Ablation electrode and ablation catheter

Abstract

The application provides an ablation electrode and an ablation catheter, the ablation electrode is used for generating radio frequency current to perform radio frequency ablation treatment on a lesion site, and the ablation electrode has a cavity, an injection port and a plurality of cooling holes which are communicated with the cavity; cooling liquid is injected into the cavity through the injection port and sprayed out of the cooling holes to cool the ablation electrode; the outer surface of the ablation electrode is provided with the cooling holes and grooves, and the grooves are also provided with the cooling holes. According to the ablation electrode, the effective heat dissipation area of the ablation electrode is increased without increasing the volume of the ablation electrode by arranging the grooves on the outer surface of the ablation electrode, and the heat dissipation and cooling effect of the ablation electrode is improved. Moreover, the outer surface of the ablation electrode is provided with a plurality of cooling holes in the grooves, the cooling liquid can be sprayed out of the cooling holes to cool the ablation electrode, and the cooling and heat dissipation effect of the ablation electrode is further improved, and the reliability and safety of the operation are improved.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to an ablation electrode and an ablation catheter. Background Technology

[0002] Catheter radiofrequency ablation is currently the most commonly used minimally invasive interventional technique for treating arrhythmias. Its basic principle is as follows: a radiofrequency ablation catheter is inserted into the target cardiac chamber through a sheath of varying lengths. Guided by three-dimensional mapping technology, the origin of the arrhythmia is precisely located. The cylindrical ablation electrode at the catheter tip is then brought into contact with the lesion tissue using effective contact force. Radiofrequency current is then delivered through a loop electrode attached to the patient's skin. The radiofrequency current flows through the electrode and across the lesion tissue beneath it, generating heat within the tissue. When the temperature reaches the level of coagulative necrosis, the tissue permanently loses its electrophysiological activity, and the arrhythmia is cured.

[0003] When the ablation electrode transmits current and causes tissue heating, the electrode material's thermal conductivity and endothermic properties will passively heat the tissue as a result. If the electrode overheats and the surrounding blood circulation fails to cool it adequately, scab formation, carbon buildup, or even blow-off may occur beneath the electrode. This increases the impedance between the electrode and the tissue, affecting the ablation depth and effectiveness; it can also cause complications such as embolism and perforation.

[0004] To prevent overheating of the ablation electrode, most related technologies employ a unidirectional circulating brine jet cooling method. Simultaneously, the cooling effect and the brine injection rate per unit time are adjusted by controlling the number of injection holes on the electrode surface. However, these related technical solutions suffer from problems such as large brine input and poor cooling effect. Summary of the Invention

[0005] The technical problem to be solved by the present invention is how to improve the cooling effect of the ablation electrode of the ablation catheter. The present invention proposes an ablation electrode and an ablation catheter.

[0006] According to an embodiment of the present invention, the ablation electrode is used to generate radiofrequency current to perform radiofrequency ablation treatment on the lesion site. The ablation electrode has a chamber, an injection port communicating with the chamber, and a plurality of cooling holes. Coolant is injected into the chamber through the injection port and sprayed out from the cooling holes to cool the ablation electrode.

[0007] The outer surface of the ablation electrode is provided with cooling holes and grooves, wherein the grooves are also provided with cooling holes.

[0008] According to embodiments of the present invention, the ablation electrode, by providing grooves on its outer surface, increases its outer surface area without increasing its volume, thereby increasing the effective heat dissipation area and improving its cooling effect. Furthermore, the outer surface of the ablation electrode includes multiple cooling holes within the grooves, allowing coolant to be sprayed through these holes to further cool the electrode, thereby enhancing its cooling performance and improving the reliability and safety of the procedure.

[0009] According to some embodiments of the present invention, the ablation electrode is columnar, and the groove is disposed on the side surface of the ablation electrode, wherein the groove is an annular groove disposed along the circumferential direction of the ablation electrode.

[0010] In some embodiments of the present invention, a plurality of annular grooves are provided at intervals along the axial direction of the ablation electrode.

[0011] According to some embodiments of the present invention, the cooling hole includes:

[0012] A spray cooling hole is located within the groove, through which the coolant in the chamber is sprayed out in a mist form;

[0013] The jet cooling hole is located on the side surface of the ablation electrode, excluding the groove, and the coolant in the chamber is ejected in a radial pattern through the jet cooling hole.

