Tumor treatment system using microwaves

Abstract

The present invention relates to a tumor treatment system comprising a microwave transfer antenna capable of precisely controlling the ablation temperature and range of tumors and a power transfer unit for supplying microwaves of a specific waveform, thereby minimizing metastasis due to tumor loss and recurrence due to unremoved tumors. The tumor treatment system has temperature sensors or impedance sensors installed on the surface of antennas such that the temperature and impedance change of a target tissue are directly measured, thereby adjusting the ablation temperature and speed, and changes in the target tissue can thus be directly identified, and the amount of microwaves and cooling water can be accurately adjusted.

Description

Microwave-based tumor treatment system

[0001] The present invention relates to a tumor treatment system using microwaves, and more specifically, to a tumor treatment system comprising a microwave transmission antenna capable of precisely controlling the cauterization temperature and range of a tumor, and a power transmission unit supplying microwaves of a specific waveform, thereby minimizing metastasis caused by tumor loss and recurrence caused by unremoved tumors.

[0002] In the case of conventional resection surgery, a part of the body must be excised to reach the affected area, which consequently requires a significant recovery time. In particular, if the resection site is located deep within the body or inside organs such as the liver, the recovery time may be even longer because non-treatable skin, muscle, or organs must be excised to reach the target tissue.

[0003] Therefore, to overcome these drawbacks, a technique is being used in which an antenna is inserted into the target tissue and then destroyed using energy delivered from the antenna. Particularly in the case of liver cancer, a common disease among Koreans, the use of thermal ablation is expanding because the cancer is located deep within the body and, due to the characteristics of liver tissue, resection can cause massive bleeding.

[0004] The thermal ablation used in this case refers to destroying target tissue by increasing the cell temperature above an irreversible damage threshold. This threshold is related to the exposure time at a given temperature; in the case of temperatures ranging from 50°C to 60°C, the time is a few minutes, whereas at temperatures above 60°C, cells die almost instantly. In fact, the temperature increase is achieved by delivering energy into the target tissue using invasive applicators. The forms of energy typically used for thermal ablation may include radio frequency and microwaves.

[0005] Among these methods, radiofrequency thermal ablation requires a significant amount of time to heat the target tissue, leading to a heat sink effect caused by blood flow. Furthermore, it is known that non-uniform heating occurs depending on the electrical conductivity of the tissue. Consequently, conventional radiofrequency thermal ablation frequently results in non-uniform tissue cauterization, posing a risk of residual tumors and subsequent recurrence due to this uneven treatment.

[0006] Therefore, the use of microwave cauterization methods is increasing to overcome the disadvantages of conventional radio frequencies.

[0007] Since this microwave cauterization method utilizes microwaves with shorter wavelengths compared to radio frequencies, it allows for the cauterization of a wide area in a short period of time, thereby minimizing thermal washing effects. Furthermore, due to this reduction in thermal washing effects, it is possible to cauterize and resect target tissues surrounding blood vessels.

[0008] However, due to the rapid heating characteristic of microwaves, excessive cauterization of surrounding tissues is a concern and can lead to damage to nearby tissues such as blood vessels or bile ducts. Furthermore, most microwave antennas are made of polymer resins, which has the disadvantage of reduced ultrasonic visibility.

[0009] Therefore, there is a need for a new tumor treatment system that can overcome the disadvantages of this microwave ablation method.

[0010] To solve the aforementioned problems, the present invention aims to provide a tumor treatment system capable of minimizing metastasis caused by tumor loss and recurrence caused by unremoved tumors by including a microwave transmission antenna capable of precisely controlling the cauterization temperature and range of the tumor and a power transmission unit that supplies microwaves of a specific waveform.

[0011] To solve the above-mentioned problem, the present invention provides a tumor treatment system comprising: a microwave transmission antenna; a heat medium supply unit for supplying a heat medium to the microwave transmission antenna; an energy supply unit for supplying microwave energy to the microwave transmission antenna; and a control unit for controlling the heat medium supply unit and the energy supply unit using a temperature or impedance measured in a target tissue.

[0012] In one embodiment, the energy supply unit can supply energy in the form of a pulse wave.

[0013] In one embodiment, the tumor treatment system may include one or more microwave delivery antennas.

[0014] In one embodiment, a temperature sensor or an impedance sensor may be installed on the outer surface of the antenna.

