CN216090742U - Radio frequency ablation device - Google Patents

Abstract

The utility model provides radio frequency ablation equipment, which comprises a first electrode assembly and a second electrode assembly, wherein the first electrode assembly comprises a first electrode tip, and the first electrode tip is provided with a first electrode; the second electrode assembly includes a second electrode tip having a second electrode; the first electrode tip comprises a first magnetic part, the second electrode tip comprises a second magnetic part, and the first magnetic part and the second magnetic part are attracted with each other so that the first electrode tip and the second electrode tip are relatively fixed and tissues to be ablated positioned between the first electrode and the second electrode are ablated through the first electrode and the second electrode. The radiofrequency ablation device can solve the problem that the ablation effect of the radiofrequency ablation device in the prior art is not ideal.

Description

Radio frequency ablation device

Technical Field

The utility model relates to the field of medical instruments, in particular to radio frequency ablation equipment.

Background

Ablation is a common measure for treating atrial fibrillation, and the principle of ablation is to create one or more ablation lines in heart tissue, cause tissue necrosis, and cut off abnormal electrical signal conduction for treating atrial fibrillation.

The current ablation treatment is divided into surgical ablation and medical intervention ablation, the surgical ablation is characterized by good curative effect and low recurrence rate after operation, but the obvious defects are that the wound is large and the postoperative recovery is slow. Medical interventional ablation is favored by more and more patients because of small wound and fast recovery, but the medical ablation is point ablation, and the biggest defect is that a complete ablation line is difficult to form; and the single-side wall-attaching type operation is adopted during ablation, the ablation depth is limited, the complete dehydration and denaturation of tissues from inside to outside are difficult to ensure, the ablation is not thorough when the ablation power is small in the operation, the power is high, the control is difficult, and the phenomena of excessive tissue necrosis, even burnthrough and burnout exist in the ablation, so the success rate of the internal medicine interventional ablation is much lower than that of the surgery.

SUMMERY OF THE UTILITY MODEL

The utility model mainly aims to provide radio frequency ablation equipment to solve the problems of large surgical ablation wound, slow postoperative recovery, limited angle during use and inconvenient operation in the prior art; the problem that the output power cannot be adjusted timely according to the ablation effect due to constant internal medicine interventional ablation energy at present, so that the excessive burn or wall impermeability is caused is solved; the problem of current surgery ablation equipment need the apparatus in addition to carry out the mark survey after melting, complex operation is solved.

In order to achieve the above object, the present invention provides a radio frequency ablation apparatus comprising: a first electrode assembly including a first electrode tip having a first electrode; a second electrode assembly including a second electrode tip having a second electrode; the first electrode tip comprises a first magnetic part, the second electrode tip comprises a second magnetic part, and the first magnetic part and the second magnetic part are attracted with each other so that the first electrode tip and the second electrode tip are relatively fixed and tissues to be ablated positioned between the first electrode and the second electrode are ablated through the first electrode and the second electrode.

Further, the radiofrequency ablation device further comprises an ablation circuit, and the first electrode and the second electrode are arranged on the ablation circuit to adjust radiofrequency energy between the first electrode and the second electrode for ablation by testing impedance between the first electrode and the second electrode.

Furthermore, the radio frequency ablation device also comprises a radio frequency host which is connected with the first electrode and the second electrode so as to detect the impedance between the first electrode and the second electrode and adjust the radio frequency power between the first electrode and the second electrode according to the detected impedance information.

Furthermore, the first electrodes and the second electrodes are multiple, and the multiple first electrodes and the multiple second electrodes are arranged in a matched mode.

Furthermore, the first electrode tip and the second electrode tip are both in a strip shape, the plurality of first electrodes are arranged at intervals along the extending direction of the first electrode tip, and the plurality of second electrodes are arranged at intervals along the extending direction of the second electrode tip.

Further, the first electrode tip includes a positioning member, and the first electrode tip is positioned on the epicardium by the positioning member.

Furthermore, the first electrode end is strip-shaped, the positioning pieces are multiple, and the positioning pieces are arranged along the extending direction of the first electrode end.

Further, the first electrode tip includes a first protective sheath, at least a portion of the first electrode being disposed within the first protective sheath; the positioning pieces are arranged in pairs, and the two positioning pieces in pairs are arranged on two opposite sides of the first protective sheath; and/or, a plurality of positioning members are disposed on one side of the first protective sheath.

Further, the first electrode has an electrode face disposed toward the tissue to be ablated, and the first protective sheath has a protective sheath face disposed toward the tissue to be ablated; wherein, the electrode surface is positioned at one side of the protective sheath surface close to the tissue to be ablated.

Furthermore, the number of the first electrodes is multiple, and the multiple first electrodes are arranged at intervals along the extending direction of the first electrode tip; the minimum distances between the electrode surfaces of the first electrodes and the protecting sheath surfaces are the same.

Further, the first protective sheath is made of a flexible material so that the first protective sheath is bendably disposed.

Further, the positioning piece is of a sucker structure.

Further, the first electrode tip includes a first protective sheath, at least a portion of the first electrode being disposed within the first protective sheath; the first electrodes are arranged at intervals along the extending direction of the first electrode tip; at least one first electrode in the plurality of first electrodes is provided with a cooling hole for circulating cooling fluid; and/or a cooling pipeline for circulating cooling fluid is arranged in the first protective sheath.

Further, at least one of the plurality of first electrodes is provided with 1 to 4 cooling holes.

Furthermore, first magnetic part and second magnetic part are a plurality ofly, and first electrode end and second electrode end are the bar, and a plurality of first magnetic part are arranged along the extending direction interval of first electrode end, and a plurality of second magnetic part are arranged along the extending direction interval of second electrode end.

Furthermore, the first electrodes and the second electrodes are all multiple, the multiple first magnetic pieces and the multiple first electrodes are arranged in a staggered and spaced mode, and the multiple second magnetic pieces and the multiple second electrodes are arranged in a staggered and spaced mode.

