JP2012223302A - Inducer used for hyperthermia apparatus, hyperthermia apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an inducer for a hyperthermia apparatus and the hyperthermia apparatus, achieving efficient heating to cancer tissues while reducing burden on a human body without complicating or enlarging the hyperthermia apparatus.SOLUTION: The inducer 5 is used for a hyperthermia apparatus for heating a heating object included in the human body 2, and includes an insulating region 7 and an non-insulating region 8. The insulating region 7 shields a high frequency signal irradiated by the hyperthermia apparatus 1 with respect to the human body 2, the non-insulating region 8 transmits the high frequency signal irradiated by the hyperthermia apparatus 1 through the human body 2, and a combination of the insulating region 7 and the non-insulating region 8 introduces the high frequency signal to the heating object.

Description

  The present invention relates to a derivative used in a thermotherapy device for performing a thermotherapy (also referred to as hyperthermia) for treating a tumor such as cancer, a derivative that promotes a temperature increase only in a treatment target such as cancer, and a thermo that uses this derivative. The present invention relates to a treatment device.

  In the treatment of cancer, there are surgical treatment for excising cancer tissue, chemical treatment using an anticancer agent, radiation treatment for irradiating the cancer tissue with radiation, immunotherapy for enhancing the immunity of the body, and the like. Each of these treatment methods has advantages and disadvantages, but there are problems such as a heavy burden on the human body and difficulty in application depending on the degree of progression of cancer.

  Under such circumstances, thermotherapy that raises the temperature of the cancer tissue to kill the cancer tissue has attracted attention. Such hyperthermia is also called hyperthermia, and utilizes the characteristic that cancer tissue is vulnerable to heat unlike normal tissue. Since a normal tissue has a large number of capillaries, even when heated, the heat received by heating can be released by expanding the capillaries or increasing blood flow. On the other hand, cancer tissue does not have capillaries or has few capillaries and cannot dilate blood vessels, and therefore cannot release heat received by heating. For this reason, it is known that cancer tissues are killed by heat of about 41.5 ° C. to 44 ° C.

  In the thermotherapy, the front and back surfaces of the human body are sandwiched between electrodes, and a high frequency signal is irradiated from one electrode to the other, thereby raising the temperature of cancer tissue inside the human body. At this time, the temperature rises on the surface and inside of the human body irradiated with the high-frequency signal, including the periphery of the cancer tissue, but the normal tissue can suppress the temperature rise by heat dissipation due to vasodilation. On the other hand, only the cancer tissue cannot suppress the temperature rise, and the temperature rises. As a result, cancer tissue is killed or reduced. In practice, this hyperthermia and surgical treatment can be used together to remove cancerous tissue.

  Thermal therapy can be performed by installing electrodes on the front and back surfaces of the human body and only irradiating the electrodes with high-frequency signals. Therefore, there are no side effects such as chemical therapy and radiotherapy, and there is little risk during surgery in surgery. For this reason, high potential for thermotherapy is expected.

  As described above, the basic configuration of the thermal treatment is electrodes installed on the front and back surfaces of the human body. Heating by irradiation of a high frequency signal from this electrode is the mechanism of thermotherapy. (1) The burden on the human body due to the inevitable heating of the part other than the cancer tissue to be heated, (2) Two problems, that is, lack of heating and temperature rise in the cancer tissue, were major issues.

  Several technical proposals have been made for thermotherapy that solves these two problems (see, for example, Patent Document 1 and Patent Document 2).

JP 1988-189149 A Special table 2007-536016 gazette

  Patent Document 1 discloses a hyperthermia device that performs a thermotherapy, and includes a close-contact type applicator that generates a thermoelectric effect and a cooling device that has a cooling function for the thermoelectric effect. The hyperthermia device performs heating to increase the temperature of cancer tissue contained in the human body due to the thermoelectric effect for thermal treatment. The technique of Patent Document 1 uses a cooling device in order to reduce the heating burden on the human body during this heating. In other words, Patent Literature 1 has an approach to solve the problem (1) in the prior art.

  However, the contact-type applicator that generates the thermoelectric effect does not change the heating of the human body other than the cancer tissue, and reducing this by the cooling device is not a fundamental solution. This is because it is not possible to avoid heating the human body part other than the cancer tissue by the close contact type applicator, and it is merely cooling from the side to be heated. Moreover, depending on the installation position and installation state of the cooling device, there is a possibility that the heating itself may be adversely affected. In this case, the heating of the cancer tissue itself becomes insufficient, and there is a possibility that the effect of the thermal treatment is not sufficiently exhibited. That is, not only the problem (1) in the prior art cannot be fundamentally solved, but also the problem (2) in the conventional technique is difficult to solve.

  Patent Document 2 discloses a hyperthermia device having a device for intensively applying a high-frequency signal to a cancer tissue. For example, the hyperthermia device of Patent Document 2 intends to enable high-frequency signals to be taken into cancer tissue by making the frequencies of the high-frequency signals multiple or combining various members. That is, Patent Document 2 has an approach for solving the problem (2) of the prior art.

  However, the hyperthermia device of Patent Document 2 requires various devices, accessories, members, operation procedures, and the like in order to concentrate high-frequency signals on cancer tissue, and there is a problem that the device becomes large and complicated. is there. In cancer treatment, it is assumed that a combination of a heat treatment and another treatment method (for example, a surgical treatment) rather than a case where only a heat treatment is assumed to be performed.

  In such combination therapy, the hyperthermia device used for hyperthermia is becoming more complex and larger, which raises the cost of the entire treatment and complicates the work of the entire treatment. Can occur.

  For this reason, patent document 2 also has the problem which brings about the cost increase to the whole treatment.

  Moreover, although patent document 2 is disclosing using an insulator, this insulator is an element for making it propagate from the electrode which transmits a high frequency signal to the electrode which receives. However, if only an insulator is used, it is difficult to concentrate heating only on the cancer tissue, as in the problem (2) in the prior art. Naturally, it is difficult to reduce the burden on the human body shown in the problem (1).

  As described above, it is difficult to ensure a balance between reducing the burden on the human body and efficiently heating the cancer tissue while reducing the cost of the entire treatment in the prior art and the techniques disclosed in Patent Documents 1 and 2 and the like. Met. Moreover, the human body has a thickness direction, and cancer tissue to be heated has various positions in the thickness direction. In order for the high frequency signal to reach the object to be heated in accordance with the position in the thickness direction, it is necessary to change the size and shape of the electrode during the treatment, and a doctor's skill is required. The treatment time also became longer, and there was a problem that the mental burden on the patient was great.

  In view of the above-mentioned problems, the present invention provides a derivative for a thermotherapy device and a thermotherapy that can realize efficient heating of cancer tissue while reducing the burden on the human body without complicating and increasing the size of the thermotherapy device. An object is to provide a therapeutic device.

  In view of the above problems, the derivative of the present invention is a derivative used in a thermal treatment device that heats a heating target included in a human body, and includes an insulating region and a non-insulating region, and the insulating region is a thermal treatment device. The high frequency signal emitted by the human body is shielded against the human body, the non-insulated region transmits the high frequency signal emitted by the thermal treatment device to the human body, and the combination of the insulated region and the non-insulated region introduces the high frequency signal to the heating target. To do.

  The derivative of the present invention can heat mainly cancer tissue contained in the human body and can reduce the burden of heating on the human body unrelated to the cancer tissue.

  In addition, although cancer tissue is mostly present in the human body, the derivative of the present invention can concentrate heating to the cancer tissue when the human body is grasped two-dimensionally, When the human body is grasped three-dimensionally, it is possible to concentrate heating on the cancer tissue.

  Furthermore, since the derivative of the present invention can be configured only by using an insulating member, the cost and work load are reduced, and the treatment cost of the thermal treatment (that is, the cost of cancer treatment) can be reduced.

