CA1209645A - Endotract antenna device for hyperthermia - Google Patents
Endotract antenna device for hyperthermiaInfo
- Publication number
- CA1209645A CA1209645A CA000437376A CA437376A CA1209645A CA 1209645 A CA1209645 A CA 1209645A CA 000437376 A CA000437376 A CA 000437376A CA 437376 A CA437376 A CA 437376A CA 1209645 A CA1209645 A CA 1209645A
- Authority
- CA
- Canada
- Prior art keywords
- antenna device
- balloon
- antenna
- tube
- draining
- 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
- 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
-
- 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
- A61B18/1815—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves
-
- 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
- A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
- A61B2018/00011—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
-
- 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
- A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
- A61B2018/00553—Sphincter
Abstract
TITLE OF THE INVENTION
Endotract Antenna Device For Hyperthermia ABSTRACT OF THE DISCLOSURE
The endotract antenna for hyperthermia comprising a microwave radiation antenna, a balloon-like member made of a thin polymeric film and surrounding the antenna and means for feeding and draining a cooling liquid to and from the inside of the balloon-like member, enables effective warming of the endotract lesion such as tumor by effectively applying the energy of the microwaves emitted from the antenna to the endotract lesion.
Endotract Antenna Device For Hyperthermia ABSTRACT OF THE DISCLOSURE
The endotract antenna for hyperthermia comprising a microwave radiation antenna, a balloon-like member made of a thin polymeric film and surrounding the antenna and means for feeding and draining a cooling liquid to and from the inside of the balloon-like member, enables effective warming of the endotract lesion such as tumor by effectively applying the energy of the microwaves emitted from the antenna to the endotract lesion.
Description
~ll2~
This invention concerns an endotract antenna device for hyperthermia and, more specifically, lt relates to an endotract antenna device applied to the hyperthermia therapy of tumors or the likes on the organs inside the body.
In the hyperthermia therapy for carcinoma, which utilizes the property of the cancer cells that they are less resistant than normal cells against heat or elevated temperature, a microwave radiation antenna is used to warm the lesion for the therapy.
Ir is desired that the radiation antenna is as thin as possible so that it may be inserted deeply in-to the endotract o the body or the therapy of organs inside the body, or example, a digestive organ,and a sort of linear dipole antenna has been employed so far for such a purpose.
However, it is difficult to dispose the conventional linear dipole antenna in direct contact with a surface of the organ at the lesion, and there is fear that gases or the fluid may remain in the gap between the antenna and the~ surface of the organ.
` As a result, the electromagnetic energy emitted from the microwave antenna of such endotract antenna device is absorbed by the body fluid in the gap, or reflected at the yap and can not always serve for effective and uniform warming of the lesion.
This invention has been made in view of the foregoings and it is an object of this invention to provide an endotract antenna device capable of effectively warming the lesion at ~k~
~L209~;45 the wall of the tract or lumen.
The above-mentioned object can be attained according to' this invention by an endotract antenna device ~or hyperthermia comprising an antenna for radiating microwave, a balloon-like member made of a thin polymeric fllm and surrounding the antenna, and means for feeding and draining cooling liquid to and from the balloon-like member.
This invention is to be described in~ more details referring to the accompanying drawing, by which the foregoing and o-ther objects, as well as the features of this invention will be made clearer, in which Fig. 1 shows an e~plana-tory view Eor an endotract an-tenna device for hyperthermia as a preferred embodiment of this invention, with a balloon being in a slightly expanded state. ~
Referrlng to Fig. l, an endotract antenna devlce for hyperthermia~l comprises~a coaxlal cable 6 for the microwave transmission connected at one end 2 to a microwave oscillator or generator 3 whlch can continuously~ generates microwaves, for example, at a frequency of 91S MHz and formed at -the other end 4 with a sort of linear dipole~antenna 5, a balloon 8 made of a flexible and elastlc polymerlc thin film and forming a chamber 7 of a variable volume~which su~rrounds the~microwave~radlatlon ~ ~ ;
antenna S and reoeives purified water for cooling,~a feed tube~ll opened at one end 9 thereof to the water-containing chamber 7 ahd communicated at the other end 9a~thereof with a feed pump 10 so as to feed the purified water into the chamber 7, andla draining tube : : :
~2a~45 15 connected at one end 12 thereof to the balloon 8 and opened at the other end 13 thereoi by way of a throttling device 14 for the water pressure control so as to drain the water from the balloon 8~ In Fig. 1, the pu~p 10, the feed tube ll, the throttling device 14 and the draining tube 15 constitute means for feeding and draining the cooling water.
