CA1115781A - Apparatus for localized heating of a living tissue, using electromagnetic waves of very high frequency, for medical applications - Google Patents
Apparatus for localized heating of a living tissue, using electromagnetic waves of very high frequency, for medical applicationsInfo
- Publication number
- CA1115781A CA1115781A CA300,656A CA300656A CA1115781A CA 1115781 A CA1115781 A CA 1115781A CA 300656 A CA300656 A CA 300656A CA 1115781 A CA1115781 A CA 1115781A
- Authority
- CA
- Canada
- Prior art keywords
- probe
- high frequency
- living tissues
- dielectric
- receiver
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/40—Applying electric fields by inductive or capacitive coupling ; Applying radio-frequency signals
- A61N1/403—Applying electric fields by inductive or capacitive coupling ; Applying radio-frequency signals for thermotherapy, e.g. hyperthermia
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
Abstract
ABSTRACT OF THE DISCLOSURE:
An apparatus for thermal treatment of the human body, using electromagnetic waves (200 to 2500 Mc/s) and radio-metric means for monitoring and possibly controlling the tempe-rature reached by the living tissues. A generator at ultrahigh frequency delivers a power of about one Watt into a coaxial cable terminated by a probe emitting electromagnetic waves in the organ to be heated by dielectric losses in the medium. A multichannel receiver, switched at intervals, analyzes the radiation re-emitted by the living tissues through the probe, then utilized as a receiving antenna. The temperature reached in a region surrounding the probe is deduced therefrom and can be utilized for controlling the power emitted through a servocontrol system.
An apparatus for thermal treatment of the human body, using electromagnetic waves (200 to 2500 Mc/s) and radio-metric means for monitoring and possibly controlling the tempe-rature reached by the living tissues. A generator at ultrahigh frequency delivers a power of about one Watt into a coaxial cable terminated by a probe emitting electromagnetic waves in the organ to be heated by dielectric losses in the medium. A multichannel receiver, switched at intervals, analyzes the radiation re-emitted by the living tissues through the probe, then utilized as a receiving antenna. The temperature reached in a region surrounding the probe is deduced therefrom and can be utilized for controlling the power emitted through a servocontrol system.
Description
578~
This invention relates to an apparatus for localized heating of a living thing using electromagnetic waves of very high frequency and to the use of this apparatus in medicine.
It is known that the local heating of an organ or of part of an organ, applied either on its own or in conjunction with another medical treatment, such as radiotherapy or chemo-therapy, can have significant therapeutic effects.
Various means for locally heating a surfaae zone of the human body are already known. The process known as dia-thermy is used for organs situated deep inside the body and consists in connecting a short-wave generator operating for ~;
example at a frequency of 13.5 or 27 Mc/s to two electrodes forming capacitors which are applied on either side of the organ to be --heated.
Now the difficulties involved in using and the disadvantages attending the known means are varlous:
The increase in temperature of the various regions of the organ is difficult to determine, complex relations existing between the heating time, the nature of the living tissue and ~ -the~temperature reached. It lS generally accepted that a temperature of 47C should not be locally exceeded which, even over a short period, results in necrosis of the living tissues.
In the case of diathermy, it is possible to a certain exten~ to delimit the region to be heated by varying the shape and size of the electrodes. However, the dimensions of the region subjected to heating are necessarily of the order of magnitude of the distance between the electrodes with the result that, depending upon the region of the body in question, the heated volume may be such greater than is desirable.
In addition, it is not possible to control the distribution of the heating temperature. Thus for example the energy per unit volume which is dissipated into a fatty tissue ls .~ '' , ,',~ ~ `
much greater than that dissipated into a muscular tissue. An effect such as this can make the apparatus ineffectual in certain cases because a given temperature in a given tissue can only be reached at the expense of necrosis of the adjacent tissues~
The present invention obviates some of the difficul-ties referred to above whilst at the same time affording the following advantages:
- very precise localization of the region subjected to heating;
- simultaneous measurement of the maximal temperature of the hottest point.
According to the invention, there is provided an apparatus for localized heating of living tissues, using electro-magnetic waves of ultra-high frequency, comprising an ultra high frequency generator, a transmission line having one end connected to said ultra high frequency generator, a probe connected to another end of said transmlssion line, said probe capable of emitting said ultra-high frequency waves and designed for being ~20 introduced into the living tissues and radiometric means for monitoring the temperature of $aid living tissues in contact with said probe, said radiometric means comprising a radiometry receiver selectively coupled to said probe through said transmission line, said reaeiver capable oE measurlng the electromagnetia radiation re-emitted by said living tissues and picked up by said probe.