It is a schematic diagram which shows the use condition of the thermotherapy apparatus in Embodiment 1 of this invention. It is a front view of the derivative | guide_body in Embodiment 1 of this invention. It is a front view of the derivative | guide_body in Embodiment 1 of this invention. It is a schematic diagram of the human body in Embodiment 1 of this invention. It is a schematic diagram which shows the arrangement | positioning state of the derivative | guide_body in Embodiment 1 of this invention. It is a schematic diagram which shows another aspect of the thermotherapy apparatus in Embodiment 1 of this invention. It is a schematic diagram of the thermotherapy apparatus in Embodiment 2 of this invention. It is a front view of the guidance member in Embodiment 2 of the present invention. It is a schematic diagram which shows the movement of the guide member in Embodiment 2 of this invention. It is a schematic diagram of the thermotherapy apparatus in Embodiment 2 of this invention. It is a schematic diagram of the thermotherapy apparatus in Embodiment 2 of this invention. It is a schematic diagram of the thermotherapy apparatus in Embodiment 2 of this invention. It is explanatory drawing which shows the state of the thermotherapy in Embodiment 3 of this invention. It is a schematic diagram which shows the experiment aspect in Experiment. It is a table | surface which shows the temperature rise of each of the position (1)-(5) in Experiment 1. It is a graph corresponding to the table | surface of FIG. It is a schematic diagram which shows the aspect of experiment 2nd. It is a table | surface which shows each temperature rise of the position (1)-(5) in Experiment 2. FIG. It is a graph corresponding to the table of FIG. It is a schematic diagram which shows the experimental state in a comparative example. It is a table | surface which shows the result in a comparative example. It is a graph corresponding to FIG.

  The derivative according to the first aspect of the present invention is a derivative used in a thermal treatment apparatus that heats a heating target included in a human body, and includes an insulating region and a non-insulating region, and the insulating region is a thermal treatment. The high frequency signal emitted by the device is shielded against the human body, the non-insulated region transmits the high frequency signal emitted by the thermal treatment device to the human body, and the combination of the insulated region and the non-insulated region sends the high frequency signal to the object to be heated. Introduce.

  With this configuration, the derivative can concentrate the high-frequency signal only on the heating target. As a result, in the heat treatment by the heat treatment apparatus, it is possible to minimize the burden on the human body and the stress and to heat the object to be heated in a concentrated manner. Furthermore, since the reach of the high frequency signal can be adjusted by the derivative, it is not necessary to replace the electrode of the thermal treatment apparatus.

  In the derivative according to the second aspect of the present invention, in addition to the first aspect, the non-insulating region includes at least one of a region formed surrounded by the insulating region and a region generated outside the insulating region.

  With this configuration, the derivative can efficiently induce a high-frequency signal to an object to be heated using not only a non-insulating region formed as a member but also a non-insulating region generated outside the member.

  In the derivative according to the third invention of the present invention, in addition to the first or second invention, when the human body is grasped in three dimensions of the X axis, the Y axis, and the Z axis orthogonal to each other, the non-insulating region Is a two-dimensional plane composed of an X axis and a Y axis, facing a heating target contained in the human body, the X axis is along the horizontal direction of the human body, and the Y axis is along the height direction of the human body The Z axis is along the thickness direction of the human body.

  With this configuration, the derivative can concentrate on the heating target and induce a high-frequency signal.

  In the derivative according to the fourth invention of the present invention, in addition to any one of the first to third inventions, the insulating region includes a plurality of insulating members having an insulating function, and a combination of the plurality of insulating members is not used. An insulating region is formed.

  With this configuration, the combination and shape of the insulating region and the non-insulating region can be formed flexibly.

  In the derivative according to the fifth aspect of the present invention, in addition to the fourth aspect, at least one of the shape, area and position of the non-insulating region is variable.

  With this configuration, the derivative can change the non-insulating region in accordance with the shape, size, and position of the heating target.

  In the derivative according to the sixth aspect of the present invention, in addition to any of the first to fifth aspects, the derivative includes a first guide member and a second guide member, and the first guide member is a surface of a human body. The second guiding member is disposed so as to face the back surface of the human body, and at least a part of the insulating region of the first guiding member is at least a part of the non-insulating region of the second guiding member. And facing through the human body.

  With this configuration, the derivative can induce high-frequency signals three-dimensionally from various angles with respect to the heating target.

  In the derivative according to the seventh invention of the present invention, in addition to the sixth invention, the non-insulating region of the first guiding member faces the insulating region of the second guiding member via the human body, and the first guiding member This insulating region faces the non-insulating region of the second guide member via the human body.

  With this configuration, the derivative can induce a high-frequency signal at an angle that intersects the thickness direction of the human body with respect to the heating target.

  In the derivative according to the eighth aspect of the present invention, in addition to the sixth or seventh aspect, at least one of the first guiding member and the second guiding member is not subjected to a non-insulating region during treatment with the thermal treatment apparatus. The position of can be moved.

  With this configuration, the derivative can suppress the burden on the living body due to heat generation on the surface of the human body that is a non-heating target, and can selectively heat only the target heating target. Moreover, although the heating to a heating object is continued, since the site | part heated on the human body surface changes, the heating stress to the human body surface can be reduced.

  In the derivative according to the ninth aspect of the present invention, in addition to the eighth aspect, the position of the non-insulating region is (1) during irradiation of a high frequency signal from the thermotherapy device, and (2) high frequency from the thermotherapy device. 9. A derivative according to claim 8, wherein the derivative is movable either while the signal is stopped.

  According to this configuration, the non-insulating region can be moved according to the treatment mode, and concentrated heat generation of the heating target is possible while reducing the burden on the human body.

  In the derivative according to the tenth invention of the present invention, in addition to the eighth or ninth invention, at least one of the first guide member and the second guide member has a position of each non-insulating region, the X axis and the Y axis. It is movable along a plane specified by the axis.

  With this configuration, the derivative can induce a high-frequency signal from various angles and positions to the object to be heated, and can suppress heat generation in the non-heated object part.

  A thermotherapy device according to an eleventh aspect of the present invention includes any one of the first to tenth derivatives and a control unit that performs at least one of installation and movement of the derivatives.

  With this configuration, the thermotherapy device can perform treatment while moving the derivative.

  In the thermotherapy apparatus according to the twelfth aspect of the present invention, in addition to the eleventh aspect, at least one of an electrode capable of irradiating a human body with a high frequency signal via a derivative and a cooling member provided between the electrode and the human body Is further provided.

  With this configuration, the thermal treatment apparatus can perform heating with high frequency while reducing the burden on the human body.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings.

  (Embodiment 1)

Embodiment 1 will be described.
(Overview)
First, an overall outline of the derivative in Embodiment 1 will be described with reference to FIG.

  FIG. 1 is a schematic diagram showing a usage state of the thermotherapy device in Embodiment 1 of the present invention. The thermotherapy device kills cancer tissue contained in a human body by applying a high frequency signal to the human body from an electrode. Such a thermotherapy device is used in an actual medical field, and expectation for cancer treatment is expected along with surgical treatment and chemical treatment.

  FIG. 1 shows a state in which electrodes and a saline bolus are installed on the front and back surfaces of the human body 2. For this reason, the names of the first, second and the like are given for the respective elements such as the electrode, the saline bolus, and the cooling saline bolus for convenience.

  The thermotherapy device 1 is intended to heat the cancer tissue 10 to be heated contained in the human body 2 and kill the cancer tissue 10.

