US20070203551A1 - Radiation applicator and method of radiating tissue - Google Patents
Radiation applicator and method of radiating tissue Download PDFInfo
- Publication number
- US20070203551A1 US20070203551A1 US11/646,141 US64614106A US2007203551A1 US 20070203551 A1 US20070203551 A1 US 20070203551A1 US 64614106 A US64614106 A US 64614106A US 2007203551 A1 US2007203551 A1 US 2007203551A1
- Authority
- US
- United States
- Prior art keywords
- ferrule
- applicator
- sleeve
- microwave applicator
- tip
- 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.)
- Abandoned
Links
Images
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
- 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
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
-
- 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
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T7/00—Image analysis
- G06T7/30—Determination of transform parameters for the alignment of images, i.e. image registration
-
- 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
- A61B2018/00023—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids closed, i.e. without wound contact by the fluid
-
- 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
- A61B2018/00029—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids open
-
- 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
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00059—Material properties
- A61B2018/00071—Electrical conductivity
- A61B2018/00077—Electrical conductivity high, i.e. electrically conducting
-
- 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
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00059—Material properties
- A61B2018/00071—Electrical conductivity
- A61B2018/00083—Electrical conductivity low, i.e. electrically insulating
-
- 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
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00172—Connectors and adapters therefor
- A61B2018/00178—Electrical connectors
-
- 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
- A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
- A61B2018/00577—Ablation
-
- 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
- A61B2018/183—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 characterised by the type of antenna
- A61B2018/1838—Dipole antennas
-
- 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
- A61B2018/1869—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 with an instrument interstitially inserted into the body, e.g. needles
-
- 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
- A61B2018/1892—Details of electrical isolations of the antenna
-
- 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
- A61N5/04—Radiators for near-field treatment
- A61N5/045—Radiators for near-field treatment specially adapted for treatment inside the body
Definitions
- the present invention relates generally to medical technology, and more specifically to microwave radiation applicators and methods of thermal ablative treatment of tissue using radiated microwaves.
- Thermal ablative therapies may be defined as techniques that intentionally decrease body tissue temperature (hypothermia) or intentionally increase body tissue temperature (hyperthermia) to temperatures required for cytotoxic effect, or to other therapeutic temperatures depending on the particular treatment.
- Microwave thermal ablation relies on the fact that microwaves form part of the electromagnetic spectrum causing heating due to the interaction between water molecules and the microwave radiation. The heat being used as the cytotoxic mechanism.
- Treatment typically involves the introduction of an applicator into tissue, such as tumors. Microwaves are released from the applicator forming a field around its tip. Heating of the water molecules occurs in the radiated microwave field produced around the applicator, rather than by conduction from the probe itself. Heating is therefore not reliant on conduction through tissues, and cytotoxic temperature levels are reached rapidly.
- Microwave thermal ablative techniques are useful in the treatment of tumors of the liver, brain, lung, bones, etc.
- U.S. Pat. No. 4,494,539 discloses a surgical operation method using micro-waves, characterized in that microwaves are radiated to tissue from a monopole type electrode attached to the tip of a coaxial cable for transmitting microwaves. Coagulation, hemostasis or transaction is then performed on the tissue through the use of the thermal energy generated from the reaction of the microwaves on the tissue. In this way, the tissue can be operated in an easy, safe and bloodless manner. Therefore, the method can be utilized for an operation on a parenchymatous organ having a great blood content or for coagulation or transaction on a parenchymatous tumor. According to the method, there can be performed an operation on liver cancer, which has been conventionally regarded as very difficult.
- a microwave radiation applicator is also disclosed.
- U.S. Pat. No. 6,325,796 discloses a microwave ablation assembly and method, including a relatively thin, elongated probe having a proximal access end, and an opposite distal penetration end adapted to penetrate into tissue.
- the probe defines an insert passage extending therethrough from the access end to the penetration end thereof.
- An ablation catheter includes a coaxial transmission line with an antenna device coupled to a distal end of the transmission line for generating an electric field sufficiently strong enough to cause tissue ablation.
- the coaxial transmission line includes an inner conductor and an outer conductor separated by a dielectric material. A proximal end of the transmission line is coupled to a microwave energy source.
- the antenna device and the transmission line each have a transverse cross-sectional dimension adapted for sliding receipt through the insert passage while the elongated probe is positioned in the tissue. Such sliding advancement continues until the antenna device is moved to a position beyond the penetration end and further into direct contact with the tissue.
- a drawback with the existing techniques include the fact that they are not optimally mechanically configured for insertion into, and perforation of, the human skin, for delivery to a zone of soft tissue to be treated.
- known radiation applicator systems do not have the heightened physical rigidity that is desirable when employing such techniques.
- some radiation applicators made available heretofore do not have radiation emitting elements for creating a microwave field pattern optimized for the treatment of soft tissue tumors.
- the present invention is directed to a microwave applicator for ablating tissue.
- the applicator is a dipole microwave antenna that transmits microwave radiation into the tissue being treated.
- the applicator is formed from a thin coaxial cable having an inner conductor surrounded by an insulator, which is surrounded by an outer conductor or shield. The end of the coaxial cable is trimmed so that a portion of the insulator and inner conductor extend beyond the outer conductor, and a portion of the inner conductor extends beyond the insulator.
- the applicator further includes a tubular ferrule defining an aperture therethrough.
- One end of the ferrule is attached to the outer conductor, while the other end, which forms a sleeve, extends out beyond the end of the insulator and around a portion of the extended inner conductor.
- a step is preferably formed on the outer surface of the ferrule between its two ends.
- a solid spacer having a central bore to receive the inner conductor abuts an end of the ferrule and surrounds the extended inner conductor.
- a tuning element is attached to the end of the extended inner conductor, and abuts an end of the spacer opposite the ferrule. The tuning element faces the step in the ferrule, and the step and the tuning element are both sized and shaped to cooperate in balancing and tuning the applicator.
- a hollow tip formed from a dielectric material, has an open end and a closed end.
- the tip encloses the tuning element, the spacer, and the extended inner conductor.
- the tip also encloses the sleeve of the ferrule, thus defining outer surface of the ferrule that is surrounded by the dielectric tip.
- the open end of the tip preferably abuts the step in the ferrule.
- a rigid sleeve surrounds the coaxial cable and extends away from the ferrule opposite the tip.
- the sleeve, which abuts the step of the ferrule opposite the tip has an inner diameter that is larger than the coaxial cable, thereby defining an annular space between the outside of the coaxial cable and the inner surface of the sleeve.
- the sleeve further includes one or more drainage holes, which permit fluid communication between the annular space around the coaxial cable and the outside of the applicator.
- microwave energy from a source is applied to the coaxial cable, and is conveyed to the tip.
- the portion of the inner conductor that extends beyond the end of the ferrule forms one arm of the dipole, and emits microwave radiation.
- the microwave energy flowing along the inner conductor of the coaxial cable and in the aperture of the ferrule induces a current to flow along the outer surface of the sleeve of the ferrule that is surrounded by the tip.
- This causes microwave radiation to be emitted from the sleeve of the ferrule, which operates as the second arm of the dipole.
- microwave energy is emitted along a substantial length of the applicator, rather than being focused solely from the tip.
- a cooling fluid is introduced from a source into the annular space defined by the outside of the coaxial cable and the inside of the sleeve.
- the cooling fluid flows along this annular space, and absorbs heat from the coaxial cable.
- the cooling fluid after having absorbed heat from the coaxial cable, then exits the annular space through the one or more drainage holes in the sleeve, and perfuses adjacent tissue.
- the closed end of the tip is preferably formed into a blade or point so that the microwave applicator may be inserted directly into the tissue being treated.
- the tip, ferrule, and rigid sleeve moreover, provide strength and stiffness to the applicator, thereby facilitating its insertion into tissue.
- the present invention further provides a method of treating target tissue, such as a tumor, the tumor being formed of, and/or being embedded within, soft tissue.
- the method includes inserting the microwave applicator into the tumor, and supplying electromagnetic energy to the applicator, thereby radiating electromagnetic energy into the tumor.
- FIG. 1 is a schematic, partial cross-sectional view of a radiation applicator in accordance with one embodiment of the invention
- FIG. 2A shows an axial cross-section
- FIG. 2B shows an end elevation of the radiating tip of the radiation applicator of FIG. 1 ;
- FIG. 3 shows a partial transverse cross-section of the tube of the radiation applicator of FIG. 1 ;
- FIG. 4A shows a transverse cross-section
- FIG. 4B shows an axial cross-section of the tuning washer of the radiation applicator of FIG. 1 ;
- FIG. 5A shows an axial cross-section
- FIG. 5B shows an end elevation of the ferrule of the radiation applicator of FIG. 1 ;
- FIG. 6A shows an axial cross-section
- FIG. 6B shows a transverse cross-section of a handle section that may be attached to the radiation applicator of FIG. 1 ;
- FIG. 7 illustrates the portion of coaxial cable that passes through the tube of the radiation applicator of FIG. 1 ;
- FIG. 8 is a plot of SI I against frequency for the radiation applicator of FIG. 1 ;
- FIG. 9A illustrates the E-field distribution
- FIG. 9B illustrates the SAR values around the radiation applicator of FIG. 1 , in use;
- FIGS. 10 A-E show a preferred sequential assembly of the radiation applicator of FIG. 1 ;
- FIG. 11 schematically illustrates a treatment system employing the radiation applicator of FIG. 1 ;
- FIG. 12 is an exploded, perspective view of another embodiment of the present invention.
- FIGS. 13-18 show a preferred sequential assembly of the radiation applicator of FIG. 12 ;
- FIG. 19 is a schematic, partial cross-sectional view of the radiation applicator of FIG. 12 .
- FIG. 1 is a schematic, partial cross-sectional view of a radiation applicator in accordance with one embodiment of the invention.
- the radiation applicator generally designated 102 , includes a distal end portion of a coaxial cable 104 that is used to couple to a source (not shown) of microwaves, a copper ferrule 106 , a tuning washer 108 attached on the end 110 of the insulator part of the coaxial cable 104 , and a tip 112 .
- the applicator 102 further includes a metal tube 114 . Tube 114 is rigidly attached to the ferrule 106 .
- An annular space 116 is defined between the outer conductor 118 of the cable 104 and the inner surface of the tube 114 , enabling cooling fluid to enter (in the direction of arrows A), contact the heated parts of the applicator 102 and exit in the direction of arrows B through radial holes 120 in the tube 114 , thereby extracting heat energy from the radiation applicator 102 .
- the washer 108 is soldered to a small length 122 of the central conductor 124 of the cable 104 that extends beyond the end 110 of the insulator 126 of the cable 104 .
- the ferrule 106 is soldered to a small cylindrical section 15 128 of the outer conductor 118 of the cable 104 .
- the tube 114 which is preferably stainless steel, but may be made of other suitable materials, such as titanium or any other medical grade material, is glued to the ferrule 106 by means of an adhesive, such as Loctite 638 retaining compound, at the contacting surfaces thereof, indicated at 130 and 132 .
- the tip 112 is also glued preferably, using the same adhesive, on the inner surfaces thereof, to corresponding outer surfaces of the ferrule 106 and the insulation 126 .
- the applicator 102 When assembled, the applicator 102 forms a unitary device that is rigid and stable along its length, which may be of the order of 250 or so millimeters including tube 114 , thereby making the applicator 102 suitable for insertion into various types of soft tissue.
- the space 116 and holes 120 enable cooling fluid to extract heat from the applicator 102 through contact with the ferrule 106 , the outer conductor 118 of the cable 104 and the end of the tube 114 .
- the ferrule 106 assists, among other things, in assuring the applicator's rigidity.
- the exposed end section 134 of cable 104 from which the outer conductor 118 has been removed, in conjunction with the dielectric tip 112 are fed by a source of radiation of predetermined frequency.
- the exposed end section 134 and dielectric tip 112 operate as a radiating antenna for radiating microwaves into tissue for therapeutic treatment.
- the applicator 102 operates as a dipole antenna, rather than a monopole device, resulting in an emitted radiation pattern that is highly beneficial for the treatment of certain tissues, such as malignant or tumorous tissue, due to its distributed, spherical directly heated area.
- FIG. 2A shows an axial cross-section
- FIG. 2B shows an end elevation of the tip 112 of the radiation applicator 102 of FIG. 1
- the tip 112 has inner cylindrical walls 202 , 204 , and abutting walls 206 , 208 , for receiving and abutting the washer 108 and the ferrule 106 , respectively, during assembly.
- the tip 112 is made of zirconia ceramic alloy. More preferably, it is a partially stabilized zirconia (PSZ) having yttria as the stabilizing oxidizing agent. Even more preferably, the tip 112 is made of Technox 2000, which is a PSZ commercially available from Dynamic Ceramic Ltd.
- the transverse dimensions of the applicator 102 are relatively small.
- the diameter of applicator 102 is preferably less than or equal to about 2.4 mm.
- the tip 112 is designed to have dimensions, and be formed of the specified material, so as to perform effective tissue ablation at the operating microwave frequency, which in this case is preferably 2.45 Gigahertz (GHz).
- the applicator 102 of the present invention is thus well adapted for insertion into, and treatment of, cancerous and/or non-cancerous tissue of the liver, brain, lung, veins, bone, etc.
- the end 210 of the tip 112 is formed by conventional grinding techniques performed in the manufacture of the tip 112 .
- the end 210 may be formed as a fine point, such as a needle or pin, or it may be formed with an end blade, like a chisel, i.e. having a transverse dimension of elongation.
- the latter configuration has the benefit of being well suited to forcing the tip 112 into or through tissue, i.e. to perforate or puncture the surface of tissue, such as skin.
- the tip 112 is preferably coated with a non-stick layer such as silicone or paralene, to facilitate movement of the tip 112 relative to tissue.
- a non-stick layer such as silicone or paralene
- FIG. 3 shows a partial transverse cross-section of the tube 114 .
- the tube 114 is preferably made of stainless steel.
- the tube 114 is preferably made from 13 gauge thin wall 304 welded hard drawn (WHD) stainless steel.
- the tube 114 is also approximately 215 mm in length.
- two sets of radial holes 120 , 120 ′ are provided at 12 mm and 13 mm, respectively, from the end 302 of the tube 114 .
- These radial holes 120 , 120 ′ permit the exit of cooling fluid.
- two sets of holes are shown, one, three, four or more sets of holes may be provided, in variants of the illustrated embodiment.
- the holes 120 , 120 ′ are of 0.5 mm diameter, but it will be appreciated that this diameter may be quite different, e.g. anything in the range of approximately 0.1 to 0.6 mm, depending on the number of sets of holes and/or the number of holes per set, in order to provide an effective flow rate.
- the illustrated distance from the end 302 is 12 or 13 mm, in alternative embodiments, this distance may range from 3 mm to 50 mm from the end 302 , in order to control the length of track that requires cauterization.
