WO1982002339A1

WO1982002339A1 - Induction heating method and apparatus for use in causing necrosis of neoplasm

Info

Publication number: WO1982002339A1
Application number: PCT/US1982/000019
Authority: WO
Inventors: Robert W Rand; Harold D Snow; David G Elliot; Glenn M Haskins
Original assignee: Robert W Rand; Harold D Snow; David G Elliot; Glenn M Haskins
Priority date: 1981-01-09
Filing date: 1982-01-07
Publication date: 1982-07-22
Also published as: EP0056697A2; BR8205337A; EP0056697B1; MX151204A; EP0056697A3; EP0208338A2; EP0208338A3; AU7912481A; JPS57136463A; CA1203851A; US4392040A; ATE28128T1; AU557749B2; DE3276683D1; IL64735A0

Abstract

Induction heating can be utilized to cause necrosis of neoplasm as a result of hyperthermia by a process involving the injection of particles having hysteresis heating characteristics into tissue either within or in close proximity to the neoplasm and then subjecting these particles to an alternating magnetic field sufficient to cause hysteresis heating. The frequency of the field is preferably sufficiently low so as to minimize eddy current and dielectric heating. The particles used are preferably initially located within a biologically inert liquid carrier which will facilitate the insertion of the particles within the body and which will automatically become non-liquid within the body so as to hold the particles in place. The actual heating is preferably carried out by positioning either the entire patient or the affected portion of the patient's body through a series of axially aligned, parallel, liquid cooled coils (12). Only one of these coils (12) is connected to a power supply (30).

Description

TITLE: INDUCTION HEATING METHOD AND APPARATUS FOR USE IN CAUSING NECROSIS OF NEOPLASM

BACKGROUND OF THE INVENTION

The invention set forth in this specification pertains to a new and improved method and apparatus for causing necrosis of neoplasm by hyperthermia.

Aberrant cells within the body, such as are frequently. referred to as neoplasm, are the subject of a great deal of concern to society and civiliza¬ tion because of the very undesirable consequences of various growths such as are commonly referred to as tumors, cancers and the like. Tremenduous sums of money have been and will continue to be spent in connection with the problem of causing necrosis of neoplasm with a minimal detrimental effect to a person at a minimal cost. It is con- sidered that no one approach to this problem of causing necrosis of neoplasm will ever be completely satisfactory for use with all different types of neoplasms.

It has been recognized that certain types of neoplasms can be effectively necrosed as the re¬ sult of the use of hyperther ia. In the past, the heating used in this type of treatment has been achieved either through the use of the electromag- netic radiation associated with a radio freqμency or microwave field or through the use of an alter¬ nating magnetic field such as is associated with induction heating. It is considered that an under¬ standing of the present invention requires an understanding as to essential differences between

these two distinctly different types of heating.

A radio frequency or microwave field can only be utilized in causing heating at or adjacent to the surface of a body because of the tendency of the body to absorb radio frequency electromagnetic radiation. The depth to which such radiation will penetrate the body will vary depending upon the frequency of the radiation. Such body tissue heating as is caused by radio frequency radiation has two principal components: eddy current heating and dielectric heating. Both result from the electromagnetic field employed contacting the tissue. Effective heating of this type can be achieved in the absence of any foreign material in tissue being heated.

As opposed to this, induction heating of body tissue as a result of the presence of a material having hysteresis characteristics may be referred to or at least considered as hysteresis heating. It is based upon the use of a magnetic field which is normally presumed to be unattenuated by tissue. Hence, induction heating can reach any desired depth or level beneath the surface of tissue. In order to achieve this manner of heating in tissue, it is necessary to locate a material exhibiting magnetic hysteresis at or about the location where heat is desired. Any such induction-hysteresis heating will be accompanied by some eddy current and dielectric heating.

The amount of eddy current and dielectric heating can be minimized by utilizing a co para- tively low frequency alternating magnetic field.

The amount of such heating varies directly with the square of the frequency of the field. As ^! opposed to this, the amount of hysteresis heating forming the operative "part" of induction heating for use with the present invention varies directly with the frequency. Thus, in general, the lower the frequency of the field the less the amount of undesired eddy current heating achieved relative to the amount of the desired hysteresis heating achieved. The frequency used, however, should not be so low as to preclude the achievement of a desired degree of hysteresis heating.

The limited amount that a radio frequency field can normally penetrate body tissue has been and remains an important factor limiting the use of this type of heating in the treatment of var¬ ious different neoplasms. Obviously, this radio frequency heating can not be utilized effectively in causing hyperthermia in aberrant growths which are sufficiently beneath the surface of tissue so as not to be reached by a radio frequency field. The use of such a field to cause hyperthermia at or adjacent to the surface of the skin or at or adjacent to the interior of an incision within the body is limited by another important factor - the problem of selectively concentrating the heat developed so that neoplasm is heated to a point sufficient to cause necrosis without there being a related or corresponding heating of adjacent' nor¬ mal tissue.

