JP3493078B2 - Ultra-high frequency heating treatment equipment - Google Patents

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention provides a pair of electrodes on the surface of a living body that sandwiches abnormal tissue such as cancer, and generates a high frequency electric field between the electrodes to kill the abnormal tissue by dielectric heating. The present invention relates to a thermotherapy device.

[0002]

2. Description of the Related Art Conventionally, there has been known an ultra-short-wave warming treatment apparatus which heats and treats abnormal tissue in a living body by radiating and supplying high-frequency energy from, for example, a pair of electrodes sandwiching the living body (Japanese Patent Laid-Open Publication No. Sho. 62-15236).

In this ultra-short-wave heating apparatus, for example, when both the abnormal tissue constituting a tumor such as cancer and the surrounding normal tissue are heated in a temperature range of 40 ° C. or higher, the former abnormal tissue is compared with the normal tissue. Focusing on the fact that the temperature rises by 2.0 to 2.5 ° C, the normal tissue is kept at 43 ° C or less, which does not necrosis, while the abnormal tissue is raised to around 45 ° C to be necrotic and destroyed. is there.

Further, in order to effectively necroticize and destroy an abnormal tissue that has been generated relatively deeply from the surface inside the living body by dielectric heating, a third electrode is arranged between a pair of electrodes for generating a high frequency electric field. A method is known (Japanese Patent Laid-Open No. 7-8564).

FIG. 8 is a schematic configuration diagram of an ultra-short wave heating treatment device provided with the conventional third electrode.

As shown in the same figure, a conventional ultra-short wave heating treatment device has a pair of electrodes 104, 1 for generating a high frequency electric field.
05 is arranged on the surface of the living body 100, the third electrode 106 is arranged in the cavity 101 of the living body 100 via the balloon 107, and high-frequency energy is supplied from the high-frequency generation control device 108 so that the third electrode 106 is placed between the electrodes 104 and 105. High frequency electric field 10
3 is formed.

With the above structure, the electrodes 104, 10
The lines of electric force formed between 5 are concentrated on the third electrode 106,
The strength of the high-frequency electric field 103 increases in the vicinity of the third electrode 106, and the abnormal tissue 102 such as cancer near the cavity 101 is effectively irradiated with the high frequency, and the heating treatment can be effectively performed. Is.

Further, 109 and 110 are cooling pads for suppressing the temperature rise of the electrodes 104 and 105 by circulating the cooling water by the cooling water circulation control device 111. Further, cooling water is circulated in the balloon 107 so that the temperature rise of the third electrode 106 is suppressed. Further, the temperature rise of the abnormal tissue 102 is detected by the temperature sensor 112 and the temperature measuring device 113,
Based on this detection, the supply of high-frequency energy is controlled so that the temperature rise of the abnormal tissue 102 falls within a predetermined temperature range (around 45 ° C).

[0009]

The former of the above-mentioned conventional ultra-short wave heating treatment devices must control the output of high frequency energy so that the heating temperature for normal cell tissue does not exceed 43 ° C. It was difficult to heat abnormal cell tissues to 45 ° C or higher. Therefore, for abnormal cell tissues that cannot be completely necrotized by heating at around 45 ° C.
For example, drug treatment and radiation therapy have to be used in combination, and the treatment burden on the patient has been large.

In the latter of the above-mentioned conventional ultra-short wave heating treatment devices, since the third electrode 106 provided between the pair of electrodes 104 and 105 is arranged in the cavity 101,
It can be applied only to abnormal tissues formed in luminal tissues such as stomach, intestine, esophagus, and large intestine, and it is difficult to effectively dielectrically heat abnormal tissues formed in all parenchymal organs such as liver, kidney, lung, and brain. is there.

In order to locally concentrate the high frequency electric field 103 on the site of the abnormal tissue 102, it is desirable to make the distance between the third electrode 106 and the abnormal tissue 102 as short as possible. Are placed via the balloon 107, the third electrode 106 and the abnormal tissue 10
There is a certain limit in reducing the distance between the two. Therefore, although the abnormal tissue 102 near the cavity 101 is treated, the treatment subject to which the ultra-short wave heating treatment method using the third electrode 106 is effectively applied is the abnormal tissue 102 formed in a position extremely close to the cavity 101. Was limited to.

