技术领域Technical field
本发明属于微波消融技术领域，涉及一种肿瘤能量消融装置，尤其涉及一种冷热结合消融装置。The invention belongs to the technical field of microwave ablation, relates to a tumor energy ablation device, and in particular, to a combined hot and cold ablation device.
背景技术Background technique
肺癌是常见的恶性肿瘤之一，且其发病率呈逐年上升的趋势。目前，外科手术切除仍然是临床实践中肺癌治疗的主要手段，但是对于年龄较大、体质偏弱或心肺功能较差的患者，并不适合进行传统外科手术治疗，因此，临床上仍在不断探索新的治疗手段以改善治疗效果并提高患者的生存率。Lung cancer is one of the common malignant tumors, and its incidence rate is increasing year by year. At present, surgical resection is still the main method for the treatment of lung cancer in clinical practice. However, patients who are older, weak, or have poor cardiopulmonary function are not suitable for traditional surgical treatment. Therefore, clinical exploration is still ongoing. New treatments to improve treatment outcomes and improve patient survival rates.
临床上近年来在肿瘤微波消融技术上取得了长足的进展，微波消融是利用微波能作用组织产生热效应，在较短的时间内形成稳定的球形热场，肿瘤组织在高温下被凝固灭活，进而逐步消融达到治疗的目的。由于微波消融技术的安全性高且创伤小，并对组织的作用范围大小可控，所以越来越受到推崇。Clinically, considerable progress has been made in tumor microwave ablation technology in recent years. Microwave ablation uses microwave energy to act on tissue to produce a thermal effect, forming a stable spherical thermal field in a short period of time. The tumor tissue is coagulated and inactivated at high temperature. Then gradually ablate to achieve the purpose of treatment. Microwave ablation technology is becoming more and more popular due to its high safety, low trauma, and controllable scope of action on tissues.
微波消融装置使用时，临床希望微波消融装置较细，以便在穿刺时对穿刺路径上的血管、神经等组织的损伤达到最小。同时，还希望微波消融装置的功率尽可能的大，以达到良好的消融效果。目前常用的微波消融装置包括同轴电缆和高频接头，同轴电缆是由金属外导体、金属内导体以及内外导体间的塑料绝缘层组成。同轴电缆的远端剥去一段金属外导体，可选择性地留下内外导体间的塑料绝缘层和金属内导体，金属内导体接微波消融装置的尖端。由于尖端不受金属外导体的屏蔽，因此，微波能量能够由此辐射出去，肿瘤吸收了微波，会产生高温热凝固作用，将肿瘤细胞热凝固灭活。When using a microwave ablation device, it is clinically desired that the microwave ablation device be thin so as to minimize damage to blood vessels, nerves and other tissues along the puncture path during puncture. At the same time, it is also hoped that the power of the microwave ablation device will be as large as possible to achieve good ablation effects. Currently commonly used microwave ablation devices include coaxial cables and high-frequency connectors. Coaxial cables are composed of a metal outer conductor, a metal inner conductor, and a plastic insulation layer between the inner and outer conductors. A section of the metal outer conductor is stripped off the distal end of the coaxial cable, leaving selectively the plastic insulation layer between the inner and outer conductors and the metal inner conductor. The metal inner conductor is connected to the tip of the microwave ablation device. Since the tip is not shielded by the metal outer conductor, microwave energy can be radiated from it. When the tumor absorbs the microwave, it will produce high-temperature thermal coagulation, which will inactivate the tumor cells.
然而，同轴电缆的截面积与其可承载的微波能量是成正比的，要想加大热凝肿瘤的范围，就需要增加同轴电缆的直径，使用直径较大的同轴电缆制成的微波消融装置进行临床穿刺，将不可避免地会对穿刺路径中的血管、神经或其它组织造成严重伤害，增加了手术操作的复杂性和危险性。当不改变同轴电缆的截面积，仅强制增大传导输出功率时，会导致电流过大而发热，可能会烧毁同轴电缆，甚至导致同轴电缆周围正常组织被烫伤。However, the cross-sectional area of a coaxial cable is proportional to the microwave energy it can carry. If you want to increase the scope of thermal coagulation tumors, you need to increase the diameter of the coaxial cable. Use a microwave oven made of a larger diameter coaxial cable. Clinical puncture with an ablation device will inevitably cause serious damage to blood vessels, nerves or other tissues in the puncture path, increasing the complexity and risk of surgical operations. When the cross-sectional area of the coaxial cable is not changed and only the conductive output power is forcibly increased, excessive current will result in heat generation, which may burn the coaxial cable or even cause burns to normal tissues around the coaxial cable.
而且，肺泡中空气含量占比大，对于微波能量的吸收效率较低，想要扩大消融范围则需要加大同轴电缆的功率，同时发热量也会相应增加，导管过热不仅会损坏导管外层的内窥镜，还会对非靶点组织造成影响。Moreover, the air content in the alveoli is large, and the absorption efficiency of microwave energy is low. If you want to expand the ablation range, you need to increase the power of the coaxial cable, and the heat generation will also increase accordingly. Overheating of the catheter will not only damage the outer layer of the catheter The endoscope will also affect non-target tissues.
冷冻的方法同样能够杀灭肿瘤，但是单纯冷冻治疗的效果不好。氩氦刀治疗利用氩气压缩制冷，并利用氦气压缩产热，经过多次冷冻-复温的循环使肿瘤灭活更为彻底，这就需要氩气压缩提供的冷却速度足够快，因此氩氦刀对于耗材管路的强度有更高的要求；另外，氦气压缩复温的温度只能达到40℃左右，影响灭杀肿瘤细胞的效果。Freezing methods can also kill tumors, but cryotherapy alone is not as effective. Argon-helium scalpel therapy uses argon gas compression for refrigeration and helium gas compression to generate heat. After multiple freezing-rewarming cycles, the tumor can be inactivated more thoroughly. This requires the cooling rate provided by argon gas compression to be fast enough, so argon Helium knives have higher requirements for the strength of consumable pipelines; in addition, the temperature of helium compression and rewarming can only reach about 40°C, which affects the effect of killing tumor cells.
CN 104720892A公开了一种用于囊性癌肿瘤消融治疗的微波消融天线，包括：绝缘刺头、极芯、同轴电缆、引水管、堵水轴、以及套在引水管外的内管和套在内管外的外管，内、外管的前端套装在绝缘刺头的后端凸台上，外管的前部开设有侧孔，内外管之间固定有一根头部伸至该侧孔附近的毛细管，适用于囊性癌肿的专用注射抽吸，引水管与同轴电缆之间的间隙形成进水道，引水管与内管之间的间隙形成出水到，利用循环的冷却水对天线进行高效降温。CN 104720892A discloses a microwave ablation antenna for cystic cancer tumor ablation treatment, including: an insulated thorn head, a polar core, a coaxial cable, a water diversion pipe, a water plugging shaft, and an inner tube and a sheath placed outside the water diversion pipe. There is an outer tube outside the inner tube. The front ends of the inner and outer tubes are set on the rear end boss of the insulating spike. A side hole is provided in the front of the outer tube. A head is fixed between the inner and outer tubes and extends to the side hole. The nearby capillary tube is suitable for special injection and aspiration of cystic cancer. The gap between the water pipe and the coaxial cable forms a water inlet. The gap between the water pipe and the inner tube forms a water outlet. The circulating cooling water is used to cool the antenna. Provide efficient cooling.
