, the human body cannot be accidentally injured.

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

The direct current 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 interactive change of the high level and the low level, keeps the periodic change of the states of the electric heating device 32-1 of power-on heating and power-off proper temperature reduction, ensures that the temperature of the part of the heating device contacted with the tissue or organ 9 is kept in a stable range and cannot be continuously increased in the process of continuously conducting heat to the deep part of the tissue or organ 9, effectively avoids the accidental injury of the tissue or organ 9 caused by overhigh temperature, and is safer and more reliable in the clinical use process.

The power supply 500 is typically a low frequency dc pulsed voltage with a frequency less than 500Hz, depending on the thermal conductivity of the tissue and organs. On one hand, the low-frequency pulse can enlarge the range selection of the duration time of high level and low level, and the sufficient heat conduction time is ensured, and meanwhile, the heating device 32 is also provided with enough cooling time, so that the temperature of the heating device 32 can be controlled within a safe temperature range. Meanwhile, the low-frequency pulse can better avoid the electromagnetic interference possibly caused by the electromagnetic pulse to peripheral equipment in the operation process of the instrument, and the electromagnetic compatibility of the instrument is better.

In this embodiment, the duty cycle of the dc pulse voltage output by the power supply 500 can be adjusted according to the thermal conductivity of the tissue or organ 9 to be ablated, cut or fused.

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

Referring to fig. 1-8, in the present embodiment, the power supply 500 is a main unit 53 capable of stably supplying power for a long time, and is particularly suitable for a large operation with a long operation time.

Referring to fig. 7, the power supply 500 may also be a battery module 51 or a battery module 52, and the battery module 51 or the battery module 52 has a small volume and a light weight, is suitable for being carried outdoors, has a low requirement on the electricity environment, and is safer for low-voltage power supply. The user can select different power supplies 500 according to different use environments and different use requirements.

In this embodiment, the specific circuit connection manner is as follows:

a positive electrode line: the positive pole of the electric heating device 32-1 is connected with a circuit 41 arranged in the rod core of the inner rod 21-1, in order to enhance the strength of the inner rod 21-1 in the translation and clamping processes, the part of the circuit 41 is arranged into a rigid conductive core rod 41-1, an inner insulating heat-resistant sleeve 21-3 is arranged between the conductive core rod 41-1 and the inner rod 21-1, one end of the conductive core rod 41-1 is connected with the positive pole of the electric heating device 32-1, the other end of the conductive core rod is connected with the positive pole of the rotor 43-1-1, the other end of the positive pole of the rotor 43-1-1 is connected with the positive pole of the stator 43-1-2 in a brush mode, and the other end of the positive pole of the stator 43-1-2 is connected with the positive pole of the elastic conductive mechanism 43-2, the other end of the positive pole of the elastic conductive mechanism 43-2 is connected with the positive pole of the electrical interface 43-3, and is connected with the positive pole of the power supply 500 through the electrical interface 43-3.

Negative electrode circuit: the negative electrode 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 electrode of the rotor 43-1-1 through the line 41, the other end of the negative electrode of the rotor 43-1-1 is connected to the negative electrode of the stator 43-1-2 through a brush, the other end of the negative electrode of the stator 43-1-2 is connected to the negative electrode of the elastic conductive mechanism 43-2, the other end of the negative electrode of the elastic conductive mechanism 43-2 is connected to the negative electrode of the electrical interface 43-3, and is connected to the negative electrode of the power supply 500 through the electrical interface 43-3.

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 into the rotor 43-1-1 through the positive electrode of the rotor 43-1-1 after flowing out through the stator 43-1-2, flows into the conductive core rod 41-1 from the proximal end of the conductive core rod 41-1 after flowing out from the rotor 43-1-1, flows into the electrical heating device 32-1 from the positive electrode of the electrical hot water 32-10 of the electrical heating device 32-1 after flowing through the conductive core rod 41-1, drives the electrical heating device 32-1 to generate heat, and then flows out from the negative electrode of the electrical heating device 32-1 and enters the distal end of the inner rod 21-1, after flowing through the inner rod 21-1, the current flows out of the proximal end of the inner rod 21-1, enters the negative electrode of the rotor 43-1-1, flows out of the negative electrode of the rotor 43-1-1, enters the negative electrode of the stator 43-1-2, flows through the stator 43-1-2, enters the elastic conducting mechanism 43-2, flows through the elastic conducting mechanism 43-2, flows into the electrical interface 43-3 from the distal end of the elastic conducting mechanism 43-2, and flows into the negative electrode of the power supply 500 through the electrical interface 43-3.

