CN219230106U - Hot-cold composite ablation needle - Google Patents

Abstract

The utility model relates to the technical field of soft tissue ablation, in particular to a thermal-cold composite ablation needle which comprises a needle rod and a needle head positioned at the lower end of the needle rod, wherein a cooling working medium pipe is arranged in the center of the inside of the needle rod, an inner conductor is arranged at the outer side of the middle upper part of the cooling working medium pipe, an insulating pipe is arranged at the outer side of the inner conductor, an insulating pipe boss is arranged at the needle head end of the insulating pipe, an outer conductor is arranged at the outer side of the insulating pipe above the insulating pipe boss, an insulating pipe embedded section is formed by the insulating pipe below the insulating pipe boss, and the insulating pipe embedded section is inserted into the upper end of the needle head. The thermal-cold composite ablation needle has the double functions of microwave thermal ablation and cryoablation, expands the application range of microwave ablation and cryoablation, and adopts cryoablation microwave rewarming to adjacent areas and microwave ablation to distant areas aiming at tumor tissues with dangerous organs around target tissues.

Description

Hot-cold composite ablation needle

Technical Field

The utility model relates to the technical field of soft tissue ablation, in particular to a hot-cold composite ablation needle.

Background

Minimally invasive ablation treatment of solid tumor tissues and nodules by adopting a thermal mode is an important clinical means and is mainly divided into two main categories: thermal ablation and cryoablation. Common heating ablations include laser, radio frequency, microwave ablations, and common cryoablations include gaseous refrigeration, liquid refrigeration.

Microwave ablation is to release microwave energy to tumor tissue by using a microwave ablation needle, polar molecules (mostly water) in the tumor tissue rotate at high speed under the action of a microwave field to rapidly generate heat to reach higher temperature, the tissue dehydration, coagulation and protein denaturation are caused, so that the tumor tissue is inactivated and the proliferation capacity is lost, and the aim of treatment is fulfilled. Rapid freezing can cause tissue cells to necrosed to form irreversible coagulative necrotic frozen areas, whereas tumor cells are particularly sensitive to freezing than normal tissue.

Microwave energy belongs to radiation emission, has the characteristics of large action area, high heating speed and high operation efficiency, but is difficult to control the influence on adjacent blood vessels, and is easy to form carbonization phenomenon in a needle head area, and in order to prevent the needle rod from scalding normal tissues due to overhigh temperature in the operation process, additional cooling measures are needed to cool the needle rod. The cryoablation forms the ice ball, has the characteristics of good controllability of the ablation boundary and obvious ultrasonic development effect, but the cryoablation belongs to contact conduction cooling, and has slower freezing speed and long operation time. In order to prevent the needle rod from freezing the normal tissue at too low temperature in the operation process, a vacuum heat insulation layer is also required to be manufactured outside the cooling working medium return pipe, and the manufacturing process and the vacuum maintaining difficulty are high.

Chinese patent application CN201910872384.9 proposes a cold-hot ablation needle, in which the temperature of target tissue is reduced by the heat absorption and expansion of liquid refrigerant at the treatment site of the ablation needle, and then the tissue is quickly rewarmed by high-temperature alcohol vapor. The U.S. EndoCare argon helium knife uses argon to effect freezing and helium to rewire.

However, these methods have problems such as complicated equipment, long operation time, expensive helium, difficult availability, and the like, and are very inconvenient to use.

Disclosure of Invention

The utility model aims to provide a thermal-cold composite ablation needle which has the functions of microwave thermal ablation and cryoablation, expands the application range of microwave ablation and cryoablation, and adopts cryoablation microwave rewarming to adjacent areas and microwave ablation to distant areas aiming at tumor tissues with dangerous organs around target tissues.

In order to achieve the above purpose, the present utility model provides the following technical solutions:

the utility model provides a compound needle that melts of heat and cold, includes needle bar and is located the syringe needle of needle bar lower extreme, the inside central authorities of needle bar are equipped with the cooling working medium pipe, the outside of the well upper portion of cooling working medium pipe is equipped with the inner conductor, the outside of inner conductor is equipped with the insulating tube, the syringe needle end of insulating tube is equipped with the insulating tube boss, the outside of insulating tube above the insulating tube boss is equipped with the outer conductor, the insulating tube of insulating tube boss below forms insulating tube embedding section, the insulating tube embedding section inserts to the inside upper end of syringe needle.

