CN201822910U - Perfusion type radiofrequency ablation catheter - Google Patents

Abstract

The utility model discloses a perfusion type radiofrequency ablation catheter which comprises a catheter body comprising a far end, a near end and a center cavity, wherein an ablation part is fixed at the far end of the catheter body; a control handle is fixed at the near end of the catheter body; the ablation part comprises an elastic head end pipe comprising a far end, a near end and at least one cavity; an ablation electrode is arranged at the far end of the elastic head end pipe; the ablation electrode comprises an electrode casing including at least one cavity; small holes are formed on the ablation electrode; perfusion liquid can flow into the cavity of the ablation electrode through a pipeline and flow out from the small holes; and the effective total area of the small holes is smaller than the effective sectional area of the pipeline. By adopting the perfusion type radiofrequency ablation catheter, the probability of blood condensation can be efficiently reduced, and the cooling effect can be improved.

Description

Filling type radio-frequency (RF) ablation conduit

Technical field

This utility model relates to a kind of radio-frequency (RF) ablation conduit, relates to a kind of filling type radio-frequency (RF) ablation conduit concretely.

Background technology

Electricity physiological electrode conduit (hereinafter to be referred as electrode catheter) has been widely used in the medical practice at present, and the electricity physiological signal that it is mainly used in inner each position of record heart carries out electricity irritation to heart, thereby reaches the purpose to heart disease mapping and treatment.Its using method is at first puncture femoral vein blood vessel or internal jugular vein blood vessel, under radioscopy, along lumen of vessels electrode catheter is delivered to diverse location in the heart, and heart is carried out electrophysiologic study, mapping or radio-frequency (RF) ablation.

In general radiofrequency ablation procedures, the ablating electrode portion temperature of conduit constantly raises, and can cause blood around it to produce and condense, and forms one deck condensed layer at electrode surface, thereby makes that in the ablation procedure, radio-frequency (RF) energy constantly increases to the impedance of organized delivery.Therefore, in some radiofrequency ablation procedures, can select to adopt filling type radio-frequency (RF) ablation conduit.

A kind of filling type conduit is disclosed as U.S. Pat 6466818, comprise catheter body, melt part and porous ablating electrode, wherein, described ablating electrode comprises a body and a plug-in unit, described body is formed by the porous material sintering, and described plug-in unit comprises at least one fluid passage; Described conduit also comprises intrusion pipe, and described infusion liquid goes out through the orifice flow of described intrusion pipe from described ablating electrode, thereby described electrode is cooled off.

Existing filling type radio-frequency (RF) ablation conduit, its cooling effect is more undesirable.

Summary of the invention

This utility model provides a kind of filling type radio-frequency (RF) ablation conduit, comprises catheter body, and described catheter body has far-end, near-end and central lumen, is fixed with at the far-end of described catheter body and melts part, is fixed with joystick at the near-end of described catheter body;

The described part that melts comprises elasticity head end pipe, and described elasticity head end pipe has far-end, near-end and at least one chamber, is provided with ablating electrode at the far-end of described elasticity head end pipe;

Described ablating electrode comprises electrode shell, and described electrode shell comprises at least one cavity, and described ablating electrode is provided with aperture;

Also comprise pipeline, draught line and lead in described central chamber, it extends in the cavity of described ablating electrode by described elasticity head end pipe; Perfusion fluid can flow in the cavity of described ablating electrode by described pipeline, and flows out in described aperture.

Effective gross area of described aperture is less than the net sectional area of described pipeline.

Preferably, at least one heat sensor extends in the cavity of described electrode shell by described elasticity head end pipe, and described heat sensor is fixed on the described electrode shell; Described heat sensor also can be suspended in the cavity of described electrode shell.

Preferably, the quantity of described aperture is for being no less than 12, and the diameter of described aperture is for being no more than 0.2mm, and is more preferred, and the diameter of described aperture is 0.07-0.15mm.

Preferably, the wall thickness of described electrode shell is 0.1-0.3mm, and is more preferred, and the wall thickness of described electrode shell is 0.15-0.2mm.

Preferably, described aperture is distributed on the described electrode shell uniformly.

