CN213758519U - Cervical ablation device - Google Patents
Cervical ablation device Download PDFInfo
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- CN213758519U CN213758519U CN202022194030.4U CN202022194030U CN213758519U CN 213758519 U CN213758519 U CN 213758519U CN 202022194030 U CN202022194030 U CN 202022194030U CN 213758519 U CN213758519 U CN 213758519U
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Abstract
The utility model relates to the field of medical equipment, especially a cervical ablation device. The existing cervical treatment field lacks a pulsed electric field ablation device, and the existing thermal ablation equipment can damage peripheral normal tissues in treatment. The utility model provides a cervical ablation device, including ablation ware and the impulse generator who is connected with it, ablation ware includes an ablation pipe that is equipped with a plurality of electrodes, and the ablation pipe body is a flexible pipe that coils, and flexible pipe top-down coils and coils the cyclic annular radius of formation and enlarge gradually, and annular path end is the upper end of flexible pipe, and big footpath end is the lower extreme of flexible pipe, and each electrode is just, the negative pole sets up in turn along the extending direction of flexible pipe, wears to establish the wire in the flexible pipe and connects just, the negative pole respectively, the wire links to each other the power supply with impulse generator. The utility model discloses can realize that the cervix of non-heat energy melts to can do accurate orientation to melting regional cervical tissue and melt, in order to prevent to cause the harm to peripheral normal tissue.
Description
Technical Field
The utility model relates to the field of medical equipment, especially a cervical ablation device.
Background
Cervical cancer has become a public health problem that seriously threatens the health of women. Epidemiological studies find that cervical cancer is one of the most common cancers of gynecological malignancies at present, and the incidence is second to breast cancer and colorectal cancer. In recent years, with the popularization of cervical cancer screening, the detection rate of early cervical cancer patients is higher and higher, and the onset age is also in the trend of younger development. Extensive cervictomy is considered as a main treatment method for retaining the fertility function of early-stage cervical cancer due to the remarkable near-term and long-term curative effects of the wide-term cervicitis. For early cervical cancer patients with lower risk, more conservative surgical methods such as cervical conization and simple cervicitis are safe and feasible. However, the above operations have great risks of postoperative bleeding, intrauterine infection, cervical canal stenosis and even occlusion, cervical insufficiency, secondary operation caused by residual focus, and other complications in near and far stages.
There is a therapeutic approach to ablation using Pulsed Electric Field (PEF) that overcomes many of the problems associated with conventional thermal ablation, has a low impact on non-target tissue, does not damage surrounding normal tissue, and is becoming increasingly recommended for tumor therapy and cardiac surgery. The principle of PEF ablation works by applying very high electric field energy for a very short time, forming irreversible electroporation (IRE) in the plasma membrane, causing leakage of the cell contents, resulting in cell death. Currently, there is no special pulsed electric field ablation device in the cervical cancer treatment field, and there is still a gap in applying pulsed electric field ablation to cervical cancer treatment devices.
SUMMERY OF THE UTILITY MODEL
The utility model aims to solve the technical problems and the technical task that is provided is to overcome the defects of the pulse electric field ablation device in the prior cervical treatment field, and the existing heat ablation equipment can damage the peripheral normal tissues and other problems in the treatment, the utility model provides a cervical ablation device which can realize the non-heat cervical ablation and can precisely and directionally ablate the cervical tissues in the ablation area so as to prevent the damage to the peripheral normal tissues; further, the utility model discloses used high-voltage pulse energy source can realize in the fixed pulse width to the accurate regulation of pulse amplitude, overcomes to have hydrogen thyratron structure energy source to need 20 minutes to preheat latency, and the system temperature of energy source device can keep at the room temperature level moreover, more need not use insulating oil cooling, reduces a whole set of system volume greatly, changes in the operation and places.
