US20040260282A1 - Multiple antenna ablation apparatus and method with multiple sensor feedback - Google Patents
Multiple antenna ablation apparatus and method with multiple sensor feedback Download PDFInfo
- Publication number
- US20040260282A1 US20040260282A1 US10/775,747 US77574704A US2004260282A1 US 20040260282 A1 US20040260282 A1 US 20040260282A1 US 77574704 A US77574704 A US 77574704A US 2004260282 A1 US2004260282 A1 US 2004260282A1
- Authority
- US
- United States
- Prior art keywords
- antenna
- introducer
- antennas
- ablation
- distal end
- 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
- 238000002679 ablation Methods 0.000 title claims abstract description 81
- 238000000034 method Methods 0.000 title claims description 17
- 238000009413 insulation Methods 0.000 claims description 20
- 238000001802 infusion Methods 0.000 claims description 12
- 238000011298 ablation treatment Methods 0.000 claims description 5
- 238000001816 cooling Methods 0.000 claims 1
- 230000001747 exhibiting effect Effects 0.000 claims 1
- 210000001519 tissue Anatomy 0.000 description 71
- 230000003902 lesion Effects 0.000 description 11
- 206010028980 Neoplasm Diseases 0.000 description 9
- 238000011282 treatment Methods 0.000 description 7
- 238000010438 heat treatment Methods 0.000 description 6
- 230000006870 function Effects 0.000 description 5
- 239000000463 material Substances 0.000 description 5
- 230000008859 change Effects 0.000 description 4
- 230000000694 effects Effects 0.000 description 4
- 239000000523 sample Substances 0.000 description 4
- 239000004952 Polyamide Substances 0.000 description 3
- 238000013019 agitation Methods 0.000 description 3
- 238000001514 detection method Methods 0.000 description 3
- 238000012544 monitoring process Methods 0.000 description 3
- 239000013307 optical fiber Substances 0.000 description 3
- 229920002647 polyamide Polymers 0.000 description 3
- 238000001356 surgical procedure Methods 0.000 description 3
- 206010020843 Hyperthermia Diseases 0.000 description 2
- 238000004873 anchoring Methods 0.000 description 2
- 230000006378 damage Effects 0.000 description 2
- 230000007423 decrease Effects 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 239000003814 drug Substances 0.000 description 2
- 230000036031 hyperthermia Effects 0.000 description 2
- 238000003384 imaging method Methods 0.000 description 2
- 229910001000 nickel titanium Inorganic materials 0.000 description 2
- 230000008569 process Effects 0.000 description 2
- 229940124597 therapeutic agent Drugs 0.000 description 2
- 238000002604 ultrasonography Methods 0.000 description 2
- 239000010963 304 stainless steel Substances 0.000 description 1
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 description 1
- 238000012369 In process control Methods 0.000 description 1
- 206010027476 Metastases Diseases 0.000 description 1
- 239000004642 Polyimide Substances 0.000 description 1
- 229910000589 SAE 304 stainless steel Inorganic materials 0.000 description 1
- 230000003466 anti-cipated effect Effects 0.000 description 1
- 239000002246 antineoplastic agent Substances 0.000 description 1
- 230000015572 biosynthetic process Effects 0.000 description 1
- 238000009529 body temperature measurement Methods 0.000 description 1
- 238000009835 boiling Methods 0.000 description 1
- 238000003763 carbonization Methods 0.000 description 1
- 210000004027 cell Anatomy 0.000 description 1
- 210000000170 cell membrane Anatomy 0.000 description 1
- 230000001413 cellular effect Effects 0.000 description 1
- 239000004020 conductor Substances 0.000 description 1
- 239000000994 contrast dye Substances 0.000 description 1
- 239000002872 contrast media Substances 0.000 description 1
- 229910052802 copper Inorganic materials 0.000 description 1
- 239000010949 copper Substances 0.000 description 1
- 230000008878 coupling Effects 0.000 description 1
- 238000010168 coupling process Methods 0.000 description 1
- 238000005859 coupling reaction Methods 0.000 description 1
- 230000001086 cytosolic effect Effects 0.000 description 1
- 229940127089 cytotoxic agent Drugs 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 238000011161 development Methods 0.000 description 1
- 102000038379 digestive enzymes Human genes 0.000 description 1
- 108091007734 digestive enzymes Proteins 0.000 description 1
- 230000003028 elevating effect Effects 0.000 description 1
- 230000005284 excitation Effects 0.000 description 1
- 239000000835 fiber Substances 0.000 description 1
- 239000012530 fluid Substances 0.000 description 1
- 230000001900 immune effect Effects 0.000 description 1
- 238000010965 in-process control Methods 0.000 description 1
- 239000012212 insulator Substances 0.000 description 1
- 150000002500 ions Chemical class 0.000 description 1
- 230000004807 localization Effects 0.000 description 1
- 238000012423 maintenance Methods 0.000 description 1
- 238000007726 management method Methods 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 230000007246 mechanism Effects 0.000 description 1
- 239000002184 metal Substances 0.000 description 1
- 229910052751 metal Inorganic materials 0.000 description 1
- 230000009401 metastasis Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 210000000633 nuclear envelope Anatomy 0.000 description 1
- 238000010899 nucleation Methods 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
- 230000035699 permeability Effects 0.000 description 1
- 229920001721 polyimide Polymers 0.000 description 1
- 102000004169 proteins and genes Human genes 0.000 description 1
- 108090000623 proteins and genes Proteins 0.000 description 1
- 230000005855 radiation Effects 0.000 description 1
- 230000029058 respiratory gaseous exchange Effects 0.000 description 1
- 239000007787 solid Substances 0.000 description 1
- 229910001220 stainless steel Inorganic materials 0.000 description 1
- 239000010935 stainless steel Substances 0.000 description 1
- 238000003786 synthesis reaction Methods 0.000 description 1
- 230000003685 thermal hair damage Effects 0.000 description 1
- 230000000472 traumatic effect Effects 0.000 description 1
- 238000012800 visualization Methods 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/06—Electrodes for high-frequency therapy
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B18/1477—Needle-like probes
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B18/1482—Probes or electrodes therefor having a long rigid shaft for accessing the inner body transcutaneously in minimal invasive surgery, e.g. laparoscopy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/1815—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/40—Applying electric fields by inductive or capacitive coupling ; Applying radio-frequency signals
- A61N1/403—Applying electric fields by inductive or capacitive coupling ; Applying radio-frequency signals for thermotherapy, e.g. hyperthermia
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/1206—Generators therefor
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B18/1402—Probes for open surgery
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B18/1485—Probes or electrodes therefor having a short rigid shaft for accessing the inner body through natural openings
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B18/1492—Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00017—Electrical control of surgical instruments
- A61B2017/00022—Sensing or detecting at the treatment site
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00017—Electrical control of surgical instruments
- A61B2017/00022—Sensing or detecting at the treatment site
- A61B2017/00084—Temperature
- A61B2017/00101—Temperature using an array of thermosensors
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
- A61B2018/00011—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00005—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
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00184—Moving parts
- A61B2018/00196—Moving parts reciprocating lengthwise
-
- 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
- A61B2018/00273—Anchoring means for temporary attachment of a device to tissue
-
- 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
- A61B2018/00273—Anchoring means for temporary attachment of a device to tissue
- A61B2018/00279—Anchoring means for temporary attachment of a device to tissue deployable
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
- A61B2018/00452—Skin
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
- A61B2018/00452—Skin
- A61B2018/00476—Hair follicles
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00666—Sensing and controlling the application of energy using a threshold value
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00666—Sensing and controlling the application of energy using a threshold value
- A61B2018/00678—Sensing and controlling the application of energy using a threshold value upper
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00696—Controlled or regulated parameters
- A61B2018/00702—Power or energy
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00696—Controlled or regulated parameters
- A61B2018/00702—Power or energy
- A61B2018/00708—Power or energy switching the power on or off
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00696—Controlled or regulated parameters
- A61B2018/00726—Duty cycle
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00696—Controlled or regulated parameters
- A61B2018/00744—Fluid flow
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00696—Controlled or regulated parameters
- A61B2018/00761—Duration
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00773—Sensed parameters
- A61B2018/00779—Power or energy
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00773—Sensed parameters
- A61B2018/00791—Temperature
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00773—Sensed parameters
- A61B2018/00791—Temperature
- A61B2018/00797—Temperature measured by multiple temperature sensors
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00773—Sensed parameters
- A61B2018/00827—Current
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00773—Sensed parameters
- A61B2018/00875—Resistance or impedance
-
- 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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00773—Sensed parameters
- A61B2018/00892—Voltage
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/1206—Generators therefor
- A61B2018/124—Generators therefor switching the output to different electrodes, e.g. sequentially
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/1206—Generators therefor
- A61B2018/1246—Generators therefor characterised by the output polarity
- A61B2018/1253—Generators therefor characterised by the output polarity monopolar
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/1206—Generators therefor
- A61B2018/1246—Generators therefor characterised by the output polarity
- A61B2018/126—Generators therefor characterised by the output polarity bipolar
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B2018/1405—Electrodes having a specific shape
- A61B2018/1425—Needle
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B2018/1405—Electrodes having a specific shape
- A61B2018/1425—Needle
- A61B2018/143—Needle multiple 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
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B2018/1405—Electrodes having a specific shape
- A61B2018/1425—Needle
- A61B2018/1432—Needle curved
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B2018/1405—Electrodes having a specific shape
- A61B2018/1435—Spiral
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B2018/1472—Probes or electrodes therefor for use with liquid electrolyte, e.g. virtual electrodes
-
- 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
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B18/16—Indifferent or passive electrodes for grounding
- A61B2018/162—Indifferent or passive electrodes for grounding located on the probe body
-
- 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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2218/00—Details of surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2218/001—Details of surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body having means for irrigation and/or aspiration of substances to and/or from the surgical site
- A61B2218/002—Irrigation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0067—Catheters; Hollow probes characterised by the distal end, e.g. tips
- A61M25/0068—Static characteristics of the catheter tip, e.g. shape, atraumatic tip, curved tip or tip structure
- A61M25/007—Side holes, e.g. their profiles or arrangements; Provisions to keep side holes unblocked
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M3/00—Medical syringes, e.g. enemata; Irrigators
- A61M3/02—Enemata; Irrigators
- A61M3/0279—Cannula; Nozzles; Tips; their connection means
-
- 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
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Surgery (AREA)
- Engineering & Computer Science (AREA)
- Animal Behavior & Ethology (AREA)
- Public Health (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Veterinary Medicine (AREA)
- Biomedical Technology (AREA)
- General Health & Medical Sciences (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Physics & Mathematics (AREA)
- Heart & Thoracic Surgery (AREA)
- Otolaryngology (AREA)
- Electromagnetism (AREA)
- Radiology & Medical Imaging (AREA)
- Plasma & Fusion (AREA)
- Surgical Instruments (AREA)
Abstract
Description
- This application is a continuation-in-part of U.S. patent application Ser. No. 08/515,379, filed Aug. 15, 1995, entitled “Multiple Antenna Ablation Apparatus”, incorporated herein by reference.
- 1. Field of the Invention
- This invention relates generally to a treatment and ablation apparatus that includes a primary antenna inserted into or adjacent to a selected body mass, such as a tumor, with one or more side deployed secondary antennas which are actively coupled to the primary antenna, and more particularly to a multiple antenna RF treatment and ablation apparatus with one or more secondary antennas actively coupled to the primary antenna, with the primary antenna coupled to a feedback control device and energy source.
- 2. Description of the Related Art
- Current open procedures for treatment of tumors are extremely disruptive and cause a great deal of damage to healthy tissue. During the surgical procedure, the physician must exercise care in not cutting the tumor in a manner that creates seeding of the tumor, resulting in metastasis. In recent years, development of products has been directed with an emphasis on minimizing the traumatic nature of traditional surgical procedures.
- There has been a relatively significant amount of activity in the area of hyperthermia as a tool for treatment of tumors. It is known that elevating the temperature of tumors is helpful in the treatment and management of cancerous tissues. The mechanisms of selective treatment are not completely understood. However, four cellular effects of hyperthermia on cancerous tissue have been proposed, (i) changes in cell or nuclear membrane permeability or fluidity, (ii) cytoplasmic lysomal disintegration, causing release of digestive enzymes, (iii) protein thermal damage affecting cell respiration and the synthesis of DNA or RNA and (iv) potential excitation of immunologic systems. Treatment methods for applying heat to tumors include the use of direct contact radio-frequency (RF) applicators, microwave radiation, inductively coupled RF fields, ultrasound, and a variety of simple thermal conduction techniques.
- Among the problems associated with all of these procedures is the requirement that highly localized heat be produced at depths of several centimeters beneath the surface of the skin. RF applications may be used at depth during surgery. However, the extent of localization is generally poor, with the result that healthy tissue may be harmed.
- With RF lesion making, a high frequency alternating current flows from the electrode into the tissue. Ionic agitation is produced in the region of tissue about the electrode tip as the ions attempt to follow the directional variations of the alternating current. This agitation results in frictional heating so that the tissue about the electrode, rather than the electrode itself, is the primary source of heat. Tissue heat generated is produced by the flow of current through the electrical resistance offered by the tissue. The greater this resistance, the greater the heat generated.
- Lesion size ultimately is governed by tissue temperature. Some idea of tissue temperature can be obtained by monitoring the temperature at an electrode or probe tip, usually with a thermistor. RF lesion heat is generated within the tissue, the temperature monitored will be the resultant heating of the electrode by the lesion. RF lesion heat is generated within the tissue, the temperature monitored is the resultant heating of the probe by the lesion. A temperature gradient extends from the lesion to the probe tip, so that the probe tip is slightly cooler than the tissue immediately surrounding it, but substantially hotter than the periphery of the lesion because of the rapid attenuation of heating effect with distance.