上述微波消融天线采用同轴冷却水管的设计，这种设计虽然能够在一定程度上增加消融体积，但这种结构会极大占用同轴电缆空间，影响同轴电缆工作功率的提升。The above-mentioned microwave ablation antenna uses a coaxial cooling water pipe design. Although this design can increase the ablation volume to a certain extent, this structure will greatly occupy the coaxial cable space and affect the improvement of the coaxial cable working power.
CN 109602490A公开了一种支气管镜下用的微波消融电极，包括：金属穿刺头、针杆与同轴电缆，针杆为柔性针杆，柔性针杆具有内设空心夹层的双层结构，柔性针杆内壁与同轴电缆外壁之间形成进水道，空心夹层形成回水道，柔性针杆前端的内壁开孔或开槽，使进水道和回水道在该处连通，天线发射窗口后方的针杆的内壁或外壁独有金属或设置金属网。其省去了传统水冷消融针的内水管结构，改由双层的柔性针杆实现水冷，其结构更为紧凑，但仍然存在占用同轴电缆空间的缺陷。CN 109602490A discloses a microwave ablation electrode for bronchoscopy, including: a metal puncture head, a needle bar and a coaxial cable. The needle bar is a flexible needle bar. The flexible needle bar has a double-layer structure with a hollow sandwich inside. The flexible needle A water inlet channel is formed between the inner wall of the rod and the outer wall of the coaxial cable, and the hollow interlayer forms a water return channel. The inner wall of the front end of the flexible needle bar is holed or slotted so that the water inlet channel and the return water channel are connected there. The needle bar behind the antenna launch window is The inner or outer wall is made of metal or has a metal mesh. It eliminates the internal water pipe structure of the traditional water-cooled ablation needle and uses a double-layer flexible needle rod to achieve water cooling. The structure is more compact, but it still has the disadvantage of occupying the space of the coaxial cable.
因此，为了提高能量消融的治疗效果，方便术中对消融体积的预测并保证消融装置的紧凑性，需要提供一种结构简单可靠的冷热结合消融装置。Therefore, in order to improve the therapeutic effect of energy ablation, facilitate the prediction of ablation volume during surgery, and ensure the compactness of the ablation device, it is necessary to provide a simple and reliable combined hot and cold ablation device.
发明内容Contents of the invention
本发明的目的在于提供一种冷热结合消融装置，依靠冷冻与微波的方式对肿瘤进行靶向治疗，所述冷热结合消融装置根据焦耳-汤姆逊效应，采用节流膨胀降温的方式替代传统水冷结构，无需常规引水管的设置，提高了冷热结合消融装置的结构紧凑性；在此基础上，还能够进一步提高同轴电缆的直径，有利于提高微波消融的功率，进而提高治疗效果；且通过降温形成冰球，便于通过外部设备观察降温区域是否完全覆盖肿瘤，同时降温还能够强化微波消融的效果。The object of the present invention is to provide a combined hot and cold ablation device that relies on freezing and microwaves for targeted treatment of tumors. The combined cold and hot ablation device uses throttling, expansion and cooling to replace traditional methods based on the Joule-Thomson effect. The water-cooling structure does not require the installation of conventional water pipes, which improves the structural compactness of the combined hot and cold ablation device. On this basis, the diameter of the coaxial cable can be further increased, which is beneficial to increasing the power of microwave ablation, thereby improving the treatment effect; And by forming an ice ball through cooling, it is convenient to observe whether the cooling area completely covers the tumor through external equipment. At the same time, cooling can also enhance the effect of microwave ablation.
为达到此发明目的，本发明采用以下技术方案：In order to achieve the purpose of this invention, the present invention adopts the following technical solutions:
本发明提供了一种冷热结合消融装置，所述冷热结合消融装置包括依次连接的穿刺头、消融导管与手柄组件；The invention provides a combined hot and cold ablation device, which includes a puncture head, an ablation catheter and a handle assembly connected in sequence;
所述消融导管包括外管以及外管内设置的同轴电缆；The ablation catheter includes an outer tube and a coaxial cable provided in the outer tube;
所述同轴电缆包括内芯以及套设于内芯的屏蔽层，所述屏蔽层由手柄组件控制沿内芯的轴向位移，内芯的远端设置于穿刺头内；The coaxial cable includes an inner core and a shielding layer sleeved on the inner core. The axial displacement of the shielding layer along the inner core is controlled by the handle assembly, and the distal end of the inner core is arranged in the puncture head;
所述内芯的轴向设置有压缩气体通路，压缩气体通路的近端通过手柄组件与外部的压缩气体供给装置连接；A compressed gas passage is provided in the axial direction of the inner core, and the proximal end of the compressed gas passage is connected to an external compressed gas supply device through a handle assembly;
所述同轴电缆与外管之间的夹层形成气体回路。The interlayer between the coaxial cable and the outer tube forms a gas circuit.
本发明对传统的微波消融装置进行改进，为了减轻临床操作时微波消融装置对穿刺路径中的血管、神经及其它组织造成的伤害，需要控制微波消融装置中消融导管的直径，这就限制了同轴电缆的截面积尺寸。同轴电缆的内芯截面积尺寸直接影响着微波消融的功率，本发明取消了传统微波消融装置中的引水管结构，无须进水管与回水管的设计，提高了微波消融装置的结构紧凑性，能够进一步提高同轴电缆的直径，进而能够提高微波消融的功率，提高微波消融的效果。The present invention improves the traditional microwave ablation device. In order to reduce the damage caused by the microwave ablation device to blood vessels, nerves and other tissues in the puncture path during clinical operation, it is necessary to control the diameter of the ablation catheter in the microwave ablation device, which limits the same time. Cross-sectional area dimensions of the shaft cable. The size of the inner core cross-sectional area of the coaxial cable directly affects the power of microwave ablation. The present invention eliminates the water diversion pipe structure in the traditional microwave ablation device, eliminates the need for the design of water inlet pipes and return pipes, and improves the structural compactness of the microwave ablation device. The diameter of the coaxial cable can be further increased, thereby increasing the power of microwave ablation and improving the effect of microwave ablation.
另外，由于节流膨胀的降温效应，压缩气体由压缩气体通路的远端出口流出后温度下降，在气体回路回流的过程中，能够进一步降低由同轴电缆通入的压缩气体的温度，从而将压缩气体持续降温以形成冰球，冰球的体积持续增大，配合本领域常规的图像观测装置(例如CT检测、超声检测或X光检测)，能够清晰地对冰球范围进行观察，即实现本发明所述“可视化”，待冰球范围超过肿瘤范围后进行后续的微波消融。In addition, due to the cooling effect of throttling expansion, the temperature of the compressed gas drops after flowing out from the far end outlet of the compressed gas passage. During the gas loop return process, the temperature of the compressed gas introduced through the coaxial cable can be further reduced, thereby reducing the temperature of the compressed gas. The compressed gas continues to cool down to form an ice ball, and the volume of the ice ball continues to increase. With conventional image observation devices in this field (such as CT detection, ultrasonic detection, or X-ray detection), the range of the ice ball can be clearly observed, which is to achieve the goal of the present invention. As described above, follow-up microwave ablation is performed after the ice ball range exceeds the tumor range.
