Radio frequency ablation forceps capable of automatically controlling temperature and temperature control method
By using the fiber probe of the fiber temperature sensor in the radio frequency ablation clamp to monitor the deep tissue temperature in real time and adjust the radio frequency energy field, the problem that traditional radio frequency ablation clamps is difficult to control the deep tissue temperature is solved, and the accuracy and safety of the radio frequency ablation process is achieved.
Patent Information
- Application Number
- CN202411450784.8
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- Filing Date
- 2024-10-17
- Publication Date
- 2025-01-03
- Estimated Expiration
- Not applicable · inactive patent
AI Technical Summary
Traditional RF ablation forceps have difficulty accurately detecting heat changes in deep tissue, especially in larger or deeper lesions, which lead to difficulty in temperature control.
An optical fiber probe using an optical fiber temperature sensor is inserted into the inside of the lesion tissue, the temperature is monitored in real time through Bragg grating or Raman scattering technology, and the radio frequency energy field is adjusted through the controller to achieve automatic temperature control.
Accurate detection and control of deep tissue temperature is achieved, tissue overheating is avoided, and the safety and accuracy of the radio frequency ablation process is ensured.
Smart Images
Figure CN119235444A_ABST
Abstract
Description
Technical Field
[0001] The present invention relates to the field of radiofrequency ablation forceps, and in particular to a radiofrequency ablation forceps with automatic temperature control and a temperature control method. Background Art
[0002] Traditional radiofrequency ablation forceps generally detect tissue temperature through temperature sensors located on the forceps head or electrode surface. This method usually indirectly infers the actual temperature of the tissue through the temperature change at the contact point between the radiofrequency ablation forceps and the diseased tissue. The limitation of this method is that it can only detect the temperature of the tissue surface and it is difficult to accurately reflect the heat changes in deep tissues, especially for larger or deeper lesion areas, where there may be a significant difference between the surface temperature and the internal temperature.
[0003] During the radiofrequency ablation procedure, local or deep overheating of the diseased tissue may occur, and the temperature sensors of traditional radiofrequency ablation forceps are difficult to detect this problem. Summary of the invention
[0004] The purpose of the present invention is to provide a radiofrequency ablation forceps with automatic temperature control and a temperature control method to solve the technical problem that the temperature sensor of the radiofrequency ablation forceps is difficult to detect the heat of deep tissue and it is difficult to control the radiofrequency ablation temperature for larger or deeper lesion areas.
[0005] In order to solve the above technical problems, the present invention specifically provides the following technical solutions:
[0006] A radiofrequency ablation forceps with automatic temperature control comprises a fixed clamp head and a movable clamp head, wherein the fixed clamp head and the movable clamp head are respectively provided with at least one electrode, wherein the electrode is connected to an external power source via a wire, wherein the external power source is used to input current into the electrode so as to generate a radiofrequency energy field between the fixed clamp head and the movable clamp head; wherein the fixed clamp head or the movable clamp head is connected to a fiber optic temperature sensor, wherein a fiber optic probe of the fiber optic temperature sensor can be inserted into a diseased tissue from between the fixed clamp head and the movable clamp head, wherein the fiber optic probe transmits a temperature signal to a controller, wherein the controller adjusts the current input from the external power source to the electrode in real time according to a preset temperature range so as to control the temperature of the diseased tissue.
[0007] Furthermore, the fixed clamp head is fixedly connected to the fixed clamp arm, the movable clamp head is fixedly connected to the movable clamp arm, the movable clamp arm is movably connected to the fixed clamp arm, and the movable clamp arm can move along the length direction of the fixed clamp arm.
[0008] Furthermore, the fiber optic probe is inserted into the diseased tissue through an electric puncture device, the electric puncture device is fixedly connected to the dynamic forceps head, the actuator of the electric puncture device is a hollow needle sheath, the fiber optic probe is fixed inside the needle sheath, and when the electric puncture device drives the needle sheath to penetrate into the diseased tissue, the fiber optic probe is inserted into the diseased tissue together with the needle sheath.
