JPS6021744B2 - Electromagnetic radiation energy hyperthermia device system and heating application tool for the device system - Google Patents

Description

[Detailed description of the invention]

FIELD OF THE INVENTION The present invention relates to the field of device systems for irradiating biological tissue with electromagnetic radiation for medical hyperthermia purposes, and in particular to the field of device systems for irradiating biological tissues with electromagnetic radiation for medical hyperthermia purposes, and in particular to the field of device systems for irradiating biological tissues with electromagnetic radiation for medical hyperthermia purposes, and in particular to the field of device systems for irradiating biological tissue with electromagnetic radiation for medical hyperthermia purposes, and in particular for the field of annular device systems in combination with hyperthermia devices of this type. This invention relates to a radiant energy thermal application odor device. BACKGROUND OF THE INVENTION A variety of therapeutic treatments are currently in common use for human cancer. These treatments include surgery, irradiation from X-ray or radioactive sources, and chemotherapy, and these treatments are often combined in various ways to enhance the effectiveness of the treatment. Although this type of conventional therapeutic technique has been successful in treating many patients with lotus and prolonging the lives of many others, it is often ineffective against many types of cancer, and is often This has a very negative and tremendous impact on the level of treatment required, if not on the level of treatment required. For example, long-term treatment of cancer patients with X-rays or chemotherapy can leave many patients vulnerable to common, if not fatal, infections such as influenza and pneumonia. attempts to destroy or suppress the patient's own immune system to a certain extent. Also, many patients with advanced cancer or pre-existing conditions are too frail to endure the trauma of surgical or other cancer treatments. Therefore, it cannot be treated and must be stopped. The prevalence of human cancer, the typically dire consequences, and the frequent ineffectiveness of current treatments mentioned above have led medical researchers to discover and develop improved or other cancer treatment methods with combined treatment devices. We are constantly researching our prospects. Over a long period of time, hyperthermia, or hyperthermia therapy that artificially increases body temperature, has been found to be extremely effective in treating various physical disorders and actually doubling the body's thermal defense mechanisms. There is. Recently, hyperthermia has been used alone in human cancer treatment.
Alternately, it has enabled the use and effectiveness of major areas of research in combination with traditional addiction treatments. This study shows that hyperthermia technology, in combination with conventional short-term treatments, is highly effective in treating many or most types of human cancer without the often severe and harmful side effects. This is important because it seems to have the potential to. Researchers working on hyperthermia in cancer heat the malignant glands at temperatures slightly lower than those that are harmful to most healthy cells, which usually leads to extremely bad side effects and the proliferation of many types of malignant cells in the human body. Cases of scales being thermally destroyed have been reported. Additionally, it has been discovered that many types of tumorous masses have substantially weaker than normal heat transfer or heat dispersion properties, which means that they have fewer blood vessels and less blood flow. It is presumed that this is due to the characteristics that there are few. Therefore, it appears that this type of proliferation can be treated selectively with hyperthermia. The result of the growth of a poorly vascular malignant tumor is that it is heated to a temperature several degrees higher than that reached by the directly surrounding healthy tissue. This means that the proliferation of this type of malignant tumor, which is less heat-sensitive than normal tissue, can be treated with hyperthermia without destroying normal cells, and furthermore, the growth of this type of malignant tumor, which is less heat-sensitive than normal tissue, can be treated with hyperthermia. Time hyperthermia treatments are promising and usually have benefits for important medical reasons. In this regard, researchers generally believe that as a result of the thermal properties of most malignant tumor growths and the thermosensitivity of normal human body cells, hyperthermia temperatures for the treatment of human cancers are relatively narrow, effective, and safe. They report that the temperature must be strictly limited within a range.
It has been discovered that below a limiting temperature of about 41.5° C., significant thermal destruction of the bulk of the cells does not normally occur. It is believed that low hyperthermia temperatures, on the contrary, stimulate the undesirable growth of many types of malignant tumors. At slightly higher hyperthermia temperatures, in the range of about 43 qo to 45 qo or above, heat loss is uniformly observed in most types of normal cells. Great care must therefore be taken not to exceed these temperatures for healthy tissues. Elevated temperatures and prolonged irradiation are of course important factors in limiting heat loss to healthy tissue. However, if a wide or limited part of the human body is heated above the range of 43 qo to 45 qo,
Severe injury or death can be expected as a result even if it is for a relatively short period of time. For example, A.R.
``Recent Results of Research on Selective Thermosensitivity of Cancer Cells,'' published by Springer in 1977.
Research. Selective HeatS
The e-ship itMV) discusses experimental observations regarding malignant eye water and the thermal sensitivity of cells, and the observed time for death due to heat is semi-logarithmic, with time vs. temperature being a straight line. (See page 9 of the same book). It has often been found that various normal human skin lesions or near-surface cancers respond favorably to treatment by direct application of surface heating, such as hot baths which produce surface hyperthermia where applied.
However, the growth of malignant eyelids in deep areas can be prevented by surface heating alone, without simultaneously damaging the surrounding healthy tissue, mainly due to the heat transfer characteristics of the characteristic blood flow of the existing healthy tissue in the middle. Cannot be heated to destructive temperatures. Non-surface heating techniques, which involve artificially inducing elevated body temperatures in thought exposed to infectious diseases, have often been used in the past. However, this is rarely done satisfactorily due to the difficulty of keeping the heat within an acceptable hyperthermia treatment range from the disease itself and the risk to the patient when attempting to maintain the heat at the required high temperature level. Hyperthermia techniques, which circulate heated blood throughout the body, are also generally unsatisfactory due to slow treatment and trauma to the patient. Because of this and other deficiencies in existing hyperthermia technologies for the treatment of human cancer, deep-penetrating electromagnetic radiation (ELEC) has been used to induce biological hyperthermia in living tissue.
tromagnetic radiation; EMR)
The possibility of using it is currently of interest, especially for hyperthermia treatment of deep and/or widely metastatic malignant pupillary growths, and also for superficial or near-superficial tumors. We are currently seriously researching this as a viable option. Historically, alternating current frequencies of about 1 Hz or more were discovered at the end of the last century to penetrate and heat biological tissues. As a result, high frequency currents are widely used for therapeutic treatment of common human diseases such as infected tissue and muscle injuries, usually in the MHZ frequency range. At the beginning of this century, the name “diathermia” was given to this EMR tissue heating technology, and MHZ
Several unrelated EM old frequencies in the range have been widely cleared for use in diathermia therapy by the Federal Executive Commission (FCC) in the United States. Experimental treatment of malignant tumor growth in living tissue by radiofrequency EMR-induced hyperthermia has been reported since at least 1933. For example, J. W. Siereshewski (J.
．． W. Schereschewsky) 1933 King 4
The title of his self-published Radiology book, “Biological Effects of Large High Frequency Electromagnetic Radiation Energy,” contains 400
Therapeutic or inhibitory effects of EMR hyperthermia on sweet day rat tumors at EMR frequencies up to MH2 have been described. A compendium of research in the field of EMR hyperthermia was also presented by Shereshsky. Recently, for example, in 1974, GuyUhma
n) and Stonebrid Trout in Proceedings of the IEEE (1974)
In January 2017, No. 62, No. 1, the paper titled "Hypertherapeutic Application of Electromagnetic Force" summarizes the background of research on high-frequency EMR medical hyperthermia and discusses recent experimental activities in this field. A number of recent papers on EMR hyperthermia in cancer have been published, for example, in the book ``Hyperthermia and Cancer Treatment by Radiation'' by Christian Streffer, published in 197 Mother Urban and Schwarzenberg. Although there have been some reports of seemingly successful medical results using EMR-directed hyperthermia to treat malignant tumor growths in humans, this treatment is usually of an experimental nature. It is commonly used in patients with incurable or otherwise considered terminal cancers, as it usually encounters serious problems with hyperthermia damage to healthy tissue. Conventional surface heating, such as The problem of healthy tissue damage is particularly caused by the thermal destruction of malignant tumor growths deep in or in close proximity to heat-sensitive tissue.This unexpected EMR heat to healthy tissue The damage is due to the design and use of existing EM legacy irradiation equipment rather than fundamental flaws in the concept of EMR hyperthermia processing. For example, EMR equipment is often used with excessive radiation and/or
The heating area was improperly managed. Another disadvantage is that the frequencies assigned for specific diathermal treatments commonly used are generally inappropriate radiant frequencies for deep penetration. In addition, existing EMR hyperthermia devices and techniques are limited by the aggressiveness of the energetic radio waves used, either through unique reflections at interfaces between different types of tissue, or through the use of more than one EMR applicator at the same time. There is a tendency to create thermal "hot spots" in healthy tissue and increase the suffering caused by physical interference. In order to overcome these and other problems of poor integration with previously available EMR hyperthermia devices used for medical research or other medical purposes, the applicant has disclosed US Patent Application No. 002,584 and No. 048,515 was filed in the United States for an improved EM crotch hyperthermia device. These patent applications describe and claim a parallel plate and waveguide type EMR thermal applied odor and a combined EMR system, which applied odor is particularly suitable for biological or extracellular tissues. It is adapted to irradiate objects to be mimicked. The potential of wide range EMR is highlighted, allowing for the study of key parameters in combination with hyperthermia treatment of malignant tumors in humans, for example. This patent application also describes the simultaneous operation of two or more thermally applied odors arranged to improve deep tissue heating properties. Applicant's following U.S. Patent Application No. 05005
This number describes an acicular, penetrating EMR thermal application odor that can perform EMR hyperthermia in subsurface texture areas. These intrusive applications can be arranged in a controlled manner to surround a localized tissue area, such as an area containing a malignant tumor, resulting in near-uniform heating in the surrounding area by active interference of synchronized EMR electromagnetic fields. It is written about. However, there is still considerable demand for EM hyperthermia devices that can deeply and uniformly EM heat thick tissue masses, such as those in the torso and thighs of an adult body, where large and widely dispersed growth of malignant tumor is found. There is. For similar parts of the human body, an encircling annular EMR thermal applied odor device with an array of small applied odor is used.
