CN116636922A - Magnetic induction thermal ablation balloon catheter and ablation method - Google Patents
Magnetic induction thermal ablation balloon catheter and ablation method Download PDFInfo
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- 238000000034 method Methods 0.000 title claims abstract description 26
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- 239000007788 liquid Substances 0.000 claims description 4
- 210000001519 tissue Anatomy 0.000 abstract description 27
- 210000003492 pulmonary vein Anatomy 0.000 abstract description 12
- 210000004165 myocardium Anatomy 0.000 abstract description 9
- 239000011162 core material Substances 0.000 description 19
- 206010003658 Atrial Fibrillation Diseases 0.000 description 7
- 230000035699 permeability Effects 0.000 description 5
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 description 4
- 230000008014 freezing Effects 0.000 description 4
- 238000007710 freezing Methods 0.000 description 4
- 230000009286 beneficial effect Effects 0.000 description 2
- 210000004204 blood vessel Anatomy 0.000 description 2
- 229910017052 cobalt Inorganic materials 0.000 description 2
- 239000010941 cobalt Substances 0.000 description 2
- GUTLYIVDDKVIGB-UHFFFAOYSA-N cobalt atom Chemical compound [Co] GUTLYIVDDKVIGB-UHFFFAOYSA-N 0.000 description 2
- 229910052802 copper Inorganic materials 0.000 description 2
- 239000010949 copper Substances 0.000 description 2
- 230000005672 electromagnetic field Effects 0.000 description 2
- 230000005674 electromagnetic induction Effects 0.000 description 2
- 239000003302 ferromagnetic material Substances 0.000 description 2
- 230000004907 flux Effects 0.000 description 2
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 2
- 206010012289 Dementia Diseases 0.000 description 1
- 206010019280 Heart failures Diseases 0.000 description 1
- 206010020772 Hypertension Diseases 0.000 description 1
- 230000006978 adaptation Effects 0.000 description 1
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- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
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- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
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- A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
- A61B2018/00345—Vascular system
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61B2018/00345—Vascular system
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- A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
- A61B2018/00577—Ablation
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- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00994—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body combining two or more different kinds of non-mechanical energy or combining one or more non-mechanical energies with ultrasound
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
- A61B2018/0212—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques using an instrument inserted into a body lumen, e.g. catheter
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Abstract
The application provides a magnetic induction thermal ablation balloon catheter and an ablation method, wherein the magnetic induction thermal ablation balloon catheter comprises: the pipe body is provided with an energy channel extending along the axial direction of the pipe body; the balloon is arranged at the distal end of the tube body; the magnetic induction thermal ablation assembly is arranged at the distal end of the tube body and positioned in the balloon, and is connected with the energy supply assembly through an energy channel. The magnetic field is generated by the magnetic induction thermal ablation assembly, induced current is generated in cardiac muscle, thermal ablation of cardiac muscle tissue is realized through the thermal effect of the current, and not only can the ablation of cardiac muscle in the annular region of the pulmonary vein orifice be completed in a single ablation, but also the low-risk rapid ablation is realized without a complex control process.
Description
Technical Field
The application relates to the technical field of medical instruments, in particular to a magnetic induction thermal ablation balloon catheter and an ablation method.
Background
Atrial fibrillation (atrial fibrillation, AF) is one of the most common cardiac arrhythmias in the clinic. From the estimates, 3300 more than ten thousand people worldwide have AF. The incidence rate of AF increases with the age, and compared with non-atrial fibrillation patients of the same age, the atrial fibrillation patients often have poorer life quality and often have diseases such as hypertension, heart failure and the like, so the thromboembolic complications and the mortality rate of the patients are higher. Recent studies have linked the progression of AF with dementia. Therefore, the effective treatment of atrial fibrillation has important clinical significance. In long-term follow-up care, control of atrial fibrillation by intervention has been shown to improve quality of life.