- the tube 114 may be omitted.
- the treatment may comprise delivering the applicator to the treatment location, e.g., to the tumorous tissue, by suitable surgical or other techniques.
- the applicator may be left in place inside the tumor, the access wound closed, and a sterile connector left at the skull surface for subsequent connection to the microwave source for follow-up treatment at a later date.
- FIG. 4A shows a transverse cross-section
- FIG. 4B shows an axial cross-section of the tuning washer 108
- the washer 108 is preferably made of copper, although other metals may be used.
- the washer 108 has an inner cylindrical surface 402 enabling it to be soldered to the central conductor 124 of the cable 104 ( FIG. 1 ). Although the washer is small, its dimensions are critical.
- the washer 108 tunes the applicator 102 , which operates as a dipole radiator, i.e., radiating energy from two locations, so that more effective treatment, i.e., ablation, of tissue is effected.
- FIG. 5A shows an axial cross-section
- FIG. 5B shows an end elevation of the ferrule 106 .
- the ferrule 106 is preferably made of copper, and is preferably gold plated to protect against any corrosive effects of the cooling fluid.
- the ferrule 106 may be produced by conventional machining techniques, such as CNC machining.
- FIG. 6A shows an axial cross-section
- FIG. 6B shows a transverse cross-section at line B-B of a handle section 602 that may be attached to the tube 114 of the radiation applicator 102 .
- the handle section 602 is preferably made from the same material as the tube 114 , i.e., stainless steel.
- the handle section 602 includes a forward channel 604 enabling insertion of the tube 114 , and a rear channel 606 enabling insertion of the coaxial cable 104 during assembly.
- a transverse port 608 having an internal thread 610 enables the connection, through a connector, to a source of cooling fluid, discussed later.
- the connector may be formed from plastic.
- FIG. 7 illustrates the portion of coaxial cable 104 that passes through the tube 114 .
- the cable 104 suitably comprises a low-loss, coaxial cable such as SJS070LL-253-Strip cable.
- a connector 702 preferably a SMA female type connector permits connection of the cable 104 to a microwave source (not shown), or to an intermediate section of coaxial cable (not shown) that, in turn, connects to the microwave source.
- FIG. 8 is a plot of S 11 against frequency for the radiation applicator 102 of FIG. 1 . This illustrates the ratio of reflective microwave power from the interface of the applicator 102 and treated tissue to total input power to the applicator 102 . As can be seen, the design of the applicator 102 causes the reflected power to be a minimum, and therefore the transmitted power into the tissue to be a maximum, at a frequency of 2.45 GHz of the delivered microwaves.
- FIG. 9A shows the E-field distribution around the radiation applicator 102 of FIG. 1 , in use. Darker colors adjacent to the applicator 102 indicate points of higher electric field.
- the position of the washer 108 is indicated at 902
- the position of the tip-ferrule junction is indicated at 904 .
- Two limited, substantially cylindrical zones 906 , 908 , of highest electric field are formed around the applicator 102 at the positions 902 and 904 respectively.
- FIG. 9B shows the specific absorption rate (SAR) value distribution around the radiation applicator 102 of FIG. 1 , in use. Darker colors adjacent the applicator 102 indicate points of SAR.
- the position of the washer 108 is indicated at 902
- the position of the tip-ferrule junction is indicated at 904
- the position of the ferrule-tube junction is indicated at 905 .
- Two limited, substantially cylindrical zones 910 , 912 , of highest SAR are formed around the applicator 102 at the positions 902 and between 904 and 905 , respectively.
- FIGS. 10 A-E show a preferred sequential assembly of components forming the radiation applicator 102 of FIG. 1 .
- the coaxial cable 104 is shown with the outer conductor 118 and the inner insulator 126 trimmed back, as illustrated earlier in FIG. 7 .
- the tube 114 is then slid over the cable 104 .
- the ferrule 106 is slid over the cable 104 ( FIG. 10C ), and fixedly attached to the tube 114 and to the cable 104 , as described earlier.
- the washer 108 is attached to the inner conductor 124 by soldering, as shown in FIG. 10D .
- the tip 112 is slid over the cable 104 and part of the ferrule 106 , and affixed thereto, as described earlier.
- the completed applicator is shown in FIG. 10E . This results in a construction of great rigidity and mechanical stability.
- FIG. 11 schematically illustrates a treatment system 1102 employing the radiation applicator 102 of FIG. 1 .
- Microwave source 1104 is couple to the input connector 1106 on handle 602 by coaxial cable 1108 .
- the microwave power is supplied at up to 80 Watts. However this could be larger for larger size applicators, e.g., up to 200 Watts for 5 mm diameter radiation applicators.
- Syringe pump 1110 operates a syringe 1112 for supplying cooling fluid 1114 via conduit 1116 and connector 1118 attached to handle 602 , to the interior of the handle section 602 .
- the fluid is not at great pressure, but is pumped so as to provide a flow rate of about 1.5 to 2.0 milliliter(ml)/minute through the pipe 114 in the illustrated embodiment.
- higher flow rates may be employed, so as to provide appropriate cooling.
- the cooling fluid is preferably saline, although other liquids or gases may be used, such as ethanol.
- a cooling liquid having a secondary, e.g., cytotoxic, effect could be used, enhancing the tumor treatment.
- the cooling fluid 1114 exits the tube 114 , as shown by arrows B in FIG. 1 , at a temperature on the order of 10° C. higher than that at which it enters the tube 114 , as shown by arrows A in FIG. 1 .
- the cooling fluid 1114 may, for example, enter the tube 114 at room temperature.
- the cooling fluid 1114 may be pre-cooled to a temperature below room temperature by any suitable technique.
- the cooling system is an open, perfusing cooling system that cools the coaxial cable connected to the radiation applicator 102 . That is, after absorbing heat from the coaxial cable, the cooling fluid perfuses the tissue near the radiation applicator 102 .
- the methodology for use of the radiation applicator 102 of the present invention may be as conventionally employed in the treatment of various soft tissue tumors.
- the applicator 102 is inserted into the body, laparoscopically, percutaneously or surgically. It is then moved to the correct position by the user, assisted where necessary by positioning sensors and/or imaging tools, such as ultrasound, so that the tip 112 is embedded in the tissue to be treated.
- the microwave power is switched on, and the tissue is thus ablated for a predetermined period of time under the control of the user.
- the applicator 102 is stationary during treatment. However, in some instances, e.g., in the treatment veins, the applicator 102 may be moved, such as a gentle sliding motion relative to the target tissue, while the microwave radiation is being applied.
- radiation applicator 102 is a dipole antenna.
- the portion of the inner conductor 124 that extends beyond the ferrule 106 operates as one arm of the dipole antenna.
- the transmission of microwave energy along the inner conductor 124 and in the aperture of the ferrule induces a current to flow on that portion of the outer surface of the ferrule 106 that is located underneath the tip 112 .
- This induced current causes this enclosed, outer surface of the ferrule 106 to emit microwave radiation, thereby forming a second arm of the dipole antenna.
- the bipolar configuration of the applicator effectively spreads the microwave radiation that is being transmitted by the applicator 102 along a greater transverse, i.e., axial, length of the antenna 102 , rather than focusing the radiation transmission solely from the tip 112 of the applicator 102 .
- the applicator 102 of the present invention may be operated at much higher power levels, e.g., up to approximately 80 Watts, than prior art designs.
- FIG. 12 is an exploded, perspective view of an alternative radiation applicator 1202 .
- the applicator 1202 includes a coaxial cable 1204 having an outer conductor 1206 that surrounds an insulator 1208 that, in turn, surrounds an inner or central conductor 1210 .
- the applicator 1202 further includes a ferrule 1212 .
- the ferrule 1212 is generally tubular shaped so as to define an aperture therethrough, and has first and second ends is 1212 a, 1212 b.
- the ferrule 1212 also has three parts or sections.
- a first section 1214 of the ferrule 1212 has an inner diameter sized to fit over the outer conductor 1206 of the coaxial cable 1204 .
- a second section 1216 of the ferrule 1212 has an inner diameter that is sized to fit over the insulator 1208 of the coaxial cable 1204 .
- the second section 1216 thus defines an annular surface or flange (not shown) around the inside the ferrule 1212 .
- the outer diameter of the second section 1216 is preferably larger than the outer diameter of the first section 1214 , thereby defining a step or flange around the outside of the ferrule 1212 .
- a third section 1218 of the ferrule 1212 has an inner diameter also sized to fit around the insulator 1208 of the coaxial cable 1204 .
- the third section 1218 has an outside diameter that is less than the outside diameter of the second section 1216 .
- the third section 1218 thus defines an outer, cylindrical surface or sleeve.
- Applicator 1202 further includes a spacer 1220 .
- the spacer 1220 is preferably cylindrical in shape with a central bore 1222 sized to receive the inner conductor 1210 of the coaxial cable 1204 .
- the outer diameter of the spacer 1220 preferably matches the outer diameter of the third section 1218 of the ferrule 1212 .
- Applicator 1202 also includes a tuning element 1224 and a tip 1226 .
- the tuning element 1224 which be may be disk-shaped, has a central hole 1228 sized to fit around the inner conductor 1210 of the coaxial cable 1204 .
- the tip 1226 is a hollow, elongated member, having an open end 1230 , and a closed end 1232 .
- the closed end 1232 may be formed into a cutting element, such as a trocar point or a blade, to cut or pierce tissue.
- Applicator 1202 also includes a rigid sleeve 1234 .
- the sleeve 1234 has an inner diameter that is slightly larger than outer diameter of the coaxial cable 1204 . As described below, an annular space is thereby defined between the outer surface of the coaxial cable 1204 and the inner surface of the sleeve 1234 .
- the sleeve 1234 further includes one or more drainage holes 1236 that extend through the sleeve.
- FIGS. 13-18 illustrate a preferred assembly sequence of the applicator 1202 .
- the coaxial cable 1204 is trimmed so that there is a length “m” of insulator 1208 that extends beyond an end 1206 a of the outer conductor 1206 , and a length “I” of inner conductor 1210 that extends beyond an end 1208 a of the insulator 1208 .
- the ferrule 1212 slides over the exposed inner conductor 1210 and over the exposed insulator 1208 such that the first section 1214 surrounds the outer conductor 1206 , and the second and third sections 1216 , 1218 surround the exposed portion of the insulator 1208 .
- the inner surface or flange formed on the second section 1216 of the ferrule 1212 abuts the end 1206 a of the outer conductor 1206 , thereby stopping the ferrule 1212 from sliding any further up the coaxial cable 1204 .
- the ferrule 1212 is preferably fixedly attached to the coaxial cable 1204 , such as by soldering the ferrule 1212 to the outer conductor 1206 of the coaxial cable 1204 .
- the third section 1218 of the ferrule 1212 extends past the end 1208 a of the exposed insulator 1208 as shown by the dashed line in FIG. 14 .
- the spacer 1220 is slid over the exposed portion of the inner conductor 1210 , and is brought into contact with the second end 1212 b of the ferrule 1212 .
- the spacer 1220 is not fixedly attached to the ferrule 1212 or the inner conductor 1210 .
- the spacer 1220 is sized so that a small portion 1210 a ( FIG. 15 ) of the inner conductor 1210 remains exposed.
- the tuning element 1224 is then slid over this remaining exposed portion 1210 a of the inner conductor 1210 .
- the tuning element 1224 is preferably fixedly attached to the inner conductor 1210 , e.g., by soldering. The tuning element 1224 , in cooperation with the ferrule 1212 , thus hold the spacer 1220 in place.
- the next step is to install the tip 1226 as shown in FIG. 16 .
- the open end 1230 of the tip 1226 is slid over the tuning element 1224 , the spacer 1224 and the third section 1218 of the ferrule 1212 .
- the open end 1230 of the tip 1226 abuts the second section or step 1216 of the ferrule 1212 .
- the tip 1226 is preferably fixedly attached to the ferrule 1212 , e.g., by bonding.
- the next step is to install the sleeve 1234 ( FIG. 17 ).
- the sleeve 1234 is slid over the coaxial cable 1234 , and up over the first section 1214 of the ferrule 1212 .
- the sleeve 1234 abuts the step 1216 in the ferrule 1212 opposite the tip 1226 .
- applicator 1202 may be assembled in different ways or in different orders.
- the tip 1226 , second section 1216 of the ferrule 1212 , and sleeve 1234 all preferably have the same outer diameter, thereby giving the applicator 1202 a smooth outer surface.
- the sleeve 1234 is formed from stainless steel, and the ferrule 1212 is formed from gold-plated copper.
- the tip 1226 and the spacer 1220 are formed from dielectric materials.
- the tip 1226 and the spacer 1220 are formed from an itrium stabilized zirconia, such as the Technox brand of ceramic material commercially available from Dynamic Ceramic Ltd. of Stoke-on-Trent, Staffordshire, England, which has a dielectric constant of 25 .
- the tip 1226 may be further provided with a composite coating, such as a polyimide undercoat layer, for adhesion, and a paralyne overcoat layer, for its non-stick properties. Alternatively, silicone or some other suitable material could be used in place of paralyne.
- the composite coating may also be applied to the ferrule and at least part of the stainless steel sleeve, in addition to being applied to the tip.
- FIG. 19 is a schematic, partial cross-sectional view of the radiation applicator 1202 .
- the insulator 1208 extends partially through the inside of the ferrule 1212 .
- the end 1208 a of the insulator 1208 is disposed a predetermined distance back from the second end 1212 b of the ferrule 1212 .
- the inner conductor 1210 extends completely through and beyond the ferrule 1212 .
- the sleeve 1234 slides over and is bonded to the first section 1214 of the ferrule 1212 .
- the inside diameter of the sleeve 1234 is greater than the outside diameter of the coaxial cable 1204 , thereby defining an annular space 1238 between the outside of the coaxial cable 1204 and the inside of the sleeve 1234 .
- Cooling fluid such as saline
- the cooling fluid absorbs heat from the coaxial cable that feeds radiation to applicator 1202 .
- the cooling fluid is then discharged through holes 1236 in the sleeve 1234 , as shown by arrows B.
- the holes 1236 are placed far enough behind the closed end 1232 of the tip 1226 such that the discharged cooling fluid does not enter that portion of the tissue that is being heated by the radiation applicator 1202 . Instead, the discharged cooling fluid preferably perfuses tissue outside of this heated region. Depending on the tissue to be treated, a suitable distance between the closed end 1232 of the tip 1226 and the holes 1236 may be approximately 30 mm.
- a first end 1220 a of the spacer 1220 abuts the second end 1212 b of the ferrule 1212 , while a second end 1220 b of the spacer 1220 abuts the tuning element 1224 .
- a space designated generally 1240 , is defined within the ferrule 1212 between the end 1208 a of the insulator and the second end 1212 b of the ferrule.
- this space 1240 is filled with air.
- the space may be filled with other materials, such as a solid dielectric, or it may be evacuated to form a vacuum.