冷冻后的肿瘤组织更易吸收微波能量，本发明提供的冷热结合消融装置结合节流膨胀降温以及微波消融，能够达到良好的肿瘤消杀效果。Frozen tumor tissue is more likely to absorb microwave energy. The hot and cold ablation device provided by the present invention combines throttling, expansion, cooling and microwave ablation to achieve a good tumor disinfecting effect.
本发明中，压缩气体通路的近端与外部的压缩气体供给装置连接，本发明不对连接方式做进一步限定，只要能够使同轴电缆中的压缩气体通路与外部压缩气体供给装置连接即可。In the present invention, the proximal end of the compressed gas passage is connected to an external compressed gas supply device. The present invention does not further limit the connection method, as long as the compressed gas passage in the coaxial cable can be connected to the external compressed gas supply device.
而且，冰球的形成能够降低肿瘤组织的温度，降温后的组织对微波的吸收能力增强，即使不增加同轴电缆的尺寸，在保持原有功率不变的条件下，也能够实现微波消融范围的扩大，提高微波消融的效果。Moreover, the formation of ice balls can reduce the temperature of tumor tissue. The cooled tissue has an enhanced ability to absorb microwaves. Even without increasing the size of the coaxial cable, microwave ablation range can be achieved while maintaining the original power. Expand and improve the effect of microwave ablation.
将压缩气体通路设置于内芯的方式还能够进一步提高冷冻微波消融装置的结构稳定性，并能够通过控制压缩气体的温度实现对内芯温度的调控。The method of arranging the compressed gas passage in the inner core can further improve the structural stability of the cryo-microwave ablation device, and can control the temperature of the inner core by controlling the temperature of the compressed gas.
本发明所述气体回路可选的与本领域常规的负压发生装置连接，以提高回流效果，本发明不对负压发生装置的型号做进一步限定。气体回路与本领域常规负压发生装置的连接方法包括但不限于在手柄组件设置出气口，本发明对此不做具体限定，本领域技术人员可根据需要，在手柄组件处设置常规结构实现气体回路与负压发生装置的连接。The gas circuit of the present invention can optionally be connected to a conventional negative pressure generating device in the field to improve the backflow effect. The present invention does not further limit the model of the negative pressure generating device. The connection method between the gas circuit and the conventional negative pressure generating device in the field includes but is not limited to setting a gas outlet on the handle assembly. The present invention does not specifically limit this. Those skilled in the art can set a conventional structure on the handle assembly to realize gas flow as needed. The connection between the circuit and the negative pressure generating device.
优选地，所述内芯的远端裸露，裸露的最短长度为2-20mm，例如可以是2mm、5mm、6mm、8mm、10mm、12mm、15mm、16mm、18mm或20mm，但不限于所列举的数值，数值范围内其它未列举的数值同样适用。Preferably, the distal end of the inner core is exposed, and the shortest exposed length is 2-20mm, for example, it can be 2mm, 5mm, 6mm, 8mm, 10mm, 12mm, 15mm, 16mm, 18mm or 20mm, but is not limited to those listed Values, other unlisted values within the value range are also applicable.
本发明所述“最短长度”是指，屏蔽层在手柄组件控制下沿内芯的轴向位移，距离内芯的远端距离最近时，内芯远端裸露的长度。The "shortest length" mentioned in the present invention refers to the exposed length of the distal end of the inner core when the shielding layer is displaced along the axial direction of the inner core under the control of the handle assembly and is closest to the distal end of the inner core.
优选地，屏蔽层在距离内芯的远端距离最近时，屏蔽层的远端与穿刺头的近端重合。Preferably, when the shielding layer is closest to the distal end of the inner core, the distal end of the shielding layer coincides with the proximal end of the puncture head.
微波消融进行之前，需将屏蔽层在手柄组件控制下位移至距离内芯远端的最近处，此时内芯的裸露部分最少。压缩气体释放后所能冷却的内芯范围最小，由于压缩气体的流动形式，此时穿刺头处的制冷量最小，可对微波消融区域产生适当的冷却效果。Before microwave ablation is performed, the shielding layer needs to be moved to the closest position to the far end of the inner core under the control of the handle assembly. At this time, the exposed part of the inner core is the least. The range of the inner core that can be cooled after the compressed gas is released is the smallest. Due to the flow pattern of the compressed gas, the cooling capacity at the puncture head is the smallest at this time, which can produce an appropriate cooling effect on the microwave ablation area.
本发明中，屏蔽层在手柄组件的控制下，沿内芯的轴向位移，从而实现对内芯远端裸露面积的调控，进而实现了对冰球大小的调节。In the present invention, the shielding layer is displaced along the axial direction of the inner core under the control of the handle assembly, thereby realizing the control of the exposed area of the distal end of the inner core, thereby realizing the adjustment of the size of the ice puck.
优选地，所述消融导管的内径为1.4-1.6mm，例如可以是1.4mm、1.45mm、1.5mm、1.55mm或1.6mm，但不限于所列举的数值，数值范围内其它未列举的数值同样适用。Preferably, the inner diameter of the ablation catheter is 1.4-1.6mm, for example, it can be 1.4mm, 1.45mm, 1.5mm, 1.55mm or 1.6mm, but is not limited to the listed values. Other unlisted values within the numerical range are the same. Be applicable.
优选地，所述同轴电缆的外径为1.35-1.55mm，例如可以是1.35mm、1.4mm、1.45mm、1.5mm或1.55mm，但不限于所列举的数值，数值范围内其它未列举的数值同样适用。Preferably, the outer diameter of the coaxial cable is 1.35-1.55mm, for example, it can be 1.35mm, 1.4mm, 1.45mm, 1.5mm or 1.55mm, but is not limited to the listed values. Other values within the range are not listed. The same applies to numerical values.
优选地，所述内芯的外径为0.6-0.8mm，例如可以是0.6mm、0.65mm、0.7mm、0.75mm或0.8mm，但不限于所列举的数值，数值范围内其它未列举的数值同样适用。Preferably, the outer diameter of the inner core is 0.6-0.8mm, for example, it can be 0.6mm, 0.65mm, 0.7mm, 0.75mm or 0.8mm, but is not limited to the listed values, and other unlisted values within the value range The same applies.
优选地，所述压缩气体通路的内径为0.15-0.35mm，例如可以是0.15mm、0.2mm、0.25mm、0.3mm或0.35mm，但不限于所列举的数值，数值范围内其它未列举的数值同样适用。Preferably, the inner diameter of the compressed gas passage is 0.15-0.35mm, for example, it can be 0.15mm, 0.2mm, 0.25mm, 0.3mm or 0.35mm, but is not limited to the listed values, and other unlisted values within the value range The same applies.