In this embodiment, the tissue ablation, cutting and fusion system 900 further comprises a temperature control assembly 401; the temperature control assembly 401 comprises a temperature acquisition system 40-1 and a data transmission system 40-2; the temperature data collected by the temperature collection system 40-1 can be transmitted to the controller 42 via the data transmission system 40-2. The temperature acquisition system 40-1 may continuously acquire operating temperature data, and transmit the acquired temperature data to the controller 42 via the data transmission system 40-2, the data processing system 42-2 in the controller 42 may monitor the collected temperature in real time, when the collected temperature value exceeds the limit temperature value set by the controller 42, the controller 42 performs a power-off process on the line 41, or the data processing system 42-2 adjusts the current or voltage output by the power supply 500, so as to achieve the control effect of reducing the working temperature of the working part 300, effectively avoid the accidental tissue damage or the accidental element damage caused by the long-term high-temperature state of the electric heating device 32-1, and ensure that the electric heating device is safer during the long-term continuous working process.

Referring to fig. 1-10 and 1-11, the tissue ablation, cutting and fusion system of the present embodiment includes a cue system 600. The prompt system 600 can prompt the operator about the use state of the apparatus according to the need, such as prompting different working states with different sounds, prompting the state of the power supply with different lights, prompting different working positions with different patterns, etc.

In the present embodiment, the applicant shows three prompting devices, namely, an audio prompting device 61, a light prompting device 62, and an image prompting device 63 in the prompting system 600. It should be understood that various other configurations of the reminder system can be devised as required by those skilled in the art without departing from the scope of the present application.

Referring to fig. 1-4, in the present embodiment, the tissue ablation, cutting and fusion system 900 includes a smoke evacuation system 700. The fume extraction system 700 includes a fume outlet 71, a fume extraction duct 72, and a fume inlet 73. The smoke outlet 71 of the smoke exhaust system 700 can be connected with a medical negative pressure source, smoke generated in the operation process is timely extracted out of the body, the operation visual field is clear, and the operation process is safer and more reliable.

Referring to fig. 6, the tissue ablation, cutting and fusion system of the present invention may also include a water delivery/drainage system 800. The water supply/drainage system 800 includes a water outlet 81, a water drainage 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 supply pipe. In the operation process, a doctor can inject normal saline or other solvents into the operation position through the water supply/drainage system 800 according to the operation requirement, and can timely discharge blood or sewage at the operation position out of the body through the water supply/drainage system 800, so that the smooth operation of the operation process is ensured. Meanwhile, the water supply/drainage system 800 can also be used as the smoke exhaust system 700 to exhaust smoke generated in the operation process out of the body in time, so as to ensure the clear field of view of the operation.

In clinical use, the power supply 500 is connected with the circuit system 400 through the electrical interface 43-3, a power switch is turned on, the trigger 11-1 is pulled to move towards the grip 14-1 to drive the inner rod 21-1 to move towards the proximal end, the pushing surface 33-1 pushes the tissue or organ 9 towards the upper end of the working surface 31 under the action of the tissue pushing mechanism 33 until the working surface 31 is closed, the working part 300 clamps the tissue to be treated, the bulge 30 on the working surface 31 pushes out the liquid in the tissue, the trigger 11-1 is continuously pulled until the force limiting mechanism 17 acts to switch on the trigger switch 42-1, the cutting gear 12-1 or the fusion gear 12-2 of the gear adjusting button 12 is selected to be pressed according to the surgical condition, the gear adjustment button 12 is connected to the controller 42, at this time, the circuit system 400 connects the power supply 500 to the electric heating device 32-1, the electric heating device 32-1 starts to generate heat, and in this process, the elastic conductive mechanism 43-2 elastically deforms under the thrust of the inner rod 21, so as to maintain stable power supply of the circuit system 400. As the bulge 30 on the working surface 31 extrudes the liquid in the tissue, the interference of the liquid is eliminated, the protein in the tissue of the working area can be quickly agglutinated and modified under the action of temperature, and the ablation, the cutting and the fusion of the tissue are realized. In the process of closing the working surface 31, 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, so as to prevent the tissue from being gathered at the bottom of the first working part 301 and/or the second working part 302, avoid causing dead corners in the process of tissue ablation, cutting or fusion, and have higher efficiency in the process of tissue ablation, cutting or fusion in the clinical use.