This can be easily illustrated by referring to specific temperatures such as have previously been recognized to be important in causing necrosis as a result of hyperthermia. It is usually con-

W. sidered that necrosis will not be caused by the exposure of most body tissue to a temperature of about 40°C for a reasonably prolonged period. It is also generally considered that if commonly found body tissue - including neoplasms - are held at a temperature of at least 42°C for a reasonably prolonged period that such cells or tissue will be destroyed if the period is adequately long for the purpose.

It is also generally conceded that commonly encountered cells and tissue - including neoplasms - will be necrosed by exposure to -a temperature of from about 60°C or, of course, a higher temperature for a very minimal or limited, practically instan¬ taneous time period. It should be noted that body tissue should not normally be subjected to a tem¬ perature reasonably approaching 100°C for even a very short, instantaneous time period because of the possibility of the vaporization of water in the body and the attendant possibility of damage being caused by the sudden expansion of vaporiza¬ tion of water. As a practical matter, it is con¬ sidered that internally the body should never be heated past 90°C to avoid any possibility of such vaporization.

Apparently, the relationship between the time that neoplasm or other body growth need be exposed to a specific temperature to cause necrosis and the time necessary for such exposure to cause necrosis are not related in exactly usual time- temperature manner applicable to the usual temper¬ ature reactions. Further, certain parts of the body or neoplasms are more susceptible to necrosis at an elevated temperature than other parts of the body and/or other certain neoplasms. Because of these factors, it is impossible to give exact relationships between the time and the temperature necessary to accomplish necrosis and, in partic¬ ular, necrosis of neoplasms. Another factor which will be important in considering the amount of hyperthermia to cause necrosis in neoplasm will involve the tendency of the body and/or a partic- ular portion of the body to serve to at least a degree as a heat insulator so as to tend to con¬ centrate heat developed as, for example, at a specific source.

With radio frequency or microwave hyperthermia the difficulty in confining the field necessary to cause necrosis of a specific area or region will normally cause necrosis of healthy tissue in an adjacent area or region. While to a degree this can be combated through the use of specialized electrodes, it is not considered that it is possi¬ ble to adequately control radio frequency or micro¬ wave heating in many applications so as to avoid detrimental damage to normal cells or tissue. While it may be possible to improve the concentra¬ tion of the heating effects achieved with radio frequency or microwave heating through the implan¬ tation of a metallic conductor or another similar material in a specific area where concentrated heating is desired, it is considered that such a use of a conductor is not always advantageous because such a conductor will not improve the depth of penetration of tissue by a radio frequency field.

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- The use of induction heating .in causing necro¬ sis of neoplasm is considered desirable in overcom¬ ing several problems involved in utilizing a radio frequency field to cause hyperthermia leading to necrosis of neoplasm as noted in the preceding. When induction heating is used for this purpose, it is necessary to utilize an invasive technique to locate a material having a magnetic permeability greater than unity and capable of exibiting hys- teresis losses - for example, ferromagnetic parti¬ cles such as a conventional ferrite or conventional iron or steel powders - in or immediately adjacent to the neoplastic growth. The use of such a mag¬ netic material in an alternating magnetic field results in hysteresis heating within the magnetic material itself. This localized or focused hyste¬ resis heating overcomes the problem of containing or limiting the heated area obtained with a radio frequency field. Because of the penetration of a low frequency magnetic field with respect to body tissue, it is possible to use a magnetic material well beneath the surface of the body.

From this it is believed that it will be apparent that the utilization of induction hyste¬ resis heating in connection with the hyperthermia of neoplasm has a great deal of advantageous poten¬ tial. Unfortunately, it is not considered that the prior efforts for accomplishing necrosis' of neoplastic growth by induction heating have been sufficiently effective and desirable for this purpose. It is considered that several factors may be important in connection with this. One of these concerns the lack of availabil¬ ity of induction heating equipment which is speci¬ fically adopted for use in treating a body such as a human or animal body in which magnetic material has been implanted so as to produce localized heating. In connection with this, it is noted that prior induction heating coils have not nor¬ mally been designed with the intent that they be utilized to provide a very intense AC magnetic field over a comparatively large volume so as to cause heating in a specific, very limited area or region coming within the "scope" of the complete magnetic field produced by the coil in which mater¬ ial capable of hysteresis heating is located. It is considered that this factor has led to a degree of inefficiency of prior induction heating coils when such coils have been utilized in conjunction with body tissue so as to cause induction heating of materials or particles embedded within such tissue.