[0015] In one embodiment, the temperature sensor or the impedance sensor may be a thin-film sensor.

[0016] In one embodiment, an ultrasonic reflection structure may be formed on the outer surface of the antenna.

[0017] In one embodiment, the microwave transmission antenna may include: an antenna sheath separating the inside and outside of the antenna; an inner conductor installed inside the antenna sheath and extending from one side to the other; an outer conductor installed on the outside of the inner conductor; an insulating layer located between the inner conductor and the outer conductor and electrically insulating the inner conductor and the outer conductor; a pin electrically connected to one end of the inner conductor; and a shield covering a portion of the outer conductor.

[0018] In one embodiment, one end of the outer conductor may be exposed to the outside of the shield.

[0019] In one embodiment, the antenna sheath may further include a cooling pipe inside.

[0020] In one embodiment, the cooling pipe is located between the antenna sheath and the shield, and one end of the cooling pipe may be installed to extend to one end of the fin.

[0021] In one embodiment, a heat medium is supplied inside the cooling pipe, and the heat medium can be supplied inside the cooling pipe and discharged between the cooling pipe and the antenna sheath.

[0022] The tumor treatment system using microwaves according to the present invention utilizes one or more antennas to implement an appropriate cauterization pattern depending on the shape of the target tissue, thereby enabling cauterization of the target tissue while minimizing damage to surrounding tissues.

[0023] In addition, the tumor treatment system using microwaves according to the present invention can directly measure changes in temperature and impedance of the target tissue by installing a temperature sensor or an impedance sensor on the surface of the antenna, thereby controlling the cauterization temperature and speed. Accordingly, changes in the target tissue can be directly verified, and at the same time, the amount of microwaves and cooling water can be accurately controlled.

[0024] Figure 1 shows the structure of a tumor treatment system using microwaves according to one embodiment of the present invention.

[0025] FIG. 2 illustrates a pulse wave type energy supply according to one embodiment of the present invention.

[0026] FIG. 3 shows the internal structure of a microwave transmission antenna according to one embodiment of the present invention.

[0027] FIG. 4 shows the range of a microwave transmission antenna according to one embodiment of the present invention, where (a) shows a conventional antenna and (b) shows the antenna of the present invention.

[0028] FIG. 5 shows the movement of a heat medium inside an antenna for microwave transmission according to one embodiment of the present invention.

[0029] FIG. 6 shows the movement of a heat medium in a microwave transmission antenna including a heat medium guide means inside a cooling pipe according to one embodiment of the present invention.

[0030] FIG. 7 shows the direction of movement of the heat medium on the inner surface of a cooling pipe according to one embodiment of the present invention.

[0031] FIG. 8 shows the movement of a heat medium on the inner surface of a cooling pipe according to one embodiment of the present invention.

[0032] FIG. 9 illustrates a cross-section of a cooling pipe according to one embodiment of the present invention.

[0033] FIG. 10 shows the movement of a heat medium in a microwave transmission antenna including a heat medium guide means outside a cooling pipe according to one embodiment of the present invention.

[0034] Preferred embodiments of the present invention are described in detail below. In describing the present invention, detailed descriptions of related prior art are omitted if it is determined that such detailed descriptions may obscure the essence of the invention. Throughout the specification, singular expressions should be understood to include plural expressions unless the context clearly indicates otherwise, and terms such as “comprising” or “having” are intended to specify the existence of the described features, numbers, steps, actions, components, parts, or combinations thereof, and should not be understood as precluding the existence or addition of one or more other features, numbers, steps, actions, components, parts, or combinations thereof. Furthermore, in carrying out the method or manufacturing method, each process constituting the method may occur differently from the specified order unless the context clearly indicates a specific order. That is, each process may occur in the same order as specified, may be performed substantially simultaneously, or may be performed in the reverse order.

[0035] The technology disclosed in this specification is not limited to the embodiments described herein and may be embodied in other forms. The embodiments introduced herein are provided merely to ensure that the disclosed content is thorough and complete, and to ensure that the technical concept of the technology is sufficiently conveyed to those skilled in the art. In the drawings, the dimensions, such as the width or thickness of each component, have been slightly enlarged to clearly represent the components of each device. The drawings are described from the perspective of an observer, and where one element is mentioned as being positioned above another element, this implies both that the element is positioned directly above the other element and that an additional element may be interposed between them. Furthermore, those skilled in the art may embody the concept of the invention in various other forms without departing from the technical concept of the invention. Also, in multiple drawings, the same reference numerals refer to substantially identical elements.