Along with the development of technology, instruments for treating atrial fibrillation are also changed day by day, and the energy sources include radio frequency, refrigeration, laser, ultrasound and the like. Wherein the two energies of the main stream are radio frequency and refrigeration. The radio frequency adopts single point ablation, and although the speed of one ablation is higher, the complete annular ablation is completed, and the total consumption is longer. Freezing can complete annular ablation once, but the balloon is inflated, liquid refrigerant is cooled, and the air is discharged after ablation, so that the control process is complex and the risk is high.
Disclosure of Invention
In view of this, the embodiments of the present disclosure provide a magnetic induction thermal ablation balloon catheter and an ablation method to achieve the purpose of magnetic induction thermal ablation.
The embodiment of the specification provides the following technical scheme: a magnetically induced thermal ablation balloon catheter, comprising: the pipe body is provided with an energy channel extending along the axial direction of the pipe body; the balloon is arranged at the distal end of the tube body; the magnetic induction thermal ablation assembly is arranged at the distal end of the tube body and positioned in the balloon, and is connected with the energy supply assembly through an energy channel.
Further, the magnetic induction thermal ablation assembly comprises a magnetic core and a coil, wherein the magnetic core is arranged inside the distal end of the tube body, and the coil is wound on the outer wall of the distal end of the tube body.
Further, the magnetic induction thermal ablation assembly is a plurality of, and is axially distributed at intervals along the distal end of the tube body.
Further, the magnetic induction thermal ablation assembly comprises a magnetic core and a coil, wherein the magnetic core is arranged outside the far end of the tube body, and the coil is wound on the outer wall of the magnetic core.
Further, the plurality of magnetic induction thermal ablation components are distributed at intervals along the circumference of the outer part of the distal end of the tube body.
Further, the pipe body includes: the connecting fluid channel is provided with a connecting channel inlet and a connecting channel outlet, the connecting channel inlet is communicated with an external liquid supply device, and the connecting fluid channel is enclosed into a hollow tubular structure; the annular fluid channel is arranged at one end of the connecting fluid channel, the annular fluid channel is provided with a plurality of annular channel inlets and a plurality of nozzles, the plurality of annular channel inlets are connected with the plurality of connecting channel outlets in a one-to-one correspondence manner, the plurality of nozzles are arranged at intervals along the circumferential direction of the annular fluid channel, and the axis of the annular fluid channel is collinear with the axis of the tubular structure.
Further, the magnetically induced thermal ablation assembly is spaced from the plurality of nozzles.
The application provides an ablation method, which is carried out by adopting the magnetic induction thermal ablation balloon catheter, and comprises the following steps: expanding the balloon and abutting against the inner wall of the blood vessel; the magnetic induction thermal ablation assembly is powered by the energy channel, the magnetic field of the magnetic induction thermal ablation assembly generates induced current in myocardial tissue, and thermal ablation of myocardial tissue is realized by the thermal effect of the induced current.
The application also provides an ablation method which is carried out by adopting the magnetic induction thermal ablation balloon catheter, and comprises the following steps: the myocardial tissue cryoablation is realized by rapid refrigeration of the refrigerant; after the cryoablation is finished, the magnetic induction thermal ablation assembly is powered through the energy channel, the magnetic field of the magnetic induction thermal ablation assembly generates induced current in myocardial tissue, and thermal ablation of the myocardial tissue is realized through the thermal effect of the induced current.
The application further provides an ablation method which is carried out by adopting the magnetic induction thermal ablation balloon catheter, and comprises the following steps: expanding the balloon and abutting against the inner wall of the blood vessel; the magnetic induction thermal ablation assembly is powered by an energy channel, the magnetic field of the magnetic induction thermal ablation assembly generates induced current in myocardial tissue, and thermal ablation of myocardial tissue is realized by the thermal effect of the induced current; after the thermal ablation is finished, the myocardial tissue is rapidly cooled by the refrigerant to realize the myocardial tissue cryoablation.