For this reason, even with the latter of the conventional ultra-short wave heating treatment devices, it was difficult to heat only abnormal cell tissues to a high temperature of 45 ° C. or higher to completely necrotize them.

The present invention has been made in view of the above-mentioned problems, and the third aspect of the present invention is directly in an abnormal cell tissue formed at an arbitrary site.
It is an object of the present invention to provide an ultrashort wave heating treatment device in which electrodes are arranged and only this abnormal cell tissue can be completely necrotized by dielectrically heating it to 50 ° C or higher.

[0014]

DISCLOSURE OF THE INVENTION The present invention is a hollow conductive needle member which is an electrode needle that is pierced into a living body affected area as a third electrode in ultra-short wave heating treatment, and a tip portion of this conductive needle member. Provided on the outer periphery except for, consisting of a tubular body, and an electrode needle consisting of an insulating layer member configured to be bendable, and the hollow conductive needle member to penetrate the electrode needle tip of the affected part The conductive needle member includes a temperature detecting means provided in the vicinity thereof, a pair of electrode plates mounted on the surface of the living body with the affected part interposed therebetween, and a high frequency generating means for supplying a high frequency between the pair of electrode plates. Is the inner peripheral portion of the insulating layer member,
The ultrashort-wave heating apparatus is characterized in that a conductive thin film is formed on the tip surface and the tip outer peripheral portion (Claim 1).

In the above ultra-short wave warming treatment device, the base end of the conductive needle member may be connected to either one of the pair of electrodes or may be grounded.
3). Further, the base end of the conductive needle member may be electrically floating or may be grounded via an inductance member (claims 4 and 5).

[0016]

According to the first aspect of the present invention, the electrode needle comprises a pair of electrode plates (first and second electrodes) mounted on the surface of the living body with the affected part interposed therebetween, and a high frequency wave for supplying a high frequency wave between the electrode plates. It is used as the third electrode of the ultra-short wave heating treatment device including the generating means. The electrode needle is inserted until the tip of the electrode needle reaches the affected area in order to place the third electrode in the affected area.

When a high frequency is supplied to the pair of electrode plates, a part of the high frequency electric field formed between the electrodes is concentrated on the electrode needle, but the outer peripheral portion excluding the tip of the electrode needle is an insulating layer member. Since it is covered with, the high frequency electric field is more concentrated in the tip portion than in the middle portion of the electrode needle, and the dielectric heating efficiency of only the affected area is increased. Then, the hollow electrode needle is pierced into the affected area, and the temperature detecting means is disposed near the tip of the electrode needle of the affected area by penetrating the tube of the electrode needle. Is detected, and the detection result is used for controlling the high frequency supplied to the electrode plate.

According to the second and third aspects of the present invention, since the base end portion of the conductive needle member is connected to either the ground or the pair of electrodes, a high frequency electric field is applied to the tip portion of the electrode needle. The concentration is large, and only the abnormal tissue near the tip of the electrode needle can be locally dielectrically heated to a temperature sufficient for necrosis.

According to the fourth aspect of the invention, since the base end of the conductive needle member is electrically floating, the concentration of the high frequency electric field at the tip of the electrode needle is such that the base end of the conductive needle member is concentrated. It becomes weaker than when the part is grounded or connected to either one of the pair of electrodes, and the local heating range of the abnormal tissue becomes wider than when the proximal end part of the conductive needle member is grounded.

Therefore, by grounding or electrically floating the base end portion of the conductive needle member according to the size of the abnormal tissue, it is possible to perform dielectric heating only on the tissue of the required size.

According to the fifth aspect of the present invention, the high frequency electric field distribution at the tip of the electrode needle is changed by adjusting the inductance value of the inductance member, and it becomes possible to control the heating range and heating temperature of the affected area. .

[0022]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS FIG. 1 is a diagram showing a schematic structure of an ultrashort wave heating treatment apparatus using an electrode needle according to the present invention. Further, FIG. 2 is a cross-sectional view of relevant parts showing a state in which an electrode needle is inserted into an affected area.