[0036] In this specification, the term "and / or" includes a combination of the plurality of described items or any one of the plurality of described items. In this specification, "A or B" may include "A," "B," or "both A and B."

[0037] The present invention relates to a tumor treatment system comprising: an antenna for microwave transmission; a heat medium supply unit for supplying a heat medium to the antenna for microwave transmission; an energy supply unit for supplying microwave energy to the antenna for microwave transmission; and a control unit for controlling the heat medium supply unit and the energy supply unit using a temperature or impedance measured in a target tissue.

[0038] The above-described tumor treatment system may include one or more microwave transmission antennas. As described below, the tumor treatment system of the present invention enables high-efficiency cauterization through the energy transmission unit. However, if the tumor is large or has an irregular shape rather than a spherical shape, cauterization must be repeated multiple times. Furthermore, performing such multiple cauterizations may result in the detachment of the target tissue, which may indicate metastasis of cancer or the like. Therefore, in the case of the present invention, by using one or more microwave transmission antennas, cauterization can be performed while minimizing the risk of metastasis even when the target tissue is large or has an irregular shape.

[0039] In this case, when only one microwave transmission antenna of the present invention is used, it is possible to insert the antenna into the target tissue and cauterize it as described above; however, when two or more antennas are used, it is preferable to insert them at regular intervals on the outer side or periphery of the target tissue to cauterize it.

[0040] The internal structure of the microwave transmission antenna of the present invention will be described later.

[0041] A temperature sensor (40) or an impedance sensor (50) may be installed on the outer surface of the antenna. In conventional microwave transmission antennas, the temperature sensor is typically located inside the antenna. That is, the temperature sensor is installed inside the antenna to protect the temperature sensor while preventing resistance caused by the protruding temperature sensor and the resulting bending of the antenna when the antenna is inserted. In addition, the temperature sensor is typically located on the outer side of the shield to prevent short circuits with the electrodes. However, in this case, the direct temperature of the target tissue cannot be verified due to the antenna sheath, and it is difficult to accurately measure the temperature of the target tissue because it is installed at a distance from the point of heating.

[0042] In the case of the present invention, to improve this, the temperature sensor (50) is installed on the outer surface of the antenna, and by using a thin-film sensor, resistance during insertion by the temperature sensor can be minimized. Accordingly, in the case of the present invention, the temperature of the target tissue can be measured directly, and since it can be installed regardless of the internal structure of the shield and antenna, the temperature sensor (40) can be installed at the location where the most cauterization is performed.

[0043] In addition, an impedance sensor (50) may be installed in the present invention. Generally, tissue denaturation and carbonization are performed during the cauterization process, and accordingly, the impedance of the tissue may change. By measuring this, the degree of cauterization of the target tissue can be confirmed, and a desired amount of cauterization can be performed. At this time, the impedance sensor (50) may also use a thin-film sensor, just like the temperature sensor (40).

[0044] An ultrasonic reflection structure may be formed on the outer surface of the above antenna. Generally, antenna insertion is performed while verifying the ultrasonic image. At this time, while it is common practice to irradiate and measure the ultrasound supplied for the image from a vertical direction relative to the target tissue, the antenna of the present invention is inserted at a certain angle from the vertical direction to avoid interference with the ultrasonic probe and to ensure smooth insertion. In this case, most of the ultrasound reflected from the antenna sheath does not return to the ultrasonic probe, making it difficult to confirm the antenna's position.

[0045] Therefore, by forming an ultrasonic reflection structure on the outer surface of the antenna, position verification by ultrasound can be performed smoothly. At this time, the ultrasonic reflection structure may utilize existing technologies, and preferably, a metamaterial having ultrasonic reflection, diffraction, and amplification effects may be used. The metamaterial refers to a material formed by repeating a certain microstructure, and through a circular or square structure, not only can the reflection effect of the ultrasound be maximized, but the ultrasonic visibility of the antenna can also be improved by having diffraction or amplification effects.

[0046] The above-mentioned heat medium supply unit (30) is a part that supplies a heat medium (31) to the antenna. As described later, a cooling pipe (700) is installed in the antenna, and the inside of the antenna is cooled through it. At this time, the above-mentioned heat medium supply unit (30) is a part that supplies a heat medium (31) to the cooling pipe (700). In addition, the above-mentioned heat medium supply unit (30) may be used as a heat medium supply unit alone, but it is possible to reuse the heat medium used for cooling the antenna by using a heat medium recovery unit and a heat medium cooling unit.

