JP2008245990A - High-frequency therapy apparatus and system, and their usage - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an RF therapy apparatus such as a therapeutic antenna probe having an RF antenna assembly and a sheath including at least an incision blade made of a hard material; an RF therapy system incorporating the RF therapy apparatus, and their usage. <P>SOLUTION: The therapeutic antenna probe includes an RF power transmission cable forming a dipole antenna assembly 420, and the sheath 401. An RF power transmission means consists of a central conductor, a tubular dielectric insulator 403, and an external conductor 404, and the dipole antenna assembly is formed by combining them together. The dipole antenna 420 is a member of the dipole antenna assembly, and consists of first and second electrodes 408 and 409 formed of part of the external conductor and connected to the single central conductor, and an insulating means 407 formed between the both electrodes. The sheath 401 is made of the hard material and stores at least a single head element having a sharp side part. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates generally to the structure and use of a radio frequency (hereinafter referred to as RF) treatment device and system. Specifically, the present invention relates to an RF treatment device such as a therapeutic antenna probe having an RF antenna assembly and a sheath including at least one cutting blade made of a hard material, and an RF treatment system including the RF treatment device. , And how to use it.

  RF surgical instruments are widely used for the purpose of removing tumors and diseased tissues. One of the features of the RF surgical instrument is that it is relatively less invasive. This is due to the surgical instrument being used in a special way and inserted into a specific area of the diseased tumor or into a specific area of tissue adjacent to the diseased tumor. An RF surgical device absorbs RF power in a tissue region where a lesion is just expressed by generating heat inside the tumor or in a lesion tissue where a lesion or cancer is expressed. Is to be heat-fired. Although treatment with an RF surgical device is performed percutaneously, since the laparotomy range is relatively narrow, the invasiveness associated with the treatment is relatively low, and the hospitalization period of the patient can be shortened.

  There are the following two types of RF surgical instruments. One is an RF ablation device, in which a current is induced inside the tissue in which the RF ablation device is inserted, and the tissue is coagulated by the heat generated by the induced current. This is proposed by LeVeen as described in Document 1. The other type of RF surgical device emits microwave power and absorbs the power into the water inside the tissue in which the RF surgical device is inserted. The tissue is heated to a temperature higher than that necessary for degrading tissue proteins and necrotizing the tissue cells by the electric power absorbed by the intracellular moisture. As a microwave frequency, 945 MHz or 2.45 GHz has been used for some time. The treatment method using the RF surgical instrument as described above is called RF hyperthermia or percutaneous microwave coagulation.

  As a therapeutic product, microtase (registered trademark of Alfresa Pharma Corporation, Reference 1) is famous. This product utilizes the above two therapeutic effects. An electric probe (hereinafter abbreviated as “probe”) used for microtase has a coaxial structure similar to a coaxial cable. Specifically, as shown in FIGS. 1 and 2, the probe includes a center conductor 102 (abbreviated as “center conductor”), a cylindrical dielectric insulator 103 surrounding the outer periphery thereof, and an external conductive cylinder. 104 (abbreviated as “external conductor”) and an outer covering 105 covering the same. The outer conductor 104 is formed as one electrode, and the center conductor 102 is formed as the other electrode. In order to facilitate the surgical operation, the tip of the probe is formed as the tip of a needle as shown in FIGS. 1 and 2, or as the bullet-like head 106 shown in FIGS. The entire structure is referred to as a thermotherapy probe, and is particularly referred to as a thermotherapy monopole antenna probe (abbreviated as TTMP) based on the electrical characteristics of the electric probe.

  In addition to the thermotherapy probe described with respect to the second type (Reference 3), a thermotherapy probe specially designed to absorb and heat microwaves has been newly announced. The probe is made of a semi-rigid coaxial cable, which has a coaxial structure that suits the purpose of the probe. Specifically, as shown in FIGS. 5 and 6, the outer conductor 104 is divided into several segments, and one electrically insulating gap 107 is provided between each two adjacent segments. is there. The first electrode 108 is one outer conductor 104 and is a segment connected to the central conductor 102 among adjacent segments, and is formed for the outer conductor 104. is there. The second electrode 109 is the other outer conductor 104 and is the other segment of the adjacent segment and is insulated from the first electrode 108 and formed from the outer conductor 104. Is. The outer conductor is covered with an outer coating 105. Therefore, the electrode of this thermotherapy probe has the structure of an antenna assembly, in particular the structure of a dipole antenna. The entire antenna assembly is covered with an insulating material or housed in an insulating case made of an insulating material. This structure is called a thermotherapy dipole antenna probe (hereinafter abbreviated as TTDP).

  The external appearance of the insulating case 117 or 117A described in Reference 1 and Reference 2 is as shown in FIGS. 5 and 6, which are made of rigid polyvinyl chloride (PVC) or polytetrafluoroethylene (PTFE). ). The insulating case 117 covers the entire dipole antenna, and the insulating case 117A houses the entire dipole antenna. In another part of the outer conductor structure, a structure in which a part of the first electrode is electrically connected to the central conductor via the conductive disk 110, thereby making the probe structure cylindrically symmetric. It has been known. Specifically, such a TTDP is covered with an insulating case 117 as shown in FIGS.

  Comparing the therapeutic effects obtained by TTMP and TTDP and confirming the actual phenomenon at the time of use, the lesion tissue in which TTMP is inserted is heated in that region, and the central conductor and the outer conductor in the vicinity thereof are heated. It can be seen that the area sandwiched between the two is heated by the dielectric current flowing there (FIG. 9). Therefore, the region cauterized by TTMP (heated to the extent that it does not burn) is localized in the section from the central conductor 102 (located at t0) to r1. Here, r1 is a separation distance from TTMP where the solid line and the dotted line intersect. On the other hand, in the case of TTDP, the first electrode and the second electrode constitute a dipole antenna. The water in the lesion tissue area around the position where the TTDP is inserted absorbs the microwaves emitted from such a position and is heated to a temperature higher than the temperature at which the protein in the lesion tissue is decomposed. Therefore, the area of the “cautery” region treated with TTDP is larger (as shown in FIG. 10) than that of the treated region with TTMP, which forms a dipole antenna composed of the first electrode and the second electrode. In the coaxial cable, the horizontal microwave propagation after conversion from the TEM mode, that is, due to the physical characteristics of the microwave radiation. The cautery region is r = ts, that is, a section from the surface of the insulating case 117 or 117A to r = r2. Here, r2 is the distance from TTDP where the solid line and the dotted line intersect. In particular, tumors such as cancer tissues are easily necrotic at low temperatures that are slightly higher than the proteolytic temperature. Therefore, with TTDP, a tumor can be cauterized and necrotized with little burden on normal tissue. This therapeutic effect on tumors is the same as hyperthermia. The detailed structures of TTMP and TTDP shown in FIGS. 11 and 12 are the same as those shown in FIGS. In FIG. 11 and FIG. 12, the symbol TR indicates a thermotherapy region, and the symbol TI indicates a tissue.

“Microtaze” (Trade Mark), a corporate booklet of Alfresa Pharma (www.alfresa-pharma.co.jp/microtaze/520e.pdf). Medical Instrument 74, No. 6, 2004, pages 292-314 “Clinical Trials of Interstitial Microwave Hyperthermia by Use of Coaxial-Slot Antenna With Two Slots”, Kazuyuki Saito, Hiroyuki Yoshimura, Koichi Ito, Yutaka Aoyagi and Hirotoshi Horita, IEEE Transaction on Microwave Theory and Techniques, Vol. 52, No. 8, August 2004.

  First, the present invention is outlined below.

  The surface of TTMP is formed of a copper outer conductor. Medical regulations do not allow direct contact between copper and tissue. Therefore, the TTDP head described in Document 3 is covered with or housed in an insulating case made of rigid PVC (polyvinyl chloride) or PTFE. However, these materials are insufficiently hard to insert TTDP percutaneously into the tissue. The surgeon must use a scalpel or a surgical blade to puncture the tumor and insert the TTDP before inserting the TTDP and performing RF thermotherapy. Therefore, the surgeon needs to perform a pre-treatment prior to the therapeutic operation. If guide grooves are provided by “pre-incision” of skin tissue and TTDP is guided, bleeding may be induced later, so TTDP is percutaneously invaded into the tumor and heated to RF thermotherapy. Single treatment treatment can be performed. By using a single treatment in this manner, the surgeon's treatment time can be shortened and the safety of the surgical operation can be improved.

  A first object of the present invention is to provide a means for eliminating the need for pre-treatment and enabling rapid RF thermotherapy. For this purpose, it is necessary to sharpen the front head of the insulating case of TTDP. Sharpening the TTDP head allows the tissue to be cut percutaneously and allows the surgeon to insert the TTDP into the tumor in a single procedure.

  Regarding TTDP in Document 3, there is a separate problem that the mechanical stability of the assembly cannot be maintained because the insulating case covering the antenna assembly is insufficient in strength. Therefore, if the patient moves on the operating table and the TTDP bends due to the muscle force and the electrical insulation gap is slightly distorted, the RF from the dipole antenna, particularly from the electrical insulation gap between the first electrode and the second electrode, The radiation direction of power radiation is deviated. The direction of the radiant power is deviated, causing uneven heating of the tumor and insufficient or incomplete RF thermotherapy. In order to solve this problem, an insulating case capable of maintaining the rigidity of the entire TTDP and holding the antenna assembly firmly is required. To achieve such an insulation case, a sheath incorporating a sharp head and a pipe that firmly holds the antenna should be used so that the deviation in the direction of RF power radiation during surgery can be suppressed. Good. The sharp head is made of hard material. Therefore, in order to achieve the first object of the present invention, an insulating case having a sharp head and a rigid pipe that makes the antenna assembly sufficiently rigid or robust may be used.

  In TTMP and TTDP described in Document 1, Document 2 and Document 3, the former is the electrical insulation gap between the center conductor and the outer conductor, and the latter is the electrical between the first electrode and the second electrode. RF power is radiated from the insulating gap. Therefore, since the induced current and the RF power are localized in the electrically insulating gap, the temperature of the tissue near the probe tends to be higher than the temperature of the tissue slightly away from the probe. Since the purpose of use of TTMP is to coagulate tumors at high temperatures, such uneven temperature distribution is not a serious problem in the use of TTMP. However, when using TTDP to maintain the tumor at a temperature that is sufficient for the protein of the tumor to decompose, the tissue near the probe becomes hot if the temperature distribution is uneven. If the temperature is high, the tissue will be burnt down, and protein decomposition will not occur due to the shochu. There is another problem with TTDP. That is, the tissue near the electrically insulating gap between the first electrode and the second electrode of TTDP is more likely to be heated by heating than other tissues in the region away from the electrically insulating gap. This is because the microwave radiation power density decreases with increasing distance from such an electrically insulating gap.

  If the RF power supplied to TTDP is reduced, the temperature rise can be suppressed. By suppressing the RF power in such a manner, the temperature of the tissue in the vicinity of TTDP can be maintained at the proteolytic temperature, but the temperature of the tissue slightly separated from TTDP is kept lower than the proteolytic temperature. Then, the advantage of TTDP that necroses a tumor that has grown in a wide area is reduced.

  The second object of the present invention is to eliminate uneven temperature distribution. In order to solve this problem, a sheath made of a nonconductive and highly heat conductive material is used as an insulating case. A hard material can be used for this sheath. Properties such as non-conductivity and high thermal conductivity allow RF radiation from the sheath and easily spread the heat concentrated near the sheath. Furthermore, it is desirable to increase the dielectric constant of the sheath. This is because if the dielectric constant of the sheath is large, the ratio of the dielectric constant between air and tumor is reduced, and the effective electrical length from TTDP can be increased to prevent overheating of the surface of the sheath.

  The TTDP in Document 3 has only one electrically insulating gap, through which RF power is radiated, and the diseased tissue is heated and necrotic. Therefore, in the case of these TTDPs, since there is only one radiation gap as described above, there is another problem that it is difficult to uniformly heat the tumor along the insulating case of TTDP.

  The third object of the present invention is to solve the above-mentioned problem due to the fact that there is only one radiation gap. Therefore, a new antenna configuration is proposed, and a plurality of electrically insulating gaps are provided above the antenna assembly for TTDP. These gaps are provided along the length of the antenna assembly.

  That is, since these antennas have a plurality of electrically insulating gaps, the intervals between the electrically insulating gaps are clogged, so that the uniformity of heating is further improved. In order to reduce the spacing as described above, the present invention provides a dipole antenna structure capable of reducing the effective wavelength of the microwave propagating in the antenna. With this new antenna structure, the RF power in the vertical direction along the antenna can be distributed long and uniformly in the axial direction. Then, it becomes possible to heat the tumor uniformly in the longitudinal direction of TTDP.

  The RF power is radiated from an electrically insulating gap provided in the antenna. This electrically insulating gap is provided between the second electrode made from the outer conductor and the first electrode connected to the center conductor. Therefore, the distance between the electrically insulating gap and the tip of the antenna is increased, and as a result, RF power radiation to the tip region of the TTDP is not sufficiently performed. This is called the “lighthouse effect”, but its origin is that the light is not radiated from the roof of the lighthouse, but the RF power is not radiated from the tip of the antenna.

  Accordingly, a fourth object of the present invention is to shorten the first electrode and diffract the RF power into the tip of the antenna, or to provide a radiation gap different from the radiation gap provided in the first to third object inventions. It is to eliminate the lighthouse effect by providing it separately at the tip of the lamp. Such an antenna structure can be additionally employed for the aforementioned new antenna assembly having a plurality of electrically insulating gaps. This makes the RF power distribution in the tumor more uniform.

  A fifth object of the present invention is to provide TTDP with a drug transport delivery function so that a drug can be injected into a diseased tissue into which TTDP is inserted. The drug after injection can be dissipated by heating with RF power emitted from TTDP or activated (so-called conversion to drug). TTDP provides such a route for drug delivery. Then, a single treatment in which TTDP is inserted into the tissue percutaneously enables heat treatment of the diseased tissue, conversion to the drug, and drug injection to be performed sequentially or simultaneously, so that TTDP is effectively used in tumor therapy. Can be used. The anti-cancer agent is delivered in an amount commensurate with the treatment of the tumor.

  A sixth object of the present invention is to provide a control system that allows a surgeon to safely use the TTDP disclosed in the present invention as described in the first to fifth objects of the present invention. Operation of the control system is performed in conjunction with drug delivery delivery by TTDP having the basic structure described in the first to fifth objects of the present invention.

  The present invention provides an improved TTDP for RF hyperthermia to achieve the first objective.

  An improved TTDP (hereinafter abbreviated as the present TTDP) has an RF power transmission means (coaxial cable or the like) forming an antenna assembly, and at least one head having a sharp side and is made of a hard material, and And a sheath made of a hard material for housing a dipole antenna assembly (hereinafter abbreviated as “antenna assembly”). The RF power transmission means is composed of one central conductor, a cylindrical dielectric insulator formed on the outer periphery of the central conductor, and an outer conductor. These all combine to form an antenna assembly. A first electrode formed from a part of the outer conductor and electrically connected to at least one central conductor; a second electrode formed from the other part of the outer conductor; a first electrode and a second electrode; And insulating means formed between the two. The head is a head element composed of a side portion and a flexible pipe, and the flexible pipe is connected to a coupling portion provided in the head element.

  Specifically, this TTDP has a sheath-like insulating case composed of a head part of which a head element made of a hard material such as sapphire forms a part. The head element of the sheath has a sharp side portion at the tip and a flexible pipe that is in close contact with the head element. The head of the sheath is composed of a head element and a flexible pipe. The head element of the sheath is hereinafter referred to as a head having a sharp side. One of the functions of the head having a sharp side is a role as a blade for a surgeon to percutaneously penetrate the TTDP into a tumor or a diseased tissue. Since a pretreatment for opening a probe insertion hole in a tissue for treatment is not necessary, treatment can be performed quickly. Since sapphire is non-conductive, the microwave field radiated from the antenna is not significantly attenuated. Therefore, the cauterization by this TTDP is comparable to the conventional TTDP using PVC or PTFE described in Reference 3.

  Pipes that hold the antenna firmly include FEP (fluorinated ethylene propylene copolymer), PTFE (polytetrafluoroethylene), ETFE (ethylene tetrafluoroethylene copolymer), and PFA (tetrafluoride). Insulating flexible pipes made of ethylene / perfluoroalkyl vinyl ether copolymer), heat shrink cross-linked polyethylene, or heat shrink ethylene propylene that mechanically and firmly contact the antenna assembly can be used. Since the solid contact with the antenna assembly is achieved by the heat shrink effect of the above material (hereinafter simply referred to as “heat shrink tube”), the insulating pipe is first manufactured in a molding process, then sharp edges To form a headed sheath. The heating process is performed on an assembly in which a head having a sharp side, an antenna assembly, an insulating pipe covering the periphery, and the like are previously incorporated. In the above process, the insulating flexible pipe contracts due to heat shrinkage, and holds the antenna assembly firmly. Therefore, it is possible to mechanically stabilize the RF power radiation from the electrically insulating gap of the TTDP against the bending force of the patient's muscles during surgery.

  The structure of the present TTDP for the above purpose is as shown in FIGS. The antenna assembly 220 includes a center conductor 202, a cylindrical dielectric insulator 203 that surrounds the outer periphery of the center conductor 202, and an outer conductor 204. The outer conductor 204 is a part of the first electrode 208 electrically connected to the center conductor 202 and the second electrode 209 electrically isolated from the first electrode 208 is its own. Has become another part. The TTDP 224 includes an antenna assembly 220 and a sheath 230 that houses the head. The head includes i) a head element (hereinafter referred to as a “head having a sharp side”) 293 composed of a sharp side and a coupling portion 292, and ii) heat shrinkage coupled to the coupling portion 292. A tube 294. The head portion 293 having a sharp side portion is made of a non-conductive and hard material such as sapphire, and is formed by a side portion 291 and a coupling portion 292 connected to the heat shrinkable tube 294. The first electrode 208 and the second electrode 209 are insulated by an electrically insulating gap 207, and all of them constitute a dipole antenna that is a member of the antenna assembly 220. The electrically insulating gap 207 is formed by removing a part of the outer conductor 204 by processing. The center conductor 202 is connected to the first electrode 208 via a conductive disc 210 for the antenna assembly 220 shown in FIGS. 13 and 14. In the case of another type of TTDP 224 shown in FIG. 15, the center conductor 202 is directly connected to the first electrode 208. FIG. 13 shows the appearance of the first electrode 208 and the second electrode 209 and the cross section of the sheath 230. The heat shrink tube 294 is configured to hold the antenna assembly 220 firmly when heated from the surroundings. Therefore, the antenna assembly does not bend easily. Since the tissue can be easily incised by the side 291 of the head 293 having a sharp side, the TTDP 224 can easily percutaneously enter the tumor by a single treatment. At this time, the TTDP 224 penetrates straight toward the tumor without bending when the surgeon pushes it. By tightening the heat shrinkable tube 294, the antenna assembly 220 is stabilized, and even if the TTDP is shaken, the RF power radiation from the dipole antenna structure including the first electrode 208, the second electrode 209, and the electrically insulating gap 207 is Does not become unstable.

  The TTDP 224 of the first object of the present invention has many advantages in addition to those described above, and further advantages will be described through the description of the individual embodiments.

  The second object of the present invention is to eliminate temperature unevenness.

  Specifically, 1) The temperature difference between the surface of TTDP (and hence the surface of the sheath) and the surrounding tissue should not be increased, and 2) the temperature of the surface of TTDP, particularly the back surface thereof should be the first electrode. Effectively suppressing the temperature of the surface of the hot part facing the electrically insulating gap between the electrode and the second electrode, 3) the temperature in the tissue on and near the surface of the TTDP, and the protein of the diseased tissue The difference between the temperature at which it decomposes and not 4) and the provision of a rigid sheath to allow TTDP to penetrate the tumor easily percutaneously with a single manipulation treatment. .

  For the second purpose of the present invention, the TTDP is made of a hard material such as sapphire, which is formed as a single body with power transmission means (coaxial cable, etc.) forming an antenna assembly and sharp edges. And a sheath for housing the antenna assembly. This RF power transmission means is composed of one central conductor, a cylindrical dielectric insulator formed on the outer periphery of the central conductor, and an outer conductor. These all combine to form an antenna assembly, and the dipole antenna is A first electrode formed from a part of the outer conductor and electrically connected to at least one central conductor; a second electrode formed from another part of the outer conductor; a first electrode and a second electrode And insulating means formed between the two.

  Specifically, the structure of TTDP provided for this purpose is as shown in FIGS. The antenna assembly 320 includes a center conductor 302, a cylindrical dielectric insulator 303 surrounding the outer periphery of the center conductor 302, and an outer conductor 304. A part of this 304 is electrically connected to the center conductor 302. The first electrode 308 is formed, and another part of the first electrode 308 forms a second electrode electrically insulated from the first electrode. The TTDP 324 includes an antenna assembly 320 and a single body sheath 301 made of a dielectric single material such as sapphire. The first electrode 308 and the second electrode 309 are electrically insulated via an electrically insulating gap 307, and all of these are combined to form a dipole antenna that is a member of the antenna assembly 320. The center conductor 302 is connected to the first electrode 308 via the conductive disk 310 in the antenna assembly 320 shown in FIGS. 16 and 17, and to the first electrode 308 in another type of TTDP 324 shown in FIG. 18. Directly connected. FIG. 16 is an external view of the first electrode 308 and the second electrode 309, but the single body sheath 301 is a cross-sectional view.

  When the material of the single body sheath 301 is sapphire, on the radiation plane at the origin corresponding to the rotation axis of the TTDP 324, the temperature distribution determined by the SAR (Specific Absorption Rate) is as shown in FIG. The solid line indicates the temperature of the tissue, and the broken line indicates the temperature of the single body sheath 301. The zero point corresponds to the surface of the outer conductor 304 (thus, the surface of the first electrode 308 and the surface of the second electrode 309). The temperature Ts indicates 42 ° C. at which protein decomposition starts. The dielectric constant of the material of the sheath 201 varies depending on the orientation of the sapphire crystal, but is considerably higher from 9.4 to 11.6. This figure is much larger than in the case of glass.

  For comparison, FIG. 9 shows the temperature distribution determined by the SAR for the conventional TTDP shown in FIGS. 5, 6, 7 and 8. FIG. A solid line indicates the temperature of the tissue, and a broken line indicates the temperature of the insulating case 117 of TTDP. In FIG. 9 (and as will be described later, FIG. 10), the symbol TT along the horizontal broken line indicates the thermotherapy temperature, and the TD along the vertical line indicates the temperature determined by SAR in Celsius.

  The relative dielectric constant of the insulating case 117 or 117A varies depending on the material such as hard PVC or hard PTFE used for the insulating case 117 or 117A. The former range is 2.3 to 3.1, and the latter range is 2.2 to 2.9. Both dielectric constants are much lower than the dielectric constant of the water in the tissue (about 80 ° C. at body temperature). Therefore, the electrical path determined by the through-electric field path of the insulating case 117 or 117A multiplied by the square of the dielectric constant is considerably short, and the attenuation of the RF power emitted from the TTMP is slight. Due to the water dielectric constant of the diseased tissue, the length of the electrical path is greater than the physical length. Therefore, the temperature rapidly decreases from the surface of the insulating case 117 or 117A (ie, r = t0 in FIG. 9) toward the diseased tissue. In order to keep the temperature of the diseased tissue higher than Ts, which is the protein decomposition temperature, the surface temperature of the insulating case 117 at r = t0 is sufficiently high.

  In the case of the TTDP of the present invention, the sheath surface at ts has an electrical distance from the origin r = 0 (see FIG. 10) than the TTDP with the case 117 or 117A shown in FIG. 9 (hereinafter referred to as conventional TTDP). large. This is because the sapphire single body sheath 301 has a higher dielectric constant than the conventional insulation sheath 117. Since the surface of the TTDP 324 sheath has a large electrical distance from the surface of the antenna assembly 320, the surface temperature of the TTDP 324 can be suppressed even if the surface temperature of the antenna assembly TTDP 324 is significantly increased by RF power. That is, by suppressing the temperature of the tissue in the vicinity of the surface of TTDP so as not to significantly exceed the proteolysis temperature Ts, it is possible to prevent the tissue from being burnt even when heated by RF power.

  Since the position of the single body sheath 301 is r = ts, the RF absorption region where the temperature of the tissue is higher than Ts is narrower than when the conventional TTDP is used. However, if the RF power supplied to the TTDP by the single body sheath 301 is increased, the RF absorption region where the temperature is higher than Ts can be greatly expanded as compared with the RF absorption region of the insulating case using the conventional TTDP. . For example, increasing the RF power by 20% increases the RF absorption region by 60%.

  The heat source of the TTDP of the present invention is an electrically insulating gap 307 between the first electrode 308 and the second electrode 309. The thermal conductivity of sapphire used for the single body sheath 301 is 25 W / m / K, which is significantly higher than the thermal conductivity of PVC used for conventional TTDP. Accordingly, such heat generated in a region close to the electrically insulating gap 307 can be suppressed because the thermal conductivity in the axial direction of the single body sheath 301 is large. Accordingly, the distribution of the temperature T determined by the SAR is as shown by the solid line in FIG. In FIG. 19, the symbol TT indicates the thermotherapy temperature, and the symbol TD indicates the tissue temperature determined by SAR in Celsius. The dotted line in FIG. 19 is the same as the solid line showing the temperature distribution in the heat absorption of the tissue in FIG. It can be easily seen from FIG. 19 that sapphire has a high heat conduction effect. Since heat generated at a position near the electrically insulating gap 307 in the single body sheath 301 spreads along the single body sheath 301 in the axial direction of the TTDP, it can be uniformly heated in the longitudinal direction along the sheath direction.

The TTDP 324 according to the second object of the present invention is housed in a sapphire single body sheath 301 having a Mohs hardness of 9. This value is significantly higher than that of a conventional insulating sheath 117, for example, made of PTFE and having a Mohs hardness of 1 to 2. Because sapphire is very rigid, the single body sheath 301 does not deform and its dissection ability in living tissue does not decrease even in high temperature environments when RF power is supplied to the TTDP 324. Therefore, the surgical operation does not take time, and post-operative recovery is considerably accelerated.

In order to quantitatively analyze the dimensions of the TTDP 324, the dipole antenna structure will be discussed below from the viewpoint of electrical structure. Here, the dipole antenna included in TTDP 324 is formed from RF power transmission means such as a coaxial cable. The dipole antenna is a member of the antenna assembly, which is hereinafter referred to as an antenna assembly (320). In order to maximize the electric field strength in the electrically insulating gap 307 (as shown in FIGS. 16 to 18), the effective length of the first electrode 308 and the second electrode 309 needs to be ¼ wavelength. When L is the physical length of the first electrode, a is the physical length of the gap 307 in the longitudinal direction of the coaxial cable, and d is the diameter of the cylindrical dielectric insulator 303, the following equation is established.

Here, λ is a microwave wavelength (λ = 122.4 mm when a microwave of 2.45 GHz is used), and k is a shortening factor of a transmission wave propagating through the coaxial cable. Taking into account the dielectric constant ε _s of the side wall of the insulating case (when the insulating case is made of sapphire, the value of ε _s is about 11.6), the maximum power radiation from TTDP is obtained at a value within the following range: It is done.

  According to Equation (2), in the case of an insulating case made of sapphire, the power obtained from TTDP 324 is maximized when the length range of each electrode is = 4.9 to 9.7 mm. This length is much shorter than the 1/4 wavelength of microwave (30.6 mm). Therefore, if an antenna assembly having a short dimension is manufactured, a small probe can be realized. Thus, TTDP 324 would be more suitable for small tumor surgery than conventional TTMP.

  There are many advantages of the TTDP 324 of the present invention in addition to the advantages described above, which will be described through the description of the individual embodiments.

  The third object of the present invention is to solve the problem that there is only one radiation gap. For this problem, an arrayed antenna assembly configured with a plurality of electrically insulating gaps is used. These electrically insulating gaps are formed along the length of such an antenna assembly.

  For the third object of the present invention, the TTDP has an RF power transmission means (such as a coupling line) forming an antenna assembly and at least one head having a sharp side made of a hard material and the antenna assembly. And a sheath made of a hard material for housing the housing. The RF power transmission means is composed of at least one central conductor, a cylindrical dielectric insulator formed on the outer periphery of the central conductor, and an outer conductor. These all combine to form an antenna assembly, and the dipole antenna At least one of the first electrode formed from a part of the outer conductor and electrically connected to at least one central conductor, the second electrode formed from the other part of the outer conductor, And insulating means formed between the first electrode and the second electrode. The head is a head element composed of a side part and a flexible pipe, and the flexible pipe is connected to a coupling part formed in the head element. The sheath is made of a hard material such as sapphire and can be formed as a single body.

  As a structure of TTDP, the first dipole antenna is formed to have a structure in which the first center conductor and the second center conductor are connected to the first electrode and the second electrode through the power supply point, respectively, and at the power supply point, 1 electrode and 2nd electrode are formed in the arrangement which faces each other side by side, and the 2nd dipole antenna connects the 1st center conductor and the 2nd center conductor to the 2nd electrode and the 1st electrode via a power supply point, respectively A structure in which the first dipole antenna and the second dipole antenna are assembled so as to be formed in a structure and formed in an arrangement in which the first electrode and the second electrode face each other at the power supply point may be employed. In this case, the first electrode pair and the second electrode pair are alternately formed in the antenna assembly.

  Furthermore, a TTDP dipole antenna may be formed at the end of the coupled line. In this case, the dipole antenna is composed of a bent first electrode and a bent second electrode, and the external electrodes of these electrodes are electrically connected to the first electrode and the second electrode formed from an external conductor, respectively. Connected.

  Specifically, the antenna assembly 420 shown in FIGS. 20 and 21 has a configuration in which a plurality of antenna assemblies are arranged. In FIGS. 11 and 12, symbols L, E, and I represent effective 4/1 wavelength, electric field strength, and current strength, respectively. In FIGS. 11 and 12, the symbol TR represents the thermotherapy region. TI indicates the organization. The effective length of the microwave radiated from the antenna assembly 420 satisfies the relationship given by Equation (2). These are made from coupled lines 435 as shown in FIGS. Specifically, a plurality of pairs of the first electrode 408 and the second electrode 409 are formed, and the first center conductor 402a and the second center conductor 402b are provided on the coupling line 435 that is an RF power transmission cable. Yes. These central conductors are connected to the first electrode 408 and the second electrode 409 via the power supply points 434a and 434b so that the first electrode 408 and the second electrode 409 face each other at the power supply points 434a and 434b. Respectively. Each first electrode 408 and each second electrode 409 are insulated by an electrically insulating gap 407.

  The TTDP 424 of the present invention (as shown in FIGS. 24 to 26) has an antenna assembly 420 having at least a plurality of center conductors as the first center conductor 402a and the second center conductor 402b (the number of center conductors can be three or more). ), A cylindrical dielectric insulator 403 surrounding the outer periphery thereof, an outer conductor 404 formed on the surface of the cylindrical dielectric insulator 403, and a plurality of dipole antennas 436a and 436b that are members of the antenna assembly 420. Composed. In the dipole antennas 436a and 436b, both the first electrode 408 and the second electrode 409 are formed from a part of the outer conductor 404 and are insulated from each other. The first electrode 408 is connected to the first center conductor, and the second electrode 409 is connected to the second center conductor. Each first electrode 408 and each second electrode 409 are insulated by an electrically insulating gap 407. The outer conductor 404 has a substantially cylindrical shape. An antenna assembly 420 having a plurality of dipole antennas such as 436a, 436b, and 436c is housed in a single body sheath 401. TTDP 424 is provided by combining antenna assembly 420 and single body sheath 401 in this manner.

  The difference in antenna assembly 420 between FIG. 20 and FIG. 21 or between FIG. 24 and FIG. 26 is that each center conductor 402a and each center conductor 402b are connected and each first electrode 408 and each second electrode are connected. This is the difference between the power supply points 434 a and 434 b that connect the terminal 409. The length in the longitudinal direction of each first electrode 408 and each second electrode 409 corresponds to a quarter wavelength of the RF wave radiated from the TTDP 424. Since the plurality of dipole antennas are physically arranged in series, each first center conductor 402a is connected to each first electrode 408, and each second center conductor 402b is connected to each second electrode 409. In this configuration, the electric field and current of the RF power have nodes and antinodes at the power supply points 434a and 434b, respectively. This is because the RF wave becomes a stationary wave in the first electrode 408 and the second electrode that function as a pair of dipole antennas. Since these power supply points 434 a and 434 b are antinodes of current, the maximum current can be supplied to the outer conductor 404. As a result, the antenna assembly 420 can include a plurality of dipole antennas such as the first dipole antenna 436a, the second dipole antenna 436b, and the third dipole antenna 436c (in FIG. 24 to FIG. Showing). Since there are a plurality of dipole antennas as described above, uniform heating by RF power radiation is possible in the operation of a diseased tissue by thermotherapy.

  In the TTDP 424, the effective wavelength of the RF wave radiated from the dipole antennas 436a, 436b, 436c and the like in the coupled line 435 is considerably shortened due to mutual coupling between the central conductors 402a and 402b. Therefore, the physical length of the electrode can be shortened in the axial direction of the coupled line 435. Due to this shortening effect, the RF radiation source, which is an electrically insulating gap, is closely placed, the spacing per unit length of the TTDP 424 is reduced, the uniformity of heating is increased, and the diseased tissue is cauterized, thereby enabling surgical operation. The required time can be shortened.

For a conventional RF power transmission cable, a coaxial cable is used when the center conductor, the cylindrical dielectric insulator surrounding the outer periphery thereof, and the outer conductor are constituent elements. The axial length of the first electrode and the second electrode is a quarter of the effective wavelength λ _e of a conventional RF power transmission cable having a coaxial cable structure. The effective wavelength λ _e is expressed by the following equation (3).

Here, λ ₀ is the wavelength under vacuum, ε _r is the dielectric constant of the dielectric insulator, D is the diameter of the induction insulator, and a is the diameter of the central conductor. For example, as an actual numerical value, if the RF frequency is 2.45 GHz and the relative dielectric constant is 2.3, the length of the first electrode and the second electrode is 4.95 cm.

As for TTDP 424, as shown in FIG. 22 and FIG. 23, a coupling line 435 using two central conductors 402a and 402b, a cylindrical dielectric insulator 403, and an outer conductor 404 is used as an RF power transmission cable. Is done. The effective wavelength is further shortened by the coupling impedance between the center conductors 402a and 402b, and this coupling impedance is expressed by Expression (2).

Here, as shown in FIG. 23, d is a separation distance between the two central conductors 402a and 402b (a distance between the centers of the two). Therefore, the entire effective wavelength is expressed by the equation (5).

Here, k and α are each expressed by the following equations.

Formula (6) represents the shielding effect k with respect to the other center conductor of a certain center conductor. The value of k is usually from 0.3 to 0.5. Therefore, the shortening effect of the coupled line 435 is enhanced by the coefficient expressed by the equation (8).

  In the case of an insulating case where D = 1.1 mm and d / a = 0.2 mm / 0.18 mm, the value of the shortening effect is 0. 0 by substituting the value of Equation (8) into Equation (5). 28. Both the lengths of the first electrode and the second electrode are 2.4 cm. The same shortening effect can be obtained for the antenna assembly 420.

電極の長さは、下記の式の係数によって短縮できる。

The shortening effect of the plurality of center conductors is enhanced by the number of center conductors. For example, when three central conductors are used, the quarter wavelength is expressed by the following equation:

The length of the electrode can be shortened by the coefficient of the following equation.

  The shortening effect is not affected by the positions of the power supply points 434a and 434b. When there are three central conductors, each central conductor is used so that the two central conductors function as the first central conductor 402a and the remaining one central conductor functions as the second central conductor 402b. The two central conductors are selected from the three central conductors of each segment defined by two adjacent power supply points 434a.

  There are many advantages of the TTDP 424 of the present invention in addition to those described above, which will be described through the description of the individual embodiments.

  The fourth object of the present invention is to eliminate the lighthouse effect. For the fourth object of the present invention, the TTDP has an RF power transmission means (such as a connecting line) forming an antenna assembly, and at least one head having a sharp side and is made of a hard material, and the antenna assembly. And a sheath made of a hard material for housing the housing. An RF power transmission means (such as a connecting line) is composed of two central conductors, a cylindrical dielectric insulator that surrounds the outer periphery of the central conductor, and an outer conductor. These all combine to form an antenna assembly. At least one of the dipole antennas is formed from a part of the outer conductor and is electrically connected to one central conductor; a second electrode formed from another part of the outer conductor; And insulating means formed between the first electrode and the second electrode. In another dipole antenna formed at the end of the coupled line, a pair of two semicircular electrodes are provided around a cylindrical dielectric insulator. This cylindrical dielectric insulator has a structure in which the two semicircular electrodes are insulated through an electrical insulation gap, and the central conductor is electrically connected to the semicircular electrode. The head is a head element composed of a side part and a flexible pipe, and the flexible pipe is connected to a coupling part provided in the head element. The sheath can be made of a hard material such as sapphire and formed as a single body.

  In any dipole antenna disposed within the antenna assembly, the RF power radiation occurs from an electrically insulating gap formed between the first electrode and the second electrode. The first electrode and the second electrode are arranged in this way to form a dipole antenna. The coupling line can supply RF power to the dipole antenna at the tip by two central conductors, and the RF power transmitted to the dipole antenna at the tip is radiated therefrom. One or a plurality of dipole antennas formed on the coupled line can also have such an antenna structure.

  The above configuration is as shown in FIGS. The basic arrangement of the antenna assembly shown in FIGS. 27 to 29 is the same as that of the antenna assembly shown in FIGS. The detailed structure of this antenna configuration is similar to that shown in FIGS. However, the additional dipole antenna that is a member of the antenna assembly 520 is attached to the tip of the antenna assembly 520. A coupling line 435 shown in FIG. 22 is used to form dipole antennas 536a, 526b, and 536c via an outer conductor 504. The two central conductors 502a and 502b that transmit RF power are terminated with a front dipole antenna 538, so that they are equally excited there with other dipole antennas 536a, 536b, 536c, etc. that are members of the antenna assembly 520. It can be carried out. The effective electrical length of the front dipole antenna 538 to the nearest dipole antenna 536a when viewed from the final power supply points 534a and 534b is set to ½ wavelength. In the case of this physical length, reflection is suppressed by the termination treatment by the front dipole antenna 538, and RF power is transmitted to the front dipole antenna 538. As a result, the transmitted RF power is finally radiated from the front dipole antenna to the tissue region. Is done.

  There are many advantages of the TTDP 524 of the present invention in addition to those described above, which will be described through the description of the individual embodiments.

  The first to fourth objects of the present invention are to suitably implement TTDP which is far more advanced than conventional TTMP. As described below, a more suitable TTDP can be implemented by adding a temperature control function for the surface of the TTDP.

  When the insulating cases of the TTDPs 324, 424, and 524 are made of a sapphire single body sheath, the temperature control of the single body sheaths 301, 401, and 501 can be easily realized by circulating a coolant inside the sheath. In this way, the surface temperature of the single body sheaths 301, 401, and 501 is kept low even when the diseased tissue is heated by RF radiation from the TTDPs 324, 424, and 524. Therefore, the temperature of the diseased tissue is uniformly controlled, and as shown in FIG. 30, even when heated, the temperature causing necrosis of the diseased tissue does not greatly exceed. In FIG. 30, the symbol TT indicates the thermotherapy temperature, and the symbol TD indicates the tissue temperature determined by SAR in Celsius. The dotted line (translator note: dotted line in the original text, is this a solid line error? I'll translate it as it is for now) indicates that the temperature of the diseased tissue is kept low, and the dotted line is TTDP The temperature change of TTDP with respect to the distance from the surface of is shown. Since the temperature of the single body sheaths 301, 401 and 501 can be greatly lowered, the coagulation of the diseased tissue into which the TTDPs 324, 424 and 524 are inserted is suppressed, but the necrosis of these tissues is not inhibited, and the TTDP 324 is not inhibited. Sticking of 424 and 524 to the tissue is also prevented. This temperature control allows the surgeon to utilize high power RF, but it can heat the diseased tissue over a wider area in hyperthermia due to therapeutic effects such as tissue necrosis and prevention of TTDP anchoring to the tissue. It becomes like this.

  A fifth object of the present invention is to provide a drug transport / delivery function to TTDP so that the drug can be injected into a diseased tissue into which TTDP has been inserted percutaneously.

  Further, for the fifth object of the present invention, the single body sheath of the TTDP described in the first to fourth objects of the present invention has a hole penetrating its own side part formed in a sharp side part. Or has been pierced from its own head. A hole is drilled in the cylindrical surface of the sheath from the inside to the outside.

  The advantages of TTDP which is the fifth object of the present invention are as follows. For example, as shown in FIGS. 106 to 110, the drug can be injected and then dispersed inside the tissue. Alternatively, after being diffused, it can be activated by heating with RF power emitted from TTDP 624. This TTDP is physically provided with a route for such drug transport delivery. The drug is enclosed in a capsule made of a heat-sensitive gel. When heated by RF radiation, the gel capsule is broken and the drug is dispersed in the tumor. Alternatively, the drug changes the protein acceptability of cells of a specific tumor by heating, and as a result, the drug penetrates into cells that form part of the tumor. TTDP can be used to heat the diseased tissue, convert it to a drug, and inject a drug by percutaneous invasion of the tissue with a single operation. is there.

  There are many advantages of the TTDP 624 of the present invention in addition to those described above, which will be described through the description of the individual embodiments.

  A sixth object of the present invention is to provide a control system for a surgeon to safely use the TTDP disclosed in the first to fifth objects of the present invention. When the RF power is guided from the RF power source to the TTDP, it is necessary to prevent the power reflection at the TTDP from returning to the RF power source and to prevent the RF power from being unstable at the RF power source due to the return power. The control system is provided with a circulator to prevent RF power reflected at TTDP from returning to the RF power source. This control system controls the output level of the RF power, keeps the RF power at an appropriate level, and prevents overheating of the diseased tissue with the TTDP inserted.

  For the sixth object of the present invention, a therapeutic antenna probe system is selected from an RF power source, a circulator connected to the RF power source, and a TTDP according to the first to fifth objects of the present invention, and The TTDP is connected to the circulator via RF power transmission means such as a coaxial cable or a coupling line, and the RF power meter is connected to the RF power source via a power coupler. This RF power meter is connected to a controller that controls the RF power generated by the RF power supply by the output signal of the power meter.

  A heat transducer is incorporated into the therapeutic antenna probe system, and an output signal from the heat transducer is used as an input to the controller. As a result, the RF power generated by the RF power source is controlled by the output signal, The control of hyperthermia can also be improved.

  There are many advantages of the therapeutic antenna probe system of the sixth object of the present invention other than those described above, which will be explained through the description of the individual embodiments.

  The seventh object of the present invention is the therapeutic antenna probe system described in the sixth object of the present invention, and an anticancer drug having a specific medicinal effect selected from a group of medicinal effects that bring about an anticancer effect and an anticancer effect. , Is to be able to be used together.

  The advantages of the combined use of the therapeutic antenna probe system of the present invention and the anticancer agent are many in addition to the above-mentioned advantages, and these will be individually described through the description of the examples.

  Returning now to the drawings, a number of TTDP embodiments will be described in accordance with the first through sixth objects of the present invention.

  First, TTDP using a sapphire head and a flexible insulating tube for the first object of the present invention will be described below.

  13 to 15 show a preferred embodiment of the first object of the present invention. The antenna assembly includes a center conductor 202, a cylindrical dielectric insulator 203 formed on the outer periphery of the center conductor 202, and an outer conductor 204. A first electrode 208 formed from a part of the outer conductor 204 is a center conductor. A second electrode 209 that is electrically connected to 202 and formed from another part of the outer conductor 204 is electrically insulated from the first electrode 208. The first electrode 208 and the second electrode 209 form a dipole antenna that supplies RF power via an RF power transmission cable such as a coaxial cable. The center conductor 202, the cylindrical dielectric insulator 203, and the outer conductor 204 may be formed at the end of the coaxial cable. The TTDP is composed of an antenna assembly 220 and a sheath 230 characterized by a head 293 having a sharp side. The head 293 having a sharp side has a side 291 and a flexible insulating pipe. And a coupling portion 292 firmly coupled to the 294. About the side part 291 of the head 293 having a sharp side part, the tip part is made into a sharp blade by machining so that the tissue can be cut percutaneously and inserted into the inside.

  For the electrical insulation between the first electrode 208 and the second electrode 209, a part of the outer conductor 204 is cut out, and an electric insulating gap 207 is formed in the outer conductor 204 as a cut-out portion. The electrical connection between the central conductor 202 and the first electrode 208 is preferably performed via a conductive disc 210 as shown in FIGS. FIG. 13 is a cross-sectional view of the antenna assembly 220. FIG. 14 is another cross-sectional view of the antenna assembly 220 shown in FIG.

  Further, FIG. 15 shows another preferred embodiment according to the first object of the present invention. The electrical connection between the central conductor and the first electrode is performed by extending the central conductor 202 and bending it to make electrical contact with the first electrode 208. The conductive disc 210 is not used in this embodiment. Therefore, this embodiment is suitable for a case where the antenna assembly 220 requires fewer components than before.

  Further, FIG. 31 shows another preferred embodiment according to the present invention. The structure of the first electrode 208 and the second electrode 209 is made of a metal pipe or a metal plate wound around the outer conductor 204, and an additional electrode 218 that is in electrical contact with the first electrode 208 and the second electrode 209. 219 is added to the first electrode 208 and the second electrode 209. If the outer conductor 204 is made from a metal mesh (used for flexible coaxial cable) or a metal mesh solidified with tin or solder (used for semi-rigid coaxial cable), the electrodes 208 and 209 are too soft Therefore, the electrically insulating gap 207 cannot have an electrode structure with a clear cut line or a high physical accuracy. Therefore, the cut lines are clarified by the additional electrodes 218 and 219 instead of the first electrode 208 and the second electrode 209, and the electrically insulating gap 207 is electrically defined by the contour lines of these additional electrodes.

  32 to 34 show another preferred embodiment relating to the first object of the present invention. The electrical insulation gap provided to electrically insulate the first electrode 208 and the second electrode 209 is an electrical insulator between the two electrodes, and preferably is made of the same or similar material as the cylindrical dielectric insulator 203. Insert the insulation ring 211 to be made. When this insulating ring 211 is used, the dielectric breakdown voltage between the first electrode 208 and the second electrode 209 can be made higher than when the electrical insulating gap is provided by simple cutting. Therefore, the supply amount of RF power can be increased and the amount of RF power radiation can be increased. The distortion of the electrically insulating gap due to the bending force can be suppressed by the mechanical rigidity of the insulating ring 211 described above. Since the insulating ring 211 shown in FIG. 34 is embedded in the gap provided in the cylindrical dielectric insulator 203, unnecessary material on the edge line between the first electrode 208 and the second electrode 209 is removed, and the electric insulating gap is thus removed. The edge of the outer conductor 204 becomes clear.

  FIG. 35 and FIG. 36 show that the TTDP 224 is connected to an outer sheath 205 that covers and protects the coaxial cable 233 that forms the TTDP antenna assembly 220 shown in FIG. 14 and FIG. Each of the other preferred embodiments for one purpose is shown. By adding the additional contraction tube 212, the inside of the contraction tube 294 is hermetically sealed so as to be shielded from the outside air, so that it is possible to suppress leakage of germs from the antenna assembly 220. Of course, the outer sheath 205 may be directly covered by a heat shrink tube 294 that covers the TTDP antenna assembly 220, but in that configuration, no additional shrink tube 212 is required.

  FIG. 37 shows another one according to the first object of the present invention, characterized in that the heat shrinkable tube 294 is stretched to cover the exposed coaxial cable without using the additional shrinkable tube 212 shown in FIGS. The preferred embodiment of is shown. The heat-shrinkable tube 294 serves as a protective coating for the exposed coaxial cable, and can effectively prevent germs from leaking from the antenna assembly 220.

  When it is intended to facilitate handling of TTDP, it may be desirable to separate the TTDP configuration from a semi-rigid coaxial cable or a flexible coaxial cable for power transmission from the RF power source to the TTDP. is there. As shown in FIG. 38, the antenna assembly 220 is separated from the cable, but is coupled via a connector 214. RF power is supplied to connector 214 via an RF power transmission line. Since the TTDP 224 is disconnected from the cable, it can be sterilized in a container of a sterilization apparatus. This makes it possible to reduce the risk of postoperative infection.

  39 and 40 show another preferred implementation according to the first object of the invention, characterized in that an additional electrode 221 is added between the first electrode 208 and the second electrode 209. An example is shown. The distribution of the SAR extends at the additional electrode, allowing it to be cauterized over a long range along the TTDP 224, so that the depth at which the TTDP 224 is percutaneously inserted into the diseased tissue rather than multiple times of cauterization. Now you can do just one treatment.

  In FIGS. 41 to 48, a blade 230 of a head 293 having a sharp side part, which is composed of a side part 291 and a joint part closely contacting the heat shrinkable tube 294, forms a single-blade probe-shaped sheath 230. Another preferred embodiment according to the first object of the present invention will be described. The heat-shrinkable tube 294 is shown in a cross-sectional view so that the method of joining the coupling portion 292 to the heat-shrinkable tube 294 can be clearly understood. Both are slightly tapered, and the right-side diameter is slightly larger than the left-side diameter. Accordingly, since the sapphire head 293 can be firmly joined to the heat shrinkable tube 294 at the coupling portion 292, the sapphire head 293 is not left behind in the tissue when the heat shrinkable tube 294 is pulled out. Can be pulled out. The side portion 291 and the coupling portion 292 are made by cutting or grinding a lump of sapphire or rough sapphire. 41 and 42 show a linear cutting edge. 43 and 44 show a tapered cutting edge. 45 and 46 show a conical cutting edge. 47 and 48 show a sagittal blade.

  49 to 51 are characterized in that the cut surface 295 of the coupling portion 292 is in close contact with the heat-shrinkable tube, and the rotation of the side portion 291 in the tube is prevented. Another preferred embodiment relating to the first object of the present invention will be described. 50 and 51 show cross-sectional views of the coupling portion 292 with the side portion 291. FIG. The cut 296 shown in FIG. 51 is also suitable for the first object of the present invention, like the cut surfaces shown in FIGS.

  The second object of the present invention is to reduce temperature unevenness. The TTDP in which the antenna assembly is covered with a sapphire sheath for the second object of the present invention will be described below with reference to FIGS.

  The structure of the TTDP provided for the second object of the present invention is as shown in FIGS. The antenna assembly 320 includes a center conductor 302, a cylindrical dielectric insulator 303 formed on the outer periphery of the center conductor 302, and an outer conductor 304, and the first electrode 308 is formed from a part of the outer conductor 304. And the second electrode 309 is formed from another portion of the outer conductor 304 that is electrically insulated from the first electrode 308. The first electrode 308 and the second electrode 309 form a dipole antenna that receives supply of RF power via a coaxial cable. The center conductor 302, the cylindrical dielectric insulator 303, and the outer conductor 304 may be formed at the end of the coaxial cable. The TTDP 324 includes an antenna assembly 320 and a single body sheath 301 made of sapphire. The head of the single body sheath 301 is a sharp blade by machining, so that the tissue can be cut percutaneously and inserted therein.

  The first electrode 308 and the second electrode 309 are electrically insulated from each other by an electrically insulating gap 307 formed in the outer conductor 304 as a part of the outer conductor 304. The electrical connection between the center conductor 302 and the first electrode 308 is performed via a conductive disc 310 as shown in FIGS. FIG. 16 shows an external view of the antenna assembly 320 and a cross-sectional view of the single body sheath 301. Further, FIG. 17 shows a cross-sectional view of the antenna assembly shown in FIG.

  Further, FIG. 18 shows another preferred embodiment relating to the second object of the present invention. The electrical connection between the central conductor and the first electrode is performed by extending the central conductor 302 and bending it to make electrical contact with the first electrode 308. Since no conductive disc 310 is used, this embodiment is suitable when there are fewer components for the antenna assembly 320 than in the prior art.

  FIG. 52 further illustrates another preferred embodiment relating to the second object of the present invention. Additional electrodes 318 and 319 made from a metal pipe or from a metal plate wrapped around the outer conductor 304 are added to the first electrode 308 and the second electrode 309. If the outer conductor 304 is made from a metal mesh pipe (used for flexible coaxial cable) or a metal mesh solidified with tin or solder (used for semi-rigid coaxial cable), the electrodes 308 and 309 are too soft Since it cannot be mechanically accurately formed, the electrically insulating gap 307 cannot have an electrode structure with a clear cut line or high physical accuracy. Accordingly, the cut lines are clarified by the additional electrodes 318 and 319 instead of the first electrode 308 and the second electrode 309, and the shape of the electrically insulating gap 307 is electrically determined by the outline of these additional electrodes.

  53 to 55 show another preferred embodiment relating to the second object of the present invention. An insulating ring 311 made of the same or similar material as that of the cylindrical dielectric insulator 303 is packed in the electrically insulating gap provided to electrically insulate the first electrode 308 and the second electrode 309. When this insulating ring 311 is used, the dielectric breakdown voltage between the first electrode 308 and the second electrode 309 can be made higher than in the case where the electrical insulating gap is a part that is simply cut away. Therefore, the supply amount of RF power can be increased and the amount of RF power radiation can be increased. The distortion of the electrically insulating gap due to the bending force can be suppressed by the mechanical rigidity of the insulating ring 311 described above. 55 is embedded in a gap provided in the cylindrical dielectric insulator 303, so that unnecessary material on the edge line between the first electrode 308 and the second electrode 309 is removed, and the electric insulation gap is removed. The side of the outer conductor 304 becomes clear.

  56 and 57 show a TTDP 324 connected to an outer sheath 305 that covers and protects the coaxial cable 333 forming the TTDP antenna assembly 320 shown in FIGS. 17 and 54 at the tip. Other preferred embodiments relating to the second purpose will be described. By adding the additional contraction tube 312, the inside of the single body sheath 301 is hermetically sealed to be blocked from the outside air, and it is possible to suppress leakage of germs from the antenna assembly 320. Of course, the unitary sheath 301 containing the TTDP antenna assembly 320 is covered with an additional shrink tube 312 and an outer sheath 305, as shown in FIGS.

  58 is made from a metal pipe or from a metal plate wrapped around the outer conductor 304, and as shown in FIG. 52, the first electrodes 318 and 319 that are in electrical contact with the first electrode 308 and the second electrode 309 are shown in FIG. Another preferred embodiment according to the second object of the present invention, characterized by being added to the electrode 308 and the second electrode 309, is shown. The additional shrinkable tube 312 serves as a protective coating for the coaxial cable 333, and can effectively prevent germs from leaking from the antenna assembly 320.

  If it is intended to facilitate handling of TTDP, it may be desirable to make the TTDP configuration separate from a semi-rigid coaxial cable or from a flexible coaxial cable. As shown in FIG. 59, the antenna assembly 320 is separated from the cable, but is coupled via a connector 314. RF power is supplied to the connector 314 via an RF power transmission line. Since the TTDP 324 is disconnected from the cable, it can be sterilized in a container of a sterilizer. This makes it possible to reduce the risk of postoperative infection.

  60 and 61 show another preferred embodiment according to the second object of the present invention in which a third electrode 321 is added between the first electrode 308 and the second electrode 304. Since the SAR distribution is extended by the additional electrode, it is possible to cauterize over a long range along the TTDP 324, thereby causing the TTDP 324 to pass through the diseased tissue rather than performing ablation multiple times (see reference 3). Only one treatment is required at the depth of skin insertion (see Document 3).

  FIGS. 62 to 69 show the second object of the present invention in which the head of the single body sheath 301 has a sharp blade by machining, and the tissue can be cut percutaneously and inserted therein. The other suitable Example concerning is shown. The single body sheath 301 is made of sapphire in this preferred embodiment, but the shape of its cutting edge is linear as shown in FIGS. The shape of the cutting edge of the sapphire head 301 shown in FIGS. 64 and 65 is tapered. The shape of the cutting edge of the sapphire head 301 shown in FIGS. 66 and 67 is conical. The shape of the cutting edge of the sapphire head 301 shown in FIGS. 68 and 69 is a spear tip shape.

  The third object of the present invention is to solve the problem that there is only one radiation gap, that is, the problem that it is difficult to perform cauterization uniformly because only one gap is applied to the tissue and RF radiation is performed. It is to be. In the antenna structure provided here, a plurality of electrically insulating gaps are formed on the antenna for TTDP.

  24 to 26 show a series of preferred embodiments according to the third object of the present invention. In each electrode pair composed of the first electrode 408 and the second electrode 409, an electrically insulating gap 407 is provided by removing a part of the outer conductor 404 of the coupling line. FIG. 25 shows a front view of the antenna assembly. The first electrode 408, the second electrode 409, and the central conductors 402a and 402b are electrically connected within the structure of the coupled line 435, as shown in FIGS. However, the electrical connection method between the first center conductor 402a and the second center conductor 402b and the electrical connection method between the first electrode 408 and the second electrode 409 are different for each figure. Each pair of first electrode 408 and second electrode 409 forms dipole antennas 436a, 436b and 436c. The TTDP 424 includes an antenna assembly including dipole antennas 436a, 436b, and 426c, and a single body sheath 401 made of sapphire. About a sheath, what consists of an insulating material which combined the head made from sapphire and the pipe made from a polymer can also be used.

  The embodiment shown in FIG. 24 is based on a coupled line having a first center conductor 402a and a second center conductor 402b. The first electrode 408 and the second electrode 409 are connected to the first center conductor 402a and the second center conductor 402b via power supply points 434a and 434b, respectively, and face each other in proximity to the power supply points 434a and 434b. Yes. The embodiment shown in FIG. 26 is based on a coupled line having a first center conductor 402a and a second center conductor 402b. The first center conductor 402a and the second center conductor 402b are connected to the first electrode 408 and the second electrode 409 forming the first electrode pair via power supply points 403a and 403b, respectively. The two electrodes 409 face each other in the vicinity of the power supply points 403a and 403b. The first and second central conductors are connected to the second electrode 409 and the first electrode 408 forming the second electrode pair via power supply points 403b and 403a, respectively, and the first electrode 408 and the second electrode 409 are supplied with power. Faces close to the points 403b and 403a. The first electrode pair and the second electrode pair are alternately formed in the antenna assembly 420.

  Further, the single body sheath 301 can be made from sapphire. In addition, the sheath has a sapphire head composed of a side and a joint that is firmly bonded to a flexible insulating pipe (made of TEFLON ™ or polyethylene other than PTFE). Formed as a sheath. The side part of the head made of sapphire can be cut through the tissue percutaneously and inserted into the inside by making the tip part a sharp blade by machining.

  70-72 show another set of preferred embodiments according to the third object of the present invention. The coupling line 435 functions as an RF power transmission cable when connected to an RF power source, and is electrically connected to the two central conductors 402a and 402b. The antenna assembly 420 includes a plurality of dipole antenna pairs, and the electrical connection configuration connecting the first electrode and the second electrode and between the central conductors 402a and 402b is the same as the configuration shown in FIGS. It is. However, the electrical connection method between the first center conductor 402a and the second center conductor 402b and the electrical connection method between the first electrode and the second electrode are different for each figure. On the other hand, the coupled line 435 functions as a power transmission cable as shown in FIGS. 70 and 72 (both cross-sectional views of this series of preferred embodiments) and FIG. 71 (front view of this series of preferred embodiments). And covered with an outer coating 405. Adding an additional shrink tube 412 ensures hermeticity between the outer sheath 405 and the single body sheath 401. This highly airtight configuration prevents leakage of germs from the TTDP antenna assembly during surgery. Either electrical connection between the first electrode and the second electrode or between the central conductors can be made by the method shown in FIG. The additional shrink tube 412 may be a heat shrink tube and the outer coating 405 may be a non-shrink coating.

  FIGS. 73 to 79 relate to the third object of the present invention, and show another series of preferred embodiments, particularly relating to the connection between the two central conductors 402a and 402b and the outer conductor 404. FIG. Further, in the structure in which the first electrode 408 and the second electrode 409 are insulated via the electrically insulating gap 407, the electrical connection is established by connecting the first electrode 408 and the second electrode 409 to the central conductors 402a and 402b. Do. The first electrode and the second electrode are formed by cutting the coupling line 435 into small parts. The center conductors 402a and 402b are drawn out from the end faces of the first electrode 408 and the second electrode 409, which are small components facing each other. As shown in FIGS. 73 and 74, the electrically insulating gap 407 is provided by an insulating gap piece 437 that can be manufactured from a printed circuit board (abbreviated as PCB) having conductive layers 438a and 438b. The insulating gap piece 437 is formed in a disk shape similar to the cross-sectional shape of the coupling line 435, and has two through holes 439 through which the central conductors 402a and 402b pass. With respect to the conductive layers 438a and 438b of the insulating gap piece 437, a hole larger than the diameter of the through hole 439 is formed so that the central conductors 402a and 402b do not contact the conductor layers 438a and 438b in the through hole 439. To do. The first center conductor 402 a on the second electrode 409 side is drawn out in the direction of the conductive layer 438 a of the insulating gap piece 437 that contacts the first electrode 408. The second center conductor 402b on the first electrode 408 side is drawn out in the direction of the other conductive layer 438b of the insulating gap piece 437 in contact with the second electrode 409. As shown in FIGS. 73 and 74 (FIG. 73 is a perspective view and FIG. 74 is a cross-sectional view), the first center conductor 402a is applied to the second electrode 409, the second center conductor 402b is applied to the first electrode 408, and the solder 445 is provided. Soldered using. In order to shorten the longitudinal length of the electrically insulating gap 407 along the coupling line 435 so that it can be incorporated into the dipole antenna constituted by the first electrode 408 and the second electrode 409, the first center The torsional portion between the conductor 402a and the second center conductor 402b is drawn out from the outer conductor 404. When the twisted portion of the first central conductor 402a and the second central conductor 402b protrudes from the surface of the outer conductor 404, the protruding portion after being solidified with solder is removed as shown in FIG. In order to prevent the center conductors 402a and 402b from unnecessarily contacting the conductive layers 438a and 438b on the insulating gap piece 437, respectively, as shown in FIG. 76 (cross-sectional view), a part of the insulating gap piece 437 is electrically conductive. The layers 438a and 438b are partially left and soldered to the second electrode 409 and the first electrode 408, respectively, and unnecessary portions are removed. When the central conductors 402a and 402b, the insulating gap piece 437, and the first electrode 408 and the second electrode 409 are soldered, they are insulated with a dielectric insulating material (such as resin) different from the cylindrical dielectric insulator 403 of the coupled line 435. A piece 443 can be manufactured separately, and this insulating piece can be packed in the gap around the central conductors 402a and 402b as shown in FIG.

  Instead of using the insulating gap piece 437, the torsion part of the center conductors 402a and 402b is pulled out and soldered to the outer conductor 404, and the part of the torsion part that protrudes from the surface of the coupling line is removed, as shown in FIG. The insulating piece 443 is inserted or stuffed into a slot which is located between the first electrode 408 and the second electrode and accommodates the twisted portion.

  The electrically insulating gap 407 is provided between the first electrode 408 and the second electrode 409 by removing a part of the outer conductor 404. Therefore, it is necessary to provide a gap in the antenna assembly 420 for the electrical connections 434a and 434b between the central conductors 402a and 402b. In order to connect the electrical connections 434a and 434b satisfactorily, a slot 442 is provided on the surface of the outer conductor 404, and the center conductors 402a and 402b and the first electrode 408 and the second electrode 409 are securely connected as shown in FIG. Enable soldering.

  FIGS. 80 to 82 relate to the second object of the present invention, and show another series of preferred embodiments particularly relating to the connection between the antenna assembly 420 and the coupling line 435 functioning as a power transmission cable. . The coupling line 435 includes two central conductors 402a and 402b, a cylindrical dielectric insulator 403, and an outer conductor 404, and an antenna assembly 420 is provided at the end thereof. The coupling line 435 may be the same as a conventional RF power transmission cable. In the present embodiment, the first center conductor 402a and the second center conductor 402b are connected to each other. An insulating gap piece 440 having a conductive layer 438 c on one side is used for the electrically insulating gap 407. The insulating gap piece 440 is formed in a disk shape similar to the cross-sectional shape of the coupling line 435, and has two through holes 439 through which the central conductors 402a and 402b pass. The center conductor 402 a is drawn out from the first electrode 408 and soldered to the outer conductor 404 of the coupling line 435. The central conductor 402a of the coupling line 435 functioning as a power transmission cable and the central conductor 402a (see FIGS. 70 to 73) in the antenna assembly 420 are connected to the conductive layer 438c of the insulating gap piece 440, as shown in FIG. As described above, the first electrode is soldered with solder 445.

  In order to ensure electrical contact between the outer conductor 404 and the center conductor 402b of the first electrode 408 without unnecessary contact between the center conductors 402a and 402b and the conductive layer 438c of the insulating gap piece 440, the through hole 439 is provided. As shown in FIG. 81 (perspective view of the main part), most of the conductive layer 438c is removed and the conductive layer 438c facing the first electrode 408 is replaced with a hole larger than the diameter of the conductive layer 438c. A part is soldered to the first electrode 408. In order to fill a gap generated around the center conductor 402b when the center conductor 402b, the insulating gap piece 440 and the first electrode 408 are soldered, the insulating piece 443 is replaced with the insulating gap piece 440 as shown in FIG. And the first electrode 408. Since the two central conductors of the coupling line 435 are terminated at the connection point 434c of the two central conductors of the coupling line 435, RF power is supplied from the RF power source using the two central conductors as one central conductor. be able to.

  The conventional RF power transmission cable is a coaxial cable 435d composed of a single center conductor 402d, a cylindrical dielectric insulator 403 formed on the outer periphery of the single center conductor 402d, and an outer conductor 404 covering the periphery thereof. 83, it can be used as a power transmission cable in which the center conductor 402d is electrically connected to the first center conductor 402a and the outer conductor 404 is electrically connected to the second conductor 402b.

  As for the insulating gap piece 440, a conductive layer 438a may be provided in a portion in contact with the first electrode 408 and the second electrode 409 by soldering. Specifically, it is necessary to provide a gap in the antenna assembly 420 that accommodates the twisted portions of the conductors 402a and 402b. In order to make a good electrical connection, a slot 442 is provided on the surface of the outer conductor 404 so that the center conductors 402a and 402b and the first electrode 408 and the second electrode 409 can be reliably soldered as shown in FIG. .

  85-87 show another set of preferred embodiments regarding the third object of the present invention. The antenna assembly 420 is composed of dipole antennas 436a and 436b each composed of a first electrode 408 and a second electrode 409, and another electrode pair 436e in which each electrode is alternately bent in the longitudinal direction. The first electrode 408 and the second electrode 409 are formed from the outer conductor 404. The other outer conductors 408a and 409a are electrically connected to the first electrode 408 and the second electrode 409, respectively, and both electrodes are bent into the shapes shown in the cross-sectional views of FIGS. The structures of the dipole antennas 436a and 436b shown in FIGS. 85 and 87 are the same as the structures of the dipole antennas 436a and 436b shown in FIG. 24, and the structures of the electrode pairs 436b and 436c are as shown in FIG. is there. The power supply points 434b and 434e are defined such that the amount of RF power radiation to the outer tissue region where the TTDP 424 is inserted is greater in the electrically insulating gap 407a compared to other locations on each electrode of the antenna assembly 420. . The electrode pair 436e functions as a dipole antenna. The electrically insulating gap 407a is formed by removing a part of the outer conductor 404 of the coupling line 435, the two outer electrodes 408a and 409a are formed by bending on the outer conductor 404, and a part of the outer conductor is the first. As one electrode 408, another part of the outer conductor is formed as a second electrode 409. The electrical connection structure between the second central conductor 402b and the bent electrode 409a is the same as the electrical connection structure shown in FIGS. 73 to 79 for the second conductor 402a and the external conductor 404. The electrical connection between the first central conductor 402a and another external electrode 408a (bending structure) is made through a conductive disk 410 similar to the conductive disk 210 shown in FIG. FIG. 86 is a front view of the antenna assembly. As shown in FIGS. 85 and 87, the first electrode 408, the second electrode 409, and the central conductor are electrically connected inside the coupling line 435 (not particularly shown in FIGS. 85 to 87). However, the electrical connection method between the first center conductor 402a and the second center conductor 402b and the electrical connection method between the first electrode 408 and the second electrode 409 differ depending on the respective drawings. A pair of first electrode 408 and second electrode 409 form dipole antennas 436a and 436b, and another pair of external electrodes 409a and 408a (folded structure) form dipole antenna 436d. The TTDP 424 includes an antenna assembly 420 including dipole antennas 436a, 436b and 426d, and a single body sheath 401 made of an insulating material.

  FIGS. 88-90 show another set of preferred embodiments according to the third object of the present invention. The coupling line 435 functions as an RF power transmission cable when connected to an RF power source, and is electrically connected to the two central conductors 402a and 402b. The antenna assembly 420 includes a plurality of dipole antenna pairs 536a, 536b, 536c, and 536d. The electrical connection configuration connecting the first electrode 408 and the second electrode 409 and between the central conductors 402a and 402b is shown in FIG. 24 and the configuration shown in FIG. On the other hand, the coupled line 435 functions as a power transmission cable as shown in FIGS. 70 and 72 (both cross-sectional views of this series of preferred embodiments) and FIG. 71 (front view of this series of preferred embodiments). And covered with an outer coating 405. FIG. 89 is also a front view of this series of preferred embodiments. By adding an additional shrink tube 412, airtightness between the outer sheath 405 and the single body sheath 401 is ensured. This highly airtight configuration prevents leakage of germs from the TTDP antenna assembly during surgery. Whether the electrical connection between the first electrode 408 and the second electrode 409 or between the central conductors 402a and 402b is performed according to either FIG. 88 or FIG. 90, the method is shown in FIG. 70 or FIG. Same as shown. The additional shrink tube 412 may be a heat shrink tube and the outer coating 405 may be a non-shrink coating.

  The single body sheath 401 of the third object of the present invention is the same as the sheath 230 for the TTDP 224, for example, a sharp side part and a heat shrinkable tube, instead of the single body structure shown in FIG. The sheath may have a head 293 having sharp edges.

  27-29 show a series of preferred embodiments according to the fourth object of the present invention. The antenna assembly 520 has electrode pairs 537a and 537b forming a front dipole antenna 538 at its tip. Center conductors 502a and 502b are connected to electrode pairs 537a and 537b, respectively. The electrode pairs 537a and 537b share two electrically insulating gaps 507a and 539, whereby each electrode is insulated from each other. The RF electrode is emitted outward from the electrically insulating gap 539. Each gap is determined by forming an electrically insulating gap 507a and an electrically insulating gap 539 so that the impedances of the dipole antennas 536a, 536b, and 536c are the same. As a result, when RF power is radiated to the outer tissue region via dipole antennas 536a, 536b, and 536c, a portion of the RF power is radiated horizontally to the cylindrical tissue region, and the RF power is When radiated to the outer tissue region via the anterior dipole antenna 538, the remaining portion of RF power is radiated perpendicular to the anterior tissue region where the TTDP 524 is inserted. FIG. 91 is an enlarged view of the front dipole antenna 538. The electrically insulating gap 507 a is formed by removing a part of the outer conductor 504 of the coupling line 535. The two electrode pairs 537a and 537b are formed so that two semi-annular electrodes (each electrode is called a semi-annular electrode) are attached around the cylindrical dielectric insulator 503. The two electrically insulating gaps 539 are formed between a pair of electrodes 537a and 537b formed in a semi-annular shape. Center conductors 502a and 502b are electrically connected to electrode pairs 537a and 537b, respectively. The length along the axis of the coupling line 535 between the electrode pairs 537a and 537b is such that the effective length of the central conductors 502a and 502b from the closest power supply points 534a and 534b to the electrically insulating gap 539 is 1 / of the RF wave. It is determined to be two wavelengths. Then, a maximum current is generated in the electrical insulation gap 539 and a certain level of current is generated in the electrical insulation gap 507a, and the remaining RF power is radiated from the electrical insulation gap 539 and the electrical insulation gap 507a. The electrode pairs 537a and 537b are formed in accordance with a dipole antenna, particularly the front dipole antenna 538. Radiation from the electrically insulating gap 539 is particularly effective in reducing the lighthouse effect. FIG. 28 shows a front view of the antenna assembly and a cross-sectional view of the single body sheath 501. The first electrode 508, the second electrode 509, and the central conductors 502a and 502b are electrically connected within the coupling line 535 as shown in FIGS. However, the electrical connection method between the first center conductor 502a and the second center conductor 502b and the electrical connection method between the first electrode 508 and the second electrode 509 differ depending on the respective drawings. The first electrode 508 and the second electrode 509 forming a pair are formed according to the dipole antennas 536a, 536b and 536c, and the electrode pairs 537a and 537b are formed according to the dipole antenna 538. The TTDP 524 includes an antenna assembly 520 composed of dipole antennas 536a, 536b, 536c and 538, and a single body sheath 501 made of an insulating material such as sapphire.

  FIGS. 92 through 94 show another set of preferred embodiments regarding the fourth object of the present invention. The coupling line 535 functions as an RF power transmission cable when connected to an RF power source (not shown in the above figure), and is electrically connected to the two central conductors 502a and 502b. The antenna assembly 520 includes a plurality of dipole antenna pairs, and the electrical connection configuration connecting the first electrode and the second electrode and between the central conductors 502a and 502b is the same as the configuration shown in FIGS. is there. On the other hand, coupled line 535 is shown in FIGS. 92 and 94 (both cross-sectional views of this preferred embodiment) and FIG. 93 (front view of this preferred embodiment and cross-sectional view of unitary sheath 501). As shown, it functions as a power transmission cable and is covered by an outer sheath 405. By adding an additional shrink tube 512, airtightness between the outer sheath 505 and the single body sheath 501 is ensured. This highly airtight configuration prevents leakage of germs from the TTDP antenna assembly 520 during surgery. Whether the electrical connection between the first electrode 508 and the second electrode 509 or between the central conductors 502a and 502b is performed according to either FIG. 92 or FIG. 94, the method is shown in FIG. 70 or FIG. Same as shown. The additional shrink tube 512 may be a heat shrink tube and the outer coating 505 may be a non-shrink coating.

  95 to 97 show another series of preferred embodiments according to the fourth object of the present invention. The antenna assembly 520 has electrode pairs 537a and 537b forming a front dipole antenna 538 at its tip. Center conductors 502a and 502b are connected to electrode pairs 537a and 537b, respectively. The electrode pair 537a and 537b has a cup-like structure cut in half as shown in FIG. These have a front dipole antenna 538 as a component. The electrode pairs 537a and 537b are formed such that two semi-annular electrodes are attached around the cylindrical dielectric insulator 503. Center conductors 502a and 502b are electrically connected to electrode pairs 537a and 537b through conductive upper surfaces 540a and 540b and embedded solder 541, respectively. The electrode pairs 537a and 537b have two electrically insulating gaps 539 so that the electrodes are insulated from each other. RF power is radiated outward from these gaps. The electrically insulating gap 539 is determined by forming the electrically insulating gap 507a and the electrically insulating gap 539 so that the impedances of the dipole antennas 536a, 536b, 536c, and 536d are the same. As a result, when RF power is radiated to the outer tissue region via the dipole antenna 538, a portion of the RF power is radiated horizontally with respect to the cylindrical tissue region, and the rest of the RF power is transferred to the TTDP 524. Radiated perpendicular to the inserted anterior tissue region. FIG. 98 is an enlarged view of the front dipole antenna 538. The electrically insulating gap 507 a is formed by removing a part of the outer conductor 504 of the coupled line 533. The length of the pair of electrodes 537a and 537b along the axis of the coupled line 535 is such that the effective length of the center conductors 502a and 502b from the closest power supply points 534a and 534b to the electrically insulating gap 539 is RF power. To be ½ wavelength. Then, a maximum current is generated in the electrically insulating gap 539 and a certain level of current is generated in the electrically insulating gap 507a, and RF power different from the RF radiation power from the gap 507 is electrically connected to the electrically insulating gap 539. Radiated from the insulating gap 507a. Radiation from the electrically insulating gap 539 is particularly effective in reducing the lighthouse effect. FIG. 96 shows a front view of the antenna assembly and a cross-sectional view of a single body sheath. The first electrode 508, the second electrode 509, and the central conductors 502a and 502b are electrically connected within the coupling line 535 as shown in FIGS. However, the electrical connection method between the first center conductor 502a and the second center conductor 502b and the electrical connection method between the first electrode 508 and the second electrode 509 differ depending on the respective drawings. Each pair 536a, 536b, 536c and 536d consisting of the first electrode 508 and the second electrode 509 is a dipole antenna, and each of the electrode pairs 537a and 537b formed in a semi-annular shape is also a dipole antenna. The TTDP 524 includes an antenna assembly 520 including dipole antennas 536a, 536b, 536c and 536d and a front dipole antenna 538, and a single body sheath 501 made of an insulating material such as sapphire.

  99 to 101 show another series of preferred embodiments according to the fourth object of the present invention. The coupling line 535 that functions as an RF power transmission cable is connected to an RF power source that is electrically connected to the two central conductors 502a and 502b. The antenna assembly 520 is composed of a plurality of dipole antenna pairs, and the electrical connection configuration connecting the first electrode and the second electrode and between the central conductors 502a and 502b is the same as the configuration shown in FIGS. It is. On the other hand, the coupled line 535 is shown in FIGS. 70 and 72 (both cross-sectional views of this series of preferred embodiments) and FIG. 71 (front view of this series of preferred embodiments and cross-sectional view of the single body sheath 501). As shown, it functions as a power transmission cable and is covered by an outer sheath 505. By adding an additional shrink tube 512, airtightness between the outer sheath 505 and the single body sheath 501 is ensured. This highly airtight configuration prevents leakage of germs from the TTDP antenna assembly during surgery. Whether the electrical connection between the first electrode and the second electrode or between the central conductors is made according to either FIG. 88 or FIG. 90, the method is the same as that shown in FIG. 70 or FIG. . The additional shrink tube 512 may be a heat shrink tube and the outer coating 505 may be a non-shrink coating.

  When the TTDP insulation case is a single body sheath made of sapphire, the temperature control of sapphire can be easily realized by circulating a coolant in the sapphire. 102 and 103 further show a preferred embodiment according to the second object of the present invention. FIG. 103 is a cross-sectional view of TTDP 324 cut along line 103. The TTDP 324 has a tube 313 a for allowing the coolant to enter and exit from the inside of the TTDP 324, particularly in the gap between the inner surface of the single body sheath 301 and the antenna assembly 320. The groove 313c is provided on the inner surface of the single body sheath 301 as a path for facilitating the flow of liquid into the TTDP 324. The surface temperature of the single body sheath 301 is kept low even when the diseased tissue is heated by RF radiation by the TTDP 324. Therefore, the temperature of the diseased tissue is uniformly controlled and does not significantly exceed the temperature causing necrosis of the diseased tissue as shown in FIG. Therefore, coagulation of the diseased tissue in which TTDP 324 is inserted is suppressed, but necrosis of these tissues is not inhibited, and adhesion of TTDP 324 to the tissue is also prevented. This temperature control allows the surgeon to utilize high power RF, but it can heat the diseased tissue in a wider area than before by the therapeutic effect such as tissue necrosis and prevention of TTDP sticking to the tissue. Become. The same cooling means as the tubes 313a and 313b and the groove 313c in the single body sheath 301 can be applied to the other TTDPs, ie, TTDP 224, TTDP 424 and TTDP 524, which are the second, third and fourth purposes of the present invention. . The individual embodiments obtained for the second, third and fourth objects of the present invention by modification with the addition of the cooling means are not shown. This is because the modification for adding the tubes 313a and 313b and the groove 313c to allow the coolant to flow into the single body sheaths 301, 401 and 501 can be easily understood. TTDP 324 shown in FIGS. 56, 57, 58, 60 and 61, TTDP 424 shown in FIGS. 70, 72, 88 and 90, and TTDP 524 shown in FIGS. 92, 94, 99 and 101 can be modified to add a coolant circulation function. .

  The single-body sheath 501 of the fourth object of the present invention is the same as the sheath 230 for the TTDP 224, for example, a sharp side portion and a heat-shrinkable tube, instead of the single-body structure shown in FIG. It is good also as a sheath which consists of head 293 which has a sharp side.

  FIGS. 104 to 107 relate to the fifth object of the present invention, particularly preferably comprising a head 693 made of sapphire and having a sharp side or a single body sheath 301 made of sapphire and providing a drug delivery route. A series of preferred embodiments according to possible TTDP 624 are shown. 104 and 105 show the cutting edge of a single body sheath 301 with a hole drilled through the edge from a sharp tip. This hole is called a drug injection tip hole 618h, and the drug is injected from this hole into the diseased tissue into which the TTDP 624 is inserted. FIG. 106 shows TTDP 624 with drug delivery delivery function. This flow path is composed of a tube 613d provided in a gap between the single body sheath 601 and the antenna assembly 620, and a drug injection tip hole 618h. Other parts of this structure are the same as TTDP 324 shown in FIG. The drug is put into an injection means such as a syringe pump and supplied from the injection means. At that time, the drug is injected into the diseased tissue through the tube 613d which is a flow path. FIG. 107 shows a TTDP 624 having another type of drug delivery delivery function, specifically the ability to inject drugs horizontally into the diseased tissue. In addition to the tip hole 618h for injecting a drug provided at the cutting edge of the single body sheath 601, a hole extending from the inside to the outside is added to the cylindrical surface of the single body sheath 601. These holes are referred to as side holes 618a for drug injection, and the drug is allowed to flow from the inside of the single body sheath to the tissue in which TTDP 624 is inserted through these holes. The tube 613d is shortened so that the drug easily flows out from the side hole 618a for drug injection. Other parts of this structure are the same as TTDP 324 shown in FIG. In order to prevent contamination of the drug due to contact with the surface of the antenna assembly 620, the surface of the antenna assembly 620 may be coated with a photoresin or photopolymer to prevent ion elution from the metal surface of the antenna assembly 620 into the drug. . The feature of this drug transport delivery method is that the drug can be transported and delivered to the diseased tissue portion in a shorter time and uniformly than the TTDP shown in FIG. This difference does not only mean that this drug delivery / delivery function is excellent, but also means that it has the ability to select and use various capsules containing drugs from a wide variety of options.

  FIG. 108 shows another preferred embodiment relating to the fifth object of the present invention. The flow path is provided in the TTDP 624 having the heat shrinkable tube 694 in the sheath 630 instead of the single body sheath 601. The method for transporting and delivering the drug is the same as in the case of TTDP 624 shown in FIG.

  109 and 110 show another set of preferred embodiments according to the fifth object of the present invention. The TTDP 424 implemented for the third purpose of the present invention has a flow path for drug transport delivery. This flow path is composed of a tube 613d that passes through the single body sheath 601 and a tip hole 618h for injecting a drug that is formed at the cutting edge of the single body sheath 601.

  It is obvious that if the above-described flow path is modified, the same drug transport delivery function as the drug transport delivery function applied to the fourth object of the present invention can be implemented. However, these examples are not shown because modifications to add the above-described flow path to enable drug delivery delivery to the diseased tissue can be readily understood. TTDP 224 shown in FIGS. 35, 37, 39 and 40, TTDP 324 shown in FIGS. 56, 58, 60 and 61, TTDP 424 shown in FIGS. 70, 72, 88 and 90, and TTDP 524 shown in FIGS. 92, 94, 99 and 101 are modified. Thus, a function of circulating the coolant can be provided.

  Anticancer agents having an anticancer effect or an anticancer effect, such as mitomycin C, adriamycin, epirubicin, pirarubine, cisplatin, metholeate, 5-FU (FU or 5-FU), tegafur, UFT, carmoflu, doxyfluridine, TS- 1. To inject irinotecan, docetazel, lycovorin (all trademarks), etc. into a diseased tissue, a liquid phase carrier or a drug carrier, that is, a thermosensitive self-destructing drug carrier, a polymer micelle, a thermosensitive nano micelle, Temperature-sensitive hydrophobic / temperature-sensitive hydrophilic hydrogel particles, new polymerized micelles like drug carriers with reactive PEG (polyethylene glycol) chains encapsulating cisdichlorodiamineplatin, and block co-polymerization encapsulating cisdichlorodiamineplatin Combined micelles are used. Anticancer drugs do not directly attack normal cells. After the injection of the drug, when the tissue is heated by TTDP 624, decomposition of the carrier or carrier containing the anticancer drug starts. Thereafter, since the anticancer drug stays in the tumor, thermal necrosis due to TTDP624 and promotion of apoptosis by the drug simultaneously occur in various places and spread to the entire hyperthermia region. Therefore, the burden on the human body accompanying the implementation of cancer treatment is reduced. Other anticancer agents such as anticancer agent-DNA complexes, chemical anticancer agents, and high molecular anticancer agents can also be used in combination with the above encapsulation technique. When this TTDP624 is applied to cancer treatment, the effect of drug activity can be enhanced and sustained for a long time. As a result, a combined effect of the RF heating function of intracellular moisture and the function of injecting drugs into specific lesion cells can be expected.

  FIG. 111 shows a preferred embodiment according to the sixth object of the present invention. The therapeutic antenna probe system 731A includes an RF power source 721 (or called a microwave power source when microwave power having a microwave frequency is used), a circulator 722 connected to the RF power source 721, a coaxial cable 233, and 333 and coupling lines 435, 535 and 635, which are RF power transmission means such as a power transmission cable 729, a power meter 723 connected to the RF power source 721 via the power coupler 728, and a power meter 723 for measuring RF power And a controller 725 for controlling the RF power generated by the RF power source 721 according to the output signal. The purpose of the power combiner 728 is to monitor the RF power output intensity level from the RF power source 721, and the amount of RF power allocated from the RF power output to the power combiner 728 may be small. This is because the purpose of use of the power combiner 728 is to monitor the RF power output because it is proportional to the RF power output. Since the circulator 722 is connected to the load 744, the circulator 722 absorbs the reflected power from the TTDP 724 and does not flow back to the RF power source 721, and can stabilize the operation of the therapeutic antenna probe system 731.

  In the case of the therapeutic antenna probe system 731A described above, whether the power transmission cable 729 is connected to the TTDP 724 by the connector, the coaxial cables 233 and 333, or the coupling lines 435 and 535 depends on the type of TTDP TTDP 224, 324, 424. 524 or 624. The outer conductor of the transmission cable 729 is the first electrode 208, 308, 408, 508 or 608 of the coaxial cable 233 or 333 or the coupling line 435, 535 or 635 and finally the second electrode via the outer conductor. It is connected to the electrode 209, 309, 409, 509 or 609.

  If the therapeutic antenna probe system 731A includes a device separate from the TTDP 724, for example, a thermal converter 726 such as a thermocouple or a platinum temperature sensor, and the TTDP 724, the output power from the RF power source 721 is controlled. It is further desirable because coagulation due to overheating of the diseased tissue by RF power is prevented. In this control method, the RF power from the RF power source 721 can be maintained at an appropriate level during the treatment operation by monitoring the temperature of the diseased tissue heated by the TTDP 724.

  The RF power source 721 generates a microwave of 2.45 GHz or a so-called UHV of 945 MHz. When the frequency of the RF power is different, the electrical insulation gaps 207, 307, 407, 407a, 507, 507a, 539 and 607 at 945 MHz are modified to 2.6 times at 2.45 GHz. Must be.

  FIG. 112 shows another preferred embodiment relating to the sixth object of the present invention. The therapeutic antenna probe system 731B includes a TTDP 724, in which a heat converter 726a is incorporated. The heat converter 726a is preferably a thermocouple or a platinum temperature sensor. 113 to 116 show the first, third, and fourth aspects of the present invention, in which the heat converter 726a is inserted into the side 791, that is, the hole 726c formed in the tip of the sheath 730. Sectional drawing of various TTDP of the objective of is shown. The heat converter 726a and the side portion 793 are brought into contact with each other by heat conductive cement or heat sink oil. For other TTDPs, it is desirable to incorporate a heat converter 726a in the single body sheath 301, 401, 501, and 601.

  117 and 118 show another preferred embodiment relating to the sixth object of the present invention. The code | symbol P2 means a difference electric power signal. Specifically, an input signal to the power meter 723 is generated by output power from the RF power source 721 and power generated by the remaining ports of the circulator 722. By monitoring the power from this remaining port, the reflected power (P1) from the TTDP 724 can be measured. The differential power between the output power from the RF power source 721 and the reflected power (P1) can be measured. By controlling the output power (P0) of the RF power source 721 by the controller 725, the input (P0-P1) to the tissue is appropriately controlled.

  As a result, a signal of differential power between the output power (P0) of the RF power source 721 and the reflected power from the TTDP 724 is measured as the differential power (P2). This differential power (P2) is regarded as the power actually transmitted to the tissue in which the TTPD 724 is inserted. Therefore, by controlling the controller 725 with the signal of the differential power (P2), the RF power source 721 can output an appropriate level of RF power to the tissue.

  FIG. 119 shows another preferred embodiment relating to the sixth object of the present invention. This embodiment relates to a control sequence of RF power from the RF power source 721, characterized in that the signal of the heat converter 726 or 726a becomes an input to the controller 725 and controls ON / OFF switching of the RF power source 721. . Specifically, the output power from the RF power source 721 is expressed in the form of an intermittent power supply period and a non-power supply period represented by time t. The RF power level in the power supply period is constant, but if it is determined by monitoring the differential power (P2) that the RF power level exceeds the tissue overheating level, the power supply is stopped. The monitoring and control of the power supply period is performed by the output signal of the heat converter 726 or 726a. By using this control method, the temperature of the tissue in which TTDP 724 is inserted can be appropriately maintained within a range in which the lesion area is necrotized without causing local coagulation by thermotherapy.

  The lower limit TL of the control temperature set in the controller 725 is a temperature close to the proteolysis temperature (42.5 ° C.) at which cell necrosis begins. When the temperature becomes lower than the lower limit TL of the control temperature, a signal is sent from the heat converter 726, and the output of the RF power source 721 is resumed. The average output power from the RF power source 721 is 10 W, the duty cycle is 50% (the power supply period and the non-power supply period are both 50% of one repetition period), and the total RF power supply (load factor less than 50%) time Is 600 seconds, which is a cautery unit of surgery by this hyperthermia. When the temperature of the tissue in which the TTDP 724 is inserted exceeds 44 ° C., the controller 721 controls the RF power source 721 and shuts off its output.

  The upper limit TH of the control temperature is set by the controller 725. The output signal of the heat converter 726 or 726a is evaluated based on the control temperatures TL and TH. Once the output signal from the heat converter 726 or 726a indicates TH, the output power from the RF power source 721 is cut off as described above. Then, the temperature of the diseased tissue in which TTDP is inserted starts to decrease, and reaches the temperature of normal cells around the diseased tissue. When the temperature of the diseased tissue falls to TL, the controller 725 restarts the RF power source 721 and supplies output power. The controller 725 controls the power ON / OFF switching in the history sequence as described above.

  FIG. 119 shows an operation sequence of the controller 725 for controlling the RF power source 721. The symbol TMP represents the temperature in degrees Celsius, the symbol t represents the time in seconds, the symbols TL and TH represent the control temperature, the symbol OTT represents the thermal temperature output, the symbol PS represents the feeding period, and the symbol NPS represents the non-feeding period. To express. The output power level of the RF power is kept constant, and ON and OFF of the RF power output from TTDP is controlled to be 50% of one cycle. When the tissue temperature exceeds TH (44 ° C.), the power output is interrupted, and when the tissue temperature falls to TL (42.5 ° C.), the power output is resumed.

  FIG. 120 shows another preferred embodiment relating to the sixth object of the present invention. The code | symbol P2 represents a difference electric power signal. The therapeutic antenna probe system 732C includes a drug delivery delivery system. This system comprises an injection unit 730 containing a syringe pump for injecting a drug through a supply tube 713e, and this supply tube 713e is extended and connected to the tube 613a of the TTDP 624.

  The injection unit 730 supplies the drug to the diseased tissue in which the TTDP 724 described above having the drug injection tip hole 618h and the side hole 618a is inserted. About the injection | pouring unit 730, it is desirable to be able to perform manual operation or automatic operation | movement with an electric motor. Other parts of the therapeutic antenna probe system 731C are the same as those of the therapeutic antenna probe system 731A or 731B. In order to activate a drug to be injected into a diseased tissue, whether the drug injection into TTDP 724 is performed before, during, or after cauterization with TTDP 724 depends on the efficacy of an anticancer drug or the like.

  FIG. 121 shows another preferred embodiment relating to the sixth object of the present invention. The structure of this TTDP 724 is the same as the structure of the TTDP of the first object of the present invention, and the heat converter 726a is inserted into the hole 726c machined in the side 791, that is, the tip of the sheath 730. And The heat converter 726a and the side portion 793 are brought into contact with each other by heat conductive cement or heat sink oil. Furthermore, TTDP 724 has the same drug delivery delivery function as shown in FIG. This TTDP 724 makes it possible to monitor the temperature of the tissue in which the TTDP 724 has been inserted, and to deliver and deliver an anticancer drug with the tissue temperature being in an appropriate state.

  As for other TTDPs, it is desirable that the single body sheaths 301, 401, 501, and 601 can also incorporate the heat converter 726a.

  The structure of the single body sheath 301, 401, 501, 601 and 701 is a single structure having high mechanical durability against bending and pressing.

  The heat-shrinkable tube 294 and the single body sheath 301 may be partially or entirely colored. By visually confirming the color of TTDP, the treatment process and the surgical method can be managed.

  The scope of the present invention is not limited to the embodiments shown in the above drawings. Modifications that fall within the scope of the same concept as the concept of the present invention are also included in the same or equivalent invention as the present invention.

  The present invention has industrial utility. The first to sixth objects of the present invention are all implemented by industrial technology, and are applied to various industrial fields, specifically, medical technology related to a high-frequency treatment device, a high-frequency treatment system, and a method for using them. Can be applied.

For a better understanding of the objects and advantages of the present invention, reference should be made to the following detailed description taken together with the accompanying figures. Parts that are similar to each other are assigned similar reference numbers:
It is a side view of the electric probe for microtases. It is sectional drawing of the electric probe for microtases. It is sectional drawing of the electric probe for microtases with a bullet-shaped head. It is sectional drawing of the electric probe for microtases with a bullet-shaped head. It is a figure of the new thermotherapy probe which is the study object in literature 2. It is a figure of the new thermotherapy probe which is the study object in literature 2. It is a figure of the new thermotherapy probe which is the study object in literature 2. It is a figure of the new thermotherapy probe which is the study object in literature 2. It is a temperature distribution map defined by SAR in the tissue. It is a temperature distribution map defined by SAR in the tissue. It is a schematic diagram of the area | region where the thermotherapy by the thermotherapy probe of a prior art is effective. It is a schematic diagram of the area | region where the thermotherapy by the thermotherapy probe of a prior art is effective. It is sectional drawing of TTDP which concerns on the 1st objective of this invention. It is sectional drawing of TTDP which concerns on the 1st objective of this invention. It is sectional drawing of TTDP which concerns on the 1st objective of this invention. It is sectional drawing of TTDP which concerns on the 2nd objective of this invention. It is sectional drawing of TTDP which concerns on the 2nd objective of this invention. It is sectional drawing of TTDP which concerns on the 2nd objective of this invention. When using TTDP which concerns on the 2nd objective of this invention, it is a temperature distribution map in the structure | tissue determined by SAR. FIG. 5 is a cross-sectional view of a TTDP antenna assembly according to a third object of the present invention. FIG. 5 is a cross-sectional view of a TTDP antenna assembly according to a third object of the present invention. It is the perspective view and sectional drawing of the coupling line used for the 3rd objective of this invention. It is the perspective view and sectional drawing of the coupling line used for the 3rd objective of this invention. It is sectional drawing of TTDP which concerns on the 3rd objective of this invention. It is sectional drawing of TTDP which concerns on the 3rd objective of this invention. It is sectional drawing of TTDP which concerns on the 3rd objective of this invention. It is sectional drawing of TTDP which concerns on the 3rd objective of this invention. It is sectional drawing of TTDP which concerns on the 3rd objective of this invention. It is sectional drawing of TTDP which concerns on the 3rd objective of this invention. FIG. 5 is a temperature distribution diagram determined by SAR in a tissue when the TTDP according to the first to third objects of the present invention has a structure for circulating a coolant inside. FIG. 2 is a diagram of TTDP according to the first object of the present invention. FIG. 2 is a diagram of TTDP according to the first object of the present invention. FIG. 2 is a diagram of TTDP according to the first object of the present invention. FIG. 2 is a diagram of TTDP according to the first object of the present invention. FIG. 2 is a diagram of TTDP according to the first object of the present invention. FIG. 2 is a diagram of TTDP according to the first object of the present invention. FIG. 2 is a diagram of TTDP according to the first object of the present invention. FIG. 2 is a diagram of TTDP according to the first object of the present invention. FIG. 2 is a diagram of TTDP according to the first object of the present invention. FIG. 2 is a diagram of TTDP according to the first object of the present invention. It is a figure of the head of TTDP which concerns on the 1st objective of this invention. It is a figure of the head of TTDP which concerns on the 1st objective of this invention. It is a figure of the head of TTDP which concerns on the 1st objective of this invention. It is a figure of the head of TTDP which concerns on the 1st objective of this invention. It is a figure of the head of TTDP which concerns on the 1st objective of this invention. It is a figure of the head of TTDP which concerns on the 1st objective of this invention. It is a figure of the head of TTDP which concerns on the 1st objective of this invention. It is a figure of the head of TTDP which concerns on the 1st objective of this invention. It is a cut surface formed in the joint part of the TTDP head element. It is a figure which shows the cut surface and notch | incision formed in the coupling | bond part of the head element of TTDP. It is a figure which shows the cut surface and notch | incision formed in the coupling | bond part of the head element of TTDP. It is a figure of the modification which added the change to the antenna assembly in TTDP of the 2nd objective of this invention. It is a figure of the modification which added the change to the antenna assembly in TTDP of the 2nd objective of this invention. It is a figure of the modification which added the change to the antenna assembly in TTDP of the 2nd objective of this invention. It is a figure of the modification which added the change to the antenna assembly in TTDP of the 2nd objective of this invention. It is a figure of the modification which added the change to the antenna assembly in TTDP of the 2nd objective of this invention. It is a figure of the modification which added the change to the antenna assembly in TTDP of the 2nd objective of this invention. It is a figure of the modification which added the change to the antenna assembly in TTDP of the 2nd objective of this invention. It is a figure of the modification which added the change to the antenna assembly in TTDP of the 2nd objective of this invention. It is a figure of the modification which added the change to the antenna assembly in TTDP of the 2nd objective of this invention. It is a figure of the modification which added the change to the antenna assembly in TTDP of the 2nd objective of this invention. It is a figure which shows the shape of the head of TTDP which concerns on the 3rd objective of this invention. It is a figure which shows the shape of the head of TTDP which concerns on the 3rd objective of this invention. It is a figure which shows the shape of the head of TTDP which concerns on the 3rd objective of this invention. It is a figure which shows the shape of the head of TTDP which concerns on the 3rd objective of this invention. It is a figure which shows the shape of the head of TTDP which concerns on the 3rd objective of this invention. It is a figure which shows the shape of the head of TTDP which concerns on the 3rd objective of this invention. It is a figure which shows the shape of the head of TTDP which concerns on the 3rd objective of this invention. It is a figure which shows the shape of the head of TTDP which concerns on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing and the fragmentary perspective view of TTDP which concern on the 3rd objective of this invention. It is sectional drawing of the modification of TTDP which concerns on the 3rd objective of this invention. It is sectional drawing of the modification of TTDP which concerns on the 3rd objective of this invention. It is sectional drawing of the modification of TTDP which concerns on the 3rd objective of this invention. It is sectional drawing of the modification of TTDP which concerns on the 3rd objective of this invention. It is sectional drawing of the modification of TTDP which concerns on the 3rd objective of this invention. It is a perspective view of the additional dipole antenna of TTDP which concerns on the 4th objective of this invention. It is sectional drawing of TTDP which concerns on the 4th objective of this invention. It is sectional drawing of TTDP which concerns on the 4th objective of this invention. It is sectional drawing of TTDP which concerns on the 4th objective of this invention. It is sectional drawing of TTDP which concerns on the 4th objective of this invention. It is sectional drawing of TTDP which concerns on the 4th objective of this invention. It is sectional drawing of TTDP which concerns on the 4th objective of this invention. It is a perspective view of the additional dipole antenna of TTDP which concerns on the 4th objective of this invention. It is sectional drawing of TTDP which concerns on the 4th objective of this invention. It is sectional drawing of TTDP which concerns on the 4th objective of this invention. It is sectional drawing of TTDP which concerns on the 4th objective of this invention. It is sectional drawing of TTDP which incorporates the cooling fluid circulation structure based on the 1st objective of this invention. It is sectional drawing of TTDP which incorporates the cooling fluid circulation structure based on the 2nd objective of this invention. It is a figure of the head of TTDP which concerns on the 5th objective of this invention. It is a figure of the head of TTDP which concerns on the 5th objective of this invention. It is sectional drawing of TTDP which concerns on the 5th objective of this invention. It is sectional drawing of TTDP which concerns on the 5th objective of this invention. It is sectional drawing of TTDP which concerns on the 5th objective of this invention. It is sectional drawing of TTDP which concerns on the 5th objective of this invention. It is sectional drawing of TTDP which concerns on the 5th objective of this invention. It is a circuit diagram of the therapeutic antenna probe system which concerns on the 6th objective of this invention. It is a circuit diagram of the therapeutic antenna probe system which concerns on the 6th objective of this invention. It is sectional drawing of TTDP used for the therapeutic antenna probe system which concerns on the 6th objective of this invention. It is sectional drawing of TTDP used for the therapeutic antenna probe system which concerns on the 6th objective of this invention. It is sectional drawing of TTDP used for the therapeutic antenna probe system which concerns on the 6th objective of this invention. It is sectional drawing of TTDP used for the therapeutic antenna probe system which concerns on the 6th objective of this invention. It is a circuit diagram of the therapeutic antenna probe system which concerns on the 6th objective of this invention. It is a circuit diagram of the therapeutic antenna probe system which concerns on the 6th objective of this invention. It is a control sequence which shows the control method of the therapeutic antenna probe system which concerns on the 6th objective of this invention. It is a block diagram of the antenna probe system for treatment concerning the 6th object of the present invention. It is sectional drawing of TTDP used for the therapeutic antenna probe system which concerns on the 6th objective of this invention.