The ultra-short-wave heating apparatus is mainly composed of electrodes 1, 1'which are attached to the surface of the living body with the affected area (cancer cells) S1 in the living body S interposed therebetween, and an electrode needle 2 which is inserted into the affected area S1 in the living body S. , A temperature detector 3 for detecting the temperature of the affected part S1, a high-frequency generation controller 4 for supplying high-frequency energy to the electrodes 1, 1'and the electrode needle 2, and a temperature of the affected part S1 from the temperature detected by the temperature detector 3. A temperature measuring device 5 for measuring, cooling pads 6, 6'for cooling the part of the living body S to which the electrodes 1, 1'are attached, and a cooling water circulation control device for circulating cooling water to the cooling pads 6, 6 '. 7 and the electrode needle 2
It is composed of an inductance member 8 connected to.

The cooling pads 6, 6'can be filled with cooling water such as physiological saline and distilled water, and the cooling water circulation control device 7 circulates the cooling water in the cooling pads 6, 6 '. , 1 ', the surface of the living body S that is dielectrically heated is cooled.

The electrode needle 2 is a hollow conductive needle member 21 made of a metal such as copper, aluminum or stainless steel, and an insulating member made of a resin such as polyethylene or Teflon which has a shorter length than the conductive needle member 21. And the layer member 22. In addition, the size of the metal portion of the tip is the affected part S
It changes according to the size of 1 and is set to several mm to 30 mm, for example.

The insulating layer member 22 has a high temperature (for example, 50 ° C.) for completely necrosing the abnormal tissue near the tip of the electrode needle 2.
It is a protective member for maintaining a temperature (for example, 43 ° C. or lower) at which normal tissue near the affected area of the electrode needle 2 is not necroticized even when dielectric heating is performed (before and after).

The insulating layer member 22 may be formed of an insulating tube through which the conductive needle member 21 can be inserted, or an insulating coating may be formed on the outer periphery of the conductive needle member 21.
In the case where the insulating layer member 22 is composed of an insulating tube, an electrode having an arbitrary insulating layer thickness and a tip electrode portion size is obtained by combining the insulating layer member 22 and the conductive needle member 21 having different thicknesses and lengths. The needle 2 can be easily configured.

The conductive needle member 21, as shown in FIG.
A mounting portion 212 to which the inductance member 8 is detachably connected is provided at the base end portion. Conductive needle member 21
The needle portion 211 of, for example, has a size of 18 gauge and is 25 cm.
It has a length of ~ 30 cm.

The needle portion 211 of the conductive needle member 21 is made hollow so that the temperature sensor 31 of the temperature detector 3 described later can be embedded in the affected area by the electrode needle 2. The needle portion 21 may be solid.

Further, although the conductive needle member 21 is made of a metal needle in this embodiment, it may be made of a conductive needle made by mixing a conductive material such as carbon into a resin material, or resin or ceramics. Alternatively, a conductive coating of gold, silver, copper or the like may be formed on the outer periphery of the needle member made of an insulating member such as.

Further, in this embodiment, the electrode needle 2 is composed of the conductive needle member 21 and the insulating layer member 22, but as shown in FIG. 4, the hollow insulating needle member 10 (insulating layer member) is used. 22
(Corresponding to (1)), the conductive thin film 11 (corresponding to the conductive needle member 21) may be formed on the inner peripheral portion, the tip surface and the tip outer peripheral portion. In this case, the conductive needle member 21 and the insulating layer member 22
Since the and are integrally configured, the structure of the electrode needle 2 is simple and can be easily manufactured.

More preferably, the electrode needle 2 may be constructed to be bendable. When the bendable electrode needle 2 is used, even if the patient changes his / her posture during the heating treatment, the electrode needle 2 inserted into the patient is flexibly deformed and the electrode needle 2 causes pain to the patient. In the case of a patient who needs multiple warming treatments, the electrode needle 2 can be pierced with relatively little pain during the multiple warming treatments. It can be held, and there is also an advantage that the physical and psychological distress of the patient to which the electrode needle 2 is inserted at each treatment can be reduced.

The bendable electrode needle 2 may be composed of, for example, a solid fine needle, but in view of workability at the time of insertion into the affected area S1, it is preferably composed of a cylindrical fine needle. . In this case, with the structure shown in FIG. 4, the electrode needle 2 having a desired flexibility can be easily manufactured.

The electrode needle 2 made of a cylindrical thin needle is inserted into the affected area S1 from the proper position of the living body S with a rigid mandrel inserted in the electrode needle 2, and then only the mandrel is removed. It can be easily inserted into the affected area S1.