[0014] In some embodiments of the present invention, both the spray cooling hole and the jet cooling hole are multiple holes evenly spaced along the circumferential direction of the ablation electrode, and the diameter of the spray cooling hole is smaller than the diameter of the jet cooling hole.

[0015] According to some embodiments of the present invention, the top and side walls of the ablation electrode are provided with multiple temperature sensors for detecting the temperature of the ablation electrode.

[0016] An ablation catheter according to an embodiment of the present invention includes:

[0017] Ablation electrode, wherein the ablation electrode is the ablation electrode described above;

[0018] The tube body, wherein the ablation electrode is connected to the end of the tube body.

[0019] According to an embodiment of the ablation catheter of the present invention, a groove is provided on the outer surface of the ablation electrode at the tip of the catheter body. This increases the outer surface area of ​​the ablation electrode without increasing its volume, thereby increasing the effective heat dissipation area and improving its cooling effect. Furthermore, the outer surface of the ablation electrode includes multiple cooling holes within the groove, through which coolant can be sprayed to cool the ablation electrode, further improving its cooling effect and thus enhancing the reliability and safety of the procedure.

[0020] According to some embodiments of the present invention, the ablation catheter further includes:

[0021] A piezoelectric component is disposed inside the tube. When the ablation electrode comes into contact with the lesion, part of the piezoelectric component is deformed by pressure and generates a piezoelectric current for obtaining the contact force at the tip of the ablation electrode.

[0022] In some embodiments of the present invention, the piezoelectric component includes:

[0023] A piezoelectric spring, wherein the piezoelectric spring is disposed adjacent to the ablation electrode;

[0024] A piezoelectric spring is located at the end of the piezoelectric spring furthest from the ablation electrode and abuts against the piezoelectric spring. When the ablation electrode abuts against the lesion, both the piezoelectric spring and the piezoelectric spring are compressed and deformed, generating the piezoelectric current.

[0025] An insulating heat insulation sheet is located between the ablation electrode and the piezoelectric spring;

[0026] A base is located at the end of the piezoelectric spring away from the piezoelectric spring and is used to fix the piezoelectric spring.

[0027] According to some embodiments of the present invention, the ablation catheter further includes a flow tube communicating with the injection port for injecting coolant into the chamber. Attached Figure Description

[0028] Figure 1 This is a schematic diagram of the structure of the ablation electrode according to an embodiment of the present invention;

[0029] Figure 2 This is a partial cross-sectional view of the ablation electrode according to an embodiment of the present invention;

[0030] Figure 3 A top view of the ablation electrode according to an embodiment of the present invention;

[0031] Figure 4 This is a schematic diagram of the ablation catheter according to an embodiment of the present invention;

[0032] Figure 5 This is an axial cross-sectional view of a partial structure of an ablation catheter according to an embodiment of the present invention;

[0033] Figure 6 This is a cross-sectional view of the ablation catheter according to an embodiment of the present invention;

[0034] Figure 7 This is an exploded view of a partial structure of the ablation catheter according to an embodiment of the present invention;

[0035] Figure 8 This is a schematic diagram of the ablation catheter according to an embodiment of the present invention;

[0036] Figure 9 This is a schematic diagram illustrating the principle of calculating contact force using the quadrilateral law according to an embodiment of the present invention;

[0037] Figure 10 This is a schematic diagram of the forces acting on a piezoelectric spring according to an embodiment of the present invention;

[0038] Figure 11 This is a schematic diagram of the force acting on a piezoelectric spring according to an embodiment of the present invention;

[0039] Figure 12 This is a schematic diagram illustrating the process of calculating contact force using the quadrilateral law according to an embodiment of the present invention.

[0040] Figure 13 This is a schematic diagram illustrating the calculation principle of the contact force at the tip of the ablation catheter according to an embodiment of the present invention.

[0041] Figure label:

[0042] 100 ablation catheters

[0043] Ablation electrode 10, chamber V1, injection port 110, cooling hole 120, spray cooling hole 121, jet cooling hole 122, groove 130, temperature sensor 140.

