CA2149310A1 - Fluid cooled ablation catheter - Google Patents
Fluid cooled ablation catheterInfo
- Publication number
- CA2149310A1 CA2149310A1 CA002149310A CA2149310A CA2149310A1 CA 2149310 A1 CA2149310 A1 CA 2149310A1 CA 002149310 A CA002149310 A CA 002149310A CA 2149310 A CA2149310 A CA 2149310A CA 2149310 A1 CA2149310 A1 CA 2149310A1
- Authority
- CA
- Canada
- Prior art keywords
- catheter
- temperature
- energy
- fluid
- tissue
- 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
- 239000012530 fluid Substances 0.000 title claims abstract description 58
- 238000002679 ablation Methods 0.000 title claims abstract description 41
- 238000000034 method Methods 0.000 claims abstract description 24
- 210000001835 viscera Anatomy 0.000 claims abstract description 5
- 230000004044 response Effects 0.000 claims description 4
- 230000001276 controlling effect Effects 0.000 claims 7
- 230000001105 regulatory effect Effects 0.000 claims 2
- 210000001519 tissue Anatomy 0.000 description 62
- 238000004804 winding Methods 0.000 description 8
- 238000010438 heat treatment Methods 0.000 description 6
- 206010003119 arrhythmia Diseases 0.000 description 5
- 230000006793 arrhythmia Effects 0.000 description 5
- 230000000747 cardiac effect Effects 0.000 description 5
- 239000008280 blood Substances 0.000 description 4
- 210000004369 blood Anatomy 0.000 description 4
- 229940079593 drug Drugs 0.000 description 4
- 239000003814 drug Substances 0.000 description 4
- 230000007246 mechanism Effects 0.000 description 4
- 238000013153 catheter ablation Methods 0.000 description 3
- 239000004020 conductor Substances 0.000 description 3
- 239000012809 cooling fluid Substances 0.000 description 3
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 3
- 230000003902 lesion Effects 0.000 description 3
- 210000000056 organ Anatomy 0.000 description 3
- 230000037361 pathway Effects 0.000 description 3
- 238000001356 surgical procedure Methods 0.000 description 3
- FAPWRFPIFSIZLT-UHFFFAOYSA-M Sodium chloride Chemical compound [Na+].[Cl-] FAPWRFPIFSIZLT-UHFFFAOYSA-M 0.000 description 2
- 210000001992 atrioventricular node Anatomy 0.000 description 2
- 238000001816 cooling Methods 0.000 description 2
- 230000006378 damage Effects 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 201000010099 disease Diseases 0.000 description 2
- 210000005003 heart tissue Anatomy 0.000 description 2
- 150000002500 ions Chemical class 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 238000012544 monitoring process Methods 0.000 description 2
- 210000004165 myocardium Anatomy 0.000 description 2
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 2
- 229920000642 polymer Polymers 0.000 description 2
- WWYNJERNGUHSAO-XUDSTZEESA-N (+)-Norgestrel Chemical compound O=C1CC[C@@H]2[C@H]3CC[C@](CC)([C@](CC4)(O)C#C)[C@@H]4[C@@H]3CCC2=C1 WWYNJERNGUHSAO-XUDSTZEESA-N 0.000 description 1
- 241000272470 Circus Species 0.000 description 1
- 229920004934 Dacron® Polymers 0.000 description 1
- 241000353097 Molva molva Species 0.000 description 1
- 239000002033 PVDF binder Substances 0.000 description 1
- 241001307210 Pene Species 0.000 description 1
- BQCADISMDOOEFD-UHFFFAOYSA-N Silver Chemical compound [Ag] BQCADISMDOOEFD-UHFFFAOYSA-N 0.000 description 1
- 230000005856 abnormality Effects 0.000 description 1
- 230000009471 action Effects 0.000 description 1
- 239000000560 biocompatible material Substances 0.000 description 1
- 230000011128 cardiac conduction Effects 0.000 description 1
- 229920001940 conductive polymer Polymers 0.000 description 1
- 239000002826 coolant Substances 0.000 description 1
- 239000000110 cooling liquid Substances 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 230000001419 dependent effect Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- HQQADJVZYDDRJT-UHFFFAOYSA-N ethene;prop-1-ene Chemical group C=C.CC=C HQQADJVZYDDRJT-UHFFFAOYSA-N 0.000 description 1
- 210000001105 femoral artery Anatomy 0.000 description 1
- 239000000835 fiber Substances 0.000 description 1
- 239000000945 filler Substances 0.000 description 1
- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 description 1
- 229910052737 gold Inorganic materials 0.000 description 1
- 239000010931 gold Substances 0.000 description 1
- 208000019622 heart disease Diseases 0.000 description 1
- 230000002401 inhibitory effect Effects 0.000 description 1
- 230000001788 irregular Effects 0.000 description 1
- 210000004072 lung Anatomy 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 230000003387 muscular Effects 0.000 description 1
- 210000000653 nervous system Anatomy 0.000 description 1
- 239000012811 non-conductive material Substances 0.000 description 1
- 229920001778 nylon Polymers 0.000 description 1
- 238000007747 plating Methods 0.000 description 1
- 229910052697 platinum Inorganic materials 0.000 description 1
- 239000005020 polyethylene terephthalate Substances 0.000 description 1
- 229920000098 polyolefin Polymers 0.000 description 1
- 229920001155 polypropylene Polymers 0.000 description 1
- -1 polytetrafluoroethylene Polymers 0.000 description 1
- 229920001343 polytetrafluoroethylene Polymers 0.000 description 1
- 239000004810 polytetrafluoroethylene Substances 0.000 description 1
- 229920002981 polyvinylidene fluoride Polymers 0.000 description 1
- 238000007674 radiofrequency ablation Methods 0.000 description 1
- 229910052709 silver Inorganic materials 0.000 description 1
- 239000004332 silver Substances 0.000 description 1
- 210000001013 sinoatrial node Anatomy 0.000 description 1
- 239000011780 sodium chloride Substances 0.000 description 1
- 239000011343 solid material Substances 0.000 description 1
- 239000000758 substrate Substances 0.000 description 1
- 230000002889 sympathetic effect Effects 0.000 description 1
- 206010047302 ventricular tachycardia Diseases 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—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
- 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
- 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
- A61B2018/00017—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids with gas
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
- A61B2018/00011—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
- A61B2018/00029—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids open
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00059—Material properties
- A61B2018/00071—Electrical conductivity
- A61B2018/00083—Electrical conductivity low, i.e. electrically insulating
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
- A61B2018/00345—Vascular system
- A61B2018/00351—Heart
- A61B2018/00357—Endocardium
-
- 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
- A61B2018/00744—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
- A61B2018/00773—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
- A61B2018/00815—Temperature measured by a thermistor
-
- 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
- A61B2018/00821—Temperature measured by a thermocouple
-
- 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
- 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
- A61B2018/1435—Spiral
Abstract
A thin, elongate and flexible ablation catheter (14), suitable for delivery to an internal organ, comprises a fluid delivery lumen (26) centrally located within the catheter (14), and first and second electrodes (18, 20) disposed on an outer surface of the catheter (14). The electrodes (18, 20) preferably are helically oriented about the catheter (14). At least one of the electrodes is in communication with a source of electro-surgical energy (12) so as to deliver ablative electro-surgical energy to tissue. The lumen (26) communicates with a fluid supply source (28) such that fluid is conveyed through the lumen (26) and is discharged to adjacent tissue during the delivery of ablative energy. The fluid delivered through the lumen (26) assists in optimizing the electrode temperature. A method and apparatus is also provided to regulate the fluid flow rate based on monitored electrode temperature and/or tissue impedance.
Description
WC~ 94/1~û59 2 1 ~ g 3 1 0 Pcr/US93/1046~
FLUID COOLED ABLATION CATHETER
` s Background of~heInvention The invention relates to an electrosurgical device, in the form of a catheter, which is suitable for use in performing tissue ablation. More particularly, the invention features methods and devices to preven~ excessi~e heating of the electrode.
The ablation of selected areas of organ tissue can be perfoImed during surgical procedures to treat disease or medical disorders. Ablation of certain cardiac tissue is perforrned with increasing frequency to keat certain heart disorders that result in arrh~thrnia.
s The heart is a muscular organ compnsing four separate chambers which cooperate to pump blood throughout the body. The heart muscles must contract andrelax in a coordinated se~uence in order for blood to be passed ~ough ~e circu}atory system in an efficient manner. The heart includes a specialized sys~em for generating 20 impulses to cause rhy~hmical con~action of the heart muscle and for corlducting ~ese impulses rapidly through the heart. In the proper sequence ~e a~aia contract about one sixth of a second prior to ventricles. This enables extra filling of ~e vent~icles before they contract to pump blood through the lungs and to other areas of the body.
The rh~ic impulse of the heart is generated in tl:le sinoatrial node (SA
~5 node)O The SA node has an inherent rhythrn which can ~e modified by the sympathetic and parasyrnpa~etic nervous system. The impulse initiated by the SA node spreadsthrough the atriurn to the atrio-ventricular node (AV node), and then through the Purlcinje fibers to the endocardial surfaces of the ven~icles.
30 I ` The rhy~hmical and condllction system of the heart is s~sceptible to disruption by disease. Damage caused to cardiac tissue can result in the in~b;lity of the cardiac conduction pathways to properly transmit ~e electrical impulses generated in the SA node, leading to arrh~ias, or irregular heartbeats. Cardiac alThythmias c~ often be detected ~rough electrocardiograms.
3s Some fiorms of cardiac arrhy~hmia are able to be controlled ~hrough medication However, other forms of arrhythmia do not respond to medication.
W094/11059 23 49310 -2- PCI`/U593/lV465 Moreover, medication ~ypically does not cure the problem, and the dosage and themedication type must be changed periodically to enable continued con~rol of the problem.
One alternative to medication is the surgical removal of a portion of the cardiac pathway which is responsible for the arrhythrnia. The many dangers associated with open heart surgery render this a less preferred treatrnent option. Recently, however, it has become possible to intravascularly insert a specialized catheter within the heart, for positioning adjacent to the conduction tissue responsible for the arrhy~mia. The0 catheter is adapted to deliver energy ~e.g., radio frequency energy) to ablate or destroy the tissue responsible for an arrhythmia. This has been ~und to be a relatively safe and effective technique for eliminating many causes of arrhythmia. ~arious ablation catheters and techni4ues for their use are described in U.S. Patent Nos. 4,641,649;
4,785,815; 4,869,248; and 4,896,671.
Cardiac ablation catheters typically have at least one electrode at the distal end of the catheter which is adapted to deliver energy to the tissue lesion. O~er electrodes can be proximally positioned on the catheter and used for sensing endocardial signals. Ablation may be achieved by the application of electncal energy, such as radio frequency (RF) or direct ~urrent (DC) energy, from a generator source, ~hrough a~ conductor disposed within the ca~eter, and to the distal elec¢ode.
;~
During ablation procedures, energy, typically in the fo~n of RF energy, is ¦ delivered to tissue by one or more ele~rodes mounted on an endocardial catheter. The 2s delivery of the RF energy through the elec~odes results in an associated temperature rise ;~ in the electrodes, and the heat is transfer~ed to adjacent tissue. Although the application of heat to tissue can destroy the tissue (thus elimi~ating the allhy~uTua), it is preferable to have the tissue ablation effiected by the application of RF energy. Excess heating of the tissue can prolong the abIation procedure as the energy must be applied intermittently 30 1 over a longer pèriod loftime to prevent an excessive fise~ issue temperat~re. ~
Moreover, if thermal ra~er ~an elec~ical destruction of tissue is effected it is often not possible to achieve deeper pene~ation o~the energy becallse the~rise in tissue impedance in tissue adjacent the catheter inhiblts the delivery of RF energy to deeper tissue. This is most coir~nonly a problem where it is necessary to treat deeper or larger lesions.
3~
It would thus be advantageous to develop an ablation catheter, si~i~able ~or use in cardiac ablation proGedures, that is able to effectively deliver electrosurgical energy to tissuej~wi.thout associated excessive heating of Lhe ablatïon electrode and the adjacent tissue. ~ ~ `
WO 94~11059 2 1 ~ 9 3 1 0 It is thus an object of the invention to provide a catheter suitable for use with cardiac ablation procedures utilizing the delivery of radio frequency energy. A
fùrther object is to provide an ablation ca~heter that more effectively delivers radio - s frequency energy to desired tissue without a significant transfer of heat to tissue from the electrode. Another object of the invention is to provide such an ablation catheter together with a system for controlling the tempera~ure of ablation electrodes. It is also an object of the invention to provide an ablation catheter able to operate in a bipolar mode.
Other objects vvill be apparent upon reading the disclosure which ~ollows.
The present invention comprises an intravascular ablation catheter and a system for operating the catheter. The system comprises a thin, flexible, elongate catheter member having dimensions suitable for intravascular delivery to an internal organ. Preferably, the elongate catheter member is constructed of a biocompatible, nonconductive material. A fluid conveying lumen is associated with the elongate catheter member, and preferably is disposed within the catheter along the longitudinal ~o axis thereof. The lumen is adapted to communicate with a fluid supply source to convey fluid from the source and through the lumen to be discharged through an ou~let port disposed at a distal portion of the member.
The catheter also has at least two electrodes, electrically isolated firom one 2~ ano~er, that are mounted on the outer surface of the member. A first electrode is adapted to communicate with an electrosurgical generator unit to deliver abl~tive eIlergy to tissue. A second electrode pre~erably is a ground electrode that enables ~e catheter to fimction in a bipolar mode. In a preferred embodiment the elee~odes are helically oriented about ~e surface of the member.
The catheter of the invention is particular~y usefill for ca~diac ablation procedures. Ablative energy is applied between the two separate elect~odes to destroy tissue within the heart responsible for the arrhythmia. While the ablative energy is applied a fluid such as no~nal saline is delivered through the lumen. The fluid flow 3s ~rough the ]umen serves to limit the heat transferred by the energy-delivering electrode to adjacent tissue. Con~ol of the temperature of the energy-delivering electrode enables effective bipolar operation of the catheter utilizing, for example, RF ablation energy.
.
W~) 94/1105g , PCr/US93tlO465 ~ 1 ~ 9 3 1 0 4 The invention also comprises a method and system for controlling the flow rate of fluid through the lurnen to optimize the cooling of the energy delivering electrode of the catheter. The control system preferably regulates the flow rate based on signals representative of the ternperature ofthe catheter tip ar.d/or tissue impedance.
s Brief Descripti~n Q~th~ I )rawings Figure 1 is a schematic il!ustration of an ablation catheter and the ablation o catheter system of the present invention.
Figure 2 is a perspective view, partia~ly cut away, illustrating the ablation catheter of Figure 1.