Furthermore, the adjacent first electrode and the first magnetic part are arranged in an insulating mode, and the adjacent second electrode and the second magnetic part are arranged in an insulating mode.

Furthermore, insulating paint is sprayed on the opposite surfaces between the adjacent first electrodes and the first magnetic parts, or insulating partition plates are arranged between the adjacent first electrodes and the first magnetic parts; insulating paint is sprayed on the opposite surfaces between the adjacent second electrodes and the second magnetic parts, or insulating partition plates are arranged between the adjacent second electrodes and the second magnetic parts.

Furthermore, the outer surfaces of the first magnetic part and the second magnetic part are coated with insulating layers.

Furthermore, the first electrode, the first magnetic part, the second electrode and the second magnetic part are all connected with an independent energizing circuit to be controlled independently.

Furthermore, the number of the first electrodes is multiple, and the energizing circuits of the two first electrodes are independently arranged to form a mapping electrode pair, so that the energizing circuits are utilized to detect the electric signal transmission condition of the ablated tissue to be ablated; and/or the second electrodes are multiple, the energizing circuits of the two second electrodes are independently arranged to form a mapping electrode pair, so that the energizing circuits are utilized to detect the electric signal transmission condition of the ablated tissue to be ablated; and/or the energizing circuits of the first electrode and the second electrode are independently arranged to form a mapping electrode pair, so that the energizing circuits are used for detecting the electric signal transmission condition after the ablation of the tissue to be ablated.

Further, the first electrode terminal and the second electrode terminal are both multiple.

Further, the second electrode tip includes a second protective sheath, and the second electrode is disposed on the second protective sheath; the second electrode is made of a metallic material including at least one of the following materials: platinum, platinum-iron alloy, tantalum, gold plated beryllium bronze; and/or the second protective sheath is made of a developer material, the composition of which includes barium sulfate.

Furthermore, the second electrode is arranged at intervals along the extending direction of the second protective sheath, is sleeved on the second protective sheath, and enables the surface of the electrode to be higher than the surface of the second protective sheath.

By applying the technical scheme of the utility model, the radio frequency ablation equipment comprises a first electrode assembly and a second electrode assembly, wherein the first electrode assembly comprises a first electrode tip with a first electrode, the second electrode assembly comprises a second electrode tip with a second electrode, the first electrode tip comprises a first magnetic part, the second electrode tip comprises a second magnetic part, and the first magnetic part and the second magnetic part are mutually attracted so as to relatively fix the first electrode tip and the second electrode tip and ablate tissues to be ablated between the first electrode and the second electrode through the first electrode and the second electrode. When the ablation instrument is used specifically, the first electrode assembly and the second electrode assembly are respectively used as an epicardial electrode and an endocardial electrode, so that the first electrode assembly and the second electrode assembly respectively act on the epicardium and the endocardium to achieve simultaneous ablation of the epicardium and the endocardium, and further achieve a good ablation effect; therefore, the radio frequency ablation device can solve the problem that the ablation effect of the radio frequency ablation device in the prior art is not ideal.

In addition, the radio frequency ablation equipment in the application can realize internal and surgical hybrid ablation, the technical wound is small, the problems of large surgical ablation wound and slow recovery in the prior art are solved, meanwhile, synchronous ablation can be performed from the epicardium and the endocardium, the output power is adjusted by testing the actual impedance between tissues, the operation is accurate and safe, and the machine alarm ablation is finished after the impedance reaches a certain resistance value, so that excessive ablation is avoided. In addition, the first electrode assembly can be independently used for acting on the epicardium to realize the ablation effect, and the second electrode assembly can be independently used for acting on the endocardium to realize the ablation effect.

No matter endocardial ablation or epicardial ablation or simultaneous ablation of the endocardial and the epicardial, a single electrode assembly or an electrode assembly working in cooperation can be mapped timely, the ablation effect is monitored, the problem that external instruments are still needed for mapping after current ablation and the problem that point mapping is needed is solved, and the surgical ablation effect is improved.

Drawings

The accompanying drawings, which are incorporated in and constitute a part of this application, illustrate embodiments of the utility model and, together with the description, serve to explain the utility model and not to limit the utility model. In the drawings:

FIG. 1 is a schematic structural diagram illustrating one state of a first embodiment of a first electrode assembly of a radio frequency ablation device in an alternative embodiment of the utility model;

FIG. 2 is a schematic structural diagram illustrating another state of the first embodiment of the first electrode assembly of the RF ablation device in an alternative embodiment of the utility model;

FIG. 3 is a schematic diagram showing the internal structure of one embodiment of the first electrode tip of the first electrode assembly of the RF ablation device of FIG. 1;

fig. 4 shows a cross-sectional view of a first electrode tip of a first electrode assembly of the radio frequency ablation device of fig. 2;

fig. 5 is a schematic diagram showing the structural arrangement of the shielding side eaves of the first electrode assembly of the radiofrequency ablation device in fig. 1;

fig. 6 shows a cross-sectional view of another embodiment of a first electrode tip of a first electrode assembly of the radio frequency ablation device of fig. 1;

fig. 7 is a schematic view of the first electrode tip of the second electrode assembly of an alternative radio frequency ablation device in accordance with the utility model;

FIG. 8 shows an enlarged partial view of the second electrode assembly of the radio frequency ablation device of FIG. 7;

fig. 9 shows an enlarged view of a portion a of the second electrode assembly of the rf ablation device of fig. 8;

fig. 10 is a schematic structural diagram of a radio frequency host of an alternative radio frequency ablation device in accordance with the present invention;

fig. 11 illustrates an assembled view of the rf main body, the first electrode assembly and the second electrode assembly of an alternative rf ablation device in accordance with the present invention;

FIG. 12 is a schematic diagram of the RF ablation device of the present invention in ablation treatment of tissue to be ablated;

fig. 13 shows a fit between the first and second electrodes of the radio frequency ablation device of the present invention and the tissue to be ablated;

FIG. 14 shows an ablation schematic for one state of the radio frequency ablation device of the present invention;

FIG. 15 shows an ablation schematic of another state of the radio frequency ablation device of the present invention;

fig. 16 shows a wiring schematic between the rf main unit and the first and second electrode assemblies of the rf ablation device of the present invention;

FIG. 17 is a schematic structural view of a second embodiment of the first electrode assembly of the RF ablation device of the present invention;

FIG. 18 is a schematic structural view of a second embodiment of the second electrode assembly of the RF ablation device of the present invention;

fig. 19 shows a mating view of the first and second electrodes of another embodiment of the ablation device of the utility model with tissue to be ablated.