[0044] Tube body 20, marking surface S1, piezoelectric spring 30, insulating and heat-insulating sheet 40, base 50, piezoelectric spring 60, flow tube 70, handle 80, tail wire 90.

[0045] First annular electrode 101, second annular electrode 102, third annular electrode 103, positioning chip 104, traction wire 105, three-dimensional visual electrode 106, and wire 107. Detailed Implementation

[0046] To further illustrate the technical means and effects of the present invention in achieving its intended purpose, the present invention will be described in detail below with reference to the accompanying drawings and preferred embodiments.

[0047] In related technologies, the use of saline irrigation to cool the radiofrequency ablation catheter has the following disadvantages:

[0048] Limited by the lateral area of ​​the cylindrical ablation electrode at the catheter tip, the cooling efficiency remains low despite increasing the number of saline infusion holes. Given a fixed lateral area of ​​the cylindrical ablation electrode, the saline infusion flow rate must be increased to achieve better cooling. Currently, the infusion flow rate for a 12-hole radiofrequency ablation catheter is 17 ml / min, and for a 56-hole catheter, it is 8 ml / min. This means that a 3-hour procedure requires the infusion of 1000-3000 ml of saline, significantly increasing the patient's cardiac burden and posing a risk of inducing heart failure.

[0049] In view of the above-mentioned defects of ablation catheters in related technologies, the present invention proposes an ablation electrode and an ablation catheter.

[0050] According to an embodiment of the present invention, the ablation electrode 10 is used to generate radiofrequency current for radiofrequency ablation treatment of the lesion site. Figure 1 and Figure 2 As shown, the ablation electrode 10 has a chamber V1, an injection port 110 communicating with the chamber V1, and a plurality of cooling holes 120. Coolant is injected into the chamber V1 through the injection port 110 and sprayed out from the cooling holes 120 to cool the ablation electrode 10. The outer surface of the ablation electrode 10 is provided with cooling holes 120 and grooves 130, wherein cooling holes 120 are also provided in the grooves 130.

[0051] According to an embodiment of the present invention, the ablation electrode 10, by providing a groove 130 on its outer surface, can increase its outer surface area without increasing its volume, thereby increasing its effective heat dissipation area and improving its cooling effect. Furthermore, the outer surface of the ablation electrode 10 includes a plurality of cooling holes 120 within the groove 130, through which coolant can be sprayed to cool the ablation electrode 10, further improving its cooling effect and thus enhancing the reliability and safety of the procedure.

[0052] According to some embodiments of the present invention, such as Figure 1 and Figure 2 As shown, the ablation electrode 10 is cylindrical, and a groove 130 is provided on the side surface of the ablation electrode 10. The groove 130 is an annular groove 130 arranged along the circumferential direction of the ablation electrode 10. It should be noted that by providing a circumferential annular groove 130 on the outer surface of the ablation electrode 10, the processing and manufacturing of the groove 130 is facilitated, reducing the production cost of the ablation electrode 10. Moreover, the area of ​​the groove 130 can be increased, improving the cooling and heat dissipation effect of the ablation electrode 10.

[0053] In some embodiments of the present invention, a plurality of annular grooves 130 are provided at intervals along the axial direction of the ablation electrode 10. It is understood that by providing a plurality of annular grooves 130, the effective heat dissipation area of ​​the ablation electrode 10 can be further increased, thereby further improving the cooling and heat dissipation effect of the ablation electrode 10.

[0054] According to some embodiments of the present invention, such as Figure 1 As shown, the cooling hole 120 includes a spray cooling hole 121 and a jet cooling hole 122.

[0055] The spray cooling hole 121 is located inside the groove 130, and the coolant in the chamber V1 is sprayed out in a mist form through the spray cooling hole 121. The jet cooling hole 122 is located on the side surface of the ablation electrode 10 excluding the groove 130, and the coolant in the chamber V1 is sprayed out in a ray form through the jet cooling hole 122.

[0056] It should be noted that when cooling the ablation electrode 10, the coolant in the chamber V1 can be sprayed out in a mist form from the spray cooling hole 121 to increase the spray range of the coolant and improve the cooling effect; the coolant in the chamber V1 can also be sprayed out in a ray form through the jet cooling hole 122 to drive the surrounding blood flow and accelerate the cooling and heat dissipation efficiency of the ablation electrode 10.