- the inside surface of the tip 1226 preferably conforms to the shape of the tuning element 1224 , the spacer 1220 , and the third section 1218 of the ferrule 1212 so that there are no gaps formed along the inside surface of the tip 1226 .
- operation of the radiation applicator 1202 causes a current to be induced on the outer surface of the third section 1218 of the ferrule 1212 , which is enclosed within the dielectric material of the tip 1226 .
- This induced current results in microwave energy being radiated from this surface of the ferrule 1212 , thereby forming one arm of the dipole.
- the section of the inner conductor 1210 that extends beyond the ferrule 1212 is the other arm of the dipole.
- Both the length of the inner conductor 1210 that extends beyond the ferrule 1212 , and the length of the third section 1218 of the ferrule 1212 , which together correspond to the two arms of the dipole, are chosen to be approximately 1 ⁇ 4 of the wavelength in the dielectric tip 1226 , which in the illustrative embodiment is approximately 6 mm. Nonetheless, those skilled in the art will understand that other factors, such as tissue permittivity, the action of the tuning element, etc., will affect the ultimate lengths of the dipole arms. For example, in the illustrative embodiment, the two arms are approximately 5 mm in length.
- the tuning element 1224 moreover, cooperates with the second section or step is 1216 of the ferrule to balance the radiation being emitted by the two arms of the dipole.
- the size and shape of the tuning element 1224 and the step 1216 are selected such that the coherent sum of the microwave power reflected back toward the cable at the aperture of the ferrule is minimized.
- Techniques for performing such design optimizations are well-known to those skilled in the relevant art.
- the radiation applicator 1202 is attached to a source of microwave radiation in a similar manner as described above in connection with the applicator 102 of FIG. 1 .
- the coaxial cable is also attached to a source of cooling fluid in a similar manner as described above.
- the present invention it is the dielectric tip, ferrule and stainless steel sleeve that cooperate to provide the necessary stiffness and mechanical strength for the applicator to be used in treatment procedures.
- the applicator does not rely on the coaxial cable for any of its strength. Indeed, a flexible coaxial cable, having little or no rigidity, could be used with the radiation applicator of the present invention.
Abstract
Description
- This application is a continuation-in-part (CIP) of application Ser. No. 10/577,414 filed Apr. 26, 2006, which in turn is a national stage application of International Application Serial Number PCT/EP2005/007103 filed Jul. 1, 2005.
- This application also claims priority to foreign patent application serial number GB0600018.6 filed Jan. 3, 2006.
- 1. Field of the Invention
- The present invention relates generally to medical technology, and more specifically to microwave radiation applicators and methods of thermal ablative treatment of tissue using radiated microwaves.
- 2. Background Information
- Thermal ablative therapies may be defined as techniques that intentionally decrease body tissue temperature (hypothermia) or intentionally increase body tissue temperature (hyperthermia) to temperatures required for cytotoxic effect, or to other therapeutic temperatures depending on the particular treatment. Microwave thermal ablation relies on the fact that microwaves form part of the electromagnetic spectrum causing heating due to the interaction between water molecules and the microwave radiation. The heat being used as the cytotoxic mechanism. Treatment typically involves the introduction of an applicator into tissue, such as tumors. Microwaves are released from the applicator forming a field around its tip. Heating of the water molecules occurs in the radiated microwave field produced around the applicator, rather than by conduction from the probe itself. Heating is therefore not reliant on conduction through tissues, and cytotoxic temperature levels are reached rapidly.
- Microwave thermal ablative techniques are useful in the treatment of tumors of the liver, brain, lung, bones, etc.
- U.S. Pat. No. 4,494,539 discloses a surgical operation method using micro-waves, characterized in that microwaves are radiated to tissue from a monopole type electrode attached to the tip of a coaxial cable for transmitting microwaves. Coagulation, hemostasis or transaction is then performed on the tissue through the use of the thermal energy generated from the reaction of the microwaves on the tissue. In this way, the tissue can be operated in an easy, safe and bloodless manner. Therefore, the method can be utilized for an operation on a parenchymatous organ having a great blood content or for coagulation or transaction on a parenchymatous tumor. According to the method, there can be performed an operation on liver cancer, which has been conventionally regarded as very difficult. A microwave radiation applicator is also disclosed.
- U.S. Pat. No. 6,325,796 discloses a microwave ablation assembly and method, including a relatively thin, elongated probe having a proximal access end, and an opposite distal penetration end adapted to penetrate into tissue. The probe defines an insert passage extending therethrough from the access end to the penetration end thereof. An ablation catheter includes a coaxial transmission line with an antenna device coupled to a distal end of the transmission line for generating an electric field sufficiently strong enough to cause tissue ablation. The coaxial transmission line includes an inner conductor and an outer conductor separated by a dielectric material. A proximal end of the transmission line is coupled to a microwave energy source. The antenna device and the transmission line each have a transverse cross-sectional dimension adapted for sliding receipt through the insert passage while the elongated probe is positioned in the tissue. Such sliding advancement continues until the antenna device is moved to a position beyond the penetration end and further into direct contact with the tissue. However, a drawback with the existing techniques include the fact that they are not optimally mechanically configured for insertion into, and perforation of, the human skin, for delivery to a zone of soft tissue to be treated. Typically, known radiation applicator systems do not have the heightened physical rigidity that is desirable when employing such techniques.
- In addition, some radiation applicators made available heretofore do not have radiation emitting elements for creating a microwave field pattern optimized for the treatment of soft tissue tumors.
- Also, given the power levels employed in some applicators and treatments, there can be problems of unwanted burning of non-target, healthy tissue due to the very high temperatures reached by the applicator or the components attached thereto.
- Further, although small diameter applicators are known, and liquid cooling techniques have been used, there has been difficulty in designing a small diameter device with sufficient cooling in applications employing power levels required to deal with soft is tissue tumors.
- Accordingly, there is a need for methods of treatment of soft tissue tumors, and for radiation applicators that overcome any or all of the aforementioned problems of the prior art techniques, and provide improved efficacy.
- Briefly, the present invention is directed to a microwave applicator for ablating tissue. The applicator is a dipole microwave antenna that transmits microwave radiation into the tissue being treated. The applicator is formed from a thin coaxial cable having an inner conductor surrounded by an insulator, which is surrounded by an outer conductor or shield. The end of the coaxial cable is trimmed so that a portion of the insulator and inner conductor extend beyond the outer conductor, and a portion of the inner conductor extends beyond the insulator. The applicator further includes a tubular ferrule defining an aperture therethrough. One end of the ferrule is attached to the outer conductor, while the other end, which forms a sleeve, extends out beyond the end of the insulator and around a portion of the extended inner conductor. A step is preferably formed on the outer surface of the ferrule between its two ends. A solid spacer having a central bore to receive the inner conductor abuts an end of the ferrule and surrounds the extended inner conductor. A tuning element is attached to the end of the extended inner conductor, and abuts an end of the spacer opposite the ferrule. The tuning element faces the step in the ferrule, and the step and the tuning element are both sized and shaped to cooperate in balancing and tuning the applicator. A hollow tip, formed from a dielectric material, has an open end and a closed end. The tip encloses the tuning element, the spacer, and the extended inner conductor. The tip also encloses the sleeve of the ferrule, thus defining outer surface of the ferrule that is surrounded by the dielectric tip. The open end of the tip preferably abuts the step in the ferrule. A rigid sleeve surrounds the coaxial cable and extends away from the ferrule opposite the tip. The sleeve, which abuts the step of the ferrule opposite the tip, has an inner diameter that is larger than the coaxial cable, thereby defining an annular space between the outside of the coaxial cable and the inner surface of the sleeve. The sleeve further includes one or more drainage holes, which permit fluid communication between the annular space around the coaxial cable and the outside of the applicator.
- In operation, microwave energy from a source is applied to the coaxial cable, and is conveyed to the tip. The portion of the inner conductor that extends beyond the end of the ferrule forms one arm of the dipole, and emits microwave radiation. In addition, the microwave energy flowing along the inner conductor of the coaxial cable and in the aperture of the ferrule induces a current to flow along the outer surface of the sleeve of the ferrule that is surrounded by the tip. This, in turn, causes microwave radiation to be emitted from the sleeve of the ferrule, which operates as the second arm of the dipole. In this way, microwave energy is emitted along a substantial length of the applicator, rather than being focused solely from the tip. By distributing the emission of microwave radiation along a length of the applicator, higher power levels may be employed.
- To keep the coaxial cable and the applicator from overheating, a cooling fluid is introduced from a source into the annular space defined by the outside of the coaxial cable and the inside of the sleeve. The cooling fluid flows along this annular space, and absorbs heat from the coaxial cable. The cooling fluid, after having absorbed heat from the coaxial cable, then exits the annular space through the one or more drainage holes in the sleeve, and perfuses adjacent tissue.
- The closed end of the tip is preferably formed into a blade or point so that the microwave applicator may be inserted directly into the tissue being treated. The tip, ferrule, and rigid sleeve, moreover, provide strength and stiffness to the applicator, thereby facilitating its insertion into tissue.
- The present invention further provides a method of treating target tissue, such as a tumor, the tumor being formed of, and/or being embedded within, soft tissue. The method includes inserting the microwave applicator into the tumor, and supplying electromagnetic energy to the applicator, thereby radiating electromagnetic energy into the tumor.
- Embodiments of the invention will now be described, by way of example, with is reference to the accompanying drawings, in which:
-
FIG. 1 is a schematic, partial cross-sectional view of a radiation applicator in accordance with one embodiment of the invention; -
FIG. 2A shows an axial cross-section, andFIG. 2B shows an end elevation of the radiating tip of the radiation applicator ofFIG. 1 ; -
FIG. 3 shows a partial transverse cross-section of the tube of the radiation applicator ofFIG. 1 ; -
FIG. 4A shows a transverse cross-section, andFIG. 4B shows an axial cross-section of the tuning washer of the radiation applicator ofFIG. 1 ; -
FIG. 5A shows an axial cross-section, andFIG. 5B shows an end elevation of the ferrule of the radiation applicator ofFIG. 1 ; -
FIG. 6A shows an axial cross-section, andFIG. 6B shows a transverse cross-section of a handle section that may be attached to the radiation applicator ofFIG. 1 ; -
FIG. 7 illustrates the portion of coaxial cable that passes through the tube of the radiation applicator ofFIG. 1 ; -
FIG. 8 is a plot of SI I against frequency for the radiation applicator ofFIG. 1 ; -
FIG. 9A illustrates the E-field distribution, andFIG. 9B illustrates the SAR values around the radiation applicator ofFIG. 1 , in use; - FIGS. 10A-E show a preferred sequential assembly of the radiation applicator of
FIG. 1 ; -
FIG. 11 schematically illustrates a treatment system employing the radiation applicator ofFIG. 1 ; -
FIG. 12 is an exploded, perspective view of another embodiment of the present invention; -
FIGS. 13-18 show a preferred sequential assembly of the radiation applicator ofFIG. 12 ; and -
FIG. 19 is a schematic, partial cross-sectional view of the radiation applicator ofFIG. 12 . - In the following description, like references are used to denote like elements, and where dimensions are given, they are in millimeters (mm). Further, it will be appreciated by persons skilled in the art that the electronic systems employed, in accordance with the present invention, to generate, deliver and control the application of radiation to parts of the human body may be as described in the art heretofore. In particular, such systems as are described in commonly owned published international patent applications WO95/04385, WO99/56642 and WOOO/49957 may be employed (except with the modifications described hereinafter). Full details of these systems have been omitted from the following for the sake of brevity.