  The thermal treatment apparatus 1 installs the first electrode 3A and the second electrode 3B above and below the human body 2, and allows a high-frequency signal to flow between the first electrode 3A and the second electrode 3B. A first saline bolus 4A is installed under the first electrode 3A (side closer to the human body 2). The first saline bolus 4A prevents direct contact between the first electrode 3A and the human body 2. The derivative 5 is installed in the lower layer (side closer to the human body 2) of the first saline bolus 4A. Further, a first cooling saline bolus 6A is installed below the derivative 5 (side closer to the human body 2). The first cooling saline bolus 6 </ b> A cools the human body 2 and reduces the burden caused by the temperature rise in parts other than the cancer tissue 10 in the thermal treatment. The cancer tissue 10 contained in the human body 2 is a heating target. Of course, the object to be heated includes not only the cancer tissue 10 but also other elements that require treatment by thermal treatment.

  The above is the configuration of the front side of the human body 2, but the back side of the human body 2 is also configured by stacking similar elements. A second saline bolus 4B is installed on the upper layer of the second electrode 3B (side closer to the human body 2). Similar to the first saline bolus 4A, the second saline bolus 4B prevents direct contact between the second electrode 3B and the human body 2. Further, a second cooling saline bolus 6B is installed as necessary. The second cooling saline bolus 6B cools the human body 2 and alleviates the burden caused by the temperature rise in parts other than the cancer tissue 10 in the thermal treatment. The second cooling saline bolus 6B may also be used as the second saline bolus 4B.

  The high-frequency signal irradiated from the first electrode 3A passes through the first saline bolus 4A and the like, and is induced by the derivative 5 to the cancer tissue 10 to be heated. The derivative 5 has an insulating region 7 and a non-insulating region 8, and the combination of the insulating region 7 and the non-insulating region 8 intensively induces a high frequency signal to the object to be heated, while the high frequency to other than the object to be heated. Suppress signal induction. As a result, the thermotherapy apparatus 1 using the derivative 5 can perform a treatment for causing only the heating target to generate heat and killing the cancer tissue 10 to be heated.

  Such a heating target can generate heat intensively because the insulating region 7 shields high-frequency signals and the non-insulating region 8 allows high-frequency signals to pass. This is because the combination can intensively induce high-frequency signals to the object to be heated.

  Note that “A” and “B” used in the reference numerals are assigned to “first” and “second”, respectively, and are identical if they do not correspond to the first and second. The symbol of the element is indicated by a symbol of only numbers. For example, the electrode is represented as an electrode 3 (when the first electrode and the second electrode are not distinguished from each other or mean including both).

(High-frequency signal passing)
The passage of a high-frequency signal will be described with reference to FIG. The broken line shown in FIG. 1 indicates the passage of a high frequency signal.

  The high frequency signal irradiated from the first electrode 3 </ b> A passes through the first saline bolus 4 </ b> A and reaches the derivative 5. Since the dielectric 5 has the insulating region 7, the high frequency signal is shielded by the insulating region 7 and passes through the non-insulating region 8. That is, as indicated by the broken line, the high frequency signal is twisted and easily concentrated on the non-insulating region 8.

  The high-frequency signal concentrated on the non-insulating region 8 passes through the first cooling saline bolus 6A and reaches the cancer tissue 10 facing the non-insulating region 8 as it is. This high-frequency signal passes through the second cooling saline bolus 6B and the second saline bolus 4B as it is and reaches the second electrode 3B. The passage of the high-frequency signal is as shown by the broken line in FIG. That is, the high-frequency signal passes through the cancer tissue 10 in a concentrated manner.

  By concentrating the high frequency signal on the cancer tissue 10, the cancer tissue 10 generates a high fever. On the other hand, in regions other than the cancer tissue 10, since there are few high-frequency signals to reach (pass), heat generation is suppressed. The same applies to the surface of the human body 2. As a result, while the burden and stress on the human body 2 are suppressed, only the heating target is concentrated to generate heat, and the cancer tissue 10 can be effectively treated.

  As described above, the derivative 5 according to the first embodiment enables efficient thermal treatment for killing the cancer tissue 10 while minimizing the burden on the patient.

  The derivative 5 can be mainly installed (introduced) in the currently used thermal treatment apparatus because the high-frequency signal can be mainly introduced into the overheat target only by the combination of the insulating region 7 and the non-insulating region 8. For this reason, it is not necessary to increase the cost of the thermotherapy device or increase the burden of the thermotherapy using the thermotherapy device.

  The derivative 5 may be distributed as an option of a thermotherapy device already on the market, or may be distributed in a state of being incorporated in the thermotherapy device. In any case, the effect of the heat treatment in the existing heat treatment apparatus can be enhanced. Since it does not increase the cost, it can be combined with a surgical treatment or a chemical treatment, and the derivative 5 brings a high positive merit for comprehensive cancer treatment.

  Next, the detail of each part is demonstrated.

(electrode)
The electrode 3 is not an element directly constituting the derivative 5, but is a necessary element of the thermal treatment apparatus 1.

  The electrode 3 irradiates a human body 2 (including not only directly on the human body 2 but also through other elements) with a high-frequency signal. A high-frequency signal propagates between the first electrode 3A and the second electrode 3B in FIG. For example, the first electrode 3A outputs a high frequency signal, and the second electrode 3B receives the output high frequency signal. For this reason, each of the first electrode 3A and the second electrode 3B is provided with a power supply for supplying a current as a high-frequency signal and a conductive path connected from the power supply.

  For this reason, it can be grasped that the electrode 3 is an irradiation unit that emits a high-frequency signal.

  The high-frequency signal only needs to have a frequency within a predetermined range, and may generally be a frequency included in the high-frequency band. As an example, the high frequency signal may have a frequency included in a high frequency band of 3 MHz to 300 MHz or a microwave band of 300 MHz to several GHz. In the present invention, it is essential to introduce a high-frequency signal into the cancer tissue to be heated, and what kind of frequency the high-frequency signal is used depends on the specifications and characteristics of the thermotherapy device 1 that is actually used. It does not need to be specified in particular.

  For example, a commercially available thermotherapy device employs 8 MHz as the frequency of the high-frequency signal from the electrode. Although not specified by this frequency, the frequency around 8 MHz can be generated by a simple electronic circuit, and the balance between heating and the burden on the human body is high. In addition, it is because a frequency of about 8 MHz is appropriate for heating the human body. Of course, by changing the frequency, an optimum high-frequency signal can be given to the type, position, depth, and size of the target cancer tissue.

  The adjustment of the reach of the high frequency signal in the Z-axis direction of the human body 2 is often realized by changing the size of the electrode. For this reason, the electrode 3 outputs a high-frequency signal suitable for heating the human body 2 by appropriately combining the frequency, the size of the electrode, the signal intensity, and the like.

  When the first electrode 3A and the second electrode 3B are paired, it is possible to output and receive a high-frequency signal. However, when the ground plane (so-called ground) has a reception function, only the first electrode 3A is available. Thus, the human body 2 can be irradiated with a high frequency signal. When the high-frequency signal is absorbed by the human body 2, the molecular motion of the human body 2 becomes active, the tissue of the human body 2 generates heat due to the increase of the molecular motion, and the temperature of the heat generating portion increases. That is, the tissue inside the human body 2 is heated by the high frequency signal.

  A normal tissue that is not a cancer tissue includes a large number of capillaries, and heat from the fever is released by dilation of the capillaries (the blood flow becomes active). That is, the temperature of normal tissue does not increase much. On the other hand, in cancer tissue, the function of capillaries is insufficient, and the capillaries do not expand even if they receive heat. That is, blood flow does not increase. As a result, in the cancer tissue, heat generated by the high frequency signal is not released, and the cancer tissue generates heat.

  Thus, by irradiating the human body 2 with the high-frequency signal, the temperature of the cancer tissue rises and is killed, and the temperature of the normal tissue hardly rises and does not die.

  As described above, the electrode 3 (the first electrode 3A and the second electrode 3B) gives a high-frequency signal to the human body 2 and heats a heating target such as a cancer tissue. Here, the cancer tissue is described as a heating target, but the heating target includes other cancer tissues such as prostate tissue, liver tissue, lung tissue, and lumbar back soft tissue.