[0057] In some embodiments of the present invention, such as Figure 1 and Figure 2 As shown, both the spray cooling holes 121 and the jet cooling holes 122 can be multiple holes evenly spaced along the circumferential direction of the ablation electrode 10. This improves the uniformity of coolant spraying, thereby enhancing the uniformity of heat dissipation from the ablation electrode 10. The aperture of the spray cooling holes 121 is smaller than that of the jet cooling holes 122. For example, the aperture of the spray cooling holes 121 can be less than 50 μm, and the aperture of the jet cooling holes 122 can be less than 100 μm.

[0058] According to some embodiments of the present invention, such as Figure 3 As shown, the top and side walls of the ablation electrode 10 are equipped with multiple temperature sensors 140 for detecting the temperature of the ablation electrode 10. This allows for real-time acquisition of the temperature of various parts of the ablation electrode 10, enabling the ablation electrode 10 to be cooled by spraying coolant when the temperature reaches a preset value.

[0059] like Figures 4-7 As shown, the ablation catheter 100 according to an embodiment of the present invention includes: an ablation electrode 10 and a tube body 20.

[0060] The ablation electrode 10 is the ablation electrode 10 described above, and the ablation electrode 10 is connected to the end of the tube body 20.

[0061] According to an embodiment of the ablation catheter 100 of the present invention, a groove 130 is provided on the outer surface of the ablation electrode 10 at the tip of the catheter body 20. This groove 130 increases the outer surface area of ​​the ablation electrode 10 without increasing its volume, thereby increasing the effective heat dissipation area and improving its cooling effect. Furthermore, the outer surface of the ablation electrode 10 includes multiple cooling holes 120 within the groove 130. Cooling liquid can be sprayed through the cooling holes 120 to cool the ablation electrode 10, further improving its cooling effect and thus enhancing the reliability and safety of the procedure.

[0062] According to some embodiments of the present invention, the ablation catheter 100 further includes a piezoelectric component disposed within the tube body 20. When the ablation electrode 10 comes into contact with the lesion, a portion of the piezoelectric component is deformed by pressure and generates a piezoelectric current for obtaining the contact force at the tip of the ablation electrode 10.

[0063] It should be noted that in related technologies, the display of the magnitude and direction of the contact force at the tip of the ablation catheter is inaccurate and unintuitive. The arrow indicating the contact force at the catheter tip can only indicate the direction of the contact force, but does not display its magnitude, changes in contact force, or warning values, which affects the progress of the surgery. In the ablation catheter 100 proposed in this invention, when the ablation electrode 10 contacts the lesion during ablation surgery, the piezoelectric component deforms under pressure, generating a piezoelectric current. The contact force between the ablation electrode 10 and the lesion can be calculated based on the magnitude of the piezoelectric current, thereby facilitating the surgeon's control over the contact state of the ablation catheter 100.

[0064] In some embodiments of the present invention, such as Figure 5 and Figure 7 As shown, the piezoelectric assembly includes: a piezoelectric spring 30, a piezoelectric spring sheet 60, an insulating and heat-insulating sheet 40, and a base 50.

[0065] The piezoelectric spring 30 is positioned adjacent to the ablation electrode 10, and the piezoelectric spring 60 is located at the end of the piezoelectric spring 30 away from the ablation electrode 10 and abuts against the piezoelectric spring 30. When the ablation electrode 10 abuts against the lesion, both the piezoelectric spring 30 and the piezoelectric spring 60 are compressed and deformed, generating a piezoelectric current.

[0066] An insulating heat shield 40 is located between the ablation electrode 10 and the piezoelectric spring 30. By providing the insulating heat shield 40, the temperature conduction of the ablation electrode 10 can be isolated and blocked, the radio frequency current of the ablation electrode 10 can be insulated, and the piezoelectric spring 30 can be fixed. The base 50 is located at the end of the piezoelectric spring 60 away from the piezoelectric spring 30 and is used to fix the piezoelectric spring 60.