本发明所述压缩气体通路的截面形状包括圆形或多边形，所述压缩气体通路的内径是指压缩气体通路的等效内经。压缩气体膨胀降温所需要的内径仅为0.15-0.35mm即可，能够减少压缩气体通路设置对微波消融功率的影响，保证了微波消融效果且提高了冷热结合消融装置的结构紧凑程度。The cross-sectional shape of the compressed gas passage in the present invention includes a circle or a polygon, and the inner diameter of the compressed gas passage refers to the equivalent inner diameter of the compressed gas passage. The inner diameter required for the expansion and cooling of compressed gas is only 0.15-0.35mm, which can reduce the impact of the compressed gas path setting on the microwave ablation power, ensure the microwave ablation effect and improve the compactness of the combined hot and cold ablation device.
优选地，所述压缩气体通路的远端螺旋设置。Preferably, the distal end of the compressed gas passage is spirally arranged.
本发明通过在压缩气体通路的远端进行螺旋设置，延长了压缩气体通路的长度，提高了压缩气体的进气散热面积。By arranging a spiral at the far end of the compressed gas passage, the present invention extends the length of the compressed gas passage and increases the air intake heat dissipation area of the compressed gas.
作为进一步优选的技术方案，压缩气体通路的远端螺旋段轴向长度与穿刺头内腔的轴向长度比值为(1.5-1.8):1，例如可以是1.5:1、1.6:1、1.7:1或1.8:1，但不限于所列举的数值，数值范围内其它未列举的数值同样适用。As a further preferred technical solution, the ratio of the axial length of the distal spiral section of the compressed gas passage to the axial length of the lumen of the puncture head is (1.5-1.8):1, for example, it can be 1.5:1, 1.6:1, or 1.7: 1 or 1.8:1, but is not limited to the listed values. Other unlisted values within the value range are also applicable.
通过控制远端螺旋段的长度，即能够保证微波消融的正常进行，又能够保证高功率下对同轴电缆的冷却效果。By controlling the length of the distal spiral segment, it is possible to ensure the normal progress of microwave ablation and to ensure the cooling effect of the coaxial cable under high power.
优选地，所述穿刺头的材质包括陶瓷或PTFE，优选为PTFE。Preferably, the puncture head is made of ceramic or PTFE, preferably PTFE.
本发明所述消融针头的材质优选为PTFE，PTFE微观结构对称，且具有耐高低温性能良好的性质。The material of the ablation needle of the present invention is preferably PTFE, which has a symmetrical microstructure and good high and low temperature resistance.
优选地，所述手柄组件包括手柄主体与手柄推杆；Preferably, the handle assembly includes a handle body and a handle push rod;
所述消融导管通过卡扣与手柄主体连接；所述手柄主体设置有控制手柄推杆位移的导槽；The ablation catheter is connected to the handle body through a buckle; the handle body is provided with a guide groove that controls the displacement of the handle push rod;
所述手柄推杆与同轴电缆的屏蔽层连接，控制屏蔽层沿内芯的轴向位移。The handle push rod is connected to the shielding layer of the coaxial cable to control the axial displacement of the shielding layer along the inner core.
示例性的，本发明所述冷热结合消融装置的消融方法包括如下步骤：Exemplarily, the ablation method of the combined hot and cold ablation device of the present invention includes the following steps:
(1)由压缩气体通路通入压缩气体进行降温，降温过程中控制内芯远端的裸露长度，形成直径满足要求的冰球；(1) The compressed gas is introduced through the compressed gas passage for cooling. During the cooling process, the exposed length of the far end of the inner core is controlled to form an ice ball with a diameter that meets the requirements;
(2)使内芯远端的裸露长度最短，然后同轴电缆接通射频连接器进行微波消融，微波消融过程中持续通入压缩气体进行冷却。(2) Keep the exposed length of the distal end of the inner core to the shortest, and then connect the coaxial cable to the RF connector for microwave ablation. During the microwave ablation process, compressed gas is continuously introduced for cooling.
应用本发明提供的冷热结合消融装置进行微波消融时，首先利用压缩气体进行降温，降温原理为焦耳-汤姆逊效应。压缩气体膨胀降温后，由气体回路回流，在回流过程中对同轴电缆内部的压缩气体进行换热降温，使同轴电缆的远端温度持续降低直至稳定，并在肿瘤组织处形成冰球，冰球的尺寸可通过压缩气体的压力以及温度进行调控。而且，冰球的尺寸可配合本领域常规的图像观测装置进行观察，从而实现“可视化”的效果，待冰球范围超过肿瘤范围后进行后续的微波消融。When using the hot and cold combined ablation device provided by the present invention to perform microwave ablation, compressed gas is first used for cooling, and the cooling principle is the Joule-Thomson effect. After the compressed gas expands and cools down, it flows back through the gas loop. During the backflow process, the compressed gas inside the coaxial cable is exchanged and cooled, so that the temperature at the distal end of the coaxial cable continues to decrease until it is stable, and an ice ball is formed at the tumor tissue. The size can be controlled by the pressure and temperature of the compressed gas. Moreover, the size of the ice ball can be observed with conventional image observation devices in this field, thereby achieving a "visualization" effect. After the ice ball range exceeds the tumor range, subsequent microwave ablation can be performed.
由于肺部组织始终处于通气与换气的过程中，容易造成肺组织与微波消融装置的相对位移，本发明提供的冷冻强化微波可视化消融装置产生冰球后，可以利用冰球相对固定冷热结合消融装置与肿瘤组织的位置。而且，冷冻后的组织对微波的吸收能力增强，有利于后续微波消融的进行。Since the lung tissue is always in the process of ventilation and ventilation, it is easy to cause relative displacement between the lung tissue and the microwave ablation device. After the freeze-enhanced microwave visualization ablation device provided by the present invention generates ice balls, the ice balls can be used to relatively fix the hot and cold combined ablation device. and the location of tumor tissue. Moreover, the frozen tissue's ability to absorb microwaves is enhanced, which is beneficial to subsequent microwave ablation.
优选地，步骤(1)所述压缩气体的通入压力为5-20MPa，例如可以是5MPa、8MPa、10MPa、12MPa、15MPa、16MPa、18MPa或20MPa，但不限于所列举的数值，数值范围内其它未列举的数值同样适用。Preferably, the inlet pressure of the compressed gas in step (1) is 5-20MPa, for example, it can be 5MPa, 8MPa, 10MPa, 12MPa, 15MPa, 16MPa, 18MPa or 20MPa, but is not limited to the listed values, within the range of values Other values not listed are also applicable.
优选地，步骤(1)所述压缩气体的温度为0-20℃，例如可以是0℃、5℃、10℃、15℃或20℃，但不限于所列举的数值，数值范围内其它未列举的数值同样适用。Preferably, the temperature of the compressed gas in step (1) is 0-20°C, for example, it can be 0°C, 5°C, 10°C, 15°C or 20°C, but is not limited to the listed values. Other values are not within the range of the values. The same applies to the listed values.