(Saline bolus)
In the saline bolus 4 (in FIG. 1, the first saline bolus 4A on the front side of the human body 2 and the second saline bolus 4B on the back side of the human body 2) are not directly in contact with the human body 2. Installed for hygiene and prevention of discomfort to the human body.

  Moreover, since the salt water bolus 4 contains the salt water inside, it can transmit a high frequency signal. Further, the angle of the high-frequency signal output from the electrode 3 can be changed depending on the concentration of the saline solution and the shape of the saline bolus 4, and it becomes easy to concentrate the high-frequency signal on the heating target in combination with the derivative 5 described later. In particular, since salt solution is contained, it becomes close to the electrical conductivity of the human body, and high-frequency signals can be easily passed through the human body.

  Further, when an air layer exists between the electrode 3 and the human body 2, the high frequency signal irradiated from the electrode 3 is difficult to reach the human body 2, or the high frequency signal is reflected or scattered by the air layer. The application of radiation to the human body 2 can be insufficient. The saline bolus 4 does not generate an air layer between the electrode 3 and the human body 2. As a result, the problem that the high-frequency signal irradiated from the electrode 3 hardly reaches the human body 2 is solved.

  For this reason, it is preferable that the saline bolus 4 has flexibility in its shape. For example, the saline bolus 4 is less likely to generate an air layer between the electrode 3 and the human body 2 by having an aspect in which a saline bag is filled in a bag of vinyl or soft resin. For this reason, the saline bolus 4 has an aspect like a water cushion.

  In FIG. 1, the first electrode 3A and the second electrode 3B are disposed so as to face the front surface and the back surface of the human body 2, respectively, and accordingly, the first saline bolus 4A and the second saline solution are arranged accordingly. Each of the boluses 4B is arranged in accordance with each of the first electrode 3A and the second electrode 3B.

  The saline bolus 4 prevents the formation of an air layer between the electrode 3 and the human body 2 and may be configured integrally with the electrode 3 or may be configured separately. In the thermotherapy device 1 of FIG. 1, the electrode 3 and the saline bolus 4 are configured separately, but may have a configuration in which the saline bolus 4 is attached to the electrode 3.

(Saline bolus for cooling)
A cooling saline bolus 6 is disposed between the later-described derivative 5 and the human body 2. Since the cooling saline bolus 6 is an element that is in direct contact with the human body 2, the surface of the human body 2 is prevented from being heated by the irradiation of the high-frequency signal, and the saline bolus 4 and the human body 2 can be generated by the arrangement of the derivative 5. Prevent air layer between.

  The thermotherapy apparatus 1 in FIG. 1 arranges the derivative 5 between the human body 2 and the electrode 3. For this reason, the saline bolus 4 arranged on the lower layer (the human body 2 side) of the electrode 3 cannot contact the human body 2 directly but contacts the derivative 5. The derivative 5 plays a role of inducing a high-frequency signal in the cancer tissue 10 to be heated, but is disposed between the saline bolus 4 and the human body 2, thereby eliminating contact of the saline bolus 4 with the human body 2. To do. In addition, since the derivative 5 has a structure having the insulating region 7 and the non-insulating region 8, it is difficult to cause flexibility or prevent the generation of an air layer.

  For this reason, like the saline bolus 4, a cooling saline bolus 6 having a flexible outer shape is disposed between the derivative 5 and the human body 2. The cooling saline bolus 6 ultimately minimizes the generation of an air layer between the electrode 3 and the human body 2 due to its flexible profile. As a result, the high-frequency signal irradiated from the electrode 3 can be reduced from being reflected or scattered before reaching the human body 2.

  The cooling saline bolus 6 is in direct contact with the human body 2. Since the cooling saline bolus 6 is filled with saline in the bag-shaped material, it can give the human body 2 a cool feeling. As a result, the cooling saline bolus 6 can cool the surface of the human body 2. There is a possibility that the surface of the human body 2 also generates heat due to heating by irradiation with a high-frequency signal. Such heat generation may be burdensome or uncomfortable for the human body 2. The cooling saline bolus 6 can reduce such a burden and discomfort.

  The cooling saline bolus 6 includes the word “for cooling”, but does not necessarily make the use of cooling essential.

  As shown in the thermotherapy device 1 of FIG. 1, the first cooling saline bolus 6 </ b> A is adapted to the first electrode 3 </ b> A and the second electrode 3 </ b> B disposed so as to face the front surface and the back surface of the human body 2. And a second cooling saline bolus 6B.

(Derivative)
Next, the derivative 5 will be described.

  The derivative 5 will be described with reference to FIGS. Here, FIGS. 2 and 3 show a single derivative 5 and a first guide member 51A and a second guide member 51B that constitute the derivative 5 described later. That is, in terms of shape, structure, etc., the single derivative 5 and the first guide member 51A (second guide member 51B) do not have to be particularly distinguished. FIG. 2 is a front view of the derivative according to the first embodiment of the present invention, and FIG. 3 is a front view of the derivative according to the first embodiment of the present invention.

(Insulated region and non-insulated region)
The derivative 5 includes an insulating region 7 and a non-insulating region 8. The insulating region 7 shields the high frequency signal irradiated from the electrode 3, and the non-insulating region 8 allows the high frequency signal to pass therethrough. Since the high-frequency signal is a current having a high frequency, it is shielded by the insulating region 7 that is an insulator. On the other hand, since the non-insulating region 8 does not have insulating properties, it allows high-frequency signals to pass therethrough.

  The insulating region 7 may be formed of an insulating material such as resin or synthetic resin. On the other hand, the non-insulating region 8 may be formed of a non-insulating material, or may be formed by voids or gaps in the derivative 5. For this reason, the insulating region 7 may be formed of an insulating material, and the portion other than the insulating region 7 may be the non-insulating region 8.

  For example, as shown in FIG. 2, the derivative 5 has a rectangular outer shape (not limited to a square, but a circle, an ellipse, a polygon, etc.) formed of an insulating material. A gap is provided in the part. For example, the gap is provided by cutting. The part other than the gap becomes the insulating region 7 and the gap becomes the non-insulating region 8. The derivative 5 shown in FIG. 2 is a single insulating material and constitutes the insulating region 7 and the non-insulating region 8. When the derivative 5 is used in the thermotherapy device 1, the derivative 5 is installed at a position where the gap that becomes the non-insulating region 8 faces the cancer tissue 10 to be heated. In other words, the derivative 5 is installed so that the insulating region 7 faces the part other than the heating target.

  Alternatively, as illustrated in FIG. 3, the derivative 5 may form the insulating region 7 and the non-insulating region 8 by a combination of a plurality of materials having insulating properties. 3 has a combination of a plurality of insulating members 71 having an insulating function. Specifically, four insulating members 71 are combined in a cross-beam shape. For this reason, a region where none of the four insulating members 71 exists is generated near the center. This region becomes the non-insulating region 8. Naturally, the region where the four insulating members 71 exist is the insulating region 7.

  A derivative 5 in which the insulating region 7 and the non-insulating region 8 are formed by one member as shown in FIG. 2 may be used, or the insulating region 7 and the plurality of members as shown in FIG. A derivative 5 in which the non-insulating region 8 is formed may be used. The derivative 5 formed of one member as shown in FIG. 2 has a merit that it is easy to transport, store and use because its shape is fixed. For example, the derivative 5 is easily distributed and used as an off-the-shelf product having a non-insulating region 8 that matches the general size and position of the cancer tissue 10 to be heated.