[0067] It should be noted that many factors affect the ablation effect and efficiency of the ablation catheter 100, mainly including: energy, time parameters, surface area of ​​the ablation electrode 10, and the contact force between the ablation electrode 10 and the tissue. Energy and time parameters can be adjusted by controlling the radiofrequency ablation device, and the surface area of ​​the ablation electrode 10 can be adjusted by controlling the outer diameter of the ablation catheter 100 and the length of the ablation electrode 10. However, adjusting the contact force between the ablation electrode 10 and the tissue is more difficult. Current solutions involve placing a pressure sensor at the tip of the ablation catheter to sense the magnitude and direction of the contact force. These sensors have the advantage of being relatively accurate in measuring the magnitude and direction of the axial contact force, but their accuracy in measuring the magnitude and direction of the lateral contact force is poor.

[0068] In this invention, when calculating the contact force of the ablation electrode 10 using the piezoelectric component, the following method can be adopted: Figure 9 The quadrilateral rule is shown. Combined with... Figures 10-13 As shown, the calculation principle and method are as follows:

[0069] The calculation principle for the magnitude and direction of the contact force of the ablation catheter 100 is based on the pressure-bearing calculation of the piezoelectric spring 60:

[0070] like Figure 10 As shown, the forces acting on the four piezoelectric springs 60, A, B, C, and D, are f1, f2, f3, and f4, respectively. Figure 12 As shown, the resultant force f1+f2+f3+f4 is obtained by calculating the magnitude and direction of the resultant force pairwise in sequence. This resultant force is then combined with... Figure 11 The axial forces f5 of the piezoelectric springs 30 shown are added together to obtain the total resultant force f1+f2+f3+f4+f5 of the ablation catheter 100. The magnitude and direction of the total resultant force f1+f2+f3+f4+f5 can be displayed in real time on the monitor connected to the ablation catheter 100.

[0071] The principle of contact force angle calculation and display is as follows: Figure 13 As shown:

[0072] The axial angle α is calculated using the plane of the ablation electrode 10 tip as a reference plane. The plane of the ablation catheter 100 tip is 0 degrees, and the extension of the axial direction of the ablation catheter 100 is 90 degrees. The axial angle range is 0-90 degrees. The circumferential angle b is calculated using the marking surface S0 of the ablation catheter 100 tip as a reference plane. The reference plane of the ablation catheter 100 tip is 0 degrees. The catheter is rotated clockwise until it returns to the reference plane after 360 degrees.

[0073] According to some embodiments of the present invention, such as Figure 4 and Figure 5As shown, the ablation catheter 100 also includes a flow tube 70, which is connected to the injection port 110 for injecting coolant into the chamber V1. It should be noted that one end of the flow tube 70 is connected to the injection port 110 of the chamber V1, and the other end extends outside the body and is connected to the coolant supply device. The coolant supply device can inject coolant into the chamber V1 through the flow tube 70.

[0074] The ablation catheter 100 according to the present invention will now be described in detail with reference to the accompanying drawings and a specific embodiment. It is to be understood that the following description is merely exemplary and not intended to limit the invention.

[0075] like Figures 4-7 As shown, the ablation catheter 100 includes: a tube body 20, an ablation electrode 10, a piezoelectric component, a flow tube 70, a positioning chip 104, a first annular electrode 101, a second annular electrode 102, a third annular electrode 103, a traction wire 105, a handle 80, a three-dimensional visual electrode 106, a lead wire 107, and a tail wire 90.

[0076] The ablation electrode 10 is a cylindrical electrode located at the tip of the tube 20, used to deliver radiofrequency current for ablation. The ablation electrode 10 can be self-cooled by spraying cooling saline. The diameter of the ablation electrode 10 can be 6F (2.00 mm), 8F (2.67 mm), 10F (3.34 mm), or 12F (4.00 mm), allowing surgeons to choose according to their specific needs.

[0077] The ablation electrode 10 has a chamber V1, an injection port 110 connecting the chamber V1, and multiple cooling holes 120. A temperature sensor 140 is provided on the top of the chamber V1 to sense the temperature change at the tip of the ablation electrode 10 during the ablation process.

[0078] The ablation electrode 10 has a plurality of annular grooves 130 spaced apart along its axial direction on its side. The depth of the grooves 130 is less than 0.5 mm and the width is less than 1 mm, which are used to increase the heat dissipation capacity of the surface of the ablation electrode 10.