The lower end of the inner conductor extends into the needle head, a needle head connecting sleeve is embedded between the outer wall of the inner conductor and the inner wall of the needle head, and the needle head connecting sleeve is positioned below the insulation pipe embedding section.

The inside of the needle head is provided with an evaporation cavity, the evaporation cavity is positioned below the needle head connecting sleeve, and the cooling working medium pipe extends into the evaporation cavity.

The needle head connecting sleeve is made of pure copper, and an inner conductor is connected with the inner wall of the needle head to form the microwave radiation antenna.

Wherein the inner conductor, the insulating tube and the outer conductor together form a rigid coaxial microwave transmission cable;

the inner conductor is made of copper, silver or a composite material with copper or silver on the surface;

the insulating tube is made of PTFE material and is tightly matched with the outer wall of the inner conductor and the inner wall of the outer conductor;

the outer conductor is made by adopting a copper plating or silver plating process on the inner wall of a medical 304 or 316 stainless steel tube, or adopts a thin-wall stainless steel tube as a needle rod, and a thin-wall copper or silver capillary tube is nested inside the needle rod.

The outer diameter of the insulation pipe embedded section is matched with the diameter of an inner hole at the upper end of the needle, and the length of the insulation pipe embedded section is 0.5-2 mm.

The outer diameter of the insulating tube boss is the same as that of the outer conductor, and the length of the insulating tube boss is 1-3 mm.

Wherein, the needle head is made of hard copper or hard metal material with copper or silver surface, the tip part is triangular needle-shaped or conical, the end part is provided with a hole towards the needle tip direction, and the wall thickness is 0.10-0.20 mm.

The inner conductor and the outer conductor are connected with the connector of the microwave input channel at the reverse end of the needle head to form a microwave transmission path.

The cooling working medium pipe is made of a stainless steel capillary, a wall surface of a needle end of the cooling working medium pipe is circumferentially perforated to form a cooling medium leakage hole, and the cooling medium leakage hole and a through hole of the cooling working medium pipe at the needle end form a cooling medium overflow channel together;

a gap of 0.2-0.3 mm is formed between the outer wall of the cooling working medium pipe and the inner wall of the inner conductor, so as to form a reflux channel of the cooling working medium;

the tail end of the cooling working medium pipe is connected with the cooling working medium supply pipe; the freezing working medium adopts liquid nitrogen or high-pressure argon.

Aiming at tumor tissues without dangerous organs around the target tissues, the thermal-cold composite ablation needle adopts microwave ablation to improve the operation efficiency; cryoablation and microwave ablation may also be used alternately to further destroy the focal tissue.

The heat-cold composite ablation needle of the utility model cancels a cooling water system of conventional microwave ablation, and simultaneously cancels a vacuum heat insulation structure of conventional cryoablation, a cooling working medium and a recovery device of heating working medium, thereby simplifying the system and improving the clinical application convenience.

Compared with the prior art, the utility model has the beneficial effects that:

(1) The microwave ablation needle in the prior art does not have the capability of performing cryoablation on focal tissues, and has limited use on focal tissues nearby dangerous organs; meanwhile, the re-heating technology adopted by the cryoablation needle in the prior art is a heat conduction mode, the ice ball melting speed is very low, and the operation efficiency is relatively low.

The interior of the thermal-cold composite ablation needle is provided with the frozen working medium channel, and the interior of the microwave ablation needle head is provided with the heat exchange structure, so that not only can the traditional microwave ablation be realized, but also the traditional cryoablation can be realized, the advantages of the two are combined, the range of focal tissue ablation treatment is widened, meanwhile, the diametrically opposite physical characteristics of the two energies are utilized, and the safety requirements of the two energy ablation processes, which need additional control, are solved through proper dosage control.

(2) By adopting the thermal-cold composite ablation needle, the ablation size of focal tissues nearby dangerous organs can be accurately controlled by utilizing a cryoablation technology, rapid ablation can be realized by utilizing a microwave ablation technology, and the operation efficiency is improved.