优选地，步骤(2)所述微波消融的功率为10-150W，例如可以是10W、20W、30W、40W、50W、60W、70W、80W、90W、100W、110W、120W、130W、140W或150W，但不限于所列举的数值，数值范围内其它未列举的数值同样适用。Preferably, the power of microwave ablation in step (2) is 10-150W, for example, it can be 10W, 20W, 30W, 40W, 50W, 60W, 70W, 80W, 90W, 100W, 110W, 120W, 130W, 140W or 150W. , but are not limited to the listed values, other unlisted values within the numerical range are also applicable.
本发明提供的冷热结合消融装置的结构紧凑，由于取消了传统微波消融装置中的引水管结构，无须进水管与回水管的设计，能够进一步提高同轴电缆的直径，进而能够提高微波消融的功率，使微波消融的功率能够达到150W，提高了微波消融的效果。The combined hot and cold ablation device provided by the present invention has a compact structure. Since the water pipe structure in the traditional microwave ablation device is eliminated, the design of the water inlet pipe and the return pipe is not required, and the diameter of the coaxial cable can be further increased, thereby improving the efficiency of microwave ablation. Power, the power of microwave ablation can reach 150W, which improves the effect of microwave ablation.
相对于现有技术，本发明具有以下有益效果：Compared with the existing technology, the present invention has the following beneficial effects:
(1)本发明取消了传统微波消融装置中的引水管结构，无须进水管与回水管的设计，提高了微波消融装置的结构紧凑性，能够进一步提高同轴电缆的直径，进而能够提高微波消融的功率，提高微波消融的效果；(1) The present invention eliminates the water diversion pipe structure in the traditional microwave ablation device and eliminates the need for the design of water inlet and return pipes. It improves the structural compactness of the microwave ablation device, can further increase the diameter of the coaxial cable, and thereby improves the efficiency of microwave ablation. power to improve the effect of microwave ablation;
(2)本发明提供的冷热结合消融装置能够配合配合本领域常规的图像观测装置，能够清晰地对冰球范围进行观察，待冰球范围超过肿瘤范围后进行后续的微波消融，降低了操作难度；(2) The combined hot and cold ablation device provided by the present invention can cooperate with conventional image observation devices in this field, and can clearly observe the ice ball range. After the ice ball range exceeds the tumor range, subsequent microwave ablation is performed, which reduces the difficulty of operation;
(3)冰球的形成能够降低肿瘤组织的温度，降温后的组织对微波的吸收能力增强，即使不增加同轴电缆的尺寸，在保持原有功率不变的条件下，也能够实现微波消融范围的扩大，提高了微波消融的效果。(3) The formation of ice balls can reduce the temperature of tumor tissue. The cooled tissue has an enhanced ability to absorb microwaves. Even without increasing the size of the coaxial cable, the microwave ablation range can be achieved while maintaining the original power. The expansion improves the effect of microwave ablation.
附图说明Description of drawings
图1为本发明提供的冷热结合消融装置的结构示意图；Figure 1 is a schematic structural diagram of a combined hot and cold ablation device provided by the present invention;
图2为本发明提供的冷热结合消融装置的爆炸图；Figure 2 is an exploded view of the hot and cold combined ablation device provided by the present invention;
图3为本发明提供的冷热结合消融装置中压缩气体流动示意图；Figure 3 is a schematic diagram of the flow of compressed gas in the hot and cold combined ablation device provided by the present invention;
图4为实施例4提供的冷热结合消融装置中压缩气体通路远端的示意图。Figure 4 is a schematic diagram of the distal end of the compressed gas passage in the combined hot and cold ablation device provided in Embodiment 4.
其中：1，穿刺头；2，消融导管；3，手柄组件；31，手柄主体；32，手柄推杆；33，导槽；4，卡扣；51，内芯；52，屏蔽层。Among them: 1, puncture head; 2, ablation catheter; 3, handle assembly; 31, handle body; 32, handle push rod; 33, guide groove; 4, buckle; 51, inner core; 52, shielding layer.
具体实施方式Detailed ways
下面通过具体实施方式来进一步说明本发明的技术方案。本领域技术人员应该明了，所述实施例仅仅是帮助理解本发明，不应视为对本发明的具体限制。The technical solution of the present invention will be further described below through specific implementations. Those skilled in the art should understand that the embodiments are only to help understand the present invention and should not be regarded as specific limitations of the present invention.
实施例1Example 1
本实施例提供了一种如图1所示的冷热结合消融装置，爆炸图如图2所示，包括依次连接的穿刺头1、消融导管2与手柄组件3。This embodiment provides a combined hot and cold ablation device as shown in Figure 1. The exploded view is shown in Figure 2, including a puncture head 1, an ablation catheter 2 and a handle assembly 3 connected in sequence.
所述消融导管2包括外管以及外管内设置的同轴电缆；The ablation catheter 2 includes an outer tube and a coaxial cable provided in the outer tube;
所述同轴电缆包括内芯51以及套设于内芯51的屏蔽层52，所述屏蔽层52由手柄组件3控制沿内芯51的轴向位移，内芯51的远端设置于穿刺头1内；The coaxial cable includes an inner core 51 and a shielding layer 52 sheathed on the inner core 51. The axial displacement of the shielding layer 52 along the inner core 51 is controlled by the handle assembly 3. The distal end of the inner core 51 is arranged on the puncture head. within 1;
所述内芯51的轴向设置有压缩气体通路，压缩气体通路的近端通过手柄组件3与外部的压缩气体供给装置连接；The inner core 51 is provided with a compressed gas passage in the axial direction, and the proximal end of the compressed gas passage is connected to an external compressed gas supply device through the handle assembly 3;
所述同轴电缆与外管之间的夹层形成气体回路(参见图3)。The interlayer between the coaxial cable and the outer tube forms a gas circuit (see Figure 3).
所述内芯51的远端裸露，裸露的最短长度为2mm。The distal end of the inner core 51 is exposed, and the shortest exposed length is 2 mm.
所述消融导管2的内径为1.4mm，所述同轴电缆的外径为1.35mm，所述内芯51的外径为0.6mm，压缩气体通路的内径为0.15mm。The inner diameter of the ablation catheter 2 is 1.4mm, the outer diameter of the coaxial cable is 1.35mm, the outer diameter of the inner core 51 is 0.6mm, and the inner diameter of the compressed gas passage is 0.15mm.
所述穿刺头1的材质为PTFE。The puncture head 1 is made of PTFE.
所述手柄组件3包括手柄主体31与手柄推杆32，消融导管2通过卡扣4与手柄主体31连接；所述手柄主体31设置有控制手柄推杆32位移的导槽33；所述手柄推杆32与同轴电缆的屏蔽层52连接，控制屏蔽层52沿内芯51的轴向位移。The handle assembly 3 includes a handle main body 31 and a handle push rod 32. The ablation catheter 2 is connected to the handle main body 31 through a buckle 4; the handle main body 31 is provided with a guide groove 33 for controlling the displacement of the handle push rod 32; The rod 32 is connected to the shielding layer 52 of the coaxial cable to control the axial displacement of the shielding layer 52 along the inner core 51 .