Figure 3 is a front end view of the ablation catheter of Figure ` 1.
Figure 4 is a schemabc lllustration of an alternative ablation catheter and ablation catheter system which operates in a monopolar mode.
Figure S is a block diagram illustrating a feedback system useful to control the temperature of energy ~elivering electrodes.
Figure 6 illustrates a circuit useful to implement the feedback system of ` ~, Figure5.
etaiJed Descn~tio f the I~venti~n Figure 1 illustrates an ablation catheter system 10, constructed according to the present invention. T e system 10 comprises an elec~osurgical generator unit 12 30 ~ I which is able to supply electrvsurgical energy to~ catheter 14. Catheter 14 e~mpnses a thin, flexible, elongate member 16 having first and second electrodes 18, 20 mounted over a distal portioII of the outer surface of the member. Electrodes~ 1~, 20 conununicate with electrosurgical generator unit 12 through eleetrode leads 22, 24. Further, a lume 26 is disposed wi~in catheter 14, preferably along the longitudinal axis thereof, and is 35 adapted to convey fluid through the catheter. Lumen 26 preferably communieates with a fluid souree 2B through conduit 30. Fluid is delivered through the lumen to be dlscharged through outlet port 32 which is disposed at a distal portion of the catheter.
The outlet port 32 preferably is disposed in the distal tip of the electrode.
~. ~
WO94/11059 æ~93l0 ~Cr/US93/1046~
Electrodes l 8, 20 preferably are helically oriented about the surface of member 16 as illustrated in Figures 1 through 3. In a preferred embodiment the electrodes are exposed only over a distal portion of the catheter, for example, over a distance of about 8 centimeters. Conductor leads 22, 24 exte:ld within the catheter and s attach to electrodes 18, 20 to convey electrosurgical energy thereto.
The catheter of the system is adapted to perform tissue ablation procedures, and is particularly well suited ~o perform ablation of tissue that forms cardiac accessory pathways which give rise to arrhythmias. The catheter can also be used to ablate cardiac 0 tissue to remedy vther electrical abnormalities, including the causes for ventricular tachycardia. Durillg an abl~tion procedure the catheter is intravascularly delivered to an organ such as the heart. Upon proper positioning of the catheter adjacent tissue to be ablated, electrosurgical energy, preferably in the radio frequency range, is delivered from generator Imit 12 through electrode 18, for example, which may serve as an active, 5 energy-delivering electrode. Electrode 20 preferably ~nctions as a ground elec~ode to enable bipolar operation of the catheter.
In an alternative embodiment, such as illustrated in Figure 4, the catheter may be one that operates in a monopolar mode, delivering electrosurgical energy from 20 generator unit 12 between electrode l 18 and a remote ground plate (not shown~. In such an embodiment electrode 120 may be a sensing eiectrode~ which communicates with monitor 140, and which serves to monitor endocardial signals.
Durirlg ablation procedures the delivery of electrosurgical energy through 2s electrode 18 tends to increase ~he temperature of the elec~ode. Over time~ ~e heat of electrode 18 is transferred to ~issue adjacent to ~e electrode. Such heating of tissue by heat transfer from electrode 18 can be counte~productive in ~at it car~ rapidly dehydrate the ~issue. Upon dessication of the tissue a significant increase in the impedance of the tissue results, thus inhibiting filrther delivery of electrosurgical energy to the tissue. As a 30 I result, ablati~n c~n be less e~ective and~ it may ~e possible to ablate lonly smaller sized areas of tissue. In or~er to ablate larger areas of tissue the ablation procedure must be conducted with intennittent`energy delivery, causing the procedure to require additional time to complete. The heat transfer from the electrode to the tissue thus limits ~e effectiveness of the ab]ation procedure as well as the size of the lesion that can be 35 ablated.
The catheter system of the present invention minimizes the rnagnitude of heat transfer from electrode l 8 to adjacent tissue, and prevents such hea~ transfer from being a limiting factor in the effectiveness of the ablation procedure. In the present WO 9~/11059 2 1 ~ 9 3 1 0 Pcr/US93~10465 invention lumen 26 delivers a fluid through the member 16 and discharges the fluid through port 32 disposed at the distal portion of member 14. ~hen fluid is delivered through lumen 26 during the application of electrosurgical energy, it tends to lower, or at least maintain, the temperature of the electrodes 18, 20 at a level where heat transfer 5 from the active electrode to adjacent tissue is within acceptable limits. Preferably the fluid conveyed through lumen 26 is normal saline, however other suitable fluids including distilled, deior~ized water may be used as well. The tempera~ure of the fluid directed through lumen 26 preferably is in the range of about 1 8C to 30C.
0 In one embodiment fluid may be continuously conveyed through lumen 26 throughout an ablation procedure. In a preferred embodiment however, the fluid flows through the lumen at a variable rate, and preferably only during the delivery ofelectrosurgical energy. The flow rate of the fluid can range from about 1 ml per minute to about l O0 ml per minute. Preferably, the flow rate is in the rallge of about 30 to S0 ml per minute7 and the fluid is not delivered in the absence of electrosurgical elergy delivery.
.
Preferably, the fluid is effective to maintain the temperature of the electrodes below about 60C.
As noted, the ablation catheter of the inve~ion possesses dimensions which render it suitable for in~avascular delivery to internal organs, particularly ~e heart.
Accordingly, the catheter should have a diameter in the range of 2-14 french to accommodate the intravascular delivery of the catheter,~ The leng~ of catheter 14 generally is relatively long (e.g. about 3~ ~eet) to ~acilitate intravascular delivery to the heart, for example, from the femoral artery. While the catheter generally is relatively long, the electrodes 18, 20 are typically disposed only over an area which ranges ~om the distal tip of catheter 14 to about 3 to 5 inches proximal of ~e distal tip.
he catheter is typically manufactured of flexible, biocompati~le materials such as non-conductive polymers. F~er, ~e n~aterial should not be ~errnally ; ~ insulating and should facilitate effective heat trans~er between electrode 1 8 and fluid in lumen 32. Exemplary polymers firom which the ca~eter can be manufactured are well known in the art and include polyolefins, nylons, polytetrafluoroethylene, polyvinylidene fluoride, and fluonnated ethylene-propylene polymers, and woven dacron with fillers.
As noted, the diameter of the catheter may be within a range which is well known in the art. Generally the catheter diameter 13 in the range of 2 to 14 french. Lumen 26 may have a diameter which ranges from about 1 to 3 french.
~ ~ :
WO 9~/1105~ ~ PCr/US93/~04~
7 ~931~ :
- The ratio of the catheter diameter to lumen diameter can be adjusted by one skilled in the art to optimize the cooling effect of fluid passing through lumen 26. Preferably, this ratio is in the range of 2.5:1 to about 3.5:1.
~he catheter may also be constructed to have additional lumens disposed therein. Also, the catheter can have multiple ports disposed in its side su~ace through which fluid can exit.
Virtually any generator able to provide eleckosurgical energy for medical lo applications may be used with the present invention. Preferably, the generator is a voltage determinative, low source impedance generator which provides radio frequency energy. A suitable generator supplies up to about 2 amps of current and has an impedance valuc of less than 10 QhIIlS.
Although virtually any frequency in the RF range may be supplied to the ablation catheter 16, the preferred range is about ~00 to 700 KHz, and most preferably about 550 KHz. The power delivered is about 20 to 50 W.
The energy requirements of the abla~ion catheter are dynamic and may vary depending upon the impedance value of ~e tissue at any time during the treatment. The impedance of tissue vanes among tissue types and the amount of blood present in or around ~e tissue. The amount of current delivered by electrodes 18 or 20 to ~e tissue thus depends on the impedance of the ~issue. Where the tissue eontacted has a lower impedance value, more current will be delivered to the tissue ~rough the electrodes.
Conversely, less current will be delivered where the tissue has a higher impedance value.
The cu~Tent delivered during ablation procedures by catheter 16 is known Ln the art and generally ranges between .1 and .75 amps. The voltage applied to the tissue between the electrodes for such ablation procedures is also known and generally ranges between about 50 to 300 volts nns, and more preferably about 45 to 6û volts nns.
I I ! 30 ! i ; i The switching mechanism or mechanisms used to eontrol the delivery of electrosurgical energy to the catheter can be of any type well known in ~e art. One having ordinary skill in the art will readily understand the most desirable type of switching m~chanism to be used for a partieular application.
Fluid source 28 may comprise a fluid reservoir haYing a pump and/or valve mechanism ~not shown) to control or regulate the flow of fluid. A switching mechanism separate from that used to control the delivery of electrosurgical energy may be used to control the flow of fluid through lumen 26. Altematively~ the flow of fluid may be WO 94/11059 2 1 4 3 3 1 ~1 PCI/US93/10465 coupled to the delivery of electrosurgical energy such that when energy is applied, the pump and/or valve are also activa~ed so as to convey fluid through conduit 30 and lumen 26. The various alternatives which may be utilized to deliver the fluid from source 28 through lumen 26 will be well understood by those having ordinary skill in the art.
s In a preferred embodiment, as noted above, one of electrodes 18, 20 serves as an active, energy delivenng electrode while the other serves as a ground electrode. In an alterna~ive embodiment illus~ated in Figure 4, electrode 118 still serves as the active, energy delivering electrode. However, electrode 120 communicates via electrical lead o 124 with a monitor apparatus 140. In this configuration electrode 120 serves as a sensing electrode, of the type well known in the art, which in combination with monitor 140, detects endocardial signals to assist in the placement of catheter 16 within the heart.
The electrodes 18, 20 preferably are manufactured of highly conductive, s biocompatible materials of the type well known in the art. Exemplary materials from which the electrodes can be constructed includes gold, silver and platinum. The electrodes may be formed of a solid material, or they m~y be formed by plating conductive materials upon a non-conductive substrate such as a polymer.
Fluid flow through the catheter, as noted above, is effective to prevent excessive heating of energy delivering electrodes 18 or 20. Preferably, ~e flow rate is variable and is dependent on monitored electrode temperature and/or tissue impedance values. In a pre~erred embodiment t;ssue impedance may be moI~itored continuously. If the monitored impedance exceeds a predeterlIi~ned set point, a disabling signal can be t~ansmitted to generator uIi~t 12, causing delivery of current to cease. At the same time electrode temperature can be monitored and compared to a temperature set point. Fluid flow can be increased or decreased, as necessary, to maintain the monitored elec~ode temperatu~e at or below ~e set point. It is understood that ~uid flow rate may also be controlled by monitoring tissue impedance alone, or by monitoring electrode temperature 3d l~ alo~e. In ànother embodiment it is possible to use ~he monitored impedance and/~
electrode temperature values to control the ou~cput power of generator unit 12. Such a technique can also ~ssist in preveneing excessive heating of tissue.
Figure 5 illus~ates a biock diagram that is representative of the 35 temperature/impedallee ~feedback system use~ul to control fluid flow rate through the catheter. Energy, sùch as RF energy, is delivered to catheter 10~ from generator u~it ~;; lOO,~and applied to tissue 104. Monitor 106 ascertains tissue impedance, based on the energy delivered to tissue, and compares the measured impedance value to a set value. If the measured impedance exceeds the set value a disabling signal 10~ is transmitted to ::
WO 94/11~59 Z 1 ~ 9 3 1 PCr/US93~10465 generator 100, ceasing ~urther delivery of energy to the catheter 102. Assuming the measured impedance is within acceptable limits energy continues to be applied to the tissue. During the application of energy to tissue a temperature sensing element 107 (such as a the~nistor, thermocouple, or the like) measures the temperature of the energy delivering electrodes. Comparator 108 receives a signal representative of the measured temperature and compares this value to a pre-set signal representative of the desired temperature. Comparator 108 communicates a signal to flow regulator 1 10 representing the need for a higher flow rate (if electrode temperature is high) or to maintain flow rate (if the temperature is adequate).
Further, output 1 17 from temperature comparator 108 can be input to generator 100 to regulate the amount of power delivered by the generator, thus controlling temperature. Similarly, output 119 from impedance monitor and comparator 106 can be input to flow regulator 1010 to regulate fluid flow and thus control electrode temperature.
One or ordinary shll in the art will readily appreciate that the feedback system illustrated in Figure S can be implemented in a variety of ways. Figure 6illustra~es a circuit usefill to facilitate the feedback system.
As shown in Figur~ 6 an energy delivering mearls, such as RF generator 100, is transformer coupled to the catheter 102, to apply a biologically safe voltage to a patient's tissue. In this embodiment, the catheter is represented as a bipolar ablation catheter 102 having an energy delivering electrode 18 and a ground electrode 20. Both 2s electrodes 18,20 are connected to the primary side ofthe transformer windings 1,2. The common primary uindLng 1,2 is magnetical~y coupled via a ~ans~ormer core to the secondary windings 1'~2' so that the cu~ent and voltage of the primary side is reflected to the secondary windings 1',2'.
According to a preferred aspect of the invention, the primary windings 1 of the first hans~rmer t~ couQle the outpu~ voltage of the catheter 102 to the secondary windings 1'. The primary windings 2 of ~Lhe second transformer t2 couple the outpu~
current of the catheter 102 to the secondary windings 2'. Those of ordinary skill in the art will appreciate that the two transformers act as step-down transformers and fiurther serve as means of isolating the high voltage between the cathe~er 102 and the secondary windings or measuring circuit 1',2'.
The measuring circuits determine the root mean square (RMS) Yalues or magnitudes of the current and voltage and these values, represented as voltages, are WO 94/110~9 '~, 1 4 9 3 1 0 PCr/US93/10465 inputted to a dividing circuit D to geometrically calculate, by dividing the RMS voltage value by the RMS current value, the impedance of the body tissue at the catheter electrode 102. Those of ordinary s~ill in the art will understand that the voltage presented at the output of the divider circuit D is representative of and a function of the impedance of the tissue adjacent to the catheter electrodes 1 8,20.
The output voltage of the divider circuit D is presented at the positive(+) input terminal of comparator A. A wltage source VO supplies a voltage across thevariable resistor Rv, thus allowing one to manually adjust, via a knob, the voltage presented at the negative input of comparator A. This vol age represents a maximum impedance value beyond which power will not be applied to the catheter 102.
Specifically, once the tissue is heated to a temperature corresponding to an impedance value greater than the ma:cimum cut-off impedance, the ~F generator 100 will stop supplying power to the catheter 271. Comparator A can be of any of a cormhercially available type that is able to control the arnplitude or pulse vidth modulation of the RF
generator 100.