[0079] Multiple spray cooling holes 121 with a diameter of less than 50 μm are evenly distributed in the groove 130. They are used to spray cooling saline solution onto the surface of the ablation electrode 10 in a cloud-like manner, and form a circulating cooling with the blood around the ablation electrode 10 to enhance the unidirectional circulating cooling effect.

[0080] The cooling saline inlet 110 is located at the tail of the ablation electrode 10 and is connected to the chamber V1 of the ablation electrode 10. It is used to deliver cooling saline into the ablation electrode 10. In conjunction with the number (more than 120) and distribution of the cooling holes 120, cooling saline is injected into the chamber V1 at a saline flow rate of less than 5 ml / min to ensure the cooling effect on the ablation electrode 10.

[0081] The ablation electrode 10 has jet cooling holes 122, with a diameter of less than 100 μm, on its side excluding the groove 130. These holes are regularly distributed on the surface of the ablation electrode 10 and are used to spray cooling saline solution into the surrounding blood, forming a circulating cooling system with the blood around the ablation electrode 10.

[0082] like Figure 5 and Figure 7 As shown, the piezoelectric assembly includes: a piezoelectric spring 30, an insulating heat-insulating sheet 40, a piezoelectric spring sheet 60, and a base 50.

[0083] The piezoelectric spring 30 is located between the ablation electrode 10 and the piezoelectric spring 60, and an insulating heat-insulating sheet 40 is provided between the piezoelectric spring 30 and the ablation electrode 10. The insulating heat-insulating sheet 40 is annular in shape and has a cooling brine injection hole in the middle. The insulating heat-insulating sheet 40 is used to insulate the radio frequency current of the ablation electrode 10, block the heat conduction of the ablation electrode 10, and fix the piezoelectric spring 30. The surface of the piezoelectric spring 30 is insulated to sense the fine axial pressure changes of the ablation electrode 10.

[0084] like Figure 10 As shown, the piezoelectric spring 60 consists of an array of four polygonal springs arranged symmetrically along the axis of the tube 20. The piezoelectric spring 60 has a central injection hole, and there are injection slots between adjacent springs. The base 50 supports and fixes the piezoelectric spring 60 array. The surface of the piezoelectric spring 60 is insulated to sense axial and lateral pressure transmitted by the piezoelectric spring 30.

[0085] like Figure 9-12 As shown, the resultant force of the pressure borne by each pair of reeds can be calculated using the parallelogram law. The final resultant force is used together with the axial pressure of the piezoelectric spring 30 to calculate the contact vector, guiding the tissue contact of the ablation electrode 10 and the ablation procedure.

[0086] The positioning chip 104 is positioned close to the base 50 and is used for three-dimensional spatial positioning of the catheter tip.

[0087] The first annular electrode 101 is located on the surface of the tube 20 near the piezoelectric spring 30. The width of the first annular electrode 101 is within 2 mm and the thickness is within 0.3 mm. The first annular electrode 101 cooperates with the ablation electrode 10 to record the bipolar potential at the distal end of the ablation catheter 100.

[0088] The second annular electrode 102 and the third annular electrode 103 are located at the tip of the tube 20, forming a proximal electrode pair. The width of both the second annular electrode 102 and the third annular electrode 103 is less than 2 mm, and their thickness is less than 0.3 mm. The distance between the second annular electrode 102 and the third annular electrode 103 is less than 5 mm, used to record the bipolar potential at the proximal end of the ablation catheter 100.

[0089] The tube body 20 includes a flexible section located between the ablation electrode 10 and the first annular electrode 101, used to control the lateral deformation of the tip of the ablation catheter 100.

[0090] The tube body 20 is equipped with a traction wire 105, which cooperates with the handle 80 and the slide to bend the catheter tip in one direction, with a maximum bending degree of 360 degrees. The ablation catheter 100 has a three-dimensional bending plane indicator at the catheter tip, and the handle 80 has a bending plane indicator at the tip.

[0091] like Figure 8 As shown, the ablation catheter 100 has a tail wire 90 for connecting to the host. The tube body 20 is provided with a three-dimensional visual electrode 106. Starting from 10cm from the tip of the ablation catheter 100, one or more three-dimensional visual electrodes 106 are set at intervals of more than 5cm to display the tip of the catheter body on the three-dimensional mapping map.