The invention will be better understood and other features thereof will become apparent from the following description in conjunction with the accompanying drawings, wherein:
Fig. 1 diagrammatically illustrates one example of embodiment of an apparatus according to the invention, comprising a radiometry receiver;
_ ~ _ .~ . .
P~
1~15781 Fig. 2 diagrammatically illustrates one example of an arrangement for calibration of the radiometric means~
Figs. 3 to 6 are diagrammatic sections through examples of probes forming part of the apparatus according to the lnvention;
Fig. 7 is an explanatory diagram;
Fig. 8 is a diagrammatic section through one example of a probe with a thermocouple incorporated therein;
Fig. 9 shows an insertion vehicle for introducing a probe;
Fig. lO is an explanatory diagram.
In the embodiment of the apparatus shown ln Fig. 1, the means for supplying electrical energy at ultra high frequency to a probe 5 are diagrammatically represented by an ultra high-frequency generator 1 connected to the probe by a line 11, for example of the coaxial type, a sw~tch 3 and a coaxial cable 4.
The generator transmits into line 11 a fixed or variable frequency for instance in the range from 200 to 2500 MHz.
In cases where a single generator is used, it may be provided 20 with a system for periodically varying the frequency (modulator) ;
underthe control of a program of the data-processing type for effecting a time-sharing of the frequencies generated.
Where several generators are combined ln the same apparatus~ they may operate either simultaneously or successively under the control of a program of the data-processing type because, as will be explained hereinafter, the penetration of the waves emitted by the probe depends upon the frequency according to a ~;~
law which depends upon the type of probe. Various probes are described hereinafter.
The switch 3 enables the line 11 to be disconnected from and the cable 4 to be connected to a radiometry receiver 2 via line 12. A receiver such as this, of conventional type, comprises several radiometric devices operating in different -~
B ~ 3 -!
. , . ~ , , . . :
~i~578~
frequency bands. In a receiver of this type, the measuring apparatus giving the noise levels existing in each band are directly graduated in degrees of temperature. In addition, it is possible to provide the receiver with a calculator and with peripheral elements giving the temperature distribution in a region surrounding the probe. By means of a five-band receiver equipped with a calcuIator, it wouId be possible to record five temperatures at different distances from the probe. For example, a measuring time of the order of one second should be sufficient for measuring the maximum temperature to a fraction of a degree in a frequency band with limits of 0.2 to 2F, F being the frequency of the heating waves.
The arrangement shown in Fig. 2 is a calibrating device for radiometry receiver. The same ~lements as in Fig. 1 have been denoted by the same reference numerals, but the probe 5 contains a system with a thermocouple incorporated therein `~
which will be described hereinafter. This system is connected by a twin-wire line 22 to a thermometric volt meter 20. The coaxial pair of the cable 4 is connected by a coaxial cable 21 to the generator l via a switch 23.
It is possible to control the heating in the apparatus of Fig. 1 and the arrangement of Fig. 2 by providlng the device with a conventional servocontrol system.
The three probes shown ln Figs. 3 to 5 are examples of embodiment designed to pierce the skin and to penetrate the living tissues of the human body. Their introduction may be facilitated by a needle acting as a so-called -insertion vehicle-(Fig. 9) of which the diameter may be very small, i.e. of the order of l millimetre. The probe and the coaxial cable which it extends have a diameter of, for example, 0.85 mm and are introduced into the vehicle before insertion into the human body. After penetration and positioning of the assembly as a whole, the ~15781 insertion vehicle is carefully withdrawn by sliding it along the coaxial cable.
A probe of the type shown in Fig. 3 is obtained simply by cutting a small-diameter coaxial cable from which the outer conductor 51 is removed over a length of, for example,2 centimetres. The dielectric 52 is an organic compound which is solid at the temperature of the human body, for example polytetrafluoroethylene. The inner conductor 53 acts as an antenna emitting the electxomagnetic waves into the living tissue, the bare dielectric acting as an impedance matcher between the antenna and the propagation medium.