The frequency o~ the microwaves generated fro~ the oscillator 3 to be applied to tumors at the wall of the tract i9 usually in the order of between 300 - 3000 MHz. The frequency of the microwaves may be selected from a plurality of oscillation ~requencies that can be generated from the oscillator 3 dependin~
on the size of the antenna 5. The ou-tput power oE the oscillator may b~ in the order of 10 to 200 watt for example.
Referring to the coaxlal;cable 6 which is extended through the drainlng~tube 15 lt lS preferably~designed, for enabling effective transmission o~ the microwaves and easy insertlon of the tube 15 into the tract where the lesian is located, such that the cable has an outer diameter of about
This invention concerns an endotract antenna device for hyperthermia and, more specifically, lt relates to an endotract antenna device applied to the hyperthermia therapy of tumors or the likes on the organs inside the body.
In the hyperthermia therapy for carcinoma, which utilizes the property of the cancer cells that they are less resistant than normal cells against heat or elevated temperature, a microwave radiation antenna is used to warm the lesion for the therapy.
Ir is desired that the radiation antenna is as thin as possible so that it may be inserted deeply in-to the endotract o the body or the therapy of organs inside the body, or example, a digestive organ,and a sort of linear dipole antenna has been employed so far for such a purpose.
However, it is difficult to dispose the conventional linear dipole antenna in direct contact with a surface of the organ at the lesion, and there is fear that gases or the fluid may remain in the gap between the antenna and the~ surface of the organ.
` As a result, the electromagnetic energy emitted from the microwave antenna of such endotract antenna device is absorbed by the body fluid in the gap, or reflected at the yap and can not always serve for effective and uniform warming of the lesion.
This invention has been made in view of the foregoings and it is an object of this invention to provide an endotract antenna device capable of effectively warming the lesion at ~k~
~L209~;45 the wall of the tract or lumen.
The above-mentioned object can be attained according to' this invention by an endotract antenna device ~or hyperthermia comprising an antenna for radiating microwave, a balloon-like member made of a thin polymeric fllm and surrounding the antenna, and means for feeding and draining cooling liquid to and from the balloon-like member.
This invention is to be described in~ more details referring to the accompanying drawing, by which the foregoing and o-ther objects, as well as the features of this invention will be made clearer, in which Fig. 1 shows an e~plana-tory view Eor an endotract an-tenna device for hyperthermia as a preferred embodiment of this invention, with a balloon being in a slightly expanded state. ~
Referrlng to Fig. l, an endotract antenna devlce for hyperthermia~l comprises~a coaxlal cable 6 for the microwave transmission connected at one end 2 to a microwave oscillator or generator 3 whlch can continuously~ generates microwaves, for example, at a frequency of 91S MHz and formed at -the other end 4 with a sort of linear dipole~antenna 5, a balloon 8 made of a flexible and elastlc polymerlc thin film and forming a chamber 7 of a variable volume~which su~rrounds the~microwave~radlatlon ~ ~ ;
antenna S and reoeives purified water for cooling,~a feed tube~ll opened at one end 9 thereof to the water-containing chamber 7 ahd communicated at the other end 9a~thereof with a feed pump 10 so as to feed the purified water into the chamber 7, andla draining tube : : :
~2a~45 15 connected at one end 12 thereof to the balloon 8 and opened at the other end 13 thereoi by way of a throttling device 14 for the water pressure control so as to drain the water from the balloon 8~ In Fig. 1, the pu~p 10, the feed tube ll, the throttling device 14 and the draining tube 15 constitute means for feeding and draining the cooling water.
The frequency o~ the microwaves generated fro~ the oscillator 3 to be applied to tumors at the wall of the tract i9 usually in the order of between 300 - 3000 MHz. The frequency of the microwaves may be selected from a plurality of oscillation ~requencies that can be generated from the oscillator 3 dependin~
on the size of the antenna 5. The ou-tput power oE the oscillator may b~ in the order of 10 to 200 watt for example.