EMR from all around the surrounding human body part for EMR heating.
Energy is released inward, which is generally desirable. For this purpose, a large annular magnetic coil is used to radiate a magnetic field through the coil to the part of the body where it is placed. Although such radiated magnetic fields are known to penetrate deeply into human tissue, uniform cross-sectional heating of the surrounding tissue remains difficult to successfully achieve. This is due to the fact that as the center of the enclosed tissue portion approaches, a progressively smaller tissue volume is presented to the magnetic field coupling. Therefore, when such an annular magnetic coil is used to hyperthermia biological tissue, it is expected that the surface tissue portions will be heated even more than the underlying tissue portions. A similar thermal gradient appears to result from a conventional annular EMR applicator made from multiple individual application odors used for localized EMR heating. Although some improvement in deep heating is expected by placing a large number of individual EMR application odors around a tissue area and operating them all at once, the necessary uniformity of tissue heating depends on tissue characteristics. It is only expected from a specific design structure that was previously unknown to the public regarding the shape of the radial aperture. Considering the above-mentioned narrow effective and safe thermal treatment range of only about 400, if all types of malignant tumors can be successfully treated by hyperthermia technology;
The need for a gradual thermal gradient through the surrounding tissue appears necessary. Therefore, uniformity of sample heating must be a critical design principle for EMR equipment. However, when success has been experienced in thermally treating deep malignant tumors with an annular heat-applied odor device of the type previously used, the results have been milder for malignant pupillary lesions that are greater than the desired uniformity of heat. The cause appears to be more due to the thermal dispersion properties.
The uniformity of the heating, which was not used as a secondary method, is effective against the malignant Hitotou cells of Group 4, which are widely dispersed in the deep region at the beginning of Hitotou proliferation, for example, before the related low heat transfer properties become obtrusive. Heat treatment could be used. The ability to substantially uniformly heat at least an enclosed portion of tissue is also of critical importance in the field of EMR hyperthermia research, for example in hyperthermia effects on normal healthy tissue. In addition to the difficult medical problems associated with non-uniform EM tissue heating, traditional annular thermal application has other problems. As an example, because there is less impedance matching to the tissue section being irradiated, many of the devices used are narrow frequency band devices and require power from sources that are much larger than what is actually irradiated to the tissue sample. It is said that This requires unnecessarily expensive equipment. This is due to the high cost of typically high power EMR power supplies, as well as the need for special tuning equipment and high temperature resistive components where the power dissipated is converted to heat. The amount of stray radiation leakage energy is also likely to increase, requiring costly EMR shielding to prevent possible radiation hazards to equipment operators as well as the equipment for such impedance matching. For these and other reasons, the inventors have developed a corresponding annular EM-applied shell that provides improved uniform EM heating to surrounding areas of biological tissue or tissue-mimetic materials. Invented the old EM irradiation method. The inventor's improved annular heat applicator device is suitable for any purpose for which EMR heating is required or desired, such as medical hyperthermia treatment of cancer or other human body disorders. Whether in the field of medical research or in other fields of medical research, the above-mentioned uniformity of heating is exhibited. SUMMARY OF THE INVENTION In accordance with the present invention, an electromagnetic radiation energy hyperthermia device system provides substantially uniform electromagnetic radiation to a generally cylindrical biological tissue sample having predetermined cross-sectional dimensions and known loss material electrical properties. an electromagnetic radiant energy source at a preselected radiant energy frequency f, and an annular thermally applied odor device. This applied odor device has a special characteristic impedance,
E on the central axis sized to receive the radiation input and tissue sample.
It is provided with means for forming a gateway for MR irradiation. The central closure forming means forms a circumferential discharge hole around the checkpoint and along the checkpoint, the discharge hole being selected between the characteristic impedance of the applied odor device and the loading impedance of the receiving sample placed in the discharge hole. It has a vertical height h and a perimeter length w selected to produce impedance matching at frequency f. This type of indirection matching not only increases the uniformity of EMR heating of the sample, but also allows operation over a relatively wide frequency range to accommodate variations in sample size and type. The system also includes electromagnetic radiant energy transmission means for interconnecting the energy source with the radiant energy input of the thermal application odor system. More specifically, the radiation frequency of the energy source is preselected so that the wavelength corresponding to the sample received at the entrance of the applied odor device is a predetermined function of the cross-sectional dimensions of the sample. The radiant energy frequency is preferably chosen such that the corresponding wavelength in the received sample is between two-thirds and twice the cross-sectional dimension of the sample, thus causing interference of incremental wavelengths in the central part of the sample. to increase energy and heating. The EMR coupling between the discharge hole and the receiving sample is achieved by using a flexible annular fluid-containing ring mass placed around the central entrance to fill the space between the applied odor device and the receiving sample. It can be enhanced by including it in The heat-applied odor device is constructed in a composite form of applied odor sections electrically arranged in parallel, each having the same characteristic impedance. The characteristic impedance of the applicator device is then the parallel sum of the characteristic impedances of the applicator. The characteristic impedance of the piece is preferably chosen to be 50 ohms, as compared to the 50 ohm impedance of conventional EMR components. The EMR transmission line between the energy source and the applied odor device includes a line splitter;
There is a 50 ohm first transmission line connecting the energy source and the line splitter, and a number of 50 ohm second transmission lines connected in parallel between the line splitter and the radiation input portion of the applied odor piece. The child can synchronize all applied odor components from a common energy source. Electrical loading of the cap is performed by providing a dielectric liquid that fills the radiant energy emitting area of at least the applicator section. Cooling of the surface portion of the sample being irradiated is sometimes necessary and desirable to increase the uniformity of heating of the sample, and means are provided for flowing a dielectric liquid into the radiant energy emitting area of the material. In order to use distilled water as the dielectric liquid while avoiding discontinuities in the energy emitting field, the application area of the piece comprises a number of spaced apart radial pieces of dielectric material. In a special configuration, the heat applicator device consists of two individual EM old applicators each arranged at 90°C.
It has four applied odor pieces arranged on the inside. In some variations, the coaxial applicator apparatus includes a single thermal applicator having a closed input end for electromagnetic radiation and an open sample receiving end. The applied odor comprises coaxially spaced inner and outer conductive shells, each shell having a radially diverging area at the input end and a radially converging area at the opposite end. .
The radially converging end areas of both shells are axially separated such that the converging end area of the outer shell is further from the input end than the converging end area of the inner shell, and the radiant energy release holes are both is formed between the convergent end areas of the. A conductive shell is formed with a generally cylindrical intermediate region between its diverging weave region and converging end region. Both the inner and outer shells are circular in cross section everywhere and are spaced to provide a substantially uniform impedance along the applied odor in either area. It is clear that the applied odor device could be used for biological tissue samples of other species of EM radiation. However, the advantages of roughly combining this device system are:
a generally cylindrical body having a preselected cross-sectional dimension and known electrical characteristics of a lossy material, comprising a source of electromagnetic radiation energy and an electromagnetic energy transmission means connecting the energy source and an applied odor device for transmitting electromagnetic energy therefrom; Systems adapted to produce electromagnetic radiation heating of biological tissue samples have been particularly successful. A method compatible with said system for heating a generally cylindrical biological tissue sample with electromagnetic radiation energy determines the cross-sectional dimensions and lost material properties of the sample to be irradiated; The method consists of selecting the heating frequency of tortoise-magnetic radiation energy that deeply heats the sample. The yield coefficient of the sample is determined from the selected electromagnetic radiation energy frequency and the loss material properties of the sample, and the dielectric coefficient of the sample is determined.
