WO1993009845A1 - Procede et systeme d'hyperthermie par micro-onde - Google Patents

Procede et systeme d'hyperthermie par micro-onde Download PDF

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Publication number
WO1993009845A1
WO1993009845A1 PCT/US1992/009927 US9209927W WO9309845A1 WO 1993009845 A1 WO1993009845 A1 WO 1993009845A1 US 9209927 W US9209927 W US 9209927W WO 9309845 A1 WO9309845 A1 WO 9309845A1
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WO
WIPO (PCT)
Prior art keywords
antenna
catheter
antennas
electrical current
set forth
Prior art date
Application number
PCT/US1992/009927
Other languages
English (en)
Inventor
B. Stuart Trembly
John A. Heaney
Evan B. Douple
Mark Yeh
P. Jack Hoopes
Original Assignee
Trustees Of Dartmouth College
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Trustees Of Dartmouth College filed Critical Trustees Of Dartmouth College
Publication of WO1993009845A1 publication Critical patent/WO1993009845A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/02—Radiation therapy 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
    • 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

Definitions

  • the invention relates generally to the field of non-surgical equipment and treatment techniques and, in particular, to such equipment and techniques used for hyperthermia treatment of the prostate.
  • the invention provides an improved energy-radiating system and method for intracavity use to heat body tissue selectively.
  • Prostatic disease malignant or benign
  • BPH benign prostatic hyperplasia
  • the treatment of choice for symptomatic BPH is surgery. That many patients suffering from BPH are elderly and may not be candidates for surgery, however, suggests that non-surgical alternatives for therapy warrant consideration.
  • Non-surgical treatments for BPH include medications such as alpha-adrenergic antagonists, 5- ⁇ reductase blockers, and hormones as well as mechanical dilatation.
  • hyperthermia has been suggested as a possible treatment for BPH. Although the precise mechanism by which hyperthermia causes cell death is not fully understood, heat is known to disrupt both the cellular membrane and nuclear function. Although the biological rationale for non-surgically treating malignant tumors with hyperthermia is not well established, clinical evidence has recently begun to suggest that hyperthermia may also be useful in the management of symptomatic BPH.
  • the anatomical location of the prostate permits various non-surgical approaches to be used for treating prostatic disease with hyperthermia. That is, intracavity approaches to the prostate are possible through both the rectum and the urethra.
  • Transrectal approaches for treating prostatic cancers have the advantage that the rectum can accommodate a relatively large instrument which in turn can heat a relatively large volume of tissue.
  • Other advantages to approaching the prostate through the rectum are that most prostatic cancers lie in the posterior portion of the prostate and are therefore accessible transrectally.
  • transrectal instruments feature water cooling to prevent damage to the rectal mucosa.
  • Water-cooled transrectal instruments deliver a maximum temperature several millimeters beneath the rectal mucosa and in the posterior prostate.
  • transurethral approaches also have significant advantages for treating BPH.
  • transurethral microwave instruments can deliver maximum temperature periurethrally and can concentrate the hyperthermia at a symptomatic lesion.
  • transurethral instruments can be easily localized within the prostate using a balloon catheter and/or imaging techniques.
  • Another problem is that by utilizing a single heat source deployed either transrectally or transurethrally, energy absorption is concentrated adjacent the so-deployed heat source.
  • the known techniques do not concentrate energy absorption selectively in the prostate center.
  • the performance of known radiating instruments is a function of insertion depth.
  • the antenna is to have antenna sections that are generally equal in length and that correspond to a quarter wavelength in the composite tissue/catheter medium. In typical practice, however, the length of one antenna section is dependent upon the depth to which the antenna is inserted into the patient. This insertion depth is determined by the clinical situation.
  • an object of the invention to provide a microwave hyperthermia system for intracavity use that creates a substantially uniform temperature distribution pattern. It is another object of the invention to provide such a system that delivers higher energy absorption rates than have been heretofore achievable,
  • Still another object of the invention is to provide a system of the above character and that exploits the benefits of both transrectal and transurethral hyperthermia treatment approaches.
  • the present invention features a system of hyperthermia apparatus for heating living tissue within an animal body.
  • the system includes first and second antennas that deposit electromagnetic energy within the animal body to heat the tissue.
  • the system includes first and second body passage catheters for deployment through first and second naturally occurring body passages, respectively.