-
FIG. 1 is a schematic, partial cross-sectional view of a radiation applicator in accordance with one embodiment of the invention. The radiation applicator, generally designated 102, includes a distal end portion of acoaxial cable 104 that is used to couple to a source (not shown) of microwaves, acopper ferrule 106, atuning washer 108 attached on the end 110 of the insulator part of thecoaxial cable 104, and atip 112. Preferably, theapplicator 102 further includes ametal tube 114.Tube 114 is rigidly attached to theferrule 106. Anannular space 116 is defined between theouter conductor 118 of thecable 104 and the inner surface of thetube 114, enabling cooling fluid to enter (in the direction of arrows A), contact the heated parts of theapplicator 102 and exit in the direction of arrows B throughradial holes 120 in thetube 114, thereby extracting heat energy from theradiation applicator 102. - In assembly of the
applicator 102, thewasher 108 is soldered to asmall length 122 of thecentral conductor 124 of thecable 104 that extends beyond the end 110 of theinsulator 126 of thecable 104. Theferrule 106 is soldered to a small cylindrical section 15 128 of theouter conductor 118 of thecable 104. Then, thetube 114, which is preferably stainless steel, but may be made of other suitable materials, such as titanium or any other medical grade material, is glued to theferrule 106 by means of an adhesive, such as Loctite 638 retaining compound, at the contacting surfaces thereof, indicated at 130 and 132. Thetip 112 is also glued preferably, using the same adhesive, on the inner surfaces thereof, to corresponding outer surfaces of theferrule 106 and theinsulation 126. - When assembled, the
applicator 102 forms a unitary device that is rigid and stable along its length, which may be of the order of 250 or somillimeters including tube 114, thereby making theapplicator 102 suitable for insertion into various types of soft tissue. Thespace 116 andholes 120 enable cooling fluid to extract heat from theapplicator 102 through contact with theferrule 106, theouter conductor 118 of thecable 104 and the end of thetube 114. Theferrule 106 assists, among other things, in assuring the applicator's rigidity. Theexposed end section 134 ofcable 104 from which theouter conductor 118 has been removed, in conjunction with thedielectric tip 112, are fed by a source of radiation of predetermined frequency. Theexposed end section 134 anddielectric tip 112 operate as a radiating antenna for radiating microwaves into tissue for therapeutic treatment. Theapplicator 102 operates as a dipole antenna, rather than a monopole device, resulting in an emitted radiation pattern that is highly beneficial for the treatment of certain tissues, such as malignant or tumorous tissue, due to its distributed, spherical directly heated area. -
FIG. 2A shows an axial cross-section, andFIG. 2B shows an end elevation of thetip 112 of theradiation applicator 102 ofFIG. 1 . As can be seen, thetip 112 has innercylindrical walls walls washer 108 and theferrule 106, respectively, during assembly. Suitably, thetip 112 is made of zirconia ceramic alloy. More preferably, it is a partially stabilized zirconia (PSZ) having yttria as the stabilizing oxidizing agent. Even more preferably, thetip 112 is made of Technox 2000, which is a PSZ commercially available from Dynamic Ceramic Ltd. of Staffordshire, England, having a very fine uniform grain compared to other PSZs, and a dielectric constant (k) of 25. As understood by those skilled in the art, the choice of dielectric material plays a part in determining the properties of the radiated microwave energy. - It will be noted that the transverse dimensions of the
applicator 102 are relatively small. In particular, the diameter ofapplicator 102 is preferably less than or equal to about 2.4 mm. Thetip 112, moreover, is designed to have dimensions, and be formed of the specified material, so as to perform effective tissue ablation at the operating microwave frequency, which in this case is preferably 2.45 Gigahertz (GHz). Theapplicator 102 of the present invention is thus well adapted for insertion into, and treatment of, cancerous and/or non-cancerous tissue of the liver, brain, lung, veins, bone, etc. - The
end 210 of thetip 112 is formed by conventional grinding techniques performed in the manufacture of thetip 112. Theend 210 may be formed as a fine point, such as a needle or pin, or it may be formed with an end blade, like a chisel, i.e. having a transverse dimension of elongation. The latter configuration has the benefit of being well suited to forcing thetip 112 into or through tissue, i.e. to perforate or puncture the surface of tissue, such as skin. - In use, the
tip 112 is preferably coated with a non-stick layer such as silicone or paralene, to facilitate movement of thetip 112 relative to tissue. -
FIG. 3 shows a partial transverse cross-section of thetube 114. As mentioned above, thetube 114 is preferably made of stainless steel. Specifically, thetube 114 is preferably made from 13 gauge thin wall 304 welded hard drawn (WHD) stainless steel. Thetube 114 is also approximately 215 mm in length. As can be seen, two sets ofradial holes end 302 of thetube 114. Theseradial holes tube 114 is not compromised. In this embodiment, theholes end 302 is 12 or 13 mm, in alternative embodiments, this distance may range from 3 mm to 50 mm from theend 302, in order to control the length of track that requires cauterization. - Further, in an embodiment used in a different manner, the
tube 114 may be omitted. In this case the treatment may comprise delivering the applicator to the treatment location, e.g., to the tumorous tissue, by suitable surgical or other techniques. For example, in the case of a brain tumor, the applicator may be left in place inside the tumor, the access wound closed, and a sterile connector left at the skull surface for subsequent connection to the microwave source for follow-up treatment at a later date. -
FIG. 4A shows a transverse cross-section, andFIG. 4B shows an axial cross-section of thetuning washer 108. Thewasher 108 is preferably made of copper, although other metals may be used. Thewasher 108 has an innercylindrical surface 402 enabling it to be soldered to thecentral conductor 124 of the cable 104 (FIG. 1 ). Although the washer is small, its dimensions are critical. Thewasher 108 tunes theapplicator 102, which operates as a dipole radiator, i.e., radiating energy from two locations, so that more effective treatment, i.e., ablation, of tissue is effected. -
FIG. 5A shows an axial cross-section, andFIG. 5B shows an end elevation of theferrule 106. Theferrule 106 is preferably made of copper, and is preferably gold plated to protect against any corrosive effects of the cooling fluid. Theferrule 106 may be produced by conventional machining techniques, such as CNC machining. -
FIG. 6A shows an axial cross-section, andFIG. 6B shows a transverse cross-section at line B-B of ahandle section 602 that may be attached to thetube 114 of theradiation applicator 102. Thehandle section 602 is preferably made from the same material as thetube 114, i.e., stainless steel. Thehandle section 602 includes aforward channel 604 enabling insertion of thetube 114, and arear channel 606 enabling insertion of thecoaxial cable 104 during assembly. Atransverse port 608 having aninternal thread 610 enables the connection, through a connector, to a source of cooling fluid, discussed later. The connector may be formed from plastic. Once assembled, the arrangement ofhandle section 602 enables cooling fluid to pass in the direction of arrow C into the tube 114 (not shown). -
FIG. 7 illustrates the portion ofcoaxial cable 104 that passes through thetube 114. Thecable 104 suitably comprises a low-loss, coaxial cable such as SJS070LL-253-Strip cable. Aconnector 702, preferably a SMA female type connector permits connection of thecable 104 to a microwave source (not shown), or to an intermediate section of coaxial cable (not shown) that, in turn, connects to the microwave source. -
FIG. 8 is a plot of S11 against frequency for theradiation applicator 102 ofFIG. 1 . This illustrates the ratio of reflective microwave power from the interface of theapplicator 102 and treated tissue to total input power to theapplicator 102. As can be seen, the design of theapplicator 102 causes the reflected power to be a minimum, and therefore the transmitted power into the tissue to be a maximum, at a frequency of 2.45 GHz of the delivered microwaves. -
FIG. 9A shows the E-field distribution around theradiation applicator 102 ofFIG. 1 , in use. Darker colors adjacent to theapplicator 102 indicate points of higher electric field. InFIG. 9A , the position of thewasher 108 is indicated at 902, and the position of the tip-ferrule junction is indicated at 904. Two limited, substantially cylindrical zones 906, 908, of highest electric field are formed around theapplicator 102 at thepositions -
FIG. 9B shows the specific absorption rate (SAR) value distribution around theradiation applicator 102 ofFIG. 1 , in use. Darker colors adjacent theapplicator 102 indicate points of SAR. InFIG. 9B , the position of thewasher 108 is indicated at 902, the position of the tip-ferrule junction is indicated at 904, and the position of the ferrule-tube junction is indicated at 905. Two limited, substantially cylindrical zones 910, 912, of highest SAR are formed around theapplicator 102 at thepositions 902 and between 904 and 905, respectively. - FIGS. 10A-E show a preferred sequential assembly of components forming the
radiation applicator 102 ofFIG. 1 . InFIG. 10A , thecoaxial cable 104 is shown with theouter conductor 118 and theinner insulator 126 trimmed back, as illustrated earlier inFIG. 7 . - As shown in
FIG. 10B , thetube 114 is then slid over thecable 104. Next, theferrule 106 is slid over the cable 104 (FIG. 10C ), and fixedly attached to thetube 114 and to thecable 104, as described earlier. Then, thewasher 108 is attached to theinner conductor 124 by soldering, as shown inFIG. 10D . Finally, thetip 112 is slid over thecable 104 and part of theferrule 106, and affixed thereto, as described earlier. The completed applicator is shown inFIG. 10E . This results in a construction of great rigidity and mechanical stability. -
FIG. 11 schematically illustrates atreatment system 1102 employing theradiation applicator 102 ofFIG. 1 .Microwave source 1104 is couple to theinput connector 1106 onhandle 602 bycoaxial cable 1108. In this embodiment, the microwave power is supplied at up to 80 Watts. However this could be larger for larger size applicators, e.g., up to 200 Watts for 5 mm diameter radiation applicators. -
Syringe pump 1110 operates asyringe 1112 for supplyingcooling fluid 1114 viaconduit 1116 andconnector 1118 attached to handle 602, to the interior of thehandle section 602. The fluid is not at great pressure, but is pumped so as to provide a flow rate of about 1.5 to 2.0 milliliter(ml)/minute through thepipe 114 in the illustrated embodiment. However, in other embodiments, where theradiation applicator 102 is operated at higher powers, higher flow rates may be employed, so as to provide appropriate cooling. The cooling fluid is preferably saline, although other liquids or gases may be used, such as ethanol. In certain embodiments, a cooling liquid having a secondary, e.g., cytotoxic, effect could be used, enhancing the tumor treatment. In the illustrative embodiment, the cooling fluid 1114 exits thetube 114, as shown by arrows B inFIG. 1 , at a temperature on the order of 10° C. higher than that at which it enters thetube 114, as shown by arrows A inFIG. 1 . Thus, substantial thermal energy is extracted from the coaxial cable. The cooling fluid 1114 may, for example, enter thetube 114 at room temperature. Alternatively, the cooling fluid 1114 may be pre-cooled to a temperature below room temperature by any suitable technique. - As shown, the cooling system is an open, perfusing cooling system that cools the coaxial cable connected to the
radiation applicator 102. That is, after absorbing heat from the coaxial cable, the cooling fluid perfuses the tissue near theradiation applicator 102. - The methodology for use of the
radiation applicator 102 of the present invention may be as conventionally employed in the treatment of various soft tissue tumors. In particular, theapplicator 102 is inserted into the body, laparoscopically, percutaneously or surgically. It is then moved to the correct position by the user, assisted where necessary by positioning sensors and/or imaging tools, such as ultrasound, so that thetip 112 is embedded in the tissue to be treated. The microwave power is switched on, and the tissue is thus ablated for a predetermined period of time under the control of the user. In most cases, theapplicator 102 is stationary during treatment. However, in some instances, e.g., in the treatment veins, theapplicator 102 may be moved, such as a gentle sliding motion relative to the target tissue, while the microwave radiation is being applied. - As described above, and as shown in
FIGS. 9A and 9B ,radiation applicator 102, is a dipole antenna. The portion of theinner conductor 124 that extends beyond theferrule 106 operates as one arm of the dipole antenna. In addition, the transmission of microwave energy along theinner conductor 124 and in the aperture of the ferrule induces a current to flow on that portion of the outer surface of theferrule 106 that is located underneath thetip 112. This induced current causes this enclosed, outer surface of theferrule 106 to emit microwave radiation, thereby forming a second arm of the dipole antenna. The bipolar configuration of the applicator effectively spreads the microwave radiation that is being transmitted by theapplicator 102 along a greater transverse, i.e., axial, length of theantenna 102, rather than focusing the radiation transmission solely from thetip 112 of theapplicator 102. As a result, theapplicator 102 of the present invention may be operated at much higher power levels, e.g., up to approximately 80 Watts, than prior art designs. - An alternative embodiment of the present invention is shown in