(3) The microwave radiation heating is utilized to accelerate the speed of the ice hockey re-heating, and the focus tissue is easier to destroy by rapid freezing and rapid re-heating.

(4) The vacuum heat insulation structure of the outer tube of the traditional cryoablation needle is eliminated, and the reliability of the product is improved.

(5) The cooling water channel of the traditional microwave ablation needle is eliminated.

(6) Quick needle withdrawal: when the cryoablation is adopted, the microwave is utilized to rapidly dissolve the ice ball needle track, so that the rapid needle withdrawal can be realized; when the microwave ablation is adopted, the cooling working medium is used for ensuring that the needle head is at a lower temperature so as not to cause tissue adhesion, and the quick needle withdrawal is realized.

Drawings

FIG. 1 is a schematic view of the needle body structure of the thermal-cold composite ablation needle of the present utility model;

FIG. 2 is a cooling medium path of the thermal-cold composite ablation needle of the utility model;

fig. 3-4 are schematic illustrations of thermal cold ablation procedures.

The device comprises a 1-cooling working medium pipe, a 2-inner conductor, a 3-insulating pipe, a 4-outer conductor, a 31-insulating pipe boss, a 32-insulating pipe embedded section, a 5-needle head connecting sleeve, a 6-evaporating cavity, a 7-leakage hole, an 8-needle head, a 9-freezing working medium, a 10-reflux working medium, a 11-thermal-cold composite ablation needle, a 12-focus tissue, a 13-freezing region, a 14-large blood vessel or organ and a 15-thermal field region.

Detailed Description

The following description of the embodiments of the present utility model will be made clearly and completely with reference to the accompanying drawings, in which it is apparent that the embodiments described are only some embodiments of the present utility model, but not all embodiments. All other embodiments, which can be made by those skilled in the art based on the embodiments of the utility model without making any inventive effort, are intended to be within the scope of the utility model.

Referring to fig. 1, a thermal-cold composite ablation needle comprises a needle rod and a needle head 8 positioned at the lower end of the needle rod, wherein a cooling working medium pipe 1 is arranged in the center of the needle rod, an inner conductor 2 is arranged at the outer side of the middle upper part of the cooling working medium pipe 1, an insulating pipe 3 is arranged at the outer side of the inner conductor 2, an insulating pipe boss 31 is arranged at the needle head end of the insulating pipe 3, an outer conductor 4 is arranged at the outer side of the insulating pipe 3 above the insulating pipe boss 31, an insulating pipe embedded section 32 is formed by the insulating pipe 3 below the insulating pipe boss 31, and the insulating pipe embedded section 32 is inserted into the upper end of the needle head 8.

The lower end of the inner conductor 2 extends into the needle 8, a needle connecting sleeve 5 is embedded between the outer wall of the inner conductor 2 and the inner wall of the needle 8, and the needle connecting sleeve 5 is positioned below the insulating tube embedded section 32.

The inside of syringe needle 8 is equipped with evaporating chamber 6, evaporating chamber 6 is located the below of syringe needle adapter sleeve 5, cooling medium pipe 1 extends to evaporating chamber 6 is interior.

The needle connecting sleeve 5 is made of pure copper, and connects the inner conductor 2 with the inner wall of the needle 8 to form a microwave radiation antenna.

The inner conductor 2, the insulating tube 3 and the outer conductor 4 together form a rigid coaxial microwave transmission cable; the inner conductor 2 is made of copper, silver or a composite material with copper or silver on the surface; the insulating tube 3 is made of PTFE material and is tightly matched with the outer wall of the inner conductor 2 and the inner wall of the outer conductor 4; the outer conductor 4 is made by adopting a copper plating or silver plating process on the inner wall of a medical 304 or 316 stainless steel tube, or adopts a thin-wall stainless steel tube as a needle rod, and a thin-wall copper or silver capillary tube is nested inside. The rigid structure of the inner conductor 2, the insulating tube 3 and the outer conductor 4 serves as the needle bar of the ablation needle.