The utility model provides a technical scheme that technical problem adopted: a cervix uteri ablation device comprises an ablation device and a pulse generator connected with the ablation device, and is characterized in that the ablation device comprises an ablation tube provided with a plurality of electrodes, the body of the ablation tube is a coiled flexible catheter, the flexible catheter is coiled from top to bottom, the radius of an annular shape formed by coiling is gradually enlarged, the small diameter end of the annular shape is the upper end of the flexible catheter, the large diameter end of the annular shape is the lower end of the flexible catheter, the electrodes are alternately arranged along the extending direction of the flexible catheter, a lead is arranged in the flexible catheter in a penetrating way and is respectively connected with a positive electrode and a negative electrode, and the lead is connected with the pulse generator for power supply; the flexible conduit is made of elastic materials and is arranged on a stretcher, the rear end of the stretcher is connected with an adjusting handle, and the stretcher can drive the flexible conduit to stretch or compress along the annular axis direction by operating the adjusting handle. The utility model discloses a coil flexible pipe and the positive and negative electrode that distributes on it in turn of establishing specially to combine impulse generator to provide impulse current, do accurate pulse electric field to the regional specific site of cervix and melt, melt the in-process and can not cause the harm to peripheral normal tissue. When the flexible catheter works, the coiled flexible catheter can perform ablation treatment at the position of a cervical orifice, wherein the coiled annular small-diameter end is arranged in front of the large-diameter end and behind the large-diameter end, the coiled flexible catheter can be closely attached to the tissue where the cervical orifice is arranged so as to perform effective electric field ablation on lesion tissues on specific medical parts such as an internal cervical orifice, a douglas pit and a recess, all anodes of the flexible catheter are connected with an output anode of a pulse generator through leads during ablation, all cathodes on the flexible catheter are connected with an output cathode of the pulse generator through leads, and discharge can be performed between the adjacent anodes and the adjacent cathodes to form a high-voltage electric field, so that irreversible electroporation is performed on the tissues adjacent to the electrodes, the cell contents of the lesion tissues are leaked, and cells are killed; when the flexible conduit is electrified, the area covered by the whole flexible conduit is an electric field distribution area, an electric field exists between the adjacent positive and negative electrodes along the extending direction of the flexible conduit, and an electric field also exists between the adjacent positive and negative electrodes along the annular inner ring and the outer ring of the flexible conduit. In addition, the pulse generator may adopt an existing high voltage pulse generator and other pulse generating devices capable of outputting pulse current. The annular flexible catheter can be stretched or compressed by operating the adjusting handle, so that the purpose of expanding or contracting the ablation catheter is achieved, the cervical part shapes of different individuals are adapted, electrodes on the flexible catheter are close to tissues to be ablated, the treatment requirement of an ablation operation is met, when the annular flexible catheter is stretched or compressed along the axial direction, the expansion or contraction of the annular radius can be achieved, ablation is implemented at any position of a cervix, and the radius of the annular large-diameter end is reduced along with the stretching; on the contrary, the ring shape of the flexible conduit is compressed along the axial direction, and the radius of the large-diameter end of the ring shape is enlarged.
As further improvement and supplement to the above technical scheme, the utility model discloses a following technical measure: the stretcher comprises a long rod, a fixing piece and a moving piece, wherein the fixing piece and the moving piece are arranged on the long rod, the fixing piece is fixedly connected to the front end of the long rod and fixed to the annular small-diameter end of the flexible guide pipe, the moving piece is movably arranged at the rear portion of the long rod and fixed to the annular large-diameter end of the flexible guide pipe, the connecting line of the fixing piece and the moving piece coincides with the annular axis of the flexible guide pipe, and the adjusting handle is connected with the moving piece and can drive the moving piece to move back and forth along the long rod. Because the two annular ends of the flexible conduit are respectively connected with the fixed piece and the movable piece, the two parts are on the same long rod, and the small annular diameter end of the flexible conduit is fixed at the front end of the long rod along with the fixed piece, the large annular diameter end of the flexible conduit can be driven to do corresponding back-and-forth movement along the axis only by operating the adjusting handle to push and pull the fixed piece to do back-and-forth movement on the long rod, thereby realizing stretching or compressing the annular flexible conduit; when the moving part moves to one side of the fixing part to be close to the fixing part, the moving part can drive the annular large-diameter end of the flexible conduit to be close to the small-diameter end, the annular shape of the flexible conduit is compressed along the axial direction, the radius of the large-diameter end is gradually increased, otherwise, when the moving part moves back to the fixing part, the moving part can drive the annular large-diameter end of the flexible conduit to be far away from the small-diameter end, the annular shape of the flexible conduit is stretched along the axial direction, and the radius of the large-diameter end is gradually reduced.