应用本实施例提供的冷热结合消融装置进行微波消融时，首先利用压缩气体进行降温，降温原理为焦耳-汤姆逊效应。压缩气体膨胀降温后，由气体回路回流，在回流过程中对同轴电缆内部的压缩气体进行换热降温，使同轴电缆的远端温度持续降低直至稳定，并在肿瘤组织处形成冰球，冰球的尺寸可通过压缩气体的压力以及温度进行调控。冷冻后的组织对微波的吸收能力增强，有利于后续微波消融的进行。When using the combined hot and cold ablation device provided in this embodiment to perform microwave ablation, compressed gas is first used to cool down, and the cooling principle is the Joule-Thomson effect. After the compressed gas expands and cools down, it flows back through the gas loop. During the backflow process, the compressed gas inside the coaxial cable is exchanged and cooled, so that the temperature at the distal end of the coaxial cable continues to decrease until it is stable, and an ice ball is formed at the tumor tissue. The size can be controlled by the pressure and temperature of the compressed gas. The frozen tissue has an enhanced ability to absorb microwaves, which is beneficial to subsequent microwave ablation.
应用本实施例提供的冷热结合消融装置进行的消融方法包括如下步骤：The ablation method using the hot and cold combined ablation device provided in this embodiment includes the following steps:
(1)由压缩气体通路通入0-20℃的压缩气体进行降温，降温过程中控制内芯51远端的裸露长度，形成直径满足要求的冰球(参见图5)；所述压缩气体为氩气，通入压力为5-20MPa；(1) The compressed gas of 0-20°C is passed through the compressed gas passage to cool down. During the cooling process, the exposed length of the far end of the inner core 51 is controlled to form an ice ball with a diameter that meets the requirements (see Figure 5); the compressed gas is argon Gas, the inlet pressure is 5-20MPa;
(2)使内芯51远端的裸露长度最短，然后同轴电缆接通射频连接器进行微波消融，微波消融过程中持续通入压缩气体进行冷却，本应用例中微波消融的功率最高可达120W。(2) Make the exposed length of the far end of the inner core 51 the shortest, and then connect the coaxial cable to the radio frequency connector to perform microwave ablation. During the microwave ablation process, compressed gas is continuously introduced for cooling. In this application example, the power of the microwave ablation is up to 120W.
实施例2Example 2
本实施例提供了一种如图1所示的冷热结合消融装置，爆炸图如图2所示，包括依次连接的穿刺头1、消融导管2与手柄组件3。This embodiment provides a combined hot and cold ablation device as shown in Figure 1. The exploded view is shown in Figure 2, including a puncture head 1, an ablation catheter 2 and a handle assembly 3 connected in sequence.
所述消融导管2包括外管以及外管内设置的同轴电缆；The ablation catheter 2 includes an outer tube and a coaxial cable provided in the outer tube;
所述同轴电缆包括内芯51以及套设于内芯51的屏蔽层52，所述屏蔽层52由手柄组件3控制沿内芯51的轴向位移，内芯51的远端设置于穿刺头1内；The coaxial cable includes an inner core 51 and a shielding layer 52 sheathed on the inner core 51. The axial displacement of the shielding layer 52 along the inner core 51 is controlled by the handle assembly 3. The distal end of the inner core 51 is arranged on the puncture head. within 1;
所述内芯51的轴向设置有压缩气体通路，压缩气体通路的近端通过手柄组件3与外部的压缩气体供给装置连接；The inner core 51 is provided with a compressed gas passage in the axial direction, and the proximal end of the compressed gas passage is connected to an external compressed gas supply device through the handle assembly 3;
所述同轴电缆与外管之间的夹层形成气体回路(参见图3)。The interlayer between the coaxial cable and the outer tube forms a gas circuit (see Figure 3).
所述内芯51的远端裸露，裸露的最短长度为10mm。The distal end of the inner core 51 is exposed, and the shortest exposed length is 10 mm.
所述消融导管2的内径为1.5mm，所述同轴电缆的外径为1.45mm，所述内芯51的外径为0.7mm，压缩气体通路的内径为0.25mm。The inner diameter of the ablation catheter 2 is 1.5mm, the outer diameter of the coaxial cable is 1.45mm, the outer diameter of the inner core 51 is 0.7mm, and the inner diameter of the compressed gas passage is 0.25mm.
所述穿刺头1的材质为PTFE。The puncture head 1 is made of PTFE.
所述手柄组件3包括手柄主体31与手柄推杆32，消融导管2通过卡扣4与手柄主体31连接；所述手柄主体31设置有控制手柄推杆32位移的导槽33；所述手柄推杆32与同轴电缆的屏蔽层52连接，控制屏蔽层52沿内芯51的轴向位移。The handle assembly 3 includes a handle main body 31 and a handle push rod 32. The ablation catheter 2 is connected to the handle main body 31 through a buckle 4; the handle main body 31 is provided with a guide groove 33 for controlling the displacement of the handle push rod 32; The rod 32 is connected to the shielding layer 52 of the coaxial cable to control the axial displacement of the shielding layer 52 along the inner core 51 .
应用本实施例提供的冷热结合消融装置进行微波消融时，首先利用压缩气体进行降温，降温原理为焦耳-汤姆逊效应。压缩气体膨胀降温后，由气体回路回流，在回流过程中对同轴电缆内部的压缩气体进行换热降温，使同轴电缆的远端温度持续降低直至稳定，并在肿瘤组织处形成冰球，冰球的尺寸可通过压缩气体的压力以及温度进行调控。冷冻后的组织对微波的吸收能力增强，有利于后续微波消融的进行。When using the combined hot and cold ablation device provided in this embodiment to perform microwave ablation, compressed gas is first used to cool down, and the cooling principle is the Joule-Thomson effect. After the compressed gas expands and cools down, it flows back through the gas loop. During the backflow process, the compressed gas inside the coaxial cable is exchanged and cooled, so that the temperature at the distal end of the coaxial cable continues to decrease until it is stable, and an ice ball is formed at the tumor tissue. The size can be controlled by the pressure and temperature of the compressed gas. The frozen tissue has an enhanced ability to absorb microwaves, which is beneficial to subsequent microwave ablation.
应用本实施例提供的冷热结合消融装置进行的消融方法包括如下步骤：The ablation method using the hot and cold combined ablation device provided in this embodiment includes the following steps:
(1)由压缩气体通路通入0-20℃的压缩气体进行降温，降温过程中控制内芯51远端的裸露长度，形成直径满足要求的冰球；所述压缩气体为氩气，通入压力为5-20MPa；(1) The compressed gas of 0-20°C is introduced through the compressed gas passage for cooling. During the cooling process, the exposed length of the far end of the inner core 51 is controlled to form an ice ball with a diameter that meets the requirements; the compressed gas is argon gas, and the pressure is introduced is 5-20MPa;
(2)使内芯51远端的裸露长度最短，然后同轴电缆接通射频连接器进行微波消融，微波消融过程中持续通入压缩气体进行冷却，本应用例中微波消融的功率最高可达137W。(2) Make the exposed length of the far end of the inner core 51 the shortest, and then connect the coaxial cable to the radio frequency connector to perform microwave ablation. During the microwave ablation process, compressed gas is continuously introduced for cooling. In this application example, the power of the microwave ablation is up to 137W.