The probes shown in Figs. 4 and 5 are variants i~
which the central conductor 53 is exposed either over the entire length of the antenna or over half its length, ~he outer conductor being removed over a length of the same order as in Fig. 3. The choice of the length of the antenna is made in dependence upon the characteristic impedance of the coaxial cable and the frequency of the electromagnetic radiation (for example 2 cm for a cable having a characteristic impedance of 50 ohms in a range from 300 to 2500 Mc/s).
Fig. 7 is a graph showing the fraction of the reflected power ~in ~) for the probes shown in Figs. 3 to 5 in dependence upon the frequency emitted by the generator. It can be seen that the three corresponding curves each have an expo-nentially decreasing part which intersects a linear 10% ordinate at a point situated:
- between 300 and 400 Mc/s for the curve 31 (probe of Fig. 3);
- between 900and 1500 Mc/s for the curve 32 ~probe of Fig. 4);
- between 1800 and 2000 Mc/s for the curve 22 ~probe of Fig. 5).
. .
. . .
.
. ~ ~
~15781 From this it follows that the percentage of total energy dissipated into the organ in the form of heat (by dielectric losses) is very high (above 90%) when the frequency exceeds a minimum frequency characteristic o~ the type of probe used for a cable having a given impedance characteristic and for a given tissue.
By contrast, it is possible with the same probe to obtain different depths of penetration by varying the frequency, whence the advantage of using a generator generating a variable frequency output under the control of a data program.
The probe shown in Fig. 6 is of a different type designed for introduction into the human body by a natural route, for example the oesophagus. The only difference between the probe shown in Fig. 6 and the preceding probes lies in the presence of an ovoidal sleeve made of a dielectric material selected for its physlcal properties (particularly its permittivity which is similar to that of the dielectric 52) and chemical properties (harmlessness to living tissue ), for example silicone rubber.
Fig. 8 shows a thermocouple system incorporated in ~20 the cable 4 feeding a probe 5. A wire 41 made of the copper (60%) nickel (40~) alloy is arranged at the periphery of the~
cable 4, being isolated by a dielectric 42 from the outer conductor Sl of the coaxial line. In the immediate vicinity of the probe 5, this wire is welded at 410 to the outer conductor Sl. The wire 41 emerges at the other end of the cable 4 where it is connected to a first conductor of the two-conductor line 22 symbolized by a single line (Fig. 2), the second conductor of this line being connected to the conductor 51. By virtue of the thermometric voltmeter described above, a system such as this makes it possible to measure the temperature prevailing at the actual location of the probe.
Fig. 10 relates to a system comprising two probes ;
101 and 102 arranged parallel to one another in an organ to be - .
~57~
treated. These two probes may be introduced by using a system comprising two insertion vehicles Eixed parallel to one another by a metallic plate to which their bases are welded, leaving the points of the needles free.
XX r~presents the axls of symmetry of thc systcm of two probes. If the distances from this axis, measured along an axis Ox, of the various points of the organ to be treated are recorded as abscissae and the temperature difference ~ between the temperature of the various points of the heated region and the normal temperature of the organ to be-treated as ordinates along a perpendicular axis, a curve 100 is obtained. A curve such as this has two rounded peaks corresponding to the respective locations of the two probes. It can be seen that the heated region is considerably enlarged and that the temperature is rendered uniform to a certain extent. It iS also possible to use systems -~
~comprising three or four insertion vehicles fixed parallel to one another in the same way as in the two-vehicle system.
Where several probes are used, they are each connected .
in~parallel by a coaxial cable optionally provided with a thermo-couple to the high frequency generator, if necessary with inter-positlon of a~switch.
:,:
' ~ ~.
., , ~
.:
: . , ~ _ 7 _ B
.~, . . . ,.; ,; .. ~. ~ . . . ;. `
This invention relates to an apparatus for localized heating of a living thing using electromagnetic waves of very high frequency and to the use of this apparatus in medicine.
It is known that the local heating of an organ or of part of an organ, applied either on its own or in conjunction with another medical treatment, such as radiotherapy or chemo-therapy, can have significant therapeutic effects.
Various means for locally heating a surfaae zone of the human body are already known. The process known as dia-thermy is used for organs situated deep inside the body and consists in connecting a short-wave generator operating for ~;
example at a frequency of 13.5 or 27 Mc/s to two electrodes forming capacitors which are applied on either side of the organ to be --heated.