Preferably, be provided with adapter between described ablating electrode and the described elasticity head end pipe.

Preferably, described elasticity head end pipe comprises first chamber, second chamber and the 3rd chamber, and described pipeline extends in first chamber of elasticity head end pipe, and lead and described heat sensor extend in described second chamber, and draught line extends in described the 3rd chamber.

In a specific embodiment, described adapter comprises three holes, and three sections hollow pipes extend in described three holes respectively, and it is connected with first chamber, second chamber and the 3rd chamber respectively.

Preferably, described three sections hollow pipes extend to the two ends of described adapter respectively.

In a specific embodiment, described three sections hollow pipes are sealingly fastened in respectively in three holes of described adapter.

Of the present utility model one preferred embodiment in, in the described filling type radio-frequency (RF) ablation conduit, effective gross area of described aperture is less than the net sectional area of described pipeline, can make perfusion fluid be spurting from described aperture flows out, improve cooling effect, and effectively reduced the chance of blood clotting.

Description of drawings

Fig. 1 is the structural representation according to filling type radio-frequency (RF) ablation conduit of the present utility model;

The cutaway view that shown in Figure 2 is according to thecatheter body 12 of preferred embodiment of the present utility model,expression catheter body 12 and the annexation that meltspart 13;

Fig. 3 is the cutaway view along A-A line shown in Figure 1;

Fig. 4 is the cutaway view along B-B line among Fig. 3.

The specific embodiment

Below by embodiment, and in conjunction with the accompanying drawings, the technical solution of the utility model is described in further detail, but this utility model is not limited only to the following examples.

Shown in Figure 1 is the structural representation of a kind of preferred filling type radio-frequency (RF)ablation conduit 10 of the present utility model, comprisecatheter body 12, it has far-end and near-end, is provided with at the far-end of describedcatheter body 12 and meltspart 13, is provided withjoystick 11 at the near-end of describedcatheter body 12.

The cutaway view that shown in Figure 2 is according to thecatheter body 12 of preferred embodiment of the present utility model,expression catheter body 12 and the annexation that melts part 13.Describedcatheter body 12 comprises reinforcedpipe 22 and is placed in its outsidemain body pipe 28 that describedmain body pipe 28 can be made by the macromolecular material of biocompatibility, and is preferred, made by polyether block amide, polyurethane or nylon material.Preferably, the inwall of describedmain body pipe 28 comprises one deck wire braid (not shown) at least, can be the rustless steel braid, and described wire braid can be one deck, two-layer or more.Described reinforcedpipe 22 comprises a singlecentral lumen 23, and it can be made by any proper polymer material, and is preferred, by polyether block amide, polyurethane or the extrusion modling of nylon material one.Describedcatheter body 12 is preferably elongated, flexible, but incompressible on its length direction, describedcentral lumen 23 extending axially in catheter body 12.Lead 25,draught line 21 andpipeline 26 extend in describedcentral lumen 23.

Preferably, the describedpart 13 that melts comprises elasticityhead end pipe 31, and it can be made by biocompatible materials, comprises far-end, near-end,first chamber 35,second chamber 36 and the 3rd chamber 37.Preferably, the inwall of described elasticityhead end pipe 31 comprises one deck wire braid (not shown) at least, can be the rustless steel braid, and described wire braid can be one deck, two-layer or more.Describedfirst chamber 35,second chamber 36 and the3rd chamber 37 can all be eccentric chambers, also can be that a central lumen and two eccentric chambers constitute.

Preferably, the near-end of described elasticityhead end pipe 31 islevigate end 34, as shown in Figure 2, its external diameter matches with the internal diameter ofcatheter body 12, describedlevigate end 34 is inserted in thecatheter body 12, it can be fixed by bonding, welding or other suitable manner, and is preferred, by ultraviolet curing glue that itself andcatheter body 12 bondings is fixing.