  • the antennas are mounted one each on each of the catheters, and are connected by transmission lines for receiving electrical current from a source.
  • the electrical source provides alternating electrical current within a selected frequency range to each of the first and second antennas so that the antennas radiate heat-producing electromagnetic energy within the animal body. While alternating electrical current in the microwave range, i.e. one-hundred megahertz to ten gigahertz, is preferred, electrical current within other ranges, such as radio frequency, might be desirable in various situations.
  • the invention further includes phasing hardware for controlling the phase of the electrical current provided to one of the antennas relative to the phase of the electrical current provided to the other of the antennas. Accordingly, the antennas cooperate to focus selectively a localized maximum heating by the electromagnetic energy and thereby attain a selectively configured local maximum specific absorption rate in the tissue.
  • the invention provides at least two significant benefits.
  • the point of maximum specific absorption rate can be focussed in the tissue at one point for depositing maximum energy at that point. Also, however, the point of maximum specific absorption rate can be continually moved throughout the tissue to provide specific absorption rate in that is more uniformly distributed overall.
  • the system features a third antenna mounted for deployment within a naturally occurring body passage and connected to a transmission line for receiving electrical current from the electrical source.
  • the third antenna can be carried either by a third body-passage catheter or by one of the catheters used for carrying the first or second antennas.
  • the third antenna enables even higher electromagnetic absorption rates at the selected body location and with even more uniform distributions.
  • the invention features structure for cooling the space within the catheters and exterior to the antennas. This enables the system to effectively provide high heat levels to the living tissue while avoiding the problems associated with ohmic heating at the surfaces of the antennas and transmission lines.
  • this aspect of the invention features structure for flowing air through the catheter space exterior to the antennas. The air may be at ambient temperature or pre-cooled.
  • At least one antenna is disposed eccentrically within the mounting catheter. This results in the antenna depositing electromagnetic energy preferentially from one side of the catheter.
  • Still another embodiment of the invention features at least one antenna having an electrical choke at a frequency within the operating range of the antenna.
  • the choke may be formed by the antenna itself or may comprise separate components. The choke enables the antenna to deposit electromagnetic energy substantially independently of the depth to which the antenna is inserted within the animal body beyond the full insertion of the antenna.
  • the invention features a method for the spatially-controlled heating of living tissue within an animal body.
  • a first antenna mounted on a first catheter is deployed through a naturally occurring body passage to position the antenna near the tissue to be heated.
  • the antenna is connected to a first transmission line for feeding electrical current from a source to the antenna.
  • a second antenna mounted on a second catheter is deployed through another naturally occurring body passage to position the second antenna near the tissue to be heated.
  • the second antenna is also connected to a transmission line for feeding electrical current from a source to the second antenna.
  • the first and second antennas are excited with alternating electrical current within a selected frequency range so that each of the antennas deposits heat producing electromagnetic energy within the animal body.
  • the phase of the alternating electrical current provided to one of the antennas is controlled relative to the phase of the alternating electrical current provided to the other of the antennas, for focusing selectively a localized maximum heating by the composite electromagnetic energy deposit by the two antennas, together. In this manner, a local maximum specific absorption rate of electromagnetic energy in the tissue is attained.
  • FIGURE 1 is a schematic depiction of a system of hyperthermia apparatus constructed in accordance with the present invention
  • FIGURE 2 is a schematic plan view of an applicator suitable for use in connection with the system shown in FIGURE 1;
  • FIGURE 3 is a cross-section view taken along line 3-3 of FIGURE 2;
  • FIGURE 3A is a cross-section view of another embodiment of the applicator shown in FIGURE 3.
  • FIGURE 4 is a schematic depiction of another embodiment of a system of hyperthermia apparatus constructed in accordance with the present invention.
  • the invention features a microwave hyperthermia system 10 including at least two intracavity applicators A and B for deployment within an animal body, such as a human, and typically by way of common or separate body cavities or passages, for depositing heat-producing electromagnetic energy into the body.
  • the system is powered by a high-frequency power source 12.
  • a power splitter 14 is provided for dividing the alternating current from the power source 12.
  • the source current flows along transmission line paths 16A and 16B after being split by the power splitter 14.
  • Current flowing along path 16A is provided directly to the intracavitary applicator A, for exciting the antenna of the applicator, as described in greater detail herein below, to deposit electromagnetic energy in the tissue for producing heat.