It is considered, however, that the prior procedures for accomplishing necrosis of neoplastic growths by hysteresis heating have also been com- paratively unsatisfactory for other reasons relat¬ ing to the technique or procedure followed in implanting the magnetic material or particles used. In general, such materials have not been utilized in such a manner as to be effectively immobilized either within or immediately adjacent to a neoplasm so as to be capable of providing a localized heating without danger of the magnetic material used moving from its initial location within the body. Any such movement would be highly disadvantageous because of the possibility of undesired interference with the normal operation of the body.

BRIEF SUMMARY OF THE INVENTION

Because of these various related considerations, it is considered that there is a need for a new and improved process of causing necrosis of neo¬ plasm as a result of hyperthermia of the neoplasm which may be easily and conveniently carried out at a comparatively nominal cost and which is effec¬ tive for its intended purpose. The invention is intended to provide such a process. A further "process" objective of this invention is to pro- vide a procedure as indicated which can be uti¬ lized in connection with a wide variety of diff¬ erent neoplasms located in various different regions of the body without significantly endangering the life or health of the body in which such neoplasms are located.

In accordance with this invention, those aspects of the invention which are directed towards the process as noted are achieved by providing a process of causing necrosis of neoplasm as a re¬ sult of hyperthermia of the neoplasm in which magnetic particles are injected into tissue in proximity with the neoplasm and are subjected to an alternating magnetic field so as to cause hys- teresis heating ot said particles in which the improvement comprises: said particles are mixed with a carrier fluid as they are injected into said tissue, said carrier fluid being biologically inert and being capable of becoming non-fluid within said tissue, and causing said carrier fluid

SUBSTITUTE SHEET -~ξ^_E* ^' to become^' non-fluid within said tissue.

As a result of the considerations indicated in the preceding, it is also considered that there is a need for a new and improved apparatus for use in causing induction hysteresis heating of specific regions or areas within a much larger region or area such as within a living body. An objective of the present invention is to fulfill this need. The invention is also intended to provide an appa¬ ratus for the purpose of which may be easily and conveniently constructed at a comparatively nominal cost, which is effective for its intended utiliza¬ tion, and which is desirable from an energy utiliza- tion standpoint, particularly when this is related to the results accomplished or achieved with the apparatus.

In accordance with this invention, those aspects of the invention which are directed to¬ wards an apparatus are achieved by providing an induction heating apparatus having a series of separate induction heating coils and means ^'for passing an alternating current through .said coils at a frequency sufficient to cause induction heat¬ ing in -which the improvement comprises: a capaci¬ tor means associated with each of said coils, each capacitor means being connected across the termi¬ nals of the coil with which it is associated so as to form a physically separate circuit, said coils being located in axial alignment with one another and being located immediately adjacent to one another, only one of said coils being connected to said means for passing AC current. BRIEF DESCRIPTION OF THE DRAWINGS

Because of the nature of this invention, it is considered that it is best more fully explained with reference to the accompanying drawing in which:

Fig. 1 is a diagramatic view illustrating the essential features or concepts of a presently

10 preferred embodiment or form of an apparatus in accordance with this invention; and

Fig. 2 is an isometric view showing the con¬ figuration and utilization of the coils explained.

5 it is to be understood that the illustration of a particular apparatus shown is not to be taken as limiting this invention in any respect. This invention involves the concepts or principals set forth and defined in the appended claims. Those

20 skilled in the field of utilizing induction heat¬ ing in treatment of neoplasm will realize that these concepts or principals may be utilized in various different ways without departing from the scope of the subject matter set forth in the

25 claims.

DETAILED DESCRIPTION

As indicated in the preceding summary, an

30 important aspect of the invention involves the formation of a mixture of magnetic particles and a carrier fluid- This mixture should have fluid or fluid like properties enabling the complete mix¬ ture to be easily and conveniently injected into a -" body through the use of a conventional hypodermic

needle or any other reasonably related procedure such as, transarterial catherization. This inten¬ ded manner of location of a mixture within the body places several important restrictions upon the ingredients of the mixture.

Within the broad purview of the present inven¬ tion, it is possible to utilize any magnetic mater¬ ial having a magnetic permeability greater-rthan unity which exhibits hysteresis heating. As a practical matter, it is desired to utilize only magnetic materials which present a minimum of a toxicity problem when used within the human body and in addition which possess or exhibit as large a hysteresis loop when subjected to an alternating magnetic field as reasonably obtainable. It is the area within such a loop that is of prime impor¬ tance in the present invention since such area corresponds with the efficiency of hysteresis caused heating. Because of this consideration, the exact shape of the hysteresis loop of the material used is not important in the sense that it is relatively unimportant as to whether or not a square wave type of hysteresis type loop is achieved.