[0047] The energy supply unit (20) is a part that supplies energy (21) to the electrode inside the antenna to generate microwaves. At this time, the energy (21) can be supplied in the form of a continuous wave, but preferably can be supplied in the form of a pulse wave (Fig. 2).

[0048] When energy is supplied in the form of pulse waves as in the present invention, the output of the radiated microwaves can be increased while the total amount of energy supplied can be reduced. Through this, smooth cauterization is possible while minimizing the heating of surrounding tissues. In addition, this pulse wave energy supply can minimize energy leakage caused by resonance during microwave generation, thereby enabling high efficiency.

[0049] In addition, when supplying pulsed energy as described above, energy can be supplied intermittently or continuously, as shown in FIG. 2. Looking at this in detail, when only one antenna is used and pulsed energy is supplied, intermittent cauterization can be performed as shown in FIG. 2(a). Also, when multiple antennas are used, if pulsed energy is supplied simultaneously to all antennas, intermittent cauterization is possible as shown in FIG. 2(a). Furthermore, when multiple antennas are used and pulsed energy is supplied sequentially to each antenna, continuous cauterization is possible even though pulsed energy is supplied, as shown in FIG. 2(b). Through this, water vapor generated from the target tissue during the cauterization process can be reduced, and tissue damage or explosion caused by water vapor can be minimized. Consequently, the occurrence of metastasis due to tissue detachment can be reduced.

[0050] In addition, the energy output supplied to the antenna may be greater than 0W and less than or equal to 150W, and may have a frequency of 2400~2500MHz. If the output is exceeded, the cauterization of the tissue may occur rapidly, making control difficult, and the antenna may also be damaged due to excessive heat.

[0051] The control unit (10) can control the heat medium supply unit (30) and the energy supply unit (20) using the measured temperature or impedance (11) of the microwave transmission antenna. As described above, the surface of the antenna of the present invention may include a thin-film type temperature sensor (40) or an impedance sensor (50). At this time, the control unit (10) can adjust the amount of energy and cooling heat medium supplied to the antenna based on the change in temperature or impedance (11) measured by the temperature sensor and the impedance sensor. For example, if the change in impedance is small and the change in temperature is large, it means that heating inside the antenna is occurring more than cauterization, so the circulation amount of the cooling heat medium can be increased; and if the change in impedance appears rapidly, it means that cauterization is being performed at a speed greater than the desired speed, so the amount of energy supplied can be reduced.

[0052] Since these changes in temperature and impedance vary depending on the type of target tissue, the depth of the target tissue, the size of the target tissue, the number of antennas used, the presence or absence of surrounding blood flow, and the patient's condition, it is desirable to input various cases through big data learning and then utilize them to operate the control unit. In addition, it is desirable to display the operating temperature, time, heat medium supply amount, or energy supply amount of the control unit on a display means linked to the control unit so that the user can verify them and easily confirm them.

[0053] FIG. 3 shows the internal structure of an antenna transmitting microwaves according to one embodiment of the present invention. The present invention will be described in detail below with reference to the drawings.

[0054] The above-mentioned antenna transmitting microwaves may include: an antenna sheath separating the inside and outside of the antenna; an inner conductor installed inside the antenna sheath and extending from one side to the other; an outer conductor installed on the outside of the inner conductor; an insulating layer located between the inner conductor and the outer conductor and electrically insulating the inner conductor and the outer conductor; a pin electrically connected to one end of the inner conductor; and a shield covering a portion of the outer conductor.

[0055] The antenna sheath (100) is a part that separates the inside and outside of the antenna and is used to separate the target tissue that is in contact with the outside and the tissue that is perforated to reach the target tissue from the conductor present inside the antenna sheath (100). In particular, in the case of the present invention, since microwaves are supplied through the conductor, if the conductor comes into direct contact with the tissue, localized heating may occur or insulation of the conductor may not be achieved, and the antenna sheath (100) can be used to prevent this.

[0056] At this time, the antenna sheath (100) may be made of metal, ceramic, or polymer resin, but preferably may be made of polymer resin having electrical insulation properties and appropriate elasticity.