In one aspect of the invention, the flow rate of the coolant can be controlled based on the tissue impedance~ as represented by signal 115, or based on the catheter tempera~ure, as represented by signal 120. In one embodiment, ~e switch S is activated to allow the impedance signal 115 ~o enter the positive(+) input terminal of comparator A. This signal along wi~ the reference voltage applied to the negative(-) input terminal actuates the comparator A to produce an output signal. If the tissue is heated to a 2s blologically damaging temperature, the tissue impedance will exceed the selected impeda~ce value seen at the negative(-) input terminal ~ereby generating a signal 105 to disable the RF generator 100, ceasing the power supplied to t~e catheter 102.
The output signal of comparator A can fi~er be communicated to pump .:, 1 30 1 125. If the temperat~re of the ablation catheter 102 is high, despite ~he tissue impedance falling within acceptable limits, the pump 125 will adjust the rate of flow of the cooling fluid subsequently applied to ~he catheter electrodes 18, 20 to decrease the catheter tempera~ure. Thus, the output signal of comparator A may either disable the RF
generator's 100 power output (depending on the tissue temperature as reflected by its impedance) or cool the ablation catheter or~perform both operations simul~aneously.
In another aspect of the invention, the rate of flow of the cooling fluid is contro}led based on t~e electrode temperature measured at the catheter tip. The switch S
is actuated so as to transfer to the positive(+) input terrninal of comparator A the WO 94/tlO59 ~ 19 31 0 P~/US93/10465 comparator B output signal 120. The temperature sensor can be a therrnistor T, disposed or adjacent the catheter lQ2. The thermistor T senses temperature and reacts to differential temperatllre changes in a predictable manner. Thus, the therrnistor actively reflects through varying resistance the temperature it is exposed to.
Both leads of the temperature sensitive theImistor T are inputted to the positive(+) and negative(-) terminals of comparator B to produce a signal 120 indicative of the catheter temperature. This signal 120 works in conjunction with the reference voltage inputted at the negative(-~ terminal to activate the comparator A to produce an output signal that is electrically cornmur~icated to the pump 12~. The pump 125, in response to the signal, selectively varies the flow rate of the cooling fluid wi~in lumen 26.
It is understood that the temperature of the electrode can be continuously monitored or randomly sampled to ensure against excessive hea~ing of the tissue.Moreover, the pump employed can be a vaIve, or series thereof, rather ~an an electrical-mecbanical apparatus. The valve can adJust the rate of flow of the cooling liquid from the fluid supply source in the same manner as a pump.
Various modifications may be made in the invention wi~out departing from the intended scope of the claims. For example, the outlet port through which fluid is discharged need not be disposed at the distal tip of the ca~eter member and may instead be disposed in a side wall of the ca~eter.
, ' .. . . . ... .... .. ... ... ... . . ..
FLUID COOLED ABLATION CATHETER
` s Background of~heInvention The invention relates to an electrosurgical device, in the form of a catheter, which is suitable for use in performing tissue ablation. More particularly, the invention features methods and devices to preven~ excessi~e heating of the electrode.
The ablation of selected areas of organ tissue can be perfoImed during surgical procedures to treat disease or medical disorders. Ablation of certain cardiac tissue is perforrned with increasing frequency to keat certain heart disorders that result in arrh~thrnia.
s The heart is a muscular organ compnsing four separate chambers which cooperate to pump blood throughout the body. The heart muscles must contract andrelax in a coordinated se~uence in order for blood to be passed ~ough ~e circu}atory system in an efficient manner. The heart includes a specialized sys~em for generating 20 impulses to cause rhy~hmical con~action of the heart muscle and for corlducting ~ese impulses rapidly through the heart. In the proper sequence ~e a~aia contract about one sixth of a second prior to ventricles. This enables extra filling of ~e vent~icles before they contract to pump blood through the lungs and to other areas of the body.
The rh~ic impulse of the heart is generated in tl:le sinoatrial node (SA
~5 node)O The SA node has an inherent rhythrn which can ~e modified by the sympathetic and parasyrnpa~etic nervous system. The impulse initiated by the SA node spreadsthrough the atriurn to the atrio-ventricular node (AV node), and then through the Purlcinje fibers to the endocardial surfaces of the ven~icles.
30 I ` The rhy~hmical and condllction system of the heart is s~sceptible to disruption by disease. Damage caused to cardiac tissue can result in the in~b;lity of the cardiac conduction pathways to properly transmit ~e electrical impulses generated in the SA node, leading to arrh~ias, or irregular heartbeats. Cardiac alThythmias c~ often be detected ~rough electrocardiograms.
3s Some fiorms of cardiac arrhy~hmia are able to be controlled ~hrough medication However, other forms of arrhythmia do not respond to medication.
W094/11059 23 49310 -2- PCI`/U593/lV465 Moreover, medication ~ypically does not cure the problem, and the dosage and themedication type must be changed periodically to enable continued con~rol of the problem.
One alternative to medication is the surgical removal of a portion of the cardiac pathway which is responsible for the arrhythrnia. The many dangers associated with open heart surgery render this a less preferred treatrnent option. Recently, however, it has become possible to intravascularly insert a specialized catheter within the heart, for positioning adjacent to the conduction tissue responsible for the arrhy~mia. The0 catheter is adapted to deliver energy ~e.g., radio frequency energy) to ablate or destroy the tissue responsible for an arrhythmia. This has been ~und to be a relatively safe and effective technique for eliminating many causes of arrhythmia. ~arious ablation catheters and techni4ues for their use are described in U.S. Patent Nos. 4,641,649;
4,785,815; 4,869,248; and 4,896,671.
Cardiac ablation catheters typically have at least one electrode at the distal end of the catheter which is adapted to deliver energy to the tissue lesion. O~er electrodes can be proximally positioned on the catheter and used for sensing endocardial signals. Ablation may be achieved by the application of electncal energy, such as radio frequency (RF) or direct ~urrent (DC) energy, from a generator source, ~hrough a~ conductor disposed within the ca~eter, and to the distal elec¢ode.
;~
During ablation procedures, energy, typically in the fo~n of RF energy, is ¦ delivered to tissue by one or more ele~rodes mounted on an endocardial catheter. The 2s delivery of the RF energy through the elec~odes results in an associated temperature rise ;~ in the electrodes, and the heat is transfer~ed to adjacent tissue. Although the application of heat to tissue can destroy the tissue (thus elimi~ating the allhy~uTua), it is preferable to have the tissue ablation effiected by the application of RF energy. Excess heating of the tissue can prolong the abIation procedure as the energy must be applied intermittently 30 1 over a longer pèriod loftime to prevent an excessive fise~ issue temperat~re. ~
Moreover, if thermal ra~er ~an elec~ical destruction of tissue is effected it is often not possible to achieve deeper pene~ation o~the energy becallse the~rise in tissue impedance in tissue adjacent the catheter inhiblts the delivery of RF energy to deeper tissue. This is most coir~nonly a problem where it is necessary to treat deeper or larger lesions.
3~
It would thus be advantageous to develop an ablation catheter, si~i~able ~or use in cardiac ablation proGedures, that is able to effectively deliver electrosurgical energy to tissuej~wi.thout associated excessive heating of Lhe ablatïon electrode and the adjacent tissue. ~ ~ `
WO 94~11059 2 1 ~ 9 3 1 0 It is thus an object of the invention to provide a catheter suitable for use with cardiac ablation procedures utilizing the delivery of radio frequency energy. A
fùrther object is to provide an ablation ca~heter that more effectively delivers radio - s frequency energy to desired tissue without a significant transfer of heat to tissue from the electrode. Another object of the invention is to provide such an ablation catheter together with a system for controlling the tempera~ure of ablation electrodes. It is also an object of the invention to provide an ablation catheter able to operate in a bipolar mode.
Other objects vvill be apparent upon reading the disclosure which ~ollows.
The present invention comprises an intravascular ablation catheter and a system for operating the catheter. The system comprises a thin, flexible, elongate catheter member having dimensions suitable for intravascular delivery to an internal organ. Preferably, the elongate catheter member is constructed of a biocompatible, nonconductive material. A fluid conveying lumen is associated with the elongate catheter member, and preferably is disposed within the catheter along the longitudinal ~o axis thereof. The lumen is adapted to communicate with a fluid supply source to convey fluid from the source and through the lumen to be discharged through an ou~let port disposed at a distal portion of the member.
The catheter also has at least two electrodes, electrically isolated firom one 2~ ano~er, that are mounted on the outer surface of the member. A first electrode is adapted to communicate with an electrosurgical generator unit to deliver abl~tive eIlergy to tissue. A second electrode pre~erably is a ground electrode that enables ~e catheter to fimction in a bipolar mode. In a preferred embodiment the elee~odes are helically oriented about ~e surface of the member.
The catheter of the invention is particular~y usefill for ca~diac ablation procedures. Ablative energy is applied between the two separate elect~odes to destroy tissue within the heart responsible for the arrhythmia. While the ablative energy is applied a fluid such as no~nal saline is delivered through the lumen. The fluid flow 3s ~rough the ]umen serves to limit the heat transferred by the energy-delivering electrode to adjacent tissue. Con~ol of the temperature of the energy-delivering electrode enables effective bipolar operation of the catheter utilizing, for example, RF ablation energy.
.
W~) 94/1105g , PCr/US93tlO465 ~ 1 ~ 9 3 1 0 4 The invention also comprises a method and system for controlling the flow rate of fluid through the lurnen to optimize the cooling of the energy delivering electrode of the catheter. The control system preferably regulates the flow rate based on signals representative of the ternperature ofthe catheter tip ar.d/or tissue impedance.
s Brief Descripti~n Q~th~ I )rawings Figure 1 is a schematic il!ustration of an ablation catheter and the ablation o catheter system of the present invention.
Figure 2 is a perspective view, partia~ly cut away, illustrating the ablation catheter of Figure 1.
Figure 3 is a front end view of the ablation catheter of Figure ` 1.
Figure 4 is a schemabc lllustration of an alternative ablation catheter and ablation catheter system which operates in a monopolar mode.
Figure S is a block diagram illustrating a feedback system useful to control the temperature of energy ~elivering electrodes.
Figure 6 illustrates a circuit useful to implement the feedback system of ` ~, Figure5.
etaiJed Descn~tio f the I~venti~n Figure 1 illustrates an ablation catheter system 10, constructed according to the present invention. T e system 10 comprises an elec~osurgical generator unit 12 30 ~ I which is able to supply electrvsurgical energy to~ catheter 14. Catheter 14 e~mpnses a thin, flexible, elongate member 16 having first and second electrodes 18, 20 mounted over a distal portioII of the outer surface of the member. Electrodes~ 1~, 20 conununicate with electrosurgical generator unit 12 through eleetrode leads 22, 24. Further, a lume 26 is disposed wi~in catheter 14, preferably along the longitudinal axis thereof, and is 35 adapted to convey fluid through the catheter. Lumen 26 preferably communieates with a fluid souree 2B through conduit 30. Fluid is delivered through the lumen to be dlscharged through outlet port 32 which is disposed at a distal portion of the catheter.
The outlet port 32 preferably is disposed in the distal tip of the electrode.
~. ~
WO94/11059 æ~93l0 ~Cr/US93/1046~
Electrodes l 8, 20 preferably are helically oriented about the surface of member 16 as illustrated in Figures 1 through 3. In a preferred embodiment the electrodes are exposed only over a distal portion of the catheter, for example, over a distance of about 8 centimeters. Conductor leads 22, 24 exte:ld within the catheter and s attach to electrodes 18, 20 to convey electrosurgical energy thereto.
The catheter of the system is adapted to perform tissue ablation procedures, and is particularly well suited ~o perform ablation of tissue that forms cardiac accessory pathways which give rise to arrhythmias. The catheter can also be used to ablate cardiac 0 tissue to remedy vther electrical abnormalities, including the causes for ventricular tachycardia. Durillg an abl~tion procedure the catheter is intravascularly delivered to an organ such as the heart. Upon proper positioning of the catheter adjacent tissue to be ablated, electrosurgical energy, preferably in the radio frequency range, is delivered from generator Imit 12 through electrode 18, for example, which may serve as an active, 5 energy-delivering electrode. Electrode 20 preferably ~nctions as a ground elec~ode to enable bipolar operation of the catheter.
In an alternative embodiment, such as illustrated in Figure 4, the catheter may be one that operates in a monopolar mode, delivering electrosurgical energy from 20 generator unit 12 between electrode l 18 and a remote ground plate (not shown~. In such an embodiment electrode 120 may be a sensing eiectrode~ which communicates with monitor 140, and which serves to monitor endocardial signals.
Durirlg ablation procedures the delivery of electrosurgical energy through 2s electrode 18 tends to increase ~he temperature of the elec~ode. Over time~ ~e heat of electrode 18 is transferred to ~issue adjacent to ~e electrode. Such heating of tissue by heat transfer from electrode 18 can be counte~productive in ~at it car~ rapidly dehydrate the ~issue. Upon dessication of the tissue a significant increase in the impedance of the tissue results, thus inhibiting filrther delivery of electrosurgical energy to the tissue. As a 30 I result, ablati~n c~n be less e~ective and~ it may ~e possible to ablate lonly smaller sized areas of tissue. In or~er to ablate larger areas of tissue the ablation procedure must be conducted with intennittent`energy delivery, causing the procedure to require additional time to complete. The heat transfer from the electrode to the tissue thus limits ~e effectiveness of the ab]ation procedure as well as the size of the lesion that can be 35 ablated.
The catheter system of the present invention minimizes the rnagnitude of heat transfer from electrode l 8 to adjacent tissue, and prevents such hea~ transfer from being a limiting factor in the effectiveness of the ablation procedure. In the present WO 9~/11059 2 1 ~ 9 3 1 0 Pcr/US93~10465 invention lumen 26 delivers a fluid through the member 16 and discharges the fluid through port 32 disposed at the distal portion of member 14. ~hen fluid is delivered through lumen 26 during the application of electrosurgical energy, it tends to lower, or at least maintain, the temperature of the electrodes 18, 20 at a level where heat transfer 5 from the active electrode to adjacent tissue is within acceptable limits. Preferably the fluid conveyed through lumen 26 is normal saline, however other suitable fluids including distilled, deior~ized water may be used as well. The tempera~ure of the fluid directed through lumen 26 preferably is in the range of about 1 8C to 30C.
0 In one embodiment fluid may be continuously conveyed through lumen 26 throughout an ablation procedure. In a preferred embodiment however, the fluid flows through the lumen at a variable rate, and preferably only during the delivery ofelectrosurgical energy. The flow rate of the fluid can range from about 1 ml per minute to about l O0 ml per minute. Preferably, the flow rate is in the rallge of about 30 to S0 ml per minute7 and the fluid is not delivered in the absence of electrosurgical elergy delivery.
.
Preferably, the fluid is effective to maintain the temperature of the electrodes below about 60C.