Wherein the figures include the following reference numerals:

100. a first electrode assembly;

110. a first electrode tip; 111. a first electrode; 1110. an electrode surface; 112. a first magnetic member; 113. a first protective sheath; 1130. protecting the sheath surface; 114. a cooling hole; 115. shielding the side eaves;

117. a positioning member; 1171. attracting the inner wall; 1172. attracting the outer wall; 1173. attracting the cavity;

1174. a first suction port; 1175. a second suction port; 1176. an air flow channel;

120. a wire laying groove;

200. a second electrode assembly;

210. a second electrode tip; 211. a second electrode; 212. a second magnetic member; 213. a developing member; 214. a second protective sheath;

310. a radio frequency host; 311. an ablation interface; 312. an electromagnetic interface; 313. a display screen; 320. an ablation circuit; 330. an ablation range; 340. the tissue is to be ablated.

Detailed Description

It should be noted that the embodiments and features of the embodiments in the present application may be combined with each other without conflict. The present invention will be described in detail below with reference to the embodiments with reference to the attached drawings.

Referring to fig. 1 to 19, the rf ablation apparatus includes a first electrode assembly 100 and a second electrode assembly 200, the first electrode assembly 100 includes a first electrode tip 110, and the first electrode tip 110 has a first electrode 111; the second electrode assembly 200 includes a second electrode tip 210, the second electrode tip 210 having a second electrode 211; the first electrode tip 110 includes a first magnetic member 112, the second electrode tip 210 includes a second magnetic member 212, and the first magnetic member 112 and the second magnetic member 212 attract each other, so that the first electrode tip 110 and the second electrode tip 210 are relatively fixed, and the tissue 340 to be ablated between the first electrode 111 and the second electrode 211 is ablated by the first electrode 111 and the second electrode 211.

In the rf ablation device of the present invention, the rf ablation device includes a first electrode assembly 100 and a second electrode assembly 200, the first electrode assembly 100 includes a first electrode tip 110 having a first electrode 111, the second electrode assembly 200 includes a second electrode tip 210 having a second electrode 211, the first electrode tip 110 includes a first magnetic member 112, the second electrode tip 210 includes a second magnetic member 212, and the first magnetic member 112 and the second magnetic member 212 are attracted to each other, so that the first electrode tip 110 and the second electrode tip 210 are relatively fixed, and the tissue 340 to be ablated between the first electrode 111 and the second electrode 211 is ablated by the first electrode 111 and the second electrode 211. In particular use, the first electrode assembly 100 and the second electrode assembly 200 are respectively used as an epicardial electrode and an endocardial electrode, so that the first electrode assembly 100 and the second electrode assembly 200 respectively act on the epicardium and the endocardium to achieve simultaneous ablation of the epicardium and the endocardium, thereby achieving good ablation effect; therefore, the radio frequency ablation device can solve the problems that the existing radio frequency ablation device works in a wall-attaching mode on one side during internal and surgical ablation, the ablation depth is limited, complete dehydration and wall penetration of tissues from inside to outside are difficult to guarantee, and the problem that the ablation effect of the radio frequency ablation device in the prior art is not ideal is solved.

Because the internal medicine intervenes and melts energy invariable, can't be in good time according to melting effect adjustment output, lead to the problem of overburning or not penetrating the wall. The cardiac surgery is dynamic ablation, which measures impedance and detects signals in time, and adjusts the power correspondingly according to different impedances, but the surgical ablation has larger trauma and slow postoperative recovery. The endocardium and the epicardium of the radio frequency ablation equipment are used in a combined and matched mode, the power is dynamically changed in real time, and the problems of overburning or wall impermeability and tissue necrosis and even burnthrough are solved.

Therefore, the radio frequency ablation equipment can realize the internal and surgical hybrid ablation, the technical trauma is small, the problems of large surgical ablation trauma and slow recovery in the prior art are solved, the epicardium and the endocardium can be synchronously ablated in a combined mode, the output power is adjusted by testing the actual impedance between tissues, the precision and the safety are realized, the machine alarm ablation is finished after the impedance reaches a certain resistance value, and the excessive ablation is avoided.

Specifically, the rf ablation device further includes an ablation circuit 320, and the first electrode 111 and the second electrode 211 are both disposed on the ablation circuit 320 to adjust rf energy between the first electrode 111 and the second electrode 211 for ablation by testing impedance between the first electrode 111 and the second electrode 211. The impedance between the first electrode 111 and the second electrode 211 is tested in real time, the radio frequency power between the first electrode 111 and the second electrode 211 is adjusted according to the impedance between the first electrode 111 and the second electrode 211 which is detected in real time, and the machine alarm is given to finish ablation after the impedance reaches a certain resistance value, so that excessive ablation is avoided, the problems that in the prior art, the ablation depth of an implanted ablation single side is limited, and complete dehydration and denaturation of tissues from inside to outside are difficult to ensure are solved, and meanwhile, the problem that the radio frequency power is not easy to control is solved, the ablation is incomplete due to low power, excessive ablation is caused by high power, and the phenomena of tissue necrosis, even burnthrough and burning leakage are caused.