- Current spreads out radially from the electrode tip, so that current density is greatest next to the tip, and decreases progressively at distances from it. The frictional heat produced from ionic agitation is proportional to current, i.e., ionic density. Therefore, the heating effect is greatest next to the electrode and decreases with distance from it. One consequence of this is that lesions can inadvertently be made smaller than anticipated for a given electrode size if the RF current level is too high. There must be time for equilibrium heating of tissue to be reached, especially at the center of the desired lesion volume. If the current density is too high, the tissue temperature next to the electrode rapidly exceeds desired levels and carbonization and boiling occurs in a thin tissue shell surrounding the electrode tip.
- A need exists for an ablation apparatus with an electromagnetic energy source and a monopolar multiple antenna device. There is a further need for a monopolar multiple antenna device with a primary antenna, and one or more secondary antennas that are positioned in a lumen of the primary antenna, laterally deployable from the primary antenna into a selected tissue mass, with both antennas electromagnetically coupled to an electromagnetic energy source. It would be desirable to provide a monopolar method to ablate a selected tissue mass by introducing the primary antenna into the selected mass, deploying a distal end of the secondary antenna into the selected mass, and applying electromagnetic energy to the primary and secondary antennas.
- Accordingly, it is an object of the invention to provide an ablation device which includes a monopolar multiple antenna.
- Another object of the invention is to provide an ablation apparatus with a monopolar multiple antenna device including a primary antenna that pierces and advances through tissue, a secondary electrode positioned in a primary antenna lumen that is laterally deployable from the primary antenna into a selected tissue mass.
- Yet another object of the invention is to provide an ablation apparatus with a monopolar multiple antenna device, including primary and secondary antennas that are each electromagnetically coupled to an electromagnetic energy source.
- A further object of the invention is to provide a method for ablating a selected tissue mass utilizing a monopolar multiple antenna device.
- These and other objectives are achieved in an ablation treatment apparatus. The apparatus includes an ablation energy source producing an electromagnetic energy output. A monopolar multiple antenna device is included and has a primary antenna with a longitudinal axis, a central lumen and a distal end, and a secondary antenna with a distal end. The secondary antenna is deployed from the primary antenna central lumen in a lateral direction relative to the longitudinal axis. The primary antenna and secondary antennas are each electromagnetically coupled to the electromagnetic energy source.
- In another embodiment, a method of ablating a selected tissue mass is provided utilizing a monopolar multiple antenna device.
- The monopolar multiple antenna device can be an RF antenna, a microwave antenna, a short wave antenna and the like. At least two secondary antennas can be included and laterally deployed from the primary antenna. The secondary antenna is retractable into the primary antenna, permitting repositioning of the primary antenna. When the multiple antenna is an RF antenna, it can be operated in monopolar or bipolar modes, and is capable of switching between the two.
- One or more sensors may be positioned at an interior or exterior of the primary or secondary antennas to detect impedance or temperature. A feedback control system is coupled to each of the sensors, the electromagnetic energy source and the primary and secondary antennas.
- An insulation sleeve can be positioned around the primary and secondary antennas. Another sensor is positioned at the distal end of the insulation sleeve surrounding the primary antenna.
- The feedback control device can detect impedance or temperature at a sensor. In some embodiments, the feedback control system can include a multiplexer. Further, the feedback control system can provide an ablation energy output for a selected length of time, adjust ablation energy output and reduce or cut off the delivery of the ablation energy output to the antennas. The feedback control system can include a temperature detection circuit which provides a control signal representative of temperature or impedance detected at any of the sensors. The feedback control system can also include a microprocessor connected to the temperature detection circuit. Initially, temperature, ablation duration and energy level are selected and manually input into the feedback control system. As process parameters change, the initial manually input values are then automatically modified by the feedback control system to achieve the desired level of ablation without impeding out, and minimize the ablation of non-targeted tissue.
- Further, the multiple antenna device can be a multi-modality apparatus. One or all of the antennas can be hollow to receive an infusion medium from an infusion source and introduce the infusion medium into the targeted tissue mass.
- FIG. 1 is a perspective view of the multiple antenna ablation apparatus of the present invention illustrating a primary antenna and a single laterally deployed secondary antenna.
- FIG. 2 is a perspective view of a conic geometric ablation achieved with the apparatus of FIG. 1.
- FIG. 3 is a perspective view of the multiple antenna ablation apparatus of the present invention with two secondary antennas.
- FIG. 4 is a perspective view illustrating the adjacent positioning of the multiple antenna ablation apparatus next to a selected tissue mass.
- FIG. 5 is a perspective view illustrating the positioning of the multiple antenna ablation apparatus in the center of a selected tissue mass, and the creation of a cylindrical ablation.
- FIG. 6(a) is a perspective view of the multiple antenna ablation of the present invention illustrating two secondary antennas which provide a retaining and gripping function.
- FIG. 6(b) is a perspective view of the multiple antenna ablation of the present invention illustrating three secondary antennas which provide a retaining and gripping function.
- FIG. 6(c) is a cross-sectional view of the apparatus of FIG. 6(b) taken along the lines 6(c)-6(c).
- FIG. 7 is a perspective view of the multiple antenna ablation of the present invention illustrating the deployment of three secondary antennas from a distal end of the insulation sleeve surrounding the primary antenna.
- FIG. 8 is a perspective view of the multiple antenna ablation of the present invention illustrating the deployment of two secondary antennas from the primary antenna, and the deployment of three secondary antennas from the distal end of the insulation sleeve surrounding the primary antenna.
- FIG. 9 is a block diagram illustrating the inclusion of a controller, energy source and other electronic components of the present invention.
- FIG. 10 is a block diagram illustrating an analog amplifier, analog multiplexer and microprocessor used with the present invention.
- The present invention provides an ablation treatment apparatus which includes an ablation energy source producing an electromagnetic energy output. A monopolar multiple antenna device is included and has a primary antenna with a longitudinal axis, a central lumen and a distal end, and a secondary antenna with a distal end. The secondary antenna is deployed from the primary antenna central lumen in a lateral direction relative to the longitudinal axis. The primary antenna and secondary antennas are each electromagnetically coupled to the electromagnetic energy source.
- As shown in FIG. 1, an
ablation treatment apparatus 10 includes a monopolarmultiple antenna device 12. Monopolarmultiple antenna device 12 includes aprimary antenna 14, and one or moresecondary antennas 16, which are typically electrodes.Secondary antennas 16 are initially positioned in a primary antenna lumen whenprimary antenna 14 is advanced through tissue. Whenprimary antenna 14 reaches a selected tissue ablation site in a selected tissue mass, including but not limited to a solid lesion,secondary antennas 16 are laterally deployed from the primary antenna lumen and into the selected tissue mass. Ablation proceeds from the interior of the selected tissue mass in a direction towards a periphery of the selected tissue mass. - Each primary and
secondary antenna secondary antennas Primary antenna 14 can be moved up and down, rotated about its longitudinal axis, and moved back and forth, in order to define, along with sensors, the periphery or boundary of the selected tissue mass, including but not limited to a tumor. This provides a variety of different geometries, not always symmetrical, that can be ablated. The ablation can be between the ablation surfaces of primary andsecondary antennas -
Primary antenna 14 is constructed so that it can be introduced percutaneously or laparoscopically through tissue without an introducer.Primary antenna 14 combines the function of an introducer and an electrode. - In one embodiment,
primary antenna 14 can have a. sharpeneddistal end 14′ to assist introduction through tissue. Eachsecondary antenna 16 has adistal end 16′ that is constructed to be less structurally rigid thanprimary antenna 14.Distal end 16′ is that section ofsecondary antenna 16 that. is advanced from thelumen antenna 14 and into the selected tissue mass. Distal end is typically less structurally rigid thatprimary antenna 14. However, even though sections ofsecondary antenna 16 which are not advanced through the selected tissue mass may be less structurally rigid thanprimary antenna 14. - Structurally rigidity is determined by, (i) choosing different materials for
antenna 14 anddistal end 16′ or some greater length ofsecondary antenna 16, (ii) using the same material but having less of it forsecondary antenna 16 ordistal end 16′, e.g.,secondary antenna 16 ordistal end 16′ is not as thick asprimary electrode 14, or (iii) including another material in one of theantennas - Primary and
secondary antennas secondary electrode 16 can be made of a shaped memory metal, such as NiTi, commercially available from Raychem Corporation, Menlo Park, Calif. - Each of primary or
secondary antennas ablation treatment apparatus 10, and more particularlymultiple antenna device 12, can be introduced through a guide to the desired tissue mass site. - An
insulation sleeve 18 may be positioned around an exterior of one or both of the primary andsecondary antennas insulation sleeve 18 is adjustably positioned so that the length of an antenna ablation surface can be varied. Eachinsulation sleeve 18 surrounding aprimary antenna 14 can include one or more apertures. This permits the introduction of asecondary antenna 16 throughprimary antenna 14 andinsulation sleeve 18. - In one embodiment,
insulation sleeve 18 can comprise a polyamide material. Asensor 24 may be positioned on top ofpolyimide insulation sleeve 18. Thepolyamide insulation sleeve 18 is semi-rigid.Sensor 24 can lay down substantially along the entire length ofpolyamide insulation sleeve 18.Primary antenna 14 is made of a stainless-steel hypodermic tubing with 2 cm of exposed ablation surface.Secondary antennas 16 have distal ends 16′ that are made of - NiTi hypodermic tubing. A handle is included with markings to show the varying distance of
secondary antennas 16 fromprimary antenna 14. Fluid infusion is delivered through a Luer port at a side of the handle. Type-T thermocouples are positioned at distal ends 16′. - An
energy source 20 is connected tomultiple antenna device 12 with one ormore cables 22.Energy source 20 can be an RF source, microwave source, short wave source, laser source and the like.Multiple antenna device 12 can be comprised of primary andsecondary antennas Energy source 20 may be a combination RF/microwave box. Further a laser optical fiber, coupled to alaser source 20 can be introduced through one or both of primary orsecondary antennas secondary antennas -
Antennas energy source 20. The coupling can be direct fromenergy source 20 to eachantenna antennas energy source 20. - One or
more sensors 24 may be positioned on at least a portion of interior or exterior surfaces ofprimary antenna 14,secondary antenna 16 orinsulation sleeve 18. Preferablysensors 24 are positioned at primary antennadistal end 14′, secondary antennadistal end 16′ and insulation sleevedistal end 18′.Sensors 24 permit accurate measurement of temperature at a tissue site in order to determine, (i) the extent of ablation, (ii) the amount of ablation, (iii) 25 whether or not further ablation is needed and (iv) the boundary or periphery of the ablated mass. Further,sensors 24 prevent non-targeted tissue from being destroyed or ablated. -
Sensors 24 are of conventional design, including but not limited to thermistors, thermocouples, resistive wires, and the like. Suitablethermal sensors 24 include a T type thermocouple with copper constantene, J type, E type, K type, fiber optics, resistive wires, thermocouple IR detectors, and the like. It will be appreciated thatsensors 24 need not be thermal sensors. -
Sensors 24 measure temperature and/or impedance to permit monitoring and a desired level of ablation to be achieved without destroying too much tissue. This reduces damage to tissue surrounding the targeted mass to be ablated. By monitoring the temperature at various points within the interior of the selected tissue mass, a determination of the selected tissue mass periphery can be made, as well as a determination of when ablation is complete. If at anytime sensor 24 determines that a desired ablation temperature is exceeded, then an appropriate feedback signal is received atenergy source 20 which then regulates the amount of energy delivered to primary and/orsecondary antennas - Thus the geometry of the ablated mass is selectable and controllable. Any number of different ablation geometries can be achieved. This is a result of having variable lengths for
primary antenna 14 andsecondary antenna 16 ablation surfaces as well as the inclusion of sensors. 24. - Preferably,
distal end 16′ is laterally deployed relative to a longitudinal axis ofprimary antenna 14 out of anaperture 26 formed inprimary antenna 14.Aperture 26 is atdistal end 14′ or formed in a side of an exterior ofantenna 14. - In one embodiment, a method for creating an ablation volume in a selected tissue mass includes; providing a monopolar ablation device with a primary antenna, a secondary antenna with a distal end, and an energy source electromagnetically coupled to both antennas. A ground pad electrode is also included. The primary antenna is inserted into the selected tissue mass with the secondary antenna distal end positioned in the primary antenna lumen. The secondary antenna distal end is advanced out of the primary antenna lumen into the selected tissue mass in a lateral direction relative to a longitudinal axis of the primary antenna. Electromagnetic energy is delivered from one of a primary antenna ablation surface, a secondary antenna ablation surface or both to the selected tissue mass. This creates an ablation volume in the selected tissue mass.