As noted, the ablation catheter of the inve~ion possesses dimensions which render it suitable for in~avascular delivery to internal organs, particularly ~e heart.
Accordingly, the catheter should have a diameter in the range of 2-14 french to accommodate the intravascular delivery of the catheter,~ The leng~ of catheter 14 generally is relatively long (e.g. about 3~ ~eet) to ~acilitate intravascular delivery to the heart, for example, from the femoral artery. While the catheter generally is relatively long, the electrodes 18, 20 are typically disposed only over an area which ranges ~om the distal tip of catheter 14 to about 3 to 5 inches proximal of ~e distal tip.
he catheter is typically manufactured of flexible, biocompati~le materials such as non-conductive polymers. F~er, ~e n~aterial should not be ~errnally ; ~ insulating and should facilitate effective heat trans~er between electrode 1 8 and fluid in lumen 32. Exemplary polymers firom which the ca~eter can be manufactured are well known in the art and include polyolefins, nylons, polytetrafluoroethylene, polyvinylidene fluoride, and fluonnated ethylene-propylene polymers, and woven dacron with fillers.
As noted, the diameter of the catheter may be within a range which is well known in the art. Generally the catheter diameter 13 in the range of 2 to 14 french. Lumen 26 may have a diameter which ranges from about 1 to 3 french.
~ ~ :
WO 9~/1105~ ~ PCr/US93/~04~
7 ~931~ :
- The ratio of the catheter diameter to lumen diameter can be adjusted by one skilled in the art to optimize the cooling effect of fluid passing through lumen 26. Preferably, this ratio is in the range of 2.5:1 to about 3.5:1.
~he catheter may also be constructed to have additional lumens disposed therein. Also, the catheter can have multiple ports disposed in its side su~ace through which fluid can exit.
Virtually any generator able to provide eleckosurgical energy for medical lo applications may be used with the present invention. Preferably, the generator is a voltage determinative, low source impedance generator which provides radio frequency energy. A suitable generator supplies up to about 2 amps of current and has an impedance valuc of less than 10 QhIIlS.
Although virtually any frequency in the RF range may be supplied to the ablation catheter 16, the preferred range is about ~00 to 700 KHz, and most preferably about 550 KHz. The power delivered is about 20 to 50 W.
The energy requirements of the abla~ion catheter are dynamic and may vary depending upon the impedance value of ~e tissue at any time during the treatment. The impedance of tissue vanes among tissue types and the amount of blood present in or around ~e tissue. The amount of current delivered by electrodes 18 or 20 to ~e tissue thus depends on the impedance of the ~issue. Where the tissue eontacted has a lower impedance value, more current will be delivered to the tissue ~rough the electrodes.
Conversely, less current will be delivered where the tissue has a higher impedance value.
The cu~Tent delivered during ablation procedures by catheter 16 is known Ln the art and generally ranges between .1 and .75 amps. The voltage applied to the tissue between the electrodes for such ablation procedures is also known and generally ranges between about 50 to 300 volts nns, and more preferably about 45 to 6û volts nns.
I I ! 30 ! i ; i The switching mechanism or mechanisms used to eontrol the delivery of electrosurgical energy to the catheter can be of any type well known in ~e art. One having ordinary skill in the art will readily understand the most desirable type of switching m~chanism to be used for a partieular application.
Fluid source 28 may comprise a fluid reservoir haYing a pump and/or valve mechanism ~not shown) to control or regulate the flow of fluid. A switching mechanism separate from that used to control the delivery of electrosurgical energy may be used to control the flow of fluid through lumen 26. Altematively~ the flow of fluid may be WO 94/11059 2 1 4 3 3 1 ~1 PCI/US93/10465 coupled to the delivery of electrosurgical energy such that when energy is applied, the pump and/or valve are also activa~ed so as to convey fluid through conduit 30 and lumen 26. The various alternatives which may be utilized to deliver the fluid from source 28 through lumen 26 will be well understood by those having ordinary skill in the art.
s In a preferred embodiment, as noted above, one of electrodes 18, 20 serves as an active, energy delivenng electrode while the other serves as a ground electrode. In an alterna~ive embodiment illus~ated in Figure 4, electrode 118 still serves as the active, energy delivering electrode. However, electrode 120 communicates via electrical lead o 124 with a monitor apparatus 140. In this configuration electrode 120 serves as a sensing electrode, of the type well known in the art, which in combination with monitor 140, detects endocardial signals to assist in the placement of catheter 16 within the heart.
The electrodes 18, 20 preferably are manufactured of highly conductive, s biocompatible materials of the type well known in the art. Exemplary materials from which the electrodes can be constructed includes gold, silver and platinum. The electrodes may be formed of a solid material, or they m~y be formed by plating conductive materials upon a non-conductive substrate such as a polymer.
Fluid flow through the catheter, as noted above, is effective to prevent excessive heating of energy delivering electrodes 18 or 20. Preferably, ~e flow rate is variable and is dependent on monitored electrode temperature and/or tissue impedance values. In a pre~erred embodiment t;ssue impedance may be moI~itored continuously. If the monitored impedance exceeds a predeterlIi~ned set point, a disabling signal can be t~ansmitted to generator uIi~t 12, causing delivery of current to cease. At the same time electrode temperature can be monitored and compared to a temperature set point. Fluid flow can be increased or decreased, as necessary, to maintain the monitored elec~ode temperatu~e at or below ~e set point. It is understood that ~uid flow rate may also be controlled by monitoring tissue impedance alone, or by monitoring electrode temperature 3d l~ alo~e. In ànother embodiment it is possible to use ~he monitored impedance and/~
electrode temperature values to control the ou~cput power of generator unit 12. Such a technique can also ~ssist in preveneing excessive heating of tissue.
Figure 5 illus~ates a biock diagram that is representative of the 35 temperature/impedallee ~feedback system use~ul to control fluid flow rate through the catheter. Energy, sùch as RF energy, is delivered to catheter 10~ from generator u~it ~;; lOO,~and applied to tissue 104. Monitor 106 ascertains tissue impedance, based on the energy delivered to tissue, and compares the measured impedance value to a set value. If the measured impedance exceeds the set value a disabling signal 10~ is transmitted to ::
WO 94/11~59 Z 1 ~ 9 3 1 PCr/US93~10465 generator 100, ceasing ~urther delivery of energy to the catheter 102. Assuming the measured impedance is within acceptable limits energy continues to be applied to the tissue. During the application of energy to tissue a temperature sensing element 107 (such as a the~nistor, thermocouple, or the like) measures the temperature of the energy delivering electrodes. Comparator 108 receives a signal representative of the measured temperature and compares this value to a pre-set signal representative of the desired temperature. Comparator 108 communicates a signal to flow regulator 1 10 representing the need for a higher flow rate (if electrode temperature is high) or to maintain flow rate (if the temperature is adequate).
Further, output 1 17 from temperature comparator 108 can be input to generator 100 to regulate the amount of power delivered by the generator, thus controlling temperature. Similarly, output 119 from impedance monitor and comparator 106 can be input to flow regulator 1010 to regulate fluid flow and thus control electrode temperature.
One or ordinary shll in the art will readily appreciate that the feedback system illustrated in Figure S can be implemented in a variety of ways. Figure 6illustra~es a circuit usefill to facilitate the feedback system.
As shown in Figur~ 6 an energy delivering mearls, such as RF generator 100, is transformer coupled to the catheter 102, to apply a biologically safe voltage to a patient's tissue. In this embodiment, the catheter is represented as a bipolar ablation catheter 102 having an energy delivering electrode 18 and a ground electrode 20. Both 2s electrodes 18,20 are connected to the primary side ofthe transformer windings 1,2. The common primary uindLng 1,2 is magnetical~y coupled via a ~ans~ormer core to the secondary windings 1'~2' so that the cu~ent and voltage of the primary side is reflected to the secondary windings 1',2'.
According to a preferred aspect of the invention, the primary windings 1 of the first hans~rmer t~ couQle the outpu~ voltage of the catheter 102 to the secondary windings 1'. The primary windings 2 of ~Lhe second transformer t2 couple the outpu~
current of the catheter 102 to the secondary windings 2'. Those of ordinary skill in the art will appreciate that the two transformers act as step-down transformers and fiurther serve as means of isolating the high voltage between the cathe~er 102 and the secondary windings or measuring circuit 1',2'.
The measuring circuits determine the root mean square (RMS) Yalues or magnitudes of the current and voltage and these values, represented as voltages, are WO 94/110~9 '~, 1 4 9 3 1 0 PCr/US93/10465 inputted to a dividing circuit D to geometrically calculate, by dividing the RMS voltage value by the RMS current value, the impedance of the body tissue at the catheter electrode 102. Those of ordinary s~ill in the art will understand that the voltage presented at the output of the divider circuit D is representative of and a function of the impedance of the tissue adjacent to the catheter electrodes 1 8,20.
The output voltage of the divider circuit D is presented at the positive(+) input terminal of comparator A. A wltage source VO supplies a voltage across thevariable resistor Rv, thus allowing one to manually adjust, via a knob, the voltage presented at the negative input of comparator A. This vol age represents a maximum impedance value beyond which power will not be applied to the catheter 102.
Specifically, once the tissue is heated to a temperature corresponding to an impedance value greater than the ma:cimum cut-off impedance, the ~F generator 100 will stop supplying power to the catheter 271. Comparator A can be of any of a cormhercially available type that is able to control the arnplitude or pulse vidth modulation of the RF
generator 100.
In one aspect of the invention, the flow rate of the coolant can be controlled based on the tissue impedance~ as represented by signal 115, or based on the catheter tempera~ure, as represented by signal 120. In one embodiment, ~e switch S is activated to allow the impedance signal 115 ~o enter the positive(+) input terminal of comparator A. This signal along wi~ the reference voltage applied to the negative(-) input terminal actuates the comparator A to produce an output signal. If the tissue is heated to a 2s blologically damaging temperature, the tissue impedance will exceed the selected impeda~ce value seen at the negative(-) input terminal ~ereby generating a signal 105 to disable the RF generator 100, ceasing the power supplied to t~e catheter 102.
The output signal of comparator A can fi~er be communicated to pump .:, 1 30 1 125. If the temperat~re of the ablation catheter 102 is high, despite ~he tissue impedance falling within acceptable limits, the pump 125 will adjust the rate of flow of the cooling fluid subsequently applied to ~he catheter electrodes 18, 20 to decrease the catheter tempera~ure. Thus, the output signal of comparator A may either disable the RF
generator's 100 power output (depending on the tissue temperature as reflected by its impedance) or cool the ablation catheter or~perform both operations simul~aneously.
In another aspect of the invention, the rate of flow of the cooling fluid is contro}led based on t~e electrode temperature measured at the catheter tip. The switch S
is actuated so as to transfer to the positive(+) input terrninal of comparator A the WO 94/tlO59 ~ 19 31 0 P~/US93/10465 comparator B output signal 120. The temperature sensor can be a therrnistor T, disposed or adjacent the catheter lQ2. The thermistor T senses temperature and reacts to differential temperatllre changes in a predictable manner. Thus, the therrnistor actively reflects through varying resistance the temperature it is exposed to.
Both leads of the temperature sensitive theImistor T are inputted to the positive(+) and negative(-) terminals of comparator B to produce a signal 120 indicative of the catheter temperature. This signal 120 works in conjunction with the reference voltage inputted at the negative(-~ terminal to activate the comparator A to produce an output signal that is electrically cornmur~icated to the pump 12~. The pump 125, in response to the signal, selectively varies the flow rate of the cooling fluid wi~in lumen 26.
It is understood that the temperature of the electrode can be continuously monitored or randomly sampled to ensure against excessive hea~ing of the tissue.Moreover, the pump employed can be a vaIve, or series thereof, rather ~an an electrical-mecbanical apparatus. The valve can adJust the rate of flow of the cooling liquid from the fluid supply source in the same manner as a pump.
Various modifications may be made in the invention wi~out departing from the intended scope of the claims. For example, the outlet port through which fluid is discharged need not be disposed at the distal tip of the ca~eter member and may instead be disposed in a side wall of the ca~eter.
, ' .. . . . ... .... .. ... ... ... . . ..
Claims
14. Canceled.
15. (Amended) A method for controlling the temperature of an energy delivering electrode disposed on an ablation catheter, comprising:
providing an ablation catheter in the form of a thin, flexible elongate member having disposed at a distal portion thereof at least one energy delivering electrode, the catheter having a fluid delivering lumen associated therewith and being adapted for intravascular delivery to an internal organ and being in electrical communication with an electrosurgical generator unit;
intravascularly delivering the catheter to an internal organ;
delivering electrosurgical energy from the generator unit through the catheter to the energy delivering electrode and adjacent tissue;
measuring the temperature of the energy delivering electrode and generating a signal representative thereof;
comparing the measured temperature of the energy delivering electrode to a predetermined maximum temperature value and generating a signal representative of the difference between the measured temperature and the predetermined temperature;
selectively delivering fluid through the lumen of the catheter at a desired flow rate; and adjusting the flow rate of fluid through the lumen of the catheter based on the difference between measured temperature and the predetermined temperature to maintain the measured temperature at or below the predetermined temperature.
16. (Amended) The method of claim 15 wherein the step of selectively delivering fluid further comprises the step of allowing the fluid to exit the catheter at a distal end thereof.
17. The method of claim 16 wherein the flow rate is adjusted by a pump means for controlling fluid flow rate that operates in response to a signal representative of the difference between the measured temperature and the predetermined temperature.
18. The method of claim 15 wherein the fluid flow rate ranges from 1 to 50 ml/minute.
19. (Amended) The method of claim 15 further comprising the step of controlling an amount of electrosurgical energy delivered by the generator unit in conjunction with controlling the temperature of the energy delivering electrode by:
measuring the impedance of the tissue based on the energy applied thereto and generating a signal representative of the measured tissue impedance value;
comparing the measured tissue impedance value with a predetermined maximum impedance value; and transmitting to the generator unit a signal to cease further energy delivery if the measured tissue impedance exceeds the predetermined maximum impedance value.
20. (Amended) A system for controlling the temperature of an energy delivering electrode disposed on an ablation catheter, comprising:
a thin, flexible elongate catheter having a central lumen disposed therein to enable fluid to be conveyed through the catheter, at a variable rate of flow, for discharge at a distal portion of the catheter, the catheter having at least one energy delivering electrode disposed at a distal portion of the catheter and the catheter having dimensions suitable for intravascular delivery;
an electrosurgical generator unit in electrical communication with the catheter for providing a desired electrosurgical energy output to the electrode for delivery to tissue adjacent the electrode;
a fluid supply source in communication with the lumen;
temperature sensing means associated with the catheter for sensing the temperature of the energy delivering electrode and generating a signal representative of measured electrode temperature;
comparator means for comparing the measured electrode temperature and a predetermined maximum temperature value and generating a signal representative of the temperature difference; and a fluid control means for regulating the rate of flow of fluid through the lumen in response to the signal from the comparator means representative of the temperature difference to maintain the measured electrode temperature at or below the predetermined temperature.