  • Current flowing along path 16B is phase shifted relative to the current flowing along path 16A, by a phase shifter 18
  • the phase shifter 18 may consist simply of an extra length of cable or other transmission line between the power splitter 14 and the applicator B. This will delay the phase of the alternating electric current provided to applicator B with respect to the phase of alternating electric current provided to applicator A. More typically, however, it is desired to control the phase shift. Accordingly, the illustrated phase shifter 18 provides a controllable phase shift, in response to a control signal it receives from a phase shift controller 20.
  • the microwave power source 12 is a Holaday Model HI-915 source.
  • the phase shifter 18 is provided by Anghel Labs of Fairfield, New Jersey.
  • An Omni Spectra 2089-4047-00 model power splitter can be used as the power splitter 14.
  • the source 12 and phase controller 20 can be interconnected, for example, to adjust the relative phase in conjunction with the source power level or frequency.
  • the illustrated source 12, power splitter 14, phase shifter 18 and phase controller 20 can be provided in a single controllable excitation unit 15.
  • FIGURE 2 A typical applicator suitable for use as either applicator A or B is shown in FIGURE 2, wherein an applicator 20 has antenna elements 22 and 24 mounted on a Foley-type catheter 26 and connected to a coaxial transmission feed line 28.
  • the catheter 26 is arranged within an outer sheath 27. While a Foley catheter is shown, other supporting envelopes suitable for deploying the feed-line 28 and antenna elements 22 and 24 within an animal body can be used.
  • the illustrated Foley catheter is suitable for transurethral deployment.
  • the illustrated feed-line 28 is of the coaxial type with an inner conductor 30 and an outer conductor 32.
  • the antenna of the illustrated applicator 20 is a form of dipole, with two radiating elements 22 and 24.
  • the antenna radiating elements 22 and 24 also are aligned with the coaxial transmission line 28.
  • the illustrated element 22 employs a tubular, e.g. cylindrical, choke conductor
  • the illustrated conductors 30, 32 and 23, therefore, have a substantially triaxial geometry.
  • the end of the choke conductor 23 distal from the source 12 (FIGURE 1) is connected to the transmission line outer conductor 32 through the wall of the catheter 26 on one side of an antenna gap 34. Accordingly, the catheter wall fills the radial gap between the transmission line conductor 32 and the antenna conductor 23.
  • the end of the conductor 23 proximal to the source, i.e. distal from the gap 34, has no connection to the transmission line and hence is terminated with an open circuit.
  • This construction of the antenna element 22 forms a choke that presents a selected impedance characteristic to the feed transmission line at the antenna gap 34.
  • the value of this impedance characteristic is a function of the outer diameter of the conductor 32, the inner diameter of the conductor 23, the dielectric constant of the catheter wall, the length of the conductor 23, and the frequency of operation.
  • the other antenna element 24 is a rod-like cylindrical conductive stub 25 that forms the other side of the antenna gap 34.
  • the feed line inner conductor 30 extends across the gap 34, beyond the outer conductor 32, and connects to the stub 25.
  • the outer diameter of the stub which typically is a hollow cylindrical conductor closed at the end thereof that forms the gap 34, preferably is the same as the outer dimension of the choke conductor 23.
  • the width of the antenna gap 34 is a small fraction of the wavelength of the source current.
  • the gap is large enough to ensure that there is no accidental contact between the antenna elements 22 and 24.
  • the gap 34 is between approximately one and two millimeters.
  • the preferred antenna elements 22 and 24 are equal in length to form a symmetrical dipole, and are located so as to radiate over a length of four to six centimeters.
  • the conductors 23 and 25 can be formed from fine wire braid.
  • a suitable wire product is manufactured by New England Electric Wire of Lisbon, New Hampshire.
  • a suitable coaxial transmission line 28 has been found to be RG-178 coaxial cable with the outer jacket removed.
  • the antenna elements 22 and 24 are configured to present an impedance to the transmission line 28 of approximately fifty ohms.
  • Other transmission lines known to those skilled in the art can also be used.
  • antenna elements 22 and 24 are configured to present an impedance that approximates the proper match for the selected transmission line. While coaxial cable is described and deemed preferable, persons skilled in the art may elect to employ other high frequency feed-lines.