[0009] Furthermore, the needle sheath is made of memory metal. After the needle sheath carries the optical fiber probe and penetrates the diseased tissue, the needle sheath is heated by the patient's body temperature and deformed. The deformation of the needle sheath causes a gradually increasing gap to form between the needle sheath and the optical fiber probe. After the needle sheath retracts into the interior of the electric puncture device, the optical fiber probe stays inside the diseased tissue.
[0010] Furthermore, one side of the needle sheath is provided with an opening extending along the axial direction of the needle sheath, so that the cross section of the needle sheath forms a fan ring shape with a central angle greater than 180 degrees.
[0011] Furthermore, the electric puncture device includes a guide and a driver, both of which are connected to the movable forceps head, the guide is used to guide the puncture direction of the needle sheath, and the driver is used to drive the needle sheath to extend or retract.
[0012] Furthermore, the guide includes a guide rod and a slider, and limiters are arranged at both ends of the guide rod, the slider is slidably connected to the guide rod, the slider is fixedly connected to the needle sheath, the driver includes a permanent magnet, a spring and an electromagnet, the permanent magnet is fixedly connected to the slider, the spring is sleeved on the outside of the guide rod, the two ends of the spring respectively abut against the slider and one of the limiters, the spring moves the slider toward the other limiter through its own elastic force, the electromagnet is fixedly connected to the other limiter that is not abutted by the spring, and when the electromagnet is energized, it generates attraction or repulsion on the permanent magnet, so that the slider overcomes the elastic force of the spring and moves.
[0013] Furthermore, an oblique brace connecting the movable pliers head and the movable pliers arm is provided between the two, one end of the oblique brace is connected to one end of the movable pliers head away from the movable pliers arm, and the other end of the oblique brace is connected to the movable pliers arm, and the electric puncture device is installed on the oblique brace so that the puncture direction of the needle sheath is inclined to the moving direction of the movable pliers head.
[0014] Furthermore, one end of the fixed clamp arm away from the fixed clamp head is fixedly connected to a fixed handle, one end of the movable clamp arm away from the movable clamp head is fixedly connected to a movable handle, a switch is provided on the outside of the fixed handle, and the movable clamp arm is provided with a through hole or a through groove for the optical fiber body of the optical fiber temperature sensor to pass through, and the optical connector of the optical fiber temperature sensor is located on the outside of the movable clamp arm and close to the movable handle.
[0015] A temperature control method for an automatically temperature-controlled radiofrequency ablation forceps, the radiofrequency ablation forceps comprising a fixed jaw and a movable jaw, the fixed jaw and the movable jaw respectively being provided with at least one electrode, the electrode being connected to an external power source via a wire, wherein the fixed jaw or the movable jaw is connected to an optical fiber temperature sensor, and an optical fiber probe of the optical fiber temperature sensor can be inserted into a diseased tissue from between the fixed jaw and the movable jaw; the temperature control method comprises the following steps: the external power source inputs current to the electrode to generate an radiofrequency energy field between the fixed jaw and the movable jaw, causing the diseased tissue to heat up and be destroyed; the optical fiber probe transmits a temperature signal to a controller, and the controller adjusts the current input to the electrode by the external power source in real time according to a preset temperature range to control the temperature of the diseased tissue.
[0016] Compared with the prior art, this application has the following beneficial effects:
[0017] Provided are a radiofrequency ablation forceps with automatic temperature control and a temperature control method. In an embodiment of the present invention, a fiber optic probe of a fiber optic temperature sensor is inserted into the interior of the diseased tissue. The fiber optic probe can detect the temperature of deep tissue and is not affected by the radio frequency energy field, so that the radiofrequency ablation temperature of larger or deeper lesion areas is easy to control. BRIEF DESCRIPTION OF THE DRAWINGS
[0018] In order to more clearly illustrate the implementation methods of the present invention or the technical solutions in the prior art, the following briefly introduces the drawings required for the implementation methods or the description of the prior art. Obviously, the drawings in the following description are only exemplary, and for ordinary technicians in this field, other implementation drawings can be derived from the provided drawings without creative work.