Compared with the prior art, the beneficial effects that above-mentioned at least one technical scheme that this description embodiment adopted can reach include at least: the magnetic field is generated by the magnetic induction thermal ablation assembly, induced current is generated in cardiac muscle, thermal ablation of cardiac muscle tissue is realized through the thermal effect of the current, and not only can the ablation of cardiac muscle in the annular region of the pulmonary vein orifice be completed in a single ablation, but also the low-risk rapid ablation is realized without a complex control process.
Drawings
In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings that are needed in the embodiments will be briefly described below, and it is obvious that the drawings in the following description are only some embodiments of the present application, and that other drawings can be obtained according to these drawings without inventive effort for a person skilled in the art.
FIG. 1 is a schematic view of a first embodiment of the present application;
FIG. 2 is a schematic diagram of a second embodiment of the present application;
fig. 3 is a schematic view of the structure of the coil when it is fitted to the pulmonary vein.
Reference numerals in the drawings: 10. a tube body; 20. a balloon; 30. a magnetic induction thermal ablation assembly; 31. a magnetic core; 32. a coil.
Detailed Description
Embodiments of the present application will be described in detail below with reference to the accompanying drawings.
It should be noted that, without conflict, the embodiments of the present application and features of the embodiments may be combined with each other. The application will be described in detail below with reference to the drawings in connection with embodiments.
The embodiment of the application provides a magnetic induction thermal ablation balloon catheter, which comprises a tube body 10, a balloon 20 and a magnetic induction thermal ablation assembly 30. The tube body 10 is provided with an energy channel extending axially along the tube body 10; the balloon 20 is disposed at the distal end of the tube 10; a magnetic induction thermal ablation assembly 30 is disposed at the distal end of the tube body 10 and within the balloon 20, the magnetic induction thermal ablation assembly 30 being connected to an energy supply assembly by an energy passageway.
The magnetic field is generated by the magnetic induction thermal ablation assembly 30, induced current is generated in cardiac muscle, thermal ablation of cardiac muscle tissue is realized through the thermal effect of the current, and not only can the ablation of cardiac muscle in the annular region of the pulmonary vein orifice be completed in a single ablation, but also low-risk rapid ablation can be realized without a complex control process.
As shown in fig. 1, the magnetic induction thermal ablation assembly 30 in the first embodiment of the present application includes a magnetic core 31 and a coil 32, the magnetic core 31 being disposed inside the distal end of the tube body 10, and the coil 32 being wound around the outer wall of the distal end of the tube body 10.
In this embodiment, the tube body 10 is a solid structure, the inside of which is filled with ferromagnetic material to form a magnetic core 31, and a corresponding coil 32 is wound around the outside of the tube body 10 at the position of the magnetic core 31 to form the magnetic induction thermal ablation assembly 30. In use, the magnetic induction thermal ablation balloon catheter of the application is abutted against the position to be ablated through the sheath tube and the dilator. After being energized, the magnetic induction thermal ablation assembly 30 with current generates a magnetic field, and myocardial cells are affected by the electromagnetic field, and ablation is achieved due to heat generated by electromagnetic induction.
Preferably, the magnetic induction thermal ablation assembly 30 is a plurality of spaced axially along the distal end of the tube body 10. By providing a plurality of magnetically induced thermal ablation assemblies 30, the overall device ablation efficiency can be improved and the time required for ablation shortened.
As shown in fig. 2, the magnetic induction thermal ablation assembly 30 in the second embodiment of the present application includes a magnetic core 31 and a coil 32, the magnetic core 31 being disposed outside the distal end of the tube body 10, the coil 32 being wound around the outer wall of the magnetic core 31.
Specifically, the pipe body 10 is made of a hollow structure, so that other instruments can be conveniently penetrated in the hollow structure, and the cooperation of the instruments and the hollow structure is realized. The magnetic core 31 is arranged outside the distal end of the tube body 10 in an external fixing manner, and the coil 32 is wound in cooperation with the magnetic core 31 to achieve the purpose of generating a magnetic field when energized. In use, the magnetic induction thermal ablation balloon catheter of the application is abutted against the position to be ablated through the sheath tube and the dilator. After being energized, the magnetic induction thermal ablation assembly 30 with current generates a magnetic field, and myocardial cells are affected by the electromagnetic field, and ablation is achieved due to heat generated by electromagnetic induction.