Determine the size of the radiant energy discharge hole of the annular radiant energy applied odor device that provides impedance matching between the specified impedance of the applied odor device and the negative impedance of the sample as seen from the discharge hole at the selected frequency, and accordingly It also includes the process of manufacturing a radiant energy applicator. After receiving the sample into the annular application odor device, the sample is irradiated with a selected electromagnetic radiation energy frequency. The process of selecting the frequency of the radiant energy also includes the process of determining the wavelength of the electromagnetic waves of the sample that is between two-thirds and twice the cross-sectional dimension of the sample. The step of sizing the radiant energy release hole is to set the preferred loading impedance of the sample based on the specific impedance of the applied odor, and to determine the height versus length that equates the sample impedance to the preferred load impedance when viewed from the release hole. It includes the step of creating a discharge hole with a certain ratio. The step of making the annular thermal application odor device further includes making the application odor device from a preselected parallel arrangement of a number of application odor pieces each having a preselected characteristic impedance, where the application odor device is The specific impedance of the applied odor device is the parallel sum of the impedances of the individual pieces, and each piece is connected in parallel to a common electromagnetic energy source, allowing for synchronized operation of the pieces. The method also includes the step of changing the phase of the electromagnetic radiation energy to selected sections of the applicator section to shift the type of tissue heating to the sample. Also, the process of creating a circular applied odor involves one E
It also includes creating a single applicator that is 360o coaxial with the MR radiation aperture. EXAMPLES A better understanding of the present invention may be had from the following detailed description taken in conjunction with the accompanying drawings. As schematically illustrated in FIG. 1, an electromagnetic radiation energy (formerly known as EM) hyperthermia device system 10 according to the present invention includes an annular thermal dust tool device 12 made for EMR irradiation and EMR uniform heating of biological tissue. It is equipped with "Biological tissue" as used in Shigeru includes not only actual biological tissue, but also materials that mimic biological tissue, such as "model tissue" commonly used for experimental EMR hyperthermia purposes. widely understood. As shown, and as further detailed below, the applied odor device 12 may be an array of individual or separate EMR applicators 14, which apply odor from multiple applicator device parts. It was built on the 16th. A cylindrical closure 18 is formed through the applied odor device 12 in the mari direction, the closure being shaped to receive a generally cylindrical biological tissue such as a human limb or torso section, and the closure being shaped to receive a generally cylindrical biological tissue such as a human limb or torso section. As will be explained later, the size is almost determined by the size of the sample. A circular radiation aperture or window 22 is formed in the outer periphery of the applied odor closure 18 through which electromagnetic radiation from the device 12 is emitted radially inwardly to the sample 20 and then to the applied odor longitudinal axis 24. be done. As mentioned later, Sekiguchi 1
The diameter D of 8 and the height h' of the applied odor device 12 are the same as the dimensions of the radiant energy discharge hole 22. In order to obtain a good EMR coupling to the sample 20, the intermediate candle or gap S between the radiant hole 22 and the sample 20 is completely filled with a water-filled annular mass or a mirrored annular envelope 26. Good. By providing several S in the gap, a well uniformly emitted EMR electromagnetic field is ensured. The apparatus system 1 further includes an electromagnetic radiation energy source 0 and a generator 32. The EMR output of power supply 32 is connected to a first EMR transmission line or transmission means 34, which transmission line preferably comprises a conventional 50 ohm impedance coaxial cable. At the end of the transmission line 34, there is an applied odor device 1 divided into a plurality of parts as shown in FIG.
For two applications, a suitable parallel coaxial line splitter 36 is connected. A number of second EMR transmission lines or transmission means 3 of the same length
8 are interconnected for synchronized operation of the line divider 36 and each applicator section 16 and applied odor. For the four divided devices 12 shown, four parallel transmission lines 38 each have a conventional
Used with 0 ohm coaxial cable. As will be discussed below, since it is sometimes necessary or desirable to stagger the type of EMR heating to the specimen 20, asynchronous EMR phase changes or displacements between multiple lines 38 may be achieved by adding a conventional "line extension" in series with each line. This is done by inserting the child ``40''. This selectively changes the EMR length of the line. E.M.
Important relationships between the frequency of the R radiation and the application tool, such as the relationship between the diameter d of the sample (or other typical cross-sectional dimension) and the height h and diameter ○ of the hole 2 of the applied odor device for the component, With careful consideration, greatly improved EMR heating uniformity for the irradiated tissue sample 20 is achieved. As is well known, the amplitude of an electromagnetic wave is attenuated as the corresponding wave propagates through a lossy medium, and the more lossy the medium, the more the wave will be attenuated. The EM power density is related to the amplitude of the EMR wave and is attenuated as the depth of wave penetration increases, and this power loss, or attenuation, is usually expressed in terms of decibels per ton of material. It will be done. Furthermore, since EMR heating is a function of EMR power density, the EMR heating effect decreases or attenuates as the depth of wave penetration into the lossy material increases. It is also commonly known that the limits of the attenuation of the electromagnetic wave's amplitude and power density as well as the depth of penetration of the EMR wave into a lossy material depend on the applied EMR frequency as well as the electrical properties of the medium through which the wave propagates. Although the human body varies greatly in composition, for the purposes of the following discussion many parts of the human body will be considered to contain one of two general types of EM old loss material. That is, the high-loss type (H-type) represented by muscle, skin, and tissues with high water content, and fat,
Low-loss type (L
-type). The attenuation coefficient, or loss factor (db/db), of the EMR power density for each of these general H and L-type human body configurations is determined experimentally as a function of the applied EMR frequency; Typical values are shown in Table 1. "Loss 1-1" is the loss factor of EMR power density in a typical H-type material, and "Loss L" is the corresponding loss factor in a typical L-type material. From Table 1, the power density loss coefficient,
That is, the loss and the loss LL appear to increase with the added frequency, and at a given frequency the loss is larger than the expected loss L. The data shown in Table 1 is based on the article by Curtis Johnson et al. in Proceedings of the I.I.E. effect "(
Ionizing Effectisn Materi
This corresponds to the one shown as an example on page 692 and subsequent pages of ``Als and S$tems''. Table 1 Plane wave characteristics of tissue
The "penetration depth" or depth (seed) that progresses before only the father mountain decreases is immediately determined. The penetration depth is a small amount of EE which is ignored above.
It is believed that MR tissue heating occurs. From Table 1, it can be seen that the optimal EMR heating frequency N for a particular type of material to be irradiated can be selected as a factor of the loss day or loss L depending on the desired depth of EMR energy density penetration. I understand. Table 1 shows, for example, that the greater the desired penetration depth and heating, the lower the applied EMR frequency should be. Therefore, the high frequency MHZ has a characteristic of relatively low penetration, and it cannot be expected to deeply heat tissue without excessively heating the surface portion. Significantly deep energy penetration at high frequencies can only be achieved by applying excessive electromagnetic power density to the sample surface. It is also widely known that the applied EMR frequency and the corresponding EMR wavelength also depend on the type of material through which the electromagnetic waves propagate. Therefore, Table 1 also shows experimentally determined wavelengths corresponding to each of the frequencies listed, and the sunset is the wavelength of the H-type material, and the onset is the wavelength of the L-type material. From Table 1, it can be seen that for a given applied frequency, for example, the corresponding wavelength is several times shorter than the corresponding wavelength. As an illustration, Table 1
has a power density loss of 1 for an applied frequency of 20 MHZ.
．． The loss date of the H-type substance with 81 valence/arc and the corresponding wavelength input date of approximately 16.6 skin are displayed. Also, at the same frequency, the power density loss, loss L, for type L material is only 0.222 ddb/k, and the corresponding wavelength L is 5
It's 9.7. The effects of wavelength changes along with frequency and sample type become even more important. Because of the attenuation of this characteristic power density as electromagnetic waves propagate through lossy media, when a sample is irradiated with a planar EMR wave from a single direction, unless the sample has a very small diameter or cross-sectional size, the power density and The corresponding tissue heating is usually substantially less in the center of the sample than in areas closer to the surface of the sample. Therefore, for further illustrative purposes, if we assume that the irradiated H-type sample has a diameter of 15 mm, which corresponds to the diameter of a typical leg, then the power density in the central part, Pc, standardized to the surface power density Ps, is calculated by the following formula: is given by Pc,=7. Anti-ne x Lost days
{11 For example, at the above applied frequency of 20 MHZ, the power density Pc at the center of a sample with a diameter of 15 mm
, is less than the surface power density, about 13. Bait b, which accounts for only about 4.4%. There is therefore a significant temperature gradient across the sample, with the central portion being cooler than the surface portion.
Heating of the deep tissue for any desired purpose cannot be expected in this example to be achieved with irradiation from only one direction without excessively heating the surface portions of the tissue. When the lossy medium of sample 50 (Fig. 2a) is irradiated with waves that are polarized identically in opposite directions on sides 52 and 54, wave interference from the two waves causes an energy addition in the sample on the one hand. (co
It is expected that a subtraction (destr ratio t) part and a subtraction (destr ratio t) part will occur. For ease of explanation, the sample 50 is shown with a square cross section in Figures 2a and 2b. Areas of overlapping additive wave interference within sample 50 have greater power density and therefore tissue heating than other portions of the sample. In areas of the sample with overlapping but subtractive wave interference, the power density and hence tissue heating is less than in other parts of the sample. Irradiating the sample from both sides 52"54 is expected to create locally hot and cold areas within the sample. These additive wave interference effects can be used to enhance heating of the central portion of the sample. , which promotes uniformity of heating through the sample 50. When the sample 50 is irradiated with EMR waves of suitably matched frequency, phase polarization, and power from opposite sides 52 and 54, the superimposed synchronous electric fields cause A standing wave is generated in the sample.The polarization of the two EMR waves is on both sides 52 and 5 in the plane of Figures 2a and 2b as shown.
4, the same energetic additive wave effect occurs in the center of the sample. Under such special conditions, one E
The electric field from the MR waves joins directly into the area of additive wave interference,
The known square relationship between field strength and power density produces a fourfold power density increment in the center of the sample. By simultaneous EMR irradiation on both sides shown in the figure, the power density Pc2 in the central portion is given by the following equation. P=4Pc,
'21 However, if, on the other hand, the polarizations of the two irradiating electromagnetic waves are perpendicular, the total power density at the center is only the sum of the power densities of the two individual center sections, and the resulting heating of the center section of the sample is therefore few. As shown in FIG. 2b, there are two further directions from which the sample 50 is irradiated by synchronous electromagnetic waves having polarizations that match the two waves described above. When these two additional waves are directed to the remaining sides 56 and 58 of the sample 50, the electric field in the center of the sample is four times that of a single wave. Therefore, the central power density Pc4 for this is given by the following equation. P's = 1 c,
'3' As described later, the electromagnetic wave frequency limit is appropriately selected so that the combined additional electric field effect from the four waves at the power density Ps on the sample surface is negligibly small, Pc, = 4.4% The central power density synthesized from the four waves for the example Ps is 16×4.4%, or 70.4%, of the surface power density Ps. In this state, the EM eave heating in the central portion is approximately 70% of the corresponding heating occurring in the surface portion of the sample. With this level of central heating, the surface of the sample can usually be cooled sufficiently, for example by water cooling, to provide substantially uniform heating of the sample. The simple sample and radiation waveform of FIG. 2b look very similar to a cylindrical sample 20 surrounded by an annular thermal application device 12 as shown in FIG. It is divided into four pieces 16 from which four synchronous EMRs are emitted to the sample. It is therefore expected that the same central power density and sample heating as described above for square sample 50 will occur. However, in (Figures 2b and 2c) four separate 90o
The equation showing the central power density PM of one vowel produced by irradiating the sample 50 or 20 from the direction of represents the theoretical maximum central partial power density that can be achieved using an annular applied odor. This is because there is no other independent radiation direction for the applied odor around the cylinder. A slightly different result for the power density in the center of the sample of the high-loss “model” is shown in the paper “
Data from ``Ion Effects in Matter and Tissue Systems'' and Jasik Lines'' published by McGraw-Hill in 1961.