Referring to the coaxlal;cable 6 which is extended through the drainlng~tube 15 lt lS preferably~designed, for enabling effective transmission o~ the microwaves and easy insertlon of the tube 15 into the tract where the lesian is located, such that the cable has an outer diameter of about
2 - 10 mm and comprises a central or inner conductor ln the form of a single wire or twisted wires made of silver-plated copper wire, an insulatorlmade of a polymeric material wit~ less ;
dielectric loss~whlch is dLsposed 'oetween the central conduatar ;
and an outer canduatar~,~the auter shLeldlng aanductar ln the l form of a braided tube ar helically wound bralded aable made ~ ~ ~¦
of silver-plated annealed capper wlres and the protection coatLng~
ar jacket at the outer perip-ery of the outer con~uator maue af ~L20~6~S
a polymeric material such as fluoro resin, polyvinyl chloride, polyethylene and silicone resin which exhibits no to~icity ln the tract.
The microwave radiation antenna 5 comprises a tubular conductor 16 of about A/4 in length (A is~
a wavelength of the microwave in the chamber 7~ which is electrically connected to -the central conductor and another t-ubular conductor 17 also of about A/4 in length which is electrically connected to the outer conductor and spaced apart from the tubular conduc-tor 16 a-t a short insulating portion 18.
The tubular conductors 16 and 17 are preferably of an identical shape or configuration. Instead of providing the tubular conductor 16, the top end of the central conductor may be exposed at least by the length of about A/4.
The baIloon 8 is secured at its base portion to the end 12 of t~e water-draLn tube lS and secured about at the center of its top end 1~9 to the top end of the microwave antenna 5.
Xt is preferred that the polymeric film of the balloon 8 is made of highly flexible material so that the film can be in close contact~with the surface of the wall of the tract where the lesion i5 located and that the film is made as thin as possible so that it may absorb less~energy of the microwaves emitted or transmitted from the an-tenna S, provided that the film has an elasticity sufficient to contain water therein under a certain 1ZI~9645 pressure. In the case of using a thin rubber film for the balloon 8, the film thickness is, for instance, less than 0.5 mm (energy loss of about 30 ~) and, preferably, less than 0.1 mm (energy loss of about 10 - 15 ~). Although the balloon 8 in the illustrated embodiment is shaped such that it is expandable through an oval or elliptic shape to a generally spheric shape, it may take any other configuration. For instance, the balloon 8 may be protruded longitudinally at the top end 19 and, in this case, the top end of the antenna 5 may he inserted into but not fix~d to the elongated recess of the top end 19. The film mat~ri~l Eor the balloon 8 is preferably rubbery polymeric mater.lal, Eor example, natural rubber or syn-thetic rubber such as silicone rubber. ~
In order to transmit the microwaves emitted fron the antenna S as eeectively as possible to the lesion, the coollng medium ~lowin~ the inside of the bal;loon 8, preferably, comprises liquid medlum at least mainly composed of water so that the emitted microwaves are transmitted therein substantially at the same wa~elength as in the lesion. Purlfied water wlth less transmission loss such as absorption is more preferred.
¦ The purlfied water as the coollng llquid~flowing lnside~
: :
of the balloon 8 is kept at an appropriate temperature of about~
O - 45C and,~`preferably, about lS - 42C so that the temperature at the lesion can be maintalned at 4Z - 45C by the purified~water in co-operation with the~antenna S. ~
Further, the flow rate of the cooling~water i9 ~:
: : ::
lZ09645 controlled by the throttling device 14. The throttling device 14 comprises a manually- or automatically-controlled valve, the opening degree of which can be adjusted continuously. The throttling device or valve 14 also serves to produce an adequate pressure within the balloon 8 so as to expand the balloon 8 into an intimate contact wlth the wall of the tràct or lumen organ.