Further, the electrode needle 2 is an ultrasonic diagnostic device or a CT.
(Computerized Axial Tomography) The position of the affected area S1 is displayed on a CRT using a scanner or the like, and the image is inserted into the affected area S1 while monitoring this image.

The temperature detector 3 is, as shown in FIG.
The optical fiber 31 and a special prism 32 provided at the tip of the optical fiber 31 and coated with a phosphor whose afterglow time changes depending on temperature are passed through the electrode needle 2 and the electrode needle of the affected area S1. It is arranged at a front position, for example, 5 to 6 mm away from the tip of No. 2.

In the temperature detector 3, the electrode needle 2 is inserted into the tip of the electrode needle 2 so that the prism 32 does not project, and the electrode needle 2 is inserted into the affected area S1 from the proper position of the living body S, and the tip of the electrode needle 2 is inserted. When reaches the affected area S1, only the electrode needle 2 is pulled out from the living body S by a predetermined size and is placed at the above-mentioned related position.

The optical fiber 31 comprises an irradiation light path for transmitting the light emitted from the temperature measuring device 5 to the prism 32 and a reflection light path for transmitting the reflected light from the prism 32 to the temperature measuring device 5, as shown in FIG. Further, the base end portion thereof penetrates through the electrode needle 2 and is connected to the temperature measuring device 5.

The temperature of the affected area S1 is measured by irradiating the phosphor of the prism 32 with pulsed light from the thermometer 5 through the optical fiber 31 and detecting the afterglow time of this phosphor from the reflected light. Changes are detected and measured. The temperature of the affected part S1 measured by the temperature measuring device 5 is input to the high frequency generation control device 4, and the high frequency output is controlled based on the detected temperature to control the dielectric heating of the affected part S1.

The inductance member 8 is a conductor wire made of a metal plate or a metal braid wire having an appropriate length, one end of which is connected to the mounting portion 212 of the electrode needle 2 and the other end of which is electrically suspended. The inductance member 8 may be connected to the electrode 1 or the electrode 1 ', or may be grounded to the ground.

The inductance member 8 is preferably a copper wire having a high electric conductivity, but any metal wire such as silver, aluminum or iron can be used. Alternatively, the surface of a support material such as resin may be coated with a conductive member such as silver, copper, or platinum.

When the inductance member 8 is connected to the electrode 1 (or the electrode 1 ') or grounded to the ground, the high frequency electric field concentrates on the tip of the electrode needle 2 as will be described later, and the vicinity of the tip of the electrode needle 2 increases. There is an advantage that only the tissue in a narrow range can be dielectrically heated to an extremely high temperature, and the affected area S1 can be spot-heated by the output control of the high frequency generation control device 4.

Instead of the inductance member 8, the conductive needle member 21 of the electrode needle 2 is made relatively long, the electrode needle 2 is directly grounded, and either one of the electrodes 1 and 1'is connected, or It may be electrically suspended.

In the above configuration, the high frequency generation control device 4
When high-frequency energy is supplied from the electrodes 1 and 1 ′ and the electrode needle 2 to each other, a high-frequency electric field 9 is formed between the electrode 1 and the electrode 1 ′ and between the electrode 1 (or the electrode 1 ′) and the electrode needle 2. As a result, the affected area S1 is dielectrically heated to be about 10.0 ° C. higher than the surrounding normal tissue, and is necrotic and destroyed.

During the heating treatment, the temperature detector 3 and the temperature measuring device 5 measure the rising temperature of the affected area S1.
The output of the high frequency generation control device 4 is adjusted based on the measurement result. Further, the cooling water circulation control device 7 circulates the cooling water to the cooling pads 6 and 6 ', and suppresses the temperature rise of the electrodes 1 and 1'.

As described above, in the high frequency electric field 9 formed between the electrode 1 and the electrode 1 ', a part of the lines of electric force is generated in the electrodes 1 and 1.
It is concentrated on the tip of the electrode needle 2 provided between 1 ', and the portion near the tip of the electrode needle 2 has a distribution having a higher electric flux density than the peripheral portion. Therefore, even when the affected area S1 is located at a deep position from the surface of the living body S, the electrode needle 2 is directly inserted into the affected area S1 to effectively irradiate a high frequency, thereby damaging normal cells by dielectric heating. The affected part S1 can be necrotized and destroyed without doing so.