[0092] The bending plane indicator at the tip of the ablation catheter 100 is located at the tip of the handle 80 and is used to indicate the bending plane at the tip of the ablation catheter 100.

[0093] like Figure 13 As shown, the calculation and three-dimensional display of the contact vector at the tip of the ablation catheter 100 are as follows: The contact angle between the tip of the ablation catheter 100 and the tissue is calculated in conjunction with the host: (1) Axial angle a: The angle range is 0-90 degrees, with the plane of the tip of the ablation electrode 10 as 0 degrees and the extension line of the central axis of the tip of the ablation catheter 100 as 90 degrees. (2) Peripheral angle b: The angle range is 0-360 degrees, with the bending plane of the tip of the ablation catheter 100 as 0 degrees and proceeding clockwise until 360 degrees.

[0094] The working process and principle of the ablation catheter 100 of the present invention are as follows:

[0095] S1, connect the ablation catheter 100 tail wire 90, connect the saline irrigation tube connector, and fully vent air.

[0096] S2, the tip of the ablation catheter 100 is inserted into the predetermined cardiac chamber through a pre-placed long sheath.

[0097] S3, balance the zero point of contact pressure, and display the contact vector arrows of the ablation catheter 100 body and the tip of the ablation catheter 100 on the predetermined three-dimensional image of the heart chamber.

[0098] S4, confirm that the magnitude and direction of the contact vector at the tip of the ablation catheter 100 are within the preset safety range.

[0099] S5, bend the tip of the ablation catheter 100 through the handle 80, and simultaneously advance the ablation catheter 100 so that the tip ablation electrode 10 contacts the endocardial tissue.

[0100] S6, due to the reaction force of the tissue to the electrode, the piezoelectric spring 30 at the tip of the ablation catheter 100 deforms, generating a weak deformation current. The magnitude of the current is proportional to the contact force, and the host computer calculates the axial contact force. At the same time, the axial angle α of the contact force is calculated.

[0101] S7. Due to the reaction force of the tissue to the electrode, the piezoelectric spring 30 at the tip of the ablation catheter 100 deforms. This further causes asymmetrical deformation of the piezoelectric spring matrix 60, generating weak deformation currents of varying magnitudes. The magnitude of the current is proportional to the contact force, and the resultant lateral contact force is calculated by the host computer. At the same time, the circumferential angle b of the contact force is calculated.

[0102] S8, the host comprehensively calculates the magnitude and direction of the contact force and displays it in the form of a vector arrow at the tip of the ablation catheter 100 and in the form of a screen display window.

[0103] S9, the surgeon, based on the vector parameters of the tip of the ablation catheter 100, manipulates the catheter handle 80 to fully position and adjust the contact quality of the electrode at the tip of the ablation catheter 100.

[0104] The ablation electrode 10 and ablation catheter 100 proposed in this invention solve the following problems:

[0105] 1. While keeping the side area of ​​the cylindrical ablation electrode 10 at the catheter tip unchanged, increase the heat dissipation area and improve the heat dissipation efficiency.

[0106] 2. Spray holes of different diameters are made on the side of the columnar ablation electrode 10 to cool the part near the ablation electrode 10 with a cloud-like brine and to cool the area around the ablation electrode 10 with a jet of brine.

[0107] 3. Increase the number of side holes on the columnar ablation electrode to more than 120, and reduce the diameter of each hole by more than 50%, so as to reduce the amount of brine input by more than 50% without reducing the existing cooling efficiency.

[0108] 4. Design ablation catheters 100 with different diameters of ablation electrodes 10 and matching cooling holes 120 to increase the operator's selectivity for different patients, different sites, and different ablation efficiencies.

[0109] In summary, the ablation catheter 100 proposed in this invention has the following advantages:

[0110] An annular groove 130 is made on the side of the ablation electrode 10 to increase the heat dissipation area; cooling holes 120 of different diameters are made on the side of the ablation electrode 10 to provide mist-like saline cooling to the area adjacent to the ablation electrode 10 and jet-flushing saline cooling around the ablation electrode, thereby improving heat dissipation efficiency; the number of holes on the side of the ablation electrode 10 is increased to more than 120, and the diameter of a single hole is reduced by more than 50%, thereby reducing the saline input by more than 50% without reducing cooling efficiency; the diameters of the ablation catheter 100 and the ablation electrode 10 include multiple models: 6F (2.00mm), 8F (2.67mm), 10F (3.34mm), and 12F (4.00mm), increasing the operator's selectivity for different patients, different sites, and different ablation efficiencies.