[0057] In the present invention, one side or one end indicates the direction in which the penetration tip (800) is installed relative to the antenna, and the other side or the other end indicates the direction in which the control unit is connected. Additionally, the inner side or inner surface indicates the direction toward the center of the antenna, and the outer side or outer surface indicates the direction in which the antenna contacts the target tissue.

[0058] The inner conductor (200) is installed inside the antenna sheath (100) and can be installed extending from one side to the other. One side of the inner conductor (200) is a part that contacts the pin (500) to be described later, and the other side can be electrically connected to the microwave supply unit to be described later. Through this, the inner conductor (200) can transmit energy to the pin (500). In addition, since the inner conductor (200) of the present invention is insulated by an insulating layer (400) to be described later, it is preferable not to directly generate microwaves, but it is also possible to generate microwaves by opening the insulating layer (400) in some sections.

[0059] In the present invention, energy may refer to energy that generates microwaves, but it may also refer to the microwaves themselves. That is, the pin (500) may receive energy for generating microwaves to generate microwaves and radiate them to the outside, and in the case where microwaves are directly supplied, the pin (500) may perform only the role of radiating the transmitted microwaves to the outside.

[0060] A pin (500) electrically connected to the inner conductor (200) may be formed at one end of the inner conductor (200). The pin (500) is electrically connected to the inner conductor (200) and is a part that emits microwaves; it may be manufactured to have a larger diameter than the inner conductor (200). Through this, energy transmitted from the inner conductor (200) can be emitted in the form of microwaves from the pin (500), and since microwaves are emitted centered around the pin (500), target tissue around the pin (500) can be cauterized. Furthermore, if microwaves are emitted from a part excluding the pin (500), cauterization may be performed in an unintended location; therefore, the inner conductor (200) may be insulated using an insulating layer (400) as described later. This insulating layer (400) is installed extending to the other end of the pin (500), and one end of the inner conductor (200) can be joined or inserted to the other end of the pin (500) to be connected.

[0061] The outer conductor (300) is a part that generates microwaves separately from the inner conductor (200). In the case of a conventional microwave transmission antenna, microwaves are generated from a pin (500) connected to one end of the inner conductor (200). The microwaves generated at this time are known to have a teardrop shape, with one side having a larger diameter and the other side having a smaller diameter, although this varies depending on the shape of the pin (500) (Fig. 4(a)). However, since most target tissues, including the arm, are formed in a spherical shape, using microwaves with such a teardrop shape may cause cauterization to parts other than the desired target tissue. Therefore, in the case of the present invention, by using the outer conductor (300), the microwaves at the tail portion of the teardrop can be enhanced, and accordingly, it is possible to form microwaves that are close to a spherical shape (Fig. 4(b)).

[0062] However, in the case of the outer conductor (300) above, since microwaves are generated in the exposed part, a part of the outer conductor (300) can be wrapped with a shield (600) to prevent microwave radiation from unwanted parts. This will be described later.

[0063] The insulating layer (400) is positioned between the inner conductor (200) and the outer conductor (300) to maintain insulation between the inner conductor (200) and the outer conductor (300). In particular, in the case of the present invention, since the inner conductor (200) does not directly generate microwaves as described above, it is preferable to use the insulating layer (400) to provide insulation, and furthermore, the insulating layer (400) can prevent the inner conductor (200) and the outer conductor (300) from short-circuiting.

[0064] The shield (600) is installed to block microwaves generated from the outer conductor, and can wrap around a part of the outer conductor (300) so that the outer conductor (300) emits microwaves only in the desired area. That is, the outer conductor (300) in the part where the shield (600) is installed simply performs the role of a conductor, and microwaves can be emitted only from the part of the outer conductor (300) exposed to the outside of the shield (600).

[0065] Looking at this in detail, the microwave formed by the pin (500) cauterizes a circular space centered on the pin (500) as described above. However, since an internal conductor is connected to the other end of the pin (500), the microwave can be radiated and cauterized in a teardrop shape (Fig. 4 (a)). In this case, if the exposed portion of the external conductor (300) is formed at the tail portion of the teardrop shape, the cauterized space by the microwave can become closer to a sphere as the tail portion of the teardrop becomes thicker. Additionally, since the shield (600) can remove the tail end of the teardrop shape and the other end of the microwave formed by the external conductor, the cauterized space by the microwave can be made closer to a sphere (Fig. 4 (b)).