In the illustrated embodiment, the drain tube 15 is constituted as a device main body which is to be inserted through the tract or lumen and through~which the coaxial cable 6 and the feed tube 11 are extended. Alternatively, the feed tube 11 may be modified to be constituted as the device main body while extending the drain tube 15 and the coaxial cable 6 inside of the Eeed tube 11. In -this modified embodlment, the ~ase portion o the balloon 8 is secured to the end of the water-eed tube 11. Furthermore, the feed~tube 11, the drain tube 15 and the coaxial cable 6 may be bundled in close contact together at their respective outer~circumferential surfaces so that the three members form an elongated antenna device main body as a whole, with the balloon 8 belng capped over the open ends of the tubes 11, 15 so as to surround the antenna 5, in the case where the assembly can be formed so smooth and thin as can be intaken, for examplet from the mouth Lnto the stomach ~ ~
The puriied water may be used recyclically by ~ ;
connecting the drain tube 15 to the pump 10 by way of a reservolr not shown. Reference numera~l 20 in the drawing denotes sealed~
portions to prevent the leak of the water.
: ~
:
~2~g64S
A thermosens~r or temperature detector 21 is fixed to the outer surface of the central por-tion of the circumferential wall of the balloon 8 to detect the temperature at the film or membrane surface of the balloon 8, that is, the temperature at the inner surface of the wall of the tract organ. The thermosensor 21 may be a thermocouple or thermistor. The lead 22 for the thermosensor 21 is disposed along the outer surf~ce of the drain tube 15 constituting the device main body in~the illustrated embodiment, it may, however, be passed through the inside of the drain tube 15 as the device main body if desired. The average output ~rom the oscillator 3 and the temperature o~ the coollng wat~r ~ecl to the balloon 8 are controlled dependin~ on the outp~t signal from the thermosensor 21, that is, on the temperature detected by the sensor 21 so that -the temperature of the lesion may be kept a-t about 42 - 45C. The temperature control may be carried out automatically by a suitable control means.
In the endotract antenna device for hyperthermia l constituted as described above, since the microwave radiation antenna 5 is disposed to the inside of the balloon 8 through which the cooling liquid passes, the balloon 8 can be deformed just correspondlng to the uneven inner profile of the wall of the tract organ and put to an lntlmate fittlng~with the inner surface of the wall, that is, the surface~of the lesion by the control of the flow rate and/or the pressure of the cooling liquid flowi~ng inside of the balloon 8~ whereby~the microwave emitted from the antenna 5 can be transmitted with little transmlssion loss to the .
lZ09~i45 lesion through the purified water in the chamber 7 and the thin film of the balloon 8. Furthermore, control for the -temperature and the flow rate of the cooling water 10wing inside of the balloon 8 can ensure the hypothermia therapy while preventing or avoiding localized over-heating and maintaining the temperature of the wide lesion area at a temperature of between 42 - 45C.
As described above, according to this invention, since the endotract antenna device for hyperthermia comprise~
a microwave radiation antenna, a balloon-like member made of a polymeric thin film and surrounding the antenna, and means for .Eeeding and draining a cooling liquid to and from the inside Qf the balloon-member, the energy o~ the microwa~es emitted Erom I.
th~ antenna can be efEectively given to the lesion in the tract or lumen organ, thereby enabling to warm tle lesion effectively.
~ ~ I
~ ~:
dielectric loss~whlch is dLsposed 'oetween the central conduatar ;
and an outer canduatar~,~the auter shLeldlng aanductar ln the l form of a braided tube ar helically wound bralded aable made ~ ~ ~¦
of silver-plated annealed capper wlres and the protection coatLng~
ar jacket at the outer perip-ery of the outer con~uator maue af ~L20~6~S
a polymeric material such as fluoro resin, polyvinyl chloride, polyethylene and silicone resin which exhibits no to~icity ln the tract.
The microwave radiation antenna 5 comprises a tubular conductor 16 of about A/4 in length (A is~
a wavelength of the microwave in the chamber 7~ which is electrically connected to -the central conductor and another t-ubular conductor 17 also of about A/4 in length which is electrically connected to the outer conductor and spaced apart from the tubular conduc-tor 16 a-t a short insulating portion 18.
The tubular conductors 16 and 17 are preferably of an identical shape or configuration. Instead of providing the tubular conductor 16, the top end of the central conductor may be exposed at least by the length of about A/4.
The baIloon 8 is secured at its base portion to the end 12 of t~e water-draLn tube lS and secured about at the center of its top end 1~9 to the top end of the microwave antenna 5.