In this embodiment, the trigger 11-1 moves toward the grip 14-1 of the housing 14 until the force limiting mechanism 17 acts, the trigger portion 11-1-3 does not touch the trigger switch 42-1, and the trigger switch 42-1 is turned on; when the trigger 11-1 moves away from the grip 14-1 of the housing 14, the trigger part 11-1-3 is disengaged from the trigger switch 42-1, and the trigger switch 42-1 is turned off. The trigger switch 42-1 can be started only when the force limiting mechanism 17 acts, so that the tissue ablation, cutting or fusion system can perform tissue ablation, cutting or fusion under the set working pressure, the operation effect is more stable, accidental injury possibly caused by misoperation is effectively prevented, and clinical effect differences of blood vessel closure, tissue fusion, cutting and the like caused by different clamping forces used by different surgeons are more safe and effective, namely the tissue ablation, cutting and fusion system can be started to perform tissue ablation, cutting and fusion only under the constant clamping force, and the difference of using effects caused by different forces of an operator is avoided.

In this embodiment, since the cutter head 3 of the tissue ablation, cutting and fusion system 900 includes the tissue pushing mechanism 33, during clinical use, in the process of closing the working surface 31, the tissue pushing mechanism 33 can push the tissue toward the upper portion of the working surface 31 of the first working portion 301 and/or the second working portion 302, so as to prevent the tissue from gathering at the bottom of the first working portion 301 and/or the second working portion 302, thereby avoiding the operation dead angle of the tissue ablation, cutting or fusion process, and during clinical use, the efficiency of the tissue ablation, cutting or fusion process is higher.

Example 3: ultrasonic heating type tissue ablation, cutting and fusion system of the present invention

Referring to fig. 8 and 8-1, the present embodiment is different from embodiment 2 in that the heating device 32 is an ultrasonic vibration heat-generating device 32-2 in the present embodiment.

The tissue ablation, cutting and fusion system 900 of this embodiment includes a handle assembly 100, a shaft assembly 200, a working portion 300, a circuit system 400, a power source 500, a reminder system 600, and a smoke evacuation system 700. The working portion 300 includes a first working portion 301 and a second working portion 302.

The second working portion 302 is provided with a heating device 32. In this embodiment, the heating device 32 is the ultrasonic vibration heat-generating device 32-2. The ultrasonic vibration heating device 32-2 comprises an ultrasonic transducer 32-21, an ultrasonic vibration rod 32-22 and an ultrasonic fusion cutting system 32-23. The ultrasonic transducers 32-21 are arranged in the shell 14, the proximal ends of the ultrasonic vibration rods 32-22 are connected to the ultrasonic transducers 32-21, and the distal ends form the second working part 302.

The ultrasonic transducers 32-21 are connected to the ultrasonic fusion cutting system 32-23 through the lines 41. In this embodiment, the ultrasonic fusion cutting system 32-23 is mounted with the main body 53 of the power supply 500. In practice, the ultrasonic fusion cutting system 32-23 can also be provided separately.

When the ultrasonic fusion cutting system is used clinically, after the power supply 500 is switched on, the ultrasonic fusion cutting system 32-23 works, the ultrasonic transducer 32-21 generates ultrasonic vibration, 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 vibration to heat tissues, so that the tissues can be ablated, cut or fused.

It should be noted that structures disclosed and illustrated herein may be replaced by other structures having the same effect, and the described embodiments of the invention are not the only structures for carrying out the invention. Although preferred embodiments of the present invention have been shown and described herein, it will be apparent to those skilled in the art that these embodiments are by way of example only and that numerous changes, modifications and substitutions may be made without departing from the invention by those skilled in the art, and it is intended that the scope of the invention be defined by the spirit and scope of the appended claims.