- There is wide variation in the amount of deflection of
secondary antenna 16. For example,secondary antenna 16 can be deflected a few degrees from the longitudinal axis ofprimary antenna 14, or secondary antenna can be deflected in any number of geometric configurations, including but not limited to a “J” hook. Further,secondary antenna 16 is capable of being introduced from primary antenna 14 a few millimeters from primary antenna, or a much larger distance. Ablation bysecondary antenna 16 can begin a few millimeters away fromprimary antenna 14, orsecondary electrode 16 can be advanced a greater distance fromprimary antenna 14 and at that point the initial ablation bysecondary antenna 16 begins. - A number of parameters permit ablation of selected tissue masses, including but not limited to tumors, of different size and shapes including, a series of ablations having primary and
secondary antennas sensors 24 and the use of the feedback control system. - As illustrated in FIG. 2,
primary antenna 14 has been introduced into a selectedtissue mass 28. One or more secondary antennas are positioned within a primary antenna lumen asprimary antenna 14 is introduced into and through the selected tissue mass. Subsequently, secondary antennadistal end 16′ is advanced out ofaperture 26 and into selectedtissue mass 28.Insulation sleeves 18 are adjusted for primary andsecondary antennas antenna 16 in a monopolar mode (RF), or alternatively,multiple antenna device 12 can be operated in a bipolar mode (RF).Multi antenna device 12 can be switched between monopolar and bipolar operation and has multiplexing capability betweenantennas distal end 16′ is retracted back intoprimary antenna 14, and primary antenna is then rotated. Secondary antennadistal end 16′ is then introduced into selectedtissue mass 28. Secondary antenna may be introduced a short distance into selectedtissue mass 28 to ablate a small area. It can then be advanced further into any number of times to create more ablation zones. Again, secondary antennadistal end 16′ is retracted back intoprimary antenna 14, andprimary antenna 14 can be, (i) rotated again, (ii) moved along a longitudinal axis of selectedtissue mass 28 to begin another series of ablations with secondary antennadistal end 16′ being introduced and retracted in and out ofprimary antenna 14, or (iii) removed from selectedtissue mass 28. A number of parameters permit ablation of selectedtissue masses 28 of different sign and shapes including a series of ablations having primary andsecondary antennas sensor 24. - In FIG. 3, two
secondary antennas 16 are each deployed out ofdistal end 14′ and introduced into selectedtissue mass 28.Secondary antennas 16 form a plane and the area of ablation extends between the ablation surfaces of primary andsecondary antennas Primary antenna 14 can be introduced in an adjacent relationship to selectedtissue mass 28. This particular deployment is particularly useful for small selectedtissue masses 28, or where piercing selectedtissue mass 28 is not desirable.Primary antenna 14 can be rotated, withsecondary antennas 16 retracted into a central lumen ofprimary antenna 14, and another ablation volume defined between the twosecondary antennas 16 is created. Further,primary electrode 14 can be withdrawn from its initial position adjacent to selectedtissue mass 28, repositioned to another position adjacent to selectedtissue mass 28, andsecondary antennas 16 deployed to begin another ablation cycle. Any variety of different positionings may be utilized to create a desired ablation geometry for selected tissue mass of different geometries and sizes. - In FIG. 4, three
secondary antennas 16 are introduced into selectedtissue mass 28. The effect is the creation of an ablation volume without leaving non-ablated areas between antenna ablation surfaces. The ablation is complete. - Referring now to FIG. 5, a center of selected
tissue mass 28 is pierced byprimary antenna 14,secondary antennas 16 are laterally deployed and retracted,primary antenna 14 is rotated,secondary antennas 16 are deployed and retracted, and so on until a cylindrical ablation volume is achieved.Multiple antenna device 12 can be operated in the bipolar mode between the twosecondary antennas 16, or between asecondary antenna 16 andprimary antenna 14. Alternatively,multiple antenna device 12 can be operated in a monopolar mode. -
Secondary antennas 16 can serve the additional function of anchoringmultiple antenna device 12 in a selected mass, as illustrated in FIGS. 6(a) and 6(b). In FIG. 6(a) one or bothsecondary antennas 16 are used to anchor and positionprimary antenna 14. Further, one or bothsecondary antennas 16 are also used to ablate tissue. In FIG. 6(b), three secondary antennas are deployed and anchorprimary antenna 14. - FIG. 6(c) illustrates the infusion capability of
multiple antenna device 12. Threesecondary antennas 16 are positioned in acentral lumen 14″ ofprimary antenna 14. One or more of thesecondary antennas 16 can also include a central lumen coupled to an infusion source.Central lumen 14″ is coupled to an infusion source and delivers a variety of infusion mediums to selected places both within and outside of the targeted ablation mass. Suitable infusion mediums include but are not limited to, therapeutic agents, conductivity enhancement mediums, contrast agents or dyes, and the like. An example of a therapeutic agent is a chemotherapeutic agent. - As shown in FIG. 7
insulation sleeve 18 can include one or more lumens for receivingsecondary antennas 16 which are deployed out of an insulation sleevedistal end 18′. FIG. 8 illustrates twosecondary antennas 16 - being introduced out of insulation sleeve
distal end 18′, and twosecondary antennas 16 introduced throughapertures 26 formed inprimary antenna 14. As illustrated, the secondary electrodes introduced throughapertures 26 provide an anchoring function. It will be appreciated that FIG. 8 illustrates howsecondary antennas 16 can have a variety of different geometric configurations inmultiple antenna device 12. - A feedback control system29 is connected to
energy source 20,sensors 24 andantennas sensors 24 and the amount of electromagnetic energy received byantennas more sensors 24. A microprocessor can be connected to the temperature control circuit. - The following discussion pertains particularly to the use of an RF energy source and RF
multiple antenna device 12. It will be appreciated that devices similar to those associated with RFmultiple antenna device 12 can be utilized with laser optical fibers, microwave devices and the like. - Referring now to FIG. 9, all or portions of feedback control system29 are illustrated. Current delivered through primary and
secondary antennas current sensor 30. Voltage is measured byvoltage sensor 32. Impedance and power are then calculated at power andimpedance calculation device 34. These values can then be displayed at user interface anddisplay 36. Signals representative of power and impedance values are received bycontroller 38. A control signal is generated bycontroller 38 that is proportional to the difference between an actual measured value, and a desired value. The control signal is used bypower circuits 40 to adjust the power output in an appropriate amount in order to maintain the desired power delivered at the respective primary and/orsecondary antennas - In a similar manner, temperatures detected at
sensors 24 provide feedback for maintaining a selected power. The actual temperatures are measured at temperature measurement device 42, and the temperatures are displayed at user interface anddisplay 36. A control signal is generated bycontroller 38 that is proportional to the difference between an actual measured temperature, and a desired temperature. The control signal is used bypower circuits 40 to adjust the power output in an appropriate amount in order to maintain the desired temperature delivered at therespective sensor 24. A multiplexer can be included to measure current, voltage and temperature, at thenumerous sensors 24, and energy is delivered betweenprimary antenna 14 andsecondary antennas 16. -
Controller 38 can be a digital or analog controller, or a computer with software. When controller 3 8 is a computer it can include a CPU coupled through a system bus. On this system can be a keyboard, a disk drive, or other non-volatile memory systems, a display, and other peripherals, as are known in the art. Also coupled to the bus are a program memory and a data memory. - User interface and
display 36 includes operator controls and a display.Controller 38 can be coupled to imaging systems, including but not limited to ultrasound, CT scanners, X-ray, MRI, mammographic X-ray and the like. Further, direct visualization and tactile imaging can be utilized. - The output of
current sensor 30 andvoltage sensor 32 is used bycontroller 38 to maintain a selected power level at primary andsecondary antennas controller 38, and a preset amount of energy to be delivered can also be profiled. - Circuitry, software and feedback to
controller 38 result in process control, and the maintenance of the selected power, and are used to change, (i) the selected power, including RF, microwave, laser and the like, (ii) the duty cycle (on-off and wattage), (iii) bipolar or monopolar energy delivery and (iv) infusion medium delivery, including flow rate and pressure. These process variables are controlled and varied, while maintaining the desired delivery of power independent of changes in voltage or current, based on temperatures monitored atsensors 24. - Referring now to FIG. 10,
current sensor 30 andvoltage sensor 32 are connected to the input of ananalog amplifier 44.Analog amplifier 44 can be a conventional differential amplifier circuit for use withsensors 24. The output ofanalog amplifier 44 is sequentially connected by ananalog multiplexer 46 to the input of A/D converter 48. The output ofanalog amplifier 44 is a voltage which represents the respective sensed temperatures. Digitized amplifier output voltages are supplied by A/D converter 48 to amicroprocessor 50.Microprocessor 50 may be Model No. 68HCII available from Motorola. However, it will be appreciated that any suitable microprocessor or general purpose digital or analog computer can be used to calculate impedance or temperature. -
Microprocessor 50 sequentially receives and stores digital representations of impedance and temperature. Each digital value received bymicroprocessor 50 corresponds to different temperatures and impedances. - Calculated power and impedance values can be indicated on user interface and
display 36. Alternatively, or in addition to the numerical indication of power or impedance, calculated impedance and power values can be compared bymicroprocessor 50 with power and impedance limits. When the values exceed predetermined power or impedance values, a warning can be given on user interface anddisplay 36, and additionally, the delivery of RF energy can be reduced, modified or interrupted. A control signal frommicroprocessor 50 can modify the power level supplied byenergy source 20. - The foregoing description of a preferred embodiment of the invention has been presented for purposes of illustration and description. It is not intended to be exhaustive or to limit the invention to the precise forms disclosed. Obviously, many modifications and variations will be apparent to practitioners skilled in this art. It is intended that the scope of the invention be defined by the following claims and their equivalents.
Claims (28)
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/775,747 US20040260282A1 (en) | 1995-08-15 | 2004-02-09 | Multiple antenna ablation apparatus and method with multiple sensor feedback |
US12/041,709 US8734439B2 (en) | 1995-08-15 | 2008-03-04 | Ablation apparatus and method |
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US08/515,379 US5683384A (en) | 1993-11-08 | 1995-08-15 | Multiple antenna ablation apparatus |
US08/577,208 US6689127B1 (en) | 1995-08-15 | 1995-12-22 | Multiple antenna ablation apparatus and method with multiple sensor feedback |
US10/775,747 US20040260282A1 (en) | 1995-08-15 | 2004-02-09 | Multiple antenna ablation apparatus and method with multiple sensor feedback |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US08/577,208 Continuation US6689127B1 (en) | 1995-08-15 | 1995-12-22 | Multiple antenna ablation apparatus and method with multiple sensor feedback |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/041,709 Continuation US8734439B2 (en) | 1995-08-15 | 2008-03-04 | Ablation apparatus and method |