Now the difficulties involved in using and the disadvantages attending the known means are varlous:
The increase in temperature of the various regions of the organ is difficult to determine, complex relations existing between the heating time, the nature of the living tissue and ~ -the~temperature reached. It lS generally accepted that a temperature of 47C should not be locally exceeded which, even over a short period, results in necrosis of the living tissues.
In the case of diathermy, it is possible to a certain exten~ to delimit the region to be heated by varying the shape and size of the electrodes. However, the dimensions of the region subjected to heating are necessarily of the order of magnitude of the distance between the electrodes with the result that, depending upon the region of the body in question, the heated volume may be such greater than is desirable.
In addition, it is not possible to control the distribution of the heating temperature. Thus for example the energy per unit volume which is dissipated into a fatty tissue ls .~ '' , ,',~ ~ `
much greater than that dissipated into a muscular tissue. An effect such as this can make the apparatus ineffectual in certain cases because a given temperature in a given tissue can only be reached at the expense of necrosis of the adjacent tissues~
The present invention obviates some of the difficul-ties referred to above whilst at the same time affording the following advantages:
- very precise localization of the region subjected to heating;
- simultaneous measurement of the maximal temperature of the hottest point.
According to the invention, there is provided an apparatus for localized heating of living tissues, using electro-magnetic waves of ultra-high frequency, comprising an ultra high frequency generator, a transmission line having one end connected to said ultra high frequency generator, a probe connected to another end of said transmlssion line, said probe capable of emitting said ultra-high frequency waves and designed for being ~20 introduced into the living tissues and radiometric means for monitoring the temperature of $aid living tissues in contact with said probe, said radiometric means comprising a radiometry receiver selectively coupled to said probe through said transmission line, said reaeiver capable oE measurlng the electromagnetia radiation re-emitted by said living tissues and picked up by said probe.
The invention will be better understood and other features thereof will become apparent from the following description in conjunction with the accompanying drawings, wherein:
Fig. 1 diagrammatically illustrates one example of embodiment of an apparatus according to the invention, comprising a radiometry receiver;
_ ~ _ .~ . .
P~
1~15781 Fig. 2 diagrammatically illustrates one example of an arrangement for calibration of the radiometric means~
Figs. 3 to 6 are diagrammatic sections through examples of probes forming part of the apparatus according to the lnvention;
Fig. 7 is an explanatory diagram;
Fig. 8 is a diagrammatic section through one example of a probe with a thermocouple incorporated therein;
Fig. 9 shows an insertion vehicle for introducing a probe;
Fig. lO is an explanatory diagram.
In the embodiment of the apparatus shown ln Fig. 1, the means for supplying electrical energy at ultra high frequency to a probe 5 are diagrammatically represented by an ultra high-frequency generator 1 connected to the probe by a line 11, for example of the coaxial type, a sw~tch 3 and a coaxial cable 4.
The generator transmits into line 11 a fixed or variable frequency for instance in the range from 200 to 2500 MHz.
In cases where a single generator is used, it may be provided 20 with a system for periodically varying the frequency (modulator) ;
underthe control of a program of the data-processing type for effecting a time-sharing of the frequencies generated.
Where several generators are combined ln the same apparatus~ they may operate either simultaneously or successively under the control of a program of the data-processing type because, as will be explained hereinafter, the penetration of the waves emitted by the probe depends upon the frequency according to a ~;~
law which depends upon the type of probe. Various probes are described hereinafter.
The switch 3 enables the line 11 to be disconnected from and the cable 4 to be connected to a radiometry receiver 2 via line 12. A receiver such as this, of conventional type, comprises several radiometric devices operating in different -~
B ~ 3 -!
. , . ~ , , . . :
~i~578~
frequency bands. In a receiver of this type, the measuring apparatus giving the noise levels existing in each band are directly graduated in degrees of temperature. In addition, it is possible to provide the receiver with a calculator and with peripheral elements giving the temperature distribution in a region surrounding the probe. By means of a five-band receiver equipped with a calcuIator, it wouId be possible to record five temperatures at different distances from the probe. For example, a measuring time of the order of one second should be sufficient for measuring the maximum temperature to a fraction of a degree in a frequency band with limits of 0.2 to 2F, F being the frequency of the heating waves.