It is considered preferable to utilize with the present invention only ferromagnetic particles such as various conventional ferrites and various commercially obtainable iron and steel particles known to have or exhibit comparatively large mag¬ netic losses. It is considered quite fortunate that such materials are relatively inert as far as most metabolic processes are concerned and can be utilized within most parts of the body without

O PI significaht concern. Other biologically inert particles capable of exhibiting hysteresis heating can, of course, be employed.

An interesting aspect of the invention lies in the fact that magnetic particles may be chosen having a Curie temperature or Curie point such as to control the maximum temperature which can be achieved during induction heating. Thus, for example, it is possible to choose a particular paramagnetic or ferromagnetic composition having a Curie point anywhere within the range of from about 42°C. to about 90°C. specified in the preced¬ ing so that hyperthermia of a neoplasm may be accomplished without fear of heating tissue beyond a desired temperature. In connection with this matter, it is noted that normally the magnetic characteristics of a material will change over a comparatively small range of temperatures and that therefore the Curie point in many respects corres¬ ponds to a limited range of temperatures.

The particles utilized should be sufficiently small so as to be capable of either going into colloidal suspension within a carrier fluid as subsequently indicated or so as to be capable of forming a slurry with the carrier fluid. Any such a slurry should have a sufficiently low viscosity so as to be capable of being compared with a sus¬ pension of aluminum hydroxide antacid in water capable of being easily handled and being poured from a bottle to a spoon and the like. As a prac¬ tical matter, it is considered that this method of utilization indicates that the particles used should have an average diameter of no greater than

SUBSTITUTE SHEET about 1 millimeter. It will be realized, however, that on occasion particles which are of slightly larger dimension can be effectively poured and handled.

It is considered that the particles used should not be sufficiently fine so that their fineness will tend to detract from the ability of a magnetic field to cause these particles to heat. In general, if the particles are undesirably small this will tend to make the hysteresis loop exhibited by the material smaller than the loop which would be obtained with somewhat larger sized particles. Because of this, the particles should be of such dimension that there is no diminution of the hysteresis loop exhibited as a result of the size of the particles used. With at least some materials, comparatively long, thin particles appear to have better hysteresis heating charac- teristics than particles of a reasonably spherical shape.

As a practical matter, it is considered that the lower level of desirable size of the particles used and that the shape of the particles used should be determined on an empirical basis as a result of testing particles of various sizes. Also as a practical matter, it is considered that, in general, the particles used should be of no less dimension than the dimension of the magnetic domains of the material within these particles. In general, it is considered undesirable to uti¬ lize particles any finer or smaller than those which are conventionally utilized within ferro- fluids in which ferromagnetic particles are held

SUBSTITUTE SHEET , _OM in colloidal suspension.

Within the broad aspects of the present inven¬ tion, virtually any type of a biologically inert liquid capable of being easily tolerated by the body can be utilized as a carrier fluid so as to facilitate the insertion of magnetic particles as indicated in the preceding. Such a carrier fluid may be of either two broad generalized types. It may be of a type which will remain fluid after being located in place within the body and/or tissue. Such a fluid may be of a type which will form a solid or at least a semi or non-newtonian solid within such tissue.

A carrier fluid of the first type is prefer¬ ably utilized when particles are to be injected in a location within a neoplasm or even within normal tissue adjacent to neoplasm where there is no reasonable possibility of the particles entering the bloodstream, since there is always a possi¬ bility that any such particles in the bloodstream would cause damage. As opposed to this, carriers of the second type which become a solid or se i- solid may be utilized in any location relative to neoplasm - including in blood vessels since the second type of carrier fluid will preclude the movement of particles within the bloodstream by becoming solidified.

Within the broad concepts of the present invention, it is even possible to utilize water as a carrier vehicle in those cases where the partic¬ les used will, in effect, be isolated from the remainder of the body by normal tissue surrounding

SUBSTITUTE SHEET the specific location where such particles are used. Other permanently liquid or at least semi- liquid fluids capable of being utilized are such liquids as Ringer's solution, albumen, essentially fluid-like starch gels and the like. It is not considered necessary to enumerate in this specifi¬ cation many other different carrier fluids which are capable of being utilized within the broad concepts of the present invention inasmuch as var- ious fluids which are compatible with body function¬ ing are well known. When water or any other liquid or semi-liquid carrier is used it is considered that it will be obvious that minor amounts of biologically inert surfactants and the like may be employed so as to facilitate the suspension of the particles used and so as to aid in controlling viscosity of the mixture.