  On the other hand, as shown in FIG. 3, the derivative 5 formed of a plurality of members has a variable shape (particularly, the position, size, and arrangement of the non-insulating region 8), so that the cancer tissue 10 to be heated is obtained. Depending on the position, size, type, or physique and characteristics of the patient being treated, it has the advantage of being used for flexibility. Further, since each of the plurality of insulating members 71 has only to be stored together, it is easy to store, and the balance between storage and flexibility of use is enhanced. For example, a plurality of insulating members 71 having the same shape and size are stored, and when used in the thermal treatment apparatus 1, the plurality of insulating members 71 are combined in accordance with the position and size of the heating target. Thus, the derivative 5 having the necessary insulating region 7 and non-insulating region 8 can be used.

  Thus, the derivative 5 by the combination of the plurality of insulating members 71 as shown in FIG. 3 can include the non-insulating region 8 that is variable in at least one of shape, area, and position. Of course, even in the case of the derivative 5 composed of a single member shown in FIG. 2, the position of the non-insulating region 8 can be changed only by changing the installation position with respect to the human body 2.

  Since the combination of the insulating region 7 and the non-insulating region 8 intensively introduces a high-frequency signal to the heating target such as the cancer tissue 10, at least the shape, area, and position of the non-insulating region 8 (in other words, the insulating region 7). It is important that one is variable. The derivative 5 can be flexibly changed at least one of the shape, area, and position of the non-insulating region 8 by combining the plurality of insulating members 71 in addition to the installation position.

  The insulating region 7 is formed of a member or material having an insulating function. The non-insulating region 8 is the remaining part of the insulating region 7, but as shown in FIGS. 2 and 3, the gap may be the non-insulating region 8, or the non-insulating region 8 may be formed by a non-insulating material. It may be formed. For example, a structure in which two different types of members are combined so that the insulating member forms the insulating region 7 and the non-insulating member forms the non-insulating region 8 may be used.

  Further, as shown in FIGS. 2 and 3, the non-insulating region 8 includes at least one of a region surrounded by the insulating region 7 and a region 81 outside the insulating region 7. That is, the region formed by being surrounded by the insulating member 71 as in the non-insulating region 8 in FIG. 3 or surrounded by the insulating region 7 of the integral member as in the non-insulating region 8 in FIG. Including. Similarly, the region 81 outside the insulating region 7 (regardless of the presence or absence of the non-insulating region 8 surrounded by the insulating region 7) can naturally be a non-insulating region. For this reason, the non-insulating region 8 also includes this outer region 81.

  That is, the derivative 5 not only uses the non-insulating region 8 included in the member itself forming the derivative 5 (or included in the structure formed by the plurality of insulating members 71), but depending on the case, the member 5 or the structure A high-frequency signal can be induced using a non-insulating region that naturally occurs outside (region around the member or structure). The same applies to a first guide member 51A and a second guide member 51B described later.

(Opposite the object to be heated and the non-insulated region)
The derivative 5 intensively induces the high frequency signal irradiated from the electrode 3 to the heating target. In particular, the derivative 5 intensively induces a high-frequency signal to the object to be heated according to factors such as the shape, position, range, and size of the combination of the insulating region 7 and the non-insulating region 8 to promote heating.

  At this time, since the non-insulating region 8 causes the high-frequency signal to reach the human body 2, the non-insulating region 8 is preferably opposed to the heating target. In particular, when the human body 2 is grasped by the X axis, the Y axis, and the Z axis orthogonal to each other, the non-insulating region 8 is a heating included in the human body 2 in a two-dimensional plane constituted by the X axis and the Y axis. It is preferable to face the object.

  FIG. 4 is a schematic diagram of a human body in the first embodiment of the present invention. FIG. 4 shows a state of the human body viewed from the front and a state viewed from the side. The X axis, the Y axis, and the Z axis described above are axes that are orthogonal to each other and define a three-dimensional space, but the X axis is along the lateral direction of the human body 2, and the Y axis is the height of the human body 2. The Z axis is along the thickness direction of the human body 2. By grasping the human body 2 in such a three-dimensional space of the X-axis, Y-axis, and Z-axis, the concentrated heating (induction of high-frequency signals) to the heating object by the derivative 5 can be grasped more clearly. Become.

  FIG. 5 is a schematic diagram showing the arrangement state of the derivative in the first embodiment of the present invention. FIG. 5 shows the human body 2 viewed from above, and the human body 2 has a heating target such as the cancer tissue 10. Since the human body 2 is grasped by the X axis, the Y axis, and the Z axis as described in FIG. 4, the surface of the human body 2 is grasped by a two-dimensional plane by the X axis and the Y axis.

  Since the non-insulating region 8 of the derivative 5 is required to induce a high-frequency signal to the cancer tissue 10 to be heated, the non-insulating region 8 is a cancer tissue in a two-dimensional plane composed of the X axis and the Y axis. It is preferable to face a heating object such as 10. FIG. 5 shows a state in which the non-insulating region 8 faces the cancer tissue 10 to be heated in a two-dimensional plane constituted by the X axis and the Y axis.

  Since the non-insulating region 8 faces the cancer tissue 10 to be heated, there is an advantage that high-frequency signals are concentrated on the object to be heated as indicated by the broken line in FIG. As a result, it is possible to perform cancer treatment by intensively generating heat in the heating target while suppressing the burden and stress on the human body 2.

(Another embodiment of the derivative)
As shown in FIG. 1, the derivative 5 may be disposed on the front surface side (or the back surface side) of the human body 2 as a single member, but may be configured to include a first guide member and a second guide member. FIG. 6 is a schematic diagram showing another aspect of the thermal treatment apparatus according to Embodiment 1 of the present invention. In FIG. 6, the first derivative 51 </ b> A is disposed on the front surface side of the human body 2, and the second guide member 51 </ b> B is disposed on the back surface side of the human body 2. Here, the structures and functions of the first guide member 51A and the second guide member 51B are the same as those of the derivative 5 described with reference to FIGS. That is, the first guiding member 51A has an insulating region 7A and a non-insulating region 8A, and the second guiding member 51B has an insulating region 7B and a non-insulating region 8B. Note that the region outside the insulating regions 7A and 7B may be regarded as a non-insulating region, as described in the derivative 5.

  Insulating regions 7 A and 7 B and non-insulating regions 8 A and 8 B have the same functions as insulating region 7 and non-insulating region 8 of derivative 5. That is, the insulating regions 7A and 7B shield high frequency signals, and the non-insulating regions 8A and 8B allow high frequency signals to pass. For this reason, each of the first induction member 51A and the second induction member 51B concentrates and induces the high-frequency signal to the heating target by the combination of the insulating regions 7A and 7B and the non-insulating regions 8A and 8B.

  The passage of the high frequency signal of the thermotherapy device 1 shown in FIG. 6 is as shown by the broken line. That is, the high frequency signal concentrates on the cancer tissue 10 to be heated by the combination of the insulating region 7A and the non-insulating region 8A of the first guide member 51A. Furthermore, since the second induction member 51B is disposed on the back surface of the human body 2, the combination of the insulating region 7B and the non-insulating region 8B provided in the second induction member 51B makes it easier to concentrate the high frequency signal on the heating target. Become. Compared with the broken line in FIG. 1, the broken line in FIG. 6 is more concentrated on the heating target due to the combination of the insulating region 7 </ b> B and the fire insulating region 8 </ b> B at the exit of the high-frequency signal (the back surface of the human body 2). I understand that.

  Thus, when the derivative 5 includes the first induction member 51A and the second induction member 51B, the intensive induction efficiency of the high-frequency signal to the heating target is increased, and while suppressing the burden and stress on the human body 2, Only the object to be heated can be concentrated to generate heat. This is because the range through which the high-frequency signal passes on the front and back surfaces of the human body 2 is easily limited to the heating target.

  At this time, it is preferable that the non-insulating regions 8A and 8B of the first guide member 51A and the second guide member 51B face the cancer tissue 10 on the front surface and the back surface of the human body 2, respectively. This is because the high-frequency signal passes from the non-insulating region 8A of the first guiding member 51A to the non-insulating region 8B of the second guiding member 51B.