The cutaway view that shown in Figure 3 is along A-A line among Fig. 1, the cutaway view that shown in Figure 4 is along B-B line among Fig. 3.As shown in Figure 4, the far-end at described elasticityhead end pipe 31 is provided with ablating electrode 17.Along bullet

The propertyhead end pipe 31 length direction on, preferably be provided withring electrode 16, its quantity can be according to actual needs and different, can not have ring electrode, also can be one, two, three, four or more.As shown in Figure 4, described ablatingelectrode 17 compriseselectrode shell 71 and is located at least onecavity 76 in the described electrode shell 71.Describedelectrode shell 71 comprises cylindricalouter surface 90 and end face 91.Preferably, be provided withadapter adapter 74 between described ablatingelectrode 17 and elasticityhead end pipe 31, it can be made of any suitable material, is preferably stainless steel material and makes.Describedadapter 74 comprises threeholes 80,81,82, is connected withfirst chamber 35,second chamber 36 and the3rd chamber 37 of elasticityhead end pipe 31 respectively.Preferably, sealing and fixing has hollow pipe respectively in threeholes 80,81,82 of describedadapter 74, and sealing and fixing hashollow pipe 83 in the wherein saidhole 80, and the hollow pipe in other two holes is not shown.Described hollow pipe can be made of any suitable material, is preferably stainless steel tube, and described hollow pipe is preferably respectively and extends to the two ends of described adapter 74.Described hollow pipe can be sealingly fastened in the describedhole 80,81,82 by welding, bonding or other suitable manner.Describedadapter 74 is used to connect described elasticityhead end pipe 31 and described ablatingelectrode 17, and can play the effect of sealing, prevents that the perfusion fluid in the ablatingelectrode 17 from flowing backwards.

Preferably, comprise also that in describedcentral lumen 23 at least oneheat sensor 33 extends within it, it can be an occasionally critesistor of thermoelectricity; The quantity of described heat sensor can also be two, three, four or more, as shown in Figure 4, in a preferred embodiment, the far-end of describedheat sensor 33 extends insecond chamber 36 of elasticityhead end pipe 31 by thecentral lumen 23 ofcatheter body 12, extends in thecavity 76 of described ablatingelectrode 17 by the hollow pipe in the hole on the describedadapter 74 81 then.Describedheat sensor 33 can be fixed on theelectrode shell 71 of described ablatingelectrode 17 by welding, bonding or other suitable manner, on theend face 91 aselectrode shell 71 as described in can being fixed in byplumb joint 73, it can be monitored the temperature of described ablatingelectrode 17 and tissue more accurately, thereby regulate the flow of pipeline as required, make ablation effect and cooling effect improve.Describedheat sensor 33 also can be suspended in the describedcavity 76, does not contact with described electrode shell 71.In the time of in perfusion fluid flow to describedcavity 76, describedheat sensor 33 is suspended in the liquid atmosphere, its temperature sensitivity to each point on described ablatingelectrode 17 surfaces is more consistent, thereby can more efficiently temperature to described ablatingelectrode 17 monitor.The near-end of describedheat sensor 33 extends into describedjoystick 11 bycentral lumen 23, and extends out from describedjoystick 11, and (not shown) links to each other with device for detecting temperature.

Describedelectrode shell 71 is provided with some apertures 72, and described aperture 72 can form by any suitable processing mode, preferably forms by boring.Described aperture 72 can be distributed on the described electrode shell in any suitable manner, can be uniform distribution, also can be irregular distribution; Described aperture 72 can be only

Be distributed on thecylindrical surface 90 of describedelectrode shell 71, also can only be distributed on theend face 91 of describedelectrode shell 71, also can be distributed in simultaneously on thecylindrical surface 90 andend face 91 of described electrode shell 71.Preferably, described aperture 72 is distributed on thecylindrical surface 90 andend face 91 of described electrode shell 72 uniformly.Effective gross area of described aperture 72 is less than the net sectional area ofpipeline 26; The net sectional area of describedpipeline 26 is meant that the effective cross section of stenosis of this pipeline is long-pending, and effective gross area of described aperture is meant the effective area sum of all apertures.This design makes in the path that perfusion fluid flows through in conduit, pressure landing at described aperture 72 places is maximum, can can make perfusion fluid be spurting from described aperture 72 with the little injection pressure of trying one's best flows out, improve described ablatingelectrode 17 uniform cooling effects, and effectively reduced the chance of blood clotting.In a preferred embodiment, the quantity of described aperture is for being no less than 12, and the diameter of described aperture is for being no more than 0.2mm, and is more preferred, and the diameter of described aperture is 0.07-0.15mm.