21. The system of claim 20 wherein the temperature sensing means comprises a thermistor or a thermocouple.
22. (Amended) The system of claim 20, further comprising a subsystem for controlling the electrosurgical energy output of the generator unit, the subsystem comprising:
impedance measuring means for measuring the impedance value of tissue based on the energy applied thereto;
impedance comparing means for comparing the measured impedance value of tissue to a predetermined maximum impedance value, the impedance comparing means generating a disabling signal if the measured impedance value exceeds the predetermined maximum impedance value; and means for communicating the disabling signal to the generator unit to cease further delivery of energy from the generator unit to the catheter.
23. (Amended) A system for controlling the temperature of an energy delivering electrode disposed on an ablation catheter, comprising:
a thin, flexible elongate catheter having a central lumen disposed therein to enable fluid to be conveyed through the catheter, at a variable flow rate, for discharge at a distal portion of the catheter, the catheter having at least one energy delivering electrode disposed at a distal portion of the catheter and the catheter having dimensions suitable for intravascular delivery;
an electrosurgical generator unit in electrical communication with the catheter for supplying electrosurgical energy to the electrode for delivery to tissue adjacent the electrode;
a fluid supply source in communication with the lumen;
impedance measuring means for measuring the impedance value of tissue based on the energy applied thereto;
impedance comparing means for comparing the measured impedance value of tissue to a predetermined maximum impedance value, the impedance comparing means generating a signal representative of the difference between themeasured impedance value and the predetermined maximum impedance value; and a fluid control means for regulating the rate of flow of fluid through the lumen in response to the signal from the impedance comparing means representative of the impedance difference to maintain the measured impedance value at or below the predetermined maximum impedance value.
15. (Amended) A method for controlling the temperature of an energy delivering electrode disposed on an ablation catheter, comprising:
providing an ablation catheter in the form of a thin, flexible elongate member having disposed at a distal portion thereof at least one energy delivering electrode, the catheter having a fluid delivering lumen associated therewith and being adapted for intravascular delivery to an internal organ and being in electrical communication with an electrosurgical generator unit;
intravascularly delivering the catheter to an internal organ;
delivering electrosurgical energy from the generator unit through the catheter to the energy delivering electrode and adjacent tissue;
measuring the temperature of the energy delivering electrode and generating a signal representative thereof;
comparing the measured temperature of the energy delivering electrode to a predetermined maximum temperature value and generating a signal representative of the difference between the measured temperature and the predetermined temperature;
selectively delivering fluid through the lumen of the catheter at a desired flow rate; and adjusting the flow rate of fluid through the lumen of the catheter based on the difference between measured temperature and the predetermined temperature to maintain the measured temperature at or below the predetermined temperature.
16. (Amended) The method of claim 15 wherein the step of selectively delivering fluid further comprises the step of allowing the fluid to exit the catheter at a distal end thereof.
17. The method of claim 16 wherein the flow rate is adjusted by a pump means for controlling fluid flow rate that operates in response to a signal representative of the difference between the measured temperature and the predetermined temperature.
18. The method of claim 15 wherein the fluid flow rate ranges from 1 to 50 ml/minute.
19. (Amended) The method of claim 15 further comprising the step of controlling an amount of electrosurgical energy delivered by the generator unit in conjunction with controlling the temperature of the energy delivering electrode by:
measuring the impedance of the tissue based on the energy applied thereto and generating a signal representative of the measured tissue impedance value;
comparing the measured tissue impedance value with a predetermined maximum impedance value; and transmitting to the generator unit a signal to cease further energy delivery if the measured tissue impedance exceeds the predetermined maximum impedance value.
20. (Amended) A system for controlling the temperature of an energy delivering electrode disposed on an ablation catheter, comprising:
a thin, flexible elongate catheter having a central lumen disposed therein to enable fluid to be conveyed through the catheter, at a variable rate of flow, for discharge at a distal portion of the catheter, the catheter having at least one energy delivering electrode disposed at a distal portion of the catheter and the catheter having dimensions suitable for intravascular delivery;
an electrosurgical generator unit in electrical communication with the catheter for providing a desired electrosurgical energy output to the electrode for delivery to tissue adjacent the electrode;
a fluid supply source in communication with the lumen;
temperature sensing means associated with the catheter for sensing the temperature of the energy delivering electrode and generating a signal representative of measured electrode temperature;
comparator means for comparing the measured electrode temperature and a predetermined maximum temperature value and generating a signal representative of the temperature difference; and a fluid control means for regulating the rate of flow of fluid through the lumen in response to the signal from the comparator means representative of the temperature difference to maintain the measured electrode temperature at or below the predetermined temperature.
21. The system of claim 20 wherein the temperature sensing means comprises a thermistor or a thermocouple.
22. (Amended) The system of claim 20, further comprising a subsystem for controlling the electrosurgical energy output of the generator unit, the subsystem comprising:
impedance measuring means for measuring the impedance value of tissue based on the energy applied thereto;
impedance comparing means for comparing the measured impedance value of tissue to a predetermined maximum impedance value, the impedance comparing means generating a disabling signal if the measured impedance value exceeds the predetermined maximum impedance value; and means for communicating the disabling signal to the generator unit to cease further delivery of energy from the generator unit to the catheter.
23. (Amended) A system for controlling the temperature of an energy delivering electrode disposed on an ablation catheter, comprising:
a thin, flexible elongate catheter having a central lumen disposed therein to enable fluid to be conveyed through the catheter, at a variable flow rate, for discharge at a distal portion of the catheter, the catheter having at least one energy delivering electrode disposed at a distal portion of the catheter and the catheter having dimensions suitable for intravascular delivery;
an electrosurgical generator unit in electrical communication with the catheter for supplying electrosurgical energy to the electrode for delivery to tissue adjacent the electrode;
a fluid supply source in communication with the lumen;
impedance measuring means for measuring the impedance value of tissue based on the energy applied thereto;
impedance comparing means for comparing the measured impedance value of tissue to a predetermined maximum impedance value, the impedance comparing means generating a signal representative of the difference between themeasured impedance value and the predetermined maximum impedance value; and a fluid control means for regulating the rate of flow of fluid through the lumen in response to the signal from the impedance comparing means representative of the impedance difference to maintain the measured impedance value at or below the predetermined maximum impedance value.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US07/975,662 US5334193A (en) | 1992-11-13 | 1992-11-13 | Fluid cooled ablation catheter |
US07/975,662 | 1992-11-13 |
Publications (1)
Publication Number | Publication Date |
---|---|
CA2149310A1 true CA2149310A1 (en) | 1994-05-26 |
Family
ID=25523264
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002149310A Abandoned CA2149310A1 (en) | 1992-11-13 | 1993-11-01 | Fluid cooled ablation catheter |
Country Status (6)
Country | Link |
---|---|
US (1) | US5334193A (en) |
EP (1) | EP0703803A1 (en) |
JP (1) | JPH08505544A (en) |
AU (1) | AU5456394A (en) |
CA (1) | CA2149310A1 (en) |
WO (1) | WO1994011059A1 (en) |
Families Citing this family (760)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5697281A (en) | 1991-10-09 | 1997-12-16 | Arthrocare Corporation | System and method for electrosurgical cutting and ablation |
US5697882A (en) | 1992-01-07 | 1997-12-16 | Arthrocare Corporation | System and method for electrosurgical cutting and ablation |
US5683366A (en) * | 1992-01-07 | 1997-11-04 | Arthrocare Corporation | System and method for electrosurgical tissue canalization |
US5830209A (en) * | 1992-02-05 | 1998-11-03 | Angeion Corporation | Multi-fiber laser catheter |
US5586982A (en) | 1992-04-10 | 1996-12-24 | Abela; George S. | Cell transfection apparatus and method |
WO1993020768A1 (en) * | 1992-04-13 | 1993-10-28 | Ep Technologies, Inc. | Steerable microwave antenna systems for cardiac ablation |
US5542916A (en) * | 1992-08-12 | 1996-08-06 | Vidamed, Inc. | Dual-channel RF power delivery system |
US5566096A (en) * | 1992-11-13 | 1996-10-15 | Quinton Electrophysiology Corporation | Integrated electrical signal switching and amplifying system |
US5348554A (en) * | 1992-12-01 | 1994-09-20 | Cardiac Pathways Corporation | Catheter for RF ablation with cooled electrode |
US6620188B1 (en) | 1998-08-24 | 2003-09-16 | Radiant Medical, Inc. | Methods and apparatus for regional and whole body temperature modification |
US6161543A (en) * | 1993-02-22 | 2000-12-19 | Epicor, Inc. | Methods of epicardial ablation for creating a lesion around the pulmonary veins |
NL9301182A (en) * | 1993-07-05 | 1995-02-01 | Cordis Europ | Catheter with strip-shaped electrode. |
US5766153A (en) * | 1993-05-10 | 1998-06-16 | Arthrocare Corporation | Methods and apparatus for surgical cutting |
US5860974A (en) * | 1993-07-01 | 1999-01-19 | Boston Scientific Corporation | Heart ablation catheter with expandable electrode and method of coupling energy to an electrode on a catheter shaft |
US5807395A (en) * | 1993-08-27 | 1998-09-15 | Medtronic, Inc. | Method and apparatus for RF ablation and hyperthermia |
US5431649A (en) * | 1993-08-27 | 1995-07-11 | Medtronic, Inc. | Method and apparatus for R-F ablation |
US5582609A (en) | 1993-10-14 | 1996-12-10 | Ep Technologies, Inc. | Systems and methods for forming large lesions in body tissue using curvilinear electrode elements |
CA2174129C (en) * | 1993-10-14 | 2004-03-09 | Sidney D. Fleischman | Electrode elements for forming lesion patterns |
US6001093A (en) | 1993-10-15 | 1999-12-14 | Ep Technologies, Inc. | Systems and methods for creating long, thin lesions in body tissue |
US5840076A (en) * | 1996-04-12 | 1998-11-24 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using electrode structures with distally oriented porous regions |
US5545193A (en) * | 1993-10-15 | 1996-08-13 | Ep Technologies, Inc. | Helically wound radio-frequency emitting electrodes for creating lesions in body tissue |
US6146379A (en) * | 1993-10-15 | 2000-11-14 | Ep Technologies, Inc. | Systems and methods for creating curvilinear lesions in body tissue |
US5575810A (en) * | 1993-10-15 | 1996-11-19 | Ep Technologies, Inc. | Composite structures and methods for ablating tissue to form complex lesion patterns in the treatment of cardiac conditions and the like |
US5797903A (en) * | 1996-04-12 | 1998-08-25 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures with electrically conductive surfaces |
WO1995010320A1 (en) | 1993-10-15 | 1995-04-20 | Ep Technologies, Inc. | Device for lengthening cardiac conduction pathways |
US5536267A (en) | 1993-11-08 | 1996-07-16 | Zomed International | Multiple electrode ablation apparatus |
US5728143A (en) * | 1995-08-15 | 1998-03-17 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method |
US6569159B1 (en) * | 1993-11-08 | 2003-05-27 | Rita Medical Systems, Inc. | Cell necrosis apparatus |
US6632221B1 (en) * | 1993-11-08 | 2003-10-14 | Rita Medical Systems, Inc. | Method of creating a lesion in tissue with infusion |
US5683384A (en) * | 1993-11-08 | 1997-11-04 | Zomed | Multiple antenna ablation apparatus |
US6071280A (en) | 1993-11-08 | 2000-06-06 | Rita Medical Systems, Inc. | Multiple electrode ablation apparatus |
US5928229A (en) | 1993-11-08 | 1999-07-27 | Rita Medical Systems, Inc. | Tumor ablation apparatus |
US6641580B1 (en) * | 1993-11-08 | 2003-11-04 | Rita Medical Systems, Inc. | Infusion array ablation apparatus |
US5462521A (en) * | 1993-12-21 | 1995-10-31 | Angeion Corporation | Fluid cooled and perfused tip for a catheter |