Publications (1)
Publication Number | Publication Date |
---|---|
US20040260282A1 true US20040260282A1 (en) | 2004-12-23 |
Family
ID=33519545
Family Applications (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US08/577,208 Expired - Fee Related US6689127B1 (en) | 1995-08-15 | 1995-12-22 | Multiple antenna ablation apparatus and method with multiple sensor feedback |
US10/775,747 Abandoned US20040260282A1 (en) | 1995-08-15 | 2004-02-09 | Multiple antenna ablation apparatus and method with multiple sensor feedback |
US12/041,709 Expired - Fee Related US8734439B2 (en) | 1995-08-15 | 2008-03-04 | Ablation apparatus and method |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US08/577,208 Expired - Fee Related US6689127B1 (en) | 1995-08-15 | 1995-12-22 | Multiple antenna ablation apparatus and method with multiple sensor feedback |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/041,709 Expired - Fee Related US8734439B2 (en) | 1995-08-15 | 2008-03-04 | Ablation apparatus and method |
Country Status (1)
Country | Link |
---|---|
US (3) | US6689127B1 (en) |
Cited By (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20110213356A1 (en) * | 2009-11-05 | 2011-09-01 | Wright Robert E | Methods and systems for spinal radio frequency neurotomy |
US20110288540A1 (en) * | 2010-05-21 | 2011-11-24 | Nimbus Concepts, Llc | Systems and methods for tissue ablation |
US20120277737A1 (en) * | 2011-04-12 | 2012-11-01 | Thermedical, Inc. | Devices and methods for remote temperature monitoring in fluid enhanced ablation therapy |
US20150141977A1 (en) * | 2012-05-14 | 2015-05-21 | National University Corporation Shiga University Of Medical Science | Organ Resection Tool |
US9610396B2 (en) | 2013-03-15 | 2017-04-04 | Thermedical, Inc. | Systems and methods for visualizing fluid enhanced ablation therapy |
US9743984B1 (en) | 2016-08-11 | 2017-08-29 | Thermedical, Inc. | Devices and methods for delivering fluid to tissue during ablation therapy |
US10022176B2 (en) | 2012-08-15 | 2018-07-17 | Thermedical, Inc. | Low profile fluid enhanced ablation therapy devices and methods |
US10058385B2 (en) | 2013-03-15 | 2018-08-28 | Thermedical, Inc. | Methods and devices for fluid enhanced microwave ablation therapy |
US11083871B2 (en) | 2018-05-03 | 2021-08-10 | Thermedical, Inc. | Selectively deployable catheter ablation devices |
CN117276846A (en) * | 2023-11-02 | 2023-12-22 | 广州博远装备科技有限公司 | Shape memory alloy-based self-adaptive short wave antenna |
US11918277B2 (en) | 2018-07-16 | 2024-03-05 | Thermedical, Inc. | Inferred maximum temperature monitoring for irrigated ablation therapy |
Families Citing this family (79)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6994706B2 (en) | 2001-08-13 | 2006-02-07 | Minnesota Medical Physics, Llc | Apparatus and method for treatment of benign prostatic hyperplasia |
US9216053B2 (en) * | 2002-03-05 | 2015-12-22 | Avent, Inc. | Elongate member providing a variation in radiopacity |
US6780177B2 (en) * | 2002-08-27 | 2004-08-24 | Board Of Trustees Of The University Of Arkansas | Conductive interstitial thermal therapy device |
US20060167445A1 (en) | 2002-08-27 | 2006-07-27 | Gal Shafirstein | Selective conductive interstitial thermal therapy device |
WO2006069313A1 (en) * | 2004-12-20 | 2006-06-29 | Vnus Medical Technologies, Inc. | Systems and methods for treating a hollow anatomical structure |
GB0504988D0 (en) * | 2005-03-10 | 2005-04-20 | Emcision Ltd | Device and method for the treatment of diseased tissue such as tumors |
US7670337B2 (en) * | 2005-03-25 | 2010-03-02 | Boston Scientific Scimed, Inc. | Ablation probe having a plurality of arrays of electrodes |
DE202006021213U1 (en) * | 2005-07-21 | 2013-11-08 | Covidien Lp | Apparatus for treating a hollow anatomical structure |
US9028469B2 (en) * | 2005-09-28 | 2015-05-12 | Candela Corporation | Method of treating cellulite |
EP2767308B1 (en) | 2007-04-19 | 2016-04-13 | Miramar Labs, Inc. | Devices, and systems for non-invasive delivery of microwave therapy |
WO2008131306A1 (en) | 2007-04-19 | 2008-10-30 | The Foundry, Inc. | Systems and methods for creating an effect using microwave energy to specified tissue |
CN101711134B (en) | 2007-04-19 | 2016-08-17 | 米勒玛尔实验室公司 | Tissue is applied the system of microwave energy and in organized layer, produces the system of tissue effect |
US8292880B2 (en) | 2007-11-27 | 2012-10-23 | Vivant Medical, Inc. | Targeted cooling of deployable microwave antenna |
US11272979B2 (en) | 2008-04-29 | 2022-03-15 | Virginia Tech Intellectual Properties, Inc. | System and method for estimating tissue heating of a target ablation zone for electrical-energy based therapies |
US9198733B2 (en) | 2008-04-29 | 2015-12-01 | Virginia Tech Intellectual Properties, Inc. | Treatment planning for electroporation-based therapies |
US10245098B2 (en) | 2008-04-29 | 2019-04-02 | Virginia Tech Intellectual Properties, Inc. | Acute blood-brain barrier disruption using electrical energy based therapy |
US9867652B2 (en) | 2008-04-29 | 2018-01-16 | Virginia Tech Intellectual Properties, Inc. | Irreversible electroporation using tissue vasculature to treat aberrant cell masses or create tissue scaffolds |
US9283051B2 (en) | 2008-04-29 | 2016-03-15 | Virginia Tech Intellectual Properties, Inc. | System and method for estimating a treatment volume for administering electrical-energy based therapies |
US10702326B2 (en) | 2011-07-15 | 2020-07-07 | Virginia Tech Intellectual Properties, Inc. | Device and method for electroporation based treatment of stenosis of a tubular body part |
US8992517B2 (en) | 2008-04-29 | 2015-03-31 | Virginia Tech Intellectual Properties Inc. | Irreversible electroporation to treat aberrant cell masses |
WO2009134876A1 (en) | 2008-04-29 | 2009-11-05 | Virginia Tech Intellectual Properties, Inc. | Irreversible electroporation to create tissue scaffolds |
US10272178B2 (en) | 2008-04-29 | 2019-04-30 | Virginia Tech Intellectual Properties Inc. | Methods for blood-brain barrier disruption using electrical energy |
US10238447B2 (en) | 2008-04-29 | 2019-03-26 | Virginia Tech Intellectual Properties, Inc. | System and method for ablating a tissue site by electroporation with real-time monitoring of treatment progress |
US10117707B2 (en) | 2008-04-29 | 2018-11-06 | Virginia Tech Intellectual Properties, Inc. | System and method for estimating tissue heating of a target ablation zone for electrical-energy based therapies |
US11254926B2 (en) | 2008-04-29 | 2022-02-22 | Virginia Tech Intellectual Properties, Inc. | Devices and methods for high frequency electroporation |
WO2010085765A2 (en) * | 2009-01-23 | 2010-07-29 | Moshe Meir H | Therapeutic energy delivery device with rotational mechanism |
US11382681B2 (en) | 2009-04-09 | 2022-07-12 | Virginia Tech Intellectual Properties, Inc. | Device and methods for delivery of high frequency electrical pulses for non-thermal ablation |
US11638603B2 (en) | 2009-04-09 | 2023-05-02 | Virginia Tech Intellectual Properties, Inc. | Selective modulation of intracellular effects of cells using pulsed electric fields |
US8246615B2 (en) | 2009-05-19 | 2012-08-21 | Vivant Medical, Inc. | Tissue impedance measurement using a secondary frequency |
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 |
US20110238057A1 (en) * | 2010-02-16 | 2011-09-29 | Angiodynamics, Inc. | Dual Bracketed Energy Delivery Probe and Method of Use |
WO2012051433A2 (en) | 2010-10-13 | 2012-04-19 | Angiodynamics, Inc. | System and method for electrically ablating tissue of a patient |
WO2012088149A2 (en) | 2010-12-20 | 2012-06-28 | Virginia Tech Intellectual Properties, Inc. | High-frequency electroporation for cancer therapy |
US9314301B2 (en) | 2011-08-01 | 2016-04-19 | Miramar Labs, Inc. | Applicator and tissue interface module for dermatological device |
US10201385B2 (en) | 2011-09-01 | 2019-02-12 | Biosense Webster (Israel) Ltd. | Catheter adapted for direct tissue contact |
US8900228B2 (en) | 2011-09-01 | 2014-12-02 | Biosense Webster (Israel) Ltd. | Catheter adapted for direct tissue contact and pressure sensing |
US9078665B2 (en) | 2011-09-28 | 2015-07-14 | Angiodynamics, Inc. | Multiple treatment zone ablation probe |
US10076383B2 (en) | 2012-01-25 | 2018-09-18 | Covidien Lp | Electrosurgical device having a multiplexer |
US9204921B2 (en) | 2012-12-13 | 2015-12-08 | Cook Medical Technologies Llc | RF energy controller and method for electrosurgical medical devices |
US9364277B2 (en) | 2012-12-13 | 2016-06-14 | Cook Medical Technologies Llc | RF energy controller and method for electrosurgical medical devices |
US9445725B2 (en) | 2012-12-17 | 2016-09-20 | Biosense Webster (Israel) Ltd. | Irrigated catheter tip with temperature sensor array |
US10499980B2 (en) | 2013-03-14 | 2019-12-10 | Spiration, Inc. | Flexible RF ablation needle |
US9161814B2 (en) * | 2013-03-15 | 2015-10-20 | Covidien Lp | Microwave energy-delivery device and system |
US9119650B2 (en) * | 2013-03-15 | 2015-09-01 | Covidien Lp | Microwave energy-delivery device and system |
US9301723B2 (en) | 2013-03-15 | 2016-04-05 | Covidien Lp | Microwave energy-delivery device and system |
US10779885B2 (en) | 2013-07-24 | 2020-09-22 | Miradry. Inc. | Apparatus and methods for the treatment of tissue using microwave energy |
FR3018444B1 (en) * | 2014-03-12 | 2021-07-23 | Paul Pittaluga | MEDICAL DEVICE INCLUDING A HYDROPHILIC HOOKED FLEXIBLE TIP FOR TREATMENT OF VARICOUS VEINS |
JP6440729B2 (en) * | 2014-03-28 | 2018-12-19 | スパイレーション インコーポレイテッド ディー ビー エイ オリンパス レスピラトリー アメリカ | Devices with ecogenic features |
CN112807074A (en) | 2014-05-12 | 2021-05-18 | 弗吉尼亚暨州立大学知识产权公司 | Electroporation system |
CA2953694A1 (en) | 2014-07-02 | 2016-01-07 | Covidien Lp | Alignment ct |
EP3164075B1 (en) | 2014-07-02 | 2021-03-24 | Covidien LP | Unified coordinate system for multiple ct scans of patient lungs |
US10624697B2 (en) | 2014-08-26 | 2020-04-21 | Covidien Lp | Microwave ablation system |
US10813691B2 (en) | 2014-10-01 | 2020-10-27 | Covidien Lp | Miniaturized microwave ablation assembly |
EP3220841B1 (en) | 2014-11-19 | 2023-01-25 | EPiX Therapeutics, Inc. | High-resolution mapping of tissue with pacing |
EP3220844B1 (en) | 2014-11-19 | 2020-11-11 | EPiX Therapeutics, Inc. | Systems for high-resolution mapping of tissue |
EP3220843B1 (en) | 2014-11-19 | 2020-01-01 | EPiX Therapeutics, Inc. | Ablation devices and methods of using a high-resolution electrode assembly |
US10694972B2 (en) | 2014-12-15 | 2020-06-30 | Virginia Tech Intellectual Properties, Inc. | Devices, systems, and methods for real-time monitoring of electrophysical effects during tissue treatment |
US9636164B2 (en) | 2015-03-25 | 2017-05-02 | Advanced Cardiac Therapeutics, Inc. | Contact sensing systems and methods |
WO2016176567A1 (en) | 2015-04-29 | 2016-11-03 | Innoblative Designs, Inc. | Cavitary tissue ablation |
WO2017075366A1 (en) | 2015-10-29 | 2017-05-04 | Innoblative Designs, Inc. | Screen sphere tissue ablation devices and methods |
US10864040B2 (en) | 2015-12-29 | 2020-12-15 | Warsaw Orthopedic, Inc. | Multi-probe system using bipolar probes and methods of using the same |
EP3410972B1 (en) | 2016-02-02 | 2021-03-10 | Innoblative Designs, Inc. | Cavitary tissue ablation system |
US10813692B2 (en) | 2016-02-29 | 2020-10-27 | Covidien Lp | 90-degree interlocking geometry for introducer for facilitating deployment of microwave radiating catheter |
WO2017151431A1 (en) | 2016-03-01 | 2017-09-08 | Innoblative Designs, Inc. | Resecting and coagulating tissue |
EP3429462B1 (en) | 2016-03-15 | 2022-08-03 | EPiX Therapeutics, Inc. | Improved devices and systems for irrigated ablation |
WO2018075389A1 (en) | 2016-10-17 | 2018-04-26 | Innoblative Designs, Inc. | Treatment devices and methods |
EP3538000A4 (en) | 2016-11-08 | 2020-04-01 | Innoblative Designs, Inc. | Electrosurgical tissue and vessel sealing device |
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 |
EP3335660B1 (en) * | 2016-12-14 | 2021-01-20 | Clinical Laserthermia Systems AB | Apparatus for controlling laser thermotherapy |
CN110809448B (en) | 2017-04-27 | 2022-11-25 | Epix疗法公司 | Determining properties of contact between catheter tip and tissue |
WO2019023328A1 (en) | 2017-07-26 | 2019-01-31 | Innoblative Designs, Inc. | Minimally invasive articulating assembly having ablation capabilities |
US11607537B2 (en) | 2017-12-05 | 2023-03-21 | Virginia Tech Intellectual Properties, Inc. | Method for treating neurological disorders, including tumors, with electroporation |
US11464576B2 (en) | 2018-02-09 | 2022-10-11 | Covidien Lp | System and method for displaying an alignment CT |