实施例3Example 3
本实施例提供了一种如图1所示的冷热结合消融装置，爆炸图如图2所示，包括依次连接的穿刺头1、消融导管2与手柄组件3。This embodiment provides a combined hot and cold ablation device as shown in Figure 1. The exploded view is shown in Figure 2, including a puncture head 1, an ablation catheter 2 and a handle assembly 3 connected in sequence.
所述消融导管2包括外管以及外管内设置的同轴电缆；The ablation catheter 2 includes an outer tube and a coaxial cable provided in the outer tube;
所述同轴电缆包括内芯51以及套设于内芯51的屏蔽层52，所述屏蔽层52由手柄组件3控制沿内芯51的轴向位移，内芯51的远端设置于穿刺头1内；The coaxial cable includes an inner core 51 and a shielding layer 52 sheathed on the inner core 51. The axial displacement of the shielding layer 52 along the inner core 51 is controlled by the handle assembly 3. The distal end of the inner core 51 is arranged on the puncture head. within 1;
所述内芯51的轴向设置有压缩气体通路，压缩气体通路的近端通过手柄组件3与外部的压缩气体供给装置连接；The inner core 51 is provided with a compressed gas passage in the axial direction, and the proximal end of the compressed gas passage is connected to an external compressed gas supply device through the handle assembly 3;
所述同轴电缆与消融导管2之间的夹层形成气体回路(参见图3)。The interlayer between the coaxial cable and the ablation catheter 2 forms a gas circuit (see Figure 3).
所述内芯51的远端裸露，裸露的最短长度为20mm。The distal end of the inner core 51 is exposed, and the shortest exposed length is 20 mm.
所述消融导管2的内径为1.6mm，所述同轴电缆的外径为1.55mm，所述内芯51的外径为0.8mm，压缩气体通路的内径为0.35mm。The inner diameter of the ablation catheter 2 is 1.6 mm, the outer diameter of the coaxial cable is 1.55 mm, the outer diameter of the inner core 51 is 0.8 mm, and the inner diameter of the compressed gas passage is 0.35 mm.
所述穿刺头1的材质为PTFE。The puncture head 1 is made of PTFE.
所述手柄组件3包括手柄主体31与手柄推杆32，消融导管2通过卡扣4与手柄主体31连接；所述手柄主体31设置有控制手柄推杆32位移的导槽33；所述手柄推杆32与同轴电缆的屏蔽层52连接，控制屏蔽层52沿内芯51的轴向位移。The handle assembly 3 includes a handle main body 31 and a handle push rod 32. The ablation catheter 2 is connected to the handle main body 31 through a buckle 4; the handle main body 31 is provided with a guide groove 33 for controlling the displacement of the handle push rod 32; The rod 32 is connected to the shielding layer 52 of the coaxial cable to control the axial displacement of the shielding layer 52 along the inner core 51 .
应用本实施例提供的冷热结合消融装置进行微波消融时，首先利用压缩气体进行降温，降温原理为焦耳-汤姆逊效应。压缩气体膨胀降温后，由气体回路回流，在回流过程中对同轴电缆内部的压缩气体进行换热降温，使同轴电缆的远端温度持续降低直至稳定，并在肿瘤组织处形成冰球，冰球的尺寸可通过压缩气体的压力以及温度进行调控。冷冻后的组织对微波的吸收能力增强，有利于后续微波消融的进行。When using the combined hot and cold ablation device provided in this embodiment to perform microwave ablation, compressed gas is first used to cool down, and the cooling principle is the Joule-Thomson effect. After the compressed gas expands and cools down, it flows back through the gas loop. During the backflow process, the compressed gas inside the coaxial cable is exchanged and cooled, so that the temperature at the distal end of the coaxial cable continues to decrease until it is stable, and an ice ball is formed at the tumor tissue. The size can be controlled by the pressure and temperature of the compressed gas. The frozen tissue has an enhanced ability to absorb microwaves, which is beneficial to subsequent microwave ablation.
应用本实施例提供的冷热结合消融装置进行的消融方法包括如下步骤：The ablation method using the hot and cold combined ablation device provided in this embodiment includes the following steps:
(1)由压缩气体通路通入0-20℃的压缩气体进行降温，降温过程中控制内芯51远端的裸露长度，形成直径满足要求的冰球；所述压缩气体为氩气，通入压力为5-20MPa；(1) The compressed gas of 0-20°C is introduced through the compressed gas passage for cooling. During the cooling process, the exposed length of the far end of the inner core 51 is controlled to form an ice ball with a diameter that meets the requirements; the compressed gas is argon gas, and the pressure is introduced is 5-20MPa;
(2)使内芯51远端的裸露长度最短，然后同轴电缆接通射频连接器进行微波消融，微波消融过程中持续通入压缩气体进行冷却，本应用例中微波消融的功率最高可达146W。(2) Make the exposed length of the far end of the inner core 51 the shortest, and then connect the coaxial cable to the radio frequency connector to perform microwave ablation. During the microwave ablation process, compressed gas is continuously introduced for cooling. In this application example, the power of the microwave ablation is up to 146W.
实施例4Example 4
本实施例提供了一种如图1所示的冷热结合消融装置，爆炸图如图2所示，包括依次连接的穿刺头1、消融导管2与手柄组件3。This embodiment provides a combined hot and cold ablation device as shown in Figure 1. The exploded view is shown in Figure 2, including a puncture head 1, an ablation catheter 2 and a handle assembly 3 connected in sequence.
所述消融导管2包括外管以及外管内设置的同轴电缆；The ablation catheter 2 includes an outer tube and a coaxial cable provided in the outer tube;
所述同轴电缆包括内芯51以及套设于内芯51的屏蔽层52，所述屏蔽层52由手柄组件3控制沿内芯51的轴向位移，内芯51的远端设置于穿刺头1内；The coaxial cable includes an inner core 51 and a shielding layer 52 sheathed on the inner core 51. The axial displacement of the shielding layer 52 along the inner core 51 is controlled by the handle assembly 3. The distal end of the inner core 51 is arranged on the puncture head. within 1;
所述内芯51的轴向设置有压缩气体通路，压缩气体通路的近端通过手柄组件3与外部的压缩气体供给装置连接；The inner core 51 is provided with a compressed gas passage in the axial direction, and the proximal end of the compressed gas passage is connected to an external compressed gas supply device through the handle assembly 3;
所述同轴电缆与消融导管2之间的夹层形成气体回路(参见图3)。The interlayer between the coaxial cable and the ablation catheter 2 forms a gas circuit (see Figure 3).
所述内芯51的远端裸露，裸露的最短长度为18mm。The distal end of the inner core 51 is exposed, and the shortest exposed length is 18 mm.