US5577509A (en) * | 1994-01-28 | 1996-11-26 | Ep Technologies, Inc. | Systems and methods for examining the electrical characteristics and timing of electrical events in cardiac tissue |
US5447529A (en) * | 1994-01-28 | 1995-09-05 | Philadelphia Heart Institute | Method of using endocardial impedance for determining electrode-tissue contact, appropriate sites for arrhythmia ablation and tissue heating during ablation |
WO1995020345A1 (en) * | 1994-01-28 | 1995-08-03 | Ep Technologies, Inc. | Minimizing blood contact in cardiac tissue measurements |
US5584830A (en) * | 1994-03-30 | 1996-12-17 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of cardiac tissue |
US5458596A (en) * | 1994-05-06 | 1995-10-17 | Dorsal Orthopedic Corporation | Method and apparatus for controlled contraction of soft tissue |
US6405732B1 (en) * | 1994-06-24 | 2002-06-18 | Curon Medical, Inc. | Method to treat gastric reflux via the detection and ablation of gastro-esophageal nerves and receptors |
US5735846A (en) * | 1994-06-27 | 1998-04-07 | Ep Technologies, Inc. | Systems and methods for ablating body tissue using predicted maximum tissue temperature |
US6113591A (en) * | 1994-06-27 | 2000-09-05 | Ep Technologies, Inc. | Systems and methods for sensing sub-surface temperatures in body tissue |
US5680860A (en) * | 1994-07-07 | 1997-10-28 | Cardiac Pathways Corporation | Mapping and/or ablation catheter with coilable distal extremity and method for using same |
US5810802A (en) | 1994-08-08 | 1998-09-22 | E.P. Technologies, Inc. | Systems and methods for controlling tissue ablation using multiple temperature sensing elements |
US6030382A (en) * | 1994-08-08 | 2000-02-29 | Ep Technologies, Inc. | Flexible tissue ablatin elements for making long lesions |
US6245068B1 (en) | 1994-08-08 | 2001-06-12 | Scimed Life Systems, Inc. | Resilient radiopaque electrophysiology electrodes and probes including the same |
US5797905A (en) * | 1994-08-08 | 1998-08-25 | E. P. Technologies Inc. | Flexible tissue ablation elements for making long lesions |
US20080167649A1 (en) * | 1994-08-12 | 2008-07-10 | Angiodynamics, Inc. | Ablation apparatus and method |
US5967976A (en) * | 1994-08-19 | 1999-10-19 | Novoste Corporation | Apparatus and methods for procedures related to the electrophysiology of the heart |
US5529067A (en) * | 1994-08-19 | 1996-06-25 | Novoste Corporation | Methods for procedures related to the electrophysiology of the heart |
US5876398A (en) * | 1994-09-08 | 1999-03-02 | Medtronic, Inc. | Method and apparatus for R-F ablation |
US5609151A (en) * | 1994-09-08 | 1997-03-11 | Medtronic, Inc. | Method for R-F ablation |
US5514130A (en) * | 1994-10-11 | 1996-05-07 | Dorsal Med International | RF apparatus for controlled depth ablation of soft tissue |
US5785705A (en) * | 1994-10-11 | 1998-07-28 | Oratec Interventions, Inc. | RF method for controlled depth ablation of soft tissue |
EP2314244A1 (en) | 1994-12-13 | 2011-04-27 | Torben Lorentzen | An electrosurgical instrument for tissue ablation, an apparatus, and a method for providing a lesion in damaged and diseased tissue from a mammal |
US6461353B1 (en) | 1995-02-17 | 2002-10-08 | Oratec Interventions, Inc. | Orthopedic apparatus for controlled contraction of collagen tissue |
US6063081A (en) * | 1995-02-22 | 2000-05-16 | Medtronic, Inc. | Fluid-assisted electrocautery device |
US5897553A (en) * | 1995-11-02 | 1999-04-27 | Medtronic, Inc. | Ball point fluid-assisted electrocautery device |
US6409722B1 (en) * | 1998-07-07 | 2002-06-25 | Medtronic, Inc. | Apparatus and method for creating, maintaining, and controlling a virtual electrode used for the ablation of tissue |
US6544264B2 (en) | 1995-03-10 | 2003-04-08 | Seedling Enterprises, Llc | Electrosurgery with cooled electrodes |
US6503248B1 (en) | 2000-10-30 | 2003-01-07 | Seedling Enterprises, Llc | Cooled, non-sticking electrosurgical devices |
US5647871A (en) | 1995-03-10 | 1997-07-15 | Microsurge, Inc. | Electrosurgery with cooled electrodes |
US5676662A (en) * | 1995-03-17 | 1997-10-14 | Daig Corporation | Ablation catheter |
US5569188A (en) * | 1995-04-11 | 1996-10-29 | Mackool; Richard J. | Apparatus for controlling fluid flow through a surgical instrument and the temperature of an ultrasonic instrument |
US6053912A (en) * | 1995-05-01 | 2000-04-25 | Ep Techonologies, Inc. | Systems and methods for sensing sub-surface temperatures in body tissue during ablation with actively cooled electrodes |
US6030379A (en) * | 1995-05-01 | 2000-02-29 | Ep Technologies, Inc. | Systems and methods for seeking sub-surface temperature conditions during tissue ablation |
US5800432A (en) * | 1995-05-01 | 1998-09-01 | Ep Technologies, Inc. | Systems and methods for actively cooling ablation electrodes using diodes |
WO1996034570A1 (en) * | 1995-05-01 | 1996-11-07 | Ep Technologies, Inc. | Systems and methods for obtaining desired lesion characteristics while ablating body tissue |
EP1011495B1 (en) * | 1995-05-04 | 2005-11-09 | Sherwood Services AG | Cool-tip electrode thermosurgery system |
US6575969B1 (en) | 1995-05-04 | 2003-06-10 | Sherwood Services Ag | Cool-tip radiofrequency thermosurgery electrode system for tumor ablation |
US5755753A (en) * | 1995-05-05 | 1998-05-26 | Thermage, Inc. | Method for controlled contraction of collagen tissue |
US5660836A (en) * | 1995-05-05 | 1997-08-26 | Knowlton; Edward W. | Method and apparatus for controlled contraction of collagen tissue |
US6425912B1 (en) | 1995-05-05 | 2002-07-30 | Thermage, Inc. | Method and apparatus for modifying skin surface and soft tissue structure |
US6241753B1 (en) | 1995-05-05 | 2001-06-05 | Thermage, Inc. | Method for scar collagen formation and contraction |
US6430446B1 (en) | 1995-05-05 | 2002-08-06 | Thermage, Inc. | Apparatus for tissue remodeling |
US5554172A (en) * | 1995-05-09 | 1996-09-10 | The Larren Corporation | Directed energy surgical method and assembly |
US6002956A (en) * | 1995-05-23 | 1999-12-14 | Cardima, Inc. | Method of treating using an over-the-wire EP catheter |
US5895355A (en) * | 1995-05-23 | 1999-04-20 | Cardima, Inc. | Over-the-wire EP catheter |
WO1996038094A1 (en) * | 1995-05-31 | 1996-12-05 | Nuvotek Ltd. | Electrosurgical cutting and coagulation apparatus |
US6149620A (en) | 1995-11-22 | 2000-11-21 | Arthrocare Corporation | System and methods for electrosurgical tissue treatment in the presence of electrically conductive fluid |
US6293942B1 (en) | 1995-06-23 | 2001-09-25 | Gyrus Medical Limited | Electrosurgical generator method |
US6015406A (en) | 1996-01-09 | 2000-01-18 | Gyrus Medical Limited | Electrosurgical instrument |
EP1050278A1 (en) | 1995-06-23 | 2000-11-08 | Gyrus Medical Limited | An electrosurgical instrument |
US6780180B1 (en) | 1995-06-23 | 2004-08-24 | Gyrus Medical Limited | Electrosurgical instrument |
CN1095641C (en) | 1995-06-23 | 2002-12-11 | 盖拉斯医疗有限公司 | Electrosurgical instrument |
US6267757B1 (en) | 1995-08-09 | 2001-07-31 | Eclipse Surgical Technologies, Inc. | Revascularization with RF ablation |
US6156031A (en) * | 1995-08-09 | 2000-12-05 | Eclipse Surgical Technologies | Transmyocardial revascularization using radiofrequency energy |
US5810804A (en) * | 1995-08-15 | 1998-09-22 | Rita Medical Systems | Multiple antenna ablation apparatus and method with cooling element |
US6090105A (en) | 1995-08-15 | 2000-07-18 | Rita Medical Systems, Inc. | Multiple electrode ablation apparatus and method |
US6059780A (en) | 1995-08-15 | 2000-05-09 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method with cooling element |
US5782827A (en) * | 1995-08-15 | 1998-07-21 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method with multiple sensor feedback |
US5672173A (en) * | 1995-08-15 | 1997-09-30 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method |
US5951547A (en) | 1995-08-15 | 1999-09-14 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method |
US5980517A (en) | 1995-08-15 | 1999-11-09 | Rita Medical Systems, Inc. | Cell necrosis apparatus |
US6080150A (en) | 1995-08-15 | 2000-06-27 | Rita Medical Systems, Inc. | Cell necrosis apparatus |
US5863290A (en) * | 1995-08-15 | 1999-01-26 | Rita Medical Systems | Multiple antenna ablation apparatus and method |
US5925042A (en) | 1995-08-15 | 1999-07-20 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method |
US6132425A (en) | 1995-08-15 | 2000-10-17 | Gough; Edward J. | Cell necrosis apparatus |
US5735847A (en) * | 1995-08-15 | 1998-04-07 | Zomed International, Inc. | Multiple antenna ablation apparatus and method with cooling element |
US5672174A (en) * | 1995-08-15 | 1997-09-30 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method |
US6689127B1 (en) | 1995-08-15 | 2004-02-10 | Rita Medical Systems | Multiple antenna ablation apparatus and method with multiple sensor feedback |
US5913855A (en) | 1995-08-15 | 1999-06-22 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method |
US5776130A (en) | 1995-09-19 | 1998-07-07 | Valleylab, Inc. | Vascular tissue sealing pressure control |
US6428538B1 (en) | 1995-10-20 | 2002-08-06 | United States Surgical Corporation | Apparatus and method for thermal treatment of body tissue |
US6007570A (en) * | 1996-08-13 | 1999-12-28 | Oratec Interventions, Inc. | Apparatus with functional element for performing function upon intervertebral discs |
US6283960B1 (en) | 1995-10-24 | 2001-09-04 | Oratec Interventions, Inc. | Apparatus for delivery of energy to a surgical site |
US6122549A (en) * | 1996-08-13 | 2000-09-19 | Oratec Interventions, Inc. | Apparatus for treating intervertebral discs with resistive energy |
US7270661B2 (en) * | 1995-11-22 | 2007-09-18 | Arthocare Corporation | Electrosurgical apparatus and methods for treatment and removal of tissue |
US7022121B2 (en) | 1999-03-09 | 2006-04-04 | Thermage, Inc. | Handpiece for treatment of tissue |
US7115123B2 (en) * | 1996-01-05 | 2006-10-03 | Thermage, Inc. | Handpiece with electrode and non-volatile memory |
US7006874B2 (en) | 1996-01-05 | 2006-02-28 | Thermage, Inc. | Treatment apparatus with electromagnetic energy delivery device and non-volatile memory |
US7141049B2 (en) | 1999-03-09 | 2006-11-28 | Thermage, Inc. | Handpiece for treatment of tissue |
US20030212393A1 (en) * | 1996-01-05 | 2003-11-13 | Knowlton Edward W. | Handpiece with RF electrode and non-volatile memory |
US7189230B2 (en) * | 1996-01-05 | 2007-03-13 | Thermage, Inc. | Method for treating skin and underlying tissue |
US6350276B1 (en) | 1996-01-05 | 2002-02-26 | Thermage, Inc. | Tissue remodeling apparatus containing cooling fluid |
US7267675B2 (en) | 1996-01-05 | 2007-09-11 | Thermage, Inc. | RF device with thermo-electric cooler |
US7229436B2 (en) | 1996-01-05 | 2007-06-12 | Thermage, Inc. | Method and kit for treatment of tissue |
US6013076A (en) | 1996-01-09 | 2000-01-11 | Gyrus Medical Limited | Electrosurgical instrument |
US6090106A (en) | 1996-01-09 | 2000-07-18 | Gyrus Medical Limited | Electrosurgical instrument |
US5891136A (en) * | 1996-01-19 | 1999-04-06 | Ep Technologies, Inc. | Expandable-collapsible mesh electrode structures |
US5830213A (en) * | 1996-04-12 | 1998-11-03 | Ep Technologies, Inc. | Systems for heating and ablating tissue using multifunctional electrode structures |
US5925038A (en) | 1996-01-19 | 1999-07-20 | Ep Technologies, Inc. | Expandable-collapsible electrode structures for capacitive coupling to tissue |
US5836874A (en) * | 1996-04-08 | 1998-11-17 | Ep Technologies, Inc. | Multi-function electrode structures for electrically analyzing and heating body tissue |
US5871483A (en) * | 1996-01-19 | 1999-02-16 | Ep Technologies, Inc. | Folding electrode structures |
US5853411A (en) * | 1996-01-19 | 1998-12-29 | Ep Technologies, Inc. | Enhanced electrical connections for electrode structures |
US5868736A (en) * | 1996-04-12 | 1999-02-09 | Ep Technologies, Inc. | Systems and methods to control tissue heating or ablation with porous electrode structures |
US5961513A (en) * | 1996-01-19 | 1999-10-05 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures |
US5879348A (en) * | 1996-04-12 | 1999-03-09 | Ep Technologies, Inc. | Electrode structures formed from flexible, porous, or woven materials |
WO1997025917A1 (en) * | 1996-01-19 | 1997-07-24 | Ep Technologies, Inc. | Multi-function electrode structures for electrically analyzing and heating body tissue |
US6071278A (en) * | 1996-02-28 | 2000-06-06 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures with specified electrical resistivities |
US5846239A (en) * | 1996-04-12 | 1998-12-08 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using segmented porous electrode structures |
US5891135A (en) * | 1996-01-19 | 1999-04-06 | Ep Technologies, Inc. | Stem elements for securing tubing and electrical wires to expandable-collapsible electrode structures |
US6475213B1 (en) | 1996-01-19 | 2002-11-05 | Ep Technologies, Inc. | Method of ablating body tissue |
WO1997025918A1 (en) * | 1996-01-19 | 1997-07-24 | Ep Technologies, Inc. | Electrode structures formed from flexible, porous, or woven materials |
US5846238A (en) * | 1996-01-19 | 1998-12-08 | Ep Technologies, Inc. | Expandable-collapsible electrode structures with distal end steering or manipulation |
US6032077A (en) * | 1996-03-06 | 2000-02-29 | Cardiac Pathways Corporation | Ablation catheter with electrical coupling via foam drenched with a conductive fluid |
US5895417A (en) * | 1996-03-06 | 1999-04-20 | Cardiac Pathways Corporation | Deflectable loop design for a linear lesion ablation apparatus |