US11311329B2 (en) | 2018-03-13 | 2022-04-26 | Virginia Tech Intellectual Properties, Inc. | Treatment planning for immunotherapy based treatments using non-thermal ablation techniques |
US11925405B2 (en) | 2018-03-13 | 2024-03-12 | Virginia Tech Intellectual Properties, Inc. | Treatment planning system for immunotherapy enhancement via non-thermal ablation |
US11135004B2 (en) | 2018-12-24 | 2021-10-05 | Industrial Technology Research Institute | Ablation device |
US11950835B2 (en) | 2019-06-28 | 2024-04-09 | Virginia Tech Intellectual Properties, Inc. | Cycled pulsing to mitigate thermal damage for multi-electrode irreversible electroporation therapy |
US20210353354A1 (en) * | 2020-05-14 | 2021-11-18 | Singlepass Transseptal, Inc. | Method for single pass large bore transseptal crossing |
Citations (90)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4016886A (en) * | 1974-11-26 | 1977-04-12 | The United States Of America As Represented By The United States Energy Research And Development Administration | Method for localizing heating in tumor tissue |
US4043342A (en) * | 1974-08-28 | 1977-08-23 | Valleylab, Inc. | Electrosurgical devices having sesquipolar electrode structures incorporated therein |
US4074718A (en) * | 1976-03-17 | 1978-02-21 | Valleylab, Inc. | Electrosurgical instrument |
US4080959A (en) * | 1976-06-18 | 1978-03-28 | Leveen Robert F | Method for detection of tumors of the breast |
US4095602A (en) * | 1976-09-27 | 1978-06-20 | Leveen Harry H | Multi-portal radiofrequency generator |
US4140130A (en) * | 1977-05-31 | 1979-02-20 | Storm Iii Frederick K | Electrode structure for radio frequency localized heating of tumor bearing tissue |
US4154246A (en) * | 1977-07-25 | 1979-05-15 | Leveen Harry H | Field intensification in radio frequency thermotherapy |
US4285346A (en) * | 1979-03-14 | 1981-08-25 | Harry V. LeVeen | Electrode system |
US4290435A (en) * | 1979-09-07 | 1981-09-22 | Thermatime A.G. | Internally cooled electrode for hyperthermal treatment and method of use |
US4346715A (en) * | 1978-07-12 | 1982-08-31 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Hyperthermia heating apparatus |
US4375220A (en) * | 1980-05-09 | 1983-03-01 | Matvias Fredrick M | Microwave applicator with cooling mechanism for intracavitary treatment of cancer |
USRE32066E (en) * | 1975-07-11 | 1986-01-21 | Method for treating benign and malignant tumors utilizing radio frequency, electromagnetic radiation | |
US4565200A (en) * | 1980-09-24 | 1986-01-21 | Cosman Eric R | Universal lesion and recording electrode system |
US4574782A (en) * | 1981-11-16 | 1986-03-11 | Corning Glass Works | Radio frequency-induced hyperthermia for tumor therapy |
US4586490A (en) * | 1984-02-27 | 1986-05-06 | Katz Harry R | Needle inserting instrument means for interstitial radiotherapy |
US4601296A (en) * | 1983-10-07 | 1986-07-22 | Yeda Research And Development Co., Ltd. | Hyperthermia apparatus |
US4676258A (en) * | 1983-01-24 | 1987-06-30 | Kureha Kagaku Kogyo Kabushiki Kaisha | Device for hyperthermia |
US4763671A (en) * | 1983-12-27 | 1988-08-16 | Stanford University | Method of treating tumors using selective application of heat and radiation |
US4800899A (en) * | 1984-10-22 | 1989-01-31 | Microthermia Technology, Inc. | Apparatus for destroying cells in tumors and the like |
US4813429A (en) * | 1986-05-12 | 1989-03-21 | Biodan Medical Systems Ltd. | Catheter and probe |
US4823791A (en) * | 1987-05-08 | 1989-04-25 | Circon Acmi Division Of Circon Corporation | Electrosurgical probe apparatus |
US4860744A (en) * | 1987-11-02 | 1989-08-29 | Raj K. Anand | Thermoelectrically controlled heat medical catheter |
US4920978A (en) * | 1988-08-31 | 1990-05-01 | Triangle Research And Development Corporation | Method and apparatus for the endoscopic treatment of deep tumors using RF hyperthermia |
US4931047A (en) * | 1987-09-30 | 1990-06-05 | Cavitron, Inc. | Method and apparatus for providing enhanced tissue fragmentation and/or hemostasis |
US4945912A (en) * | 1988-11-25 | 1990-08-07 | Sensor Electronics, Inc. | Catheter with radiofrequency heating applicator |
US4947842A (en) * | 1988-09-22 | 1990-08-14 | Medical Engineering And Development Institute, Inc. | Method and apparatus for treating tissue with first and second modalities |
US4983159A (en) * | 1985-03-25 | 1991-01-08 | Rand Robert W | Inductive heating process for use in causing necrosis of neoplasms at selective frequencies |
US5003991A (en) * | 1987-03-31 | 1991-04-02 | Olympus Optical Co., Ltd. | Hyperthermia apparatus |
US5007908A (en) * | 1989-09-29 | 1991-04-16 | Everest Medical Corporation | Electrosurgical instrument having needle cutting electrode and spot-coag electrode |
US5009656A (en) * | 1989-08-17 | 1991-04-23 | Mentor O&O Inc. | Bipolar electrosurgical instrument |
US5010897A (en) * | 1989-04-26 | 1991-04-30 | Leveen Harry H | Apparatus for deep heating of cancer |
US5047027A (en) * | 1990-04-20 | 1991-09-10 | Everest Medical Corporation | Tumor resector |
US5078717A (en) * | 1989-04-13 | 1992-01-07 | Everest Medical Corporation | Ablation catheter with selectively deployable electrodes |
US5085659A (en) * | 1990-11-21 | 1992-02-04 | Everest Medical Corporation | Biopsy device with bipolar coagulation capability |
US5099756A (en) * | 1989-06-01 | 1992-03-31 | Harry H. Leveen | Radio frequency thermotherapy |
US5100423A (en) * | 1990-08-21 | 1992-03-31 | Medical Engineering & Development Institute, Inc. | Ablation catheter |
US5122137A (en) * | 1990-04-27 | 1992-06-16 | Boston Scientific Corporation | Temperature controlled rf coagulation |
US5125928A (en) * | 1989-04-13 | 1992-06-30 | Everest Medical Corporation | Ablation catheter with selectively deployable electrodes |
US5190517A (en) * | 1991-06-06 | 1993-03-02 | Valleylab Inc. | Electrosurgical and ultrasonic surgical system |
US5190541A (en) * | 1990-10-17 | 1993-03-02 | Boston Scientific Corporation | Surgical instrument and method |
US5197466A (en) * | 1983-01-21 | 1993-03-30 | Med Institute Inc. | Method and apparatus for volumetric interstitial conductive hyperthermia |
US5197964A (en) * | 1991-11-12 | 1993-03-30 | Everest Medical Corporation | Bipolar instrument utilizing one stationary electrode and one movable electrode |
US5197963A (en) * | 1991-12-02 | 1993-03-30 | Everest Medical Corporation | Electrosurgical instrument with extendable sheath for irrigation and aspiration |
US5203782A (en) * | 1990-04-02 | 1993-04-20 | Gudov Vasily F | Method and apparatus for treating malignant tumors by local hyperpyrexia |
US5217458A (en) * | 1992-04-09 | 1993-06-08 | Everest Medical Corporation | Bipolar biopsy device utilizing a rotatable, single-hinged moving element |
US5236410A (en) * | 1990-08-02 | 1993-08-17 | Ferrotherm International, Inc. | Tumor treatment method |
US5275162A (en) * | 1991-11-08 | 1994-01-04 | Ep Technologies, Inc. | Valve mapping catheter |
US5277696A (en) * | 1991-11-19 | 1994-01-11 | Delma Elektro- Und Medizinische Apparatebau Gesellschaft Mbh | Medical high frequency coagulation instrument |
US5281217A (en) * | 1992-04-13 | 1994-01-25 | Ep Technologies, Inc. | Steerable antenna systems for cardiac ablation that minimize tissue damage and blood coagulation due to conductive heating patterns |
US5281218A (en) * | 1992-06-05 | 1994-01-25 | Cardiac Pathways Corporation | Catheter having needle electrode for radiofrequency ablation |
US5282797A (en) * | 1989-05-30 | 1994-02-01 | Cyrus Chess | Method for treating cutaneous vascular lesions |
US5293869A (en) * | 1992-09-25 | 1994-03-15 | Ep Technologies, Inc. | Cardiac probe with dynamic support for maintaining constant surface contact during heart systole and diastole |
US5295955A (en) * | 1992-02-14 | 1994-03-22 | Amt, Inc. | Method and apparatus for microwave aided liposuction |
US5309910A (en) * | 1992-09-25 | 1994-05-10 | Ep Technologies, Inc. | Cardiac mapping and ablation systems |
US5314466A (en) * | 1992-04-13 | 1994-05-24 | Ep Technologies, Inc. | Articulated unidirectional microwave antenna systems for cardiac ablation |
US5313943A (en) * | 1992-09-25 | 1994-05-24 | Ep Technologies, Inc. | Catheters and methods for performing cardiac diagnosis and treatment |
US5328467A (en) * | 1991-11-08 | 1994-07-12 | Ep Technologies, Inc. | Catheter having a torque transmitting sleeve |
US5334193A (en) * | 1992-11-13 | 1994-08-02 | American Cardiac Ablation Co., Inc. | Fluid cooled ablation catheter |
US5342357A (en) * | 1992-11-13 | 1994-08-30 | American Cardiac Ablation Co., Inc. | Fluid cooled electrosurgical cauterization system |
US5348554A (en) * | 1992-12-01 | 1994-09-20 | Cardiac Pathways Corporation | Catheter for RF ablation with cooled electrode |
US5383917A (en) * | 1991-07-05 | 1995-01-24 | Jawahar M. Desai | Device and method for multi-phase radio-frequency ablation |
US5385544A (en) * | 1992-08-12 | 1995-01-31 | Vidamed, Inc. | BPH ablation method and apparatus |
US5398683A (en) * | 1991-05-24 | 1995-03-21 | Ep Technologies, Inc. | Combination monophasic action potential/ablation catheter and high-performance filter system |
US5403311A (en) * | 1993-03-29 | 1995-04-04 | Boston Scientific Corporation | Electro-coagulation and ablation and other electrotherapeutic treatments of body tissue |
US5409453A (en) * | 1992-08-12 | 1995-04-25 | Vidamed, Inc. | Steerable medical probe with stylets |
US5417687A (en) * | 1993-04-30 | 1995-05-23 | Medical Scientific, Inc. | Bipolar electrosurgical trocar |
US5421819A (en) * | 1992-08-12 | 1995-06-06 | Vidamed, Inc. | Medical probe device |
US5423807A (en) * | 1992-04-16 | 1995-06-13 | Implemed, Inc. | Cryogenic mapping and ablation catheter |
US5423808A (en) * | 1991-11-08 | 1995-06-13 | Ep Technologies, Inc. | Systems and methods for radiofrequency ablation with phase sensitive power detection |
US5431649A (en) * | 1993-08-27 | 1995-07-11 | Medtronic, Inc. | Method and apparatus for R-F ablation |
US5433708A (en) * | 1991-05-17 | 1995-07-18 | Innerdyne, Inc. | Method and device for thermal ablation having improved heat transfer |
US5435805A (en) * | 1992-08-12 | 1995-07-25 | Vidamed, Inc. | Medical probe device with optical viewing capability |
US5484400A (en) * | 1992-08-12 | 1996-01-16 | Vidamed, Inc. | Dual channel RF delivery system |
US5486161A (en) * | 1993-02-02 | 1996-01-23 | Zomed International | Medical probe device and method |
US5505730A (en) * | 1994-06-24 | 1996-04-09 | Stuart D. Edwards | Thin layer ablation apparatus |
US5507743A (en) * | 1993-11-08 | 1996-04-16 | Zomed International | Coiled RF electrode treatment apparatus |
US5514131A (en) * | 1992-08-12 | 1996-05-07 | Stuart D. Edwards | Method for the ablation treatment of the uvula |
US5514130A (en) * | 1994-10-11 | 1996-05-07 | Dorsal Med International | RF apparatus for controlled depth ablation of soft tissue |
US5531676A (en) * | 1992-08-12 | 1996-07-02 | Vidamed, Inc. | Medical probe device and method |
US5536267A (en) * | 1993-11-08 | 1996-07-16 | Zomed International | Multiple electrode ablation apparatus |
US5542928A (en) * | 1991-05-17 | 1996-08-06 | Innerdyne, Inc. | Method and device for thermal ablation having improved heat transfer |
US5542916A (en) * | 1992-08-12 | 1996-08-06 | Vidamed, Inc. | Dual-channel RF power delivery system |
US5542915A (en) * | 1992-08-12 | 1996-08-06 | Vidamed, Inc. | Thermal mapping catheter with ultrasound probe |
US5545161A (en) * | 1992-12-01 | 1996-08-13 | Cardiac Pathways Corporation | Catheter for RF ablation having cooled electrode with electrically insulated sleeve |
US5545171A (en) * | 1994-09-22 | 1996-08-13 | Vidamed, Inc. | Anastomosis catheter |
US5545193A (en) * | 1993-10-15 | 1996-08-13 | Ep Technologies, Inc. | Helically wound radio-frequency emitting electrodes for creating lesions in body tissue |
US5546267A (en) * | 1994-12-08 | 1996-08-13 | Illinois Tool Works Inc. | Communication circuit protector |
US5549108A (en) * | 1992-09-25 | 1996-08-27 | Ep Technologies, Inc. | Cardiac mapping and ablation systems |
US5549644A (en) * | 1992-08-12 | 1996-08-27 | Vidamed, Inc. | Transurethral needle ablation device with cystoscope and method for treatment of the prostate |
US5855576A (en) * | 1995-03-24 | 1999-01-05 | Board Of Regents Of University Of Nebraska | Method for volumetric tissue ablation |
Family Cites Families (152)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE1007960B (en) | 1953-09-19 | 1957-05-09 | Richard Wolf | Coagulation electrode for endoscopes |
US3474777A (en) | 1966-02-10 | 1969-10-28 | Amp Inc | Method of administering therapeutic agents |
US3858586A (en) * | 1971-03-11 | 1975-01-07 | Martin Lessen | Surgical method and electrode therefor |
DE2124684A1 (en) | 1971-05-18 | 1972-11-30 | Stadelmann W | Puncture electrode |