The arrangement shown in Fig. 2 is a calibrating device for radiometry receiver. The same ~lements as in Fig. 1 have been denoted by the same reference numerals, but the probe 5 contains a system with a thermocouple incorporated therein `~
which will be described hereinafter. This system is connected by a twin-wire line 22 to a thermometric volt meter 20. The coaxial pair of the cable 4 is connected by a coaxial cable 21 to the generator l via a switch 23.
It is possible to control the heating in the apparatus of Fig. 1 and the arrangement of Fig. 2 by providlng the device with a conventional servocontrol system.
The three probes shown ln Figs. 3 to 5 are examples of embodiment designed to pierce the skin and to penetrate the living tissues of the human body. Their introduction may be facilitated by a needle acting as a so-called -insertion vehicle-(Fig. 9) of which the diameter may be very small, i.e. of the order of l millimetre. The probe and the coaxial cable which it extends have a diameter of, for example, 0.85 mm and are introduced into the vehicle before insertion into the human body. After penetration and positioning of the assembly as a whole, the ~15781 insertion vehicle is carefully withdrawn by sliding it along the coaxial cable.
A probe of the type shown in Fig. 3 is obtained simply by cutting a small-diameter coaxial cable from which the outer conductor 51 is removed over a length of, for example,2 centimetres. The dielectric 52 is an organic compound which is solid at the temperature of the human body, for example polytetrafluoroethylene. The inner conductor 53 acts as an antenna emitting the electxomagnetic waves into the living tissue, the bare dielectric acting as an impedance matcher between the antenna and the propagation medium.
The probes shown in Figs. 4 and 5 are variants i~
which the central conductor 53 is exposed either over the entire length of the antenna or over half its length, ~he outer conductor being removed over a length of the same order as in Fig. 3. The choice of the length of the antenna is made in dependence upon the characteristic impedance of the coaxial cable and the frequency of the electromagnetic radiation (for example 2 cm for a cable having a characteristic impedance of 50 ohms in a range from 300 to 2500 Mc/s).
Fig. 7 is a graph showing the fraction of the reflected power ~in ~) for the probes shown in Figs. 3 to 5 in dependence upon the frequency emitted by the generator. It can be seen that the three corresponding curves each have an expo-nentially decreasing part which intersects a linear 10% ordinate at a point situated:
- between 300 and 400 Mc/s for the curve 31 (probe of Fig. 3);
- between 900and 1500 Mc/s for the curve 32 ~probe of Fig. 4);
- between 1800 and 2000 Mc/s for the curve 22 ~probe of Fig. 5).
. .
. . .
.
. ~ ~
~15781 From this it follows that the percentage of total energy dissipated into the organ in the form of heat (by dielectric losses) is very high (above 90%) when the frequency exceeds a minimum frequency characteristic o~ the type of probe used for a cable having a given impedance characteristic and for a given tissue.
By contrast, it is possible with the same probe to obtain different depths of penetration by varying the frequency, whence the advantage of using a generator generating a variable frequency output under the control of a data program.
The probe shown in Fig. 6 is of a different type designed for introduction into the human body by a natural route, for example the oesophagus. The only difference between the probe shown in Fig. 6 and the preceding probes lies in the presence of an ovoidal sleeve made of a dielectric material selected for its physlcal properties (particularly its permittivity which is similar to that of the dielectric 52) and chemical properties (harmlessness to living tissue ), for example silicone rubber.
Fig. 8 shows a thermocouple system incorporated in ~20 the cable 4 feeding a probe 5. A wire 41 made of the copper (60%) nickel (40~) alloy is arranged at the periphery of the~
cable 4, being isolated by a dielectric 42 from the outer conductor Sl of the coaxial line. In the immediate vicinity of the probe 5, this wire is welded at 410 to the outer conductor Sl. The wire 41 emerges at the other end of the cable 4 where it is connected to a first conductor of the two-conductor line 22 symbolized by a single line (Fig. 2), the second conductor of this line being connected to the conductor 51. By virtue of the thermometric voltmeter described above, a system such as this makes it possible to measure the temperature prevailing at the actual location of the probe.
Fig. 10 relates to a system comprising two probes ;
101 and 102 arranged parallel to one another in an organ to be - .
~57~
treated. These two probes may be introduced by using a system comprising two insertion vehicles Eixed parallel to one another by a metallic plate to which their bases are welded, leaving the points of the needles free.