FIG. 5 and FIG. 6 are diagrams showing the experimental results of the heating effect by the ultrashort wave heating treatment apparatus according to the present invention. FIG. 5 shows the inductance member 8 grounded, and FIG. 6 shows the inductance member 8 electrically floated. FIG. 7 is a diagram showing the measurement system of the above experiment.

The experiment was carried out by using a cubic sample 12 (hereinafter referred to as phantom 12) made of agar and having a side of 30 cm, which has a dielectric constant substantially the same as that of the living body S. Cooling pad 6, 6'on the bottom
A circular electrode plate 1, 1'having a diameter of 25 cm is attached through the electrode needle 2, and the electrode needle 2 is attached to one side surface (the right side surface in the figure) of the phantom 12 so that the tip reaches the center of the phantom 12.
, And a high frequency of a predetermined output is supplied from the high frequency generation control device 4 to the electrode plates 1, 1 ′ to dielectrically heat the phantom 12.

The electrode needle 2 is inserted 3 cm above the horizontal line N passing through the center O in parallel with the horizontal line N, and the conductive needle member 21 is made of polyethylene resin with its tip exposed by 15 mm. It is covered with a layer member 22. An inductance member 8 made of a copper wire having a diameter of 0.3 mm and a length of 80 cm is connected to the mounting portion 212 of the conductive needle member 21.

Further, M1 to M4 are temperature measuring lines provided with a plurality of temperature measuring points. M1 and M4 are temperature measurement lines on a vertical line passing through the center O, and M2 is approximately 6 cm from the center O above.
A temperature measuring line parallel to the temperature measuring line M1 outside the above range, M
Reference numeral 3 is a temperature measuring line which is approximately 12 cm outside the center O and is parallel to the temperature measuring line M1.

The temperature measurement on the temperature measuring lines M1, M2, M3 is performed by the position P near the electrode needle 2 on each temperature measuring line.
Temperature sensors were arranged at 1 to P3, respectively, and after performing a predetermined heating treatment, the temperature sensors were pulled upward by 10 mm each. For temperature measurement on the temperature measurement line M4, the temperature sensor is arranged at the symmetrical position P4 of the temperature sensor of the temperature measurement line M1 with respect to the horizontal line N, and the temperature sensor is pulled out by 10 mm downward after a predetermined heating process. went.

The temperature measuring lines M1, M2, M3 are temperature measuring lines for investigating the effect of dielectric heating by the electrode needles 2, and the temperature measuring line M4 is little affected by the electrode needles 2 and is mostly the electrodes 1, 1 This is a temperature measurement line for investigating the effect considered to be dielectric heating (hereinafter referred to as capacitive heating) due to ', and compares the temperature increase distribution of the temperature measurement lines M1, M2, M3 with the temperature increase distribution of the temperature measurement line M4. Then, the effect of dielectric heating by the electrode needle 2 was confirmed.

First, the effect of heating when the inductance member 8 is grounded will be described. In FIG. 5, the vertical axis represents the temperature rise Δt due to dielectric heating (= temperature t after heating treatment).
1-temperature before heating process t0), and the horizontal axis is the pull-out length d of the temperature sensor provided in each of the temperature measurement lines M1 to M4. It should be noted that d = 0 cm is the position where the electrode needle 2 was inserted and corresponds to positions P1 to P4 in FIG.

As is clear from the distribution of the rising temperature Δt on the temperature measuring lines M2 to M4, the position P is set at d = 0 mm.
2, the temperature rise Δt of P3 is higher than the temperature rise Δt of position P4 by about 1 ° C, but at other positions (d = 1 to 4 cm).
It can be seen that the temperature increase Δt on the temperature measurement lines M2 and M3 is substantially the same as the temperature increase Δt on the temperature measurement line M4 at the position (1)), which is the same as that due to capacitive heating.

On the other hand, according to the distribution of the rising temperature Δt on the temperature measuring line M1, it is understood that the heating effect is significantly greater in the vicinity of the tip of the electrode needle 2 than in the peripheral area. When the heating effect of the electrode needle 2 is examined by the difference between the temperature rise by the electrode needle 2 (temperature rise on the temperature measurement line M1) and the temperature rise by capacitive heating (temperature rise on the temperature measurement line M4), 20 ° C at the tip of 2 and 1 from the tip of the electrode needle 2
Since the temperature is higher by about 5 ° C. at a position separated by cm and about 1 ° C. at a position separated by 2 cm from the tip of the electrode needle 2, only abnormal tissue within a range of about 3 cm in diameter with the tip of the electrode needle 2 as the center. It can be seen that the tissue can be locally necrotized by heating at 3 ° C. or more as compared with the normal tissue around it.