所述消融导管2的内径为1.5mm，所述同轴电缆的外径为1.45mm，所述内芯51的外径为0.7mm，压缩气体通路的内径为0.25mm；所述压缩气体通路的远端螺旋设置(参见图4)，远端螺旋段轴向长度与穿刺头1的内腔轴向长度比值为1.6:1。The inner diameter of the ablation catheter 2 is 1.5mm, the outer diameter of the coaxial cable is 1.45mm, the outer diameter of the inner core 51 is 0.7mm, and the inner diameter of the compressed gas passage is 0.25mm; The distal spiral is set (see Figure 4), and the ratio of the axial length of the distal spiral segment to the axial length of the lumen of the puncture head 1 is 1.6:1.
所述穿刺头1的材质为PTFE。The puncture head 1 is made of PTFE.
所述手柄组件3包括手柄主体31与手柄推杆32，消融导管2通过卡扣4与手柄主体31连接；所述手柄主体31设置有控制手柄推杆32位移的导槽33；所述手柄推杆32与同轴电缆的屏蔽层52连接，控制屏蔽层52沿内芯51的轴向位移。The handle assembly 3 includes a handle main body 31 and a handle push rod 32. The ablation catheter 2 is connected to the handle main body 31 through a buckle 4; the handle main body 31 is provided with a guide groove 33 for controlling the displacement of the handle push rod 32; The rod 32 is connected to the shielding layer 52 of the coaxial cable to control the axial displacement of the shielding layer 52 along the inner core 51 .
与实施例1-3相比，本实施例通过使压缩气体通路的远端螺旋设置，延长了压缩气体通路的长度，提高了压缩气体的进气散热面积。Compared with Embodiments 1-3, in this embodiment, the distal end of the compressed gas passage is spirally arranged, thereby extending the length of the compressed gas passage and increasing the air intake heat dissipation area of the compressed gas.
应用本实施例提供的冷热结合消融装置进行的消融方法包括如下步骤：The ablation method using the hot and cold combined ablation device provided in this embodiment includes the following steps:
(1)由压缩气体通路通入0-20℃的压缩气体进行降温，降温过程中控制内芯51远端的裸露长度，形成直径满足要求的冰球；所述压缩气体为氩气，通入压力为5-20MPa；(1) The compressed gas of 0-20°C is introduced through the compressed gas passage for cooling. During the cooling process, the exposed length of the far end of the inner core 51 is controlled to form an ice ball with a diameter that meets the requirements; the compressed gas is argon gas, and the pressure is introduced is 5-20MPa;
(2)使内芯51远端的裸露长度最短，然后同轴电缆接通射频连接器进行微波消融，微波消融过程中持续通入压缩气体进行冷却，本应用例中微波消融的功率最高可达146W。(2) Make the exposed length of the far end of the inner core 51 the shortest, and then connect the coaxial cable to the radio frequency connector to perform microwave ablation. During the microwave ablation process, compressed gas is continuously introduced for cooling. In this application example, the power of the microwave ablation is up to 146W.
实施例5Example 5
本实施例提供了一种冷热结合消融装置，与实施例4相比，除远端螺旋段轴向长度与穿刺头1的内腔轴向长度比值为1.5:1外，其余均与实施例4相同。This embodiment provides a combined hot and cold ablation device. Compared with Embodiment 4, except that the ratio of the axial length of the distal spiral segment to the axial length of the inner cavity of the puncture head 1 is 1.5:1, the rest are the same as those in Embodiment 4. 4 is the same.
应用本实施例提供的冷热结合消融装置进行微波消融时，微波消融的功率最高可达142W。When using the hot and cold combined ablation device provided in this embodiment to perform microwave ablation, the microwave ablation power can reach up to 142W.
实施例6Example 6
本实施例提供了一种冷热结合消融装置，与实施例4相比，除远端螺旋段轴向长度与穿刺头1的内腔轴向长度比值为1.8:1外，其余均与实施例4相同。This embodiment provides a combined hot and cold ablation device. Compared with Embodiment 4, except that the ratio of the axial length of the distal spiral segment to the axial length of the inner cavity of the puncture head 1 is 1.8:1, the rest are the same as those in Embodiment 4. 4 is the same.
应用本实施例提供的冷热结合消融装置进行微波消融时，微波消融的功率最高可达150W。When using the combined hot and cold ablation device provided in this embodiment to perform microwave ablation, the microwave ablation power can reach up to 150W.
综上所述，本发明取消了传统微波消融装置中的引水管结构，无须进水管与回水管的设计，提高了装置的结构紧凑性，能够进一步提高同轴电缆的直径，进而能够提高微波消融的功率，提高微波消融的效果；本发明提供的冷热结合消融装置能够配合配合本领域常规的图像观测装置，能够清晰地对冰球范围进行观察，待冰球范围超过肿瘤范围后进行后续的微波消融，降低了操作难度；冰球的形成能够降低肿瘤组织的温度，降温后的组织对微波的吸收能力增强，即使不增加同轴电缆的尺寸，在保持原有功率不变的条件下，也能够实现微波消融范围的扩大，提高了微波消融的效果。To sum up, the present invention eliminates the water diversion pipe structure in the traditional microwave ablation device and does not require the design of the water inlet pipe and the return pipe. It improves the structural compactness of the device and can further increase the diameter of the coaxial cable, thereby improving the efficiency of microwave ablation. power to improve the effect of microwave ablation; the hot and cold combined ablation device provided by the present invention can cooperate with conventional image observation devices in this field, and can clearly observe the ice ball range, and perform subsequent microwave ablation after the ice ball range exceeds the tumor range. , reducing the difficulty of operation; the formation of the ice ball can reduce the temperature of the tumor tissue, and the tissue's ability to absorb microwaves after cooling is enhanced. Even without increasing the size of the coaxial cable, it can be achieved while maintaining the original power. The expansion of microwave ablation range has improved the effect of microwave ablation.
以上所述仅为本发明的具体实施方式，但本发明的保护范围并不局限于此，所属技术领域的技术人员应该明了，任何属于本技术领域的技术人员在本发明揭露的技术范围内，可轻易想到的变化或替换，均落在本发明的保护范围和公开范围之内。The above are only specific embodiments of the present invention, but the protection scope of the present invention is not limited thereto. Those skilled in the technical field should understand that any person skilled in the technical field, within the technical scope disclosed in the present invention, Changes or substitutions that can be easily imagined fall within the protection scope and disclosure scope of the present invention.
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202210644917.XACN117224221A (en) | 2022-06-08 | 2022-06-08 | Cold and hot combination ablation device |
| Application Number | Priority Date | Filing Date | Title |
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| CN202210644917.XACN117224221A (en) | 2022-06-08 | 2022-06-08 | Cold and hot combination ablation device |
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| CN117224221Atrue CN117224221A (en) | 2023-12-15 |
| Application Number | Title | Priority Date | Filing Date |
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| CN202210644917.XAPendingCN117224221A (en) | 2022-06-08 | 2022-06-08 | Cold and hot combination ablation device |
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