Preferably, the magnetic induction thermal ablation assembly 30 is a plurality of spaced circumferentially along the exterior of the distal end of the tube body 10. By providing a plurality of magnetically induced thermal ablation assemblies 30, the overall device ablation efficiency can be improved and the time required for ablation shortened.
The tubular body 10 in the embodiment of the present application includes a connection fluid passage and an annular fluid passage. The connecting fluid channel is provided with a connecting channel inlet and a connecting channel outlet, the connecting channel inlet is communicated with an external liquid supply device, and the connecting fluid channel is enclosed into a hollow tubular structure; the annular fluid channel is arranged at one end of the connecting fluid channel, the annular fluid channel is provided with a plurality of annular channel inlets and a plurality of nozzles, the plurality of annular channel inlets are connected with the plurality of connecting channel outlets in a one-to-one correspondence manner, the plurality of nozzles are arranged at intervals along the circumferential direction of the annular fluid channel, and the axis of the annular fluid channel is collinear with the axis of the tubular structure.
The device can realize cryoablation by arranging the connecting fluid channel and the annular fluid channel, and the cryoablation and the thermal ablation can be used alternately, and one of the two can be selected for use according to different requirements, so that the adaptation range of the device is wider.
Preferably, the magnetically induced thermal ablation assembly 30 is spaced from the plurality of jets. The magnetic induction thermal ablation assembly 30 is arranged at the position of the nozzle in a staggered manner, so that interference between the nozzle and the magnetic induction thermal ablation assembly can be effectively avoided.
Taking the structure of the first embodiment as an example, how the required ablation time length is known by the preset increase of the ablation temperature is described.
The maximum current that the wire can bear is I m The angular frequency of the alternating current is omega, and at any time point t 0 When the current on the wire is I, then:
I＝I m ·sin(ωt 0 )
the number of turns of the coil is n, the magnetic permeability of the magnetic core material is mu, and the magnetic induction intensity generated by the coil is B, so that:
B＝μnI＝μ·n·I m ·sin(ωt 0 )
the magnetic core has magnetic permeability of mu and magnetic flux ofThe area of the pulmonary vein 40 surrounding the coil is S, and the induced electromotive force of the coil is epsilon:
maximum induced electromotive force epsilon max The effective value of the induced electromotive force is U:
ε max ＝μ·n·I m ·ω·S，
as shown in FIG. 3, the internal circumference of the pulmonary vein 40 where the coil effect is greatest is O, and the area of the pulmonary vein 40 is S Ring(s) When the resistivity of the myocardial tissue of the human body is ρ (ρ=17500 Ω·m according to common knowledge in the art), the resistance of the spherical dotted line portion is R:
in summary, the power dissipated by the induced electromotive force on the pulmonary vein 40 is:
in addition:
the current frequency of the alternating current is f, then: ω=2pi f
The pulmonary vein 40 has an inner diameter D, the area of the pulmonary vein 40 surrounding the coil:inner perimeter of pulmonary vein 40: o=pi D and,
the pulmonary vein 40 has a thickness d, a coil length L,S ring(s) ≈d·L
The density of human myocardial tissue is approximately 1000, the mass of human myocardial tissue: m=s Ring(s) L×10 3 ＝πd(D+d)L×10 3 ，
Since 70% of the human tissue is water, the specific heat capacity C of the human tissue is approximately water, C is approximately 4.2X10 3 。
Let d=15×10 -3 m、d＝1×10 -3 m, f=460 kHz according toThe relationship between the ablation duration and the elevated temperature at the time of ablation is:
the magnetic induction intensity generated by the coil is directly related to the magnetic permeability of the magnetic core, the number of turns of the coil and the maximum current which can be passed by the lead, and the larger the magnetic induction intensity generated by the coil is, the larger the magnetic flux is, so that the time consumption is shorter when the same delta T is obtained. This is also demonstrated by the above formula.