The fixed piece and the moving piece are both cylinders, the moving piece is sleeved on the long rod, and the end part of the cylinder of the fixed piece is arc-shaped. The fixed piece and the movable piece are both designed into a cylinder shape so as to be convenient to enter the human body; the fixing piece at the front end is designed into an arc shape corresponding to the end part of the cylinder body, and the fixing piece with the arc end part can be directly inserted into the uterine orifice through the vagina as the front end in use and brings the ablation tube into the body.
The number of the electrodes on the flexible conduit is 20-24, the number of the positive electrodes and the number of the negative electrodes are the same, and the distance between the annular small-diameter end and the annular large-diameter end on the flexible conduit is 0-10 cm. The number of the electrodes on the flexible conduit can be between 20 and 24, and the total number of the positive electrodes and the negative electrodes is 20 or 22 or 24 because the number of the positive electrodes and the number of the negative electrodes are equal; the two ends of the ring formed by the flexible catheter can be movably close to or far away from each other, and the distance between the two ends can be adjusted between 0cm and 10cm, so that the length of each electrode can be changed to enable each electrode to be close to the tissue to be ablated, and the treatment requirement is met.
The pulse generator comprises a grounding high-voltage power supply, a current-limiting resistor, an electrode positive contact and an electrode negative contact, wherein the current-limiting resistor is connected to the positive electrode of the high-voltage power supply, the electrode negative contact is connected to the negative electrode of the high-voltage power supply, the pulse generator is characterized in that the circuit further comprises an air switch, two equal-length first coaxial cables and two equal-length second coaxial cables which are of the same specification, the first coaxial cables and the second coaxial cables respectively comprise an inner side central copper wire and an outer side netted conducting layer, the air switch is connected to the circuit between the current-limiting resistor and the electrode positive contact, the air switch comprises two pointed A conductors and two pointed B conductors, the pointed ends on the A, B conductors are just opposite and the intervals can be movably adjusted, the A, B conductor is connected into the circuit through a wire, and the central copper wires of the first coaxial cables and the second coaxial cables are connected in series through a wire, the other end of the central copper wire of the first coaxial cable is connected with the current-limiting resistance output circuit, the other end of the central copper wire of the second coaxial cable is connected with the conductor A, the two ends of the reticular conducting layer of the first coaxial cable are connected with the negative electrode of the high-voltage power supply and the negative electrode contact of the electrode, and the two ends of the reticular conducting layer of the second coaxial cable are connected with the positive electrode contact of the electrode and the conductor B. The utility model discloses an arc discharge is adjusted to the distance of two cusps on the air switch to accurate control voltage amplitude realizes that high-pressure nanosecond pulse sends, and air switch discharges immediately and need not prepare long-time preheating and wait just can work, and the operating temperature of device can also keep at room temperature level, need not insulating oil scattered heat treatment, effectively reduces the appearance volume of device, easily hospital's operation place's operation and putting. When the charging voltage is large enough to exceed the threshold voltage of the two coaxial cables during working, the electric arc between the upper tips of the two conductors can break down air, the air switch discharges to form nanosecond-level high-voltage pulse, the triggering times and the triggering time can be controlled, the subsequent high-voltage nanosecond pulse can be transmitted to the positive electrode contact and the negative electrode contact, and then the positive electrode and the negative electrode discharge to perform pulse ablation. When the distance between the two sharp heads on the air switch is far in use, the voltage and the current of the high-voltage source need to be increased simultaneously so as to ensure that the transmitted coaxial cable has enough energy for charging. In addition, the high-voltage power supply can adopt a kilovolt high voltage converted from a 220V household low voltage and then connected into a circuit. The coaxial cable comprises an inner concentric conductor and an outer concentric conductor which are coaxial, and insulators are wrapped between the concentric conductors and outside the outer conductor, which is the prior art; the first coaxial cable and the second coaxial cable are equal-length cables with the same material specification.