Antenna Engineering Handbook” (An MEngine
It is obtained using the equation for power loss in a lossy medium as seen in EringHand 8). From this analysis, the power density Pc at the center of the sample due to a single EM calm wave is calculated to be about 3.13%, and P for this is about 50% of Ps (compared to 70% of the upper air). . However, both analyzes agree relatively accurately with our experimental determinations on homogeneous "model" samples, and the value of P
The yield is about 61%. Many body parts consist of several layers of different tissue types with different water content,
More rigorous calculations of the central power densities Pc, and P are also performed for particular body parts to account for their relative non-homogeneity. Such a detailed analysis can be found in the applicant's unpublished paper titled ``Annular thermal W-sphere device for deep heating of cylindrical or elliptical tissues.'' As expected, such a rigorous analysis Different parts of have different values of central densities Pc, and Pc4.For example, in the human chest part, such an analysis shows that the power density Pc4 of the combined central part is theoretically larger than the above values. However, regardless of the actual or theoretical value of Pc4, the important thing is that the power density at the center of the sample can be increased by additive wave interference from four synchronized EMR waves that impinge on the sample from four directions separately. , thereby substantially increasing EMR heating of the core and greatly improving EMR uniformity for biological samples due to hyperthermia with less heating than four separate EMR radio waves. However, this emphasizes that increasing the power density in the central part of the upper air and correspondingly increased EMR heating in the central part represents an optimum; This cannot necessarily be achieved simply by simultaneously irradiating the sample from tens of thousands of separate directions.The most appropriately enhanced effect at the center can be achieved if the applied frequency is selected with due consideration to the size and components of the sample. If the applied frequency is not chosen properly, there will be a low power density in the central region and other hot or cold regions will be created in the sample due to additive and subtractive wave interference.The present invention In our experiments, when the wavelength of the EMR waves in a particular irradiated sample falls within the appropriate range given by indicates that there is a minimum hot spot and cold spot. 2/Flip^H/L Kuphant

[4' finally d
is the diameter of the sample or a characteristic cross-sectional dimension of the sample, H/L is the applicable frequency in H-type material or L-type material, depending on the sample type, and H is the corresponding wavelength of the sample. It is observed that if the EMR frequency cutoff is chosen such that ^H/L is greater than about twice the sample diameter, it is difficult to obtain impedance matching and there is little improvement in the heating of the central part. In contrast, if ^H/L is about 2/3 or less of the sample diameter,
Hot spots are observed to occur off-center, as are cold spots elsewhere. However, if the applied frequency is chosen such that the corresponding wavelength is within the range given by Equation '41, the undesirable minimum 'hot and cold spots will be substantially added to the central part while producing them in other parts. It can be seen that thermal heating occurs. Procedurally, if the sample diameter is d, the optimal EMR wavelength range is determined by Equation '41. The optimal EMR frequency range for EMR heating of the sample is selected from Table 1, which displays the input and input L for type 1 and L-type materials for various corresponding EMR frequencies. As shown in the figure, for a sample diameter d of approximately 33 arcs, which corresponds to the diameter of a general adult's chest or pelvis, Equation '41 is approximately 22 to 6 & that wavelength / L is the heating uniformity of the sample over the grain. Indicates that it will be selected against. Considering that the sample contains both H-type and L-type parts due to various skin layers, muscles, fat, and bones, Table 1 shows that the corresponding EMR frequency na of about 10 MHZ is for sample irradiation. It is often selected as the wavelength corresponding to the occasion ^ day is 27 skin, ^
L is 06, which is close to the optimal wavelength range of 22 to 66 skin. Table 1 shows 10 times HZ for a pure daily type sample.
Lower frequency na below can also be chosen, pure L-
It is shown that frequencies greater than 10 MHZ can also be chosen for mold samples. It can also be seen from Table 1 that, by way of example, for small diameter samples a high frequency is required to correspond to a low optimum H/L range in combination with the small diameter. By way of example, to perform uniform EMR hyperthermia on a limb with a diameter of about 20 mm, from equation {4} the wavelength is between about 13 and 14 arcs, and Table 1 shows the frequencies of EMR radiation of about 20 MH2. This indicates that it is preferable to select From the above, 13.5; 27.12: 40.68: 915; 2
The FCC-assigned diathermy frequency of 450:Moth 00:20129MHZ is optimal for EMR heating of anything other than relatively large or small samples in an annular thermal application odor device such as Device 12. It turns out that it is not. Furthermore, using diathermy frequencies such as those assigned by the FCC for common sample sizes is expected to result in undesirably high thermal gradients and/or undesirably hot and cold spots in the sample. Assuming that an optimal EMR heating frequency or frequency range has been selected for the system 10 according to the procedure described above, it is important to provide a good impedance match between the applied odor system 12 and the sample 20 packed into the system. Important considerations remain. Matching the impedance between the device 12 and the sample 20 means determining the size of the fake emission hole 22 according to the size and characteristics of the sample at the selected EM old frequency, as will be described later. Impedance matching between device 12 and sample 20 is important for a variety of reasons, some of which are well known to those skilled in the microwave arts. Without good indirection matching between the emitter and the load,
For example, it is known that applied EMR energy is reflected from the load into the emission system. A combined effect of the described EMR system 10 is that the transmission line 34 typically requires costly tuning means (not shown) near the energy source to protect the energy source 32 from reflected wave energy. Furthermore, equipment system 101
Since the energy from this established resultant standing wave must be dissipated as heat into the system, an unnecessarily expensive thermal resistance system component is also required to add to the system cost. Despite the impedance matching of the apparatus 12 to the sample 20, the apparatus system 10, when equipped with the tuning means and thermal resistance components described above, is capable of providing the amount of EMR power to the sample required for EM hyperthermia. is usually overexcited. However, if this overexcitation is provided, the energy source 32 must be equipped with equipment that requires a higher output than is required for good impedance matching conditions, and the equipment system 10' will also have additional costs. Become. Furthermore, feeding EMR standing waves into equipment systems with weak load impedance matching generally results in more EMR radiation leakage than would otherwise occur, and this leakage is potentially harmful to equipment system personnel. . Weak load impedance matching therefore requires expensive leakage shielding devices in the system. An even more important problem with EMR hyperthermia devices, especially in conjunction with annular thermally applied odor devices, is that they weaken and concentrate the EMR energy in areas with limited impedance matching, creating unwanted hot spots on the sample. That is to say. In an annular applied odor device system such as device system 10, a sample hot spot with weak impedance matching is generated from this sample 20 in the case of a human body part that is not circular in cross section and has a protruding portion closer to the discharge hole 22 than the rest of the sample. try to arise. Although there is a weak impedance matching state in the part where the distance between the sample and the hole is the smallest, a large amount of EMR energy flow channel exists, and a high energy density of EMR is concentrated in the part of the sample that is the closest to the hole. give rise to Furthermore, it has been found that if good sample load impedance matching is achieved for the sample 20' at the optimum EMR frequency, the system 10 can be operated over a reasonably wide band. In other words, if the load impedance matching is good at the optimum EM old frequency as described above, the device system 10 will not cause excessive hot spots on the sample, and will not excessively require the output of the energy source or leak radiation. without, usually operating over a reasonably wide frequency range at approximately the optimum frequency. The ability to operate with such a wide range of systems is an important advantage, as it allows a given applicator system 12 and system 10 to be adapted to the size and composition of the various samples that would normally be encountered in the human body. It can be used effectively. Thus, for example, a single device 12 can be used to advantage for normally expected variations in the size components of the human body, and the optimum EMR frequency selected for each such variation. Therefore, for many sample sizes and types, only a few sizes of applicable odor devices 12 are usually sufficient, which reduces the cost of the device system. The starting point for impedance matching the device 12 to a typical sample 201 is the free space characteristic impedance filter. It is widely known that the impedance of free space is approximately 377 ohms per square. That is, a loading impedance of 377 ohms is "seen" when radiating from the square emission hole into free space. However, if the discharge hole is not square, such as hole 22, a different loading impedance will be observed. Load impedance Zo is given by the following equation. ro=h/w377 {5) Here, h and w are the height and middle (or length) of the emission hole, respectively, and the polarization of the emitted wave is parallel to the dimension of h. The ratio h/w is defined as the aspect ratio of the hole. By way of example, a horizontally elongated EMR vent 62 with an h/w ratio less than 1, as shown in FIG. EMR vent 64 is allowed to have a free space loading impedance of greater than 377 ohms. Therefore, widening the inside of the hole w has the effect of adding electrical impedance in parallel, while widening the height h of the hole has the effect of adding electrical impedance in series. When radiating to a medium other than free space, such as inside the sample 20, the equation '51' is as follows. zm=h/W device Ohm '6) Furthermore, Zm is the impedance of the medium, and em is the dielectric coefficient of the medium. For a hole 22 on a cylindrical surface with a diameter D, equation (2) becomes as follows. Zm of h 377:--
---mD〆Since the sample is "observed" in all parts of the hole 22, the hole diameter D is used in equation {71 rather than the sample diameter d. Furthermore, by filling the gap S between the hole 22 and the sample 20 with the annular soul 26 filled with water, the entire peacock D is filled with the sample-like substance. The dielectric coefficient of distilled water used in the annular mass is close to that of human tissue. Once the dielectric coefficient em of the sample is determined from equations {6) and [7}, the aspect ratio of the hole can be freely varied for any desired load impedance. This ability to freely select the load impedance Zm of the sample means that, as will be shown later, the thermal application odor of one or more 50 ohm applicators that matches the 50 ohm impedance of the commonly used EMR power source and transmission line It has the advantage of making the device more cost effective to use in the device system. In order to determine the appropriate value of the dielectric coefficient em for use in equations '6} and '7}, it can be seen that the dielectric coefficient of the material exemplified in sample 20 depends not only on the type of material but also on the radiant energy frequency. That is, different radiant energy frequencies for a given sample will present different negative drop impedances to the device 12, and the value of em will generally decrease with increasing frequency. It is known that the dielectric coefficient of a lossy material is a value given by the following equation and includes a complex value e gain. e grandpa = e skin ten jem''
'81e. em and em'' are the real and imaginary dielectric coefficient components, respectively, and e is the permittivity of free space. On the other hand, a real dielectric coefficient component and an imaginary dielectric coefficient component are displayed correspondingly for the H-type material and the L-type material. For example, the real component emr day and the imaginary component em'' day of the dielectric coefficient of the H-type material. are the corresponding components emrL and em″ of the L-type substance
It can be seen that the real number component changes little as the frequency decreases above 20 MHZ, which is substantially higher than L. Equation {8} shows that the complex number concession coefficient e is the load impedance, or the equation [6'
or '7} should be used to determine the aspect ratio,
For many types of biological materials using this dielectric coefficient real component emr, these equations calculate the Zm value (given h/w
ratio), which is found to be in close agreement with the experimentally determined load impedance. As an illustrative example of the formula for determining the shape of the apparatus 12, proceeding with the above example and using 10 molar MH to irradiate a 3 molar diameter day-type specimen
It is estimated that the EMR frequency " is selected at Z. From Table 3, it can be seen that the corresponding concession coefficient real component is 71.7.