[0066] A gap (410) in which the insulating portion is exposed may be formed between the pin (500) and the outer conductor (300). As described above, the exposed portion of the outer conductor (300) may be formed to make the microwave generated by the pin (500) spherical. Therefore, it is preferable that the outer conductor (300) be manufactured to be spaced apart from the pin (500) at a certain distance, and accordingly, a gap (410) in which the insulating portion is exposed may be formed. In the case of such a gap (410), it may have a different length depending on the output of the microwave by the pin (500), but preferably it may be 1 to 10 mm. If the length of the gap (410) is less than 1 mm, the microwave interruption portion by the external electrode may become thicker, and if it exceeds 10 mm, the diameter of the central portion of the ablation space may become smaller.

[0067] A reinforcing pipe may be installed at the other end of the shield (600). The reinforcing pipe is installed extending from the other end of the shield toward the other end of the antenna, thereby supplementing the shielding of the antenna while simultaneously strengthening the antenna's durability and maintaining its shape. In other words, the antenna can maintain a straight line and be inserted into the human body through the reinforcing pipe. Furthermore, it is preferable that the reinforcing pipe and the shield be installed at a certain distance apart for insulation. As mentioned above, since the shield is used to control the shape of the antenna, it must be electrically insulated. Therefore, the electrical insulation of the shield can be maintained by installing it at a certain distance apart from the reinforcing pipe.

[0068] A cooling pipe (700) may be further included inside the antenna sheath (100). Such microwave radiation may cause heating of the fin (500) and electrode. This heating of the fin (500) and electrode may not only cause unwanted cauterization but also cause the internal components of the antenna to deform due to heat. Therefore, it is desirable for the interior of the antenna to be cooled to maintain a constant temperature. Furthermore, when such cooling is performed, the antenna and the target tissue surrounding the antenna may be rapidly cooled after the cauterization is completed, thereby preventing the cauterization from spreading to unwanted areas.

[0069] The cooling pipe (700) is positioned between the antenna outer shell (100) and the shield (600). At this time, a heat transfer medium can pass through the inside of the cooling pipe (700), and cooling of the fin (500) and electrode can be performed through the movement of this heat transfer medium.

[0070] The heat transfer fluid mentioned above refers to a fluid that transfers heat and can perform the role of absorbing heat generated in a certain part and transferring it to another part. In the case of the present invention, the heat transfer fluid can perform the role of transferring heat generated from the fin (500) and electrode to the outside of the antenna. At this time, the heat transfer fluid used in the present invention may be a liquid such as water, alcohol, or oil, but may also be a gas such as nitrogen, helium, carbon dioxide, and air, or a liquefied gas such as liquid carbon dioxide or liquid nitrogen, or a supercritical fluid. Preferably, water may be used.

[0071] The heat medium can be supplied from within the cooling pipe (700) and discharged between the cooling pipe (700) and the antenna sheath (100) (Fig. 5). The method of supplying the heat medium can be broadly divided into two types. When the heat medium is supplied between the cooling pipe (700) and the antenna sheath (100) and then discharged through the inside of the cooling pipe (700), the heat medium heated by the temperature of the target tissue, i.e., body temperature, comes into contact with the pin (500). In particular, since cauterization is being performed in the case of the present invention, the heat medium may be heated by the target tissue heated to a temperature higher than body temperature. That is, in this case, not only may the cooling effect of the pin (500) be reduced, but the target tissue may also be cooled by the heat medium, so the cauterization efficiency may be reduced.

[0072] Accordingly, in the case of the present invention, the heat medium passes through the interior of the cooling pipe (700) and is discharged toward one end of the cooling pipe (700), and subsequently can be discharged toward the other end of the antenna through the space between the cooling pipe (700) and the antenna outer sheath (100). Through this, not only can the cooling effect of the electrode and the pin (500) be maximized, but as the heat medium heated by the pin (500) and the electrode passes through the outside of the cooling pipe (700), the reduction in efficiency caused by the movement of the heat medium during cauterization of the target tissue can be minimized.

[0073] In addition, the cooling pipe (700) may be installed such that one end of the cooling pipe (700) extends to one end of the fin (500) to maximize the cooling effect of the fin (500). At this time, one end of the cooling pipe (700) may extend to the same position as one end of the antenna, and may also have a difference of 5 mm or less from one end of the fin (500). If the length of the cooling pipe (700) is formed to be longer than 5 mm compared to the fin (500), there is no difference in cooling efficiency, and since the length of the antenna becomes longer, the antenna must be inserted to the lower part of the target tissue; if it is formed to be shorter than 5 mm, the cooling efficiency of one end of the fin (500) may decrease.