Claims

1. A thermal energy tool bit, characterized in that:

A. the heat energy cutter head (3) comprises a pair of a first working part (301) and a second working part (302) which are matched with each other;

B. the first working part (301) and the second working part (302) are respectively 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 near 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 cutter head (3) to the working surface (31).

2. A thermal energy head according to claim 1, wherein: the tissue pushing mechanism (33) is arranged at the proximal end of the first working part (301) and is connected with an outer rod (21-2) of the shaft assembly (200); the pushing surface (33-1) of the tissue pushing mechanism (33) and the axis of the outer rod (21-2) form an angle beta.

3. A thermal energy head according to claim 2, wherein: the beta angle is less than 90 deg..

4. A thermal energy head according to claim 1, wherein: the pushing surface (33-1) is a blunt smooth surface.

5. A thermal energy head according to claim 2, wherein: an alpha angle is formed between the pushing surface (33-1) and the working surface (31) of the first working part (301).

6. A thermal energy head according to claim 5, wherein: the alpha angle is less than 180 deg..

7. A thermal energy head according to claim 2, wherein: the tissue pushing mechanism (33) is integrally manufactured with the first working portion (301).

8. A thermal energy head according to claim 1, wherein: at least one of the working surfaces (31) has projections (30) thereon which are capable of pushing fluid out of the tissue.

9. A thermal energy head according to claim 8, wherein: the working surface (31) of the first working part (301) and the working surface (31) of the second working part (302) both comprise protrusions (30) which can extrude liquid in the tissue outwards.

10. A thermal energy head according to claim 9, wherein: 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) are matched with each other.

11. A thermal energy head according to claim 8, wherein: the heating means (32) may be at least one of a pair of mutually matching protrusions (30).

12. A thermal energy head according to claim 1, wherein: the heating device (32) can be an electric heating device (32-1) or an ultrasonic vibration heating device (32-2).

13. A thermal energy head according to claim 12, wherein: the electric heating device (32-1) adopts a direct current pulse mode for heating.

14. A thermal energy head according to claim 1, wherein: the tissue pushing mechanism (33) is connected to the proximal end of the first working part (301), the tissue pushing mechanism (33) is connected with an outer rod (21-2) of the shaft assembly (200), the first working part (301) is provided with the bulge (30) made of insulating and heat-insulating materials, and the bulge (30) is embedded in the first working part (301) to form a first bulge (30-1); the near end of the second working part (302) is connected with an inner rod (21-1) of a shaft assembly (200), a conductive core rod (41-1) serving as a positive electrode is arranged in the inner rod (21-1), and an inner insulation heat-resistant sleeve (21-3) is arranged 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 with the far end of the conductive core rod (41-1), the electric heating body extends out of the far end of the second working part (302) and then is tightly attached to the inner insulating heat-resistant sleeve (21-3) to be wound back, the other end of the electric heating body (32-10) is connected with the far end of the inner rod (21-1), and the inner rod (21-1) is used as a negative pole and is connected with a power supply (500) to form an electric circuit; the convex electric heating body (32-10) arranged on the working surface (31) of the inner insulating heat-resistant sleeve (21-3) of the second working part (302) and the convex cambered surface of the inner insulating heat-resistant sleeve (21-3) form 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 mutually matched protrusions (30); the outer rod (21-2) is movably arranged on the inner rod (21-1), and the extension or retraction of the inner rod (21-1) can control the opening or closing between the second working part (302) and the first working part (301).

15. A thermal energy head according to claim 2, wherein: the outer rod (21-2) can also be provided with an insulating heat-shrinkable sleeve (21-6) capable of reducing the friction coefficient.

16. Tissue ablation, cutting and fusion system, its characterized in that: the tissue ablation, cutting and fusion system (900) comprises the thermal blade (3) of claim 1.