1.7, the sample loading impedance Zm is explained as follows. zm = magazine x younger brother's poem ■ Zm = h/D x 14.17 (gong) formula (
The characteristic load impedance of the exemplary sample is 44.5 ohms/square (assuming h/w equals 1). Continuing with the example of use, the specific application device 12 used is made of four pieces 16 arranged in a circle in parallel arrangement in FIG.
Assuming that each piece has an impedance of 50 ohms, the desired sample loading impedance for each device is 50 ohms.
/4 ohm, or 12.5 ohm. The height-to-diameter ratio h and D of the corresponding discharge hole 22 is 0. It turns out that it is woven. Further assuming that a discharge hole diameter D of about 5 peaks is preferred for a sample of 3 specific current diameters, the corresponding optimum hole height h is determined to be 44 degrees for load impedance matching. It is preferable that the four pieces 16 each have a height of approximately 44 mm × 50/4, that is, 39.3 mm. As shown in FIG. 1, each applicator piece 16 is further divided into 2 x 2 rows of four individual 50 ohm applicators 14, each of which is approximately 22 feet high xl9. .7 It is preferable to be an enemy. Similarly, for a tissue sample 20 having a predetermined or selected mold diameter (or cross-sectional dimension) d, the optimum EMR irradiation frequency is set from equation [3' and Table 1]. The sample dielectric coefficient corresponding to the sample type and the set irradiation frequency is determined from Table 2. Using Equation '7}, the sample loading impedance Zm, the height h or the diameter D of the discharge hole are determined based on design objectives or limitations to achieve impingance matching with the sample. As mentioned above, the ejection hole aspect ratio h/w is preferably selected such that one or more 50 ohm impedance application shells in an annular arrangement can be used. By choosing an appropriate EMR frequency cutoff and irradiation aperture shape based on the above description, this method provides a safe and uniform sample EMR heating that has not always been achieved with any type of applicator or applicator arrangement. It exhibits excellent theoretical and experimental results in a relatively economical manner. That is, in order to carry out the optimum benefits achieved by selecting the EMR irradiation frequency and ejection aperture shape in the manner described above, each individual applied odor, such as the applicator 14 of the device 12, has a separate illumination surface of the applied odor. That is, it is necessary to provide a substantially uniform EMR field across hole 66 (FIG. 1). As for the application of a uniform electric field, that of U.S. patent application Ser. However, it is even more advantageous to integrate the individual applicators 14 into a composite array so that the changes in the emitted electric field are minimized, especially at the corners of the intersections between the individual applicators 14. It turns out that there is. For this purpose, the use of a large number of very small individual applicators operated synchronously seems preferable, since corner effects are less apparent and the sample 20 is uniformly and neatly distributed. In practice, not only is it difficult and expensive to make and synchronize a very large number of 4-type applicators, but arranging a very large number of small applicators in a ring generally results in virtually no uniform heating of the sample. It is useless to do so. The use of two first and second circular rows 68, 70 of applied odor 14 stacked in the same bag orientation as shown in FIG. For many types of tissue samples, including generally large diameter samples, the EM sample heating is determined to be substantially uniform in the axial direction. However, for irradiation of the entire human body, which requires a truly long vertical height h, a circular array of applicators is required.
Alternatively, a modified coaxial applicator configuration may be preferred for such applications, as described below. Similarly, heating the EMR sample substantially uniformly around the circumference of the sample 20 can be achieved by arranging the eight application shells 14 in a circle in contact with each other, even for the large diameter samples described above. I found that I was getting results. Thus, the exemplary annular applicator 12 has two rows 6 of eight applicators in each row.
8, 70 circular arrays with the same applied odor 14
Equipped with. For convenience of construction and for other reasons that will become apparent below, the device 12 is shown divided into four 900 pieces 16 to form eight applicators 14, two of each piece. Each piece is separately supplied with electromagnetic energy from an energy source 33 described below. Thus, the annular applied odor device 12 is a composite odor applied structure made of one needle applicator; (FIG. 4) is a generally cylindrical compound hole formed. 1 between adjacent holes 66 for two rows of 8 applied odors, respectively.
350, and the perpendicular from the adjacent hole is 450. As shown in FIG. 5, the applied odor device 12 has upper, middle (center) and lower conductive ring plates 74, 76, 78, and corresponding circular inner circumferential green plates 84, 86, 88 that form the entrances of the applied odor device. and are integrated into a composite structure. Plates 74, 76, 78 may be made in the form of steel ground plates. The outer conductive plate 90 includes the outer peripheral edge 94 of the upper and lower plates 74 and 78,
98, respectively, and surround the device 12 on the outside of the series/parallel EMR energy receiver 100 as described below (FIG. 6). To better illustrate the EMR receiving section 100, the outer plate 90 has been cut away in FIG. The applied odor 14 is preferably constructed such that the applied odor device 12 is symmetrical about a central axis plate 102 made of a middle plate 76, as shown in FIG. The first applicator 14a of the first applicator array 68 includes first and second arms 108, 110 having a trumpet-like antenna structure and radiating inwardly and expanding toward the end in the circumferential direction. The radial inner edge 112 of the first plate 108 is in contact with the inner circumferential edge 84 of the upper plate 74 .
Similarly, the radial inner edge 114 of the second plate 110 is also electrically connected to the inner circumferential green 86 of the middle plate 76 . Similarly, the second applied odor 14b of the second applied odor row 70 is applied to the first and second spreading conductive plates 116,1.
18, whose radial inner edges are the lower slope 78 and the middle plate 76.
Midori 88 and 86 are the electricians, respectively. Opposing board 108
, 110 and 116 and 118 were chosen to maintain a constant application impedance of, for example, 50 ohms. radial outer ends 120 of second plates 110 and 118;
122 are electrically connected to each other by an octagonal conductive plate 124,
Conductive plate 124 is coextensive with outer plate 90 and radially spaced from the inner side and extends approximately one third of the axial height of device 12. The divergent sides of the applicator top plates 108 and 110 are closed by non-conductive rectangular first and second side plates 134, 136 (FIG. 5);
This side is preferably made of a hard dielectric material such as resin glass. Side plates of similar dielectric material are used to surround the sides of the lower application odor 14b. The radiant energy release holes 66 of the first and second all-applied odors 14a and 14b are also made of a rectangular plate 13 made of dielectric material.
8 (Figures 6 and 7) to completely close off the applied odor. Electromagnetic energy is supplied from the second transmission line 38 to the respective EMR input of the applicator 14 (14a and 14b) through the energy distribution section 100 of each applicator section 16. A second transmission line 38 associated with each section 16 by means of a distribution section 100, which is a parallel plate transmission line, is connected to the four individual application odors 1 in combination.
It is connected to each of 4. Four EMR distribution units 100
(only one shown) is generally "H" shaped and has first and second conductive pieces 140, 142, respectively. Short ears or tabs 144, 146 projecting radially outward from the center of the guide box pieces 140, 142 and placed at a distance.