[0074] A plurality of heat medium guide means (710) may be formed on the inner surface of the cooling pipe (700) (Fig. 6). Generally, when a heat medium passes through the inside of a pipe to perform heat exchange, mixing of the heat medium is performed as a method to increase the efficiency of heat exchange. This mixing of the heat medium not only prevents a local temperature rise but also increases the heat exchange efficiency by reducing the boundary layer formed at the interface between the heat medium and the pipe or between the heat medium and the object to be heat exchanged.

[0075] In the case of the present invention, the mixing efficiency of the heat medium can be increased by forming a plurality of heat medium guide means (710) on the inner surface of the cooling pipe (700).

[0076] It is preferable that the heat medium guide means (710) be installed at an angle of 10 to 45° relative to the longitudinal direction of the antenna (see FIG. 7). As described above, the heat medium guide means (710) can prevent the heat medium from performing simple linear motion. In this case, when installed at a constant angle relative to the longitudinal direction of the antenna as described above, the heat medium is supplied from the other end of the antenna to the first end and can be supplied while rotating relative to the center of the antenna (Fig. 6). In the present invention, since an electrode and a pin (500) are installed at the center of the antenna, the cooling efficiency of the electrode and the pin (500) can be increased when the heat medium is supplied while rotating by the heat medium guide means (710). In this case, if the angle of the heat medium guide means (710) is less than 10°, the rotational mixing effect as described above may decrease, and if it exceeds 45°, it is inefficient because a large amount of fluid resistance occurs.

[0077] Additionally, the heat medium guide means (710) may be manufactured simply as a plate, but may have a structure to increase the mixing efficiency of the heat medium. As an example, the heat medium guide means (710) may have a cross-section in the shape of a 'ㅅ' by combining two or more mixing plates (712) on one side of a single guide plate (711) (see FIG. 8). Through this, the heat medium introduced from the direction of the guide plate is separated into two flows by the mixing plate, and the separated flows can collide with adjacent flows to form vortices and mix. That is, the overall flow of the heat medium rotates by the guide plate (711) and moves toward one side of the antenna, but the heat medium can be simultaneously mixed inside the cooling pipe by the mixing plate (712). Consequently, when the heat medium guide means (710) of the present invention is installed, the heat exchange efficiency by the heat medium can be increased.

[0078] Additionally, the heat medium guide means (710) may be used as a support means to support the electrode and pin (500). In the case of the present invention, the electrode and pin (500) may be installed inside the cooling pipe (700) as described above. However, in order to increase the efficiency of the heat medium circulating inside the cooling pipe (700) and at the same time prevent damage to the electrode, it is preferable to install the cooling pipe (700) and the electrode at a certain distance. In this case, since a plurality of the heat medium guide means (710) are installed at a certain distance inside the cooling pipe (700) in the case of the present invention, the electrode may have a certain distance from the cooling pipe (700) by means of the heat medium guide means (710).

[0079] In addition, the inner side of the heat medium guide means (710) is located on the inner side of the cooling pipe (700), and the outer side is joined to the inner surface of the cooling pipe (700). At this time, the diameter (720) formed by the inner end of the heat medium guide means (710) may be 80 to 100% of the diameter of the electrode structure.

[0080] In the present invention, the electrode structure refers to a structure installed inside the cooling pipe (700), comprising a pin (500), an inner conductor (200), an insulator, an outer conductor (300), and a shield (600).

[0081] The diameter (720) of the portion formed by the inner end of the heat medium guide means (710) refers to the diameter of a circle that contacts the inner end of the heat medium guide means (710) (see FIG. 9), and in the case of the present invention, since a plurality of heat medium guide means (710) are installed, it refers to the diameter of a circle that has a constant distance from the cooling pipe (700).

[0082] As described above, when the diameter (720) of the portion formed by the inner end of the heat medium guide means (710) is smaller than that of the electrode structure, the heat medium guide means (710) can be deformed into a random shape when the cooling pipe (700) is installed. This deformation of the heat medium guide means (710) can not only elastically support the electrode structure, but the deformed shape can also accelerate the mixing of the heat medium passing through the interior. However, if the diameter (720) of the portion formed by the inner end of the heat medium guide means (710) is less than 80% of that of the electrode structure, it is difficult to insert the electrode when the cooling pipe (700) is installed, and the heat medium guide means (710) may be damaged.