  • the transmission line 28 passes through a drainage channel 36 in the Foley catheter 26. Connections to the antenna sections 22 and 24 are made through an exit hole made at the antenna gap 34 (FIGURE 2) . As stated, the antenna section 24 is electrically connected to the inner conductor 30 of the feed-line 28 and the antenna section 22 is electrically connected to the feed-line outer conductor 32.
  • the applicators A and B are deployed, for example, one each transrectally and transurethrally to position the antennas near a patient's prostate. With in-phase excitation of the two applicators, from the excitation unit 15, the pattern of specific absorption rate (SAR), measured in watts per kilogram, produced by the antennas is characteristically nonuniform.
  • SAR specific absorption rate
  • tissue-equivalent phantom material is a substance that absorbs electromagnetic energy in the same way living tissue does. It is familiar to those practiced in the art as a means of studying the energy deposition pattern of electromagnetic applicators.
  • phase controller can dictate what portion of, for example, the prostate will be heated without changing any other parameter of the system.
  • the structure of the antenna elements 22 and 24 be cooled during hyperthermia treatment. Since microwaves deposit power at a distance from the antenna element(s), it is possible to cool the antenna surface actively while still heating tissue located away from the antenna. Several advantage accrue from such a cooled system. For example, some hyperthermia treatments fail because the patient complains of pain at the sensitive point of insertion of the catheter. Accordingly, power must be reduced and the therapeutic benefits of the treatment lessened. Active cooling, can reduce the temperature developed at sensitive areas without reducing the amount of heat delivered to the tissue.
  • the applicator 20 also has an annular space 38 within the outer sheath 27 and exterior to the antenna surface.
  • the system 10 of FIGURE 1 includes, therefore, a coolant source 40, and flow meters 42A and 42B for establishing and monitoring a flow of coolant through the enclosed space 38.
  • a Cole-Parmer model DOA-104-AA coolant source is suitable for the coolant source 40, and a Fisher and Porter model 10AG130AA flow meter can be used for the flow meters 42A and 42B.
  • Antenna cooling can be established, therefore, by the coolant source 40 flowing coolant through flow lines 41A and 41B. From the flow lines 41A and 41B, coolant can flow out through channels 44 (FIGURE 3) and into the annular space 38. This flow path is represented in FIGURE 2 by arrows 45. The continued flow of coolant fluid in the direction of arrows 45 will cause the fluid to flow over the surfaces of the antenna elements 22 and 24 to effect the cooling thereof. Coolant is then exhausted along exhaust lines 43A and 43B (FIGURE 1) .
  • a temperature sensing device 46 such as a fibre-optic thermometry probe, is provided, for monitoring the temperature near the antenna.
  • the temperature sensing device 46 typically is connected to communicate with other components of the system, such as the coolant source 40, the power source 12 and/or the phasing controller 20, for feed back control.
  • the coolant source 40 the power source 12 and/or the phasing controller 20
  • the phasing controller 20 for feed back control.
  • various fluids are suitable for use as a coolant. For example, both pre-cooled and room temperature air work well. Water is also suitable.
  • Various other acceptable coolant fluids will be apparent to those skilled in the art.
  • FIGURE 3A shows an applicator 20' similar to the applicator 20 except that it employs a catheter 26', upon which antenna elements are mounted, that is disposed eccentrically within an outer sheath 27.
  • the antenna elements deposit heat preferentially from one side of the sheath 27. It has been found that shifting the catheter 26 from, for example, the left-most side of sheath 27 to the right-most side of sheath 27 causes a ten fold increase in power deposition on the right side of the applicator 20. This enables heat to be focussed at, for example, a particular location in a patient's prostate.
  • One embodiment of the method of the invention includes the steps of deploying two antennas, one each transrectally and transurethrally, near a patient's prostate.
  • antennas so deployed are positioned approximately between three and five centimeters apart.
  • the antennas are excited with alternating electrical current, typically within the microwave range, for example 915 MHz, so that they deposit electromagnetic energy in the patient's prostate.
  • the phase of the electrical current provided to one antenna is shifted with respect to the phase of the electrical current provided to the other antenna. This relative phase shift attains a local maximum specific absorption rate in the tissue by selectively focusing a localized maximum heating by the electro-magnetic energy. Additionally by moving the focus point of maximum SAR, a more uniform temperature distribution can be achieved than that achieved by by driving either single antenna or by driving the two antennas in phase.