  As described above, the derivative 5 intensively induces the high-frequency signal irradiated from the electrode 3 to the heating target such as the cancer tissue 10 by the combination of the insulating region 7 and the non-insulating region 8. As a result, the heating target is intensively heated. From another viewpoint, induction of high-frequency signals can be reduced for other than the heating target, and heat generation outside the heating target can be suppressed. In particular, the derivative 5 can realize these effects by making the non-insulating region 8 face the heating target. Of course, the derivative 5 alone may be disposed only on the front surface (or only the back surface) of the human body 2, and as shown in FIG. 1, the first guide member 51 </ b> A and the second guide member 51 </ b> B are provided on the front surface of the human body 2. And may be arranged on the back surface.

  Therefore, the derivative 5 can intensively heat only the object to be heated while minimizing the burden on the human body, and is very effective for cancer treatment and the like when applied to a thermal treatment apparatus. Moreover, since the derivative | guide_body 5 should just be integrated in the existing thermotherapy apparatus 1, the cost of the thermotherapy apparatus 1 can also be held down. Since the thermal treatment is preferably used in combination with a surgical treatment or a chemical treatment, reducing the cost of the thermal treatment device 1 also has an advantage of facilitating treatment combined with other treatment methods.

  As described above, the derivative according to Embodiment 1 can realize a thermotherapy device and a thermotherapy that can cause a heating target to generate heat intensively and suppress heat generation from other than the heating target to suppress a burden on the human body.

  (Embodiment 2)

  Next, a second embodiment will be described.

  In the second embodiment, the derivative 5 includes the first guide member 51A and the second guide member 51B. (1) At least a part of the insulating region 7A of the first guide member 51A is inserted into the first guide member 51A via the human body 2. (2) At least one of the first guide member 51A and the second guide member 51B is movable during irradiation of the high-frequency signal. The two guide members 51B face at least a part of the non-insulating region 8B of the two guide member 51B. The pattern will be described.

(Alternate facing)
FIG. 7 is a schematic diagram of a thermotherapy device according to Embodiment 2 of the present invention. FIG. 7 shows a state in which the thermal treatment device 1 is viewed from the side, and elements having the same reference numerals as those in FIG. 1 and the like have the same functions and configurations as those described with reference to FIG. Is an element.

  In the thermotherapy device 1 of FIG. 7, the derivative 5 includes a first guide member 51A and a second guide member 51B. Here, the first guide member 51 </ b> A is disposed on the front side of the human body 2, and the second guide member 51 </ b> B is disposed on the back side of the human body 2. Furthermore, at least a part of the insulating region 7A of the first guiding member 51A is opposed to at least a part of the non-insulating region 8B of the second guiding member 51B via the human body 2. In FIG. 6, the non-insulating region 8A of the first guiding member 51A and the non-insulating region 8B of the second guiding member 51B coincide with each other in the coordinates (X axis, Y axis). In other words, they face each other so as to substantially match. On the other hand, in FIG. 7, the insulating region 7A of the first guiding member 51A and the insulating region 7B of the second guiding member 51B are not completely coincident with each other (X axis, Y axis). The same applies to the insulating regions 8A and 8B.

  That is, at least a part of the insulating region 7A of the first guiding member 51A and at least a part of the non-insulating region 8B of the second guiding member 51B are opposed to each other via the human body 2. Of course, the insulating region 7A of the first guiding member 51A may be opposed to the non-insulating region 8B of the second guiding member 51B in a substantially matched state.

  Since the non-insulating region 8A and the non-insulating region 8B are different in the coordinate values indicated by (X-axis, Y-axis), the high-frequency signal irradiated from the first electrode 3A is first the insulating region 7A of the first induction member 51A. Is passed through the non-insulating region 8A. The boundary between the insulating region 7A and the non-insulating region 8A is at a position facing the cancer tissue 10 to be heated, and the high-frequency signal passing through the boundary between the insulating region 7A and the non-insulating region 8A is near the cancer tissue 10. Easy to pass. At this time, the high-frequency signal that has passed through the human body 2 passes through the non-insulating region 8B of the second guide member 51B. This is because the high frequency signal is shielded by the insulating region 7B of the second guide member 51B. That is, as indicated by the broken line shown in FIG. 7, the high-frequency signal reaches the second electrode 3B from the first electrode 3A with a twist.

  Due to this twist, the high-frequency signal is easily introduced into the cancer tissue 10 to be heated from various angles.

  For example, depending on the position and shape of the cancer tissue 10 to be heated, as shown in FIG. 1, the cancer tissue 10 is irradiated with a high-frequency signal from an oblique direction rather than being irradiated with a high-frequency signal substantially vertically. May tend to generate heat intensively. In such a case, it is also preferable to arrange the first guide member 51A and the second guide member 51B alternately along the Z-axis as shown in FIG.

  As shown in FIG. 7, when the first guide member 51A and the second guide member 51B are alternately arranged with respect to the human body 2, each of the first guide member 51A and the second guide member 51B It may have a shape as shown in FIG. FIG. 8 is a front view of the guide member according to Embodiment 2 of the present invention.

  The first guide member 51A (or the second guide member 51B) has an insulating region 7A (or insulating region 7B) biased in one direction and a non-insulating region 8A (or non-insulating region 8B) biased in the other direction. ing. The periphery of the non-insulating regions 8A and 8B is surrounded by members. Of course, it does not need to be enclosed. In this case, the first induction member 51A and the second induction member 51B are composed only of the insulating regions 7A and 7B, and the outside of the insulating regions 7A and 7B is not insulated. It becomes an area.

  As described above, at least a part of the insulating region 7A of the first guiding member 51A is opposed to at least a part of the non-insulating region 8B of the second guiding member 51B via the human body 2, so that a high frequency signal is obtained. It can be intensively guided to the object to be heated at a twisted angle.

(Movement / change of non-insulating region)
It is also preferable that at least one of the first guide member 51A and the second guide member 51B is movable in the non-insulating regions 8A and 8B during the thermal treatment by the thermal treatment apparatus.

(Part 1)
For example, as shown in FIG. 6, the non-insulating region 8A of the first guiding member 51A and the non-insulating region 8B of the second guiding member 51B are opposed to the cancer tissue 10. In this state, a high frequency signal is induced substantially perpendicularly to the cancer tissue 10. From this state, the first guide member 51 </ b> A and the second guide member 51 </ b> B are moved in the same direction (plane direction on the X axis and the Y axis).

  FIG. 9 is a schematic diagram illustrating movement of the guide member according to Embodiment 2 of the present invention. In FIG. 9, since it is seen from the front of the human body, only the first guide member 51A is shown. However, the first guide member 51A and (overlapping) the second guide member 51B are superposed via the human body.

  The left side of FIG. 9 shows a state where the first guide member 51A and the second guide member 51B are arranged at a certain position. Thereafter, as shown on the right side of FIG. 9, the first guide member 51A and the second guide member 51B are moved in the same direction on the two-dimensional plane indicated by the X axis and the Y axis. As a result, the positions of the non-insulating region 8A and the non-insulating region 8B also change. In particular, a change occurs at the position facing the cancer tissue 10. As a result, the high-frequency signal induction path to the cancer tissue 10 changes, and the cancer tissue 10 can be uniformly heated. For example, it is suitable when it is necessary to promote fever including around the cancer tissue 10.

  As described above, the movement of the first induction member 51A and the second induction member 51B while aligning the opposing positions of the non-insulating regions 8A and 8B can heat the heating target more effectively and flexibly. .

  The movement of the non-insulating region on the X-axis and Y-axis planes not only effectively heats the heating target in this way, but also changes the surface of the human body 2 that is irradiated with the high-frequency signal. be able to. As a result, the time during which the specific part of the surface of the human body 2 is heated by the high frequency signal is shortened, and the heating stress on the surface of the human body 2 can be reduced.