17. The tissue ablation, cutting and fusion system of claim 16, wherein:

A. the tissue ablation, cutting and fusion system (900) comprises a handle assembly (100), a shaft assembly (200), a working portion (300), a circuit system (400) and a power source (500):

B. the handle assembly (100) comprises a trigger assembly (11), a gear adjusting button (12), a shaft connecting mechanism (13) and a shell (14); the trigger assembly (11), the gear adjusting button (12) and the shaft connecting mechanism (13) are arranged on the shell (14);

C. the shaft assembly (200) comprises a shaft rod (21) and a connecting assembly (22);

D. the working part (300) comprises the heat energy tool bit (3), and a heating device (32) is arranged on at least one working surface (31) of the heat energy tool bit (3);

E. the circuit system (400) comprises a circuit (41), a controller (42) and an electrical interface device (43); -said circuitry (400) is connected to said power supply (500) via said electrical interface means (43);

F. the proximal end of the shaft assembly (200) is connected with the handle assembly (100) through the shaft connecting mechanism (13); the distal end of the shaft assembly (200) is connected with the working part (300); the heating device (32) is connected to the power supply (500) via the circuit system (400).

18. The tissue ablation, cutting and fusion system of claim 17, wherein: the controller (42) comprises a trigger switch (42-1); movement of the trigger assembly (11) may switch the trigger development (42-1) on or off.

19. The tissue ablation, cutting and fusion system of claim 18, wherein: the handle assembly (100) further comprises a fixing mechanism (15); the trigger assembly (11) is fixedly mounted on the housing (14) through the fixing mechanism (15).

20. The tissue ablation, cutting and fusion system of claim 19, wherein: the trigger assembly (11) comprises a trigger (11-1), a rocker arm (11-2) and a sliding block (11-3); the trigger (11-1) is provided with a trigger rotating shaft (11-1-1) and a rocker arm driving shaft (11-1-2); the rocker arm (11-2) comprises a rocker arm fulcrum (11-2-1), a moving chute (11-2-2) and a push block clamping groove (11-2-3); the sliding block (11-3) comprises a moving push block (11-3-1), a sliding convex step (11-3-2) and a working boss (11-3-3); the trigger rotating shaft (11-1-1) is connected with the fixing mechanism (15) and fixed on the shell (14); one end of the rocker arm driving shaft (11-1-2) is connected to the trigger (11-1), and the other end of the rocker arm driving shaft is embedded in the moving chute (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 arranged in the shell (14); the moving push block (11-3-1) is embedded in the push block clamping groove (11-2-3), and the sliding convex step (11-3-2) is embedded in a positioning sliding groove (15-1) of the fixing mechanism (15) and connected with the fixing mechanism (15); pulling the trigger (11-1), wherein the trigger (11-1) rotates around the trigger rotating shaft (11-1-1) to drive the rocker driving shaft (11-1-2) to reciprocate along the moving chute (11-2-2), so that the rocker (11-2) is pushed to reciprocate around the rocker fulcrum (11-2-1); the reciprocating swing of the rocker arm (11-2) pushes a moving push block (11-3-1) embedded in the push block clamping groove (11-2-3) to drive the sliding block to linearly move back and forth along the positioning sliding groove (15-1), so that the working surface (31) of the working part (300) is closed and opened.

21. The tissue ablation, cutting and fusion system of claim 18, wherein: the trigger (11-1) is provided with a trigger part (11-1-3); when the trigger (11-1) moves towards the direction of 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 switched on; when the trigger (11-1) moves away from the grip (14-1) of the shell (14) in the direction, the trigger part (11-1-3) is separated from the trigger switch (42-1), and the trigger switch (42-1) is disconnected.

22. The tissue ablation, cutting and fusion system of claim 17, wherein: the gear adjusting button (12) is connected with the controller (42) through the line (41).

23. The tissue ablation, cutting and fusion system of claim 17, wherein: the gear adjusting button (12) comprises a cutting gear (12-1) and a fusion gear (12-2); the cutting rail (12-1) and the fusion rail (12-2) are linked together by a lever mechanism (12-3) such that the cutting rail (12-1) and the fusion rail (12-2) cannot be pressed simultaneously.

24. The tissue ablation, cutting and fusion system of claim 17, wherein: the handle assembly (100) also includes a reset mechanism (16).

25. The tissue ablation, cutting and fusion system of claim 17, wherein: the handle assembly (100) further comprises a force limiting mechanism (17).

26. The tissue ablation, cutting and fusion system of claim 25, wherein: the trigger (11-1) moves towards the handle (14-1) of the shell (14) until the force limiting mechanism (17) acts, the trigger switch (42-1) can be started, the gear adjusting button (12) can be closed under the on state of the trigger switch (42-1), the circuit system (400) is switched on, and the tissue ablation, cutting or fusion system (900) performs tissue ablation, cutting or fusion under the set working pressure.