The conductor A and the conductor B are respectively arranged on the two installation bases, at least one of the two installation bases is a movable base capable of translating, and the movable base is close to the other installation base through translation so as to adjust the distance between the two tips of the conductor A, B. The two conductors are respectively arranged on the two mounting seats, and at least one of the mounting seats is arranged to be capable of moving in a translation mode so as to change the distance between the two sharp heads to adjust arc discharge and control the voltage amplitude. The two conductors can also be respectively arranged on the two movable seats, and the two movable seats can move horizontally to rapidly change the distance between the two sharp heads to adjust the discharge of the air switch.
The conductor A is arranged on a fixed mounting seat, the conductor B is arranged on a movable seat which translates, the movable seat which translates is sleeved on a rotatable screw rod, an internal thread which is matched with the screw rod is arranged on the movable seat, the fixed mounting seat is arranged on a frame which is connected with one end of the screw rod, and the screw rod is connected with a numerical control stepping motor in a transmission way. The stepping motor through numerical control programming accurately controls the rotation stroke of the screw rod, then the translational sliding of the movable seat on the screw rod is accurately adjusted, so that the conductor B on the movable seat is close to the conductor A which is fixed, and the effect of accurately changing the discharge distance between the upper pointed ends of the two conductors is realized.
The sliding seat bottom is clamped on the sliding table and can move horizontally along the sliding table, and the extending direction of the sliding table corresponds to the length direction of the screw rod. The movable base is clamped on the sliding table to limit the translation direction, and the sliding table and the rotating screw rod act together to ensure that the movable base keeps good stability and directivity in translation.
The conductor A and the conductor B are both made of metal copper. The metal copper used as a conductor has excellent conductivity, better machining characteristics and convenience for processing a required shape and manufacturing an integrally-formed pointed end.
The total length of the first coaxial cable line and the second coaxial cable line is calculated according to the following formula:
propagation velocity of electromagnetic waves in cable
=1/
High voltage pulse width t =
L*
The characteristic impedance of the first coaxial cable line and the second coaxial cable line is designed to be Z0，Z0=
Wherein the high voltage pulse width is in units of nanoseconds; l is the total length of the first coaxial cable and the second coaxial cable in unit meter;
the inductance value is the unit length of the coaxial cable, and the unit is H/m;
is the capacitance per unit length of the coaxial cable, i.e. the permittivity, in F/m.
The pulse width is determined by the length of the cable: the longer the cable, the wider the pulse. The utility model discloses if the high-voltage pulse of the output 300 nsec pulsewidth, the high-voltage cable total length that obtains through aforementioned formula calculation is about 60 meters, and wherein each 30 meters of first coaxial cable and second coaxial cable, two sections transmission lines are identical.
Furthermore, the voltage and the current of the high-voltage power supply can be adjusted, and the voltage grade of the high-voltage power supply can be continuously adjusted within a wide range of 0kV to 10 kV. When the myocardial tissue is ablated, the voltage amplitude needs to be adjusted according to different positions and electrode sizes, and when the high-voltage pulse amplitude with the pulse width of 300 nsec needs to be output, the required voltage range is 0 kV-10 kV.