[0083] In addition, the heat medium guide means (730) can be installed on the outer surface as well as the inner surface of the cooling pipe (700) (Fig. 10). As described above, the heat medium is supplied from inside the cooling pipe (700) and discharged into the space between the cooling pipe (700) and the antenna outer shell (100). Therefore, when the heat medium guide means (730) is installed on the outer surface of the cooling pipe (700), the space between the cooling pipe (700) and the antenna outer shell (100) can be secured at a constant level, and the cooling efficiency of the target tissue by the heat medium discharged through the outer surface of the cooling pipe (700) can also be increased. The shape and size of the heat medium guide means (730) installed on the outer surface of the cooling pipe are the same as those of the heat medium guide means (710) installed on the inner surface of the cooling pipe (700), so a description is omitted.

[0084] The heat medium guide means (730) may be configured to have a gap of 0.1 to 1 mm between the cooling pipe (700) and the antenna sheath (100). If the gap between the cooling pipe and the antenna sheath is less than 0.1 mm, the discharge of the heat medium is not easy, and if the gap exceeds 1 mm, the thickness of the antenna becomes thicker, making it difficult to use.

[0085] A through tip (800) may be attached to one end of the antenna sheath (100). The through tip (800) is a structure that allows the antenna to be inserted into the human body, and one end is pointed so that it can be easily inserted into the human body. To facilitate such insertion into the human body, the through tip (800) has a pointed tip formed at one end and the other end is formed to have the same diameter as the antenna sheath (100). In addition, the through tip (800) may be made of a polymer resin or ceramic so as not to interfere with the formation of microwaves by the electrode and pin (500), and it is more preferable to make it of ceramic. Furthermore, it is possible to attach a groove, a protrusion, or a blade to the outer surface of the through tip (800) to facilitate insertion into the human body.

[0086]

[0087] Foregoing, specific parts of the present invention have been described in detail. It will be apparent to those skilled in the art that such specific descriptions are merely preferred embodiments and do not limit the scope of the invention. Accordingly, the actual scope of the invention is defined by the appended claims and their equivalents.

Claims

1. Antenna for microwave transmission; A heat transfer medium supply unit that supplies a heat transfer medium to the above-mentioned microwave transmission antenna; An energy supply unit that supplies microwave energy to the above-mentioned microwave transmission antenna; and A control unit that controls the heat medium supply unit and the energy supply unit using the temperature or impedance measured in the target organization; A tumor treatment system including 2. In Paragraph 1, A tumor treatment system characterized by the above energy supply unit supplying energy in the form of pulse waves.

3. In Paragraph 1, The above tumor treatment system is characterized by including one or more microwave transmission antennas.

4. In Paragraph 1, A tumor treatment system characterized by having a temperature sensor or an impedance sensor installed on the outer surface of the above antenna.

5. In Paragraph 4, A tumor treatment system characterized in that the temperature sensor or the impedance sensor is a thin-film sensor.

6. In Paragraph 1, A tumor treatment system characterized by having an ultrasonic reflection structure formed on the outer surface of the above antenna.

7. In Paragraph 1, The above microwave transmission antenna is, An antenna sheath that distinguishes the inside and outside of the above antenna; An inner conductor installed inside the outer shell of the antenna and extending from one side to the other; An outer conductor installed on the outer side of the inner conductor; An insulating layer located between the inner conductor and the outer conductor, which electrically insulates the inner conductor and the outer conductor; A pin electrically connected to one end of the inner conductor; and A shield covering a portion of the above outer conductor; A tumor treatment system including 8. In Paragraph 7, A tumor treatment system characterized in that one end of the outer conductor is exposed to the outside of the shield.

9. In Paragraph 7, A tumor treatment system characterized by further including a cooling pipe inside the antenna sheath.

10. In Paragraph 9, A tumor treatment system characterized in that the cooling pipe is located between the antenna outer shell and the shield, and one end of the cooling pipe is installed extending to one end of the fin.

11. In Paragraph 10, A heat transfer medium is supplied to the inside of the above cooling pipe, and A tumor treatment system characterized by the above-mentioned heat medium being supplied inside the cooling pipe and discharged between the cooling pipe and the antenna sheath.

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