(Part 2)
In addition, when the positions of the non-insulating regions are staggered as shown in FIG. 8, it is also preferable to change the positions of the non-insulating regions. FIG. 10 is a schematic diagram of the thermal treatment apparatus according to the second embodiment of the present invention, and shows the same configuration as FIG. 10, the non-insulating region 8A of the first guiding member 51A and the insulating region 7B of the second guiding member 51B are opposed to each other with the human body 2 interposed therebetween. In this case, a high-frequency signal path as shown by the broken line is formed. By this path, the cancer tissue 10 generates heat intensively.

  From the state of FIG. 10, the first guide member 51A and the second guide member 51B are moved so that the first guide member 51A and the second guide member 51B are opposite to each other. FIG. 11 shows a state after the first guide member 51A and the second guide member 51B have moved in this way. The non-insulating regions 8A and 8B are changed to positions opposite to those in FIG. 10 in the X-axis direction. In other words, the non-insulating region 8A of the first guiding member 51A is opposed to the insulating region 7B of the second guiding member 51B via the human body 2 after being in a state opposite to that in FIG. The insulating region 7A of the first guiding member 51B faces the non-insulating region 8B of the second guiding member 51B. FIG. 11 is a schematic diagram of a thermotherapy device according to Embodiment 2 of the present invention.

  As a result, the high frequency signal is guided to the cancer tissue 10 from an oblique direction different from that in FIG. 10, as indicated by a broken line in FIG. The cancer tissue 10 generates heat due to the induced high frequency signal. Although the cancer tissue 10 generates heat by induction of the high-frequency signal to the cancer tissue 10, the cancer tissue 10 can generate heat uniformly by changing the approach angle of the high-frequency signal during the thermal treatment. Of course, the first guide member 51A and the second guide member 51B gradually move during the change from FIG. 10 to FIG. 11 (in other words, the non-insulating region 8A and the non-insulating region 8B gradually move). Therefore, the approach angle of the high-frequency signal induced in the cancer tissue 10 changes little by little. This change further increases the fever of the cancer tissue 10. This is because heat generation in the cancer tissue 10 is likely to increase due to the uneven force that promotes molecular motion.

  Moreover, the site | part of the surface of the human body 2 irradiated with a high frequency signal also changes with the movement of a non-insulating area | region. For this reason, the irradiation time in a specific site | part is shortened and the heat stress in the surface of the human body 2 can be reduced.

  As described above, the first guiding member 51A and the second guiding member 51B are movable during the thermal treatment (in other words, the non-insulating region 8A and the non-insulating region 8B are movable), and the derivative 5 Can effectively induce a high-frequency signal to be heated. As a result, the effect of hyperthermia increases.

  At this time, the derivative 5 (first guide member 51A, second guide member 51B) may be moved while the high-frequency signal is in an irradiation state, or may be moved while the high-frequency signal irradiation is stopped. In the latter case, the derivative 5 is moved after high-frequency signal irradiation is stopped, and high-frequency signal irradiation is started again after the movement. By repeating this, it is possible to sufficiently irradiate the object to be heated.

(Control part)
FIG. 12 is a schematic diagram of a thermotherapy device according to Embodiment 2 of the present invention. The thermotherapy device 1 shown in FIG. 12 includes a control unit 20.

  The thermal treatment apparatus 1 includes a control unit 20 that performs at least one of installation and movement of at least one of the first guide member 51A and the second guide member 51B. The control unit 20 installs or moves the derivative 5 (when the derivative 5 includes the first guide member 51A and the second guide member 51B, these guide members) according to the human body 2. For example, as described above, the first induction member 51A and the second induction member 51B can be moved in the X-axis direction and the Y-axis direction to change the induction path of the high-frequency signal for the heating target with time. Such a change in the induction path of the high-frequency signal can increase heat generation in the heating target.

  As described above, the derivative 5 in the second embodiment includes the first induction member 51A and the second induction member 51B, so that the induction of the high-frequency signal to the heating target can be performed with higher accuracy or can be performed flexibly. You can. As a result, the cancer tissue 10 having various shapes and modes can be treated.

(Embodiment 3)
Next, a third embodiment will be described. In the third embodiment, a thermotherapy device 1 using the derivative 5 described in the first and second embodiments and a thermotherapy method using the thermotherapy device 1 will be described.

  FIG. 13 is an explanatory diagram showing the state of the thermal treatment in the third embodiment of the present invention. FIG. 13 shows a state in which thermotherapy is performed on a patient 200 having a disease that is a target of thermotherapy such as cancer tissue.

  The thermal therapy device 1 has the elements and functions described in the first and second embodiments, and can realize thermal therapy. The patient 200 has the cancer tissue 10, and the thermotherapy device 1 aims to kill the cancer tissue 10 by intensively heating the cancer tissue 10. The thermotherapy device 1 includes a first electrode 3A and a second electrode 3B, and applies a high-frequency signal to the cancer tissue 10. At this time, the first guide member 51 </ b> A and the second guide member 51 </ b> B constituting the derivative 5 are disposed on the front surface and the back surface of the patient 200. Each of the first guide member 51A and the second guide member 51B includes insulating regions 7A and 7B and non-insulating regions 8A and 8B. The high-frequency signal is concentrated at a certain part of the cancer tissue 10 by the combination of the insulating region and the non-insulating region, and does not reach the other part much. As a result, the burden and stress on the patient 200 are minimized, and the cancer tissue 10 to be heated can be intensively heated.

  At this time, the thermal treatment apparatus 1 applies a high frequency signal from the first electrode 3A, a concentration step in which the high frequency signal is concentrated by the derivative 5, and heat generation in which the heating target is heated by the concentrated high frequency signal. And performing thermal therapy by these methods.

  In FIG. 13, the non-insulating region 8A of the first guiding member 51A and the non-insulating region 8B of the second guiding member 51B are opposed to the cancer tissue 10, but as described in the first and second embodiments, The first guide member 51A and the second guide member 51B may move during the thermal treatment.

  As described above, the thermotherapy device 1 using the derivative 5 described in the first and second embodiments can perform treatment while reducing the burden on the patient while intensively heating the cancer tissue 10. .

(Experimental result)
The inventor confirmed the effect of using the thermotherapy device 1 using the derivative 5 described in the first and second embodiments through experiments.

(Experiment 1)
First, an experiment was conducted on the effect of the derivative 5 in the embodiment described with reference to FIG. 6 in the first embodiment. FIG. 14 is a schematic diagram showing an experiment mode in Experiment 1. FIG. 14 is similar to FIG. 6 in which the first guide member 51A and the second guide member 51B are installed on the front and back surfaces of the agar phantom 21 that schematically represents a human body, and the first electrode 3A and the second electrode 3B High frequency signal was irradiated. Positions (1) to (5) in the agar phantom 21 are positions for measuring the heating state. In FIG. 14, the position (1) and the position (2) are heating targets in which the non-insulating regions 8A and 8B of the first induction member 51A and the second induction member 51B face each other. That is, the heating of the positions (1) and (2) is required to be higher than the other positions (1) to (5). Note that an agar phantom is generally used in experiments that model the human body.

(Experimental conditions)
Each of the first electrode 3A and the second electrode 3B is equipped with a first saline bolus 4A and a second saline bolus 4B. Further, each of the first electrode 3A and the second electrode 3B has a diameter of 30 cm and irradiates a high frequency signal of 8 MHz.

  Further, the first cooling saline bolus 6A and the second cooling saline bolus 6B are installed in accordance with the first guiding member 51A and the second guiding member 51B.

  Each of the first guide member 51A and the second guide member 51B has insulating regions 7A and 7B and non-insulating regions 8A and 8B. The non-insulating region 8A and the non-insulating region 8B are opposed to the positions (1) and (2) of the agar phantom 21. Further, the first guide member 51A and the second guide member 51B are not moved during the thermal treatment, and their positions are fixed.