The outer diameter of the insulation tube embedded section 32 is matched with the diameter of an inner hole at the upper end of the needle 8, the length of the insulation tube embedded section 32 is 0.5-2 mm, and the insulation tube embedded section is tightly matched with the needle 8 to play a supporting role.

The outer diameter of the insulating tube boss 31 is the same as the outer diameter of the outer conductor 4, and the length of the insulating tube boss 31 is 1-3 mm for insulation between the inner conductor 2 and the outer conductor 4.

The needle 8 is made of hard copper or a hard metal material with copper or silver on the surface, the tip part of the needle is triangular needle-shaped or conical, the end part of the needle is provided with a hole towards the direction of the needle tip, and the wall thickness is 0.10-0.20 mm.

The inner conductor 2 and the outer conductor 4 are connected with the connector of the microwave input channel at the opposite end of the needle head to form a microwave transmission path.

The cooling working medium pipe 1 is made of a stainless steel capillary, a leakage hole 7 (namely an orifice) for cooling medium is formed by circumferentially opening a hole in the wall surface of the needle end of the cooling working medium pipe 1, the leakage hole 7 and a through hole of the cooling working medium pipe 1 at the needle end form a cooling medium overflow channel together, and the overflow speed of the cooling working medium is increased.

A gap of 0.2-0.3 mm is arranged between the outer wall of the cooling working medium pipe 1 and the inner wall of the inner conductor 2, so as to form a reflux channel of the cooling working medium;

the tail end of the cooling working medium pipe 1 is connected with a cooling working medium supply pipe; the freezing medium 9 adopts liquid nitrogen or high-pressure argon.

Referring to fig. 2, the phase change process and the refrigeration process of the cooling working medium are specifically as follows:

after entering the cooling working medium pipe 1, the freezing working medium 9 flows out from the leakage hole 7 (orifice) to the evaporation cavity 6, and absorbs heat through the needle head 8 to expand and evaporate, the reflux working medium channel is normal pressure, and the reflux working medium 10 is naturally discharged from the ablation needle reflux working medium channel under the extrusion of the freezing working medium 9, so that the heat of the needle head 8 is continuously taken away. Because the temperature of the freezing medium 9 is between minus 180 ℃ and minus 196 ℃ in theory and a great temperature difference exists between the freezing medium and focal tissues, the needle head 8 is a good conductor of heat, thereby the focal tissue temperature contacted by the needle head 8 is rapidly reduced to form an ice ball state so as to achieve the aim of destroying the cell structure of the focal tissues, which is also a general use principle for cryoablation of tissues at present.

The temperature of the reflux working medium 10 for completing cold and heat exchange through the needle head 8 is still lower, and the insulation tube 3 has poor heat conductivity, so that the temperature influence on the outer surface of the needle rod is limited, and the normal tissue frostbite degree can not be reached.

The reflux working medium 10 is argon or liquid nitrogen which is near normal temperature, is nontoxic, odorless and harmless, and can be directly discharged into the air without recovery treatment.

Referring to fig. 3-4, the thermal-cold ablation method and control method specifically comprises the following steps:

fig. 3-4 show the positional relationship of focal tissue ablation in the vicinity of a dangerous organ, which uses cryoablation, microwave rewarming, and needle withdrawal microwave ablation.

As shown in fig. 3, the tip of the needle 8 is penetrated into the far end of the focal tissue 12, the cryoablation mode is started to fill larger flow of the cooling working medium until a freezing area 13 is formed, and the freezing working medium 9 is kept closed for a proper time; the low power microwaves are started to rewet, and the rewet microwave power is preferably insufficient to heat the large blood vessels or the viscera 14. And repeating the process for a plurality of times to realize the cold and hot ablation of the dangerous area. The stage adopts microwave radiation heating, and the speed of the microwave radiation heating is much faster than that of the traditional heat conduction rewarming.

As shown in fig. 4 (wherein 15 is a thermal field area), then the ablation needle is retracted for a certain distance, a microwave ablation mode is started according to the conventional power, and meanwhile, a refrigerating working medium 9 with smaller flow is started to cool the inner conductor of the thermal-cold composite ablation needle 11 and the needle head 8, so that the condition that normal tissues are scalded due to the fact that the surface temperature of a needle rod is too high during high-power microwave ablation is prevented; as the surface temperature of the needle head 8 is reduced, the carbonization adhesion phenomenon of contact tissues is reduced, and the high-efficiency characteristic of microwave ablation is fully utilized to realize rapid thermal ablation at the moment, so that the operation efficiency is improved. Both modes of energy ablation provide complete coverage of the focal tissue 12.