In a specific ablation process, the impedance of the ablated tissue between the electrodes is changed from low to high; in the first stage of ablation, the impedance of the ablated tissue between the electrodes is gradually increased, and the radio frequency power is kept unchanged so as to accelerate the vibration of molecules in cells; in the second stage of ablation, along with the increase of the impedance of the ablated tissue between the electrodes, the radio frequency power is gradually increased, when the impedance of the ablated tissue between the electrodes is increased to the first preset value, the radio frequency power is also increased to the preset maximum value, and in the ablation stage, cells are rapidly dehydrated to generate irreversible change; in the third stage of ablation, along with the continuous increase of the impedance of the ablated tissue between the electrodes, the radio frequency power is gradually reduced so as to ensure the ablation thoroughness and prevent the phenomenon that the tissue surface is scabbed or a patient is injured due to the high-power radio frequency output; and prompting to end the ablation until the impedance of the ablated tissue between the electrodes is increased to a second preset value.

Preferably, as shown in fig. 2 and 7, each of the first electrodes 111 and the second electrodes 211 is provided in plurality, and the plurality of first electrodes 111 and the plurality of second electrodes 211 are disposed in cooperation with each other; by arranging the plurality of first electrodes 111 and the plurality of second electrodes 211, the plurality of first electrodes 111 and the plurality of second electrodes 211 can act on corresponding tissues at the same time, so that the ablation effect is enhanced, and the ablation efficiency is improved.

Specifically, the first electrode tip 110 and the second electrode tip 210 are both strip-shaped, the plurality of first electrodes 111 are arranged at intervals along the extending direction of the first electrode tip 110, the plurality of second electrodes 211 are arranged at intervals along the extending direction of the second electrode tip 210, and each first electrode 111 is arranged in pairs with the corresponding second electrode 211; namely, the plurality of first electrodes 111 and the plurality of second electrodes 211 act on the corresponding tissues at the same time to form a complete ablation line, so that the ablation effect is ensured, and the ablation efficiency is improved; the first electrodes 111 are arranged at intervals, and the second electrodes 211 are arranged at intervals, so that mutual influence between two adjacent first electrodes 111 and between two adjacent second electrodes 211 can be avoided.

In the present embodiment, the number of the first electrodes 111 and the number of the second electrodes 211 are each 2 to 10.

Specifically, the first electrode 111 and the second electrode 211 are operated independently of each other, i.e., the number of working electrodes can be controlled.

In this embodiment, the first electrode tip 110 further includes a positioning member 117, and the first electrode tip 110 is positioned on the epicardium by the positioning member 117. Specifically, the positioning members 117 are arranged in pairs, and each pair of positioning members 117 relatively independently work during work, that is, the number of the working positioning members can be determined according to actual requirements.

Optionally, the positioning member 117 is a suction cup structure.

In this embodiment, the first electrode tip 110 further comprises a first protective sheath 113, at least a portion of the first electrode 111 being disposed within the first protective sheath 113; that is, the plurality of first electrodes 111 are disposed at intervals in the first protective sheath 113 in the extending direction of the first protective sheath 113.

Specifically, the first protective sheath 113 is made of a flexible material. Thus, the first protective sheath 113 can be made to oscillate in the X-Y-Z direction.

In the present embodiment, as shown in fig. 3, the first electrode 111 has an electrode face 1110 disposed toward the tissue to be ablated 340, and the first protective sheath 113 has a protective sheath face 1130 disposed toward the tissue to be ablated 340; wherein the electrode surface 1110 is located on the side of the protective sheath surface 1130 that is adjacent to the tissue 340 to be ablated.

In the present embodiment, the first electrode 111 is a plurality of first electrodes 111, and the plurality of first electrodes 111 are arranged at intervals along the extending direction of the first electrode tip 110; the minimum distances between the electrode faces 1110 and the protective sheath faces 1130 of the plurality of first electrodes 111 are all the same. The minimum distance between the electrode surface 1110 of the first electrode 111 and the protective sheath surface 1130 ranges from 0 mm to 0.5mm, and the first electrode can be fully contacted with the ablated surface due to the height difference, so that the ablation effect is ensured. The height difference between the electrode surface 1110 of the first electrode 111 and the protective sheath surface 1130 is preferably 0.2 mm.

In this embodiment, the electrode face 1110 and the protective sheath face 1130 are both planar.

In order to achieve cooling of the first electrode tip 110, as shown in fig. 2, the first electrodes 111 are plural, and the plural first electrodes 111 are arranged at intervals along the extending direction of the first electrode tip 110; at least one first electrode 111 of the plurality of first electrodes 111 is provided with a cooling hole 114 for flowing a cooling fluid; and/or a cooling pipe for circulating cooling fluid is provided in the first protective sheath 113. This embodiment protects the ablated tissue from excessive cauterization by providing cooling holes 114 for localized cooling during the ablation process.

In the present embodiment, at least one first electrode 111 of the plurality of first electrodes 111 is provided with 1 to 4 cooling holes 114. The number of cooling holes on each first electrode 111 is 0-4 to ensure temperature control during ablation.

Optionally, the first protective sheath 113 is made of a flexible material so that the first protective sheath 113 is bendably disposed.

Optionally, the first protective sheath 113 is tubular, and the plurality of first electrodes 111 are each disposed within a lumen of the first protective sheath 113.

Specifically, as shown in fig. 3 and 5, the positioning member 117 includes an inner attracting wall 1171 and an outer attracting wall 1172, an attracting cavity 1173, a first attracting port 1174 and a second attracting port 1175 communicated with the attracting cavity 1173 are formed between the inner attracting wall 1171 and the outer attracting wall 1172, and the first attracting port 1174 and the second attracting port 1175 have the same orientation.

The suction inner wall 1171 and the suction inner wall 1171 are both of a U-shaped structure, and the suction inner wall 1171 and the suction outer wall 1172 are arranged around the first protective sheath 113.

The positioning member 117 further includes an air flow channel 1176, and an air outlet end of the air flow channel 1176 is communicated with the attraction cavity 1173 so as to charge and exhaust air into the attraction cavity 1173 through the air flow channel 1176.

Optionally, the positioning member 117 is a plurality of positioning members 117, and the plurality of positioning members 117 are arranged along the extending direction of the first electrode tip 110, so that the first electrode tip 110 is stably positioned on the epicardium, and the positioning effect of the first electrode tip 110 is ensured.