The utility model provides a pulse current by a specially arranged coiled flexible catheter and positive and negative electrodes alternately distributed on the coiled flexible catheter and combining with a pulse generator, and carries out precise pulse electric field ablation on specific parts of a cervical region, and can not damage surrounding normal tissues in the ablation process; the pulse generator can accurately control the voltage amplitude, high-voltage nanosecond pulse transmission is realized, the air switch can work immediately without preparing for long-time preheating waiting, the working temperature of the pulse generator can be kept at the room temperature level, insulating oil heat dissipation treatment is not needed, and the appearance volume of the whole pulse generator is greatly reduced.
Drawings
FIG. 1: the utility model discloses an ablation tube structure sketch map.
FIG. 2: the cross-sectional view taken along line C-C of FIG. 1.
FIG. 3: schematic diagram of the ablation tube covering the cervix after opening.
FIG. 4: schematic view of the cervix covered after the ablation tube is contracted.
FIG. 5: the ablation tube is shown in a schematic view at the cervical position.
FIG. 6: pulse generator's electrical connection schematic diagram.
FIG. 7: fig. 6 is a schematic structural diagram of the air switch.
In the figure: 1. the device comprises a high-voltage power supply, 2 current-limiting resistors, 3 first coaxial cables, 4 second coaxial cables, 5 air switches, 6 electrode positive electrode contacts, 7 electrode negative electrode contacts, 8A conductors, 9B conductors, 10 pointed ends, 11 movable seats, 12 fixed seats, 13 lead screws, 14 sliding seats, 15 flexible guide pipes, 16 fixed pieces, 17 movable pieces, 18 cervix and 19 long rods.
Detailed Description
The invention will be further described with reference to the following description and embodiments in conjunction with the accompanying drawings.
As shown in fig. 1 to 5, a cervical ablation device comprises an ablation device and a pulse generator connected thereto, the ablation device comprises an ablation tube provided with a plurality of electrodes, a body of the ablation tube is a coiled flexible conduit 15, the flexible conduit 15 is made of an elastic material, the flexible conduit 15 is coiled from top to bottom, a radius of a ring formed by coiling is gradually enlarged, a small diameter end of the ring is an upper end of the flexible conduit 15, a large diameter end of the ring is a lower end of the flexible conduit 15, the electrodes are alternately arranged along an extending direction of the flexible conduit 15, the total number of the positive and negative electrodes is 22, the number of the positive and negative electrodes is the same, the length and the width of each positive and negative electrode are 2mm, and the distance between the adjacent positive and negative electrodes is also 2mm, as shown in fig. 2, L1, L3 and L5 … … L21 are both positive electrodes, L2, L4 and L6 … … L22 are both negative electrodes, the flexible conduit 15 is internally provided with a lead in a penetrating way to respectively connect each anode and each cathode, and the lead is connected with the pulse generator to supply power; the flexible conduit 15 is arranged on a stretcher, the stretcher comprises a long rod 19, a fixing piece 16 and a moving piece 17, wherein the fixing piece 16 and the moving piece 17 are both cylinders, the end part of the cylinder of the fixing piece 16 is arc-shaped, the fixing piece 16 is fixedly connected to the front end of the long rod 19 and is fixed to the annular small diameter end of the flexible conduit 15, the moving piece 17 is movably sleeved on the rear part of the long rod 19 and is fixed to the annular large diameter end of the flexible conduit 15, the connecting line of the fixing piece 16 and the moving piece 17 is overlapped with the annular axis of the flexible conduit 15, the rear end of the stretcher is connected with an adjusting handle, the adjusting handle is connected with the moving piece 17 and can drive the moving piece to move back and forth along the long rod 19, and the stretcher can drive the flexible conduit 15 to stretch or compress along the annular axis direction by operating the adjusting handle.