Whenever a carrier is used which will not become solid or semi-solid in time in connection with magnetic particles as noted, it is considered preferable to completely surround such particles with a biologically inert, adherent, conventional protective coating. While in a sense the use of such coated particles is optional, it is never¬ theless considered highly preferable to minimize any chance of any sort of unintended interference with normal metabollic processes. Many different types of such coatings are, of course, known. It is considered that coatings such as various poly- olefin coatings are particularly suitable. The coatings used on the particles should, of course, be as thin as reasonably possible. A nominal amount of agglomeration of the particles caused by the inherent character of the coating material

o:.;?ι employed will not normally prove detrimental.

With the present invention it is preferred to utilize a carrier fluid which is of such a charac- 5 ter that it will change from a liquid or fluid to essentially a solid or semi-solid after is has been injected into a neoplasm or into a body ad¬ jacent to a neoplasm either as a result of a poly¬ merization or similar action initiated as a result 0 of one or more components present in the carrier fluid or as a result of the application of extern¬ al "energy". Such "energy" may be derived from normal body heat. The energy used may be derived directly from the magnetic field used in causing 5 hysteresis heating or may be the heat resulting from such heating of the particles within the carrier fluid.

The primary reason why the use of a carrier 0 fluid which changes so as to become non-fluid or substantially non-fluid in character is preferred with the present invention relates to the desira¬ bility of creating a physical structure within the

A. body which will physically hold the particles used 5 , so that such particles cannot move throughout the body in the blood and so that such particles can¬ not become lodged in various passages or cells where they might cause at least a degree of damage. The precise method or mode of forming a solid or a 0 non-newtonian semi-solid from the mixture of'the particles and carrier fluid employed is in many respects immaterial to the present invention.

Further, the solidity of the non-fluid body 5 or composition created is also a matter of choice. From the point of view of patient comfort it is considered that the ultimate non-fluid body created from the carrier fluid should either be of a some¬ what flexible, somewhat elastomeric character corresponding to a reasonable degree to the charac¬ ter of human tissue or should be of a non-newtonian character capable of being deformed while still remaining as a coherent body or unit.

As a result of these considerations, it is considered preferable to utilize as the carrier fluid an elastomer which will develop elastomeric, non-fluid properties within the body after being mixed with an amount of particles which is effec¬ tive so that the complete mixture will in turn be effective in the production of heat by hysteresis heating. Any such fluid composition may contain a wide variety of different biologically inert secon¬ dary ingredients such as fumed silica, various surfactants, and the like serving various secondary functions such as, for example, a degree of control of the ultimate elasticity of the polymer body produced. The liquid or fluid composition employed may be a pre-polymer or partially polymerized solution containing one or more catalysts. Such a liquid carrier composition may include inert liquid such as water which will not enter into an ultimate or final solid or non-newtonian semi-solid composi¬ tion but which will serve as a dilutent viscosity control agent until such time that the composition becomes non-fluid in character.

It is presently preferred with the present invention to utilize as the carrier fluid a sili- cone elastomer composition which is capable of

C P ^' being injected into the body as a liquid and which will set up when in place within the body as a polymer serving to physically hold the various magnetic particles used in virtually any intended location within the body. The use of this mater¬ ial is considered to be especially desirable be¬ cause of the fact that mixtures of this type of composition and of particles as noted are normally adequately coherent so that they will not separate or break up into smaller "units". Further, sili- cone elastomers as noted herein are normally ac¬ ceptable for use within the human body.

It is considered quite important that a carrier which is intended to become solid or semi-solid within the body is reasonably able to "wet" various magnetic particles as noted so that such particles are completely coated by the carrier fluid in such a manner that they are effectively isolated from normal body fluids in the final non-fluid body created. This minimizes any chance of the material within the particles used interfering with normal metabolic processes. It also makes it possible to utilize with the invention particles of magnetic material which are somewhat biologically active. The use of any such biologically active material is not, however, preferred because of the possibil¬ ity of some sort of unintended interference with normal metabolic processes.

The relative proportions of particles and the carrier fluid which should be utilized together in a mixture as described will depend upon the physi¬ cal properties of the ingredients used. In general, the mixture should contain the minimum amount of

OMFI the fluid^' carrier which is effective to suspend and hold the particles so that they will not sepa¬ rate out of the mixture during the time period when the mixture is being injected into a body as indicated in the preceding discussion. Further, the proportions should be such that adequate carrier fluid is present so that the inherent physical cohesive "character" of the fluid will tend to hold the mixture together as a unit after the mixture is injected into the body.