FIGS. 12-19 .FIG. 12 is an exploded, perspective view of analternative radiation applicator 1202. As shown, theapplicator 1202 includes acoaxial cable 1204 having anouter conductor 1206 that surrounds aninsulator 1208 that, in turn, surrounds an inner orcentral conductor 1210. Theapplicator 1202 further includes aferrule 1212. Theferrule 1212 is generally tubular shaped so as to define an aperture therethrough, and has first and second ends is 1212 a, 1212 b. Theferrule 1212 also has three parts or sections. Afirst section 1214 of theferrule 1212 has an inner diameter sized to fit over theouter conductor 1206 of thecoaxial cable 1204. Asecond section 1216 of theferrule 1212 has an inner diameter that is sized to fit over theinsulator 1208 of thecoaxial cable 1204. Thesecond section 1216 thus defines an annular surface or flange (not shown) around the inside theferrule 1212. The outer diameter of thesecond section 1216 is preferably larger than the outer diameter of thefirst section 1214, thereby defining a step or flange around the outside of theferrule 1212. Athird section 1218 of theferrule 1212 has an inner diameter also sized to fit around theinsulator 1208 of thecoaxial cable 1204. Thethird section 1218 has an outside diameter that is less than the outside diameter of thesecond section 1216. Thethird section 1218 thus defines an outer, cylindrical surface or sleeve. -
Applicator 1202 further includes aspacer 1220. Thespacer 1220 is preferably cylindrical in shape with acentral bore 1222 sized to receive theinner conductor 1210 of thecoaxial cable 1204. The outer diameter of thespacer 1220 preferably matches the outer diameter of thethird section 1218 of theferrule 1212.Applicator 1202 also includes atuning element 1224 and atip 1226. Thetuning element 1224, which be may be disk-shaped, has acentral hole 1228 sized to fit around theinner conductor 1210 of thecoaxial cable 1204. Thetip 1226 is a hollow, elongated member, having anopen end 1230, and aclosed end 1232. Theclosed end 1232 may be formed into a cutting element, such as a trocar point or a blade, to cut or pierce tissue.Applicator 1202 also includes arigid sleeve 1234. Thesleeve 1234 has an inner diameter that is slightly larger than outer diameter of thecoaxial cable 1204. As described below, an annular space is thereby defined between the outer surface of thecoaxial cable 1204 and the inner surface of thesleeve 1234. Thesleeve 1234 further includes one ormore drainage holes 1236 that extend through the sleeve. -
FIGS. 13-18 illustrate a preferred assembly sequence of theapplicator 1202. As shown inFIG. 13 , thecoaxial cable 1204 is trimmed so that there is a length “m” ofinsulator 1208 that extends beyond anend 1206 a of theouter conductor 1206, and a length “I” ofinner conductor 1210 that extends beyond anend 1208 a of theinsulator 1208. Theferrule 1212 slides over the exposedinner conductor 1210 and over the exposedinsulator 1208 such that thefirst section 1214 surrounds theouter conductor 1206, and the second andthird sections insulator 1208. The inner surface or flange formed on thesecond section 1216 of theferrule 1212 abuts theend 1206 a of theouter conductor 1206, thereby stopping theferrule 1212 from sliding any further up thecoaxial cable 1204. Theferrule 1212 is preferably fixedly attached to thecoaxial cable 1204, such as by soldering theferrule 1212 to theouter conductor 1206 of thecoaxial cable 1204. In the preferred embodiment, thethird section 1218 of theferrule 1212 extends past theend 1208 a of the exposedinsulator 1208 as shown by the dashed line inFIG. 14 . - Next, the
spacer 1220 is slid over the exposed portion of theinner conductor 1210, and is brought into contact with thesecond end 1212 b of theferrule 1212. In the preferred embodiment, thespacer 1220 is not fixedly attached to theferrule 1212 or theinner conductor 1210. Thespacer 1220 is sized so that asmall portion 1210 a (FIG. 15 ) of theinner conductor 1210 remains exposed. Thetuning element 1224 is then slid over this remaining exposedportion 1210 a of theinner conductor 1210. Thetuning element 1224 is preferably fixedly attached to theinner conductor 1210, e.g., by soldering. Thetuning element 1224, in cooperation with theferrule 1212, thus hold thespacer 1220 in place. - With the
tuning element 1224 in place, the next step is to install thetip 1226 as shown inFIG. 16 . Theopen end 1230 of thetip 1226 is slid over thetuning element 1224, thespacer 1224 and thethird section 1218 of theferrule 1212. Theopen end 1230 of thetip 1226 abuts the second section orstep 1216 of theferrule 1212. Thetip 1226 is preferably fixedly attached to theferrule 1212, e.g., by bonding. With thetip 1226 in place, the next step is to install the sleeve 1234 (FIG. 17 ). Thesleeve 1234 is slid over thecoaxial cable 1234, and up over thefirst section 1214 of theferrule 1212. Thesleeve 1234 abuts thestep 1216 in theferrule 1212 opposite thetip 1226. - Those skilled in the art will understand that the
applicator 1202 may be assembled in different ways or in different orders. - As illustrated in
FIG. 18 , upon assembly, thetip 1226,second section 1216 of theferrule 1212, andsleeve 1234 all preferably have the same outer diameter, thereby giving the applicator 1202 a smooth outer surface. - Preferably, the
sleeve 1234 is formed from stainless steel, and theferrule 1212 is formed from gold-plated copper. Thetip 1226 and thespacer 1220 are formed from dielectric materials. In the illustrative embodiment, thetip 1226 and thespacer 1220 are formed from an itrium stabilized zirconia, such as the Technox brand of ceramic material commercially available from Dynamic Ceramic Ltd. of Stoke-on-Trent, Staffordshire, England, which has a dielectric constant of 25. Thetip 1226 may be further provided with a composite coating, such as a polyimide undercoat layer, for adhesion, and a paralyne overcoat layer, for its non-stick properties. Alternatively, silicone or some other suitable material could be used in place of paralyne. The composite coating may also be applied to the ferrule and at least part of the stainless steel sleeve, in addition to being applied to the tip. - Those skilled in the art will understand that alternative materials may be used in the construction of the
radiation applicator 1202. -
FIG. 19 is a schematic, partial cross-sectional view of theradiation applicator 1202. As shown, at least part of thefirst section 1214 of theferrule 1212 overlies and is attached to theouter conductor 1206. Theinsulator 1208 extends partially through the inside of theferrule 1212. In particular, theend 1208 a of theinsulator 1208 is disposed a predetermined distance back from thesecond end 1212 b of theferrule 1212. Theinner conductor 1210 extends completely through and beyond theferrule 1212. Thesleeve 1234 slides over and is bonded to thefirst section 1214 of theferrule 1212. As shown, the inside diameter of thesleeve 1234 is greater than the outside diameter of thecoaxial cable 1204, thereby defining anannular space 1238 between the outside of thecoaxial cable 1204 and the inside of thesleeve 1234. Cooling fluid, such as saline, is pumped through thisannular space 1238, as shown by arrows A. The cooling fluid absorbs heat from the coaxial cable that feeds radiation toapplicator 1202. The cooling fluid is then discharged throughholes 1236 in thesleeve 1234, as shown by arrows B. - In the preferred embodiment, the
holes 1236 are placed far enough behind theclosed end 1232 of thetip 1226 such that the discharged cooling fluid does not enter that portion of the tissue that is being heated by theradiation applicator 1202. Instead, the discharged cooling fluid preferably perfuses tissue outside of this heated region. Depending on the tissue to be treated, a suitable distance between theclosed end 1232 of thetip 1226 and theholes 1236 may be approximately 30 mm. - A
first end 1220 a of thespacer 1220 abuts thesecond end 1212 b of theferrule 1212, while asecond end 1220 b of thespacer 1220 abuts thetuning element 1224. Accordingly a space, designated generally 1240, is defined within theferrule 1212 between theend 1208 a of the insulator and thesecond end 1212 b of the ferrule. In the illustrative embodiment, thisspace 1240 is filled with air. Those skilled in the art will understand that the space may be filled with other materials, such as a solid dielectric, or it may be evacuated to form a vacuum. The inside surface of thetip 1226 preferably conforms to the shape of thetuning element 1224, thespacer 1220, and thethird section 1218 of theferrule 1212 so that there are no gaps formed along the inside surface of thetip 1226. - As indicated above, operation of the
radiation applicator 1202 causes a current to be induced on the outer surface of thethird section 1218 of theferrule 1212, which is enclosed within the dielectric material of thetip 1226. This induced current results in microwave energy being radiated from this surface of theferrule 1212, thereby forming one arm of the dipole. The section of theinner conductor 1210 that extends beyond theferrule 1212 is the other arm of the dipole. Both the length of theinner conductor 1210 that extends beyond theferrule 1212, and the length of thethird section 1218 of theferrule 1212, which together correspond to the two arms of the dipole, are chosen to be approximately ¼ of the wavelength in thedielectric tip 1226, which in the illustrative embodiment is approximately 6 mm. Nonetheless, those skilled in the art will understand that other factors, such as tissue permittivity, the action of the tuning element, etc., will affect the ultimate lengths of the dipole arms. For example, in the illustrative embodiment, the two arms are approximately 5 mm in length. - The
tuning element 1224, moreover, cooperates with the second section or step is 1216 of the ferrule to balance the radiation being emitted by the two arms of the dipole. - In particular, the size and shape of the
tuning element 1224 and thestep 1216 are selected such that the coherent sum of the microwave power reflected back toward the cable at the aperture of the ferrule is minimized. Techniques for performing such design optimizations are well-known to those skilled in the relevant art. - In use, the
radiation applicator 1202 is attached to a source of microwave radiation in a similar manner as described above in connection with theapplicator 102 ofFIG. 1 . The coaxial cable is also attached to a source of cooling fluid in a similar manner as described above. With the present invention, it is the dielectric tip, ferrule and stainless steel sleeve that cooperate to provide the necessary stiffness and mechanical strength for the applicator to be used in treatment procedures. The applicator does not rely on the coaxial cable for any of its strength. Indeed, a flexible coaxial cable, having little or no rigidity, could be used with the radiation applicator of the present invention. - The foregoing has been a detailed description of illustrative embodiments of the invention. Various modifications and additions can be made without departing from the spirit and scope thereof. For example, the materials described herein are not exhaustive, and any acceptable material can be employed for any component of the described system and method. In addition, modifications can be made to the shape of various components. Accordingly, this description is meant to be taken only by way of example, and not to otherwise limit the scope of the invention.
Claims (15)
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/646,141 US20070203551A1 (en) | 2005-07-01 | 2006-12-27 | Radiation applicator and method of radiating tissue |
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
PCT/EP2005/007103 WO2006002943A1 (en) | 2004-07-02 | 2005-07-01 | Radiation applicator and method of radiating tissue |
GB0600018A GB2434314B (en) | 2006-01-03 | 2006-01-03 | Microwave applicator with dipole antenna |
GB0600018.6 | 2006-01-03 | ||
US11/646,141 US20070203551A1 (en) | 2005-07-01 | 2006-12-27 | Radiation applicator and method of radiating tissue |
Related Parent Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/EP2005/007103 Continuation WO2006002943A1 (en) | 2004-07-02 | 2005-07-01 | Radiation applicator and method of radiating tissue |
US11/577,414 Continuation US20090130205A9 (en) | 2004-10-19 | 2005-10-19 | Solid Pharmaceutical Composition Comprising Donepezil Hydrochloride |
Publications (1)
Publication Number | Publication Date |
---|---|
US20070203551A1 true US20070203551A1 (en) | 2007-08-30 |
Family
ID=35841437
Family Applications (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/158,831 Abandoned US20080294155A1 (en) | 2006-01-03 | 2006-12-15 | Radiation Applicator and Method of Radiating Tissue |
US11/646,141 Abandoned US20070203551A1 (en) | 2005-07-01 | 2006-12-27 | Radiation applicator and method of radiating tissue |
US14/940,354 Active US9907613B2 (en) | 2005-07-01 | 2015-11-13 | Radiation applicator and method of radiating tissue |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/158,831 Abandoned US20080294155A1 (en) | 2006-01-03 | 2006-12-15 | Radiation Applicator and Method of Radiating Tissue |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US14/940,354 Active US9907613B2 (en) | 2005-07-01 | 2015-11-13 | Radiation applicator and method of radiating tissue |
Country Status (12)
Country | Link |
---|---|
US (3) | US20080294155A1 (en) |
EP (1) | EP1968469B8 (en) |
JP (1) | JP5318581B2 (en) |
KR (1) | KR20080092402A (en) |
CN (1) | CN101631506B (en) |
AU (1) | AU2006332213B2 (en) |
BR (1) | BRPI0620875A2 (en) |
CA (1) | CA2635316A1 (en) |
GB (1) | GB2434314B (en) |
IL (1) | IL192469A0 (en) |
TW (1) | TW200740407A (en) |
WO (1) | WO2007076924A2 (en) |
Cited By (61)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20060259024A1 (en) * | 2005-05-10 | 2006-11-16 | Roman Turovskiy | Reinforced high strength microwave antenna |
US20080266203A1 (en) * | 2007-04-25 | 2008-10-30 | Vivant Medical, Inc. | Cooled helical antenna for microwave ablation |
US20080319434A1 (en) * | 2007-06-20 | 2008-12-25 | Rick Kyle R | Reflective power monitoring for microwave applications |
US20090082762A1 (en) * | 2007-09-20 | 2009-03-26 | Ormsby Theodore C | Radio frequency energy transmission device for the ablation of biological tissues |
US20090163911A1 (en) * | 2007-12-21 | 2009-06-25 | Hong Cao | Thermally insulated irrigation catheter assembly |
US20090187180A1 (en) * | 2008-01-23 | 2009-07-23 | Vivant Medical, Inc. | Choked Dielectric Loaded Tip Dipole Microwave Antenna |