As shown in fig. 6, the pulse generator includes a circuit formed by connecting a grounded high-voltage power supply 1, a current-limiting resistor 2, an electrode positive electrode contact 6 and an electrode negative electrode contact 7 in series, the current-limiting resistor is connected to the positive electrode of the high-voltage power supply, the electrode negative electrode contact 7 is connected to the negative electrode of the high-voltage power supply, the circuit further includes an air switch 5, two sections of first coaxial cables 3 and second coaxial cables 4 with the same length and the same specification, the first coaxial cables 3 and the second coaxial cables 4 both include an inner central copper wire and an outer meshed conductive layer, the air switch is connected to the circuit between the current-limiting resistor 2 and the electrode positive electrode contact 6, the air switch 5 includes two conductors a 8 and B9 with tips 10, in this embodiment, the conductors a 8 and B9 are made of metal copper, the tips 10 on the A, B conductor are opposite and the distance D is movably adjustable, the conductor a is movably connected to the conductor a conductor 8 and B9, The conductor B is connected into the circuit through a lead, the central copper wires of the first coaxial cable 3 and the second coaxial cable 4 are connected in series through leads, the other end of the central copper wire of the first coaxial cable 3 is connected with the output circuit of the current-limiting resistor 2, the other end of the central copper wire of the second coaxial cable 4 is connected with the conductor A8, the two ends of the reticular conducting layer of the first coaxial cable 4 are connected with the negative electrode of the high-voltage power supply 1 and the negative electrode contact 7, and the two ends of the reticular conducting layer of the second coaxial cable 4 are connected with the positive electrode contact 6 and the conductor B9. The voltage and the current of the high-voltage power supply are adjustable, and the voltage grade of the high-voltage power supply is continuously adjustable in a wide range from 0kV to 10 kV.
As shown in fig. 7, conductor a 8 and conductor B9 divide and locate on two insulating mount pads, but one is the sliding seat 11 of translation in two mount pads, another is fixing base 12, and sliding seat 11 is close to the fixing base through the translation in order to adjust the distance between two cusps of A, B conductor, and preferred conductor a 8 establishes on fixed base 12 that is a mount pad of motionless in this embodiment, and conductor B9 establishes on the sliding seat 11 of translation, and the sliding seat cover of translation is put on rotatable lead screw 13, is equipped with the internal thread that matches with lead screw 13 on the sliding seat 11, and the joint in sliding seat 11 bottom simultaneously can follow the slip table translation on slip table 14, the extending direction and the lead screw length direction of slip table 14 correspond, the fixing base is established in the frame that lead screw one end is connected, the lead screw links to each other with the step motor transmission of numerical control.
When the charging voltage is large enough, the arc breaks down the air switch to form nanosecond-level high-voltage pulse, and the control of the triggering times and the triggering time is realized. High-voltage nanosecond pulses are input to the positive electrodes and the negative electrodes of the flexible catheter through the catheter, a high-voltage pulse electric field can be formed between the adjacent positive electrodes and the adjacent negative electrodes, a high-voltage pulse electric field can be formed between every two adjacent positive electrodes and every two adjacent negative electrodes in the 22 electrodes, and all the high-voltage pulse electric fields can cover an erosion area of a cervical orifice to realize local ablation; during ablation, all positive electrodes on the ablation tube are connected to the point a in fig. 6, and all negative electrodes are connected to the point b in fig. 6. In addition, the annular flexible catheter can be stretched or compressed only by operating the adjusting handle, the distance h between the annular small-diameter end and the annular large-diameter end on the flexible catheter 15 can be movably adjusted between 0cm and 10cm, so that the whole ablation tube is expanded as shown in fig. 3 or contracted as shown in fig. 4, ablation is implemented at any position of the cervix 18, specifically, the flexible catheter is compressed along the annular axial direction when the ablation tube is expanded, and conversely, the flexible catheter is stretched along the annular axial direction when the ablation tube is contracted.