US3834392A (en) | 1973-02-01 | 1974-09-10 | Kli Inc | Laparoscopy system |
US4016881A (en) * | 1973-07-04 | 1977-04-12 | Centre De Recherche Industrielle Du Quebec | Instrument for use in laparoscopic tubal cauterization |
US3991770A (en) | 1974-01-24 | 1976-11-16 | Leveen Harry H | Method for treating benign and malignant tumors utilizing radio frequency, electromagnetic radiation |
DE2513868C2 (en) * | 1974-04-01 | 1982-11-04 | Olympus Optical Co., Ltd., Tokyo | Bipolar electrodiathermy forceps |
US4033351A (en) | 1974-06-14 | 1977-07-05 | Siemens Aktiengesellschaft | Bipolar cutting electrode for high-frequency surgery |
US4303636A (en) | 1974-08-20 | 1981-12-01 | Gordon Robert T | Cancer treatment |
US3987795A (en) | 1974-08-28 | 1976-10-26 | Valleylab, Inc. | Electrosurgical devices having sesquipolar electrode structures incorporated therein |
CH587664A5 (en) | 1974-09-05 | 1977-05-13 | Fischer Fa F L | |
US4026301A (en) * | 1975-04-21 | 1977-05-31 | Medtronic, Inc. | Apparatus and method for optimum electrode placement in the treatment of disease syndromes such as spinal curvature |
US4000743A (en) * | 1975-07-09 | 1977-01-04 | Kenneth Weaver | Uterine anteverter |
US4230129A (en) | 1975-07-11 | 1980-10-28 | Leveen Harry H | Radio frequency, electromagnetic radiation device having orbital mount |
US4121592A (en) | 1975-08-04 | 1978-10-24 | Critical Systems, Inc. | Apparatus for heating tissue |
US4237898A (en) | 1978-03-27 | 1980-12-09 | Critical Systems, Inc. | Apparatus for heating tissue and employing protection against transients |
US4337760A (en) | 1978-10-13 | 1982-07-06 | Adolf Schwimmer | Method for the treatment of tumors with β-glucuronidase activity dependent pharmaceuticals |
US4418692A (en) | 1978-11-17 | 1983-12-06 | Guay Jean Louis | Device for treating living tissue with an electric current |
SE418248B (en) | 1978-11-23 | 1981-05-18 | Tekniska Roentgencentralen Ab | DEVICE FOR DESTRUCTING A BIOLOGICAL TISSUE PARTY |
US4345588A (en) | 1979-04-23 | 1982-08-24 | Northwestern University | Method of delivering a therapeutic agent to a target capillary bed |
US4269174A (en) * | 1979-08-06 | 1981-05-26 | Medical Dynamics, Inc. | Transcutaneous vasectomy apparatus and method |
DE3050386C2 (en) | 1980-05-13 | 1987-06-25 | American Hospital Supply Corp | Multipolar electrosurgical device |
US4331654A (en) * | 1980-06-13 | 1982-05-25 | Eli Lilly And Company | Magnetically-localizable, biodegradable lipid microspheres |
JPS5725863A (en) | 1980-07-23 | 1982-02-10 | Olympus Optical Co | Endoscope with microwave heater |
US4411266A (en) | 1980-09-24 | 1983-10-25 | Cosman Eric R | Thermocouple radio frequency lesion electrode |
US4562838A (en) * | 1981-01-23 | 1986-01-07 | Walker William S | Electrosurgery instrument |
JPS57168656A (en) | 1981-04-10 | 1982-10-18 | Medos Kenkyusho Kk | Endoscope laser coagulator |
US4512762A (en) * | 1982-11-23 | 1985-04-23 | The Beth Israel Hospital Association | Method of treatment of atherosclerosis and a balloon catheter for same |
US4583556A (en) * | 1982-12-13 | 1986-04-22 | M/A-Com, Inc. | Microwave applicator/receiver apparatus |
US4524770A (en) | 1983-01-25 | 1985-06-25 | Ahmad Orandi | Endoscope injection needle |
US4506680A (en) * | 1983-03-17 | 1985-03-26 | Medtronic, Inc. | Drug dispensing body implantable lead |
US4545368A (en) | 1983-04-13 | 1985-10-08 | Rand Robert W | Induction heating method for use in causing necrosis of neoplasm |
US4662359A (en) * | 1983-08-12 | 1987-05-05 | Robert T. Gordon | Use of magnetic susceptibility probes in the treatment of cancer |
JPS6055966A (en) | 1983-09-05 | 1985-04-01 | オリンパス光学工業株式会社 | Medical electrode apparatus |
US4658819A (en) * | 1983-09-13 | 1987-04-21 | Valleylab, Inc. | Electrosurgical generator |
US4818542A (en) * | 1983-11-14 | 1989-04-04 | The University Of Kentucky Research Foundation | Porous microspheres for drug delivery and methods for making same |
CA1237482A (en) | 1984-03-09 | 1988-05-31 | Frank B. Stiles | Catheter for effecting removal of obstructions from a biological duct |
US4652257A (en) * | 1985-03-21 | 1987-03-24 | The United States Of America As Represented By The Secretary Of The Navy | Magnetically-localizable, polymerized lipid vesicles and method of disrupting same |
US4648892A (en) * | 1985-03-22 | 1987-03-10 | Massachusetts Institute Of Technology | Method for making optical shield for a laser catheter |
US4838265A (en) | 1985-05-24 | 1989-06-13 | Cosman Eric R | Localization device for probe placement under CT scanner imaging |
US4660571A (en) * | 1985-07-18 | 1987-04-28 | Cordis Corporation | Percutaneous lead having radially adjustable electrode |
US4823793A (en) * | 1985-10-30 | 1989-04-25 | The United States Of America As Represented By The Administrator Of The National Aeronuautics & Space Administration | Cutting head for ultrasonic lithotripsy |
US4690130A (en) | 1985-12-19 | 1987-09-01 | Mirell Stuart G | Electromagnetic therapy control system |
SE455920B (en) | 1986-01-29 | 1988-08-22 | Hans Wiksell | TUMOR HYPERTERMY TREATMENT DEVICE |
US4700716A (en) | 1986-02-27 | 1987-10-20 | Kasevich Associates, Inc. | Collinear antenna array applicator |
US4709701A (en) | 1986-04-15 | 1987-12-01 | Medical Research & Development Associates | Apparatus for medical treatment by hyperthermia |
NL8601808A (en) * | 1986-07-10 | 1988-02-01 | Hooft Eric T | METHOD FOR TREATING A BODY PART WITH RADIOACTIVE MATERIAL AND CART USED THEREIN |
US5365926A (en) | 1986-11-14 | 1994-11-22 | Desai Jawahar M | Catheter for mapping and ablation and method therefor |
US4940064A (en) | 1986-11-14 | 1990-07-10 | Desai Jawahar M | Catheter for mapping and ablation and method therefor |
US5215103A (en) | 1986-11-14 | 1993-06-01 | Desai Jawahar M | Catheter for mapping and ablation and method therefor |
US5231995A (en) * | 1986-11-14 | 1993-08-03 | Desai Jawahar M | Method for catheter mapping and ablation |
US4962761A (en) | 1987-02-24 | 1990-10-16 | Golden Theodore A | Thermal bandage |
DE3718139C1 (en) | 1987-05-29 | 1988-12-08 | Strahlen Umweltforsch Gmbh | Cardiac catheter |
US5170789A (en) | 1987-06-17 | 1992-12-15 | Perinchery Narayan | Insertable NMR coil probe |
US4825880A (en) * | 1987-06-19 | 1989-05-02 | The Regents Of The University Of California | Implantable helical coil microwave antenna |
US4753248A (en) | 1987-06-24 | 1988-06-28 | Duke University | Probe translation system for use in hyperthermia treatment |
US5015227A (en) * | 1987-09-30 | 1991-05-14 | Valleylab Inc. | Apparatus for providing enhanced tissue fragmentation and/or hemostasis |
JPH01139081A (en) | 1987-11-27 | 1989-05-31 | Olympus Optical Co Ltd | Apparatus for radiating laser beam |
US4907589A (en) * | 1988-04-29 | 1990-03-13 | Cosman Eric R | Automatic over-temperature control apparatus for a therapeutic heating device |
US4989601A (en) * | 1988-05-02 | 1991-02-05 | Medical Engineering & Development Institute, Inc. | Method, apparatus, and substance for treating tissue having neoplastic cells |
US5178620A (en) * | 1988-06-10 | 1993-01-12 | Advanced Angioplasty Products, Inc. | Thermal dilatation catheter and method |
US4881543A (en) | 1988-06-28 | 1989-11-21 | Massachusetts Institute Of Technology | Combined microwave heating and surface cooling of the cornea |
US5249585A (en) | 1988-07-28 | 1993-10-05 | Bsd Medical Corporation | Urethral inserted applicator for prostate hyperthermia |
US4967765A (en) | 1988-07-28 | 1990-11-06 | Bsd Medical Corporation | Urethral inserted applicator for prostate hyperthermia |
US5183455A (en) * | 1988-10-07 | 1993-02-02 | Omnitron International, Inc. | Apparatus for in situ radiotherapy |
US4976680A (en) | 1988-10-07 | 1990-12-11 | Hayman Michael H | Apparatus for in situ radiotherapy |
US5026959A (en) | 1988-11-16 | 1991-06-25 | Tokyo Keiki Co. Ltd. | Microwave radiator for warming therapy |
DE3838840C2 (en) | 1988-11-17 | 1997-02-20 | Leibinger Gmbh | High frequency coagulation device for surgical purposes |
FR2639238B1 (en) | 1988-11-21 | 1991-02-22 | Technomed Int Sa | APPARATUS FOR SURGICAL TREATMENT OF TISSUES BY HYPERTHERMIA, PREFERABLY THE PROSTATE, COMPRISING MEANS OF THERMAL PROTECTION COMPRISING PREFERABLY RADIOREFLECTIVE SCREEN MEANS |
US4985022A (en) * | 1988-11-23 | 1991-01-15 | Med Institute, Inc. | Catheter having durable and flexible segments |
US5205289A (en) * | 1988-12-23 | 1993-04-27 | Medical Instrumentation And Diagnostics Corporation | Three-dimensional computer graphics simulation and computerized numerical optimization for dose delivery and treatment planning |
US5128147A (en) | 1989-01-06 | 1992-07-07 | Thermal Developments, Inc. | Heat intensifier and localizer for radiofrequency thermotherapy |
US4966604A (en) | 1989-01-23 | 1990-10-30 | Interventional Technologies Inc. | Expandable atherectomy cutter with flexibly bowed blades |
USRE34086E (en) | 1989-02-27 | 1992-10-06 | Medical placement device | |
US4963364A (en) | 1989-04-10 | 1990-10-16 | Fox Sidney W | Microencapsulated antitumor agent |
US5059199A (en) | 1989-04-12 | 1991-10-22 | Olympus Optical Co., Ltd. | Treating device for endoscopes |
US5057107A (en) | 1989-04-13 | 1991-10-15 | Everest Medical Corporation | Ablation catheter with selectively deployable electrodes |
US4976711A (en) | 1989-04-13 | 1990-12-11 | Everest Medical Corporation | Ablation catheter with selectively deployable electrodes |
US5055100A (en) | 1989-06-19 | 1991-10-08 | Eugene Olsen | Suction attachment for electrosurgical instruments or the like |
US5011483A (en) * | 1989-06-26 | 1991-04-30 | Dennis Sleister | Combined electrosurgery and laser beam delivery device |
US5119832A (en) | 1989-07-11 | 1992-06-09 | Ravi Xavier | Epidural catheter with nerve stimulators |
JP3046315B2 (en) | 1989-09-05 | 2000-05-29 | 株式会社エス・エル・ティ・ジャパン | Laser irradiation equipment |
DE3930451C2 (en) | 1989-09-12 | 2002-09-26 | Leibinger Gmbh | Device for high-frequency coagulation of biological tissue |
US5203353A (en) * | 1989-10-24 | 1993-04-20 | Surgical Technologies, Inc. | Method of penetrating and working in the vitreous humor of the eye |
US5273535A (en) | 1991-11-08 | 1993-12-28 | Ep Technologies, Inc. | Catheter with electrode tip having asymmetric left and right curve configurations |
US5115818A (en) | 1990-02-14 | 1992-05-26 | Medtronic, Inc. | Implantable electrode |
US5016615A (en) * | 1990-02-20 | 1991-05-21 | Riverside Research Institute | Local application of medication with ultrasound |
US5013312A (en) * | 1990-03-19 | 1991-05-07 | Everest Medical Corporation | Bipolar scalpel for harvesting internal mammary artery |
US5067952A (en) | 1990-04-02 | 1991-11-26 | Gudov Vasily F | Method and apparatus for treating malignant tumors by local hyperpyrexia |
JPH03297475A (en) * | 1990-04-16 | 1991-12-27 | Ken Ishihara | Controlling method for emission of medicine by means of resonance sound wave |
US5071419A (en) | 1990-04-30 | 1991-12-10 | Everest Medical Corporation | Percutaneous laparoscopic cholecystectomy instrument |
US5080660A (en) * | 1990-05-11 | 1992-01-14 | Applied Urology, Inc. | Electrosurgical electrode |
FR2663048B1 (en) * | 1990-06-06 | 1992-09-18 | Ishikawa Seisakusho Kk | DOUBLE TORSION SPINDLE APPARATUS. |
US5169396A (en) | 1990-06-08 | 1992-12-08 | Kambiz Dowlatshahi | Method for interstitial laser therapy |
US5190539A (en) * | 1990-07-10 | 1993-03-02 | Texas A & M University System | Micro-heat-pipe catheter |
US5083565A (en) * | 1990-08-03 | 1992-01-28 | Everest Medical Corporation | Electrosurgical instrument for ablating endocardial tissue |
US5084045A (en) | 1990-09-17 | 1992-01-28 | Helenowski Tomasz K | Suction surgical instrument |
US5167626A (en) | 1990-10-02 | 1992-12-01 | Glaxo Inc. | Medical capsule device actuated by radio-frequency (RF) signal |
US5170805A (en) | 1990-12-11 | 1992-12-15 | Kensey Nash Corporation | Method of destroying tissue such as a gall bladder utilizing a sclerosing agent alone or with a symphysis agent |
FR2670664A1 (en) | 1990-12-21 | 1992-06-26 | Benhaim Jean | Probe for non-surgical treatment of cardiovascular disease |
FR2671010B1 (en) | 1990-12-27 | 1993-07-09 | Ela Medical Sa | ENDOCARDIAC PROBE PROVIDED WITH AN ACTIVE FIXING MEMBER |
DE4100422A1 (en) | 1991-01-09 | 1992-07-16 | Wolf Gmbh Richard | Surgical instrument for separating tissue and achieving coagulation - includes handle with hollow shaft in which HF needle electrode is LED which is laterally deflectable at its distal end |
US5156151A (en) | 1991-02-15 | 1992-10-20 | Cardiac Pathways Corporation | Endocardial mapping and ablation system and catheter probe |
US5252922A (en) | 1991-04-30 | 1993-10-12 | Hewlett-Packard Company | Radiofrequency focusing of magnetic resonance images |