Specifically, the positioning members 117 are arranged in pairs, and the two positioning members 117 in pairs are respectively arranged on two opposite sides of the first protective sheath 113, so as to ensure that the two sides of the first protective sheath 113 and the ablated tissue have good fitting degree, and further, the corresponding first electrode 111 can better act on the corresponding ablated tissue, and ensure the ablation effect.

Specifically, the positioning members 117 are disposed on one side of the first protective sheath 113 to ensure that the one side of the first protective sheath 113 and the ablated tissue have good fitting degree, so that the corresponding first electrode 111 can act on the corresponding ablated tissue better to ensure the ablation effect.

The plurality of pairs of positioning members 117 are arranged at intervals along the extending direction of the first protective sheath 113 to ensure the overall fit degree between the first protective sheath 113 and the ablated tissue, so that each first electrode 111 can better act on the corresponding ablated tissue, and the ablation effect is ensured.

Specifically, the first magnetic members 112 and the second magnetic members 212 are both multiple, the multiple first magnetic members 112 are arranged at intervals along the extending direction of the first electrode tip 110, and the multiple second magnetic members 212 are arranged at intervals along the extending direction of the second electrode tip 210, so as to ensure the overall fixing effect between the first electrode tip 110 and the second electrode tip 210.

Specifically, each pair of the first magnetic member 112 and the second magnetic member 212 work independently, i.e. the number of the magnetic members can be determined according to actual requirements.

Optionally, the magnetic force of the magnetic part is controllable and adjustable, a small magnetic force is used during initial positioning, and a large magnetic force is used during final positioning, so that the inner electrode assembly and the outer electrode assembly are flexible during initial positioning and firm after final positioning, the fitting degree of the electrodes is guaranteed, and the ablation effect is guaranteed.

Optionally, the plurality of first magnetic members 112 are each disposed within the lumen of the first protective sheath 113.

Optionally, the first magnetic member 112 is an electromagnet or a permanent magnet; and/or the second magnetic member 212 is an electromagnet or a permanent magnet.

Specifically, as shown in fig. 2, the plurality of first magnetic members 112 are each disposed within the first protective sheath 113, and the plurality of first magnetic members 112 are disposed at intervals along the extending direction of the first protective sheath 113. Preferably, the plurality of first magnetic members 112 and the plurality of first electrodes 111 are arranged to be staggered along the extending direction of the first protective sheath 113, so that the plurality of first electrodes 111 are arranged at intervals, i.e., the respective two first electrodes 111 are separated by each first magnetic member 112. When the magnetic piece works, each pair of the first magnetic piece and the second magnetic piece work relatively independently, namely the working quantity of the magnetic pieces can be determined according to actual requirements. The magnetic force of the magnetic part is controllable and adjustable, small magnetic force is used during initial positioning, and large magnetic force is used during final positioning, so that the inner electrode assembly and the outer electrode assembly are flexible during initial positioning, firm after final positioning, the fitting degree of the electrodes is guaranteed, and the ablation effect is guaranteed.

When the first magnetic member 112 is in a non-working state, i.e. when no magnetism is applied, the first electrode assembly can perform epicardial linear ablation on the outer membrane. In this embodiment, as shown in fig. 4, two opposite sides of the first protective sheath 113 are respectively provided with a shielding side eaves 115 to form a shielding protection effect on the first electrodes 111 and the first magnetic members 112 inside the first protective sheath 113, so as to prevent blood and the like of pericardial tissue from entering a region between the first protective sheath 113 and the epicardium during an ablation process to affect a tight adhesion degree between the first protective sheath 113 and the epicardium, and prevent measurement accuracy of a resistance value between the first electrode and the second electrode during ablation, thereby affecting an ablation effect.

In some embodiments, the first electrode 111 and the second electrode 211 are both multiple, the first magnetic members 112 are disposed alternately with the first electrodes 111, and the second magnetic members 212 are disposed alternately with the second electrodes 211.

In some embodiments, the adjacent first electrode 111 and the first magnetic member 112 are insulated from each other, and the adjacent second electrode 211 and the second magnetic member 212 are insulated from each other.

In some embodiments, the opposite surfaces between the adjacent first electrodes 111 and the first magnetic members 112 are both coated with insulating varnish, or an insulating partition plate is disposed between the adjacent first electrodes 111 and the first magnetic members 112; insulating paint is sprayed on the opposite surfaces between the adjacent second electrodes 211 and the second magnetic members 212, or an insulating partition plate is arranged between the adjacent second electrodes 211 and the second magnetic members 212.

In some embodiments, the outer surfaces of the first magnetic element 112 and the second magnetic element 212 are coated with an insulating layer.

In some embodiments, the first electrode 111, the first magnetic member 112, the second electrode 211, and the second magnetic member 212 are connected to separate energizing circuits for individual control.

In some embodiments, the first electrodes 111 are multiple, and the energizing circuits of two first electrodes 111 are independently arranged to form a mapping electrode pair, so as to detect the electrical signal transmission condition of the ablated tissue 340 to be ablated by using the energizing circuits; and/or the number of the second electrodes 211 is multiple, and the energizing circuits of the two second electrodes 211 are independently arranged to form a mapping electrode pair, so that the energizing circuits are used for detecting the electrical signal transmission condition of the ablated tissue 340 to be ablated; and/or the energizing circuits of the first electrode 111 and the second electrode 211 are independently arranged to form a mapping electrode pair, so that the energizing circuits are used for detecting the electric signal transmission condition of the tissue to be ablated 340 after ablation.

In some embodiments, the first electrode tip 110 and the second electrode tip 210 are each plural in number.

Referring to fig. 12 to 15, the ablation principle of the ablation device to the tissue to be ablated 340 in the present embodiment can be seen, and the ablation range 330 of the ablation device can be embodied.