27. The tissue ablation, cutting and fusion system of claim 17, wherein: the shaft assembly (200) further comprises a knob (23); the knob (23) can drive the shaft rod (21) to rotate.

28. The tissue ablation, cutting and fusion system of claim 27, wherein: the shaft lever (21) comprises an inner lever (21-1) and an outer lever (21-2); the near end of the first working part (301) is connected with the outer rod (21-2), the near end of the second working part (302) is connected with the inner rod (21-1), and the knob (23) is rotated to drive the inner rod (21-1) and the outer rod (21-2) to rotate so as to drive the working surfaces (31) of the first working part (301) and the second working part (302) to rotate.

29. The tissue ablation, cutting and fusion system of claim 17, wherein: the electrical interface device (43) is an elastic electrical interface device (431), the elastic electrical interface device (431) comprises an electrically conductive joint (43-1), an elastic electrically conductive mechanism (43-2) and an electrical interface (43-3); one end of the conductive joint (43-1) is connected with the electric heating device (32) through the circuit (41), and the other end of the conductive joint is connected with the elastic conductive mechanism (43-2); the other end of the elastic conductive mechanism (43-2) is connected with the electrical interface (43-3), and the electrical interface (43-3) is connected with the power supply (500).

30. The tissue ablation, cutting and fusion system of claim 29, wherein: the conductive joint (43-1) comprises a rotor (43-1-1) and a stator (43-1-2); the rotor (43-1-1) is rotatable; the distal end of the rotor (43-1-1) and the proximal end of the shaft (21) are connected together, and the rotor (43-1-1) can synchronously rotate when the shaft (21) rotates; the proximal end of the stator (43-1-2) is connected with the distal end of the elastic conductive mechanism (43-2).

31. The tissue ablation, cutting and fusion system of claim 29, wherein: the elastic conductive mechanism (43-2) is a conductive mechanism which can be elastically deformed under the action of external force under the condition of keeping the circuit unobstructed.

32. The tissue ablation, cutting and fusion system of claim 17, wherein: the tissue ablation, cutting and fusion system (900) further comprises a temperature control assembly (401); the temperature control assembly (401) comprises a temperature acquisition system (40-1) and a data transmission system (40-2); the temperature data collected by the temperature collection system (40-1) can be transmitted to the controller (42) through the data transmission system (40-2).

33. The tissue ablation, cutting and fusion system of claim 17, wherein: the power supply (500) is a low voltage power supply with an output voltage less than 24V.

34. The tissue ablation, cutting and fusion system of claim 17, wherein: the power supply (500) outputs direct current pulse voltage.

35. A power supply for a tissue ablation, cutting and fusion system according to claim 34, wherein: the frequency of the direct current pulse voltage output by the power supply (500) is less than 500 Hz.

36. A power supply for a tissue ablation, cutting and fusion system according to claim 34, wherein: the duty cycle of the DC pulse voltage output by the power supply (500) is adjustable according to the difference of the thermal conductivity of the tissue or organ (9) to be ablated, cut or fused.

37. A power supply for a tissue ablation, cutting and fusion system according to claim 17, wherein: the power supply (500) is a battery module (51), or a battery pack module (52) or a host (53).

38. The tissue ablation, cutting and fusion system of claim 17, wherein: the tissue ablation, cutting and fusion system (900) further includes a cue system (600).

39. The tissue ablation, cutting and fusion system of claim 38, wherein: the prompting system (600) is a voice prompting device (61), a light prompting device (62) or an image prompting device (63).

40. The tissue ablation, cutting and fusion system of claim 17, wherein: the tissue ablation, cutting and fusion system (900) further comprises a smoke evacuation system (700); the smoke exhaust system (700) comprises a smoke outlet (71), a smoke exhaust pipe (72) and a smoke inlet (73).

41. The tissue ablation, cutting and fusion system of claim 17, wherein: the tissue ablation, cutting and fusion system (900) further comprises a water supply/drainage system (800); the water supply/drainage system (800) comprises a water outlet (81), a water drainage pipe (82) and a water inlet (83).