The wall thickness of describedelectrode shell 71 can bring certain influence to the heat conductivility of described ablatingelectrode 17, the wall thickness of wherein saidelectrode shell 71 is more little, its heat conductivility is good more, cooling effect behind the perfusion fluid is also good more, therefore, those skilled in the art can be according to actual needs be provided with the wall thickness of describedelectrode shell 71, and the wall thickness of electrode shell described in the utility model is preferably 0.1-0.3mm; More preferred, the wall thickness of described electrode shell is 0.15-0.2mm.

Pipeline 26, it can be made by any suitable material, is preferably made by rustless steel or platinumiridio material.The far-end of describedpipeline 26 can extend to first chamber, the 35 interior parts of described elasticityhead end pipe 31 by thecentral lumen 23 ofcatheter body 12, describedpipeline 26 also can extend infirst chamber 35 of elasticityhead end pipe 31, extends in thecavity 76 of described ablatingelectrode 17 by the hollow pipe in thehole 80 on describedadapter 74 then.

The near-end of describedpipeline 26 extends in the describedjoystick 11 by thecentral lumen 23 ofcatheter body 12, its fixing means can adopt any suitable method well known to those skilled in the art to fix, for example the near-end at describedpipeline 26 connects onesection arm 14, as shown in Figure 1, describedarm 14 can be made by any suitable material, preferably make by polyether block amide, polyurethane or nylon material, it extends to describedjoystick 11 outsides, and end andfemale Luer 15 are connected and fixed.

Perfusion fluid, can be any suitable liquid, preferred cool brine, it enters in the describedpipeline 26 by describedarm 14, whenpipeline 26 extends in thecavity 76 of described ablatingelectrode 17, perfusion fluid flow in the describedcavity 76 bypipeline 26, flow to the outside of describedconduit 10 then by described hole 72.Whenpipeline 26 extended infirst chamber 35 of described elasticityhead end pipe 31, perfusion fluid was frompipeline 26

After flowing out, flow in thecavity 76 of described ablatingelectrode 17 by thehollow pipe 83 infirst chamber 35 and the describedhole 80, thereby described ablatingelectrode 17 is cooled off, lowers the temperature.Perfusion fluid is injected into the surface of ablatingelectrode 17, and not only counter electrode surface and surrounding tissue have played cooling, cooling effect, has also effectively reduced the degree of condensing of blood, has effectively improved ablation effect.

Draught line 21 is preferably made by rustless steel or Nitinol, and as shown in Figure 3 and Figure 4, its far-end extends in the3rd chamber 37 of elasticityhead end pipe 31 by central lumen 23.The one section draughtline 21 that incatheter body 12, extends, preferred, its outside is withbourdon tube 29, and describedbourdon tube 29 is preferably the tight structure of band tightening force, and its outside is with the second protective casing (not shown).Described second protective casing can be made by any suitable material, is preferably made by polyamide material, is used for describedbourdon tube 29 and extends within it.The far-end of described second protective casing and near-end can be fixed on the describedbourdon tube 29 by bonding, welding or other suitable manner, and be preferred, is bonded on the describedbourdon tube 29 by ultraviolet curing glue.As shown in Figure 4; the one section draughtline 21 that in described elasticityhead end pipe 31, extends; preferably; its outside is with firstprotective casing 32; described firstprotective casing 32 can be made by any suitable material; preferably made by polytetrafluoroethylmaterial material, it is located in the described elasticityhead end pipe 31, is used for describeddraught line 21 and extends within it.

The far-end of describeddraught line 21 extends in thecavity 76 of described ablatingelectrode 17 by the hollow pipe in the hole on the describedadapter 74 82, its end is fixed in the described ablatingelectrode 17 by welding, bonding or other suitable manner, preferably fixes by welding.

The near-end of describeddraught line 21 is fixed on the describedjoystick 11, and its fixing means can adopt any suitable method well known to those skilled in the art to fix.The fixing means of the draught line that has disclosed among laid-open U.S. Patents US7300438 and the US6571131 for example.