In this embodiment, as shown in fig. 7 and 8, the second electrode tip 210 includes a second protective sheath 214, and the second electrode 211 is disposed on the second protective sheath 214; wherein the second electrode tip 210 includes a developing member 213, and the developing member 213 is disposed on the second protective sheath 214 to mark the position of the second electrode tip 210 by the developing member 213; and/or, the second electrode 211 is made of a metal developing material including at least one of the following materials: platinum, platinum-iron alloy, tantalum, gold plated beryllium bronze; and/or the second protective sheath 214 is made of a developing material including barium sulfate (BaSO 4).

The visualization member 213, the second electrode 211 having visualization function, and the second protective sheath 214 having visualization function in this embodiment can indicate the position when the second electrode assembly 200 enters the ablated tissue. Alternatively, the number of the developing members 213 on the second electrode tip 210 is 1 to 6, and may be separately provided or the second electrode 211 may have a developing function. The sheath outer walls of the visualization element 213 and the second protective sheath 214 in this embodiment are flush to prevent injury to the patient during surgery.

In this embodiment, the second electrodes 211 are spaced along the extending direction of the second protective sheath 214, and are sleeved on the second protective sheath 214, and the electrode surface is higher than the surface of the second protective sheath 214. There may be no developing member, or there may be a plurality of developing members 213, and the plurality of developing members 213 are provided at intervals along the extending direction of the second protective sheath 214; and/or, the outer surface of the second protective sheath 214 is divided into a first surface portion and a second surface portion, wherein the first surface portion corresponds to the developing member 213, the second surface portion is connected with the first surface portion, the first surface portion is a concave structure, the developing member 213 is sleeved on the first surface portion, and the outer surface of the developing member 213 is flush with or lower than the second surface portion.

In operation, the first electrode assembly 100 is first fixed on the epicardium by the positioning member, then the second electrode assembly 200 enters the interior of the heart, the second electrode assembly 200 is placed in the endocardium at the position corresponding to the first electrode assembly 100 by the indication of the developing member 213, and then the first pair of magnetic members, the second pair of magnetic members and the third pair of magnetic members at the first electrode tip 110 and the second electrode tip 210 are synchronously and sequentially turned on, and at this time, the two groups of electrodes complete the initial positioning. After the initial positioning is completed, the two electrode assemblies are opened in pairs, and the final positioning is completed.

Optionally, the shielding side eaves 115 are strip-shaped, and the shielding side eaves 115 extend along the extending direction of the first protective sheath 113. Through setting up and sheltering from side eaves 115, can shelter from liquid such as interstitial fluid and normal saline outside the ablation line and get into and melt the position, the measurement accuracy of resistance value between first electrode and the second electrode when avoiding melting to influence and melt the effect.

Specifically, the first electrode 111 and/or the first magnetic member 112 are provided with a lead laying groove 120 for accommodating a lead, which is used for connecting with the first electrode 111; alternatively, a wire-laying groove 120 for laying a wire is provided on the inner wall of the first protective sheath 113.

Specifically, the second electrode tip 210 further includes a second protective sheath, and the plurality of second magnetic members 212 and the plurality of second electrodes 211 are all sleeved on the second protective sheath; alternatively, the plurality of second magnetic members 212 and the plurality of second electrodes 211 are arranged alternately along the extending direction of the second protective sheath, so that the plurality of second electrodes 211 are arranged at intervals, i.e., the respective two second electrodes 211 are separated by each second magnetic member 212.

Alternatively, referring to fig. 13 and 19, the plurality of second magnetic elements 212 and the plurality of second electrodes 211 are both ring-shaped structures, or are square, V-shaped, D-shaped, or arched cross-sectional structures. As shown in fig. 19, the cross section of the second electrode 211 is polygonal, and may be square.

The rf ablation device of the present invention further includes an rf host 310, as shown in fig. 9, the rf host 310 is connected to both the first electrode 111 and the second electrode 211 to detect the impedance between the first electrode 111 and the second electrode 211, and adjust the rf power between the first electrode 111 and the second electrode 211 according to the detected impedance information.

Specifically, each of the plurality of first electrodes 111 and the plurality of second electrodes 211 is connected to the rf host 310 to detect the impedance of the ablated tissue between the corresponding first electrode 111 and the corresponding second electrode 211, and adjust the rf power between the corresponding first electrode 111 and the corresponding second electrode 211 according to the detected corresponding impedance information.

Specifically, as shown in fig. 9, the rf host 310 is provided with a display screen 313, and the display screen 313 is used for displaying the measured impedance and/or the rf power between the two corresponding first electrodes 111 and second electrodes 211.

Specifically, the rf main unit 310 is further provided with an ablation interface 311, each of the first electrode assembly 100 and the second electrode assembly 200 includes a plurality of lead assemblies, each lead assembly includes a lead connector and a plurality of parallel leads connected to the lead connector, and each lead is used for connecting to a corresponding electrode; the ablation interface 311 has a first ablation interface portion having a plurality of first ablation interfaces for insertion of a plurality of wire connectors of the first electrode assembly 100 and a second ablation interface portion having a plurality of second ablation interfaces for insertion of a plurality of wire connectors of the second electrode assembly 200 to provide suitable radio frequency power to the respective first electrodes 111 and the respective second electrodes 211 through the respective first ablation interfaces and the respective second ablation interfaces.

Specifically, when the first magnetic member 112 and the second magnetic member 212 are both electromagnets, the rf host 310 is further provided with an electromagnetic interface 312, each of the first electrode assembly 100 and the second electrode assembly 200 includes a plurality of electromagnet assemblies, each of the electromagnet assemblies includes an electromagnetic joint and a plurality of electromagnetic wires connected to the electromagnetic joint and arranged in parallel, and each of the electromagnetic wires is used for being connected to a corresponding electromagnet; the electromagnetic interface 312 has a first electromagnetic interface portion having a plurality of first magnetic interfaces for inserting the plurality of electromagnetic connectors of the first electrode assembly 100, and a second electromagnetic interface portion having a plurality of second magnetic interfaces for inserting the plurality of electromagnetic connectors of the second electrode assembly 200, so as to supply power to the corresponding first magnetic member 112 and the corresponding second magnetic member 212 through the respective first magnetic interfaces and the respective second magnetic interfaces, thereby generating attraction force between the corresponding first magnetic member 112 and the corresponding second magnetic member 212.