US6015407A (en) * | 1996-03-06 | 2000-01-18 | Cardiac Pathways Corporation | Combination linear ablation and cooled tip RF catheters |
US5800482A (en) * | 1996-03-06 | 1998-09-01 | Cardiac Pathways Corporation | Apparatus and method for linear lesion ablation |
US5755760A (en) * | 1996-03-11 | 1998-05-26 | Medtronic, Inc. | Deflectable catheter |
US5733281A (en) * | 1996-03-19 | 1998-03-31 | American Ablation Co., Inc. | Ultrasound and impedance feedback system for use with electrosurgical instruments |
US6016452A (en) * | 1996-03-19 | 2000-01-18 | Kasevich; Raymond S. | Dynamic heating method and radio frequency thermal treatment |
US5769880A (en) * | 1996-04-12 | 1998-06-23 | Novacept | Moisture transport system for contact electrocoagulation |
US7604633B2 (en) | 1996-04-12 | 2009-10-20 | Cytyc Corporation | Moisture transport system for contact electrocoagulation |
US6813520B2 (en) | 1996-04-12 | 2004-11-02 | Novacept | Method for ablating and/or coagulating tissue using moisture transport |
AUPN957296A0 (en) * | 1996-04-30 | 1996-05-23 | Cardiac Crc Nominees Pty Limited | A system for simultaneous unipolar multi-electrode ablation |
NL1003024C2 (en) | 1996-05-03 | 1997-11-06 | Tjong Hauw Sie | Stimulus conduction blocking instrument. |
US6419673B1 (en) * | 1996-05-06 | 2002-07-16 | Stuart Edwards | Ablation of rectal and other internal body structures |
US6066139A (en) * | 1996-05-14 | 2000-05-23 | Sherwood Services Ag | Apparatus and method for sterilization and embolization |
US5800428A (en) * | 1996-05-16 | 1998-09-01 | Angeion Corporation | Linear catheter ablation system |
US5800486A (en) * | 1996-06-17 | 1998-09-01 | Urologix, Inc. | Device for transurethral thermal therapy with cooling balloon |
GB9612993D0 (en) | 1996-06-20 | 1996-08-21 | Gyrus Medical Ltd | Electrosurgical instrument |
US6565561B1 (en) | 1996-06-20 | 2003-05-20 | Cyrus Medical Limited | Electrosurgical instrument |
GB2314274A (en) | 1996-06-20 | 1997-12-24 | Gyrus Medical Ltd | Electrode construction for an electrosurgical instrument |
US6126682A (en) | 1996-08-13 | 2000-10-03 | Oratec Interventions, Inc. | Method for treating annular fissures in intervertebral discs |
US6726685B2 (en) | 2001-06-06 | 2004-04-27 | Oratec Interventions, Inc. | Intervertebral disc device employing looped probe |
US6832997B2 (en) | 2001-06-06 | 2004-12-21 | Oratec Interventions, Inc. | Electromagnetic energy delivery intervertebral disc treatment devices |
US7069087B2 (en) | 2000-02-25 | 2006-06-27 | Oratec Interventions, Inc. | Apparatus and method for accessing and performing a function within an intervertebral disc |
US6733496B2 (en) | 2001-06-06 | 2004-05-11 | Oratec Interventions, Inc. | Intervertebral disc device employing flexible probe |
US6645203B2 (en) | 1997-02-12 | 2003-11-11 | Oratec Interventions, Inc. | Surgical instrument with off-axis electrode |
US6106521A (en) * | 1996-08-16 | 2000-08-22 | United States Surgical Corporation | Apparatus for thermal treatment of tissue |
US6068628A (en) * | 1996-08-20 | 2000-05-30 | Oratec Interventions, Inc. | Apparatus for treating chondromalacia |
IL121476A0 (en) * | 1996-09-04 | 1998-02-08 | Esc Medical Systems Ltd | Device and method for cooling skin during laser treatment |
NL1004655C2 (en) * | 1996-11-29 | 1998-06-03 | Cordis Europ | Ablation catheter comprising hose-shaped basic body with proximal and distal ends |
US6015404A (en) * | 1996-12-02 | 2000-01-18 | Palomar Medical Technologies, Inc. | Laser dermatology with feedback control |
US6517532B1 (en) | 1997-05-15 | 2003-02-11 | Palomar Medical Technologies, Inc. | Light energy delivery head |
US7204832B2 (en) | 1996-12-02 | 2007-04-17 | Pálomar Medical Technologies, Inc. | Cooling system for a photo cosmetic device |
US8182473B2 (en) | 1999-01-08 | 2012-05-22 | Palomar Medical Technologies | Cooling system for a photocosmetic device |
US6653618B2 (en) | 2000-04-28 | 2003-11-25 | Palomar Medical Technologies, Inc. | Contact detecting method and apparatus for an optical radiation handpiece |
US5954719A (en) * | 1996-12-11 | 1999-09-21 | Irvine Biomedical, Inc. | System for operating a RF ablation generator |
GB9626512D0 (en) | 1996-12-20 | 1997-02-05 | Gyrus Medical Ltd | An improved electrosurgical generator and system |
US6235022B1 (en) * | 1996-12-20 | 2001-05-22 | Cardiac Pathways, Inc | RF generator and pump apparatus and system and method for cooled ablation |
US5913854A (en) * | 1997-02-04 | 1999-06-22 | Medtronic, Inc. | Fluid cooled ablation catheter and method for making |
JP2002515801A (en) * | 1997-02-12 | 2002-05-28 | オーレイテック インターヴェンションズ インコーポレイテッド | Concave tip for arthroscopic surgery |
AU6326298A (en) | 1997-02-12 | 1998-08-26 | Oratec Interventions, Inc. | Electrode for electrosurgical ablation of tissue and method of manufacturing thesame |
US5954716A (en) * | 1997-02-19 | 1999-09-21 | Oratec Interventions, Inc | Method for modifying the length of a ligament |
US7220257B1 (en) | 2000-07-25 | 2007-05-22 | Scimed Life Systems, Inc. | Cryotreatment device and method |
US5868735A (en) | 1997-03-06 | 1999-02-09 | Scimed Life Systems, Inc. | Cryoplasty device and method |
ES2353846T3 (en) | 1997-04-11 | 2011-03-07 | United States Surgical Corporation | APPLIANCE FOR RF ABLATION AND CONTROLLER OF THE SAME. |
EP1769762B9 (en) * | 1997-04-11 | 2011-03-09 | Tyco Healthcare Group LP | Rf ablation apparatus and controller therefor |
CA2232967C (en) * | 1997-04-11 | 2008-10-21 | United States Surgical Corporation | Controller for thermal treatment of tissue |
JP4056091B2 (en) | 1997-05-15 | 2008-03-05 | パロマー・メディカル・テクノロジーズ・インコーポレーテッド | Dermatological treatment method and apparatus |
US6312426B1 (en) | 1997-05-30 | 2001-11-06 | Sherwood Services Ag | Method and system for performing plate type radiofrequency ablation |
US5997532A (en) * | 1997-07-03 | 1999-12-07 | Cardiac Pathways Corporation | Ablation catheter tip with a buffer layer covering the electrode |
US6241666B1 (en) | 1997-07-03 | 2001-06-05 | Cardiac Pathways Corp. | Ablation catheter tip with a buffer layer covering the electrode |
US6096037A (en) | 1997-07-29 | 2000-08-01 | Medtronic, Inc. | Tissue sealing electrosurgery device and methods of sealing tissue |
US6080151A (en) | 1997-07-21 | 2000-06-27 | Daig Corporation | Ablation catheter |
US6010500A (en) * | 1997-07-21 | 2000-01-04 | Cardiac Pathways Corporation | Telescoping apparatus and method for linear lesion ablation |
US6024739A (en) * | 1997-09-05 | 2000-02-15 | Cordis Webster, Inc. | Method for detecting and revascularizing ischemic myocardial tissue |
US6402719B1 (en) | 1997-09-05 | 2002-06-11 | Cordis Webster, Inc. | Steerable DMR catheter with infusion tube |
US6004320A (en) * | 1997-09-19 | 1999-12-21 | Oratec Interventions, Inc. | Clip on electrocauterizing sheath for orthopedic shave devices |
US6007533A (en) * | 1997-09-19 | 1999-12-28 | Oratec Interventions, Inc. | Electrocauterizing tip for orthopedic shave devices |
US6214001B1 (en) | 1997-09-19 | 2001-04-10 | Oratec Interventions, Inc. | Electrocauterizing tool for orthopedic shave devices |
US20030130653A1 (en) * | 1997-09-30 | 2003-07-10 | Scimed Life Systems, Inc. | Electrosurgical tissue removal with a selectively insulated electrode |
US5995875A (en) * | 1997-10-01 | 1999-11-30 | United States Surgical | Apparatus for thermal treatment of tissue |
US6579288B1 (en) | 1997-10-10 | 2003-06-17 | Scimed Life Systems, Inc. | Fluid cooled apparatus for supporting diagnostic and therapeutic elements in contact with tissue |
US6176857B1 (en) | 1997-10-22 | 2001-01-23 | Oratec Interventions, Inc. | Method and apparatus for applying thermal energy to tissue asymmetrically |
US6120476A (en) * | 1997-12-01 | 2000-09-19 | Cordis Webster, Inc. | Irrigated tip catheter |
US6280441B1 (en) | 1997-12-15 | 2001-08-28 | Sherwood Services Ag | Apparatus and method for RF lesioning |
US6778853B1 (en) * | 1997-12-17 | 2004-08-17 | University Of South Florida | Electroporation device |
US6312452B1 (en) | 1998-01-23 | 2001-11-06 | Innercool Therapies, Inc. | Selective organ cooling catheter with guidewire apparatus and temperature-monitoring device |
US6251130B1 (en) | 1998-03-24 | 2001-06-26 | Innercool Therapies, Inc. | Device for applications of selective organ cooling |
US7371254B2 (en) | 1998-01-23 | 2008-05-13 | Innercool Therapies, Inc. | Medical procedure |
US6254626B1 (en) | 1998-03-24 | 2001-07-03 | Innercool Therapies, Inc. | Articulation device for selective organ cooling apparatus |
US6238428B1 (en) | 1998-01-23 | 2001-05-29 | Innercool Therapies, Inc. | Selective organ cooling apparatus and method employing turbulence-inducing element with curved terminations |
US6096068A (en) * | 1998-01-23 | 2000-08-01 | Innercool Therapies, Inc. | Selective organ cooling catheter and method of using the same |
US6991645B2 (en) | 1998-01-23 | 2006-01-31 | Innercool Therapies, Inc. | Patient temperature regulation method and apparatus |
US6231595B1 (en) * | 1998-03-31 | 2001-05-15 | Innercool Therapies, Inc. | Circulating fluid hypothermia method and apparatus |
US6325818B1 (en) | 1999-10-07 | 2001-12-04 | Innercool Therapies, Inc. | Inflatable cooling apparatus for selective organ hypothermia |
US6383210B1 (en) | 2000-06-02 | 2002-05-07 | Innercool Therapies, Inc. | Method for determining the effective thermal mass of a body or organ using cooling catheter |
US6471717B1 (en) | 1998-03-24 | 2002-10-29 | Innercool Therapies, Inc. | Selective organ cooling apparatus and method |
US6379378B1 (en) | 2000-03-03 | 2002-04-30 | Innercool Therapies, Inc. | Lumen design for catheter |
US6245095B1 (en) | 1998-03-24 | 2001-06-12 | Innercool Therapies, Inc. | Method and apparatus for location and temperature specific drug action such as thrombolysis |
US6251129B1 (en) | 1998-03-24 | 2001-06-26 | Innercool Therapies, Inc. | Method for low temperature thrombolysis and low temperature thrombolytic agent with selective organ temperature control |
US6491716B2 (en) | 1998-03-24 | 2002-12-10 | Innercool Therapies, Inc. | Method and device for applications of selective organ cooling |
US6464716B1 (en) | 1998-01-23 | 2002-10-15 | Innercool Therapies, Inc. | Selective organ cooling apparatus and method |
US6051019A (en) | 1998-01-23 | 2000-04-18 | Del Mar Medical Technologies, Inc. | Selective organ hypothermia method and apparatus |
US6558412B2 (en) | 1998-01-23 | 2003-05-06 | Innercool Therapies, Inc. | Selective organ hypothermia method and apparatus |
US6719779B2 (en) | 2000-11-07 | 2004-04-13 | Innercool Therapies, Inc. | Circulation set for temperature-controlled catheter and method of using the same |
US6491039B1 (en) | 1998-01-23 | 2002-12-10 | Innercool Therapies, Inc. | Medical procedure |
US6585752B2 (en) | 1998-06-23 | 2003-07-01 | Innercool Therapies, Inc. | Fever regulation method and apparatus |
US6843800B1 (en) | 1998-01-23 | 2005-01-18 | Innercool Therapies, Inc. | Patient temperature regulation method and apparatus |
US6261312B1 (en) | 1998-06-23 | 2001-07-17 | Innercool Therapies, Inc. | Inflatable catheter for selective organ heating and cooling and method of using the same |
US8906010B2 (en) | 1998-02-19 | 2014-12-09 | Mederi Therapeutics, Inc. | Graphical user interface for association with an electrode structure deployed in contact with a tissue region |
US6273886B1 (en) * | 1998-02-19 | 2001-08-14 | Curon Medical, Inc. | Integrated tissue heating and cooling apparatus |
US6358245B1 (en) | 1998-02-19 | 2002-03-19 | Curon Medical, Inc. | Graphical user interface for association with an electrode structure deployed in contact with a tissue region |
US6042559A (en) * | 1998-02-24 | 2000-03-28 | Innercool Therapies, Inc. | Insulated catheter for selective organ perfusion |
WO1999046005A1 (en) | 1998-03-12 | 1999-09-16 | Palomar Medical Technologies, Inc. | System for electromagnetic radiation of the skin |
AU3104999A (en) | 1998-03-19 | 1999-10-11 | Oratec Interventions, Inc. | Catheter for delivery of energy to a surgical site |
US6599312B2 (en) | 1998-03-24 | 2003-07-29 | Innercool Therapies, Inc. | Isolated selective organ cooling apparatus |
US6224624B1 (en) | 1998-03-24 | 2001-05-01 | Innercool Therapies, Inc. | Selective organ cooling apparatus and method |
US6551349B2 (en) | 1998-03-24 | 2003-04-22 | Innercool Therapies, Inc. | Selective organ cooling apparatus |
US6576002B2 (en) | 1998-03-24 | 2003-06-10 | Innercool Therapies, Inc. | Isolated selective organ cooling method and apparatus |
GB9807303D0 (en) | 1998-04-03 | 1998-06-03 | Gyrus Medical Ltd | An electrode assembly for an electrosurgical instrument |
US6605080B1 (en) | 1998-03-27 | 2003-08-12 | The General Hospital Corporation | Method and apparatus for the selective targeting of lipid-rich tissues |
US6047700A (en) * | 1998-03-30 | 2000-04-11 | Arthrocare Corporation | Systems and methods for electrosurgical removal of calcified deposits |
US6905494B2 (en) | 1998-03-31 | 2005-06-14 | Innercool Therapies, Inc. | Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing tissue protection |
US6685732B2 (en) | 1998-03-31 | 2004-02-03 | Innercool Therapies, Inc. | Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing microporous balloon |
US6602276B2 (en) * | 1998-03-31 | 2003-08-05 | Innercool Therapies, Inc. | Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation |
US7291144B2 (en) | 1998-03-31 | 2007-11-06 | Innercool Therapies, Inc. | Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation |
US6338727B1 (en) | 1998-08-13 | 2002-01-15 | Alsius Corporation | Indwelling heat exchange catheter and method of using same |