XX r~presents the axls of symmetry of thc systcm of two probes. If the distances from this axis, measured along an axis Ox, of the various points of the organ to be treated are recorded as abscissae and the temperature difference ~ between the temperature of the various points of the heated region and the normal temperature of the organ to be-treated as ordinates along a perpendicular axis, a curve 100 is obtained. A curve such as this has two rounded peaks corresponding to the respective locations of the two probes. It can be seen that the heated region is considerably enlarged and that the temperature is rendered uniform to a certain extent. It iS also possible to use systems -~
~comprising three or four insertion vehicles fixed parallel to one another in the same way as in the two-vehicle system.
Where several probes are used, they are each connected .
in~parallel by a coaxial cable optionally provided with a thermo-couple to the high frequency generator, if necessary with inter-positlon of a~switch.
:,:
' ~ ~.
., , ~
.:
: . , ~ _ 7 _ B
.~, . . . ,.; ,; .. ~. ~ . . . ;. `
Claims (10)
1. An apparatus for localized heating of living tissues, using electromagnetic waves of ultra-high frequency, comprising an ultra-high frequency generator, a transmission line having one end connected to said ultra high frequency generator, a probe connected to another end of said transmission line, said probe capable of emitting said ultra-high frequency waves and designed for being introduced into the living tissues, and radiometric means for monitoring the temperature of said living tissues in contact with said probe, said radiometric means comprising a radiometry receiver selectively coupled to said probe through said transmission line, said receiver capable of measuring the electromagnetic radiation re-emitted by said living tissues and picked up by said probe.
2. An apparatus as claimed in claim 1, wherein said transmission line is of the coaxial type and designed to be introduced with the probe into the living tissues.
3. An apparatus as claimed in claim 2, wherein said probe comprises:
a coaxial cable having an outer conductor and an inner conductor separated by a solid dielectric, the outer conductor of said cable being removed over a length of the order of half the wavelength of the radiation of said generator.
a coaxial cable having an outer conductor and an inner conductor separated by a solid dielectric, the outer conductor of said cable being removed over a length of the order of half the wavelength of the radiation of said generator.
4. An apparatus as claimed in claim 2, wherein said probe comprises:
a coaxial cable having an outer conductor and an inner conductor separated by a solid dielectric, the outer conductor of said cable being removed over a length of the order of half the wavelength of the radiation of the generator, and at least a part of said dielectric being bare over at least a part of the length of said probe.
a coaxial cable having an outer conductor and an inner conductor separated by a solid dielectric, the outer conductor of said cable being removed over a length of the order of half the wavelength of the radiation of the generator, and at least a part of said dielectric being bare over at least a part of the length of said probe.
5. An apparatus as claimed in claim 1, wherein said probe is surrounded by a sleeve of dielectric material.
6. An apparatus as claimed in claim 2, wherein the probe comprises a coaxial cable including an outer conductor, and an inner conductor separated by a dielectric wherein the dielectric of said coaxial cable is polytetrafluorethylene.
7. An apparatus as claimed in claim 5, wherein said sleeve is made of silicone rubber.
8. An apparatus as claimed in claim 1, wherein said radiometric receiver is of the type comprising several frequency bands and comprises a temperature indicator corresponding to each of said frequency bands.
9. An apparatus as claimed in claim 8, wherein said radiometric receiver additionally comprises a calculator and peripheral elements giving the distribution of temperatures in a region surrounding said probe.