From the above description, it can be seen that the above-described embodiments of the present invention achieve the following technical effects:

in the rf ablation device of the present invention, the rf ablation device includes a first electrode assembly 100 and a second electrode assembly 200, the first electrode assembly 100 includes a first electrode tip 110 having a first electrode 111, the second electrode assembly 200 includes a second electrode tip 210 having a second electrode 211, the first electrode tip 110 includes a first magnetic member 112, the second electrode tip 210 includes a second magnetic member 212, and the first magnetic member 112 and the second magnetic member 212 are attracted to each other, so that the first electrode tip 110 and the second electrode tip 210 are relatively fixed, and the tissue 340 to be ablated between the first electrode 111 and the second electrode 211 is ablated by the first electrode 111 and the second electrode 211. In particular use, the first electrode assembly 100 and the second electrode assembly 200 are respectively used as an epicardial electrode and an endocardial electrode, so that the first electrode assembly 100 and the second electrode assembly 200 respectively act on the epicardium and the endocardium to achieve simultaneous ablation of the epicardium and the endocardium, thereby achieving good ablation effect; therefore, the radio frequency ablation device can solve the problem that the ablation effect of the radio frequency ablation device in the prior art is not ideal.

In addition, the radio frequency ablation equipment in the application can realize internal and surgical hybrid ablation, the technical wound is small, the problems of large surgical ablation wound and slow recovery in the prior art are solved, meanwhile, synchronous ablation can be performed from the epicardium and the endocardium, the output power is adjusted by testing the actual impedance between tissues, the operation is accurate and safe, and the machine alarm ablation is finished after the impedance reaches a certain resistance value, so that excessive ablation is avoided. In addition, the first electrode assembly can be independently used for acting on the epicardium to realize the ablation effect, and the second electrode assembly can be independently used for acting on the endocardium to realize the ablation effect.

No matter endocardial ablation or epicardial ablation or simultaneous ablation of the endocardial and the epicardial, a single electrode assembly or an electrode assembly working in cooperation can be mapped timely, the ablation effect is monitored, the problem that external instruments are still needed for mapping after current ablation and the problem that point mapping is needed is solved, and the surgical ablation effect is improved.

Spatially relative terms, such as "above … …," "above … …," "above … …," "above," and the like, may be used herein for ease of description to describe one device or feature's spatial relationship to another device or feature as illustrated in the figures. It will be understood that the spatially relative terms are intended to encompass different orientations of the device in use or operation in addition to the orientation depicted in the figures. For example, if a device in the figures is turned over, devices described as "above" or "on" other devices or configurations would then be oriented "below" or "under" the other devices or configurations. Thus, the exemplary term "above … …" can include both an orientation of "above … …" and "below … …". The device may be otherwise variously oriented (rotated 90 degrees or at other orientations) and the spatially relative descriptors used herein interpreted accordingly.

It is noted that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of example embodiments according to the present application. As used herein, the singular forms "a", "an" and "the" are intended to include the plural forms as well, and it should be understood that when the terms "comprises" and/or "comprising" are used in this specification, they specify the presence of stated features, steps, operations, devices, components, and/or combinations thereof, unless the context clearly indicates otherwise.

It should be noted that the terms "first," "second," and the like in the description and claims of this application and in the drawings described above are used for distinguishing between similar elements and not necessarily for describing a particular sequential or chronological order. It is to be understood that the data so used is interchangeable under appropriate circumstances such that the embodiments of the application described herein are, for example, capable of operation in sequences other than those illustrated or otherwise described herein. Furthermore, the terms "comprises," "comprising," and "having," and any variations thereof, are intended to cover a non-exclusive inclusion, such that a process, method, system, article, or apparatus that comprises a list of steps or elements is not necessarily limited to those steps or elements expressly listed, but may include other steps or elements not expressly listed or inherent to such process, method, article, or apparatus.

The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention, and various modifications and changes may be made by those skilled in the art. Any modification, equivalent replacement, or improvement made within the spirit and principle of the present invention should be included in the protection scope of the present invention.

Claims (25)

1. A radio frequency ablation device, comprising:

a first electrode assembly (100), the first electrode assembly (100) comprising a first electrode tip (110), the first electrode tip (110) having a first electrode (111);

a second electrode assembly (200), the second electrode assembly (200) comprising a second electrode tip (210), the second electrode tip (210) having a second electrode (211);

the first electrode tip (110) comprises a first magnetic part (112), the second electrode tip (210) comprises a second magnetic part (212), and the first magnetic part (112) and the second magnetic part (212) attract each other, so that the first electrode tip (110) and the second electrode tip (210) are relatively fixed, and the tissue (340) to be ablated between the first electrode (111) and the second electrode (211) is ablated through the first electrode (111) and the second electrode (211).

2. The radio frequency ablation device of claim 1, further comprising:

an ablation circuit (320), the first electrode (111) and the second electrode (211) each disposed on the ablation circuit (320) to adjust radio frequency energy between the first electrode (111) and the second electrode (211) for ablation by testing impedance between the first electrode (111) and the second electrode (211).

3. The radio frequency ablation device of claim 1, further comprising:

a radio frequency host (310), wherein the radio frequency host (310) is connected with the first electrode (111) and the second electrode (211) to detect impedance between the first electrode (111) and the second electrode (211) and adjust radio frequency power between the first electrode (111) and the second electrode (211) according to the detected impedance information.

4. The radiofrequency ablation device of claim 1, wherein the first electrode (111) and the second electrode (211) are each provided in plurality, and the first electrodes (111) and the second electrodes (211) are arranged in cooperation with each other.