IT1247029B (en) | 1991-06-19 | 1994-12-12 | S M A Segnalamento Marittimo E | MICROWAVE EQUIPMENT FOR CLINICAL HYPERTHERMIA IN ENDOGENIC THERMOTHERAPY |
US5251645A (en) | 1991-06-26 | 1993-10-12 | Massachusetts Institute Of Technology | Adaptive nulling hyperthermia array |
US5620481A (en) * | 1991-07-05 | 1997-04-15 | Desai; Jawahar M. | Device for multi-phase radio-frequency ablation |
US5207675A (en) | 1991-07-15 | 1993-05-04 | Jerome Canady | Surgical coagulation device |
US5222953A (en) | 1991-10-02 | 1993-06-29 | Kambiz Dowlatshahi | Apparatus for interstitial laser therapy having an improved temperature sensor for tissue being treated |
US5562703A (en) | 1994-06-14 | 1996-10-08 | Desai; Ashvin H. | Endoscopic surgical instrument |
US5322503A (en) | 1991-10-18 | 1994-06-21 | Desai Ashvin H | Endoscopic surgical instrument |
CA2106410C (en) | 1991-11-08 | 2004-07-06 | Stuart D. Edwards | Ablation electrode with insulated temperature sensing elements |
US5257451A (en) | 1991-11-08 | 1993-11-02 | Ep Technologies, Inc. | Method of making durable sleeve for enclosing a bendable electrode tip assembly |
US5363861A (en) | 1991-11-08 | 1994-11-15 | Ep Technologies, Inc. | Electrode tip assembly with variable resistance to bending |
US5259395A (en) | 1992-01-15 | 1993-11-09 | Siemens Pacesetter, Inc. | Pacemaker lead with extendable retractable lockable fixing helix |
FR2686136B1 (en) | 1992-01-15 | 1995-06-30 | Alsthom Velan | METALLIC JOINT VALVE, ESPECIALLY BUTTERFLY VALVE. |
US5304214A (en) * | 1992-01-21 | 1994-04-19 | Med Institute, Inc. | Transurethral ablation catheter |
US5267994A (en) | 1992-02-10 | 1993-12-07 | Conmed Corporation | Electrosurgical probe |
US5300099A (en) * | 1992-03-06 | 1994-04-05 | Urologix, Inc. | Gamma matched, helical dipole microwave antenna |
WO1993020768A1 (en) | 1992-04-13 | 1993-10-28 | Ep Technologies, Inc. | Steerable microwave antenna systems for cardiac ablation |
WO1993020886A1 (en) | 1992-04-13 | 1993-10-28 | Ep Technologies, Inc. | Articulated systems for cardiac ablation |
US5281213A (en) * | 1992-04-16 | 1994-01-25 | Implemed, Inc. | Catheter for ice mapping and ablation |
US5300068A (en) | 1992-04-21 | 1994-04-05 | St. Jude Medical, Inc. | Electrosurgical apparatus |
US5236424A (en) | 1992-06-05 | 1993-08-17 | Cardiac Pathways Corporation | Catheter with retractable cannula for delivering a plurality of chemicals |
US5411025A (en) | 1992-06-30 | 1995-05-02 | Cordis Webster, Inc. | Cardiovascular catheter with laterally stable basket-shaped electrode array |
WO1994002077A2 (en) | 1992-07-15 | 1994-02-03 | Angelase, Inc. | Ablation catheter system |
US5300069A (en) * | 1992-08-12 | 1994-04-05 | Daniel Hunsberger | Electrosurgical apparatus for laparoscopic procedures and method of use |
US5470308A (en) | 1992-08-12 | 1995-11-28 | Vidamed, Inc. | Medical probe with biopsy stylet |
US5456662A (en) | 1993-02-02 | 1995-10-10 | Edwards; Stuart D. | Method for reducing snoring by RF ablation of the uvula |
US5556377A (en) | 1992-08-12 | 1996-09-17 | Vidamed, Inc. | Medical probe apparatus with laser and/or microwave monolithic integrated circuit probe |
US5258006A (en) | 1992-08-21 | 1993-11-02 | Everest Medical Corporation | Bipolar electrosurgical forceps |
US5401272A (en) * | 1992-09-25 | 1995-03-28 | Envision Surgical Systems, Inc. | Multimodality probe with extendable bipolar electrodes |
US5471982A (en) | 1992-09-29 | 1995-12-05 | Ep Technologies, Inc. | Cardiac mapping and ablation systems |
US5286253A (en) * | 1992-10-09 | 1994-02-15 | Linvatec Corporation | Angled rotating surgical instrument |
AU5456494A (en) * | 1992-11-13 | 1994-06-08 | American Cardiac Ablation Co., Inc. | Fluid cooled electrosurgical probe |
US5354296A (en) | 1993-03-24 | 1994-10-11 | Symbiosis Corporation | Electrocautery probe with variable morphology electrode |
US5336222A (en) | 1993-03-29 | 1994-08-09 | Boston Scientific Corporation | Integrated catheter for diverse in situ tissue therapy |
US5405346A (en) * | 1993-05-14 | 1995-04-11 | Fidus Medical Technology Corporation | Tunable microwave ablation catheter |
CA2164860C (en) | 1993-06-10 | 2005-09-06 | Mir A. Imran | Transurethral radio frequency ablation apparatus |
US5472441A (en) | 1993-11-08 | 1995-12-05 | Zomed International | Device for treating cancer and non-malignant tumors and methods |
US5599345A (en) * | 1993-11-08 | 1997-02-04 | Zomed International, Inc. | RF treatment apparatus |
US5458597A (en) | 1993-11-08 | 1995-10-17 | Zomed International | Device for treating cancer and non-malignant tumors and methods |
US5589645A (en) * | 1993-11-30 | 1996-12-31 | Unisia Jecs Corporation | Structure of magnetostrictive shaft applicable to magnetostriction-type torque sensor for detecting torque applied to rotatable shaft and method for manufacturing the same |
US5462521A (en) | 1993-12-21 | 1995-10-31 | Angeion Corporation | Fluid cooled and perfused tip for a catheter |
US5437664A (en) | 1994-01-18 | 1995-08-01 | Endovascular, Inc. | Apparatus and method for venous ligation |
US5458596A (en) | 1994-05-06 | 1995-10-17 | Dorsal Orthopedic Corporation | Method and apparatus for controlled contraction of soft tissue |
US6009877A (en) * | 1994-06-24 | 2000-01-04 | Edwards; Stuart D. | Method for treating a sphincter |
US5560358A (en) | 1994-09-08 | 1996-10-01 | Radionics, Inc. | Connector design for multi-contact medical electrode |
US5609151A (en) * | 1994-09-08 | 1997-03-11 | Medtronic, Inc. | Method for R-F ablation |
US5558673A (en) | 1994-09-30 | 1996-09-24 | Vidamed, Inc. | Medical probe device and method having a flexible resilient tape stylet |
US5817092A (en) | 1995-11-09 | 1998-10-06 | Radio Therapeutics Corporation | Apparatus, system and method for delivering radio frequency energy to a treatment site |
-
1995
- 1995-12-22 US US08/577,208 patent/US6689127B1/en not_active Expired - Fee Related
-
2004
- 2004-02-09 US US10/775,747 patent/US20040260282A1/en not_active Abandoned
-
2008
- 2008-03-04 US US12/041,709 patent/US8734439B2/en not_active Expired - Fee Related
Patent Citations (99)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4043342A (en) * | 1974-08-28 | 1977-08-23 | Valleylab, Inc. | Electrosurgical devices having sesquipolar electrode structures incorporated therein |
US4016886A (en) * | 1974-11-26 | 1977-04-12 | The United States Of America As Represented By The United States Energy Research And Development Administration | Method for localizing heating in tumor tissue |
USRE32066E (en) * | 1975-07-11 | 1986-01-21 | Method for treating benign and malignant tumors utilizing radio frequency, electromagnetic radiation | |
US4074718A (en) * | 1976-03-17 | 1978-02-21 | Valleylab, Inc. | Electrosurgical instrument |
US4080959A (en) * | 1976-06-18 | 1978-03-28 | Leveen Robert F | Method for detection of tumors of the breast |
US4095602A (en) * | 1976-09-27 | 1978-06-20 | Leveen Harry H | Multi-portal radiofrequency generator |
US4140130A (en) * | 1977-05-31 | 1979-02-20 | Storm Iii Frederick K | Electrode structure for radio frequency localized heating of tumor bearing tissue |
US4154246A (en) * | 1977-07-25 | 1979-05-15 | Leveen Harry H | Field intensification in radio frequency thermotherapy |
US4346715A (en) * | 1978-07-12 | 1982-08-31 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Hyperthermia heating apparatus |
US4285346A (en) * | 1979-03-14 | 1981-08-25 | Harry V. LeVeen | Electrode system |
US4290435A (en) * | 1979-09-07 | 1981-09-22 | Thermatime A.G. | Internally cooled electrode for hyperthermal treatment and method of use |
US4375220A (en) * | 1980-05-09 | 1983-03-01 | Matvias Fredrick M | Microwave applicator with cooling mechanism for intracavitary treatment of cancer |
US4565200A (en) * | 1980-09-24 | 1986-01-21 | Cosman Eric R | Universal lesion and recording electrode system |
US4574782A (en) * | 1981-11-16 | 1986-03-11 | Corning Glass Works | Radio frequency-induced hyperthermia for tumor therapy |
US5197466A (en) * | 1983-01-21 | 1993-03-30 | Med Institute Inc. | Method and apparatus for volumetric interstitial conductive hyperthermia |
US4676258A (en) * | 1983-01-24 | 1987-06-30 | Kureha Kagaku Kogyo Kabushiki Kaisha | Device for hyperthermia |
US4601296A (en) * | 1983-10-07 | 1986-07-22 | Yeda Research And Development Co., Ltd. | Hyperthermia apparatus |
US4763671A (en) * | 1983-12-27 | 1988-08-16 | Stanford University | Method of treating tumors using selective application of heat and radiation |
US4586490A (en) * | 1984-02-27 | 1986-05-06 | Katz Harry R | Needle inserting instrument means for interstitial radiotherapy |
US4800899A (en) * | 1984-10-22 | 1989-01-31 | Microthermia Technology, Inc. | Apparatus for destroying cells in tumors and the like |
US4983159A (en) * | 1985-03-25 | 1991-01-08 | Rand Robert W | Inductive heating process for use in causing necrosis of neoplasms at selective frequencies |
US4813429A (en) * | 1986-05-12 | 1989-03-21 | Biodan Medical Systems Ltd. | Catheter and probe |
US5003991A (en) * | 1987-03-31 | 1991-04-02 | Olympus Optical Co., Ltd. | Hyperthermia apparatus |
US4823791A (en) * | 1987-05-08 | 1989-04-25 | Circon Acmi Division Of Circon Corporation | Electrosurgical probe apparatus |
US4931047A (en) * | 1987-09-30 | 1990-06-05 | Cavitron, Inc. | Method and apparatus for providing enhanced tissue fragmentation and/or hemostasis |
US4860744A (en) * | 1987-11-02 | 1989-08-29 | Raj K. Anand | Thermoelectrically controlled heat medical catheter |
US4920978A (en) * | 1988-08-31 | 1990-05-01 | Triangle Research And Development Corporation | Method and apparatus for the endoscopic treatment of deep tumors using RF hyperthermia |
US4947842A (en) * | 1988-09-22 | 1990-08-14 | Medical Engineering And Development Institute, Inc. | Method and apparatus for treating tissue with first and second modalities |
US4945912A (en) * | 1988-11-25 | 1990-08-07 | Sensor Electronics, Inc. | Catheter with radiofrequency heating applicator |
US5246438A (en) * | 1988-11-25 | 1993-09-21 | Sensor Electronics, Inc. | Method of radiofrequency ablation |
US5125928A (en) * | 1989-04-13 | 1992-06-30 | Everest Medical Corporation | Ablation catheter with selectively deployable electrodes |
US5078717A (en) * | 1989-04-13 | 1992-01-07 | Everest Medical Corporation | Ablation catheter with selectively deployable electrodes |
US5010897A (en) * | 1989-04-26 | 1991-04-30 | Leveen Harry H | Apparatus for deep heating of cancer |
US5282797A (en) * | 1989-05-30 | 1994-02-01 | Cyrus Chess | Method for treating cutaneous vascular lesions |
US5099756A (en) * | 1989-06-01 | 1992-03-31 | Harry H. Leveen | Radio frequency thermotherapy |
US5009656A (en) * | 1989-08-17 | 1991-04-23 | Mentor O&O Inc. | Bipolar electrosurgical instrument |
US5007908A (en) * | 1989-09-29 | 1991-04-16 | Everest Medical Corporation | Electrosurgical instrument having needle cutting electrode and spot-coag electrode |
US5203782A (en) * | 1990-04-02 | 1993-04-20 | Gudov Vasily F | Method and apparatus for treating malignant tumors by local hyperpyrexia |
US5047027A (en) * | 1990-04-20 | 1991-09-10 | Everest Medical Corporation | Tumor resector |
US5122137A (en) * | 1990-04-27 | 1992-06-16 | Boston Scientific Corporation | Temperature controlled rf coagulation |
US5236410A (en) * | 1990-08-02 | 1993-08-17 | Ferrotherm International, Inc. | Tumor treatment method |
US5100423A (en) * | 1990-08-21 | 1992-03-31 | Medical Engineering & Development Institute, Inc. | Ablation catheter |
US5190541A (en) * | 1990-10-17 | 1993-03-02 | Boston Scientific Corporation | Surgical instrument and method |
US5085659A (en) * | 1990-11-21 | 1992-02-04 | Everest Medical Corporation | Biopsy device with bipolar coagulation capability |
US5542928A (en) * | 1991-05-17 | 1996-08-06 | Innerdyne, Inc. | Method and device for thermal ablation having improved heat transfer |
US5433708A (en) * | 1991-05-17 | 1995-07-18 | Innerdyne, Inc. | Method and device for thermal ablation having improved heat transfer |
US5398683A (en) * | 1991-05-24 | 1995-03-21 | Ep Technologies, Inc. | Combination monophasic action potential/ablation catheter and high-performance filter system |
US5190517A (en) * | 1991-06-06 | 1993-03-02 | Valleylab Inc. | Electrosurgical and ultrasonic surgical system |
US5383917A (en) * | 1991-07-05 | 1995-01-24 | Jawahar M. Desai | Device and method for multi-phase radio-frequency ablation |
US5423808A (en) * | 1991-11-08 | 1995-06-13 | Ep Technologies, Inc. | Systems and methods for radiofrequency ablation with phase sensitive power detection |
US5328467A (en) * | 1991-11-08 | 1994-07-12 | Ep Technologies, Inc. | Catheter having a torque transmitting sleeve |