10. An apparatus as claimed in claim 1, further comprising a servocontrol system for controlling the power delivered by the ultra-high frequency generator to the probe based on the temperature measured by the receiver.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| FR7710756 | 1977-04-08 | ||
| FR7710756A FR2421628A1 (en) | 1977-04-08 | 1977-04-08 | LOCALIZED HEATING DEVICE USING VERY HIGH FREQUENCY ELECTROMAGNETIC WAVES, FOR MEDICAL APPLICATIONS |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1115781A true CA1115781A (en) | 1982-01-05 |
Family
ID=9189245
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA300,656A Expired CA1115781A (en) | 1977-04-08 | 1978-04-07 | Apparatus for localized heating of a living tissue, using electromagnetic waves of very high frequency, for medical applications |
Country Status (6)
| Country | Link |
|---|---|
| US (1) | US4312364A (en) |
| JP (1) | JPS54486A (en) |
| CA (1) | CA1115781A (en) |
| DE (1) | DE2815156A1 (en) |
| FR (1) | FR2421628A1 (en) |
| GB (1) | GB1596459A (en) |
Families Citing this family (148)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4341227A (en) * | 1979-01-11 | 1982-07-27 | Bsd Corporation | System for irradiating living tissue or simulations thereof |
| US4285346A (en) * | 1979-03-14 | 1981-08-25 | Harry V. LeVeen | Electrode system |
| US4311154A (en) * | 1979-03-23 | 1982-01-19 | Rca Corporation | Nonsymmetrical bulb applicator for hyperthermic treatment of the body |
| JPS55130640A (en) * | 1979-03-30 | 1980-10-09 | Olympus Optical Co | Endoscope |
| US4448198A (en) * | 1979-06-19 | 1984-05-15 | Bsd Medical Corporation | Invasive hyperthermia apparatus and method |
| FR2475399A1 (en) * | 1980-02-08 | 1981-08-14 | Telecommunications Sa | DEVICE FOR HYPERTHERMIC TREATMENT BY RADIO FREQUENCY FIELD |
| US4346716A (en) * | 1980-03-31 | 1982-08-31 | M/A Com, Inc. | Microwave detection system |
| US4557272A (en) * | 1980-03-31 | 1985-12-10 | Microwave Associates, Inc. | Microwave endoscope detection and treatment system |
| US4798215A (en) * | 1984-03-15 | 1989-01-17 | Bsd Medical Corporation | Hyperthermia apparatus |
| WO1981003616A1 (en) * | 1980-06-17 | 1981-12-24 | T Sandhu | Microwave antenna system for intracavitary insertion |
| JPS5725863A (en) * | 1980-07-23 | 1982-02-10 | Olympus Optical Co | Endoscope with microwave heater |
| JPS5755124A (en) * | 1980-09-18 | 1982-04-01 | Olympus Optical Co | Endoscope |
| FR2511876A1 (en) * | 1981-08-31 | 1983-03-04 | Centre Nat Rech Scient | MICROWAVE APPLICATOR FOR LOCALIZED HYPERTHERMIA |
| JPS58173541A (en) * | 1982-04-03 | 1983-10-12 | 銭谷 利男 | Operation by microwave |
| US4600018A (en) * | 1982-06-02 | 1986-07-15 | National Research Development Corporation | Electromagnetic medical applicators |
| GB2122092B (en) * | 1982-06-02 | 1985-06-19 | Secr Defence | Improvements in or relating to electromagnetic medical applicators |
| JPS5917361A (en) * | 1982-07-20 | 1984-01-28 | 株式会社東芝 | Microwave treating apparatus |
| US5435805A (en) * | 1992-08-12 | 1995-07-25 | Vidamed, Inc. | Medical probe device with optical viewing capability |
| US5385544A (en) * | 1992-08-12 | 1995-01-31 | Vidamed, Inc. | BPH ablation method and apparatus |
| US5542915A (en) * | 1992-08-12 | 1996-08-06 | Vidamed, Inc. | Thermal mapping catheter with ultrasound probe |
| US5421819A (en) | 1992-08-12 | 1995-06-06 | Vidamed, Inc. | Medical probe device |
| US5370675A (en) * | 1992-08-12 | 1994-12-06 | Vidamed, Inc. | Medical probe device and method |
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-
1977
- 1977-04-08 FR FR7710756A patent/FR2421628A1/en active Granted
-
1978
- 1978-04-05 US US05/893,814 patent/US4312364A/en not_active Expired - Lifetime
- 1978-04-05 GB GB13405/78A patent/GB1596459A/en not_active Expired
- 1978-04-07 CA CA300,656A patent/CA1115781A/en not_active Expired
- 1978-04-07 DE DE19782815156 patent/DE2815156A1/en active Granted
- 1978-04-07 JP JP4115378A patent/JPS54486A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| FR2421628B1 (en) | 1980-09-12 |
| DE2815156C2 (en) | 1988-05-05 |
| GB1596459A (en) | 1981-08-26 |
| JPS54486A (en) | 1979-01-05 |
| US4312364A (en) | 1982-01-26 |
| JPS6132025B2 (en) | 1986-07-24 |
| DE2815156A1 (en) | 1978-10-19 |
| FR2421628A1 (en) | 1979-11-02 |
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