  • FIGURE 4 shows another embodiment of the invention wherein a third applicator C is provided.
  • applicator C is utilized transrectally.
  • Applicator C can be driven either at the base frequency put out by power source 12 or at a phase-delayed frequency.
  • the phase-delayed frequency can be either that which drives applicator B or a second phase-delayed frequency.
  • Applicator C therefore, provides another degree of selectivity for controlling the local maximum specific absorption rate of electromagnetic energy in the tissue.
  • a third antenna can be mounted on either applicator A or B. That is, applicator A, for example, can be fitted with two antennas, typically spaced apart along the length of the supporting catheter and outer sheath structure.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Surgery (AREA)
  • Biomedical Technology (AREA)
  • Engineering & Computer Science (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Molecular Biology (AREA)
  • Physics & Mathematics (AREA)
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  • Otolaryngology (AREA)
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  • Pathology (AREA)
  • Radiology & Medical Imaging (AREA)
  • Radiation-Therapy Devices (AREA)

Abstract

Un système d'hyperthermie s'appliquant au tissu humain comprend un cathéter (43A) que l'on introduit dans un passage naturel du corps humain et sur lequel est montée une antenne. L'antenne est connectée à une ligne de transmission (16A) permettant d'alimenter l'antenne en courant électrique. Le système comprend également un autre ensemble cathéter (43B)/antenne/ligne de transmission (16B) similaire à celui décrit précédemment. Une source électrique (15) est connectée aux deux systèmes pour fournir un courant électrique alternatif dans une plage de fréquence de sorte que les antennes fournissent au tissu humain une énergie électromagnétique produisant de la chaleur. La phase de l'énergie électromagnétique est commandée (20) en fonction d'une antenne par rapport à l'autre afin de contrôler et localiser l'apport d'énergie électromagnétique en vue de maximaliser l'absorption par les tissus de cette énergie électromagnétique.
PCT/US1992/009927 1991-11-12 1992-11-10 Procede et systeme d'hyperthermie par micro-onde WO1993009845A1 (fr)

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US78999591A 1991-11-12 1991-11-12
US07/789,995 1991-11-12

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WO1993009845A1 true WO1993009845A1 (fr) 1993-05-27

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Cited By (24)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2720948A1 (fr) * 1994-06-10 1995-12-15 Sadis Bruker Spectrospin Appareil de traitement in situ par hyperthermie ou thermothérapie.
WO2000047283A3 (fr) * 1999-02-09 2000-12-14 Kai Tech Inc Systèmes à micro-ondes pour l'hyperthermie, la thermothérapie et le diagnostic en médecine
US6233490B1 (en) 1999-02-09 2001-05-15 Kai Technologies, Inc. Microwave antennas for medical hyperthermia, thermotherapy and diagnosis
EP1092452A3 (fr) * 1992-03-06 2001-08-01 Urologix, Inc. Antenne à dipôles pour micro-ondes utilisée en thermothérapie asymétrique
WO2001098764A3 (fr) * 2000-06-20 2002-05-16 Celsion Corp Systeme et procede de chauffage de la glande prostatique pour traiter ou prevenir la croissance et la propagation de tumeurs de la prostate
US6788977B2 (en) 2000-06-20 2004-09-07 Celsion Corporation System and method for heating the prostate gland to treat and prevent the growth and spread of prostate tumor
US6958075B2 (en) 2001-09-18 2005-10-25 Celsion Corporation Device and method for treatment of tissue adjacent a bodily conduit by thermocompression
WO2007112102A1 (fr) * 2006-03-24 2007-10-04 Micrablate Dipôle à alimentation centrale destiné à être utilisé avec des systèmes, des dispositifs, et des procédés d'ablation tissulaire
US7837720B2 (en) 2000-06-20 2010-11-23 Boston Scientific Corporation Apparatus for treatment of tissue adjacent a bodily conduit with a gene or drug-coated compression balloon