US20090222002A1 (en) * | 2008-03-03 | 2009-09-03 | Vivant Medical, Inc. | Intracooled Percutaneous Microwave Ablation Probe |
US20090248006A1 (en) * | 2008-03-31 | 2009-10-01 | Paulus Joseph A | Re-Hydration Antenna for Ablation |
US20090295674A1 (en) * | 2008-05-29 | 2009-12-03 | Kenlyn Bonn | Slidable Choke Microwave Antenna |
US20100053015A1 (en) * | 2008-08-28 | 2010-03-04 | Vivant Medical, Inc. | Microwave Antenna |
US20100097284A1 (en) * | 2008-10-17 | 2010-04-22 | Vivant Medical, Inc. | Choked Dielectric Loaded Tip Dipole Microwave Antenna |
US20100234839A1 (en) * | 2009-03-10 | 2010-09-16 | Vivant Medical, Inc. | Cooled Dielectrically Buffered Microwave Dipole Antenna |
US7826904B2 (en) | 2006-02-07 | 2010-11-02 | Angiodynamics, Inc. | Interstitial microwave system and method for thermal treatment of diseases |
US7862559B2 (en) | 2001-11-02 | 2011-01-04 | Vivant Medical, Inc. | High-strength microwave antenna assemblies and methods of use |
US7875024B2 (en) | 2003-07-18 | 2011-01-25 | Vivant Medical, Inc. | Devices and methods for cooling microwave antennas |
US20110060326A1 (en) * | 2009-09-09 | 2011-03-10 | Vivant Medical, Inc. | System and Method for Performing an Ablation Procedure |
US20110077637A1 (en) * | 2009-09-29 | 2011-03-31 | Vivant Medical, Inc. | Flow Rate Monitor for Fluid Cooled Microwave Ablation Probe |
US20110077636A1 (en) * | 2009-09-29 | 2011-03-31 | Vivant Medical, Inc. | Management of Voltage Standing Wave Ratio at Skin Surface During Microwave Ablation |
US8035570B2 (en) | 2001-11-02 | 2011-10-11 | Vivant Medical, Inc. | High-strength microwave antenna assemblies |
KR101173455B1 (en) | 2010-01-26 | 2012-08-14 | 서울대학교산학협력단 | Applicator with plural slots having each different size |
US20120259324A1 (en) * | 2011-04-08 | 2012-10-11 | Vivant Medical, Inc. | Microwave Tissue Dissection and Coagulation |
US8353901B2 (en) | 2007-05-22 | 2013-01-15 | Vivant Medical, Inc. | Energy delivery conduits for use with electrosurgical devices |
US20130197504A1 (en) * | 2009-10-06 | 2013-08-01 | Nigel Cronin | Medical devices and pumps therefor |
WO2013151788A1 (en) * | 2012-04-06 | 2013-10-10 | Winsconsin Alumni Research Foundation | Feeding structure for dual slot microwave ablation probe |
US8568404B2 (en) | 2010-02-19 | 2013-10-29 | Covidien Lp | Bipolar electrode probe for ablation monitoring |
US20130317495A1 (en) * | 2007-06-28 | 2013-11-28 | Covidien Lp | Broadband microwave applicator |
US8740893B2 (en) | 2010-06-30 | 2014-06-03 | Covidien Lp | Adjustable tuning of a dielectrically loaded loop antenna |
US20140171932A1 (en) * | 2012-12-17 | 2014-06-19 | Covidien Lp | Ablation probe with tissue sensing configuration |
US8882759B2 (en) | 2009-12-18 | 2014-11-11 | Covidien Lp | Microwave ablation system with dielectric temperature probe |
US9192439B2 (en) | 2012-06-29 | 2015-11-24 | Covidien Lp | Method of manufacturing a surgical instrument |
US20160045256A1 (en) * | 2010-04-26 | 2016-02-18 | 9234438 Canada Inc. | Electrosurgical Devices and Methods |
US9333035B2 (en) | 2012-09-19 | 2016-05-10 | Denervx LLC | Cooled microwave denervation |
US20160199130A1 (en) * | 2013-08-08 | 2016-07-14 | H.S. - Hospital Service S.P.A. | Microwave Device For Tissue Ablation |
US9566115B2 (en) | 2009-07-28 | 2017-02-14 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US9770295B2 (en) | 2003-06-23 | 2017-09-26 | Angiodynamics, Inc. | Radiation applicator for microwave medical treatment |
US9788896B2 (en) | 2004-07-02 | 2017-10-17 | Angiodynamics, Inc. | Radiation applicator and method of radiating tissue |
US20170296269A1 (en) * | 2014-11-11 | 2017-10-19 | Nanjing Vison-China Medical Devices R & D Center | Manufacturing method for non-magnetic water-cooled microwave ablation needle |
US9861440B2 (en) | 2010-05-03 | 2018-01-09 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US9888956B2 (en) | 2013-01-22 | 2018-02-13 | Angiodynamics, Inc. | Integrated pump and generator device and method of use |
US9901398B2 (en) | 2012-06-29 | 2018-02-27 | Covidien Lp | Microwave antenna probes |
WO2018140816A1 (en) | 2017-01-26 | 2018-08-02 | Broncus Medical Inc. | Bronchoscopic-based microwave ablation system and method |
US20180221090A1 (en) * | 2011-01-05 | 2018-08-09 | Covidien Lp | Energy-delivery devices with flexible fluid-cooled shaft, inflow / outflow junctions suitable for use with same, and systems including same |
US10179029B2 (en) | 2014-01-24 | 2019-01-15 | Denervx LLC | Cooled microwave denervation catheter configuration and method |
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 |
US10390881B2 (en) | 2013-10-25 | 2019-08-27 | Denervx LLC | Cooled microwave denervation catheter with insertion feature |
US10531917B2 (en) | 2016-04-15 | 2020-01-14 | Neuwave Medical, Inc. | Systems and methods for energy delivery |
US10660691B2 (en) | 2015-10-07 | 2020-05-26 | Angiodynamics, Inc. | Multiple use subassembly with integrated fluid delivery system for use with single or dual-lumen peristaltic tubing |
US10667860B2 (en) | 2011-12-21 | 2020-06-02 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
WO2020165375A1 (en) * | 2019-02-13 | 2020-08-20 | National University Of Ireland, Galway | An ablation probe |
US20210038303A1 (en) * | 2019-08-07 | 2021-02-11 | Biocompatibles Uk Limited | Microwave ablation probe |
US10952792B2 (en) | 2015-10-26 | 2021-03-23 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US11213339B2 (en) | 2015-11-17 | 2022-01-04 | Medtronic Holding Company Sàrl | Spinal tissue ablation apparatus, system, and method |
US11389235B2 (en) | 2006-07-14 | 2022-07-19 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US11399915B2 (en) | 2013-03-15 | 2022-08-02 | TriAgenics, Inc. | Therapeutic tooth bud ablation |
US11576716B2 (en) | 2013-03-15 | 2023-02-14 | Medtronic Holding Company Sàrl | Electrosurgical mapping tools and methods |
US11583337B2 (en) * | 2019-06-06 | 2023-02-21 | TriAgenics, Inc. | Ablation probe systems |
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 |
US11864961B2 (en) | 2013-03-15 | 2024-01-09 | TriAgenics, Inc. | Therapeutic tooth bud ablation |
US11931016B2 (en) | 2013-03-07 | 2024-03-19 | Medtronic Holding Company Sàrl | Systems and methods for track coagulation |
Families Citing this family (28)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB0624658D0 (en) | 2006-12-11 | 2007-01-17 | Medical Device Innovations Ltd | Electrosurgical ablation apparatus and a method of ablating biological tissue |
US8403924B2 (en) | 2008-09-03 | 2013-03-26 | Vivant Medical, Inc. | Shielding for an isolation apparatus used in a microwave generator |
US8394086B2 (en) * | 2008-09-03 | 2013-03-12 | Vivant Medical, Inc. | Microwave shielding apparatus |
US8903488B2 (en) | 2009-05-28 | 2014-12-02 | Angiodynamics, Inc. | System and method for synchronizing energy delivery to the cardiac rhythm |
US9895189B2 (en) | 2009-06-19 | 2018-02-20 | Angiodynamics, Inc. | Methods of sterilization and treating infection using irreversible electroporation |
US8328801B2 (en) * | 2009-08-17 | 2012-12-11 | Vivant Medical, Inc. | Surface ablation antenna with dielectric loading |
TWI397399B (en) * | 2009-08-26 | 2013-06-01 | Univ Nat Cheng Kung | Two-portion device for electromagnetic hyperthermia therapy |
US8069553B2 (en) | 2009-09-09 | 2011-12-06 | Vivant Medical, Inc. | Method for constructing a dipole antenna |
US9993294B2 (en) | 2009-11-17 | 2018-06-12 | Perseon Corporation | Microwave coagulation applicator and system with fluid injection |
US8551083B2 (en) | 2009-11-17 | 2013-10-08 | Bsd Medical Corporation | Microwave coagulation applicator and system |
US9700368B2 (en) | 2010-10-13 | 2017-07-11 | Angiodynamics, Inc. | System and method for electrically ablating tissue of a patient |
US9770294B2 (en) | 2011-01-05 | 2017-09-26 | Covidien Lp | Energy-delivery devices with flexible fluid-cooled shaft, inflow/outflow junctions suitable for use with same, and systems including same |
US8932281B2 (en) * | 2011-01-05 | 2015-01-13 | Covidien Lp | Energy-delivery devices with flexible fluid-cooled shaft, inflow/outflow junctions suitable for use with same, and systems including same |
US9017319B2 (en) | 2011-01-05 | 2015-04-28 | Covidien Lp | Energy-delivery devices with flexible fluid-cooled shaft, inflow/outflow junctions suitable for use with same, and systems including same |
US20120310230A1 (en) * | 2011-06-01 | 2012-12-06 | Angiodynamics, Inc. | Coaxial dual function probe and method of use |
US9078665B2 (en) | 2011-09-28 | 2015-07-14 | Angiodynamics, Inc. | Multiple treatment zone ablation probe |
US9529025B2 (en) | 2012-06-29 | 2016-12-27 | Covidien Lp | Systems and methods for measuring the frequency of signals generated by high frequency medical devices |
WO2014160931A1 (en) | 2013-03-29 | 2014-10-02 | Covidien Lp | Step-down coaxial microwave ablation applicators and methods for manufacturing same |
US9872719B2 (en) | 2013-07-24 | 2018-01-23 | Covidien Lp | Systems and methods for generating electrosurgical energy using a multistage power converter |
US9636165B2 (en) | 2013-07-29 | 2017-05-02 | Covidien Lp | Systems and methods for measuring tissue impedance through an electrosurgical cable |
CN104905874A (en) * | 2015-06-16 | 2015-09-16 | 翟博 | Microwave ablation needle having biopsy function and method for manufacturing stab head thereof |
CA3001388C (en) * | 2015-10-16 | 2024-03-19 | U.S. Patent Innovations Llc | Low electromagnetic field electrosurgical cable |
TWI577413B (en) * | 2016-05-26 | 2017-04-11 | 和鑫生技開發股份有限公司 | Brachytherapy apparatus and radiation source thereof |
US10905492B2 (en) | 2016-11-17 | 2021-02-02 | Angiodynamics, Inc. | Techniques for irreversible electroporation using a single-pole tine-style internal device communicating with an external surface electrode |
GB2576481B (en) * | 2018-05-30 | 2022-07-20 | Creo Medical Ltd | Electrosurgical instrument |
US11524538B2 (en) | 2018-07-01 | 2022-12-13 | Ree Automotive Ltd | Wheel suspension and transmission gear assembly |
GB2575485A (en) * | 2018-07-12 | 2020-01-15 | Creo Medical Ltd | Electrosurgical instrument |
WO2023180355A1 (en) | 2022-03-24 | 2023-09-28 | Huber+Suhner Ag | Cable assembly |
Citations (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4612940A (en) * | 1984-05-09 | 1986-09-23 | Scd Incorporated | Microwave dipole probe for in vivo localized hyperthermia |
US6047216A (en) * | 1996-04-17 | 2000-04-04 | The United States Of America Represented By The Administrator Of The National Aeronautics And Space Administration | Endothelium preserving microwave treatment for atherosclerosis |
US6223085B1 (en) * | 1997-05-06 | 2001-04-24 | Urologix, Inc. | Device and method for preventing restenosis |
US20030088242A1 (en) * | 2001-11-02 | 2003-05-08 | Mani Prakash | High-strength microwave antenna assemblies |
US20030100894A1 (en) * | 2001-11-23 | 2003-05-29 | John Mahon | Invasive therapeutic probe |
US20050245920A1 (en) * | 2004-04-30 | 2005-11-03 | Vitullo Jeffrey M | Cell necrosis apparatus with cooled microwave antenna |
US7311703B2 (en) * | 2003-07-18 | 2007-12-25 | Vivant Medical, Inc. | Devices and methods for cooling microwave antennas |
Family Cites Families (67)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE1112593B (en) | 1959-11-14 | 1961-08-10 | Philips Patentverwaltung | HF emitter for diathermy and therapy purposes |
US3461261A (en) | 1966-10-31 | 1969-08-12 | Du Pont | Heating apparatus |
US3871359A (en) | 1973-06-25 | 1975-03-18 | Interscience Technology Corp | Impedance measuring system |
SE441640B (en) | 1980-01-03 | 1985-10-21 | Stiftelsen Inst Mikrovags | PROCEDURE AND DEVICE FOR HEATING BY MICROVAGS ENERGY |
SE417780B (en) | 1980-01-22 | 1981-04-06 | Por Microtrans Ab | DIELECTRIC HEATING DEVICE |
US4557272A (en) * | 1980-03-31 | 1985-12-10 | Microwave Associates, Inc. | Microwave endoscope detection and treatment system |
US4446874A (en) | 1981-12-30 | 1984-05-08 | Clini-Therm Corporation | Microwave applicator with discoupled input coupling and frequency tuning functions |
GB8300779D0 (en) | 1983-01-12 | 1983-02-16 | Univ Glasgow | Microwave thermographic apparatus for bio-medical use |
CA1244889A (en) | 1983-01-24 | 1988-11-15 | Kureha Chemical Ind Co Ltd | Device for hyperthermia |
US4891483A (en) | 1985-06-29 | 1990-01-02 | Tokyo Keiki Co. Ltd. | Heating apparatus for hyperthermia |
US5564417A (en) | 1991-01-24 | 1996-10-15 | Non-Invasive Technology, Inc. | Pathlength corrected oximeter and the like |
US4945912A (en) | 1988-11-25 | 1990-08-07 | Sensor Electronics, Inc. | Catheter with radiofrequency heating applicator |
US5540737A (en) | 1991-06-26 | 1996-07-30 | Massachusetts Institute Of Technology | Minimally invasive monopole phased array hyperthermia applicators and method for treating breast carcinomas |
US6277112B1 (en) | 1996-07-16 | 2001-08-21 | Arthrocare Corporation | Methods for electrosurgical spine surgery |
US5697882A (en) | 1992-01-07 | 1997-12-16 | Arthrocare Corporation | System and method for electrosurgical cutting and ablation |
US6142992A (en) | 1993-05-10 | 2000-11-07 | Arthrocare Corporation | Power supply for limiting power in electrosurgery |
US5227730A (en) | 1992-09-14 | 1993-07-13 | Kdc Technology Corp. | Microwave needle dielectric sensors |
US5620479A (en) | 1992-11-13 | 1997-04-15 | The Regents Of The University Of California | Method and apparatus for thermal therapy of tumors |
US5364392A (en) | 1993-05-14 | 1994-11-15 | Fidus Medical Technology Corporation | Microwave ablation catheter system with impedance matching tuner and method |
US5683384A (en) | 1993-11-08 | 1997-11-04 | Zomed | Multiple antenna ablation apparatus |
US5536267A (en) | 1993-11-08 | 1996-07-16 | Zomed International | Multiple electrode ablation apparatus |
US5458597A (en) | 1993-11-08 | 1995-10-17 | Zomed International | Device for treating cancer and non-malignant tumors and methods |
US5728143A (en) | 1995-08-15 | 1998-03-17 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method |
US6056744A (en) | 1994-06-24 | 2000-05-02 | Conway Stuart Medical, Inc. | Sphincter treatment apparatus |
US5810742A (en) | 1994-10-24 | 1998-09-22 | Transcan Research & Development Co., Ltd. | Tissue characterization based on impedance images and on impedance measurements |
US5630426A (en) | 1995-03-03 | 1997-05-20 | Neovision Corporation | Apparatus and method for characterization and treatment of tumors |