For this purpose, ferromagnetic materials with a high magnetic permeability, for example cobalt-based amorphous alloys, are chosen among the existing materials, whose magnetic permeability is 1.256H/m. Meanwhile, copper which can bear large current is selected as a wire, the maximum current which can be borne by copper is 6-10A/mm < 2 >, and the maximum current which can be borne by a copper wire with the outer diameter of 0.1mm is 0.07A.
Taking cobalt-based amorphous alloy as a magnetic core, a copper wire with an outer diameter of 0.1mm is wound around a coil, and the number of winding turns is 200 as an example:
when the ablation temperature needs to be increased by 30 ℃, the ablation duration is as follows: t.apprxeq.0.432. DELTA.T.apprxeq.12.96 (S).
The application provides an ablation method, which is carried out by adopting the magnetic induction thermal ablation balloon catheter, and comprises the following steps:
expanding balloon 20 and against the inner wall of the vessel;
the magnetic induction thermal ablation assembly 30 is powered by the energy channel, the magnetic field of the magnetic induction thermal ablation assembly 30 generates induced current in the myocardial tissue, and thermal ablation of the myocardial tissue is achieved by the thermal effect of the induced current. In this embodiment, thermal ablation of myocardial tissue is achieved only by the magnetic induction thermal ablation assembly 30, thereby achieving the desired ablation effect.
The application also provides an ablation method which is carried out by adopting the magnetic induction thermal ablation balloon catheter, and comprises the following steps:
the myocardial tissue cryoablation is realized by rapid refrigeration of the refrigerant;
after the cryoablation is finished, the magnetic induction thermal ablation assembly 30 is powered through the energy channel, the magnetic field of the magnetic induction thermal ablation assembly 30 generates induced current in myocardial tissue, and thermal ablation of the myocardial tissue is realized through the thermal effect of the induced current.
In this embodiment, cryoablation and thermal ablation are used in combination, specifically, cryoablation is performed first, and thermal ablation is performed after the cryoablation is completed, so that an intended ablation effect can be achieved.
Of course, in another embodiment, the following ablation method is provided, which is also performed using the magnetic induction thermal ablation balloon catheter described above, and the ablation method includes the following steps:
expanding balloon 20 and against the inner wall of the vessel;
supplying energy to the magnetic induction thermal ablation assembly 30 through an energy channel, wherein the magnetic field of the magnetic induction thermal ablation assembly 30 generates induced current in myocardial tissue, and thermal ablation of the myocardial tissue is realized through the thermal effect of the induced current;
after the thermal ablation is finished, the myocardial tissue is rapidly cooled by the refrigerant to realize the myocardial tissue cryoablation.
In the embodiment, the cryoablation and the thermal ablation are combined, and the specific operation is to perform the thermal ablation first and perform the cryoablation after the thermal ablation is finished, so that the expected ablation effect can be achieved.
The application has the following beneficial effects:
1. relative to radio frequency and freezing, rapid ablation can be achieved.
2. There is no high pressure refrigerant control relative to freezing, and therefore, there is no risk of refrigerant leakage.
3. Compared with radio frequency, in the ablation process, the operation is simple.
4. Compared with freezing, the pressure and the temperature of the refrigerant do not need to be controlled in a closed loop in the ablation process, so the control process is simple.
Because the cryoablation is to rapidly refrigerate by a high-pressure refrigerant to realize the cryonecrosis of myocardial cells, the ablation effect is realized. In the process, the pressure value and the temperature value need to be strictly controlled, otherwise, too high pressure can cause leakage of the refrigerant, and too low temperature can cause complications to be increased and is not easy to treat.
The foregoing description of the embodiments of the application is not intended to limit the scope of the application, so that the substitution of equivalent elements or equivalent variations and modifications within the scope of the application shall fall within the scope of the patent. In addition, the technical characteristics and technical scheme, technical characteristics and technical scheme can be freely combined for use.