EP2407205A1 (fr) * 2010-07-16 2012-01-18 Vivant Medical, Inc. Ensemble d'antenne double avec commutation de phase contrôlée par l'utilisateur
US8224455B2 (en) 2002-02-15 2012-07-17 Boston Scientific Corporation Drug delivery
WO2013120224A1 (fr) * 2012-01-31 2013-08-22 Liu Zhongyi Instrument d'acupuncture micro-ondes multifréquence
US9119649B2 (en) 2009-07-28 2015-09-01 Neuwave Medical, Inc. Energy delivery systems and uses thereof
US9192438B2 (en) 2011-12-21 2015-11-24 Neuwave Medical, Inc. Energy delivery systems and uses thereof
US9861440B2 (en) 2010-05-03 2018-01-09 Neuwave Medical, Inc. Energy delivery systems and uses thereof
CN108938081A (zh) * 2018-08-01 2018-12-07 赛诺微医疗科技（浙江）有限公司 N通道微波消融系统
US10342614B2 (en) 2004-04-29 2019-07-09 Wisconsin Alumni Research Foundation Triaxial antenna for microwave tissue ablation
US10363092B2 (en) 2006-03-24 2019-07-30 Neuwave Medical, Inc. Transmission line with heat transfer ability
US10376314B2 (en) 2006-07-14 2019-08-13 Neuwave Medical, Inc. Energy delivery systems and uses thereof
US10531917B2 (en) 2016-04-15 2020-01-14 Neuwave Medical, Inc. Systems and methods for energy delivery
US10952792B2 (en) 2015-10-26 2021-03-23 Neuwave Medical, Inc. Energy delivery systems and uses thereof
US11389235B2 (en) 2006-07-14 2022-07-19 Neuwave Medical, Inc. Energy delivery systems and uses thereof
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

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Cited By (49)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1092452A3 (fr) * 1992-03-06 2001-08-01 Urologix, Inc. Antenne à dipôles pour micro-ondes utilisée en thermothérapie asymétrique
FR2720948A1 (fr) * 1994-06-10 1995-12-15 Sadis Bruker Spectrospin Appareil de traitement in situ par hyperthermie ou thermothérapie.
WO1995034345A1 (fr) * 1994-06-10 1995-12-21 Sadis Bruker Spectrospin Societe Anonyme De Diffusion De L'instrumentation Scientifique Bruker Spectrospin (Societe Anonyme A Directoire) Appareil de traitement in situ par hyperthermie ou thermotherapie
WO2000047283A3 (fr) * 1999-02-09 2000-12-14 Kai Tech Inc Systèmes à micro-ondes pour l'hyperthermie, la thermothérapie et le diagnostic en médecine
US6233490B1 (en) 1999-02-09 2001-05-15 Kai Technologies, Inc. Microwave antennas for medical hyperthermia, thermotherapy and diagnosis
EP1647305A2 (fr) * 2000-06-20 2006-04-19 Celsion Corporation Système de chauffage de la glande prostatique par micro-ondes
US6788977B2 (en) 2000-06-20 2004-09-07 Celsion Corporation System and method for heating the prostate gland to treat and prevent the growth and spread of prostate tumor
EP1647305A3 (fr) * 2000-06-20 2006-04-26 Celsion Corporation Système de chauffage de la glande prostatique par micro-ondes
US7837720B2 (en) 2000-06-20 2010-11-23 Boston Scientific Corporation Apparatus for treatment of tissue adjacent a bodily conduit with a gene or drug-coated compression balloon
EP2258445A1 (fr) * 2000-06-20 2010-12-08 Boston Scientific Corporation Système de chauffage de la glande prostatique utilisant des micro-ondes
WO2001098764A3 (fr) * 2000-06-20 2002-05-16 Celsion Corp Systeme et procede de chauffage de la glande prostatique pour traiter ou prevenir la croissance et la propagation de tumeurs de la prostate
US6958075B2 (en) 2001-09-18 2005-10-25 Celsion Corporation Device and method for treatment of tissue adjacent a bodily conduit by thermocompression
US7811313B2 (en) 2001-09-18 2010-10-12 Boston Scientific Corporation Device for treatment of tissue adjacent a bodily conduit by thermocompression
US8221413B2 (en) 2001-09-18 2012-07-17 Boston Scientific Corporation Device and method for treatment of tissue adjacent a bodily conduit by thermocompression
US8374702B2 (en) 2002-02-15 2013-02-12 Medifocus, Inc. Drug delivery
US8224455B2 (en) 2002-02-15 2012-07-17 Boston Scientific Corporation Drug delivery
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