[0019] Figure 1 A three-dimensional diagram of an embodiment of the present invention;
[0020] Figure 2 A top view of an embodiment of the present invention;
[0021] Figure 3 for Figure 2 Cross-sectional view in the AA direction;
[0022] Figure 4 for Figure 3A partial enlarged view of point A, showing the working condition of the electric puncture device before it is started;
[0023] Figure 5 for Figure 4 A schematic diagram of another working condition is shown, in which the needle sheath of the electric puncture device carries the optical fiber probe and punctures the diseased tissue;
[0024] Figure 6 for Figure 4 A schematic diagram of another working condition, in which the needle sheath of the electric puncture device is retracted and the optical fiber probe remains inside the diseased tissue;
[0025] Figure 7 A three-dimensional diagram of an electric puncture device according to an embodiment of the present invention;
[0026] The numbers in the figure represent the following:
[0027] 1-fixed clamp arm; 11-fixed clamp head; 12-fixed handle; 13-switch; 2-movable clamp arm; 21-movable clamp head; 22-movable handle; 23-through slot; 24-diagonal support; 3-optical fiber temperature sensor; 31-optical fiber probe; 32-optical fiber body; 4-electric puncture device; 41-needle sheath; 42-guide rod; 43-slider; 44-limiter; 45-spring. DETAILED DESCRIPTION
[0028] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.
[0029] Traditional radiofrequency ablation forceps generally detect the temperature of tissues through temperature sensors located on the surface of the forceps head or electrode. This method usually indirectly infers the actual temperature of the tissue through the temperature change at the contact point between the radiofrequency ablation forceps and the diseased tissue. The limitation of this method is that it can only detect the temperature of the tissue surface and it is difficult to accurately reflect the heat changes in deep tissues, especially for larger or deeper lesion areas, there may be a significant difference between the surface temperature and the internal temperature. In order to solve this problem, the following provides a radiofrequency ablation forceps with automatic temperature control.
[0030] Combination Figure 1 , Figure 2 , Figure 3The radiofrequency ablation forceps include a fixed forceps arm 1, a movable forceps arm 2, a fixed forceps head 11, a fixed handle 12, a movable forceps head 21, a movable handle 22 and an electrode. The movable forceps arm 2 is movably connected to the fixed forceps arm 1, and the movable forceps arm 2 can move along the length direction of the fixed forceps arm 1. The fixed forceps head 11 and the fixed handle 12 are respectively fixedly connected to the two ends of the fixed forceps arm 1, and the movable forceps head 21 and the movable handle 22 are respectively fixedly connected to the two ends of the movable forceps arm 2. The fixed forceps head 11 and the movable forceps head 21 are respectively equipped with at least one electrode, and the electrode is connected to an external power supply through a switch 13 and a wire. The switch 13 is arranged on the outside of the fixed handle 12.
[0031] The electrodes, wires and external power supply are not shown in the figure. The two electrodes are respectively embedded in the sides of the fixed clamp head 11 and the movable clamp head 21 close to each other, and the two wires are respectively embedded in the fixed clamp arm 1 and the movable clamp arm 2.
[0032] The radio frequency ablation forceps is equipped with an optical fiber temperature sensor 3 , and the optical fiber probe 31 of the optical fiber temperature sensor 3 can be inserted into the diseased tissue between the fixed forceps head 11 and the movable forceps head 21 .
[0033] The doctor operates the movable handle 22 to bring it close to the fixed handle 12, and the fixed clamp head 11 and the movable clamp head 21 approach each other and close at the location of the diseased tissue. Then the switch 13 is turned on to connect the electrode and the external power supply. The electrode is energized to activate the radio frequency energy field. The radio frequency energy field causes the polar ions and molecules inside and outside the cells to oscillate and generate heat, and the diseased tissue cells are heated up and destroyed, thereby achieving ablation treatment. During the ablation process, the optical fiber probe 31 transmits the temperature signal to the controller, and the controller adjusts the current input to the electrode by the external power supply in real time according to the preset upper and lower temperature limits.
[0034] The fiber optic probe 31 uses Bragg grating or Raman scattering technology to measure the temperature of the tissue by reflecting or scattering the light signal, avoiding the problem that the traditional metal probe may be affected by radio frequency current and electromagnetic interference. This enables the fiber optic probe 31 to accurately reflect the actual temperature inside the tissue in real time.