Xt is preferred that the polymeric film of the balloon 8 is made of highly flexible material so that the film can be in close contact~with the surface of the wall of the tract where the lesion i5 located and that the film is made as thin as possible so that it may absorb less~energy of the microwaves emitted or transmitted from the an-tenna S, provided that the film has an elasticity sufficient to contain water therein under a certain 1ZI~9645 pressure. In the case of using a thin rubber film for the balloon 8, the film thickness is, for instance, less than 0.5 mm (energy loss of about 30 ~) and, preferably, less than 0.1 mm (energy loss of about 10 - 15 ~). Although the balloon 8 in the illustrated embodiment is shaped such that it is expandable through an oval or elliptic shape to a generally spheric shape, it may take any other configuration. For instance, the balloon 8 may be protruded longitudinally at the top end 19 and, in this case, the top end of the antenna 5 may he inserted into but not fix~d to the elongated recess of the top end 19. The film mat~ri~l Eor the balloon 8 is preferably rubbery polymeric mater.lal, Eor example, natural rubber or syn-thetic rubber such as silicone rubber. ~
In order to transmit the microwaves emitted fron the antenna S as eeectively as possible to the lesion, the coollng medium ~lowin~ the inside of the bal;loon 8, preferably, comprises liquid medlum at least mainly composed of water so that the emitted microwaves are transmitted therein substantially at the same wa~elength as in the lesion. Purlfied water wlth less transmission loss such as absorption is more preferred.
¦ The purlfied water as the coollng llquid~flowing lnside~
: :
of the balloon 8 is kept at an appropriate temperature of about~
O - 45C and,~`preferably, about lS - 42C so that the temperature at the lesion can be maintalned at 4Z - 45C by the purified~water in co-operation with the~antenna S. ~
Further, the flow rate of the cooling~water i9 ~:
: : ::
lZ09645 controlled by the throttling device 14. The throttling device 14 comprises a manually- or automatically-controlled valve, the opening degree of which can be adjusted continuously. The throttling device or valve 14 also serves to produce an adequate pressure within the balloon 8 so as to expand the balloon 8 into an intimate contact wlth the wall of the tràct or lumen organ.
In the illustrated embodiment, the drain tube 15 is constituted as a device main body which is to be inserted through the tract or lumen and through~which the coaxial cable 6 and the feed tube 11 are extended. Alternatively, the feed tube 11 may be modified to be constituted as the device main body while extending the drain tube 15 and the coaxial cable 6 inside of the Eeed tube 11. In -this modified embodlment, the ~ase portion o the balloon 8 is secured to the end of the water-eed tube 11. Furthermore, the feed~tube 11, the drain tube 15 and the coaxial cable 6 may be bundled in close contact together at their respective outer~circumferential surfaces so that the three members form an elongated antenna device main body as a whole, with the balloon 8 belng capped over the open ends of the tubes 11, 15 so as to surround the antenna 5, in the case where the assembly can be formed so smooth and thin as can be intaken, for examplet from the mouth Lnto the stomach ~ ~
The puriied water may be used recyclically by ~ ;
connecting the drain tube 15 to the pump 10 by way of a reservolr not shown. Reference numera~l 20 in the drawing denotes sealed~
portions to prevent the leak of the water.
: ~
:
~2~g64S
A thermosens~r or temperature detector 21 is fixed to the outer surface of the central por-tion of the circumferential wall of the balloon 8 to detect the temperature at the film or membrane surface of the balloon 8, that is, the temperature at the inner surface of the wall of the tract organ. The thermosensor 21 may be a thermocouple or thermistor. The lead 22 for the thermosensor 21 is disposed along the outer surf~ce of the drain tube 15 constituting the device main body in~the illustrated embodiment, it may, however, be passed through the inside of the drain tube 15 as the device main body if desired. The average output ~rom the oscillator 3 and the temperature o~ the coollng wat~r ~ecl to the balloon 8 are controlled dependin~ on the outp~t signal from the thermosensor 21, that is, on the temperature detected by the sensor 21 so that -the temperature of the lesion may be kept a-t about 42 - 45C. The temperature control may be carried out automatically by a suitable control means.