US6106524A (en) | 1995-03-03 | 2000-08-22 | Neothermia Corporation | Methods and apparatus for therapeutic cauterization of predetermined volumes of biological tissue |
US5735847A (en) | 1995-08-15 | 1998-04-07 | Zomed International, Inc. | Multiple antenna ablation apparatus and method with cooling element |
US5810804A (en) * | 1995-08-15 | 1998-09-22 | Rita Medical Systems | Multiple antenna ablation apparatus and method with cooling element |
US5800484A (en) | 1995-08-15 | 1998-09-01 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus with expanded electrodes |
US5807272A (en) | 1995-10-31 | 1998-09-15 | Worcester Polytechnic Institute | Impedance spectroscopy system for ischemia monitoring and detection |
US6016452A (en) | 1996-03-19 | 2000-01-18 | Kasevich; Raymond S. | Dynamic heating method and radio frequency thermal treatment |
US5904709A (en) * | 1996-04-17 | 1999-05-18 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Microwave treatment for cardiac arrhythmias |
US6289249B1 (en) * | 1996-04-17 | 2001-09-11 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Transcatheter microwave antenna |
JP4033495B2 (en) | 1996-08-15 | 2008-01-16 | デカ・プロダクツ・リミテッド・パートナーシップ | Medical irrigation pump and system |
US5873849A (en) | 1997-04-24 | 1999-02-23 | Ichor Medical Systems, Inc. | Electrodes and electrode arrays for generating electroporation inducing electrical fields |
US6009347A (en) | 1998-01-27 | 1999-12-28 | Genetronics, Inc. | Electroporation apparatus with connective electrode template |
US7776014B2 (en) | 1998-01-29 | 2010-08-17 | Peter Visconti | Disposable surgical suction/irrigation trumpet valve tube cassette |
US6027502A (en) | 1998-01-29 | 2000-02-22 | Desai; Ashvin H. | Surgical apparatus providing tool access and replaceable irrigation pump cartridge |
US6558378B2 (en) | 1998-05-05 | 2003-05-06 | Cardiac Pacemakers, Inc. | RF ablation system and method having automatic temperature control |
US6312425B1 (en) | 1998-05-05 | 2001-11-06 | Cardiac Pacemakers, Inc. | RF ablation catheter tip electrode with multiple thermal sensors |
US6050994A (en) | 1998-05-05 | 2000-04-18 | Cardiac Pacemakers, Inc. | RF ablation apparatus and method using controllable duty cycle with alternate phasing |
US6059778A (en) | 1998-05-05 | 2000-05-09 | Cardiac Pacemakers, Inc. | RF ablation apparatus and method using unipolar and bipolar techniques |
US6171305B1 (en) | 1998-05-05 | 2001-01-09 | Cardiac Pacemakers, Inc. | RF ablation apparatus and method having high output impedance drivers |
US6635055B1 (en) | 1998-05-06 | 2003-10-21 | Microsulis Plc | Microwave applicator for endometrial ablation |
JP2000005180A (en) | 1998-06-25 | 2000-01-11 | Olympus Optical Co Ltd | Acoustic impedance measuring device |
US6723094B1 (en) | 1998-12-18 | 2004-04-20 | Kai Desinger | Electrode assembly for a surgical instrument provided for carrying out an electrothermal coagulation of tissue |
US6478793B1 (en) | 1999-06-11 | 2002-11-12 | Sherwood Services Ag | Ablation treatment of bone metastases |
US6287302B1 (en) | 1999-06-14 | 2001-09-11 | Fidus Medical Technology Corporation | End-firing microwave ablation instrument with horn reflection device |
US6770070B1 (en) | 2000-03-17 | 2004-08-03 | Rita Medical Systems, Inc. | Lung treatment apparatus and method |
AU5113401A (en) | 2000-03-31 | 2001-10-15 | Rita Medical Systems Inc | Tissue biopsy and treatment apparatus and method |
US6962587B2 (en) | 2000-07-25 | 2005-11-08 | Rita Medical Systems, Inc. | Method for detecting and treating tumors using localized impedance measurement |
US6840935B2 (en) | 2000-08-09 | 2005-01-11 | Bekl Corporation | Gynecological ablation procedure and system using an ablation needle |
JP2002109971A (en) | 2000-09-27 | 2002-04-12 | Mitsubishi Cable Ind Ltd | Highly foamed plastic insulation coaxial cable |
ITPI20010006A1 (en) * | 2001-01-31 | 2002-07-31 | Cnr Consiglio Naz Delle Ricer | INTERSTITIAL ANTENNA WITH MINIATURIZED CHOKE FOR MICROWAVE HYPERTEMIA APPLICATIONS IN MEDICINE AND SURGERY |
US7008421B2 (en) | 2002-08-21 | 2006-03-07 | Resect Medical, Inc. | Apparatus and method for tissue resection |
US6497704B2 (en) | 2001-04-04 | 2002-12-24 | Moshe Ein-Gal | Electrosurgical apparatus |
US7070597B2 (en) | 2001-10-18 | 2006-07-04 | Surgrx, Inc. | Electrosurgical working end for controlled energy delivery |
US7128739B2 (en) * | 2001-11-02 | 2006-10-31 | Vivant Medical, Inc. | High-strength microwave antenna assemblies and methods of use |
GB2387544B (en) * | 2002-10-10 | 2004-03-17 | Microsulis Plc | Microwave applicator |
JP4138468B2 (en) * | 2002-12-06 | 2008-08-27 | アルフレッサファーマ株式会社 | Microwave surgical device |
JP4138469B2 (en) * | 2002-12-06 | 2008-08-27 | アルフレッサファーマ株式会社 | Microwave surgical device |
US20040267340A1 (en) | 2002-12-12 | 2004-12-30 | Wit Ip Corporation | Modular thermal treatment systems with single-use disposable catheter assemblies and related methods |
JP4231743B2 (en) | 2003-07-07 | 2009-03-04 | オリンパス株式会社 | Biological tissue resection device |
GB2406521B (en) * | 2003-10-03 | 2007-05-09 | Microsulis Ltd | Treatment of hollow anatomical structures |
WO2005048862A2 (en) | 2003-11-18 | 2005-06-02 | Scimed Life Systems, Inc. | System and method for tissue ablation |
GB2415630C2 (en) * | 2004-07-02 | 2007-03-22 | Microsulis Ltd | Radiation applicator and method of radiating tissue |
-
2006
- 2006-01-03 GB GB0600018A patent/GB2434314B/en not_active Expired - Fee Related
- 2006-12-15 CN CN2006800502779A patent/CN101631506B/en not_active Expired - Fee Related
- 2006-12-15 JP JP2008547872A patent/JP5318581B2/en active Active
- 2006-12-15 WO PCT/EP2006/012144 patent/WO2007076924A2/en active Application Filing
- 2006-12-15 AU AU2006332213A patent/AU2006332213B2/en not_active Ceased
- 2006-12-15 BR BRPI0620875-4A patent/BRPI0620875A2/en not_active IP Right Cessation
- 2006-12-15 US US12/158,831 patent/US20080294155A1/en not_active Abandoned
- 2006-12-15 CA CA002635316A patent/CA2635316A1/en not_active Abandoned
- 2006-12-15 KR KR1020087019019A patent/KR20080092402A/en not_active Application Discontinuation
- 2006-12-15 EP EP06829673.0A patent/EP1968469B8/en active Active
- 2006-12-18 TW TW095147386A patent/TW200740407A/en unknown
- 2006-12-27 US US11/646,141 patent/US20070203551A1/en not_active Abandoned
-
2008
- 2008-06-26 IL IL192469A patent/IL192469A0/en unknown
-
2015
- 2015-11-13 US US14/940,354 patent/US9907613B2/en active Active
Patent Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4612940A (en) * | 1984-05-09 | 1986-09-23 | Scd Incorporated | Microwave dipole probe for in vivo localized hyperthermia |
US6047216A (en) * | 1996-04-17 | 2000-04-04 | The United States Of America Represented By The Administrator Of The National Aeronautics And Space Administration | Endothelium preserving microwave treatment for atherosclerosis |
US6223085B1 (en) * | 1997-05-06 | 2001-04-24 | Urologix, Inc. | Device and method for preventing restenosis |
US20030088242A1 (en) * | 2001-11-02 | 2003-05-08 | Mani Prakash | High-strength microwave antenna assemblies |
US20030100894A1 (en) * | 2001-11-23 | 2003-05-29 | John Mahon | Invasive therapeutic probe |
US6706040B2 (en) * | 2001-11-23 | 2004-03-16 | Medlennium Technologies, Inc. | Invasive therapeutic probe |
US7311703B2 (en) * | 2003-07-18 | 2007-12-25 | Vivant Medical, Inc. | Devices and methods for cooling microwave antennas |
US20050245920A1 (en) * | 2004-04-30 | 2005-11-03 | Vitullo Jeffrey M | Cell necrosis apparatus with cooled microwave antenna |
Cited By (161)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9579152B2 (en) | 2001-11-02 | 2017-02-28 | Covidien Lp | High-strength microwave antenna assemblies |
US7862559B2 (en) | 2001-11-02 | 2011-01-04 | Vivant Medical, Inc. | High-strength microwave antenna assemblies and methods of use |
US8035570B2 (en) | 2001-11-02 | 2011-10-11 | Vivant Medical, Inc. | High-strength microwave antenna assemblies |
US10154880B2 (en) | 2001-11-02 | 2018-12-18 | Covidien Lp | High-strength microwave antenna assemblies |
US8643561B2 (en) | 2001-11-02 | 2014-02-04 | Covidien Lp | High-strength microwave antenna assemblies |
US9041616B2 (en) | 2001-11-02 | 2015-05-26 | Covidien Lp | High-strength microwave antenna assemblies |
US9549779B2 (en) | 2001-11-02 | 2017-01-24 | Covidien Lp | High-strength microwave antenna assemblies |
US9770295B2 (en) | 2003-06-23 | 2017-09-26 | Angiodynamics, Inc. | Radiation applicator for microwave medical treatment |
US10772682B2 (en) | 2003-06-23 | 2020-09-15 | Angiodynamics, Inc. | Radiation applicator for microwave medical treatment |
US7875024B2 (en) | 2003-07-18 | 2011-01-25 | Vivant Medical, Inc. | Devices and methods for cooling microwave antennas |
US9480528B2 (en) | 2003-07-18 | 2016-11-01 | Covidien Lp | Devices and methods for cooling microwave antennas |
US9468499B2 (en) | 2003-07-18 | 2016-10-18 | Covidien Lp | Devices and methods for cooling microwave antennas |
US9820814B2 (en) | 2003-07-18 | 2017-11-21 | Covidien Lp | Devices and methods for cooling microwave antennas |
US10405921B2 (en) | 2003-07-18 | 2019-09-10 | Covidien Lp | Devices and methods for cooling microwave antennas |
US9788896B2 (en) | 2004-07-02 | 2017-10-17 | Angiodynamics, Inc. | Radiation applicator and method of radiating tissue |
US8663213B2 (en) | 2005-05-10 | 2014-03-04 | Covidien Lp | Reinforced high strength microwave antenna |
US10537386B2 (en) | 2005-05-10 | 2020-01-21 | Covidien Lp | Reinforced high strength microwave antenna |
US7799019B2 (en) | 2005-05-10 | 2010-09-21 | Vivant Medical, Inc. | Reinforced high strength microwave antenna |
US11717347B2 (en) | 2005-05-10 | 2023-08-08 | Covidien Lp | Reinforced high strength microwave antenna |
US20060259024A1 (en) * | 2005-05-10 | 2006-11-16 | Roman Turovskiy | Reinforced high strength microwave antenna |
US8974452B2 (en) | 2005-05-10 | 2015-03-10 | Covidien Lp | Reinforced high strength microwave antenna |
US8012148B2 (en) | 2005-05-10 | 2011-09-06 | Vivant Medical, Inc. | Reinforced high strength microwave antenna |
US8192423B2 (en) | 2005-05-10 | 2012-06-05 | Vivant Medical, Inc. | Reinforced high strength microwave antenna |
US9186216B2 (en) | 2005-05-10 | 2015-11-17 | Covidien Lp | Reinforced high strength microwave antenna |
US7826904B2 (en) | 2006-02-07 | 2010-11-02 | Angiodynamics, Inc. | Interstitial microwave system and method for thermal treatment of diseases |
US11944376B2 (en) | 2006-03-24 | 2024-04-02 | Neuwave Medical, Inc. | Transmission line with heat transfer ability |
US10363092B2 (en) | 2006-03-24 | 2019-07-30 | Neuwave Medical, Inc. | Transmission line with heat transfer ability |
US11576723B2 (en) | 2006-07-14 | 2023-02-14 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US10376314B2 (en) | 2006-07-14 | 2019-08-13 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US11576722B2 (en) | 2006-07-14 | 2023-02-14 | 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 |
US11596474B2 (en) | 2006-07-14 | 2023-03-07 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US20080266203A1 (en) * | 2007-04-25 | 2008-10-30 | Vivant Medical, Inc. | Cooled helical antenna for microwave ablation |
US7998139B2 (en) | 2007-04-25 | 2011-08-16 | Vivant Medical, Inc. | Cooled helical antenna for microwave ablation |
US8353901B2 (en) | 2007-05-22 | 2013-01-15 | Vivant Medical, Inc. | Energy delivery conduits for use with electrosurgical devices |
US10271903B2 (en) | 2007-05-22 | 2019-04-30 | Covidien Lp | Energy delivery conduits for use with electrosurgical devices |
US8628523B2 (en) | 2007-05-22 | 2014-01-14 | Covidien Lp | Energy delivery conduits for use with electrosurgical devices |
US9808313B2 (en) | 2007-05-22 | 2017-11-07 | Covidien Lp | Energy delivery conduits for use with electrosurgical devices |
US9301802B2 (en) | 2007-05-22 | 2016-04-05 | Covidien Lp | Energy delivery conduits for use with electrosurgical devices |
US10987165B2 (en) | 2007-06-20 | 2021-04-27 | Covidien Lp | Reflective power monitoring for microwave applications |
US20080319434A1 (en) * | 2007-06-20 | 2008-12-25 | Rick Kyle R | Reflective power monitoring for microwave applications |
US9827043B2 (en) | 2007-06-20 | 2017-11-28 | Covidien Lp | Reflective power monitoring for microwave applications |
US9023024B2 (en) | 2007-06-20 | 2015-05-05 | Covidien Lp | Reflective power monitoring for microwave applications |
US20130317495A1 (en) * | 2007-06-28 | 2013-11-28 | Covidien Lp | Broadband microwave applicator |
US20090082762A1 (en) * | 2007-09-20 | 2009-03-26 | Ormsby Theodore C | Radio frequency energy transmission device for the ablation of biological tissues |
US20090163911A1 (en) * | 2007-12-21 | 2009-06-25 | Hong Cao | Thermally insulated irrigation catheter assembly |
US8221409B2 (en) * | 2007-12-21 | 2012-07-17 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Thermally insulated irrigation catheter assembly |
US10743934B2 (en) * | 2008-01-23 | 2020-08-18 | Covidien Lp | Choked dielectric loaded tip dipole microwave antenna |
US8945111B2 (en) | 2008-01-23 | 2015-02-03 | Covidien Lp | Choked dielectric loaded tip dipole microwave antenna |
US20150133908A1 (en) * | 2008-01-23 | 2015-05-14 | Covidien Lp | Choked dielectric loaded tip dipole microwave antenna |
EP2736122A1 (en) * | 2008-01-23 | 2014-05-28 | Covidien LP | Unbalanced dipole microwave antenna |
US20190000548A1 (en) * | 2008-01-23 | 2019-01-03 | Covidien Lp | Choked dielectric loaded tip dipole microwave antenna |
US20200360087A1 (en) * | 2008-01-23 | 2020-11-19 | Covidien Lp | Choked dielectric loaded tip dipole microwave antenna |
US10058384B2 (en) * | 2008-01-23 | 2018-08-28 | Covidien Lp | Choked dielectric loaded tip dipole microwave antenna |
US9861439B2 (en) | 2008-01-23 | 2018-01-09 | Covidien Lp | Choked dielectric loaded tip dipole microwave antenna |
US20090187180A1 (en) * | 2008-01-23 | 2009-07-23 | Vivant Medical, Inc. | Choked Dielectric Loaded Tip Dipole Microwave Antenna |
US8965536B2 (en) | 2008-03-03 | 2015-02-24 | Covidien Lp | Intracooled percutaneous microwave ablation probe |
US20090222002A1 (en) * | 2008-03-03 | 2009-09-03 | Vivant Medical, Inc. | Intracooled Percutaneous Microwave Ablation Probe |
US9198723B2 (en) | 2008-03-31 | 2015-12-01 | Covidien Lp | Re-hydration antenna for ablation |
US9750571B2 (en) | 2008-03-31 | 2017-09-05 | Covidien Lp | Re-hydration antenna for ablation |
US20090248006A1 (en) * | 2008-03-31 | 2009-10-01 | Paulus Joseph A | Re-Hydration Antenna for Ablation |
US8059059B2 (en) | 2008-05-29 | 2011-11-15 | Vivant Medical, Inc. | Slidable choke microwave antenna |