[0111] Through the description of specific embodiments, a more in-depth and specific understanding should be gained of the technical means and effects adopted by the present invention to achieve the intended purpose. However, the accompanying drawings are only provided for reference and illustration and are not intended to limit the present invention.

Claims

1. An ablation electrode, characterized by, The ablation electrode is used to generate radio frequency current to perform radio frequency ablation treatment on a lesion site, and has a chamber, an injection port communicating with the chamber, and a plurality of cooling holes, through which cooling liquid is injected into the chamber and sprayed out of the cooling holes to cool the ablation electrode; The outer surface of the ablation electrode is provided with the cooling holes and grooves, wherein the grooves are also provided with the cooling holes; The cooling holes include: The spray cooling holes are located in the grooves, and the cooling liquid in the chamber is sprayed out of the spray cooling holes in the form of mist to form a circulating cooling with blood around the ablation electrode, thereby enhancing the one-way circulating cooling effect; The jet cooling holes are located on the side surface of the ablation electrode except the grooves, and the cooling liquid in the chamber is sprayed out of the jet cooling holes in the form of a jet. The top wall and the side wall of the ablation electrode are each provided with a plurality of temperature sensors for detecting the temperature of the ablation electrode, so that when the temperature reaches a preset value, the ablation electrode is cooled by spraying cooling liquid.

2. The ablation electrode of claim 1, wherein, The ablation electrode is columnar, and the grooves are arranged on the side surface of the ablation electrode and are annular grooves arranged along the circumferential direction of the ablation electrode.

3. The ablation electrode of claim 2, wherein, A plurality of annular grooves are arranged along the axial direction of the ablation electrode.

4. The ablation electrode of claim 1, wherein, The spray cooling holes and the jet cooling holes are both a plurality of holes uniformly spaced along the circumferential direction of the ablation electrode, and the aperture of the spray cooling holes is smaller than that of the jet cooling holes.

5. An ablation catheter characterized by, It comprises: The ablation electrode is the ablation electrode according to any one of claims 1-4; The ablation electrode is connected to the end of the tube body; The piezoelectric assembly includes a piezoelectric spring and a piezoelectric reed, and is arranged in the tube body. When the ablation electrode abuts against a lesion site, part of the piezoelectric assembly is deformed under pressure and generates a pressure variable current for obtaining the contact force of the head end of the ablation electrode. According to the size of the pressure variable current, the resultant force of the pressure borne by the piezoelectric reed, and the axial pressure of the piezoelectric spring, the size and direction of the contact force between the ablation electrode and the lesion site are calculated, and the form of the ablation catheter head end vector arrow and the form of the screen display window are displayed respectively, so as to facilitate the control of the contact state of the ablation catheter by the operator; The calculation of the size and direction of the contact force between the ablation electrode and the lesion site includes: The axial angle a is calculated with the ablation electrode head end plane as the reference plane, the ablation catheter head end plane is 0 degrees, the extension line of the ablation catheter axis is 90 degrees, the axial angle range is 0-90 degrees, the circumferential angle b is calculated with the ablation catheter head end identification plane S0 as the reference, and the ablation catheter head end reference plane is 0 degrees, which is rotated in the clockwise direction until 360 degrees returns to the reference plane.

6. The ablation catheter of claim 5, wherein, The piezoelectric assembly includes: The piezoelectric spring is arranged adjacent to the ablation electrode. a piezoelectric spring plate located at one end of the piezoelectric spring away from the ablation electrode and abutting against the piezoelectric spring, when the ablation electrode abuts against the lesion site, the piezoelectric spring and the piezoelectric spring plate are both compressed and deformed, and the compression current is generated; an insulating and heat-insulating sheet located between the ablation electrode and the piezoelectric spring; a base located at one end of the piezoelectric spring plate away from the piezoelectric spring, for fixing the piezoelectric spring plate.

7. The ablation catheter of claim 6, wherein, the ablation catheter further comprises a flow pipe in communication with the injection port, for injecting the cooling liquid into the chamber.

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