In the endotract antenna device for hyperthermia l constituted as described above, since the microwave radiation antenna 5 is disposed to the inside of the balloon 8 through which the cooling liquid passes, the balloon 8 can be deformed just correspondlng to the uneven inner profile of the wall of the tract organ and put to an lntlmate fittlng~with the inner surface of the wall, that is, the surface~of the lesion by the control of the flow rate and/or the pressure of the cooling liquid flowi~ng inside of the balloon 8~ whereby~the microwave emitted from the antenna 5 can be transmitted with little transmlssion loss to the .
lZ09~i45 lesion through the purified water in the chamber 7 and the thin film of the balloon 8. Furthermore, control for the -temperature and the flow rate of the cooling water 10wing inside of the balloon 8 can ensure the hypothermia therapy while preventing or avoiding localized over-heating and maintaining the temperature of the wide lesion area at a temperature of between 42 - 45C.
As described above, according to this invention, since the endotract antenna device for hyperthermia comprise~
a microwave radiation antenna, a balloon-like member made of a polymeric thin film and surrounding the antenna, and means for .Eeeding and draining a cooling liquid to and from the inside Qf the balloon-member, the energy o~ the microwa~es emitted Erom I.
th~ antenna can be efEectively given to the lesion in the tract or lumen organ, thereby enabling to warm tle lesion effectively.
~ ~ I
~ ~:
Claims (20)
1. An endotract antenna device for hyperthermia comprising an antenna for radiating microwave, a balloon-like member made of a polymeric thin film and surrounding said antenna, and means for feeding and draining a cooling liquid to and from an inside of said balloon-like member.
2. The antenna device as defined in claim 1, in which said radiation antenna comprises a generally linear dipole antenna.
3. The antenna device as defined in claim 2, in which the dipole antenna comprises a pair of conductors each having a same configuration.
4. The antenna device as defined in claim 2, in which the dipole antenna comprises a pair of conductors, one of the paired conductors being a central conductor of a coaxial cable.
5. The antenna device as defined in claim 1, in which said radiation antenna is connected by way of a coaxial cable to a microwave oscillator.
6. The antenna device as defined in claim 1, in which said radiation antenna is fixed at a top end thereof with a central portion of a top end of said balloon-like member.
7. The antenna device as defined in claim 1, in which the thin polymeric film of said balloon-like member is flexible and elastic.
8. The antenna device as defined in claim 1, in which the thin polymeric film is made of rubber.
9. The antenna device as defined in claim 8, in which the rubber is synthetic rubber.
10. The antenna device as defined in claim 8, in which the rubber is natural rubber.
11. The antenna device as defined in claim 1, in which said feeding and draining means comprises a feeding tube communicated at one end thereof with said balloon-like member so as to feed the cooling liquid to the inside of said balloon-like member and a draining tube communicated at one end thereof with said balloon-like member so as to drain the cooling liquid from said balloon-like member.
12. The antenna device as defined in claim 11, in which said feeding and draining means further comprises a pump connected to an other end of the feeding tube so as to supply the cooling liquid by way of the feeding tube to the inside of said balloon-like member.
13. The antenna device as defined in claim 12, in which said feeding and draining means further comprises a throttling means for controlling a flow rate or a pressure of the cooling liquid flowing the inside of said balloon-like member.
14. The antenna device as defined in claim 13, in which the throttling means is disposed at an other end of the draining tube.
15. The antenna device as defined in claim 14, in which said balloon-like member is capped liquid-tightly over the one end of the draining tube, the feeding tube is inserted in the draining tube at a side of the one end of the draining tube, and a transmission line for connecting a microwave oscillator with said radiation antenna is inserted in the draining tube.
16. The antenna device as defined in claim 14, in which said balloon-like member is capped liquid-tightly over the one end of the. feeding tube, the draining tube is inserted in the feeding tube at a side of the one end of the feeding tube, and a transmission line for connecting a microwave oscillator with said radiation antenna is inserted in the feeding tube.
17. The antenna device as defined in claim 11, in which said feeding and draining means comprises means for controlling a temperature of the cooling liquid to be supplied by way of the feeding tube to said balloon-like member.