[0035] The temperature control method of the radiofrequency ablation forceps is: before connecting the electrode and the external power supply, the optical fiber probe 31 is inserted into the interior of the diseased tissue, and the optical fiber probe 31 is used to detect the temperature of the diseased tissue. When the temperature exceeds the safety threshold, the current input to the electrode is reduced or turned off, thereby reducing or turning off the radiofrequency energy to prevent tissue overheating or damage to healthy tissue; when the temperature is lower than the set value, the current input to the electrode is increased or turned on, thereby reducing or turning on the radiofrequency energy to ensure the ablation effect.
[0036] Through this automatic feedback adjustment mechanism, the radiofrequency ablation forceps can achieve accurate and efficient tissue ablation while ensuring surgical safety. This device is suitable for complex operations that require precise temperature control, such as tumor ablation and cardiac catheter ablation.
[0037] Specifically, the fiber optic probe 31 is inserted into the diseased tissue through the electric puncture device 4, the electric puncture device 4 is fixedly connected to the dynamic forceps head 21, the actuator of the electric puncture device 4 is a hollow needle sheath 41, and the fiber optic probe 31 is fixed inside the needle sheath 41. When the electric puncture device 4 drives the needle sheath 41 to penetrate into the diseased tissue, the fiber optic probe 31 is inserted into the diseased tissue together with the needle sheath 41.
[0038] Preferably, the needle sheath 41 is made of memory metal. After the needle sheath 41 carries the optical fiber probe 31 and penetrates the diseased tissue, the needle sheath 41 is heated by the patient's body temperature and deformed. The deformation of the needle sheath 41 causes a gradually increasing gap to form between the needle sheath 41 and the optical fiber probe 31. After the needle sheath 41 retracts into the interior of the electric puncture device 4, the optical fiber probe 31 stays inside the diseased tissue. During the radiofrequency ablation operation, the optical fiber temperature sensor 3 monitors the temperature of the diseased tissue in real time and transmits the signal to the controller.
[0039] Preferably, combined Figure 7 The cross-section of the needle sheath 41 is a fan-shaped ring with a central angle greater than 180 degrees, that is, the needle sheath 41 has an opening extending along its own axial direction on one side. This design makes the needle sheath 41 easy to deform. Compared with the cylindrical needle sheath 41, the contact area between the fan-shaped needle sheath 41 and the optical fiber probe 31 is smaller.
[0040] Combination Figure 3 , Figure 4 The movable forceps arm 2 is provided with a through hole or a through groove 23 for the optical fiber body 32 of the optical fiber temperature sensor 3 to pass through. The optical connector of the optical fiber temperature sensor 3 is located on the outside of the movable forceps arm 2 and close to the movable handle 22. After the radiofrequency ablation operation is completed, the doctor can drag the optical fiber body 32 beside the movable handle 22 to retract the optical fiber probe 31 into the interior of the movable forceps head 21.
[0041] Combination Figure 3 , Figure 4 The electric puncture device 4 includes a guide and a driver, both of which are connected to the movable forceps head 21. The guide is used to guide the puncture direction of the needle sheath 41, and the driver is used to drive the needle sheath 41 to extend or retract.
[0042] The guide includes a guide rod 42 and a slider 43 , as well as stoppers 44 disposed at both ends of the guide rod 42 . The slider 43 is slidably connected to the guide rod 42 , and the slider 43 is fixedly connected to the needle sheath 41 .
[0043] Preferably, an oblique brace 24 connecting the movable clamp head 21 and the movable clamp arm 2 is provided between the two, one end of the oblique brace 24 is connected to the end of the movable clamp head 21 away from the movable clamp arm 2, and the other end of the oblique brace 24 is connected to the movable clamp arm 2, and the guide rod 42 is installed on the oblique brace 24, so that the puncture direction of the needle sheath 41 is inclined to the moving direction of the movable clamp head 21. The advantage of this design is that the optical fiber probe 31 using Bragg grating technology can realize multi-point temperature monitoring, and the inclined optical fiber probe 31 can monitor the temperature of different positions in the thickness direction of the diseased tissue and the length direction of the fixed clamp head 11 in the radio frequency energy field formed between the movable clamp head 21 and the fixed clamp head 11, so as to timely detect local overheating of the diseased tissue.