In operation, the pulse width is determined by the length of the cable: the longer the cable, the wider the pulse. The amplitude of the adjustment pulse can be achieved by simply adjusting the distance of the air switch (see fig. 7). The two conductors of the air switch are made of two metal copper with prongs. When the charging voltage exceeds the threshold voltage of the transmission line cable (i.e., the first coaxial cable line and the second coaxial cable line), the arc breaks through the air and discharges with the air switch. The distance D between the two tips can be accurately controlled by only programming the stepping motor, so that the voltage amplitude can be accurately controlled. When the air switch is far away, the voltage and the current of the high-voltage source need to be increased at the same time, so that the transmission line cable is ensured to have enough energy for charging.
The total length of the first coaxial cable and the second coaxial cable in this embodiment is calculated according to the following formula:
propagation velocity of electromagnetic waves in cable
=1/
High voltage pulse width t =
L*
The characteristic impedance of the first coaxial cable line and the second coaxial cable line is designed to be Z0，Z0=
Wherein the high voltage pulse width is in units of nanoseconds; l is the total length of the first coaxial cable and the second coaxial cable in unit meter;
the inductance value is the unit length of the coaxial cable, and the unit is H/m;
is the capacitance per unit length of the coaxial cable, i.e. the permittivity, in F/m.
According to the electromagnetic wave transmission theory, the best transmission effect can be achieved only by matching the characteristic impedance of a transmission medium with the impedance of a load in the electromagnetic wave transmission process, and the loss is minimum; ideally, the electromagnetic energy is transmitted by a homogeneous lossless transmission line, for example, to realize a high voltage pulse with a pulse width of 300 nsec, the total length L of the high voltage cable is calculated to be about 60 meters, wherein the length of the first coaxial cable line and the length of the first coaxial cable line are 30 meters each, and the two transmission lines are completely the same.
Claims (10)
1. A cervix uteri ablation device comprises an ablation device and a pulse generator connected with the ablation device, and is characterized in that the ablation device comprises an ablation tube provided with a plurality of electrodes, the body of the ablation tube is a coiled flexible catheter, the flexible catheter is coiled from top to bottom, the radius of an annular shape formed by coiling is gradually enlarged, the small diameter end of the annular shape is the upper end of the flexible catheter, the large diameter end of the annular shape is the lower end of the flexible catheter, the electrodes are alternately arranged along the extending direction of the flexible catheter, a lead is arranged in the flexible catheter in a penetrating way and is respectively connected with a positive electrode and a negative electrode, and the lead is connected with the pulse generator for power supply; the flexible conduit is made of elastic materials and is arranged on a stretcher, the rear end of the stretcher is connected with an adjusting handle, and the stretcher can drive the flexible conduit to stretch or compress along the annular axis direction by operating the adjusting handle.
2. The cervical ablation device of claim 1, wherein the stretcher includes an elongated shaft, a fixed member and a movable member, the fixed member is fixedly connected to the front end of the elongated shaft and fixed to the small annular diameter end of the flexible catheter, the movable member is movably disposed at the rear end of the elongated shaft and fixed to the large annular diameter end of the flexible catheter, a connecting line between the fixed member and the movable member coincides with the annular axis of the flexible catheter, and the adjustment handle is connected to the movable member and drives the movable member to move back and forth along the elongated shaft.
3. The cervical ablation device of claim 2, wherein the fixed member and the movable member are both cylindrical members, the movable member is mounted on the shaft, and the end of the cylindrical member of the fixed member is curved.
4. The cervical ablation device of claim 2, wherein the number of the electrodes on the flexible catheter is between 20 and 24, the number of the positive and negative electrodes is the same, and the distance between the small diameter end and the large diameter end of the ring on the flexible catheter is between 0 and 10 cm.