Further, for abnormal tissue having a diameter of about 1 cm with the tip of the electrode needle 2 as the center, it is 5 ° C. or more compared to normal tissue around it, particularly 10 ° C. or more near the tip of the electrode needle 2. It can be seen that the abnormal tissue in this range can be completely necroticized by the dielectric heating since it can be heated to 0.

Next, the heating effect when the tip of the inductance member 8 is electrically floated will be described.

The vertical and horizontal axes in FIG. 6 are the same as those in FIG. Comparing FIG. 6 and FIG. 5, the inductance member 8
It can be seen that the effect of heating in the vicinity of the tip of the electrode needle 2 is suppressed more than when grounded by electrically floating. In this experiment, the temperature rise Δ on the temperature measuring line M1 at d = 0 mm
t is suppressed to about 1/3. On the other hand, the distribution of the rising temperature Δt on the temperature measurement lines M2, M3, M4 is hardly affected even if the inductance member 8 is electrically floated.

When the inductance member 8 is electrically floated, the relatively long inductance member 8 acts as an antenna, and the electrode needle 2 is connected to the outside other than the electrodes 1 and 1'and has a constant potential. Needle 2 and the electrode 1,
A potential difference occurs between 1'and the same effect as when the tip of the inductance member 8 is grounded is obtained, but the relative potential of the electrode needle 2 to the electrodes 1, 1'grounds the tip of the inductance member 8. Lower than when, electrode needle 2
Since the concentration of the lines of electric force at the tip of is reduced, it is considered that the heating effect is suppressed by electrically floating the inductance member 8.

Therefore, from the experimental results shown in FIGS. 5 and 6, by controlling the output of the high frequency generation control device, the temperature rise Δt near the tip of the electrode needle 2 rises to the same extent as when the inductance member 8 is grounded. When the temperature is adjusted to the temperature Δt, the heating range of the electrode needle 2 is set to the inductance member 8
When the abnormal tissue is relatively large, if the inductance member 8 is electrically floated and the output of the high frequency generation control device is controlled, only the abnormal tissue can be normally restored. It can be seen that it can be heated more than 5 ° C. higher than that of the tissue and can be completely necroticized by dielectric heating.

In the method of electrically floating the inductance member 8, the inductance value of the inductance member 8 may easily change due to the influence of the floating state, and the heating effect of the electrode needle 2 may change. For this reason,
Preferably, for example, the inductance member 8 is grounded and its length is variable (inductance value is variable).
Then, the inductance value of the inductance member 8 may be adjusted to adjust the heating range of the electrode needle 2.

As described above, the electrode needle 2 is inserted into the affected area S1 and a part of the high-frequency electric field 9 generated between the electrodes 1 and 1'is concentrated on the tip of the electrode needle 2 to locally induce the affected area S1. Since the heating is performed, the affected part S1 located deep inside the living body S1
Only can necrosis effectively without damaging normal tissue.

Particularly, since the third electrode provided between the electrodes 1 and 1'is the electrode needle 2, only a small area (area having a diameter of about 3 cm) at the tip of the electrode needle 2 is compared with the normal tissue around it. The heating can be performed at a temperature of 10 ° C. or higher, and only the region to be removed can be completely necroticized by dielectric heating, which makes it possible to perform ultrashort wave heating treatment that is simpler and more efficient than conventional treatments.

In the above embodiment, one electrode needle 2 is used, but a plurality of electrode needles may be used.

[0065]

As described above, according to the first aspect of the present invention, a hollow conductive needle member is an electrode needle that is pierced into a diseased part of a living body as a third electrode in ultrashort wave heating treatment, Since an electrode needle made of a cylindrical body and an insulating layer member that is configured to be bendable is provided on the outer periphery of the conductive needle member excluding the tip portion, the electrode needle is used. It is possible to concentrate the high frequency waves irradiated to the inside of the body on the affected area and effectively heat only this affected area by dielectric heating. Since the temperature detecting means is provided in the vicinity of the tip of the electrode needle of the affected area through the hollow electrode needle, it is not necessary to puncture the temperature sensor needle separately from the electrode needle, and the wiring for treatment is provided. It is simple and reduces the pain to the patient.