Because the heat-cold composite ablation needle can realize the capability of microwave radiation and cold-heat exchange, only a cryoablation mode or a microwave ablation mode or a combination of the two can be adopted according to the size and the position of focal tissue 12 in clinical practical application.

Although embodiments of the present utility model have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made therein without departing from the principles and spirit of the utility model, the scope of which is defined in the appended claims and their equivalents.

Claims (10)

1. A hot and cold compound ablation needle, which is characterized in that: including needle bar and needle (8) that are located the needle bar lower extreme, the inside central authorities of needle bar are equipped with cooling working medium pipe (1), the outside on the well upper portion of cooling working medium pipe (1) is equipped with inner conductor (2), the outside of inner conductor (2) is equipped with insulating tube (3), the needle end of insulating tube (3) is equipped with insulating tube boss (31), the outside of insulating tube (3) of insulating tube boss (31) top is equipped with outer conductor (4), insulating tube (3) of insulating tube boss (31) below forms insulating tube embedding section (32), insulating tube embedding section (32) inserts inside the upper end of needle (8).

2. The thermal-cold composite ablation needle of claim 1, wherein: the lower end of the inner conductor (2) extends into the needle head (8), a needle head connecting sleeve (5) is embedded between the outer wall of the inner conductor (2) and the inner wall of the needle head (8), and the needle head connecting sleeve (5) is positioned below the insulating tube embedded section (32).

3. The thermal-cold composite ablation needle of claim 2, wherein: the inside of syringe needle (8) is equipped with evaporating chamber (6), evaporating chamber (6) are located the below of syringe needle adapter sleeve (5), cooling medium pipe (1) extend to in evaporating chamber (6).

4. A thermal-cold composite ablation needle according to claim 3, wherein: the needle head connecting sleeve (5) is made of pure copper, and the inner conductor (2) is connected with the inner wall of the needle head (8) to form the microwave radiation antenna.

5. The thermal-cold composite ablation needle of claim 1, wherein: the inner conductor (2), the insulating tube (3) and the outer conductor (4) together form a rigid coaxial microwave transmission cable;

the insulating tube (3) is tightly matched with the outer wall of the inner conductor (2) and the inner wall of the outer conductor (4).

6. The thermal-cold composite ablation needle of claim 1, wherein: the outer diameter of the insulating tube embedded section (32) is matched with the diameter of an inner hole at the upper end of the needle head (8), and the length of the insulating tube embedded section (32) is 0.5-2 mm.

7. The thermal-cold composite ablation needle of claim 1, wherein: the outer diameter of the insulating tube boss (31) is the same as the outer diameter of the outer conductor (4), and the length of the insulating tube boss (31) is 1-3 mm.

8. The thermal-cold composite ablation needle of claim 1, wherein: the tip of the needle head (8) is triangular needle-shaped or conical, the end part of the needle head is provided with a hole towards the direction of the needle tip, and the wall thickness is 0.10-0.20 mm.

9. The thermal-cold composite ablation needle of claim 1, wherein: the inner conductor (2) and the outer conductor (4) are connected with a connector of the microwave input channel at the reverse end of the needle head to form a microwave transmission path.

10. The thermal-cold composite ablation needle of claim 1, wherein: a leakage hole (7) of the cooling medium is formed by circumferentially opening a hole on the wall surface of the needle end of the cooling medium pipe (1), and the leakage hole (7) and a through hole of the cooling medium pipe (1) at the needle end form a cooling medium overflow channel;

a gap of 0.2-0.3 mm is arranged between the outer wall of the cooling working medium pipe (1) and the inner wall of the inner conductor (2) to form a reflux channel of the cooling working medium;

the tail end of the cooling working medium pipe (1) is connected with a cooling working medium supply pipe; the freezing working medium (9) adopts liquid nitrogen or high-pressure argon.

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