5. The cervical ablation device of claim 1, wherein the pulse generator comprises a circuit formed by connecting a grounded high voltage power supply, a current limiting resistor, an electrode positive contact and an electrode negative contact in series, the current limiting resistor is connected to the positive electrode of the high voltage power supply, the electrode negative contact is connected to the negative electrode of the high voltage power supply, the cervical ablation device is characterized in that the circuit further comprises an air switch and two sections of first coaxial cable and second coaxial cable with the same length and the same specification, the first coaxial cable and the second coaxial cable both comprise an inner central copper wire and an outer meshed conductive layer, the air switch is connected to the circuit between the current limiting resistor and the electrode positive contact, the air switch comprises two conductors A and B with tips, the tips on the conductor A, B are opposite and the distance between the two conductors can be movably adjusted, the conductor A, B is connected to the circuit through a lead, and the central copper wires of the first coaxial cable and the second coaxial cable are connected in series through a lead, the other end of the central copper wire of the first coaxial cable is connected with the current-limiting resistance output circuit, the other end of the central copper wire of the second coaxial cable is connected with the conductor A, the two ends of the reticular conducting layer of the first coaxial cable are connected with the negative electrode of the high-voltage power supply and the negative electrode contact of the electrode, and the two ends of the reticular conducting layer of the second coaxial cable are connected with the positive electrode contact of the electrode and the conductor B.
6. The cervical ablation device of claim 5, wherein the conductor a and the conductor B are separately provided on two mounting blocks, at least one of the two mounting blocks being a translatable movable block that is translated closer to the other mounting block to adjust A, B the distance between the tines of the conductor.
7. The cervical ablation device according to claim 6, wherein the conductor A is disposed on a fixed mounting seat, the conductor B is disposed on a translational movable seat, the translational movable seat is sleeved on a rotatable lead screw, the movable seat is provided with an internal thread matched with the lead screw, the fixed mounting seat is disposed on a frame connected to one end of the lead screw, and the lead screw is in transmission connection with a numerical control stepper motor.
8. The cervical ablation device of claim 7, wherein the bottom of the movable seat is clamped on the sliding table and can move horizontally along the sliding table, and the extending direction of the sliding table corresponds to the length direction of the screw rod.
9. The cervical ablation device of any of claims 5 to 8, wherein both the A and B conductors are made of metallic copper.
10. The cervical ablation device according to any of claims 5 to 8, wherein the total length of the first coaxial cable line plus the second coaxial cable line is calculated according to the following equation:
propagation velocity of electromagnetic waves in cable
=1/
High voltage pulse width t =
L*
The characteristic impedance of the first coaxial cable line and the second coaxial cable line is designed to be Z0，Z0=
WhereinHigh voltage pulse width, in nanoseconds; l is the total length of the first coaxial cable and the second coaxial cable in unit meter;
the inductance value is the unit length of the coaxial cable, and the unit is H/m;
is the capacitance per unit length of the coaxial cable, i.e. the permittivity, in F/m.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202022194030.4U CN213758519U (en) | 2020-09-29 | 2020-09-29 | Cervical ablation device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202022194030.4U CN213758519U (en) | 2020-09-29 | 2020-09-29 | Cervical ablation device |
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| Publication Number | Publication Date |
|---|---|
| CN213758519U true CN213758519U (en) | 2021-07-23 |
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ID=76907899
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| CN202022194030.4U Active CN213758519U (en) | 2020-09-29 | 2020-09-29 | Cervical ablation device |
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| CN (1) | CN213758519U (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN113662654A (en) * | 2021-09-13 | 2021-11-19 | 杭州旸瑞医疗器械有限公司 | Ablation device and ablation catheter thereof |
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2020
- 2020-09-29 CN CN202022194030.4U patent/CN213758519U/en active Active
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN113662654A (en) * | 2021-09-13 | 2021-11-19 | 杭州旸瑞医疗器械有限公司 | Ablation device and ablation catheter thereof |
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