A transmission line 38 (shown as a coaxial cable for convenience) is connected to this ear piece. The outer cable conductor 148 is connected to the first lug 144, and the inner cable conductor 150 is connected to the second lug 146 across the gap 152 between the ears 144,146. The gap 152 is selected to impedance match the transmission line 38 in a known manner, e.g.
wide ear piece 144 and 146,50 ohm transmission line 38
Assuming impedance, it is approximately 1 skin. Considering the second conductive piece 140, which can be exemplarily shown in FIG. 5, this piece has a sub-section 164 in which a second lug 146 is formed in an octagonal shape. The conductive piece portion 164 is parallel to the applicator axis 24 and is attached to the inner plate 124.
They are radially closely spaced to form a 5 ohm parallel plate EMR transmission line. The conductive piece 142 is the first application tool 1
The EMR input area of 4a is aligned with the circumferential surface of the ear piece 146.
The left and right parts 166, 16 are located a little apart in the axial direction from the left and right parts, respectively.
8 (FIG. 5), which extend radially apart from the plate 124 to the application 14a to form a parallel plate transmission line. The initial gap 170 between portions 166, 168 and plate 124 provides an impedance of 25 ohms, and the spacing is such that it creates a wide gap 172 with a matching impedance of 50 ohms for the two associated applicators 14a. It has a stepped section. If the inside of parts 166 and 168 are 5 skins, the gap 170
and 172 are 0.5 arc and 1 skin, respectively. A low dielectric spacer 174, such as a piece of styrene foam, is used to keep the conductors separated in the gap 172. Part 166 and 1
Both ends of 68 are octagonal portions 176 and 178, respectively, which extend in the direction of the ball and are in contact with the upper plate 74. However, beyond the EMR distribution portions of the two applied odors 14a, octagonal portions 176, 178 extend in all axial directions and extend beyond the upper end green 180 of the inner plate 124, and the member 142 and the inner plate 124 stop at the upper edge. Create a parallel plate transmission line between. As can be seen in FIG. 6, the EMR input path indicated by arrow "A"
176 and the intersection area of the inner plate 124 is formed at the left side applied odor 14 input portion. Similarly, the EMR path is on the right side application tool 1.
4a, the same applied odor 14b is created on both sides. (Arrow “B”). The radial hard plate 182 connects the conductors 166 and 16.
It can be seen that it is attached across 8 and maintains a gap with the inner plate 124. Similar conductors are attached to corresponding portions of second guide member 142. The first conductor 140, which provides electromagnetic energy from the transmission line 38 to the lower two applicators 14b, is made as a mirror image of the described conductor 142. Therefore, the first conductor will not be described further. Interference due to EMR coupling of the transmission line 38 to the ear piece EMR distribution section 100 will cause the outer conductive plate 90 to extend outwardly from the ends of the ear pieces 144, 146 at least about five times into the gap 152, e.g. This can be avoided by keeping them at least a distance equal to about 5 skins apart. In the configuration of the EMR input section 100 described, the energy source 3
2 to an individual applicator 14 with a piece 16 for applied odors (
14a-14b) Entire equipment system 101 Broken 50
Ohmic impedance matching is maintained (Figure 8). However, because the four applicator sections 16 are electrically parallel, the applicator device 12 itself has an impedance of only 12.5 ohms. Line splitter 36, which includes a standard reactive power divider from Micro Labno FXR of Livingston, New Jersey, therefore also provides impedance matching. Furthermore, the annular applied odor device 12 has a dielectric fluid channel 184.
to the applied odor 14 (14a and 14b), the flow path of which is closed by a dielectric fluid such as distilled water, or at least its EM
R is supplied to the discharge section and flushed. The channel 184 is double to allow the fluid to flow, or the applicator 1
A flow entrance (not shown) is provided between 4 and 4. Application tool 1
By using a fluid dielectric at 4, the 50 ohm characteristic impedance of the applicator is more convenient than would otherwise be possible. Pump 186 (FIG. 1) may also flow a dielectric fluid through applicator 14 to cool the applicator and the surface portion of sample 20, as may be desirable or necessary depending on the characteristics of the sample. The uniformity of sample heating over the entire diameter d of can be improved. Filling the applied odor 14 with a dielectric fluid may be accomplished by closing the EMR input area of each applicator with a dielectric element 188. In order to easily use distilled water as the current transfer medium at low cost, a large number of thin dielectric plates or dielectric pieces 190 can be arranged at intervals within the application chamber. The pieces 190 that extend across the applied odor have various lengths, and the pieces extend from the front aperture plate 138 so that the axis of the applied odor increases as the distance from the center of the applicator device increases. The distance away from 24 becomes gradually shorter. Applicable odor board 108,
With respect to the thin plates 192 of dielectric material attached to the inner surfaces of the surfaces 110, 116, 118, the dew strips 190 are shaped to increase the thickness of the solid dielectric material toward the axis of application 24. In this regard, it has been determined that, in construction in the form shown, the applicator 14 is preferably filled with a material having a dielectric constant of about 100 nm. Liquid fluid materials are preferred for cooling the fluid flow.
Liquids with modest dielectric constants are not easily obtained and are relatively expensive. Therefore, it is advantageous to use distilled water, which has a dielectric constant of about 78, instead. This can be done using dielectric strip 192 and plate 190 without using a thick butterfly of solid dielectric material. This is to maintain a uniform energy distribution.
. The following equation relates to the required thickness of the transfer body with respect to the total thickness t in the applicable cross section. where er is the desired dielectric constant (e.g. the total above), e
d is the dielectric constant of the solid (for example, about 2.2 for resin glass)
It is. 78 indicates the dielectric coefficient of water. So for the above concession coefficient, the ratio td/tt is approximately 0.0
Equal to 87. This means that the height (tt) of the applied odor 14 is axis 2
4 indicates that the thickness of the solid dielectric (td) must be increased to maintain a constant composite transfer coefficient (er). It is usually the applied odor plates 108, 110 that provide the desired thickness increase relative to the thickness of the solid dielectric.
, 116, 118 are formed with a bare dielectric plate 192, so that the thickness of this plate increases as it approaches the mouse 24 based on the above relationship. However, with a relatively thick portion of dielectric proximate the edge of the discharge hole 66, there will be undesirable electric field discontinuities or disturbances through the dielectric. In order to properly form a solid dielectric in a rectangular shape while avoiding electric field discontinuity in combination with a dielectric, the stepped dielectric piece 190 is made with an appropriate length and has a td/t of 0.87.
When properly spaced to satisfy the t ratio, the electric field discontinuity emitted by each induction piece has little adverse effect on the uniformity of tissue heating. An important advantage of incorporating four applied odor sections 16, each individually connected to an energy source 32, is that when non-uniform heating of the sample 20 is required, a type of EMR tissue heating can be applied to the sample 20.
This means that, for example, one or more track extenders 40 can be manipulated to reduce the EMR between the pieces.
This is to perform a synchronous operation in which the phase is shifted to shift the type of energy density applied to the sample. Also, for example, instead of all four secondary wires 38, a line divider that divides into one, two or three secondary wires 38 is used,
When the energy source 32 is connected to any of the items in 6, the heating mold of the sample is shifted toward one or more discharge applicators (a variation of FIG. 9). This is a first modification of the device system 198. In this modification device system 198, the hexagonal applicator device 200 has six applicator sections 202 arranged in contact with each other in an annular manner, each section being individually separated by a secondary transmission line 204 from a line divider 206. It is receiving EMR energy. This divider 2
06 is also connected to the EMR energy source 208 by a primary transmission line 210. Adjacent E of six applied odor pieces 202
The MR emitting hole 212 forms a substantially cylindrical radiation emitting compound hole 214 around the sample receiving entrance 216 in the axial direction. Each piece 202 includes a single applicator made similar to the individual applicator 14 described above. The device 200 then forms a single circumferential row of six single applied odors. The upper and lower annular conductive ground plates 224, 226 of the hexagonal device 200 generally correspond to the upper and lower plates 74 and 76 of the applied odor device 12. An outer conductive plate 228 electrically connected to the outer periphery of plates 224 and 226 corresponds to the outer plate 9 described above. The EMR energy receiving portion of piece 202 is similar to the coaxial line coupled to the EMR energy receiving portion 1001 of piece 16 described above.
A coaxial parallel plate transmission line coupling means 230 connects to the coaxial line 204, but does not require an "H" type power division distribution section. If each piece 202 has a 50 ohm EMR applied odor, the combined impedance of the hexagonal applied odor device is 50/6.
That is, 8.33 ohms, which is the loading impedance Zm of the receiving sample that should be allowed (or included) for the EMR emitter 214. Assuming, as an illustrative example, that an 8 $ ohm device 200 is suitable for irradiating a 20 C diameter sample, the optimal irradiation frequency wavelength (from equation 2) is approximately 13 to 4
Understand what should be between 0 skin. Table 1 shows the corresponding EM old irradiation frequencies from about 10 to 2 HZ. 20 mark MHZ in the assumed H type material
For a frequency limit equal to , the dielectric constant erh of the material is 56.5 from Table 2. The preferred hole height h for the discharge hole 214 at a diameter of about 25 mm is calculated from the equation (desired) for a sample loading impedance Zm of 8 paper ohms as follows: h = Drop perforation (11) That is, approximately 13.0 skin. For uniform EMR heating of a substantially cylindrical body part, if an axially long heating type is not required, a row of hexagonal type applicable odor devices 20 is used.