(Experimental result)
The experimental result of Experiment 1 is shown in FIGS. FIG. 15 is a table showing the temperature rise at each of the positions (1) to (5) in Experiment 1, and FIG. 16 is a graph corresponding to the table of FIG.

  As is apparent from the results of FIGS. 15 and 16, the temperature rise at positions (1) and (2) (facing the non-insulating region) increases to other positions (3) to (5) as the irradiation time of the high-frequency signal becomes longer. ) The temperature rises (facing the insulating region). After the final 30-minute irradiation, a difference from 2.7 ° C. to 4.6 ° C. occurs. Moreover, it is 44 degreeC or more in position (1), (2), and has risen to the temperature generally considered that a cancer tissue is killed.

  As described above, the derivative 5 described in the first embodiment concentrates the position to be heated (positions (1) and (2) in Experiment 1) by the combination of the insulating region 7 and the non-insulating region 8. It is clear from Experiment 1 that it can be heated automatically. If cancer tissue or the like is present at the positions (1) and (2) to be heated, the derivative 5 (that is, the thermal apparatus 1) can intensively heat only the cancer tissue, and can provide a high therapeutic effect. it can. In addition, the stress on the human body other than the object to be heated is small.

(Experiment 2)
Next, in Experiment 2, the experiment described in the second embodiment with reference to FIGS. 10 and 11 was performed. FIG. 17 is a schematic diagram showing Experiment 2. FIG. 17 shows a state in which treatment is performed while moving the first guide member 51A and the second guide member 51B, similarly to FIGS. 10 and 11 used in the second embodiment. The position (1) of the agar phantom 21 that schematically represents the human body is the heating target.

(Experimental conditions)
The elements used are basically the same as in Experiment 1. However, the first guide member 51A and the second guide member 51B are different in shape and movement after installation.

  Each of the first guide member 51A and the second guide member 51B has insulating regions 7A and 7B and non-insulating regions 8A and 8B. Further, the non-insulating region 8A of the first guiding member 51A and the non-insulating region 8B of the second guiding member 51B are opposed to each other through the agar phantom 21 in a mismatched state. In addition, after irradiating the high frequency signal for 10 minutes, the positions of the first guiding member 51A and the second guiding member 51B are reversed (the state changes from FIG. 10 to FIG. 11), and the high frequency signal is irradiated again. Went.

(Experimental result)
The results of Experiment 2 are shown in FIGS. FIG. 18 is a table showing the results of Experiment 2 of the present invention, and FIG. 19 is a graph corresponding to the table of FIG.

  As can be seen from the results of FIGS. 18 and 19, the temperature rise at the position (1) to be heated was higher than at other positions. That is, it can be seen that only the heating target can be intensively heated to reduce the stress and burden on heating at other positions. Further, the temperature at the position (1) to be heated has risen to about 44 ° C., which is a temperature rise sufficient to kill the cancer tissue.

  As described above, Experiment 2 revealed that only the heating target can be intensively heated by moving the derivative 5 during the thermal treatment as described in the second embodiment.

  Experiments were also conducted on comparative examples for Experiment 1 and Experiment 2. FIG. 20 is a schematic diagram showing an experimental state in a comparative example. In the comparative example, unlike the experiment 1 and the experiment 2, the derivative 5 described in the mobile phones 1 and 2 is not used, but from the electrode 3 to the agar phantom 21 via the saline bolus 4 and the cooling saline bolus 6. A high frequency signal is directly applied to the. The temperature rise at each of the positions (1) to (4) was measured so as to correspond to Experiment 1 and Experiment 2.

  FIG. 21 is a table showing the results in the comparative example, and FIG. 22 is a graph corresponding to FIG. As is clear from FIGS. 21 and 22, there is almost no difference in the temperature rise at each of the positions (1) to (4), and it is difficult to heat a specific heating target such as a cancer tissue in a concentrated manner.

  In particular, the temperature rise at the site to be heated (in the comparative example, each of the positions (1) and (2)) is small compared to Experiments 1 and 2, and the derivative 5 is not used as in the comparative example. In that case, the temperature rise in the heating object is insufficient. In addition, it can be seen that the difference in temperature rise from other than the heating target is small, and that the heating stress to the heating target is large.

  Comparison of this comparative example with Experiment 1 and Experiment 2 also shows the superiority of the derivative 5 described in the first and second embodiments. That is, only the heating target can be heated intensively, and heating stress to other than the heating target can be reduced.

  As mentioned above, the derivative | guide_body and thermotherapy apparatus demonstrated in Embodiment 1-3 are an example explaining the meaning of this invention, and the deformation | transformation and remodeling in the range which do not deviate from the meaning of this invention are included.

DESCRIPTION OF SYMBOLS 1 Thermal therapy apparatus 2 Human body 3 Electrode 3A 1st electrode 3B 2nd electrode 4 Saline bolus 4A 1st salt bolus 4B 2nd salt bolus 5 Derivative 51A 1st guide member 51B 2nd guide member 6 Cooling saline bolus 6A First cooling saline bolus 6B Second cooling saline bolus 7, 7A, 7B Insulating region 71 Insulating member 8, 8A, 8B Non-insulating region 10 Cancer tissue 20 Control unit 200 Patient

Claims (12)

A derivative used in a thermotherapy device for heating a heating target contained in a human body,
An insulating region;
A non-insulating region,
The insulating region shields the human body from a high-frequency signal irradiated by the thermal treatment device, and the non-insulating region transmits the high-frequency signal irradiated by the thermal treatment device to the human body,
The combination of the insulating region and the non-insulating region is a derivative that introduces the high-frequency signal into the heating target.   The derivative according to claim 1, wherein the non-insulating region includes at least one of a region surrounded by the insulating region and a region generated outside the insulating region. When grasping the human body in a three-dimensional X-axis, Y-axis, and Z-axis orthogonal to each other,
The non-insulating region is a two-dimensional plane constituted by the X axis and the Y axis, and is opposed to a heating target included in the human body.
The X-axis is along a lateral direction of the human body, the Y-axis is along a height direction of the human body, and the Z-axis is along a thickness direction of the human body. Derivatives described.   4. The derivative according to claim 1, wherein the insulating region includes a plurality of insulating members having an insulating function, and the non-insulating region is formed by a combination of the plurality of insulating members.   The derivative according to claim 4, wherein at least one of a shape, an area, and a position of the non-insulating region is variable. The derivative includes a first guide member and a second guide member,
The first guide member is disposed to face the surface of the human body, and the second guide member is disposed to face the back surface of the human body,
The derivative according to any one of claims 1 to 5, wherein at least a part of the insulating region of the first guiding member opposes at least a part of a non-insulating region of the second guiding member via the human body. The non-insulating region of the first guiding member faces the insulating region of the second guiding member via the human body,
The derivative according to claim 6, wherein the insulating region of the first guiding member faces the non-insulating region of the second guiding member via the human body.   The derivative according to claim 6 or 7, wherein at least one of the first guide member and the second guide member is movable in a position of each non-insulated region during treatment by the thermal treatment apparatus.   The position of the non-insulating region is movable either during (1) irradiation of a high-frequency signal from the thermotherapy device or (2) during stoppage of a high-frequency signal from the thermotherapy device. 8. The derivative according to 8.   The at least one of the first guide member and the second guide member can move the position of the non-insulating region along a plane specified by the X axis and the Y axis. Derivatives described. A derivative according to any one of claims 1 to 10;
A thermotherapy device comprising: a control unit that performs at least one of installation and movement of the derivative.   The thermotherapy device according to claim 11, further comprising at least one of an electrode capable of irradiating a human body with a high-frequency signal through the derivative and a cooling member provided between the electrode and the human body.