According to the second and third aspects of the invention, since the base end of the conductive needle member is connected to either one of the pair of electrodes or is grounded, the high frequency to the tip of the electrode needle is high. The concentration of the electric field is large, and only abnormal tissue near the tip of the electrode needle can be dielectrically heated to the treatment temperature simply and easily.

According to the fourth aspect of the invention, since the base end of the conductive needle member is electrically floated, the concentration of the high frequency electric field at the tip of the electrode needle causes the conductive needle member to concentrate. It becomes weaker than the case where the base end is connected to the ground or one of the pair of electrodes, and the heating range by the electrode needle is expanded.
As a result, even if the abnormal tissue is relatively large, it can be sufficiently dielectrically heated to the treatment temperature and can be surely necrotic.

According to the fifth aspect of the present invention, since the base end portion of the conductive needle member is grounded through the inductance member, the heating range of the affected area and the warming range of the affected area can be adjusted by adjusting the inductance value of the inductance member. The heating temperature can be controlled relatively easily.

[Brief description of drawings]

FIG. 1 is a schematic configuration diagram of an ultrashort-wave heating treatment apparatus using an electrode needle according to the present invention.

FIG. 2 is a cross-sectional view of relevant parts showing a state in which an electrode needle according to the present invention is inserted into an affected area.

FIG. 3 is a sectional view showing a structure of an electrode needle according to the present invention.

FIG. 4 is a cross-sectional view showing the structure of another embodiment of the electrode needle according to the present invention.

FIG. 5 is a diagram showing an experimental result of a heating effect by an ultrashort-wave heating treatment apparatus using an electrode needle having an inductance member in an electrically floating state.

FIG. 6 is a diagram showing an experimental result of a heating effect by an ultrashort-wave heating treatment apparatus using an electrode needle having an earthed inductance member.

FIG. 7 is a diagram showing an experimental measurement system.

FIG. 8 is a schematic configuration diagram of a conventional ultra-short wave heating treatment device.

[Explanation of symbols]

1,1 'electrode (electrode plate) 2 electrode needle 21 Conductive needle member 211 Needle 212 installation part 22 Insulating layer member 3 Temperature detector (temperature detection means) 31 prism 32 optical fiber 4 High frequency generation control device (high frequency generation means) 5 Temperature measuring instrument 6,6 'cooling pad 7 Cooling water circulation control device 8 Inductance member 9 high frequency electric field 10 Insulating needle member (insulating layer member) 11 Conductive thin film 12 Biological sample (phantom) S living body S1 affected area (cancer cells)

─────────────────────────────────────────────────── ─── Continuation of the front page (56) Reference JP-A-7-8564 (JP, A) JP-A-6-190059 (JP, A) JP-A-2-121675 (JP, A) Actual development Sho-59- 114147 (JP, U) (58) Fields surveyed (Int.Cl. ⁷ , DB name) A61N 1/06 A61N 1/40

Claims (5)

(57) [Claims] And 1. A VHF warming as a third electrode in the treatment an electrode needles pierced biological affected part hollow conductive needle member is provided on the outer circumference excluding the front end portion of the conductive needle member, An electrode needle formed of a cylindrical body and an insulating layer member that is configured to be bendable, and a position near the tip of the electrode needle of the affected area that penetrates through the hollow conductive needle member. A temperature detecting means provided, a pair of electrode plates mounted on the surface of the living body with the affected part sandwiched therebetween, and a high frequency generating means for supplying a high frequency between the pair of electrode plates, the conductive needle member,
Conducted on the inner peripheral part, the front surface and the outer peripheral part of the insulating layer member.
An ultra-short wave heating treatment device, characterized in that an electroconductive thin film is formed . 2. The ultrashort-wave hyperthermia treatment apparatus according to claim 1, wherein a proximal end portion of the conductive needle member is connected to one of the pair of electrodes. 3. The ultra-short wave heating treatment device according to claim 1, wherein a proximal end portion of the conductive needle member is grounded. 4. The ultrashort-wave heating treatment device according to claim 1, wherein the base end portion of the conductive needle member is electrically floating. 5. The ultrashort-wave heating apparatus according to claim 1, wherein a proximal end portion of the conductive needle member is grounded via an inductance member.