US5275162A (en) * | 1991-11-08 | 1994-01-04 | Ep Technologies, Inc. | Valve mapping catheter |
US5290286A (en) * | 1991-11-12 | 1994-03-01 | Everest Medical Corporation | Bipolar instrument utilizing one stationary electrode and one movable electrode |
US5197964A (en) * | 1991-11-12 | 1993-03-30 | Everest Medical Corporation | Bipolar instrument utilizing one stationary electrode and one movable electrode |
US5277696A (en) * | 1991-11-19 | 1994-01-11 | Delma Elektro- Und Medizinische Apparatebau Gesellschaft Mbh | Medical high frequency coagulation instrument |
US5197963A (en) * | 1991-12-02 | 1993-03-30 | Everest Medical Corporation | Electrosurgical instrument with extendable sheath for irrigation and aspiration |
US5295955A (en) * | 1992-02-14 | 1994-03-22 | Amt, Inc. | Method and apparatus for microwave aided liposuction |
US5217458A (en) * | 1992-04-09 | 1993-06-08 | Everest Medical Corporation | Bipolar biopsy device utilizing a rotatable, single-hinged moving element |
US5281217A (en) * | 1992-04-13 | 1994-01-25 | Ep Technologies, Inc. | Steerable antenna systems for cardiac ablation that minimize tissue damage and blood coagulation due to conductive heating patterns |
US5314466A (en) * | 1992-04-13 | 1994-05-24 | Ep Technologies, Inc. | Articulated unidirectional microwave antenna systems for cardiac ablation |
US5423807A (en) * | 1992-04-16 | 1995-06-13 | Implemed, Inc. | Cryogenic mapping and ablation catheter |
US5281218A (en) * | 1992-06-05 | 1994-01-25 | Cardiac Pathways Corporation | Catheter having needle electrode for radiofrequency ablation |
US5435805A (en) * | 1992-08-12 | 1995-07-25 | Vidamed, Inc. | Medical probe device with optical viewing capability |
US5542915A (en) * | 1992-08-12 | 1996-08-06 | Vidamed, Inc. | Thermal mapping catheter with ultrasound probe |
US5549644A (en) * | 1992-08-12 | 1996-08-27 | Vidamed, Inc. | Transurethral needle ablation device with cystoscope and method for treatment of the prostate |
US5385544A (en) * | 1992-08-12 | 1995-01-31 | Vidamed, Inc. | BPH ablation method and apparatus |
US5409453A (en) * | 1992-08-12 | 1995-04-25 | Vidamed, Inc. | Steerable medical probe with stylets |
US5542916A (en) * | 1992-08-12 | 1996-08-06 | Vidamed, Inc. | Dual-channel RF power delivery system |
US5421819A (en) * | 1992-08-12 | 1995-06-06 | Vidamed, Inc. | Medical probe device |
US5540655A (en) * | 1992-08-12 | 1996-07-30 | Vidamed, Inc. | PBH ablation method and apparatus |
US5536240A (en) * | 1992-08-12 | 1996-07-16 | Vidamed, Inc. | Medical probe device and method |
US5531677A (en) * | 1992-08-12 | 1996-07-02 | Vidamed, Inc. | Steerable medical probe with stylets |
US5531676A (en) * | 1992-08-12 | 1996-07-02 | Vidamed, Inc. | Medical probe device and method |
US5514131A (en) * | 1992-08-12 | 1996-05-07 | Stuart D. Edwards | Method for the ablation treatment of the uvula |
US5484400A (en) * | 1992-08-12 | 1996-01-16 | Vidamed, Inc. | Dual channel RF delivery system |
US5509419A (en) * | 1992-09-25 | 1996-04-23 | Ep Technologies, Inc. | Cardiac mapping and ablation systems |
US5309910A (en) * | 1992-09-25 | 1994-05-10 | Ep Technologies, Inc. | Cardiac mapping and ablation systems |
US5549108A (en) * | 1992-09-25 | 1996-08-27 | Ep Technologies, Inc. | Cardiac mapping and ablation systems |
US5293869A (en) * | 1992-09-25 | 1994-03-15 | Ep Technologies, Inc. | Cardiac probe with dynamic support for maintaining constant surface contact during heart systole and diastole |
US5313943A (en) * | 1992-09-25 | 1994-05-24 | Ep Technologies, Inc. | Catheters and methods for performing cardiac diagnosis and treatment |
US5342357A (en) * | 1992-11-13 | 1994-08-30 | American Cardiac Ablation Co., Inc. | Fluid cooled electrosurgical cauterization system |
US5334193A (en) * | 1992-11-13 | 1994-08-02 | American Cardiac Ablation Co., Inc. | Fluid cooled ablation catheter |
US5437662A (en) * | 1992-11-13 | 1995-08-01 | American Cardiac Ablation Co., Inc. | Fluid cooled electrosurgical cauterization system |
US5348554A (en) * | 1992-12-01 | 1994-09-20 | Cardiac Pathways Corporation | Catheter for RF ablation with cooled electrode |
US5423811A (en) * | 1992-12-01 | 1995-06-13 | Cardiac Pathways Corporation | Method for RF ablation using cooled electrode |
US5545161A (en) * | 1992-12-01 | 1996-08-13 | Cardiac Pathways Corporation | Catheter for RF ablation having cooled electrode with electrically insulated sleeve |
US5486161A (en) * | 1993-02-02 | 1996-01-23 | Zomed International | Medical probe device and method |
US5403311A (en) * | 1993-03-29 | 1995-04-04 | Boston Scientific Corporation | Electro-coagulation and ablation and other electrotherapeutic treatments of body tissue |
US5417687A (en) * | 1993-04-30 | 1995-05-23 | Medical Scientific, Inc. | Bipolar electrosurgical trocar |
US5431649A (en) * | 1993-08-27 | 1995-07-11 | Medtronic, Inc. | Method and apparatus for R-F ablation |
US5545193A (en) * | 1993-10-15 | 1996-08-13 | Ep Technologies, Inc. | Helically wound radio-frequency emitting electrodes for creating lesions in body tissue |
US5507743A (en) * | 1993-11-08 | 1996-04-16 | Zomed International | Coiled RF electrode treatment apparatus |
US5536267A (en) * | 1993-11-08 | 1996-07-16 | Zomed International | Multiple electrode ablation apparatus |
US5505730A (en) * | 1994-06-24 | 1996-04-09 | Stuart D. Edwards | Thin layer ablation apparatus |
US5545171A (en) * | 1994-09-22 | 1996-08-13 | Vidamed, Inc. | Anastomosis catheter |
US5514130A (en) * | 1994-10-11 | 1996-05-07 | Dorsal Med International | RF apparatus for controlled depth ablation of soft tissue |
US5546267A (en) * | 1994-12-08 | 1996-08-13 | Illinois Tool Works Inc. | Communication circuit protector |
US5855576A (en) * | 1995-03-24 | 1999-01-05 | Board Of Regents Of University Of Nebraska | Method for volumetric tissue ablation |
US5868740A (en) * | 1995-03-24 | 1999-02-09 | Board Of Regents-Univ Of Nebraska | Method for volumetric tissue ablation |
Cited By (31)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US11806070B2 (en) | 2009-11-05 | 2023-11-07 | Stratus Medical, LLC | Methods and systems for spinal radio frequency neurotomy |
US10925664B2 (en) | 2009-11-05 | 2021-02-23 | Stratus Medical, LLC | Methods for radio frequency neurotomy |
US20170065335A1 (en) * | 2009-11-05 | 2017-03-09 | Nimbus Concepts, Llc | Methods and systems for spinal radio frequency neurotomy |
US10736688B2 (en) * | 2009-11-05 | 2020-08-11 | Stratus Medical, LLC | Methods and systems for spinal radio frequency neurotomy |
US20110213356A1 (en) * | 2009-11-05 | 2011-09-01 | Wright Robert E | Methods and systems for spinal radio frequency neurotomy |
US10716618B2 (en) | 2010-05-21 | 2020-07-21 | Stratus Medical, LLC | Systems and methods for tissue ablation |
US20110288540A1 (en) * | 2010-05-21 | 2011-11-24 | Nimbus Concepts, Llc | Systems and methods for tissue ablation |
US10966782B2 (en) * | 2010-05-21 | 2021-04-06 | Stratus Medical, LLC | Needles and systems for radiofrequency neurotomy |
US9730748B2 (en) | 2011-04-12 | 2017-08-15 | Thermedical, Inc. | Devices and methods for shaping therapy in fluid enhanced ablation |
US10881443B2 (en) | 2011-04-12 | 2021-01-05 | Thermedical, Inc. | Devices and methods for shaping therapy in fluid enhanced ablation |
US9937000B2 (en) | 2011-04-12 | 2018-04-10 | Thermedical, Inc. | Methods and devices for controlling ablation therapy |
US11950829B2 (en) | 2011-04-12 | 2024-04-09 | Thermedical, Inc. | Methods and devices for use of degassed fluids with fluid enhanced ablation devices |
US11871979B2 (en) | 2011-04-12 | 2024-01-16 | Thermedical, Inc. | Methods and devices for controlling ablation therapy |
US20120277737A1 (en) * | 2011-04-12 | 2012-11-01 | Thermedical, Inc. | Devices and methods for remote temperature monitoring in fluid enhanced ablation therapy |
US10307201B2 (en) | 2011-04-12 | 2019-06-04 | Thermedical, Inc. | Methods and devices for use of degassed fluids with fluid enhanced ablation devices |
US10448987B2 (en) | 2011-04-12 | 2019-10-22 | Thermedical, Inc. | Methods and devices for controlling ablation therapy |
US10548654B2 (en) | 2011-04-12 | 2020-02-04 | Thermedical, Inc. | Devices and methods for remote temperature monitoring in fluid enhanced ablation therapy |
US11583330B2 (en) | 2011-04-12 | 2023-02-21 | Thermedical, Inc. | Devices and methods for remote temperature monitoring in fluid enhanced ablation therapy |
US11135000B2 (en) | 2011-04-12 | 2021-10-05 | Thermedical, Inc. | Methods and devices for use of degassed fluids with fluid enhanced ablation devices |
US9877768B2 (en) | 2011-04-12 | 2018-01-30 | Thermedical, Inc. | Methods and devices for heating fluid in fluid enhanced ablation therapy |
US9445861B2 (en) | 2011-04-12 | 2016-09-20 | Thermedical, Inc. | Methods and devices for controlling ablation therapy |
US20150141977A1 (en) * | 2012-05-14 | 2015-05-21 | National University Corporation Shiga University Of Medical Science | Organ Resection Tool |
US10166040B2 (en) * | 2012-05-14 | 2019-01-01 | National University Corporation Shiga University Of Medical Science | Organ resection tool |
US10022176B2 (en) | 2012-08-15 | 2018-07-17 | Thermedical, Inc. | Low profile fluid enhanced ablation therapy devices and methods |
US9610396B2 (en) | 2013-03-15 | 2017-04-04 | Thermedical, Inc. | Systems and methods for visualizing fluid enhanced ablation therapy |
US10058385B2 (en) | 2013-03-15 | 2018-08-28 | Thermedical, Inc. | Methods and devices for fluid enhanced microwave ablation therapy |
US11013555B2 (en) | 2016-08-11 | 2021-05-25 | Thermedical, Inc. | Devices and methods for delivering fluid to tissue during ablation therapy |
US9743984B1 (en) | 2016-08-11 | 2017-08-29 | Thermedical, Inc. | Devices and methods for delivering fluid to tissue during ablation therapy |
US11083871B2 (en) | 2018-05-03 | 2021-08-10 | Thermedical, Inc. | Selectively deployable catheter ablation devices |
US11918277B2 (en) | 2018-07-16 | 2024-03-05 | Thermedical, Inc. | Inferred maximum temperature monitoring for irrigated ablation therapy |
CN117276846A (en) * | 2023-11-02 | 2023-12-22 | 广州博远装备科技有限公司 | Shape memory alloy-based self-adaptive short wave antenna |
Also Published As
Publication number | Publication date |
---|---|
US20080154259A1 (en) | 2008-06-26 |
US6689127B1 (en) | 2004-02-10 |
US8734439B2 (en) | 2014-05-27 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6689127B1 (en) | Multiple antenna ablation apparatus and method with multiple sensor feedback | |
US5782827A (en) | Multiple antenna ablation apparatus and method with multiple sensor feedback | |
US5863290A (en) | Multiple antenna ablation apparatus and method | |
US5951547A (en) | Multiple antenna ablation apparatus and method | |
US5728143A (en) | Multiple antenna ablation apparatus and method | |
US6958062B1 (en) | Multiple antenna ablation apparatus and method | |
US5913855A (en) | Multiple antenna ablation apparatus and method | |
US5672174A (en) | Multiple antenna ablation apparatus and method | |
US5672173A (en) | Multiple antenna ablation apparatus and method | |
US6132425A (en) | Cell necrosis apparatus | |
US6080150A (en) | Cell necrosis apparatus | |
US5980517A (en) | Cell necrosis apparatus | |
US5735847A (en) | Multiple antenna ablation apparatus and method with cooling element | |
US5925042A (en) | Multiple antenna ablation apparatus and method | |
US5683384A (en) | Multiple antenna ablation apparatus | |
US6090105A (en) | Multiple electrode ablation apparatus and method | |
US5928229A (en) | Tumor ablation apparatus | |
US5800484A (en) | Multiple antenna ablation apparatus with expanded electrodes | |
US6053937A (en) | Multiple electrode ablation apparatus and method with cooling element | |
EP1109504B1 (en) | Electrosurgical device for cell necrosis induction | |
US6551311B2 (en) | Cell necrosis apparatus and method | |
US20080167649A1 (en) | Ablation apparatus and method | |
US20050101950A1 (en) | Multiple antenna ablation apparatus and method | |
WO1999022657A1 (en) | Multiple antenna ablation apparatus and method |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: RITA MEDICAL SYSTEMS, INC., CALIFORNIA Free format text: CHANGE OF NAME;ASSIGNOR:ZOMED INTERNATIONAL, INC.;REEL/FRAME:018556/0312 Effective date: 19961001 Owner name: ZOMED INTERNATIONAL, INC., CALIFORNIA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:GOUGH, EDWARD J.;STEIN, ALAN A.;REEL/FRAME:018556/0028 Effective date: 19960327 |
|
AS | Assignment |
Owner name: ANGIODYNAMICS, INC., NEW YORK Free format text: MERGER;ASSIGNOR:RITA MEDICAL SYSTEMS, INC.;REEL/FRAME:020674/0816 Effective date: 20070129 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |