JP5055500B2 - Therapeutic antenna probe, method of use thereof, and electromagnetic therapeutic system - Google Patents

Description

  The present invention relates to a therapeutic antenna probe that can be used in a treatment method for tumors and the like, a method of using the same, and an electromagnetic treatment system using the same.

  In the surgical treatment of various tumor diseases such as cancer, a local treatment method using an electromagnetic surgical device is widely used due to the advantage of quick postoperative recovery. In such an electromagnetic surgical device, a probe having a treatment electrode is inserted into a diseased tissue in a living body of a patient or a patient, and electromagnetic waves are induced or emitted from the treatment electrode. This electromagnetic wave causes treatment by causing dielectric heating and microwave absorption to the affected tissue.

There are two specific principles and actions for electromagnetic surgical instruments:
1) When performing dielectric heating on a diseased tissue, the treatment electrode is inserted into the diseased tissue without applying heat from outside the body. Then, an electromagnetic induction current is passed from the treatment electrode to the diseased tissue, and the living tissue is heated and coagulated. (The method is also called RFA (radio frequency ablation).)
2) When microwave absorption is performed on the diseased tissue, the treatment electrode is inserted into the diseased tissue without applying heat from outside the body. Then, microwaves with high electromagnetic wave absorption in water are radiated from the treatment electrode, and the diseased tissue containing water is heated to the proteolytic temperature to kill the living tissue. As the frequency of such a microwave, 945 MHz or 2.45 GHz is used. The method is also called hyperthermia or microwave coagulation therapy.

  Microtase (registered trademark) is known as a product related to the electromagnetic surgical instrument (Non-patent Document 1). This is used in the methods shown in 1) and 2) above. The treatment electrode possessed by the probe of Microtase (registered trademark) is a coaxial structure similar to a coaxial cable, specifically, a central conductor 2 and a cylindrical insulation formed on the outer periphery of the central conductor 2. It consists of a dielectric 3 and a cylindrical outer conductor 4 formed on the outer periphery of the insulating dielectric 3. The outer conductor 4 is formed as one electrode and the center conductor 2 is formed as the other electrode. Further, the tip shape of the probe is a shape that is easy to perform treatment, for example, FIGS. 1A and 1B (in FIG. 1, (a) is an external view thereof, and (b) is a cross-sectional view thereof). A puncture needle shape as shown, or a bullet-shaped head 6 as shown in FIGS. 2 (a) and 2 (b) ((a) is an external view thereof and (b) is a cross-sectional view thereof). There are known. Such an electrode structure is also called a therapeutic electrode probe. These are probes constituting a monopolar electrode in terms of electrical characteristics.

  In addition, a hyperthermia treatment device specialized in the above method 2), that is, microwave absorption has been recently announced (Non-patent Document 2). The probe of the hyperthermia treatment device is obtained by processing a coaxial structure included in a semi-rigid coaxial cable. Specifically, an electrically isolated gap 7 is formed for the outer conductor 4 of the coaxial structure. Then, an electrode that is a part of the outer conductor 4 and is electrically connected to the central conductor 2 is defined as a first electrode 8, and the other outer conductor 4 that is electrically isolated from the first electrode 8 by the gap 7 described above. Each electrode is formed using the electrode made of the second electrode 9 as an electrode. Therefore, the treatment electrode of the hyperthermia treatment device constitutes a dipole antenna. Hereinafter, such an electrode structure is referred to as a therapeutic antenna probe.

  As the tip shape of the therapeutic antenna probe announced in 2) above, FIG. 3 (a), (b) or FIG. 4 (a), (b) (both (a) is an external view thereof, (B) is a cross-sectional view thereof), and the outermost portion is covered with a case or coating (hereinafter simply referred to as case 17) made of hard vinyl chloride or PTFE (tetrafluoroethylene resin). It is a thing. The antenna structure includes a central conductor 2, a cylindrical insulating dielectric 3 formed on the outer periphery of the central conductor 2, and a cylindrical outer conductor 4 formed on the outer periphery of the insulating dielectric 3. And a first electrode 8 electrically connected to the central conductor 2, a second electrode 9 composed of another external conductor 4, and a first electrode 8. 4 (a) and 4 (b), for the first electrode 8, a part of the outer conductor 4 and the central conductor 2 are electrically connected via a disk-shaped conductor piece 10 to be completely cylindrical. Symmetrical.

Here, the treatment area | region of the lesioned tissue of said therapeutic electrode probe and therapeutic antenna probe is compared. The therapeutic electrode probe heats a diseased tissue around a region where an electromagnetic induction current flows between the center conductor 2 and the outer conductor 4 (see FIG. 5A). Therefore, the treatment area by the treatment electrode probe is narrow. On the other hand, in the therapeutic antenna probe, the first electrode 8 and the second electrode 9 constitute a dipole antenna, and the microwave radiation radiated from the dipole antenna and the region where the microwave is absorbed In this method, the diseased tissue is heated above the proteolytic temperature. Therefore, the treatment area for the diseased tissue by the treatment antenna probe is determined based on the microwave radiation area, and thus is wider than the case where the treatment electrode probe is used (see FIG. 5B). This is because, in the dipole antenna constituted by the first electrode 8 and the second electrode 9, the arrival area of the propagation wave extending in the horizontal direction from the coaxial center using the propagation wave of the TEM mode with respect to the coaxial direction as the wave source becomes the radiation region. .
Medicine 74, No. 6 (2004) 292-314 K. Saito et al., IEEE Trans. MTT, vol. 52, no.8, pp.1987-1991, Aug. 2004

  In the therapeutic electrode probe according to the prior art and the above-described therapeutic antenna probe, high-frequency power is fed between the central conductor 2 and the outer conductor 4 or to excite the dipole antenna (referred to as a feeding point). Since the induced current or electromagnetic wave is likely to be localized between the first electrode 8 and the second electrode 9, the temperature of the probe surface and the vicinity of the surface are far higher than the temperature of the other surface or the treatment target biological region. It tends to be hot. Among them, in the above-described method 1), when the probe surface temperature is higher, the diseased tissue can be heated and coagulated at a higher temperature, so this has not been a problem. However, in the above method 2), if the surface temperature of the probe is high, the diseased tissue is heated far beyond the proteolysis temperature, and the diseased tissue is cauterized. In particular, when the above method 2) is performed using a therapeutic antenna probe, microwave radiation is performed via the dipole antenna, so that the surface temperature of the probe near the gap between the two electrodes is There was a problem of becoming higher. When the therapeutic antenna probe becomes hot, the insulating dielectric 3 becomes soft and it becomes difficult to maintain the structure or shape of the therapeutic antenna probe. As a result, there is a problem that the electrical characteristics of the therapeutic antenna probe change during the operation.

  On the other hand, it is not impossible to reduce the input power to the therapeutic antenna probe in order to suppress the temperature rise of the therapeutic antenna probe. However, in this method, although the temperature of the probe surface is set to about the proteolysis temperature, the region that reaches the proteolysis temperature is significantly reduced in the peripheral region. Therefore, there is a problem that the advantage of the therapeutic antenna probe that heats and necroses a larger lesion tissue is destroyed.

The present invention has been made in view of such problems, and the object thereof is as follows:
The first is to provide a therapeutic antenna probe that can suppress a temperature difference between the surface temperature of the probe and the ambient temperature to be small.
Second, of the surface temperature of the therapeutic antenna probe, the surface temperature of the probe in the vicinity of the gap between the two electrodes having a high temperature can be suppressed to a lower level. Is to provide
The third is to provide a therapeutic antenna probe that can reduce the temperature difference between the surface temperature of the therapeutic antenna probe and the vicinity thereof and the proteolytic temperature of the diseased tissue,
A fourth object is to provide a therapeutic antenna probe that has a certain degree of hardness, can be easily punctured and inserted into a diseased tissue without thermal deformation, and can be easily operated.

<Basic configuration of therapeutic antenna probe of the present invention>
The therapeutic antenna probe 24 according to the present invention includes, for example, FIGS. 8A, 8B, and 8C (in FIG. 8, (a) shows a state in which the antenna portion is its appearance and the sheath portion is its cross section. (B) shows a cross section of both the antenna portion and the sheath portion, and (c) shows a cross section of another structure). That is, the center conductor 2, the cylindrical insulating dielectric 3 formed on the outer periphery of the central conductor 2, and the cylindrical outer conductor 4 formed on the outer periphery of the insulating dielectric 3, which are composed of a part thereof. And a second electrode 9 comprising a first electrode 8 electrically connected to the central conductor 2, another external conductor 4 electrically isolated from the first electrode 8, and a first electrode 8. And a sheath antenna 1 made of at least sapphire in which the second electrode 9 is housed, and a therapeutic antenna probe 24 comprising at least the sheath 1 made of sapphire, and the structure of the dipole antenna made of such a coaxial structure. It contains the body. 8A and 8B show the structure of a dipole antenna in which the central conductor 2 and the first electrode 8 are electrically connected via the conductor piece 10, and FIG. 8C shows the central conductor. 2 shows a dipole antenna structure in which a first electrode 8 and 2 are directly electrically connected.

<Basic Principle of Treatment Antenna Probe of the Present Invention>
The superior point of the therapeutic antenna probe 24 according to the present invention will be described in comparison with a conventional therapeutic antenna probe.

  First, for comparison, a therapeutic antenna probe 24 having a surface covered with a case 17 made of hard vinyl chloride or PTFE (for example, the one shown in FIG. 4; the case 17 is shown as being transparent). 6) shows the distribution of the temperature T determined from the SAR (Specific Absorption Rate) from the central portion in the axial direction of the gap 7 to the radial plane of the dipole antenna. The solid line portion indicates the temperature T of the living body portion, and the broken line indicates the temperature T in the case 17.

In this case, the relative dielectric constant of the material constituting the case 17, such as hard vinyl chloride or PTFE, is about 2.3 to 3.1 for the former and about 2.2 to 2.9 for the latter. It is overwhelmingly smaller than 80 which is the relative dielectric constant of water as a component. Therefore, the electrical length in the case 17 is as small as the thickness of the case 17 multiplied by the square root of the relative dielectric constant. Accordingly, the attenuation of electromagnetic waves in the case 17 is small. On the other hand, in the living body of a diseased tissue, the electrical length becomes longer than the physical length due to the effect of a large relative permittivity of the biological water. As a result, the above-described temperature T decreases rapidly from the surface position t ₀ of the case 17 toward the diseased tissue. On the other hand, if the power supply is increased to increase the temperature of the diseased tissue above T _S , the temperature near the surface position t ₀ of the case 17 increases.

On the other hand, in the therapeutic antenna probe 24 according to the present invention, the gap portion 7 of the therapeutic antenna probe 24 (for example, shown in FIGS. 8A, 8B, and 8C) housed in the sapphire sheath 1 is used. FIG. 6B shows the distribution of the temperature T determined from the SAR in the radial direction plane of the dipole antenna from the central portion in the cylindrical axial direction (hereinafter simply referred to as the axial direction). A solid line portion indicates the temperature T of the living body portion, and a broken line indicates the temperature T in the sheath 1. Here, the reference point (0 point) of the distance r in the radial direction of the therapeutic antenna probe 24 is the surface position of the outer conductor 4 (and hence the first electrode 8 or the second electrode 9). Further, T _S represents the 42 ° C. which is required for treatment by the hyperthermia process temperature (proteolytic temperature). Here, the relative dielectric constant of the sapphire constituting the sheath 1 has a high value of about 9.4 to 11.6 although it depends on the crystal orientation of the sapphire.

In the therapeutic antenna probe 24 according to the present invention, since the relative permittivity of the sheath 1 is large, the surface position of the sheath 1 is equivalent to the position t _S further toward the diseased tissue than t _{0 in} FIG. This is because it becomes a position. The position is different from the surface position t ₀ shown in FIG. 6A because of the difference in electrical length in the radial direction due to the large relative permittivity of the sapphire constituting the sheath 1. That is, the surface position is electrically separated from the feeding point of the dipole antenna. Therefore, the temperature around the probe be greater than T _S, it is possible to lower the surface temperature of the sheath 1, as shown in Figure 6 (b). Further, the temperature of the surface and its vicinity of a therapeutic antenna probe 24, it is possible to reduce the temperature difference between the protein decomposition temperature T _S of the diseased tissue.

Here, since the surface position of the sheath 1 is equivalent to the position t _S , when the input power to the therapeutic antenna probe 24 is the same, the therapeutic region of the therapeutic antenna probe 24, that is, the proteolysis temperature T The region where the temperature exceeds _S is slightly narrower than when the case 17 according to the conventional configuration is used. However, in this case, by slightly increasing the input power to the therapeutic antenna probe 24, the treatment area can be greatly increased while the surface temperature of the probe remains lower than before. For example, when the supplied power is increased by 20%, the treatment area increases by about 60%.

  In the therapeutic antenna probe 24 according to the present invention, a specific portion of the probe having a particularly high surface temperature, for example, from the vicinity of the gap 7 sandwiched between the first electrode 8 and the second electrode 9, through the sapphire material of the sheath 1. Heat is dissipated. Here, the thermal conductivity of sapphire has a high value of 25 W / m / K. This value is very high compared to the cover material according to the conventional structure, for example, 0.15 W / m / K of hard vinyl chloride and 0.25 W / m / K of PTFE. Therefore, even if electromagnetic heating proceeds at a specific location of the sheath 1 (for example, near the gap 7 of the outer conductor 4), heat near the surface of the probe easily escapes in the axial direction via the sheath 1.

  In consideration of the high thermal conductivity of the temperature T distribution determined from the SAR at this time, T is as shown by a solid line in FIG. Here, the dotted line is the SAR for the lesion tissue shown in FIG. 6B, that is, the temperature viewed from the amount of absorbed energy of the lesion tissue (that is, the temperature T determined from the SAR). Therefore, it can be seen that the heat dissipation effect of sapphire in the axial direction has the effect of lowering the surface temperature of the sheath 1. In addition, the heat of the surface of the therapeutic antenna probe 24 concentrated near the gap 7 of the outer conductor 4 is transmitted in the axial direction of the above-described sheath 1, so that the lesion tissue is also added in the axial direction. The region to be warmed spreads, and the thermal treatment can be performed uniformly over a wider region of the diseased tissue in the living body.

  The therapeutic antenna probe 24 according to the present invention is housed in the sapphire sheath 1, and the therapeutic antenna probe 24 has a high sapphire Mohs hardness of nine. This value is very high even when the material of the cover 17 according to the conventional configuration, for example, PTFE has a Mohs hardness of 1 to 2. Further, the sheath 1 is made of rigid sapphire, and does not soften and deform like the conventional therapeutic antenna probe 24 even if the surface temperature is increased by using the probe for thermal treatment. That is, since the therapeutic antenna probe 24 using the sheath 1 made of sapphire can be inserted into the center of the diseased tissue easily and accurately, the operation using this is therefore impossible. It can be done well and the postoperative recovery is fast.

  As described above, the present invention has a plurality of features, but still has many other features. These will be described in detail in the description of the examples below.

  The therapeutic antenna probe 24 according to the present embodiment has a structure as shown in FIGS. 8A, 8B, and 8C, for example. That is, the center conductor 2, the cylindrical insulating dielectric 3 formed on the outer periphery of the central conductor 2, and the cylindrical outer conductor 4 formed on the outer periphery of the insulating dielectric 3, which are composed of a part thereof. A first electrode 8 electrically connected to the central conductor 2, a second electrode 9 composed of another external conductor 4 electrically isolated from the first electrode 8, A therapeutic antenna probe 24 comprising at least a sapphire sheath 1 in which a second electrode 9 is housed, and a dipole antenna structure comprising such a coaxial structure in at least the sapphire sheath 1. Is stored. Here, the insulating dielectric 3 is made of Teflon (registered trademark) or PTFE. The outer conductor 4 is a drawn copper pipe, a copper wire knitted in a mesh shape, or a mesh obtained by melting and impregnating tin wax. Here, if the sheath 1 is formed integrally with sapphire, it can be formed with a small number of man-hours, which is preferable in terms of the manufacturing process.

  As shown in FIG. 8 (b), a conductor piece 10 electrically connected to both the first electrode 8 and the center conductor 2 and particularly preferably one that constitutes such connection via a disk-shaped conductor piece 10 is used. Formed. Alternatively, as shown in FIG. 8C, the first electrode 8 and the central conductor 2 are directly connected at the tip of the dipole antenna without using the conductor piece 10, and the connection is configured with a smaller number of parts. Formed a thing. In particular, in the former case, the distribution of electromagnetic radiation that is electrically cylindrical and axially symmetric can be created, and the region where the thermal treatment is performed on the diseased tissue can be made into a region shape with little bias.

  Further, the electrical isolation between the first electrode 8 and the second electrode 9 is between the first electrode 8 and the second electrode 9 as shown in FIGS. 8 (a), (b), and (c). The outer conductor 4 of the coaxial structure was formed by removing a part of the cylindrical axial direction (also referred to as the coaxial direction) over the axial circumferential surface to form the gap 7. This is because the dipole antenna can be easily configured.

の関係を満たす。
ここで、λは真空中の電磁波の波長（例えば、マイクロ波の周波数２.４５ＧＨｚのとき、λ＝１２２.４ｍｍ）、ｋは治療用アンテナプローブ２４の波長短縮率である。更に、鞘１による影響を考えるならば、

を満たすＬが治療用アンテナプローブ２４の最大の出力が得られる範囲となる。ここでε_Ｓは鞘１の側壁の比誘電率とする（ε_Ｓは鞘１の材質がサファイヤならば、その値は後述の如く最大で１１.６程度である）。従って、上式より、Ｌ＝４.９〜９.７ｍｍのときに、治療用アンテナプローブ２４の出力を最大化させることができる。 The therapeutic antenna probe 24 described above has a structure of a dipole antenna composed of a coaxial structure, and since the electric field is maximized in the gap 7, the electrical length of the first electrode 8 is radiated from the coaxial transmission end. It must be a quarter wave length of the electromagnetic wave. That is, when the axial length of the first electrode 8 is L, the cylindrical axial length of the gap 7 is a, and the diameter of the insulating dielectric 3 is d, L is

Satisfy the relationship.
Here, λ is the wavelength of electromagnetic waves in vacuum (for example, λ = 12.4 mm when the microwave frequency is 2.45 GHz), and k is the wavelength reduction rate of the therapeutic antenna probe 24. Furthermore, if we consider the effect of sheath 1,

L satisfying this is a range in which the maximum output of the therapeutic antenna probe 24 can be obtained. Here, ε _S is a relative dielectric constant of the side wall of the sheath 1 (ε _S is a maximum value of about 11.6 as will be described later if the material of the sheath 1 is sapphire). Therefore, from the above equation, when L = 4.9 to 9.7 mm, the output of the therapeutic antenna probe 24 can be maximized.

  In the present embodiment, the coaxial conductor outer conductor 4, the cylindrical insulating dielectric 3, and the central conductor 2 constituting the therapeutic antenna probe 24 have a characteristic impedance for electromagnetic wave transmission of 50 ohms. In this case, k = 0.67 is obtained in the same manner as the wavelength shortening rate of the coaxial cable. Therefore, since the dimensions in this example are a = 1 mm and d = 1.14 mm, L = 9.7 mm.

  The first electrode 8 and the second electrode 9 described above are both formed from the outer conductor 4 having a coaxial structure. As such a coaxial structure, a normal flexible coaxial cable can be used in the therapeutic antenna probe 24 in addition to the conventional semi-rigid coaxial cable. This is because the sapphire sheath 1 has higher rigidity than conventional PTFE. In this case, since the coaxial cable itself is processed into the first electrode 8 and the second electrode 9, an additional coaxial cable that connects the therapeutic antenna probe 24 and the high frequency power source 21 for excitation is unnecessary. As a result, the number of parts of the system using the therapeutic antenna probe 24 can be reduced, and a problem of high-frequency power coupling at the connection portion can be prevented.

の関係を満足する必要がある。最大の電磁放射を得るためである。また、図９（ａ）、（ｂ）においては、導体片１０が用いられているが、中心導体２を直接外部導体４と電気的に接続して、導体片１０を省く構成としても良い。 This embodiment is a therapeutic antenna probe 24 illustrated in FIG. 9A (a cross-sectional view of the main part). That is, the therapeutic antenna probe 24 according to the present invention shown in the first embodiment is one in which a dipole antenna structure made of a coaxial structure is housed in a sheath 1 made of at least sapphire. However, it may be difficult to maintain the dimension of the gap 7 of the coaxial structure with high accuracy. For example, when the therapeutic antenna probe 24 is made using a coaxial cable, the outer conductor 4 is made of a copper wire knitted in a mesh shape, or a brazed tin of the mesh knitted material. Since it is configured, it is difficult to form the dimension of the gap portion 7 with high accuracy because the end side thereof is easily formed into an unclear annular shape due to burrs. On the other hand, as shown in FIG. 9A, either or all of the first electrode 8 and the second electrode 9 are electrically connected to the outer conductor 4 and are on the surface of the outer conductor 4. The electrode formed by the formed conductor layer 19 was used. As a result, the gap portion 7 can be replaced with the gap portion 7 of the external conductor 4 and the edge thereof can be the gap portion 7, so that the problem of dimensional accuracy due to the above-described burr hardly occurs. Therefore, the therapeutic antenna probe 24 having stable electrical characteristics can be manufactured. The conductor layer 19 can also be formed by a conductor pipe or a conductor plate wound around the surface of the outer conductor 4. Further, as shown in FIG. 19B (which is a cross-sectional view of the main part), a conductor layer 19 electrically connected to the outer conductor 4 is formed on the surface of the outer conductor 4 corresponding to the first electrode 8. It is good also as a shape extended from the body 4 to the axial direction of the cylindrical shape. In this case, the length L ′ of the conductor layer 19 formed by being electrically connected to the surface of the outer conductor 4 corresponding to the first electrode 8 is the rule of the length of the quarter wavelength of the radiated electromagnetic wave. To protect,

It is necessary to satisfy the relationship. This is to obtain maximum electromagnetic radiation. 9A and 9B, the conductor piece 10 is used. However, the conductor piece 10 may be omitted by electrically connecting the central conductor 2 directly to the external conductor 4. FIG.

  In order to introduce high-frequency power into a living tissue using the therapeutic antenna probe 24 shown in the first and second embodiments, to keep the temperature of the living tissue near the surface of the probe at 44 degrees, and to necrotize the diseased tissue. When the region that maintains the therapeutic temperature of 42 degrees, which is the proteolysis temperature of the living body, is secured to the living tissue that is 3.5 cm away from the surface, the temperature of the living tissue site that is the highest temperature in that region is 44. I was able to get 5 degrees. Therefore, it can be seen that by using the therapeutic antenna probe 24 according to the present invention, a wide lesion tissue region can be subjected to thermal treatment at a uniform temperature.

  Moreover, the therapeutic antenna probe 24 shown in Example 1 and Example 2 has a high sapphire Mohs hardness of 9. This value is very high even when the material of the cover 17 according to the conventional configuration, for example, PTFE has a Mohs hardness of 1 to 2. Furthermore, the sheath 1 is made of rigid sapphire, and does not soften even if its surface temperature increases due to the use of the probe for thermotherapy. That is, the therapeutic antenna probe 24 using the sheath 1 made of sapphire can be inserted into the center of the lesion tissue easily and accurately, so that an appropriate probe for the lesion tissue region can be obtained. In this position, the entire region can be treated with heat evenly. Therefore, surgery using this could be done well and post-operative recovery was quick. This can also be understood from the fact that ruby colored sapphire is a material used for a surgical knife.

  Further, the therapeutic antenna probe 24 has a lower sapphire surface wettability with respect to water and fat in the living body than a material of the cover 17 having a conventional configuration, for example, hard vinyl chloride or PTFE. In addition, since the surface of the probe is not easily heated, blood coagulation and adhesion to the surface is reduced. Therefore, the residue of the living tissue including the diseased tissue is less likely to adhere to the surface of the therapeutic antenna probe 24. Accordingly, the probe can be easily pulled out from the living body, particularly after surgery, and it is difficult to cause laceration on the diseased tissue in contact with the probe.

  Further, since the sheath 1 of the therapeutic antenna probe 24 is transparent, the unique color of blood or lymph can be easily discriminated by passing through the backlight. As a result, it was possible for the surgeon to easily confirm whether or not normal treatment could be performed from that color.

  10 (a), (b), and (c) ((a) in FIG. 10 (a) shows the state that the antenna portion is the appearance and the sheath 1 is the cross section). (B) shows a cross section of both the antenna portion and the sheath 1, and (c) shows a cross section of another structure), and has the same or substantially the same dielectric constant as that of the insulating dielectric 3. The electrical insulation was more reliably performed by adopting a structure in which the collar 11 made of the material was fitted in the gap 7. Further, the gap portion 7 may be formed by removing a part of the insulating dielectric 3 in addition to the outer conductor 4, and in this case, the collar 11 becomes thick (FIG. 10C). By using the collar 11, the electrical variation of the gap 7 between the first electrode 8 and the second electrode 9 due to the above-described burr can be suppressed, and the therapeutic antenna probe 24 having stable electrical characteristics is manufactured. be able to. The conductor layer 19 can also be formed by a conductor pipe or a conductor plate wound around the surface of the external conductor 4.

  In the therapeutic antenna probe 24 according to the present embodiment, the outer surface of the sheath 1 is seen in FIGS. 11 (a) and 11 (b) (both in FIGS. 11 (a) and 11 (b) show cross sections). A sealing tube 12 that is indirectly attached to the (side wall surface) and the surface of the outer conductor 4 via a jacket 5 that covers the outer conductor 4 was further provided.

  In this example, a semi-rigid coaxial tube or a flexible coaxial cable was used as the coaxial structure. The jacket 5 in the portion of the coaxial structure housed in the sheath 1 was peeled off and removed. And in the example shown to Fig.11 (a), the gap | interval part 7 was formed in the outer conductor 4 of a coaxial structure. On the other hand, in the example shown in FIG. 11B, the collar 11 having substantially the same dielectric constant as that of the insulating dielectric 3 of the coaxial structure shown in the third embodiment is fitted in the gap portion 7. Moreover, the front-end | tip of the said coaxial structure electrically connected the 1st electrode 8 and the center conductor 2 via the conductor piece 10 which consists of a copper body board. And the joint of the said jacket 5 and the sheath 1 was sealed using the sealing tube 12 with high heat-shrinkability. The sealing tube 12 can seal the sheath 1 and prevent invasion of germs from the inside of the sheath 1 to the outside lesioned tissue side. Of course, when using a semi-rigid coaxial tube or a flexible coaxial cable in which the jacket 5 is not used, the sealing tube 12 directly covers and seals the sheath 1 and these coaxial tubes or coaxial cables.

  As the structure of the dipole antenna of the therapeutic antenna probe 24 according to the present embodiment, the dipole antenna and a semi-rigid coaxial tube or a flexible coaxial cable for supplying high-frequency power were separated from each other. In this case, the dipole antenna may be connected to the high frequency power source 21 through the high frequency coaxial cable or the high frequency coaxial tube via the coaxial connector 14 at the opposite end of the dipole antenna and outside the sheath 1 (see FIG. 12). By doing so, the treatment antenna probe 24 according to the present invention is divided by the coaxial connector 14 from a long semi-rigid coaxial tube or a flexible coaxial cable for supplying high-frequency power, and the operation has a convenient length for handling. Can be treated as an instrument. As such a coaxial connector 14, an SMA connector or a BNC connector can be used.

  The above-described dipole antenna used in the present invention is composed of only the first electrode 8 and the second electrode 9. In this case, it is known that the SAR changes depending on the depth at which the therapeutic antenna probe 24 is inserted into a living tissue (described in FIG. 3 of Non-Patent Document 2 and related matters). On the other hand, by providing a third electrode 20 serving as a buffer electrode between the first electrode 8 and the second electrode 9 so as to be electrically isolated from the first electrode 8 and the second electrode 9, a therapeutic antenna is provided. It is known that the SAR is not significantly affected by the insertion depth of the probe 24 into the living tissue. Therefore, in this embodiment, a dipole antenna having the same configuration is used. As a result, it is possible to realize the therapeutic antenna probe 24 that can perform the thermal treatment without being affected by the depth of the diseased tissue. There are two methods of electrical isolation, the method using the simple gap 7 (see FIG. 13A) already described and the method using the collar 11 (see FIG. 13B). A plurality of third electrodes 20 can be used as buffer electrodes between the first electrode 8 and the second electrode 9. This is because the influence of the SAR on the insertion depth of the therapeutic antenna probe 24 into the living tissue is further reduced. Of course, in order to increase the accuracy of the gap 7, those electrodes that are electrically connected to the outer conductor 4 and formed by the conductor layer 19 formed on the surface of the outer conductor 4 may be used.

  In this embodiment, as shown in FIG. 14, after forming the head element 15 constituting the tip and the pipe element 16 constituting the side wall portion for housing the first electrode 8 and the second electrode 9, These were brazed with nickel or the like to form a sheath 1 similar to the integral structure. Here, both the head element 15 and the pipe element 16 may be made of sapphire, but the head element 15 may be made of a material different from the colorless and transparent sapphire. That is, sapphire is preferable as the material of the pipe element 16, but diamond having high wear resistance and colored sapphire are preferable examples of the material of the head element 15.

  For example, in the configuration using diamond with high wear resistance as the head element 15, it can be used even if the lesion tissue to be operated is hard, such as cartilage tissue. As described above, by dividing the sheath 1 into the head element 15 and the pipe element 16, it is possible to provide an appropriate therapeutic antenna probe 24 with high selectivity according to the type of the diseased tissue.

  Further, in the configuration using sapphire colored in green as the head element 15, when the sheath 1 is extracted after performing the thermal treatment, it is possible to easily determine whether or not the blood adheres to the head element 15 and thereby cause lesions. It was possible to use it as a measure of the degree of biological destruction of the body and the suitability of thermotherapy. Further, by selecting a colorless and transparent material as the pipe element 16, the color of blood or lymph fluid adhering to the pipe element 16 can be easily determined, and the progress of the lesion can be confirmed and appropriate treatment for the thermal treatment can be performed. It was also possible to confirm and evaluate.

  In this embodiment, the distal end portion of the integrally formed sheath 1 or the distal end portion of the head element 15 has a sharp shape, for example, a knife edge shape, so that the therapeutic antenna probe 24 can be easily inserted into a diseased tissue in the living body. (FIGS. 15A and 15B). Further, the tip portion may be processed into a conical shape (FIG. 15C), or a curved knife shape processed to obtain a knife edge over the entire cross-section of the tip portion (FIG. 15D). Since the distal end portion is configured to have a sharp shape, the knife-edge effect makes it possible to cut the fibrous lesion tissue in the living body and insert it as it is, so that the therapeutic antenna probe 24 is operated. Excellent as a tool. Here, the sharp shape means a sharp shape that allows the surgeon to puncture and insert the therapeutic antenna probe 24 into the living body by hand without using any other jig that exhibits pressure. Say.

  In this embodiment, a sheath 1 made of colored sapphire is used (there is no particular drawing). Sapphire matrix is usually colorless and transparent. As a coloring method, a small amount of a metal additive such as nickel, chromium, titanium, or the like is added to alumina, which is a raw material of sapphire, when the sapphire single crystal serving as the material of the sheath 1 is grown. It used that the metal ion which is a component of a thing colored. Here, by selecting the type and amount of metal ions appropriately, it is colored pink, red (also called ruby), yellow, green, and blue to form colored sapphire, which is used as the material for sheath 1 Using. Of course, sapphire colored in this way may be used as the material of the pipe element 16.

  At the site of a thermotherapy operating room, the output power of the high-frequency power source 21 used for the thermotherapy and the time required for the thermotherapy differ depending on the size of the diseased tissue. There are also cases where a plurality of probes having different lengths or electrical characteristics are used. Here, by configuring the therapeutic antenna probe 24 with colored sapphire, it becomes easy to identify individual therapeutic antenna probes 24 necessary at the time of surgery depending on the presence or absence of coloring or the difference in colored color. As a result, the surgeon can easily discriminate the type of treatment probe, and can effectively prevent confusion with other probes.

  In this embodiment, FIGS. 16A and 16B (FIG. 16A is an axial cross section, and FIG. 16B is a cross section in a radial plane when cut along the plane AA ′. As shown in FIG. 4A, in order to cool the sheath 1 made of sapphire, a fluid import tube 13a for introducing a cooling fluid into the inside of the sheath 1 and a fluid import for discharging the fluid from the inside of the sheath 1 A tube 13b and a groove 13c for guiding a fluid to the inner surface of the sheath 1 were provided to constitute a therapeutic antenna probe 24. This groove 13 c was provided in parallel with the longitudinal axial direction of the sheath 1. The surface temperature of the probe could be further lowered by flowing a cooling fluid through the groove 13c and forcibly cooling the sheath 1. Here, ethylene glycol or physiological saline with a reduced salt concentration could be used as the cooling fluid. Accordingly, the temperature T based on the SAR before the forced cooling is the one shown in FIG. 7, but the surface temperature of the probe is further lowered as shown in FIG. 17 by flowing the cooling fluid in this way. In addition, the proteolytic temperature can be effectively maintained for a wide range of lesioned tissue regions by slightly increasing the power supply to compensate for the decrease. This effect is based on the high thermal conductivity of sapphire.

  The fluid that flows through the groove 13c is not limited to the cooling fluid. In this embodiment, a drug is poured into the groove 13c described above, and as shown in FIG. 18 (a), an anticancer drug or an anticancer drug is applied to the diseased tissue from the hole 18 provided at the distal end of the sheath 1 of the therapeutic antenna probe 24. As a result, the drug was injected into the diseased tissue. Of course, if the effect of forced cooling is sacrificed, a drug transport tube 13e is installed along the groove 13c and provided at the distal end of the sheath 1 as shown in FIG. It may be connected to the hole 18. If there is a sufficient gap between the sheath 1 and the first electrode 8 and the second electrode 9 to install the drug transport tube 13e, the groove 13c may be omitted. Furthermore, as shown in FIG. 18 (c), a hole 18 'communicating with the inner space of the sheath 1 may be provided in the side wall portion of the sheath 1, and a chemical solution of an anticancer drug or an anticancer drug may be injected into the diseased tissue. In other words, this therapeutic antenna probe 24 was also made to function as an injection needle. Here, the medicine was supplied from a medicine transport tube 13e provided separately. If necessary, the drug transport tube 13d may be connected to the hole 18 provided at the tip of the sheath 1 as described above. Such a structure of the sheath 1 allows the drug to be injected into the living tissue through these or these holes 18, 18 '. In addition, when the medicine soaks into the dipole antenna part, its electrical characteristics may deteriorate. Therefore, it is preferable to coat only the dipole antenna with a resin in order to prevent the infiltration of the drug. As such a resin, a photo-curing resin or a vinyl chloride paint can be used.

  Since at least sapphire is used as the material of the sheath 1 according to the present invention, it is hard and has high toughness. Accordingly, holes 18 and 18 'leading to the inner space of the sheath 1 are formed in the distal end portion or the side wall portion, and the medicine is injected into the sheath 1 from the outside, so that the therapeutic antenna probe 24 functions as an injection needle. be able to. As a result, as an actual effect, it was possible to more reliably treat tumors and the like by injecting anticancer agents and anticancer agents into the diseased tissue in conjunction with the thermal treatment of the diseased tissue with the therapeutic antenna probe 24. This makes it possible to perform a treatment with less burden on the living body without injecting an anticancer agent or an anticancer agent into the diseased tissue separately from the therapeutic antenna probe 24.

  In this example, an anticancer agent or an anticancer agent to be injected into a diseased tissue is a thermosensitive nano micelle, a thermosensitive hydrophobic hydrogel fine particle, a thermosensitive poly (NIPAM-g-PEG) having a reactive PEG chain, and the anticancer agent is cisplatin. Using a new polymer micelle-type drug carrier encapsulated and a novel block copolymer micelle encapsulating cisplatin, it was injected into a diseased tissue (there is no particular drawing). In this way, the anticancer agent or anticancer agent is included in the drug carrier, and the anticancer agent or anticancer agent does not directly attack healthy cells. On the other hand, the drug carrier is decomposed by heating with the therapeutic antenna probe 24 at the same time or after the injection of the drug into the diseased tissue via the therapeutic antenna probe 24, and the contained anticancer agent or anticancer agent. Will stay directly in the affected area. As a result, thermal necrosis and killing of cells by anticancer agents and anticancer agents were locally performed on the cancer cells as the lesion, and treatment with less burden on the living body could be performed. As a result, it was possible to obtain a high efficacy and a long duration of efficacy of anticancer agents and anticancer agents. As a result, a new application was obtained for the use of the therapeutic antenna probe 24 and a high therapeutic effect was obtained.

  As shown in FIG. 19, the electromagnetic therapy system according to the present embodiment includes a high-frequency power source 21 (also called a high-frequency power source or a microwave power source), a circulator 22 connected to the high-frequency power source 21, and a high-frequency coaxial cable connected to the circulator 22. The above-described therapeutic antenna probe 24 connected via the power supply 29, the power measuring device 23 connected to the high-frequency power source 21 via the power distributor 28, and the original high-frequency power source 21 based on the output signal of the power measuring device 23 Is controlled to output proper power. Here, the power distributor 28 is for monitoring the magnitude of the output power of the high-frequency power source 21, and may slightly distribute the output power of the high-frequency power source 21 that is distributed to the power measuring device 23. Further, it may be a coupler capable of monitoring simple high-frequency power.

  Further, in the above system, the above-described therapeutic antenna probe 24 is connected to the tip of the high-frequency coaxial cable 29. The outer conductor of the high-frequency coaxial cable 29 is electrically connected to the second electrode 9 of the therapeutic antenna probe 24, and the center conductor of the high-frequency coaxial cable 29 is electrically connected to the first electrode 8 of the therapeutic antenna probe 24. .

  On the other hand, this electromagnetic treatment system has a system configuration in which a temperature sensor 26 for puncturing and inserting into a diseased tissue is further added as necessary, and the output power of the high-frequency power source 21 is controlled by the output signal of the temperature sensor 26. This is to prevent the diseased tissue from cauterizing when the temperature of the diseased tissue greatly exceeds the proteolysis temperature (about 42 degrees). At the same time, the temperature of the diseased tissue is monitored and the output of the high-frequency power source 21 is controlled to an appropriate output power during the thermal treatment.

  In this embodiment, the microwave frequency output from the high frequency power supply 21 is 2.45 GHz, but other microwave frequencies may be used. For example, it may be 945 MHz which is generally approved for use in the United States. However, the gap between the electrodes of the gap portion 7 needs to be about 2.6 times that in the case where a frequency of 2.45 GHz is used.

  FIG. 20 shows a modification of the electromagnetic therapy system. The electromagnetic therapy system according to the present embodiment adds the power input to the power meter 23 to the output power from the high frequency power supply 21 shown in the thirteenth embodiment, and the remaining ports of the circulator 22 connected to the high frequency power supply 21. The power from With the power from this port, the reflected power (P1) from the therapeutic antenna probe 24 can be measured. As a result, it is possible to measure the difference power between the reflected power (P1) and the output power (P0) of the high-frequency power source 21. The output power (P0) of the high-frequency power source 21 was controlled using the control unit 25 for the purpose of controlling the input power (P0-P1) to the living tissue.

  That is, by this connection, a signal of the difference power (P2) between the output power (P0) of the high frequency power supply 21 and the reflected power (P1) from the therapeutic antenna probe 24 is generated by the power measurement. The difference power (P2) between the output power (P0) and the reflected power (P1) of the high-frequency power source 21 can be regarded as the input power (P3) from the therapeutic antenna probe 24 to the living tissue. Therefore, by controlling the control unit 25 with the signal of the difference power (P2), it was possible to control the original high frequency power supply 21 to output appropriate power to the living tissue.

  In this embodiment, a signal of the temperature measured by the temperature sensor 26 is input to the control unit 25 and the high frequency power supply 21 is controlled by turning on and off the output power of the high frequency power supply 21 with respect to the electromagnetic treatment system described above. . That is, in the electromagnetic therapy system shown in FIG. 19, the output power of the high frequency power supply 21 has a pulsed power waveform having a power supply period and a power non-supply period in the electromagnetic therapy system. The power is set constant, and the output power of the high frequency power source 21 is monitored as described above. If the output power becomes excessive, the output power of the high frequency power source 21 is stopped. Further, the power supply period of the output power is monitored and controlled by the output signal of the temperature sensor 26. This is because the diseased tissue into which the temperature sensor 26 is punctured and inserted can be appropriately heated while preventing local ablation as a treatment range. Here, the lower limit control set temperature TL of the control unit 25 is set in the vicinity of the proteolysis temperature of the diseased tissue. And when the temperature which the output signal from the temperature sensor 26 falls to control setting temperature TL, it is comprised so that predetermined electric power may be output from the high frequency power supply 21. FIG. The output power of the high frequency power supply 21 is assumed to be 10 watts on average, and is 600 with a 50% duty cycle (a power supply method in which the power supply period is 50% in one cycle and the power non-supply period is 50% in one cycle). The basic operation setting condition is to output for a second, and when the body tissue temperature exceeds 44 degrees, the control unit 25 controls the high-frequency power source 21 so that the power is not output during that period. Specifically, as shown in FIG. 21, in the control unit 25, TU and TL are set as upper and lower control set temperatures for the measured temperature of the temperature sensor 26 inserted into the diseased tissue. Here, TU is 44 degrees and TL is 42.5 degrees.

  That is, once the measurement signal of the temperature sensor 26 inserted into the living tissue reaches 44 degrees, the power when the output power (P0) of the high-frequency power source 21 is on is not output. As a result, the temperature of the living tissue decreased. On the other hand, when the temperature reaches 42.5 degrees close to the proteolysis temperature, the output of the power when the output power (P0) of the high-frequency power source 21 is turned on is resumed. The control unit 25 of this embodiment is configured to perform such hysteresis control with respect to the input of the measured temperature.

  The method using the output signal of the temperature sensor 26 can also be applied to the electromagnetic therapy system shown in FIG. That is, the output power of the high frequency power supply 21 is constant during the power supply period, and the input power (P3) to the living tissue of the high frequency power supply 21 is monitored as described above and the output power is excessive. If so, the output power of the high frequency power supply 21 is set to stop. The configuration monitored and controlled by the output signal of the temperature sensor 26 is the same as the above embodiment. That is, as a basic operation setting condition, when the living tissue temperature exceeds 44 degrees, the control unit 25 controls the high-frequency power source 21 so that the power is not output during that period. Specifically, as shown in FIG. 21, in the control unit 25, TU and TL are set as upper and lower control set temperatures for the measured temperature of the temperature sensor 26 inserted into the diseased tissue. Here, TU is 44 degrees and TL is 42.5 degrees.

  In Examples 15 and 16, the temperature sensor 26 is used as a device independent of the therapeutic antenna probe 24. However, the temperature sensor 26 may be mounted inside the therapeutic antenna probe 24, and the output signal of the temperature sensor 26 may be input to the control unit 25 to control the output power of the high-frequency power source 21 (particularly in the drawing). Absent). That is, since the sheath 1 of the therapeutic antenna probe 24 is made of sapphire, the thermal conductivity is high, and even if the temperature sensor 26 is inside the therapeutic antenna probe 24, the temperature of the heated lesioned tissue is controlled. It can be reflected well. Therefore, the temperature sensor 26 attached to the inside of the therapeutic antenna probe 24 can be used in place of the temperature sensor 26 directly inserted into the lesion tissue. As a method of mounting the temperature sensor 26 in the therapeutic antenna probe 24, it can be mounted on the inner space of the sheath 1 or the inner surface of the sheath 1. The therapeutic antenna probe 24 to which the temperature sensor 26 can be attached is the therapeutic antenna probe 24 shown in the first to ninth embodiments.

  In this embodiment, as shown in FIG. 22, the above-described electromagnetic treatment system is configured using the therapeutic antenna probe 24 shown in the eleventh embodiment. Here, the drug transport tube 13d or 13e was connected to the drug supply pump 30, and the drug was automatically or manually injected from the drug supply pump 30 through the hole 18 provided at the distal end portion of the sheath 1 into the diseased tissue. The electromagnetic treatment system is the same as that shown in FIG. 20, and the method for monitoring and controlling the output power of the high frequency power source 21 used in the system and the method for using the output signal of the temperature sensor 26 are the same as in the sixteenth embodiment. For this electromagnetic therapy system, using the therapeutic antenna probe 24 of Example 11 and further using the drug supply pump 30, the tip of the sheath 1 from the drug supply pump 30 through the drug transport tube 13d or 13e. This is an electromagnetic treatment system in which a drug is injected into a diseased tissue automatically or manually through a hole 18 drilled in a hole 18 or a hole 18 ′ drilled in a side wall of the sheath 1. The timing of injection of a drug such as an anticancer drug or an anticancer drug is after the therapeutic antenna probe 24 is punctured and inserted into the diseased tissue and before, simultaneously with, or after the power of the high frequency power supply 21 is supplied. About the time, it can be decided by drugs, such as an anticancer agent and an anticancer agent to be used.

  If necessary, a simple treatment system that does not control the output power of the high-frequency power source by the control unit 25 using the output signal of the temperature sensor 26 may be used.

It is the (a) principal part front view and (b) principal part sectional drawing of the puncture needle-shaped therapeutic electrode probe based on the conventional form. It is the (a) principal part front view of the bullet-shaped therapeutic electrode probe based on the conventional form, and (b) principal part sectional drawing. It is the (a) principal part front view and (b) principal part sectional drawing of the therapeutic antenna probe which covered the outermost part with the case based on the conventional form. It is the (a) principal part external view and (b) principal part sectional drawing of the therapeutic antenna probe which has a conductor piece based on the conventional form. It is a schematic diagram of a treatment area of (a) a therapeutic electrode probe and (b) a therapeutic antenna probe according to a conventional form. (A) The temperature distribution determined from the SAR of the therapeutic electrode probe according to the conventional form, and (b) the temperature distribution determined from the SAR of the therapeutic antenna probe according to the present embodiment. It is a temperature distribution determined from the SAR of the therapeutic antenna probe in consideration of the thermal conductivity of the sheath according to the present embodiment. It is the (a) principal part front view of the therapeutic antenna probe which has a gap | interval part based on Example 1, (b) principal part sectional drawing, (c) principal part sectional drawing of another structure. (A) principal part sectional drawing of the treatment antenna probe which has a conductor layer based on Example 2, (b) It is principal part sectional drawing of another structure. It is the (a) principal part front view of the therapeutic antenna probe which has a color | collar based on Example 3, (b) principal part sectional drawing, (c) principal part sectional drawing of another structure. It is principal part sectional drawing of the form which has (a) gap | interval part and (b) collar of the therapeutic antenna probe which has a sealing tube based on Example 4. FIG. FIG. 10 is a cross-sectional view of a main part of a therapeutic antenna probe having a coaxial connector according to a fifth embodiment. It is principal part sectional drawing of the form which has (a) gap | interval part and (b) collar of the therapeutic antenna probe which has a 3rd electrode based on Example 6. FIG. FIG. 10 is a cross-sectional view of main parts of a head element and a pipe element according to a seventh embodiment. Example 8 of a sheath having a sharp tip, (a) a form having a knife edge shape, (b) another form having a knife edge shape, (c) a form having a conical shape, (d) a curve, according to Example 8. It is a principal part front view and principal part side view of a form which has a knife shape. (A) Front view of principal part and (b) Cross section of radial plane when cut along AA ′ plane of therapeutic antenna probe according to Example 10 in which groove is formed on inner surface of sheath is there. FIG. 10 is a temperature distribution determined from the SAR of the therapeutic antenna probe when cooling fluid is passed through the inner surface of the sheath according to Example 10. FIG. Example 11 (a) Front view and main part side view of main part of therapeutic antenna probe with hole drilled, (b) Cross section of main part of therapeutic antenna probe with hole drilled at the tip, (C) It is principal part sectional drawing of the antenna probe for a treatment by which the hole was drilled in the front-end | tip and a side surface. It is a schematic diagram of the circuit structure of the electromagnetic therapy system which monitors the output electric power of the high frequency electric power source based on Example 13 and Example 15. FIG. It is a schematic diagram of a circuit structure of the electromagnetic treatment system using the reflected power from the therapeutic antenna probe according to Example 14 and Example 16. It is an example of the hysteresis control by the control unit of the electromagnetic therapy system based on Example 15 and Example 16. FIG. It is a schematic diagram of the circuit structure of the electromagnetic therapy system which has a chemical | medical agent supply pump based on Example 18. FIG.

Explanation of symbols

1 sheath 2 center conductor 3 insulating dielectric 4 outer conductor 5 jacket 6 head 7 gap 8 first electrode 9 second electrode 10 conductor piece 11 collar 12 sealing tube 13a fluid import tube 13b fluid export tube 13c groove 13d, 13e medicine Transport tube 14 Coaxial connector 15 Head element 16 Pipe element 17 Case 18, 18 ′ Hole 19 Conductor layer 20 Third electrode 21 High-frequency power source 22 Circulator 23 Power measuring instrument 24 Treatment antenna probe 25 Control unit 26 Temperature sensor 28 Power distributor 29 High-frequency coaxial cable 30 Drug supply pump

Claims (20)

A central conductor;
A cylindrical insulating dielectric formed on the outer periphery of the central conductor;
A cylindrical outer conductor formed on the outer periphery of the insulating dielectric, the first electrode being configured from a part thereof and electrically connected to the central conductor;
A second electrode composed of another outer conductor electrically isolated from the first electrode;
A sheath made of at least sapphire in which the first electrode and the second electrode are housed;
Consists of
Between the first electrode and the second electrode, one or more third electrodes, which are made of the other outer conductor and are electrically isolated from the first electrode and the second electrode, are provided in the sapphire. Is housed in a sheath consisting of
An electrical gap between the first electrode and the second electrode and an electrical gap between the third electrode and the first electrode or the second electrode are formed in the cylindrical outer conductor. Department,
The wavelength shortening rate of the therapeutic antenna probe is k, the relative dielectric constant of the side wall of the sheath is εS, the wavelength of the electromagnetic wave fed to the therapeutic antenna probe is λ, and the axial direction of the cylindrical shape of the gap Where a is the length of the insulating dielectric and d is the diameter of the insulating dielectric.
The axial length L of the cylindrical shape of the first electrode is

A therapeutic antenna probe that is long enough to meet . In place of the axial length L of the cylindrical shape of the first electrode,
The cylindrical axial length L ′ of the conductor layer electrically connected to the outer conductor on the surface of the outer conductor corresponding to the first electrode,

The therapeutic antenna probe according to claim 1, which has a length satisfying the above . The therapeutic antenna probe according to claim 1 or 2, wherein the central conductor and the first electrode are electrically connected via a conductor piece. The therapeutic antenna probe according to any one of claims 1 to 3, further comprising a collar made of a material having the same or substantially the same relative dielectric constant as the insulating dielectric fitted in the gap . The therapeutic antenna probe according to claim 1 or 2, wherein any or all of the first electrode, the second electrode, and the third electrode are formed of a conductor layer electrically connected to the conductor layer on the surface of the outer conductor . The therapeutic antenna probe according to claim 1 or 2, further comprising a sealing tube that is directly or indirectly attached to a part of the outer surface of the sheath and the surface of the outer conductor . The therapeutic antenna probe according to claim 1, wherein the center conductor and the outer conductor are connected to a coaxial connector outside the sheath . The therapeutic antenna probe according to claim 1, wherein the sheath is integrally formed of sapphire . The therapeutic antenna probe according to any one of claims 1 to 3 or 5, wherein the sheath includes a head element constituting a tip portion thereof and a pipe element constituting a side wall portion thereof . The therapeutic antenna probe according to claim 9 , wherein the distal end portion of the sheath has a sharp shape . The therapeutic antenna probe according to any one of claims 1 to 3 or 5, wherein a groove parallel to an axial direction of the sheath is provided on an inner surface of the sheath . The therapeutic antenna probe according to claim 9 or 10 , wherein a hole leading to an inner space of the sheath is formed in the distal end portion of the sheath or the distal end portion of the head element . The therapeutic antenna probe according to claim 12, further comprising a hole in the side wall portion of the sheath that leads to the inner space . The therapeutic antenna probe according to claim 1, wherein the sapphire is colored. A high frequency power supply,
A circulator connected to the high frequency power source;
The therapeutic antenna probe according to any one of claims 1 to 3 or 5 connected to the circulator via a high-frequency coaxial cable;
A power measuring instrument connected to the circulator and the high-frequency power source via a power distributor;
An electromagnetic therapy system comprising: a control unit that controls output power of the high-frequency power source according to an output signal of the power meter. The electromagnetic therapy system further includes a temperature sensor,
The output signal of the temperature sensor is input to the control unit,
The electromagnetic therapy system according to claim 15, wherein output power of the high-frequency power source is controlled by an output signal of the temperature sensor. The output signal of the power meter is
The difference power between the output power of the high-frequency power source and the reflected power from the therapeutic antenna probe obtained via the circulator,
An output signal from the temperature sensor;
The electromagnetic therapy system according to claim 16, wherein the electromagnetic therapy system is controlled by . The output power of the high-frequency power source is a pulsed power waveform composed of a power supply period and a power non-supply period, the output power of the power supply period is set, and the power supply period of the output power is at least the The electromagnetic therapy system according to claim 16 or 17 , which is controlled by an output signal of a temperature sensor . The electromagnetic treatment system according to any one of claims 15 to 18, wherein the electromagnetic treatment system further includes a medicine supply pump . The therapeutic antenna probe according to any one of claims 1 to 3, wherein a temperature sensor is attached to an inner space or an inner surface of the sheath .

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