This is considered to be particularly impor¬ tant as, for example, when a mixture as used is inserted into a blood vessel. The mixture should not fragmentize within such a blood vessel but should be of such a character as to hold together as a result of cohesion until such time as it is rendered non-fluid or solidified as indicated in the preceding discussion. In certain applications of the present invention it is highly desirable for the mixture of particles and the fluid carrier to be sufficiently coherent so that such a mixture may to a degree be guided to a specific location or held in such a specific location within or adjacent to neoplasm through the use of an external magnetic field until such time as the mixture is rendered sufficiently non-fluid that it is held in place as a result of physical engagement with adjacent walls or tissue.

In some cases, to increase the amount of hysteresis heating attainable at a given magnetic field intensity, it may be desirable to apply a DC magnetic field to the magnetic mixture while it is solidifying. This will align all of the magnetic

SUBSTITUTE SHEET particles in one direction. Subsequent applica¬ tions of the AC magnetic field along the same axis will cause more magnetic heating than if the par¬ ticles were randomly oriented.

In addition, the mixture may contain tempera¬ ture-indicating ingredients that can be monitored by X-ray, ultrasonic, or other means while the induction heating is in progress.

After a mixture as indicated in the preceding has been located with respect to a neoplasm and, except in those cases where the carrier fluid is "set up" as a^' esult of hysteresis heating as subsequently discussed, the tissue containing the neoplastic growth is subject to an alternating magnetic field as discussed in the preceding which will cause adequate hypertheremia to cause necrosis of the neoplasm adjacent to the magnetic particles present.

Although such heating may be caused with any sort of a coil capable of being utilized for induc¬ tion heating purposes, it is considered preferable within the concepts of the present invention to utilize a specialized induction heating apparatus 10 as illustrated in the accompanying drawing. For convenience this apparatus 10 is referred to as including circuit components as hereinafter described.

This particular apparatus 10 includes a series of coaxial, identically constructed and dimen¬ sioned flat, "pancake" coils 12. Each of these coils 12 consists of a series of turns (not sepa-

SUBSTITUTE SHEET rately numbered) of an electrically non-conductive tube 14 such as an extruded polyvinyl polymer tube located in two flat, parallel planes and a conductor 16 going through the interior of each tube 14. These conductors 16 are sufficiently small so as to permit a cooling liquid such as, for example, a dielectric oil or distilled water to be circulated through the tubes 14 around the conductors 16.

Appropriate conventional fittings 18 are provided at the ends (not separately numbered) of the tubes 14 for the purpose of joining the ends (not separately numbered) of the tubes 14 to mani¬ folds or distributing pipes 20 used in connection with a storage reservoir 22 and a pump 24. These fittings 18 are formed in a conventional or known manner so that the conductors 16 extend through them so that these conductors 16 may be connected as hereinafter indicated.

With the present invention each conductor 16 constitutes the electrically "active" part of a coil 12 and is connected into a tank circuit 26 across two separate capacitors 28 of equal capaci- , tance value located in series with one another.

All of the coils 12 and the associated capacitors 28 together constitute a tank circuit having a specific resonant frequency.

A known adjustable power supply 30 capable of being adjusted so as to operate at various fre¬ quencies is used as a means for supplying a current at the noted resonant frequency to a transformer 32 which in turn is connected to only one of the tank circuits 26. In the particular embodiment

IRS, illustrated the transformer 32 is connected across only one of the two capacitors 28 in such a circuit 26. However, it desired, this transformer 32 can be connected across both the capacitors 28 in this particular circuit 26.

All of the circuits 26 are grounded by conven¬ tional grounds 34. In order to promote safety it is preferred to ground each circuit 26 between the capacitors 28 in such circuit as shown. With the present invention the particular coil 12 which is driven by the power supply 30 and the transformer 32 may be any one of the individual coils 12 used in the complete apparatus 10.

The coils 12 are assembled closely together as shown in a "stack" of aligned, identical pancake- type coils 12. They preferably are secured together as a unit (not numbered) by the use of a conventional, appropriate adhesive (not shown) . Because they are used in this manner, in effect, the coils 12 constitute a series of closely coupled transformer coils. As a consequence of this, the use of the power supply 30 with a single coil 12 has the effect of "driving" the remainder of the coils 12 and, of course, the associated tank circuits 26 including these coils 12.

In order to achieve the degree of hysteresis heating desired with the present invention in, connection with a comparatively small area or region of a mixture of a carrier and particles as indicated in the preceding discussion it is neces¬ sary to drive the particular circuit 26 connected to the power supply 30 utilizing a comparatively

O significant amount of power. The exact amount of such power will, of course, vary in accordance with many factors. At this time, it is believed that the exact amount of power used in various different reasonably related treatments of neoplas¬ tic tissue should be judged on an emperical basis as an outgrowth of experience, taking into consider¬ ation factors as are subsequently indicated.