Claims (10)
1. A magnetically induced thermal ablation balloon catheter, comprising:
the pipe body (10) is provided with an energy channel extending along the axial direction of the pipe body (10);
a balloon (20) arranged at the distal end of the tube body (10);
and the magnetic induction thermal ablation assembly (30) is arranged at the distal end of the tube body (10) and positioned in the balloon (20), and the magnetic induction thermal ablation assembly (30) is connected with the energy supply assembly through the energy channel.
2. The magnetic induction thermal ablation balloon catheter of claim 1, wherein the magnetic induction thermal ablation assembly (30) comprises a magnetic core (31) and a coil (32), the magnetic core (31) is disposed inside the distal end of the tube body (10), and the coil (32) is wound around the distal outer wall of the tube body (10).
3. The magnetically induced thermal ablation balloon catheter of claim 2, wherein the plurality of magnetically induced thermal ablation assemblies (30) are axially spaced along the distal end of the tube body (10).
4. The magnetic induction thermal ablation balloon catheter according to claim 1, wherein the magnetic induction thermal ablation assembly (30) comprises a magnetic core (31) and a coil (32), the magnetic core (31) is disposed outside the distal end of the tube body (10), and the coil (32) is wound around the outer wall of the magnetic core (31).
5. The magnetically induced thermal ablation balloon catheter of claim 4, wherein the plurality of magnetically induced thermal ablation assemblies (30) are circumferentially spaced along the distal exterior of the tube body (10).
6. The magnetically induced thermal ablation balloon catheter according to any one of claims 1 to 5, wherein the tube (10) comprises:
the connecting fluid channel is provided with a connecting channel inlet and a connecting channel outlet, the connecting channel inlet is communicated with an external liquid supply device, and the connecting fluid channel is enclosed into a hollow tubular structure;
the annular fluid channel is arranged at one end of the connecting fluid channel, the annular fluid channel is provided with a plurality of annular channel inlets and a plurality of nozzles, the annular channel inlets are connected with the connecting channel outlets in a one-to-one correspondence manner, the nozzles are arranged at intervals along the circumferential direction of the annular fluid channel, and the axis of the annular fluid channel is collinear with the axis of the tubular structure.
7. The magnetically induced thermal ablation balloon catheter of claim 6, wherein a magnetically induced thermal ablation assembly (30) is spaced apart from a plurality of the nozzles.
8. An ablation method using the magnetically induced thermal ablation balloon catheter of any one of claims 1 to 7, characterized in that the ablation method comprises the steps of:
expanding the balloon (20) and abutting against the inner wall of the vessel;
the magnetic induction thermal ablation assembly (30) is powered through the energy channel, the magnetic field of the magnetic induction thermal ablation assembly (30) generates induction current in myocardial tissue, and thermal ablation of the myocardial tissue is achieved through the thermal effect of the induction current.
9. An ablation method using the magnetically induced thermal ablation balloon catheter of any one of claims 1 to 7, characterized in that the ablation method comprises the steps of:
the myocardial tissue cryoablation is realized by rapid refrigeration of the refrigerant;
after the cryoablation is finished, the magnetic induction thermal ablation assembly (30) is powered through the energy channel, the magnetic field of the magnetic induction thermal ablation assembly (30) generates induced current in myocardial tissue, and thermal ablation of myocardial tissue is realized through the thermal effect of the induced current.
10. An ablation method using the magnetically induced thermal ablation balloon catheter of any one of claims 1 to 7, characterized in that the ablation method comprises the steps of:
expanding the balloon (20) and abutting against the inner wall of the vessel;
the magnetic induction thermal ablation assembly (30) is powered through the energy channel, the magnetic field of the magnetic induction thermal ablation assembly (30) generates induced current in myocardial tissue, and thermal ablation of the myocardial tissue is realized through the thermal effect of the induced current;
after the thermal ablation is finished, the myocardial tissue is rapidly cooled by the refrigerant to realize the myocardial tissue cryoablation.
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| CN202310539011.6A CN116636922B (en) | 2023-05-12 | 2023-05-12 | Magnetic induction thermal ablation balloon catheter and ablation method |
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| CN116636922B (en) | 2024-05-03 |
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