US8361062B2 (en) | 2008-05-29 | 2013-01-29 | Vivant Medical, Inc. | Slidable choke microwave antenna |
US20090295674A1 (en) * | 2008-05-29 | 2009-12-03 | Kenlyn Bonn | Slidable Choke Microwave Antenna |
US10022186B2 (en) | 2008-08-28 | 2018-07-17 | Covidien Lp | Microwave antenna with cooled handle |
US8251987B2 (en) | 2008-08-28 | 2012-08-28 | Vivant Medical, Inc. | Microwave antenna |
US9113932B1 (en) | 2008-08-28 | 2015-08-25 | Covidien Lp | Microwave antenna with choke |
US9375280B2 (en) | 2008-08-28 | 2016-06-28 | Covidien Lp | Microwave antenna with cooling system |
US11147620B2 (en) | 2008-08-28 | 2021-10-19 | Covidien Lp | Microwave antenna with cooled hub |
US9707038B2 (en) | 2008-08-28 | 2017-07-18 | Covidien Lp | Microwave antenna with cooled handle |
US20100053015A1 (en) * | 2008-08-28 | 2010-03-04 | Vivant Medical, Inc. | Microwave Antenna |
US9198725B2 (en) | 2008-08-28 | 2015-12-01 | Covidien Lp | Microwave antenna with choke |
US10188460B2 (en) | 2008-10-17 | 2019-01-29 | Covidien Lp | Choked dielectric loaded tip dipole microwave antenna |
US9113924B2 (en) | 2008-10-17 | 2015-08-25 | Covidien Lp | Choked dielectric loaded tip dipole microwave antenna |
US20100097284A1 (en) * | 2008-10-17 | 2010-04-22 | Vivant Medical, Inc. | Choked Dielectric Loaded Tip Dipole Microwave Antenna |
US8118808B2 (en) | 2009-03-10 | 2012-02-21 | Vivant Medical, Inc. | Cooled dielectrically buffered microwave dipole antenna |
US20100234839A1 (en) * | 2009-03-10 | 2010-09-16 | Vivant Medical, Inc. | Cooled Dielectrically Buffered Microwave Dipole Antenna |
US8832927B2 (en) | 2009-03-10 | 2014-09-16 | Covidien Lp | Method of manufacturing surgical antennas |
US9566115B2 (en) | 2009-07-28 | 2017-02-14 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US10357312B2 (en) | 2009-07-28 | 2019-07-23 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US11013557B2 (en) | 2009-07-28 | 2021-05-25 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US9877783B2 (en) | 2009-07-28 | 2018-01-30 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US20110060326A1 (en) * | 2009-09-09 | 2011-03-10 | Vivant Medical, Inc. | System and Method for Performing an Ablation Procedure |
US9113925B2 (en) * | 2009-09-09 | 2015-08-25 | Covidien Lp | System and method for performing an ablation procedure |
US9113926B2 (en) * | 2009-09-29 | 2015-08-25 | Covidien Lp | Management of voltage standing wave ratio at skin surface during microwave ablation |
US9572625B2 (en) | 2009-09-29 | 2017-02-21 | Covidien Lp | Flow rate monitor for fluid cooled microwave ablation probe |
US20110077637A1 (en) * | 2009-09-29 | 2011-03-31 | Vivant Medical, Inc. | Flow Rate Monitor for Fluid Cooled Microwave Ablation Probe |
US20110077638A1 (en) * | 2009-09-29 | 2011-03-31 | Vivant Medical, Inc. | Flow Rate Monitor For Fluid Cooled Microwave Ablation Probe |
US20110077636A1 (en) * | 2009-09-29 | 2011-03-31 | Vivant Medical, Inc. | Management of Voltage Standing Wave Ratio at Skin Surface During Microwave Ablation |
US8556889B2 (en) | 2009-09-29 | 2013-10-15 | Covidien Lp | Flow rate monitor for fluid cooled microwave ablation probe |
US10390882B2 (en) | 2009-09-29 | 2019-08-27 | Covidien Lp | Flow rate monitor for fluid cooled microwave ablation probe |
US9237927B2 (en) | 2009-09-29 | 2016-01-19 | Covidien Lp | Flow rate monitor for fluid cooled microwave ablation probe |
US9370399B2 (en) | 2009-09-29 | 2016-06-21 | Covidien Lp | Flow rate monitor for fluid cooled microwave ablation probe |
US8568398B2 (en) | 2009-09-29 | 2013-10-29 | Covidien Lp | Flow rate monitor for fluid cooled microwave ablation probe |
US10182866B2 (en) | 2009-09-29 | 2019-01-22 | Covidien Lp | Flow rate monitor for fluid cooled microwave ablation probe |
US10675089B2 (en) | 2009-09-29 | 2020-06-09 | Covidien Lp | Management of voltage standing wave ratio at skin surface during microwave ablation |
US20130197504A1 (en) * | 2009-10-06 | 2013-08-01 | Nigel Cronin | Medical devices and pumps therefor |
US9757197B2 (en) * | 2009-10-06 | 2017-09-12 | Angiodynamics, Inc. | Medical devices and pumps therefor |
US10405922B2 (en) * | 2009-10-06 | 2019-09-10 | Angiodynamics, Inc. | Medical devices and pumps therefor |
US9968401B2 (en) | 2009-12-18 | 2018-05-15 | Covidien Lp | Microwave ablation system with dielectric temperature probe |
US8882759B2 (en) | 2009-12-18 | 2014-11-11 | Covidien Lp | Microwave ablation system with dielectric temperature probe |
KR101173455B1 (en) | 2010-01-26 | 2012-08-14 | 서울대학교산학협력단 | Applicator with plural slots having each different size |
US8568404B2 (en) | 2010-02-19 | 2013-10-29 | Covidien Lp | Bipolar electrode probe for ablation monitoring |
US9839477B2 (en) | 2010-02-19 | 2017-12-12 | Covidien Lp | Bipolar electrode probe for ablation monitoring |
US20160045256A1 (en) * | 2010-04-26 | 2016-02-18 | 9234438 Canada Inc. | Electrosurgical Devices and Methods |
US11224475B2 (en) * | 2010-04-26 | 2022-01-18 | Medtronic Holding Company Sàrl | Electrosurgical device and methods |
US10448990B2 (en) | 2010-04-26 | 2019-10-22 | Medtronic Holding Company Sàrl | Electrosurgical device and methods |
US9788889B2 (en) * | 2010-04-26 | 2017-10-17 | Kyphon SÀRL | Electrosurgical devices and methods |
US11490960B2 (en) | 2010-05-03 | 2022-11-08 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US10603106B2 (en) | 2010-05-03 | 2020-03-31 | 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 |
US10524862B2 (en) | 2010-05-03 | 2020-01-07 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US9872729B2 (en) | 2010-05-03 | 2018-01-23 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US9549778B2 (en) | 2010-06-30 | 2017-01-24 | Covidien Lp | Adjustable tuning of a dielectrically loaded loop antenna |
US8740893B2 (en) | 2010-06-30 | 2014-06-03 | Covidien Lp | Adjustable tuning of a dielectrically loaded loop antenna |
US20180221090A1 (en) * | 2011-01-05 | 2018-08-09 | Covidien Lp | Energy-delivery devices with flexible fluid-cooled shaft, inflow / outflow junctions suitable for use with same, and systems including same |
US9198724B2 (en) * | 2011-04-08 | 2015-12-01 | Covidien Lp | Microwave tissue dissection and coagulation |
US10098697B2 (en) | 2011-04-08 | 2018-10-16 | Covidien Lp | Microwave tissue dissection and coagulation |
US20120259324A1 (en) * | 2011-04-08 | 2012-10-11 | Vivant Medical, Inc. | Microwave Tissue Dissection and Coagulation |
US10799290B2 (en) | 2011-04-08 | 2020-10-13 | Covidien Lp | Microwave tissue dissection and coagulation |
US11638607B2 (en) | 2011-12-21 | 2023-05-02 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US10667860B2 (en) | 2011-12-21 | 2020-06-02 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US9095360B2 (en) | 2012-04-06 | 2015-08-04 | Wisconsin Alumni Research Foundation | Feeding structure for dual slot microwave ablation probe |
WO2013151788A1 (en) * | 2012-04-06 | 2013-10-10 | Winsconsin Alumni Research Foundation | Feeding structure for dual slot microwave ablation probe |
US9192439B2 (en) | 2012-06-29 | 2015-11-24 | Covidien Lp | Method of manufacturing a surgical instrument |
US9901398B2 (en) | 2012-06-29 | 2018-02-27 | Covidien Lp | Microwave antenna probes |
US11510732B2 (en) | 2012-06-29 | 2022-11-29 | Covidien Lp | Microwave antenna probes |
US9333035B2 (en) | 2012-09-19 | 2016-05-10 | Denervx LLC | Cooled microwave denervation |
US10092352B2 (en) | 2012-09-19 | 2018-10-09 | Denervx LLC | Cooled microwave denervation |
US11786302B2 (en) | 2012-09-19 | 2023-10-17 | Denervx LLC | Cooled microwave denervation |
US10828102B2 (en) | 2012-12-17 | 2020-11-10 | Covidien Lp | Ablation probe with tissue sensing configuration |
US20140171932A1 (en) * | 2012-12-17 | 2014-06-19 | Covidien Lp | Ablation probe with tissue sensing configuration |
US9901399B2 (en) * | 2012-12-17 | 2018-02-27 | Covidien Lp | Ablation probe with tissue sensing configuration |
US9888956B2 (en) | 2013-01-22 | 2018-02-13 | Angiodynamics, Inc. | Integrated pump and generator device and method of use |
US11931016B2 (en) | 2013-03-07 | 2024-03-19 | Medtronic Holding Company Sàrl | Systems and methods for track coagulation |
US11864961B2 (en) | 2013-03-15 | 2024-01-09 | TriAgenics, Inc. | Therapeutic tooth bud ablation |
US11730564B2 (en) | 2013-03-15 | 2023-08-22 | TriAgenics, Inc. | Therapeutic tooth bud ablation |
US11576716B2 (en) | 2013-03-15 | 2023-02-14 | Medtronic Holding Company Sàrl | Electrosurgical mapping tools and methods |
US11399915B2 (en) | 2013-03-15 | 2022-08-02 | TriAgenics, Inc. | Therapeutic tooth bud ablation |
US9925004B2 (en) * | 2013-08-08 | 2018-03-27 | H.S.—Hospital Service S.P.A. | Microwave device for tissue ablation |
US20160199130A1 (en) * | 2013-08-08 | 2016-07-14 | H.S. - Hospital Service S.P.A. | Microwave Device For Tissue Ablation |
US10390881B2 (en) | 2013-10-25 | 2019-08-27 | Denervx LLC | Cooled microwave denervation catheter with insertion feature |
US10179029B2 (en) | 2014-01-24 | 2019-01-15 | Denervx LLC | Cooled microwave denervation catheter configuration and method |
US20170296269A1 (en) * | 2014-11-11 | 2017-10-19 | Nanjing Vison-China Medical Devices R & D Center | Manufacturing method for non-magnetic water-cooled microwave ablation needle |
US10874458B2 (en) * | 2014-11-11 | 2020-12-29 | Nanjing Vison-China Medical Devices R & D Center | Manufacturing method for non-magnetic water-cooled microwave ablation needle |
US10660691B2 (en) | 2015-10-07 | 2020-05-26 | Angiodynamics, Inc. | Multiple use subassembly with integrated fluid delivery system for use with single or dual-lumen peristaltic tubing |
US11678935B2 (en) | 2015-10-26 | 2023-06-20 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US10952792B2 (en) | 2015-10-26 | 2021-03-23 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US11213339B2 (en) | 2015-11-17 | 2022-01-04 | Medtronic Holding Company Sàrl | Spinal tissue ablation apparatus, system, and method |
US10531917B2 (en) | 2016-04-15 | 2020-01-14 | Neuwave Medical, Inc. | Systems and methods for energy delivery |
US11395699B2 (en) | 2016-04-15 | 2022-07-26 | Neuwave Medical, Inc. | Systems and methods for energy delivery |
US11751943B2 (en) | 2017-01-26 | 2023-09-12 | State University Research | Method for monitoring bronchoscopic-based microwave ablation and related system |
EP3573561A4 (en) * | 2017-01-26 | 2020-11-18 | Broncus Medical Inc. | Bronchoscopic-based microwave ablation system and method |
WO2018140816A1 (en) | 2017-01-26 | 2018-08-02 | Broncus Medical Inc. | Bronchoscopic-based microwave ablation system and method |
US11672596B2 (en) | 2018-02-26 | 2023-06-13 | Neuwave Medical, Inc. | Energy delivery devices with flexible and adjustable tips |
WO2020165375A1 (en) * | 2019-02-13 | 2020-08-20 | National University Of Ireland, Galway | An ablation probe |
US11832879B2 (en) | 2019-03-08 | 2023-12-05 | Neuwave Medical, Inc. | Systems and methods for energy delivery |
US11583337B2 (en) * | 2019-06-06 | 2023-02-21 | TriAgenics, Inc. | Ablation probe systems |
US11737824B2 (en) * | 2019-08-07 | 2023-08-29 | Biocompatibles Uk Limited | Microwave ablation probe |
WO2021026471A3 (en) * | 2019-08-07 | 2021-03-18 | Biocompatibles Uk Limited | Microwave ablation probe |
US20210038303A1 (en) * | 2019-08-07 | 2021-02-11 | Biocompatibles Uk Limited | Microwave ablation probe |
Also Published As
Publication number | Publication date |
---|---|
KR20080092402A (en) | 2008-10-15 |
AU2006332213A1 (en) | 2007-07-12 |
BRPI0620875A2 (en) | 2011-11-29 |
JP5318581B2 (en) | 2013-10-16 |
WO2007076924A3 (en) | 2007-08-30 |
IL192469A0 (en) | 2009-02-11 |
US20160262832A1 (en) | 2016-09-15 |
CN101631506A (en) | 2010-01-20 |
GB2434314B (en) | 2011-06-15 |
TW200740407A (en) | 2007-11-01 |
GB0600018D0 (en) | 2006-02-08 |
EP1968469B1 (en) | 2016-11-02 |
JP2009521967A (en) | 2009-06-11 |
US20080294155A1 (en) | 2008-11-27 |
US9907613B2 (en) | 2018-03-06 |
CA2635316A1 (en) | 2007-07-12 |
CN101631506B (en) | 2011-12-28 |
EP1968469A2 (en) | 2008-09-17 |
AU2006332213B2 (en) | 2013-01-10 |
GB2434314A (en) | 2007-07-25 |
WO2007076924A2 (en) | 2007-07-12 |
EP1968469B8 (en) | 2017-01-11 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US9907613B2 (en) | Radiation applicator and method of radiating tissue | |
US9788896B2 (en) | Radiation applicator and method of radiating tissue | |
JP2009521967A5 (en) | ||
US5556377A (en) | Medical probe apparatus with laser and/or microwave monolithic integrated circuit probe | |
JP5027439B2 (en) | Reinforced high-intensity microwave antenna | |
US7108696B2 (en) | Bone-treatment instrument and method | |
US5599295A (en) | Medical probe apparatus with enhanced RF, resistance heating, and microwave ablation capabilities | |
US20050245920A1 (en) | Cell necrosis apparatus with cooled microwave antenna | |
US9095360B2 (en) | Feeding structure for dual slot microwave ablation probe | |
MX2008008716A (en) | Radiation applicator and method of radiating tissue | |
AU2007202890A1 (en) | Bone-treatment instrument and method |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: MICROSULIS LTD., GREAT BRITAIN Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:BOIX-RIQUELME, MARIA J.;REEL/FRAME:019245/0989 Effective date: 20070330 |
|
AS | Assignment |
Owner name: MICROSULIS LTD., UNITED KINGDOM Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:CRONIN, NIGEL;REEL/FRAME:020051/0683 Effective date: 20070618 |
|
AS | Assignment |
Owner name: UK INVESTMENT ASSOCIATES LLC, NEVADA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:MICROSULIS LIMITED;REEL/FRAME:029491/0357 Effective date: 20070614 |
|
AS | Assignment |
Owner name: ANGIODYNAMICS, INC., NEW YORK Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:MICROSULIS MEDICAL LIMITED;REEL/FRAME:031228/0239 Effective date: 20130122 |
|
AS | Assignment |
Owner name: JPMORGAN CHASE BANK, N.A., AS ADMINISTRATIVE AGENT, ILLINOIS Free format text: SECURITY AGREEMENT;ASSIGNOR:ANGIODYNAMICS, INC.;REEL/FRAME:031315/0720 Effective date: 20130919 Owner name: JPMORGAN CHASE BANK, N.A., AS ADMINISTRATIVE AGENT Free format text: SECURITY AGREEMENT;ASSIGNOR:ANGIODYNAMICS, INC.;REEL/FRAME:031315/0720 Effective date: 20130919 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |
|
AS | Assignment |
Owner name: ANGIODYNAMICS, INC., NEW YORK Free format text: RELEASE BY SECURED PARTY;ASSIGNOR:JPMORGAN CHASE BANK, N.A., AS ADMINISTRATIVE AGENT;REEL/FRAME:040688/0540 Effective date: 20161107 |