Lead 25, as Fig. 2 and Fig. 3 and shown in Figure 4, preferred, its far-end extends insecond chamber 36 of elasticityhead end pipe 31 bycentral lumen 23, be electrically connected with ablatingelectrode 17 andring electrode 16 respectively, its connected mode is welding or other suitable manner, and is preferably fixing by welding.Preferably, be provided with thread-protectedtube 27 in the outside of describedlead 25.

The near-end oflead 25 is fixed on the described joystick 1, and its fixing means can adopt any suitable method well known to those skilled in the art to fix, and for example is fixed by welding on the corresponding plug.

It is described that embodiment of the present utility model is not limited to the foregoing description; under the situation that does not depart from spirit and scope of the present utility model; those of ordinary skills can make various changes and improvements to this utility model in form and details, and these all are considered to fall into protection domain of the present utility model.

Claims (12)

1. a filling type radio-frequency (RF) ablation conduit is characterized in that comprising catheter body, and described catheter body has far-end, near-end and central lumen, and the far-end of described catheter body is fixed with and melts part, and the near-end of described catheter body is fixed with joystick;

The described part that melts comprises elasticity head end pipe, and described elasticity head end pipe has far-end, near-end and at least one chamber, is provided with ablating electrode at the far-end of described elasticity head end pipe;

Described ablating electrode comprises electrode shell, and described electrode shell comprises at least one cavity, and described ablating electrode is provided with aperture;

Also comprise pipeline, draught line and lead in described central chamber, it extends in the cavity of described ablating electrode by described elasticity head end pipe; Perfusion fluid can flow in the cavity of described ablating electrode by described pipeline, and flows out in described aperture;

Effective gross area of described aperture is less than the net sectional area of described pipeline.

2. filling type radio-frequency (RF) ablation conduit according to claim 1 is characterized in that at least one heat sensor extends in the cavity of described electrode shell by described elasticity head end pipe, and described heat sensor is fixed on the described electrode shell.

3. filling type radio-frequency (RF) ablation conduit according to claim 1 is characterized in that at least one heat sensor extends in the cavity of described electrode shell by described elasticity head end pipe, and described heat sensor is suspended in the described cavity.

4. according to claim 1 or 2 or 3 described filling type radio-frequency (RF) ablation conduits, the quantity that it is characterized in that described aperture is for being no less than 12, and the diameter of described aperture is for being no more than 0.2mm.

5. filling type radio-frequency (RF) ablation conduit according to claim 4, the diameter that it is characterized in that described aperture is 0.07-0.15mm.

6. according to claim 1 or 2 or 3 described filling type radio-frequency (RF) ablation conduits, the wall thickness that it is characterized in that described electrode shell is 0.1-0.3mm.

7. filling type radio-frequency (RF) ablation conduit according to claim 6, the wall thickness that it is characterized in that described electrode shell is 0.15-0.2mm.

8. according to claim 1 or 2 or 3 described filling type radio-frequency (RF) ablation conduits, it is characterized in that described aperture is distributed on the described electrode shell uniformly.

9. according to claim 1 or 2 or 3 described filling type radio-frequency (RF) ablation conduits, it is characterized in that being provided with adapter between described ablating electrode and the described elasticity head end pipe.

10. filling type radio-frequency (RF) ablation conduit according to claim 9, it is characterized in that described elasticity head end pipe comprises first chamber, second chamber and the 3rd chamber, described pipeline extends in first chamber of elasticity head end pipe, lead and described heat sensor extend in described second chamber, and draught line extends in described the 3rd chamber.

11. filling type radio-frequency (RF) ablation conduit according to claim 10 is characterized in that described adapter comprises three holes, three sections hollow pipes extend in described three holes respectively, and it is connected with first chamber, second chamber and the 3rd chamber respectively; Preferably, described three sections hollow pipes extend to the two ends of described adapter respectively.

12. filling type radio-frequency (RF) ablation conduit according to claim 11 is characterized in that described three sections hollow pipes are sealingly fastened in respectively in three holes of described adapter.

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