18. The antenna device as defined in claim 1, in which the cooling liquid is water.
19. The antenna device as defined in claim 18, in which the water is purified water.
20. The antenna device as defined in claim 1, in which a thermosensor is disposed on a surface of said balloon-like member.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57167978A JPS5957650A (en) | 1982-09-27 | 1982-09-27 | Probe for heating body cavity |
| JP167978/82 | 1982-09-27 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1209645A true CA1209645A (en) | 1986-08-12 |
Family
ID=15859538
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000437376A Expired CA1209645A (en) | 1982-09-27 | 1983-09-22 | Endotract antenna device for hyperthermia |
Country Status (3)
| Country | Link |
|---|---|
| US (1) | US4662383A (en) |
| JP (1) | JPS5957650A (en) |
| CA (1) | CA1209645A (en) |
Families Citing this family (203)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6055966A (en) * | 1983-09-05 | 1985-04-01 | オリンパス光学工業株式会社 | Medical electrode apparatus |
| US4800899A (en) * | 1984-10-22 | 1989-01-31 | Microthermia Technology, Inc. | Apparatus for destroying cells in tumors and the like |
| US5019075A (en) * | 1984-10-24 | 1991-05-28 | The Beth Israel Hospital | Method and apparatus for angioplasty |
| US5226430A (en) * | 1984-10-24 | 1993-07-13 | The Beth Israel Hospital | Method for angioplasty |
| US4700716A (en) * | 1986-02-27 | 1987-10-20 | Kasevich Associates, Inc. | Collinear antenna array applicator |
| JPS6323676A (en) * | 1986-07-17 | 1988-01-30 | オリンパス光学工業株式会社 | High frequency heating method and apparatus |
| JPH0511882Y2 (en) * | 1987-01-06 | 1993-03-25 | ||
| US4819655A (en) * | 1987-08-04 | 1989-04-11 | Webler William E | Injectateless thermal cardiac output determination method and apparatus |
| US5097845A (en) * | 1987-10-15 | 1992-03-24 | Labthermics Technologies | Microwave hyperthermia probe |
| DE3743578A1 (en) * | 1987-12-22 | 1989-07-13 | Andreas Dr Zeiher | BALLOON CATHETER FOR RECANALIZING STENOSES IN BODY CHANNELS, IN PARTICULAR CORONARY VESSELS AND PERIPHERAL ARTERIAL VESSELS |
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| US11672596B2 (en) | 2018-02-26 | 2023-06-13 | Neuwave Medical, Inc. | Energy delivery devices with flexible and adjustable tips |
| US11832879B2 (en) | 2019-03-08 | 2023-12-05 | Neuwave Medical, Inc. | Systems and methods for energy delivery |
| WO2021050767A1 (en) | 2019-09-12 | 2021-03-18 | Relievant Medsystems, Inc. | Systems and methods for tissue modulation |
Family Cites Families (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3125096A (en) * | 1964-03-17 | Compressor | ||
| US3837347A (en) * | 1972-04-20 | 1974-09-24 | Electro Catheter Corp | Inflatable balloon-type pacing probe |
| DE2407559C3 (en) * | 1974-02-16 | 1982-01-21 | Dornier System Gmbh, 7990 Friedrichshafen | Heat probe |
| US4140130A (en) * | 1977-05-31 | 1979-02-20 | Storm Iii Frederick K | Electrode structure for radio frequency localized heating of tumor bearing tissue |
| US4375220A (en) * | 1980-05-09 | 1983-03-01 | Matvias Fredrick M | Microwave applicator with cooling mechanism for intracavitary treatment of cancer |
| WO1981003616A1 (en) * | 1980-06-17 | 1981-12-24 | T Sandhu | Microwave antenna system for intracavitary insertion |
| US4469103A (en) * | 1982-03-03 | 1984-09-04 | Barrett Harold F | Method of treating conditions such as tumors in living bodies |
-
1982
- 1982-09-27 JP JP57167978A patent/JPS5957650A/en active Pending
-
1983
- 1983-09-22 CA CA000437376A patent/CA1209645A/en not_active Expired
- 1983-09-23 US US06/535,291 patent/US4662383A/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| JPS5957650A (en) | 1984-04-03 |
| US4662383A (en) | 1987-05-05 |
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| MKEX | Expiry |