Explanation of symbols

102 Central conductor 103, 203, 403, 503 Cylindrical dielectric insulator 104 Outer conductor 105, 205, 305, 405, 505, 605 Outer coating 106 Bullet head 107, 207, 307, 407, 407a, 507, 507a, 607 Electrical insulation gap 108, 208, 308, 408, 508, 608 First electrode 109, 209, 309, 409, 509, 609 Second electrode 117 Conventional insulation sheath 117A Insulation case 202, 302 Central conductor 204, 304 , 404, 504 Outer conductor 208, 308, 408, 508, 608 First electrode 210, 310, 410 Conductive disk 211, 311 Insulating ring 212, 312, 412, 512 Additional heat shrink tube 214, 314 Connector 218, 219 318, 319, 618, 619 Additional electrode 220, 320, 420, 520, 620 Antenna assembly 224, 324, 424, 524, 624, 724 TTDP (dipole antenna for thermal therapy)
230, 630, 730 Sheath 233, 333, 435d, 533 Coaxial cable 291, 691, 791 Side 292, 692, 792 Joint 293, 693, 793 Head with sharp sides 294, 694, 794 Heat shrinkable tube 295 Cut surface 296 Cut 301, 401, 501, 601, 701 Single body sheath 303, 403, 503 Cylindrical dielectric insulator 313a, 613d Tube 313c Groove 320, 420, 520, 620, 720 Antenna assembly 321 Third electrode 402a, 502a First central conductor 402b, 502b Second central conductor 404, 504 External conductor 408a, 409a External electrode 434a, 434b, 534a, 534b Feed point 435, 535, 635 Coupling line 436a, 436b, 436c, 436d 536a, 526b, 536c, 536d Dipole antenna 436e Electrode pair 437, 440 Insulation gap piece 537a, 537b Electrode pair 438a, 438b, 438c Conductive layer 439 Through hole 538 Front dipole antenna 443 Insulation piece 434c Connection point 402d Single center conductor 442 Groove 436e Other electrode pair 539 Electrical insulation gap 540a, 540b Conductive end 541 Embedded soldering 613a Tube 618a, 618h Side hole and tip hole for drug injection 713e Supply tube 731A, 731B, 731C Therapeutic antenna probe system 721 RF Power supply 722 Circulator 729 Power transmission cable 723 Power meter 728 Power combiner 725 Controller 722 Circulator 729 Power transmission cable 731 Osamu Therapeutic antenna probe system 744 Load 726, 726a Thermal converter 731B Therapeutic antenna probe system 726c Hole 725 Controller 730 Injection unit

Claims (34)

High-frequency power transmission means in which a dipole antenna assembly is formed;
A therapeutic antenna probe comprising a sheath made of a hard material at least at the head, the head having a sharp side and enclosing the dipole antenna. The high-frequency power transmission means comprises at least one central conductor, a dielectric insulator formed around the central conductor, and an outer conductor,
All of these form the dipole antenna component,
One of the dipole antennas includes a first electrode formed from a part of the outer conductor and electrically connected to the at least one central conductor, and a second electrode formed from the other part of the outer conductor. An electrode and an insulating means formed between the first electrode and the second electrode,
The therapeutic antenna probe according to claim 1. The insulating means is formed by cutting out the outer conductor,
The therapeutic antenna probe according to claim 1 or 2. The insulating means is formed by an insulating ring filled between the first electrode and the second electrode,
The therapeutic antenna probe according to claim 1 or 2. The head is the head, and the head is composed of a side part and a flexible pipe coupled to a coupling part formed on the head.
The therapeutic antenna probe according to claim 1 or 2. The head is made of sapphire, and the flexible pipe is a heat shrinkable tube,
The therapeutic antenna probe according to claim 1, claim 2, and claim 5. The sheath is formed in a single body shape, and the hard material is sapphire,
The therapeutic antenna probe according to claim 1 or 2. All the central conductors are in the dipole antenna assembly and electrically connected to the section of the first electrode on the opposite side of the head,
The therapeutic antenna probe according to claim 2.

It is characterized by
The therapeutic antenna probe according to claim 2, 7, and 8. The other covering tube for covering the outside of the sheath covering the high-frequency power transmission means and the sheath is added,
The therapeutic antenna probe according to claim 2 to 5 and 8. The coupling part has a cut or cut surface around it,
The therapeutic antenna probe according to claim 5 and 6. The insulating means is an insulating gap piece, has a disk shape having the same diameter as the outer conductor, and has a hole through which the central conductor passes,
The therapeutic antenna probe according to any one of claims 2 to 3, and 5 to 8. The insulating gap piece has a conductive layer on at least one side, and one of the first electrode and the second electrode is in contact with the conductive layer,
The therapeutic antenna probe according to claim 12. The insulating means is an insulating gap piece, and the conductive layer of the insulating gap piece is connected in part to the first electrode and the second electrode by a soldering row,
The therapeutic antenna probe according to claim 12. A third electrode is formed between the first electrode and the second electrode,
The therapeutic antenna probe according to claim 2 and claims 5 to 7. The first electrode is connected to the central conductor via a disk having electrical conductivity,
The therapeutic antenna probe according to claim 2. An additional electrode electrically connected to the first electrode and the second electrode is added to the surfaces of the first electrode and the second electrode,
The therapeutic antenna probe according to claim 2. A connector is connected to the dipole antenna assembly, and high frequency power is supplied through the connector.
The therapeutic antenna probe according to claim 2. The high-frequency power transmission means includes at least first and second center conductors, a dielectric insulator formed around the at least first and second center conductors, and an external conductor, which is A coupling comprising at least one pair of one electrode and a second electrode formed with an insulating means interposed between the first electrode and the second electrode, thereby forming the at least one dipole antenna. A track,
In the dipole antenna, the first and second central conductors are connected to the first electrode and the second electrode via electrode supply points, respectively, and the first electrode and the second electrode are connected to the power supply point, respectively. In, it is formed as an arrangement facing each other,
The therapeutic antenna probe according to claim 2 and claims 5 to 8. The high-frequency power transmission means includes at least first and second center conductors, a dielectric insulator formed around the at least first and second center conductors, and an external conductor, which is The first dipole antenna and the second dipole antenna are configured by forming at least two pairs of one electrode and the second electrode together with the insulating means interposed between the first electrode and the second electrode. A coupling line comprising the external electrode,
The first dipole antenna has the first and second central conductors connected to the second electrode and the first electrode via electrode supply points, respectively, and the first electrode and the second electrode are respectively It is formed as an arrangement facing each other at the power supply point,
A second dipole antenna has the first and second central conductors connected to the second electrode and the first electrode via electrode supply points, respectively, and the first electrode and the second electrode are respectively It is formed as an arrangement facing each other at the power supply point,
The first electrode set of the first electrode and the second electrode and the second electrode set of the first electrode and the second electrode are alternately formed on the coupling line,
The therapeutic antenna probe according to claim 2 and claims 5 to 8. The dipole antenna formed at the end of the coupling line has a bent first electrode and a bent second electrode, which are electrically connected to the first electrode and the second electrode formed from the outer conductor, respectively. Having connected external electrodes,
The therapeutic antenna probe according to any one of claims 6 to 8, 19 and 20. The dipole antenna formed at the end of the coupling line is a set of two semi-circular electrodes surrounding the dielectric insulator, the semi-circular electrodes being isolated via an electrically insulating gap, The central conductor is connected to the semi-annular electrode,
The therapeutic antenna probe according to claim 19 and 20. The sheath is at least partially colored,
The therapeutic antenna probe according to claim 2 and claims 5 to 7. The sheath has a groove formed on the inner surface of the sheath,
The therapeutic antenna probe according to claim 7. The sheath has an opening hole that penetrates the tip and is drilled in a sharp side,
The therapeutic antenna probe according to claim 2 and claims 5 to 7. The sheath has a hole drilled from the inside to the outside on the cylindrical surface of the sheath,
The therapeutic antenna probe according to claim 7. A heat converter is added to the tip of the sheath,
The therapeutic antenna probe according to claim 2 and claims 5 to 7.   A high frequency power source, a circulator connected to the high frequency power source, and the circulator connected to the circulator via a high frequency power transmission means, and any of claims 18 to 24. The radio frequency power meter connected to the radio frequency power source via a power combiner, and the radio frequency power generated by the radio frequency power source is controlled by an output signal of the power meter. A therapeutic antenna probe system comprising a controller. The output signal of the high-frequency power meter is controlled by a differential power between the high-frequency power generated by the high-frequency power source and the reflected power that is a reflection from the therapeutic antenna probe obtained through the circulator. It is characterized by
30. The therapeutic antenna probe system according to claim 28. An output signal from a heat converter is input to the controller, and the high frequency power generated by the high frequency power source is further controlled by the output signal.
30. The therapeutic antenna probe system according to claim 28 and claim 29. A high frequency power source is provided so that the high frequency power generated by the high frequency power source alternately and repeatedly appears in a pulse form in a period in which there is a case where there is a supply of high frequency power and a case where there is no supply of the high frequency power. A high frequency power is set, and a predetermined period during which the high frequency power is supplied is controlled by the output from the thermal converter,
The therapeutic antenna probe system according to any one of claims 28 to 30.   32. The therapeutic antenna probe system according to claim 28, further comprising a syringe for injecting a medicine through the therapeutic antenna probe according to any one of claims 16 and 17. .   Mitomycin C, Adriamycin, Epirubicin, Pirarubicin, Cisplatin, Metorethete, 5-FU (FU, 5-FU,), Tegaflu, UFT, Carmoflu, Doxyfluridine, TS-1, Irinotecan, Docetazel, Lycovorin (all trademarks) One or more anticancer agents having an anticancer effect and a cancer suppression effect selected from the medicinal effects of a group of drugs are in a liquid phase, in a chemical carrier, or in a thermosensitive self-destructive body, polymerized micelle, Temperature-sensitive nano micelles, temperature-sensitive hydrophilic / hydrophobic hydrogel microparticles, drug carrier-like polymerized micelles with reactive PEG (polyethylene glycol) chains encapsulating cisdichlorodiamineplatin, or block co-polymerization encapsulating cisdichlorodiamineplatin Combined with a thermosensitive drug carrier with combined micelles and injected into a living organism. Using the use of therapeutic antenna probe system of claim 32.   The method according to claim 33, wherein the anticancer drug is supplied to the therapeutic antenna probe by injection means while supplying high frequency power from a high frequency power source.

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