The frequency of the AC current supplied to a coil 12 and its associated circuit 26 is normally determined on the basis of the factors indicated in the preceding discussion relative to the back¬ ground of the invention so as to minimize eddy- current type heating losses while concurrently maximizing the efficiency of the hysteresis heating obtained. At this time, it is believed that a frequency of from about 1000 to about 5000 Hz - and preferably of about 2000 Hz - initially repre- sents the most desirable "balance" between competi¬ tive factors which are involved in achieving the desired hyperthermia in accordance with the inven¬ tion and that the individual tank circuits 26 should be formed to a specific frequency as noted and that the power supply 30 should be operated at such frequency.

As power is supplied to a circuit 26 and its associated coil 12 a cooling liquid will, of course, be supplied to the individual coils 12 in an effort to prevent any damaging temperature rise in these coils or their manner of operation. However, in spite of this some heating will normally occur in the individual conductors 16 in the various coils 12 and in connection with the various associated

SUBSTITUTE SHEET capacitors 28. Because of such heating, the indi¬ vidual circuits 26 will change slightly as they are used and this in turn will affect the resonant frequency of the complete apparatus.

Because of this, as the complete apparatus 10 is operated the frequency of the power supply 30 used to drive directly one circuit 26 and its associated coil 12 and the remainder of the circuits 26 and coils 12 indirectly should be adjusted so as to always match the new resonant frequency of the complete collection of circuits 26. In order to further minimiz-e power losses it is considered highly preferable to utilize as the conductors 16 either wires composed of a twisted multitude of strands o£ individual wires or conventional Litz wires.

The utilization of such conductors may also be advantageous for another reason. During the use of the coil 12 at high power levels, as indicat¬ ed, a cooling fluid irrus-t be circulated through the tube 16, as previously indicated, so as to prevent damage to either the tubes 14 or melting of the conductor 16. It is considered that the surface configuration of either a twisted or a Litz wire conductor, as noted, is effective in promoting efficient heat transfer from the conductor to the cooling liquid employed.

During the utilization of the apparatus 10 power will be supplied from the power supply 30 to a connected tank circuit 26 at a frequency matching the resonant frequency of all of the circuits 26 as a "unit". As this specific circuit 26 is driven

' or powered- in this manner it will set up a flux field which will in turn couple to the adjacent coils 12 so as to power these adjacent coils in a transformer-like manner by mutual induction. This will have the effect of utilizing one specific coil 12 to drive all of the various coils 12 solely as the result of the mutual induction between the coils 12. This has several significant advantages. First, only comparatively low voltages are required at the terminals of the individual coils since they are electrically in parallel; a series-wound coil of the same total number of turns would require many kilovolts of excitation voltage, with accompa¬ nying high-voltage insulation requirements, corona discharge problems, and safety hazards. Second, the circuits 26 are electrically isolated so that they need not all have exactly the same voltage, a requirement that would exist if all of the circuits 26 were connected to a common voltage source.

It is not to be assumed from the above that the apparatus 10 requires the utilization of coils 12 which are symmetrical relative to an axis. In increasing the efficiency of the apparatus 10, it is considered desirable to construct all the coils 12 used so that they are of an identical oval shape such that their interiors reasonably conform to the non-rectilinear shape in a human body. When the interiors of the coils 12 are of such dimension an entire significantly sized segment of the body can be located within them. This is quite important in the treatment of many internal neoplasms located generally within the "trunk" of the body. It is considered significant that appar- ently the insertion of even the heart within an alternatiήg magnetic field having a frequency as noted does not affect the body to any significant or material extent. As a result of this, an ap¬ paratus 10 can be utilized in treating even a neoplasm which is immediatley adjacent to or is associated with the heart in one manner or another.

The amount of time that a part of the body is generally within the coils 12 in practicing the present invention will, of course, vary depending upon the total amount of heat or the maximum tem¬ perature required in order to cause necrosis of neoplastic growth. When the magnetic particles employed have a Curie point from about 42°C. to about 90°C. , excessive overheating will normally be prevented by the loss of magnetic properties of the particles used as they reach a temperature corresponding to their Curie points. When, however, magnetic particles are used which have Curie points above the specific temperature range noted, it is considered highly desirable to carefully monitor the time that a specific area containing magnetic particles is generally within the coils 12 and the power supplied to these coils. Generally speaking, at a specific power level the coils 12 should not be operated any longer than is necessary to cause necrosis of neoplastic tissue. Since this is dependent upon both temperature and time, it is considered desirable to carefully monitor the temperature.