[0044] The driver includes a permanent magnet, a spring 45 and an electromagnet. The permanent magnet is fixedly connected to the slider 43. The spring 45 is mounted on the outside of the guide rod 42. The two ends of the spring 45 respectively abut against the slider 43 and a limiter 44. The spring 45 moves the slider 43 toward the other limiter 44 through its own elastic force. The electromagnet is fixedly connected to the other limiter 44 that is not abutted by the spring 45. When the electromagnet is energized, it generates an attractive force or a repulsive force on the permanent magnet, so that the slider 43 overcomes the elastic force of the spring 45 and moves.
[0045] The permanent magnet and the electromagnet are not shown in the figure, wherein the permanent magnet is embedded in the slider 43 and the electromagnet is embedded in the limiter 44 .
[0046] Combination Figure 4 After the fixed forceps head 11 and the movable forceps head 21 clamp the diseased tissue.
[0047] Combination Figure 5 When the electromagnet is energized, it generates a repulsive force on the permanent magnet, causing the slider 43 to move against the elastic force of the spring 45, and the needle sheath 41 extends from the inside of the movable forceps head 21 and carries the optical fiber probe 31 into the diseased tissue. Then, the needle sheath 41 is heated by the temperature of the diseased tissue and gradually flattens.
[0048] Combination Figure 6 , the electromagnet is powered off, the spring 45 drives the slider 43 to reset by its own elastic force, the needle sheath 41 withdraws from the inside of the diseased tissue, and the optical fiber probe 31 stays inside the diseased tissue.
[0049] The above embodiments are only exemplary embodiments of the present invention and are not intended to limit the present invention. The protection scope of the present invention is defined by the claims. Those skilled in the art may make various modifications or equivalent substitutions to the present invention within the essence and protection scope of the present invention, and such modifications or equivalent substitutions shall also be deemed to fall within the protection scope of the present invention.
Claims
1. A radiofrequency ablation forceps with automatic temperature control, characterized in that: The invention comprises a fixed clamp head (11) and a movable clamp head (21), wherein the fixed clamp head (11) and the movable clamp head (21) are respectively provided with at least one electrode, wherein the electrode is connected to an external power source via a wire, and the external power source is used to input current into the electrode to generate a radio frequency energy field between the fixed clamp head (11) and the movable clamp head (21); The fixed clamp head (11) or the movable clamp head (21) is connected to an optical fiber temperature sensor (3), and an optical fiber probe (31) of the optical fiber temperature sensor (3) can be inserted into the diseased tissue between the fixed clamp head (11) and the movable clamp head (21). The optical fiber probe (31) transmits a temperature signal to a controller, and the controller adjusts the current input to the electrode by the external power supply in real time according to a preset temperature range to control the temperature of the diseased tissue.
2. The automatic temperature-controlled radiofrequency ablation forceps according to claim 1, characterized in that: The fixed clamp head (11) is fixedly connected to the fixed clamp arm (1), the movable clamp head (21) is fixedly connected to the movable clamp arm (2), the movable clamp arm (2) is movably connected to the fixed clamp arm (1), and the movable clamp arm (2) can move along the length direction of the fixed clamp arm (1).
3. The automatic temperature-controlled radiofrequency ablation forceps according to claim 2, characterized in that: The optical fiber probe (31) is inserted into the diseased tissue through an electric puncture device (4). The electric puncture device (4) is fixedly connected to the dynamic forceps head (21). The actuator of the electric puncture device (4) is a hollow needle sheath (41). The optical fiber probe (31) is fixed inside the needle sheath (41). When the electric puncture device (4) drives the needle sheath (41) to penetrate into the diseased tissue, the optical fiber probe (31) is inserted into the diseased tissue together with the needle sheath (41).