0 is applied directly. The advantage of the hexagonal-shaped device 200 over the four-piece one-needle applied odor device 12 described above is that it is greatly simplified and is less expensive to manufacture. The operation of the device 200 is similar to that described for the applied odor device 12 in terms of displacement operations of the pieces 202 and/or individual displacement operations of the pieces. A fluid dielectric fill with a cooling flow system is also provided in device 200 in a manner similar to device 12, but is not shown. (Modifications of FIGS. 10 and 11) FIGS. 10 and 11 show a second variation of the EMR hyperthermia device system 250 according to the present invention, in which a coaxial It has a heat applicator device 252. Line 256 is preferably a conventional 50 ohm coaxial cable. The coaxial applied odor device 252 is the coaxial inner and outer conductive shell 2
58 and 260, both shells having a circular cross section. There is no device 2 anywhere in the space between the inner and outer shells 258 and 260.
52 is maintained to set a uniform characteristic impedance of, for example, 50 ohms. An appropriate shell spacing for the characteristic impedance Zo of the coaxial transmission line is determined by the following equation. Otsu = Rokushowan (12) Here, e is the dielectric coefficient of the material between the inner and outer shells 258 and 260, d (outer) d (inner)
are the cross-sectional diameters of the shells, respectively. For air-filled coaxial transmission lines, such as device 252, e is equal to 1. The outer shell 258 has a conical radially divergent EMR input section 266, with a small diameter input section connected to the line 25.
electrically connected to the outer conductor 268 of 6 (FIG. 11).
. At one end of the approximately cylindrical shell there is a middle section 27 and a conical section 266.
electrically connected to the flared end of the radial introversion,
That is, the convergent annular end 272 is connected to the other end of the intermediate section 270. The inlet and end sections 274 and 276 of the intermediate section 270 may be diverging and converging to provide smooth EMR transfer between the conical section 266 and the intermediate section 270 and between the intermediate section 270 and the end 272, respectively. inner shell 26
0 likewise has a conical and radially diverging inlet portion 282;
Its small diameter end is electrically connected to the inner conductor 284 of the transmission line 256. One end of a small cylindrical portion 286 is connected to the widening end of the conical portion 282 . A radially inward or converging annular end portion 288 is connected to the end of the intermediate section 286 . The inner peripheral edges 290 and 292 of the two terminal portions 272 and 288 spaced apart in the rutting direction have a diameter D.
An axial sample receiving application odor closure 294 is formed. An annular EMR hole 296 of diameter D and axial height h is formed between the end portions for the outer shell distal end 272 extending beyond the inner shell distal end 288 in the hoe direction. Hole 296 and Sekiguchi 2
94 is formed by a tubular non-conductive member 298 located between the inner edges 290 and 292 of the distal end. Because the applied odor device 252 is coaxial, the sample receiving opening 294 does not extend throughout the device. Instead, a generally conical, non-radial axial chamber 300 is provided in the inner shell 28.
2 in front of the discharge hole 296. For example, the 11th
As shown, when the coaxial device 252 is sized to illuminate the torso region of the human body 304, the leg portions 360 of the body enter the chamber 300 but are not illuminated. Since the device 252 comprises a thermally applied odor, the load impedance of the sample received at the device entrance 294 is preferably equal to the characteristic impedance of the device. Assuming an applied odor characteristic impedance of 50 ohms as an illustrative example, a sample load impedance Z of 50 ohms is used to match the 50 ohm transmission line 256 and the energy source 254.
m is preferred. Further assuming the overall human body size for device 252, an ejection hole diameter D of approximately 55 mm is selected to accommodate a 5 rené human torso section with a typical diameter d. The corresponding preferred radiant energy frequency limit is determined to be 10+ MHZ in the manner described above for device 12 (see Table 1). By substituting equation (11), the following equation is obtained for the height h of the discharge hole 296. h = Gakubo X no eM (
13) Assuming an H-type sample, the value of emr in one dish MHZ is 71.7 from Table 2, which is about the height of the applicator of section 194, which is just above the height of a normal person. Good impedance matching between the coaxial application odor device 252 and the large-diameter tissue sample for any type of sample requires that the device be long in the vertical direction; This is disadvantageous for this type of applicator shape, since the required outer diameter of the device approximates the vertical height h of the hole. Further, since the discharge hole 296 has a considerable height in the direction of the steel, it is expected that even if the radiant energy is uniform in the axial direction, there will be some non-uniformity in the EMR direction of the received sample. This is due to variations in constituents in axially different sample areas, such as the thoracic, pelvic area, or due to the sample "filling factor" of different cross-sections. However, at least some fill factor variation is typically compensated for with a fluid dielectric, such as a distilled water-filled annulus 310, between the device member 298 and the specimen 304, such as a human body, to eliminate air gaps. Coaxial applicable odor device 2
The advantage of 52 is the uniform E in the direction of the circle around the circle, which is important when rapid heating of the entire human body is required.
The MR energy distribution is generally along and around the holes 296. Uniform distribution of EMR energy for hyperthermia throughout the human body, for example, is important in treatment of Ikebana or to rapidly raise a patient's body temperature from a hyperthermia condition in combination with cold exposure. Another advantage of the applied odor device 252 is that it is relatively simple in construction compared to, for example, the illustrated applied odor device 12. The Wakachi applicator device 12,200,252 and the EMR hyperthermia device system 10,198 combined therewith.
, 250 selects the irradiation frequency depending on the size and type of the sample, and establishes good impedance matching between the sample and the applied odor through the appropriate shape of the ejection hole, thereby producing a substantially uniform and concentrated biological tissue sample. This is an exemplary illustration of carrying out the above-described method of producing EMR heating at a time. Good impedance matching under specific design conditions is useful and comparable under such design conditions, as it is often desired to accommodate variations in actual sample size and shape that are regularly encountered in use. It is also emphasized that the vehicle can be driven in a wide range of areas. (Effects of the Invention) As already mentioned in the background of the present invention, in the hyperthermia device system of the present invention, when biological tissue inserted into the closed opening of the heating application device is irradiated and heated with electromagnetic radiation from around it, The deep part of the tissue can be directly heated to a relatively high temperature of 41.5 to 4300 °C without heating the tissue surface to extremely high temperatures. Thereby, it is possible to heat and destroy only the target malignant tumor located deep without damaging surface tissue or healthy tissue. In addition, by interposing a fluid dielectric such as an annular mass filled with distilled water around the tissue and the aperture, the sample surface is cooled while improving the efficiency of energy use and reducing irradiation, which is difficult to achieve in the conventional manner. It can be done with energy. In order to explain the method in which the present invention is advantageously used, the hyperthermia device system for annular electromagnetic wave radiation according to the present invention and the various envisaged deployments of the device have been described, but the present invention is not limited to these. It's not something you can do. Therefore, any or all modifications, modifications, or equivalent arrangements that occur to those skilled in the art should be considered as falling within the scope of the invention as defined by the claims.

[Brief explanation of the drawing]

FIG. 1 is a partially cutaway, partially schematic perspective view of an EMR system having an annular thermally applied odor device for electromagnetic radiation (EMR) heating of a generally cylindrical biological tissue sample; FIG. Figure 2a illustrates the effect of EMR irradiation of a cylindrical tissue sample from multiple distinct directions; Figure 2a illustrates the effect of EMR irradiation of an ideal square cross-section sample from both sides; Figure 2b illustrates the effect of EMR irradiation of a sample with a square cross section Fig. 2c shows the effect of EMR irradiation on a sample with a circular cross section using the same annular application tool as in Fig. 1, and Fig. 3 shows the effect of EMR irradiation on a sample with a circular cross section from four directions. Schematic diagrams illustrating the effect of the height-to-medium ratio of EMR emitting holes, Figure 3a illustrating the effect of a hole with a height-to-medium ratio greater than 1, and Figure 3b illustrating the effect of a hole having a height-to-medium ratio less than 1. Figure 4 explains the effect of holes with a certain ratio.