As the apparatus 10 is used, it is obvious that normal cells or tissue adjacent to any magnetic materials or particles present will become heated to at least a degree and that frequently such normal tissue or growth will be necrosed. Normally, this does not present any significant problems. As is well known, the body has what may be regarded as inherent mechanisms for dealing with, many dif- ferent eventualities and is reasonably capable of disposing of both necrosed normal and neoplastic tissue or cells through normal metabollic processes. Further, the body is reasonably capable of developing what may be loosely referred to as scar tissue in compensating for normal growth which has been lost as a result of hyperthermia. Not infrequently, the body, through its own internal mechanisms, will develop barriers of a known or conventional type isolating areas where magnetic particles have been used from the normal metabollic operation of the body.

Claims

I CLAIM:

1. A process of causing necrosis of neoplasm as a result of hyperthermia of the neoplasm in which particles capable of exhibiting hysteresis heating are injected into tissue in proximity with the neoplasm and are subjected to an alternating magnetic field so as to cause hysteresis heating of said particles in which the improvement com- prises: said particles are mixed with a carrier fluid as they are injected into said tissue, said carrier fluid being biologically inert and being capable of becoming non-fluid within said tissue, and causing said carrier fluid to become non- fluid within said tissue.

2. A process as claimed in claim 1 wherein: said carrier fluid is capable of being poly¬ merized so as to become non-fluid through the action of a catalyst, and said carrier fluid includes a catalyst for causing polymerization of said carrier fluid.

3. A process as claimed in claim 1 wherein: said particles are coated within an adherent coating of a biologically inert material.

4. A process as claimed in claim 1 wherein: said carrier fluid forms an adherent coating of a biologically inert character around said particles.

5. A process as claimed in claim 1 wherein: said particles are ferromagnetic particles.

6. A process as claimed in claim 1 wherein: said particles are ferromagnetic particles and are no less dimension than the dimension of the magnetic domains of the material within said particles.

7. A process as claimed in claim 1 wherein: said particles are magnetic particles having a Curie point which is sufficiently high so as to correspond to a temperature required to cause necrosis by hyperthermia but which is below about 90°C.

8. A process as claimed in claim 1 wherein: said particles are ferrite particles.

9. A process as claimed in claim 1 wherein: said particles are ferrite particles, said particles are ferromagnetic particles having a Curie point which is sufficiently high so as to correspond to a temperature required to cause necrosis by hyperthermia but which is below about 90°C.

10. A process as claimed in claim 1 wherein: said carrier fluid is present within said mixture in an amount sufficient to wet all of the surfaces of said particles and wetting the sur¬ faces of said particles.

11. A process as claimed in claim 1 wherein: said mixture of particles and carrier fluid being sufficiently cohesive so as to remain to¬ gether as a unit as it is injected into tissue and until it is rendered non-fluid.

12. A process as claimed in claim 1 wherein: said carrier fluid is a silicone composition including a catalyst capable of causing said compo¬ sition to solidify to form an elastomeric body, said carrier fluid wetting said particles and is present in an amount sufficient to wet all of the surfaces of said particles, said particles -have a Curie point which is sufficiently high so as to correspond to a tem¬ perature required to cause necrosis of a particu- lar neoplasm by hyperthermia but which is below about 90°C. , said mixture of particles and carrier fluid being sufficiently cohesive so as to remain togeth¬ er as a body as it is injected into tissues and until it is rendered -non-fluid.

13. A process as claimed in claim 12 wherein: said particles are ferromagnetic particles.

14. An induction heating apparatus having a series of separate induction heating coils and means for passing an alternating current through said coils at a frequency sufficient to cause induction heating in which the improvement com- prises: a capacitor means associated with each of said coils, each capacitor means being connected across the terminal of the coil with which it is associated so as to form a physically separate tank circuit, said coils being located in axial alignment with one another and being located immediately adjacent to one another, only one of said coils being connected to said means for passing AC current.

15. An induction heating apparatus as claimed in claim 1.4 wherein: said means for passing an AC current -is ad- justable so as to be capable of being adjusted to vary the frequency of said current.

16. An induction heating apparatus as claimed in claim 14 wherein: the openings in said coils are of an identical oval shape reasonably corresponding to the config¬ uration of the human body and are aligned with one another.

17. An induction heating apparatus as claimed in claim 14 wherein: each of said coils is a coil of a litz wire conductor disposed within a hollow tube; and including means for circulating water through the tubes of said coils.

18. An induction heating apparatus as claimed in claim 14 wherein: said coils are identical coils, said means for passing an AC current supplies said current at said resonant frequency, said means for passing an AC current is ad¬ justable so as to be capable of being adjusted to vary the frequency of said current.

X. *3._4T

__ c: PI each of said coils is a coil of a litz wire conductor disposed within a hollow tube, and including means for circulating water through the tubes of said coils.

19. An induction heating apparatus as claimed in claim 18 wherein: the openings in said coils are of an identical oval shape reasonably corresponding to the config¬ uration of the human body and are aligned with one another.

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