4. The automatic temperature-controlled radiofrequency ablation forceps according to claim 3, characterized in that: The needle sheath (41) is made of memory metal. After the needle sheath (41) carries the optical fiber probe (31) and pierces the diseased tissue, the needle sheath (41) is heated by the patient's body temperature and deformed. The deformation of the needle sheath (41) causes a gradually increasing gap to form between the needle sheath (41) and the optical fiber probe (31). After the needle sheath (41) retracts into the interior of the electric puncture device (4), the optical fiber probe (31) stays inside the diseased tissue.
5. The automatic temperature-controlled radiofrequency ablation forceps according to claim 4, characterized in that: One side of the needle sheath (41) is provided with an opening extending along its own axial direction, so that the cross section of the needle sheath (41) forms a fan ring shape with a central angle greater than 180 degrees.
6. The automatic temperature-controlled radiofrequency ablation forceps according to claim 3, characterized in that: The electric puncture device (4) comprises a guide and a driver, both of which are connected to the movable forceps head (21), the guide is used to guide the puncture direction of the needle sheath (41), and the driver is used to drive the needle sheath (41) to extend or retract.
7. The automatic temperature-controlled radiofrequency ablation forceps according to claim 6, characterized in that: The guide comprises a guide rod (42) and a slider (43), and stoppers (44) arranged at both ends of the guide rod (42); the slider (43) is slidably connected to the guide rod (42); the slider (43) is fixedly connected to the needle sheath (41); the driver comprises a permanent magnet, a spring (45) and an electromagnet; the permanent magnet is fixedly connected to the slider (43); the spring (45) is sleeved on the outer side of the guide rod (42); the two ends of the spring (45) respectively abut against the slider (43) and one of the stoppers (44); the spring (45) moves the slider (43) toward the other stopper (44) through its own elastic force; the electromagnet is fixedly connected to the other stopper (44) not abutted by the spring (45); when the electromagnet is energized, it generates an attractive force or a repulsive force on the permanent magnet, so that the slider (43) overcomes the elastic force of the spring (45) and moves.
8. The automatic temperature-controlled radiofrequency ablation forceps according to claim 3, characterized in that: An oblique support (24) is provided between the movable forceps head (21) and the movable forceps arm (2) to connect the two. One end of the oblique support (24) is connected to an end of the movable forceps head (21) away from the movable forceps arm (2), and the other end of the oblique support (24) is connected to the movable forceps arm (2). The electric puncture device (4) is mounted on the oblique support (24) so that the puncture direction of the needle sheath (41) is inclined to the moving direction of the movable forceps head (21).
9. The automatic temperature-controlled radiofrequency ablation forceps according to claim 2, characterized in that: The fixed clamp arm (1) has one end away from the fixed clamp head (11) fixedly connected to a fixed handle (12), the movable clamp arm (2) has one end away from the movable clamp head (21) fixedly connected to a movable handle (22), a switch (13) is arranged on the outside of the fixed handle (12), the movable clamp arm (2) is provided with a through hole or a through groove (23) through which an optical fiber body (32) of the optical fiber temperature sensor (3) can pass, and the optical connector of the optical fiber temperature sensor (3) is located on the outside of the movable clamp arm (2) and close to the movable handle (22).
10. A temperature control method for an automatic temperature control radiofrequency ablation forceps, characterized in that: The radiofrequency ablation forceps comprises a fixed forceps head (11) and a movable forceps head (21), wherein the fixed forceps head (11) and the movable forceps head (21) are respectively provided with at least one electrode, wherein the electrode is connected to an external power supply via a wire, wherein the fixed forceps head (11) or the movable forceps head (21) is connected to an optical fiber temperature sensor (3), and an optical fiber probe (31) of the optical fiber temperature sensor (3) can be inserted into the diseased tissue from between the fixed forceps head (11) and the movable forceps head (21); The temperature control method comprises the following steps: The external power source inputs current into the electrode to generate a radio frequency energy field between the fixed clamp head (11) and the movable clamp head (21), so as to heat up the diseased tissue and destroy it; The optical fiber probe (31) transmits the temperature signal to the controller, and the controller adjusts the current input from the external power supply to the electrode in real time according to a preset temperature range to control the temperature of the diseased tissue.