A cross-sectional view taken along line 4-4 in the figure shows the internal shape of the heat applicator device shown in FIG. 1, and FIG. Fig. 6 is a partially cutaway perspective view of the receiving part, and Fig. 6 is a sectional view taken along line 6-6 in Fig. 5, showing the internal shape of the applied odor device in Fig. 1 and the features of each applied odor including the cap. is shown in elevation, FIG. 7 is a sectional view taken along line 7-7 of FIG. 6, showing other features of the individual applied odors, and FIG. 8 is a schematic diagram of the EMR system of FIG. 1. FIG. 9 is a partially cutaway partially schematic perspective view similar to FIG. 1, showing a hexagonal EMR energy application odor device and a matching EMR energy heating device. system, the 10th
The figure is a perspective view, partially cut away and partially schematic, similar to Figures 1 and 2, showing a second modification of the coaxial EMR applied odor device and the EM snake heating device system combined therewith, and Figure 11 is the same as Figure 10. 11-11
The internal shape of the coaxial application odor path is shown in a cross-sectional view along the line. 10,198,250: Equipment system, 12,200,252
: Applicable tool Ryodan, 16,202: Applicable tool part, 18,21
6,294: Central closed, 20: Sample, 22,214,2
96: Release hole, 32, 208, 254: Energy source, 3
4,210,256: Transmission line, 38,204: Secondary transmission line, 100: Energy receiving section, 258: Outer shell, 260:
Inner shell, 266: Outer shell conical portion, 270: Outer shell intermediate portion, 27
2: Outer shell end, 282: Inner shell conical part, 286: Inner shell cylindrical part. Traditional drawings, 2 Q drawings, inferior 2 b drawings, 2 c drawings, frequent drawings, 34 Kenzo b drawings, 5 vol. Number of illustrations/0 number of pictures number of 6 number of pictures

Claims (1)

[Claims] 1. A method for producing electromagnetic radiation energy heating in a cylindrical biological tissue sample having a predetermined characteristic cross-sectional dimension and known loss material electrical properties, including: (a) an energy source of electromagnetic radiation at a set radiant energy frequency f; an annular heat applicator device having a characteristic impedance of , the central aperture defining a peripheral aperture for radiant energy emission around the aperture along the aperture, the radiant energy emission aperture forming a peripheral aperture of the applicator device. an axial height h and a circumferential length w selected to produce impedance matching at the frequency f between a particular impedance and the load impedance of the sample placed in the discharge hole;
A hyperthermia device system for electromagnetic radiant energy, further comprising: (c) electromagnetic radiant energy transmission means for interconnecting the energy source with a radiant energy input section of an applicator device. 2. The frequency f of the energy radiation is preselected to produce a corresponding wavelength for the sample received in the aperture of the thermal applicator device to be a preselected function of the specific cross-sectional dimensions of the sample. A hyperthermia device system for electromagnetic radiation energy according to claim 1. 3. The frequency f of the energy radiation is preselected to produce a corresponding wavelength for the receiving sample between 2/3 and twice the characteristic cross-sectional dimension of the sample. The electromagnetic radiation energy hyperthermia device system described. 4. causing heating of electromagnetic radiation energy to a cylindrical biological sample having predetermined characteristic cross-sectional dimensions and known lossy material electrical properties, (a) transmitting a corresponding wavelength to said sample; (b) an energy source of electromagnetic radiation having a frequency of radiant energy, f, preselected to produce a frequency of between two-thirds and twice the characteristic cross-sectional dimension of the specimen;
an annular thermal applicator device having a particular characteristic impedance, comprising a radiant energy input and a central axial opening configured to receive said sample for irradiation;
c) A hyperthermia device system for electromagnetic radiant energy, characterized in that it comprises means for transmitting electromagnetic radiant energy interconnecting said energy source with a radiant energy input section of an applicator device. 5. The axially formed central aperture has a peripheral hole formed around the aperture and along the aperture for emitting radiant energy;
The peripheral hole of the discharge has an axial height selected to produce an impedance match at the selected frequency f between the characteristic impedance of the thermal applicator device and the load impedance of the receiving sample as seen through the peripheral hole of the discharge. 5. A hyperthermia device system for electromagnetic radiation energy according to claim 4, which has a circumferential length h and a peripheral length w. 6. The thermal applicator device comprises a flexible annular fluid-containing bladder disposed around the central opening to bridge the gap between the applicator device and the biological tissue sample received into the device. A hyperthermia device system for electromagnetic radiation energy according to claim 1 or 4. 7. The heat applicator device comprises a plurality of applicator pieces electrically arranged in parallel, each having the same characteristic impedance, and the characteristic impedance of the applicator device is equal to the electrical characteristic impedance of the applicator pieces. A hyperthermia device system for electromagnetic radiation energy according to claim 1 or claim 5, which is a sum of parallel elements. 8 said heat applicator device is comprised of a series and parallel array of individual electromagnetic radiant energy applicators each having the same individual characteristic impedance, the characteristic impedance of said applicator device being a series of characteristic impedances of said individual applicators; A hyperthermia device system for electromagnetic radiant energy according to claim 1 or 5, which is a sum in parallel with . 9. The thermal applicator device comprises a single applicator having a closed electromagnetic radiant energy input end and a sample receiving open end;
The applicator has inner and outer conductive shells disposed coaxially and spaced apart, each shell having a radially diverging portion at an input end and a radially converging portion at the other end; The ends are axially spaced apart such that the convergent end of the outer shell is further away from the input end than the convergent end of the inner shell, and the radiant energy release hole is located between the convergent ends. A hyperthermia device system for electromagnetic radiation energy according to claim 1 or 5, which is formed. 10 producing electromagnetic heating in a cylindrical biological sample having predetermined specific cross-sectional dimensions and known lossy material electrical properties, (a) having a predetermined radiant energy frequency f; (b) a source of electromagnetic radiation energy;
An annular heating device having a specific characteristic impedance, comprising a plurality of applicator pieces each having a discharge hole for electromagnetic radiant energy and a receiving portion for electromagnetic radiant energy and having a predetermined specific impedance. an applicator apparatus, the plurality of applicator pieces being arranged in electrical parallel abutting one another to form a central opening of the applicator apparatus for receiving the sample for irradiation; the applicator piece's radiant energy emitting apertures to form a substantially continuous annular radiant energy emitting aperture; at an energy frequency f, the shape is configured to create an impedance match between a particular impedance of the applicator device and a load impedance of a biological tissue sample received in the central aperture and presented in the annular radiant energy emitting hole. and
A hyperthermia device system for electromagnetic radiant energy, further comprising (c) electromagnetic radiant energy transmission means for interconnecting the energy source with a radiant energy receiving portion of the applicator device. 11. A generally cylindrical body having a preselected characteristic cross-sectional dimension and known lossy material electrical properties, comprising a source of electromagnetic radiation energy and an electromagnetic energy transmission means connected to the energy source for transmitting electromagnetic energy from the energy source. An annular thermal applicator device in an electromagnetic radiant energy hyperthermia device system for producing electromagnetic radiant energy heating in a biological tissue sample, the device comprising: (a) an electromagnetic radiant energy input; (b) an electromagnetic radiation energy release hole formed around the periphery of the axial center opening; produces an impedance match between the characteristic impedance of the applicator device and the loaded impedance of the receiving sample as viewed from the discharge hole at a preselected electromagnetic radiant energy frequency to provide optimal uniformity of heating of the receiving sample with the electromagnetic radiant energy. It has the axial height and peripheral length, and also (
c) means for making an electrical connection between the input section for receiving electromagnetic radiation energy from an energy source and a transmission means; . 12. The structure of the applicator comprises a plurality of electromagnetic radiant energy applicator pieces arranged annularly to form the axially central opening, the applicator pieces being electrically parallel to each other. , each of the pieces has a radiant energy release hole, and the energy release hole of the applicator device is formed by the radiant energy release holes of the plurality of pieces. Heat application device. 13 The applicator device is constructed to have a preselected characteristic impedance, and the height to perimeter ratio of the energy emitting hole is such that at the preselected radiant energy frequency f, the load impedance of the sample viewed through the emitting hole is 12. An annular heat applicator device according to claim 11, wherein the annular heat applicator device is selected to be equal to the characteristic impedance of the applicator device. 14. A cylindrical organism having specific preselected cross-sectional dimensions and known lossy material electrical properties, comprising an energy source of electromagnetic radiation and an electromagnetic energy transmission means connected to the energy source for transmitting electromagnetic energy from the energy source. For use in a hyperthermia device system of electromagnetic radiation energy that causes heating of a biological tissue sample with electromagnetic radiation energy,
(a) having a plurality of similar applicator pieces each having a preselected characteristic impedance and defining a radiant energy receiving portion and a rectangular radiant energy emitting hole; (b) ) the plurality of applicator sections are electrically interconnected in parallel to each other to form an annular composite applicator structure with annular composite radiant energy emitting holes; A biological tissue sample to be irradiated by the annular radiant energy emitting hole formed with the radiant energy emitting hole is received, and the shape of the radiant energy emitting hole of the applicator piece and the number of applicator pieces are set as described above. (c) a selected radiant energy frequency f selected to match the characteristic load impedance of the sample and the composite characteristic impedance of the composite applicator as viewed from the composite discharge hole; A hyperthermia device system for electromagnetic radiant energy, comprising means for separately electrically connecting a radiant energy receiving portion of each applicator part and the transmission means so as to receive electromagnetic radiant energy from An annular heat applicator device. 15. Each applicator piece comprises separate applicators arranged in 2×2 rows, each separate applicator having a characteristic impedance that is the same as the characteristic impedance of the applicator piece; Claim 14, further comprising series and parallel electromagnetic radiant energy transmission means for transmitting electromagnetic radiant energy from the radiant energy receiving part of the piece to the radiant energy receiving part of each of the applicators. An annular heat applicator device. 16 an electromagnetic radiation energy source and an electromagnetic energy transmission means of two conductors connected to the energy source for the transmission of electromagnetic energy from the energy source to an electromagnetic source of preselected characteristic cross-sectional dimensions and known lossy material; an annular thermal applicator device in a system of electromagnetic radiant energy hyperthermia devices for producing electromagnetic radiant heating of a generally cylindrical biological tissue sample having a characteristic, the device comprising: (a) connected to a first conductor of said transmission means; (b) a radiant energy receiving end configured to be disposed within said outer shell coaxially with the outer shell and connected to a second conductor of said transmission means; a conductive inner shell formed to have a conical flare connecting to the radiant energy receiving end; and an elongated cylindrical intermediate portion connected to the flare end of the flare. a radially inwardly convergent portion connected to the cylindrical portion to form an end, the inner shell having a conical flared portion connecting to the radiant energy receiving end and a flared end of the inner shell flared portion; a cylindrical intermediate portion that connects, and a radially inwardly converging portion that connects to the cylindrical portion of the inner shell to form a distal end, the outer shell end extending axially from the inner shell end; an axial applicator opening for receiving the sample to be irradiated and an axial annular electromagnetic radiation energy emitting hole formed between the ends; A coaxial annular thermal applicator system of electromagnetic radiant energy hyperthermia devices spaced in a shape to provide uniform electrical impedance.