5. The radiofrequency ablation device of claim 4, wherein the first electrode tip (110) and the second electrode tip (210) are each strip-shaped, and wherein the plurality of first electrodes (111) are arranged at intervals along an extension direction of the first electrode tip (110), and the plurality of second electrodes (211) are arranged at intervals along an extension direction of the second electrode tip (210).

6. The radiofrequency ablation device of claim 1, wherein the first electrode tip (110) includes a positioning member (117), the first electrode tip (110) being positioned epicardially via the positioning member (117).

7. The radiofrequency ablation device of claim 6, wherein the first electrode tip (110) is strip-shaped, the plurality of positioning members (117) are provided, and the plurality of positioning members (117) are arranged along an extending direction of the first electrode tip (110).

8. The radiofrequency ablation device of claim 6, wherein the first electrode tip (110) comprises a first protective sheath (113), at least a portion of the first electrode (111) being disposed within the first protective sheath (113); the number of the positioning pieces (117) is multiple, the positioning pieces (117) are arranged in pairs, and two positioning pieces (117) in pairs are arranged on two opposite sides of the first protective sheath (113); and/or a plurality of positioning members (117) are arranged on one side of the first protective sheath (113).

9. A radiofrequency ablation device according to claim 8, wherein the first protective sheath (113) is made of a flexible material.

10. The radiofrequency ablation device of claim 8, wherein the first electrode (111) has an electrode face (1110) disposed toward the tissue to be ablated (340), the first protective sheath (113) having a protective sheath face (1130) disposed toward the tissue to be ablated (340); wherein the electrode surface (1110) is positioned on one side of the protective sheath surface (1130) close to the tissue (340) to be ablated.

11. The radiofrequency ablation device of claim 10, wherein the first electrode (111) is a plurality of first electrodes (111), and the first electrodes (111) are arranged at intervals along an extending direction of the first electrode tip (110); the minimum distances between the electrode surfaces (1110) of the plurality of first electrodes (111) and the protective sheath surface (1130) are all the same.

12. A radiofrequency ablation device according to claim 8, wherein the first protective sheath (113) is made of a flexible material such that the first protective sheath (113) is bendably arranged.

13. A radio frequency ablation device according to claim 6, wherein the positioning member (117) is a suction cup structure.

14. The radiofrequency ablation device of claim 1, wherein the first electrode tip (110) comprises a first protective sheath (113), at least a portion of the first electrode (111) being disposed within the first protective sheath (113);

the number of the first electrodes (111) is multiple, and the multiple first electrodes (111) are arranged at intervals along the extending direction of the first electrode tip (110); at least one first electrode (111) in the plurality of first electrodes (111) is provided with a cooling hole (114) for circulating cooling fluid; and/or

A cooling pipeline for circulating cooling fluid is arranged in the first protective sheath (113).

15. The radiofrequency ablation device of claim 14, wherein from 1 to 4 of the cooling holes (114) are provided on at least one of the first electrodes (111) of the plurality of first electrodes (111).

16. The rf ablation device according to claim 1, wherein the first magnetic member (112) and the second magnetic member (212) are each a plurality of members, the first electrode tip (110) and the second electrode tip (210) are each a strip-shaped member, the plurality of first magnetic members (112) are arranged at intervals along an extending direction of the first electrode tip (110), and the plurality of second magnetic members (212) are arranged at intervals along an extending direction of the second electrode tip (210).

17. The rf ablation device according to claim 16, wherein the first electrode (111) and the second electrode (211) are each provided in plurality, the first magnetic members (112) are alternately disposed with respect to the first electrodes (111), and the second magnetic members (212) are alternately disposed with respect to the second electrodes (211).

18. A radio frequency ablation device according to claim 17, wherein adjacent first electrodes (111) are insulated from the first magnetic member (112), and adjacent second electrodes (211) are insulated from the second magnetic member (212).

19. The radiofrequency ablation device according to claim 17, wherein the facing surfaces between the first electrodes (111) and the first magnetic members (112) which are adjacent to each other are coated with an insulating varnish, or an insulating partition is arranged between the first electrodes (111) and the first magnetic members (112) which are adjacent to each other; insulating paint is sprayed on the opposite surfaces between the adjacent second electrodes (211) and the second magnetic pieces (212), or insulating partition plates are arranged between the adjacent second electrodes (211) and the second magnetic pieces (212).

20. The radiofrequency ablation device of claim 1, wherein the outer surfaces of the first and second magnetic members (112, 212) are coated with an insulating layer.

21. A radiofrequency ablation device according to claim 1, wherein the first electrode (111), the first magnetic element (112), the second electrode (211) and the second magnetic element (212) are each connected to separate energizing circuits for individual control.

22. The radiofrequency ablation device of claim 1, wherein the first electrodes (111) are multiple, and the energizing circuits of the two first electrodes (111) are independently arranged to form a mapping electrode pair, so as to detect the electrical signal transmission condition of the ablated tissue (340) to be ablated by using the energizing circuits; and/or the second electrodes (211) are multiple, and the energizing circuits of the two second electrodes (211) are independently arranged to form a mapping electrode pair, so that the energizing circuits are utilized to detect the electrical signal transmission condition of the ablated tissue (340); and/or the energizing circuits of the first electrode (111) and the second electrode (211) are independently arranged to form a mapping electrode pair, so as to detect the electric signal transmission condition of the ablated tissue (340) to be ablated by using the energizing circuits.

23. The radiofrequency ablation device of claim 1, wherein the first electrode tip (110) and the second electrode tip (210) are each plural.

24. The radiofrequency ablation device of claim 1, wherein the second electrode tip (210) comprises a second protective sheath (214), the second electrode (211) being disposed on the second protective sheath (214);

the second electrode (211) is made of a metal material; and/or the presence of a gas in the gas,

the second protective sheath (214) is made of a developer material.

25. The radiofrequency ablation device of claim 24, wherein the second electrode (211) is spaced along the extension of the second protective sheath (214), is fitted over the second protective sheath (214), and has an electrode surface higher than the surface of the second protective sheath (214).

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