US8551082B2 (en) | 1998-05-08 | 2013-10-08 | Cytyc Surgical Products | Radio-frequency generator for powering an ablation device |
US6706039B2 (en) | 1998-07-07 | 2004-03-16 | Medtronic, Inc. | Method and apparatus for creating a bi-polar virtual electrode used for the ablation of tissue |
US6537272B2 (en) | 1998-07-07 | 2003-03-25 | Medtronic, Inc. | Apparatus and method for creating, maintaining, and controlling a virtual electrode used for the ablation of tissue |
US6537248B2 (en) | 1998-07-07 | 2003-03-25 | Medtronic, Inc. | Helical needle apparatus for creating a virtual electrode used for the ablation of tissue |
US7276063B2 (en) | 1998-08-11 | 2007-10-02 | Arthrocare Corporation | Instrument for electrosurgical tissue treatment |
US6673098B1 (en) * | 1998-08-24 | 2004-01-06 | Radiant Medical, Inc. | Disposable cassette for intravascular heat exchange catheter |
JP4136118B2 (en) * | 1998-09-30 | 2008-08-20 | オリンパス株式会社 | Electrosurgical equipment |
US6208881B1 (en) | 1998-10-20 | 2001-03-27 | Micropure Medical, Inc. | Catheter with thin film electrodes and method for making same |
US7364577B2 (en) | 2002-02-11 | 2008-04-29 | Sherwood Services Ag | Vessel sealing system |
US7137980B2 (en) | 1998-10-23 | 2006-11-21 | Sherwood Services Ag | Method and system for controlling output of RF medical generator |
US7901400B2 (en) | 1998-10-23 | 2011-03-08 | Covidien Ag | Method and system for controlling output of RF medical generator |
US6221039B1 (en) * | 1998-10-26 | 2001-04-24 | Scimed Life Systems, Inc. | Multi-function surgical instrument |
US6328735B1 (en) * | 1998-10-30 | 2001-12-11 | E.P., Limited | Thermal ablation system |
US8244370B2 (en) | 2001-04-13 | 2012-08-14 | Greatbatch Ltd. | Band stop filter employing a capacitor and an inductor tank circuit to enhance MRI compatibility of active medical devices |
US6701176B1 (en) | 1998-11-04 | 2004-03-02 | Johns Hopkins University School Of Medicine | Magnetic-resonance-guided imaging, electrophysiology, and ablation |
US7844319B2 (en) * | 1998-11-04 | 2010-11-30 | Susil Robert C | Systems and methods for magnetic-resonance-guided interventional procedures |
US6514242B1 (en) | 1998-12-03 | 2003-02-04 | David Vasily | Method and apparatus for laser removal of hair |
US6171275B1 (en) | 1998-12-03 | 2001-01-09 | Cordis Webster, Inc. | Irrigated split tip electrode catheter |
US6210406B1 (en) * | 1998-12-03 | 2001-04-03 | Cordis Webster, Inc. | Split tip electrode catheter and signal processing RF ablation system |
US6830581B2 (en) | 1999-02-09 | 2004-12-14 | Innercool Therspies, Inc. | Method and device for patient temperature control employing optimized rewarming |
US6869440B2 (en) | 1999-02-09 | 2005-03-22 | Innercool Therapies, Inc. | Method and apparatus for patient temperature control employing administration of anti-shivering agents |
US6887235B2 (en) * | 1999-03-24 | 2005-05-03 | Micrus Corporation | Variable stiffness heating catheter |
US8285393B2 (en) * | 1999-04-16 | 2012-10-09 | Laufer Michael D | Device for shaping infarcted heart tissue and method of using the device |
US6939346B2 (en) | 1999-04-21 | 2005-09-06 | Oratec Interventions, Inc. | Method and apparatus for controlling a temperature-controlled probe |
US6461352B2 (en) * | 1999-05-11 | 2002-10-08 | Stryker Corporation | Surgical handpiece with self-sealing switch assembly |
US6214003B1 (en) | 1999-05-11 | 2001-04-10 | Stryker Corporation | Electrosurgical tool |
US6478793B1 (en) * | 1999-06-11 | 2002-11-12 | Sherwood Services Ag | Ablation treatment of bone metastases |
US6852120B1 (en) | 1999-08-10 | 2005-02-08 | Biosense Webster, Inc | Irrigation probe for ablation during open heart surgery |
US7097641B1 (en) | 1999-12-09 | 2006-08-29 | Cryocath Technologies Inc. | Catheter with cryogenic and heating ablation |
US8221402B2 (en) | 2000-01-19 | 2012-07-17 | Medtronic, Inc. | Method for guiding a medical device |
US7706882B2 (en) | 2000-01-19 | 2010-04-27 | Medtronic, Inc. | Methods of using high intensity focused ultrasound to form an ablated tissue area |
CA2398238A1 (en) * | 2000-01-25 | 2001-08-02 | Palomar Medical Technologies, Inc. | Method and apparatus for medical treatment utilizing long duration electromagnetic radiation |
US6953461B2 (en) | 2002-05-16 | 2005-10-11 | Tissuelink Medical, Inc. | Fluid-assisted medical devices, systems and methods |
US6558385B1 (en) | 2000-09-22 | 2003-05-06 | Tissuelink Medical, Inc. | Fluid-assisted medical device |
US8048070B2 (en) | 2000-03-06 | 2011-11-01 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices, systems and methods |
US6689131B2 (en) | 2001-03-08 | 2004-02-10 | Tissuelink Medical, Inc. | Electrosurgical device having a tissue reduction sensor |
US7811282B2 (en) | 2000-03-06 | 2010-10-12 | Salient Surgical Technologies, Inc. | Fluid-assisted electrosurgical devices, electrosurgical unit with pump and methods of use thereof |
ES2643763T3 (en) | 2000-03-06 | 2017-11-24 | Salient Surgical Technologies, Inc. | Fluid supply system and controller for electrosurgical devices |
US6770070B1 (en) * | 2000-03-17 | 2004-08-03 | Rita Medical Systems, Inc. | Lung treatment apparatus and method |
US6569162B2 (en) | 2001-03-29 | 2003-05-27 | Ding Sheng He | Passively self-cooled electrode design for ablation catheters |
US6488680B1 (en) | 2000-04-27 | 2002-12-03 | Medtronic, Inc. | Variable length electrodes for delivery of irrigated ablation |
US6458123B1 (en) | 2000-04-27 | 2002-10-01 | Biosense Webster, Inc. | Ablation catheter with positional sensor |
WO2001082812A1 (en) * | 2000-04-27 | 2001-11-08 | Medtronic, Inc. | Vibration sensitive ablation apparatus and method |
US6514250B1 (en) | 2000-04-27 | 2003-02-04 | Medtronic, Inc. | Suction stabilized epicardial ablation devices |
DE20009426U1 (en) * | 2000-05-26 | 2001-10-31 | Desinger Kai | Surgical instrument |
US6726708B2 (en) | 2000-06-14 | 2004-04-27 | Innercool Therapies, Inc. | Therapeutic heating and cooling via temperature management of a colon-inserted balloon |
US7235073B2 (en) | 2000-07-06 | 2007-06-26 | Ethicon Endo-Surgery, Inc. | Cooled electrosurgical forceps |
US6840935B2 (en) * | 2000-08-09 | 2005-01-11 | Bekl Corporation | Gynecological ablation procedure and system using an ablation needle |
US7678106B2 (en) * | 2000-08-09 | 2010-03-16 | Halt Medical, Inc. | Gynecological ablation procedure and system |
US6942661B2 (en) | 2000-08-30 | 2005-09-13 | Boston Scientific Scimed, Inc. | Fluid cooled apparatus for supporting diagnostic and therapeutic elements in contact with tissue |
US6673063B2 (en) * | 2000-10-06 | 2004-01-06 | Expanding Concepts, Llc. | Epidural thermal posterior annuloplasty |
US6926669B1 (en) | 2000-10-10 | 2005-08-09 | Medtronic, Inc. | Heart wall ablation/mapping catheter and method |
US7104987B2 (en) | 2000-10-17 | 2006-09-12 | Asthmatx, Inc. | Control system and process for application of energy to airway walls and other mediums |
CN101194856A (en) * | 2000-12-28 | 2008-06-11 | 帕洛玛医疗技术有限公司 | Methods and products for producing lattices of EMR-treated islets in tissues, and uses therefor |
US20040138621A1 (en) | 2003-01-14 | 2004-07-15 | Jahns Scott E. | Devices and methods for interstitial injection of biologic agents into tissue |
US7740623B2 (en) | 2001-01-13 | 2010-06-22 | Medtronic, Inc. | Devices and methods for interstitial injection of biologic agents into tissue |
US6695839B2 (en) | 2001-02-08 | 2004-02-24 | Oratec Interventions, Inc. | Method and apparatus for treatment of disrupted articular cartilage |
US6888319B2 (en) | 2001-03-01 | 2005-05-03 | Palomar Medical Technologies, Inc. | Flashlamp drive circuit |
US6699243B2 (en) | 2001-09-19 | 2004-03-02 | Curon Medical, Inc. | Devices, systems and methods for treating tissue regions of the body |
US6666858B2 (en) | 2001-04-12 | 2003-12-23 | Scimed Life Systems, Inc. | Cryo balloon for atrial ablation |
US9295828B2 (en) | 2001-04-13 | 2016-03-29 | Greatbatch Ltd. | Self-resonant inductor wound portion of an implantable lead for enhanced MRI compatibility of active implantable medical devices |
US20070088416A1 (en) | 2001-04-13 | 2007-04-19 | Surgi-Vision, Inc. | Mri compatible medical leads |
US8600519B2 (en) * | 2001-04-13 | 2013-12-03 | Greatbatch Ltd. | Transient voltage/current protection system for electronic circuits associated with implanted leads |
US8509913B2 (en) | 2001-04-13 | 2013-08-13 | Greatbatch Ltd. | Switched diverter circuits for minimizing heating of an implanted lead and/or providing EMI protection in a high power electromagnetic field environment |
US8219208B2 (en) | 2001-04-13 | 2012-07-10 | Greatbatch Ltd. | Frequency selective passive component networks for active implantable medical devices utilizing an energy dissipating surface |
US8989870B2 (en) | 2001-04-13 | 2015-03-24 | Greatbatch Ltd. | Tuned energy balanced system for minimizing heating and/or to provide EMI protection of implanted leads in a high power electromagnetic field environment |
US8457760B2 (en) | 2001-04-13 | 2013-06-04 | Greatbatch Ltd. | Switched diverter circuits for minimizing heating of an implanted lead and/or providing EMI protection in a high power electromagnetic field environment |
US8977355B2 (en) | 2001-04-13 | 2015-03-10 | Greatbatch Ltd. | EMI filter employing a capacitor and an inductor tank circuit having optimum component values |
CA2482202C (en) | 2001-04-13 | 2012-07-03 | Surgi-Vision, Inc. | Systems and methods for magnetic-resonance-guided interventional procedures |
US6699240B2 (en) | 2001-04-26 | 2004-03-02 | Medtronic, Inc. | Method and apparatus for tissue ablation |
US6648883B2 (en) | 2001-04-26 | 2003-11-18 | Medtronic, Inc. | Ablation system and method of use |
US6989010B2 (en) | 2001-04-26 | 2006-01-24 | Medtronic, Inc. | Ablation system and method of use |
US6663627B2 (en) | 2001-04-26 | 2003-12-16 | Medtronic, Inc. | Ablation system and method of use |
US6807968B2 (en) | 2001-04-26 | 2004-10-26 | Medtronic, Inc. | Method and system for treatment of atrial tachyarrhythmias |
US7250048B2 (en) * | 2001-04-26 | 2007-07-31 | Medtronic, Inc. | Ablation system and method of use |
US7959626B2 (en) | 2001-04-26 | 2011-06-14 | Medtronic, Inc. | Transmural ablation systems and methods |
WO2002089686A1 (en) * | 2001-05-10 | 2002-11-14 | Rita Medical Systems, Inc. | Rf tissue ablation apparatus and method |
US20030208252A1 (en) * | 2001-05-14 | 2003-11-06 | O' Boyle Gary S. | Mri ablation catheter |
AU2002303819B2 (en) * | 2001-05-17 | 2007-03-01 | Xenogen Corporation | Method and apparatus for determining target depth, brightness and size within a body region |
US6638276B2 (en) | 2001-06-06 | 2003-10-28 | Oratec Interventions, Inc. | Intervertebral disc device employing prebent sheath |
WO2003003903A2 (en) | 2001-07-02 | 2003-01-16 | Palomar Medical Technologies, Inc. | Laser device for medical/cosmetic procedures |
US7298415B2 (en) | 2001-07-13 | 2007-11-20 | Xenogen Corporation | Structured light imaging apparatus |
WO2003015672A1 (en) | 2001-08-15 | 2003-02-27 | Innercool Therapies, Inc. | Method and apparatus for patient temperature control employing administration of anti-shivering |
JP4341907B2 (en) | 2001-09-05 | 2009-10-14 | セイリアント・サージカル・テクノロジーズ・インコーポレーテッド | Fluid-assisted medical device, system and method |
US20060155261A1 (en) * | 2001-09-19 | 2006-07-13 | Curon Medical, Inc. | Systems and methods for treating tissue regions of the body |
US7615049B2 (en) | 2001-09-19 | 2009-11-10 | Mederi Therapeutics, Inc. | Devices, systems and methods for treating tissue regions of the body |
US7344533B2 (en) * | 2001-09-28 | 2008-03-18 | Angiodynamics, Inc. | Impedance controlled tissue ablation apparatus and method |
US6939350B2 (en) | 2001-10-22 | 2005-09-06 | Boston Scientific Scimed, Inc. | Apparatus for supporting diagnostic and therapeutic elements in contact with tissue including electrode cooling device |
US6656175B2 (en) | 2001-12-11 | 2003-12-02 | Medtronic, Inc. | Method and system for treatment of atrial tachyarrhythmias |
AU2002357166A1 (en) | 2001-12-12 | 2003-06-23 | Tissuelink Medical, Inc. | Fluid-assisted medical devices, systems and methods |
US6709431B2 (en) | 2001-12-18 | 2004-03-23 | Scimed Life Systems, Inc. | Cryo-temperature monitoring |
US7540869B2 (en) | 2001-12-27 | 2009-06-02 | Palomar Medical Technologies, Inc. | Method and apparatus for improved vascular related treatment |
AU2003207615A1 (en) * | 2002-01-18 | 2003-12-02 | Std Manufacturing, Inc. | Ablation technology for catheter based delivery systems |
US6827715B2 (en) | 2002-01-25 | 2004-12-07 | Medtronic, Inc. | System and method of performing an electrosurgical procedure |
US7967816B2 (en) | 2002-01-25 | 2011-06-28 | Medtronic, Inc. | Fluid-assisted electrosurgical instrument with shapeable electrode |
US6757565B2 (en) | 2002-02-08 | 2004-06-29 | Oratec Interventions, Inc. | Electrosurgical instrument having a predetermined heat profile |
US7163536B2 (en) * | 2004-06-10 | 2007-01-16 | Baylis Medical Company Inc. | Determining connections of multiple energy sources and energy delivery devices |
US8882755B2 (en) * | 2002-03-05 | 2014-11-11 | Kimberly-Clark Inc. | Electrosurgical device for treatment of tissue |
US6896675B2 (en) | 2002-03-05 | 2005-05-24 | Baylis Medical Company Inc. | Intradiscal lesioning device |
US8518036B2 (en) | 2002-03-05 | 2013-08-27 | Kimberly-Clark Inc. | Electrosurgical tissue treatment method |
US8043287B2 (en) | 2002-03-05 | 2011-10-25 | Kimberly-Clark Inc. | Method of treating biological tissue |
CN1652729A (en) * | 2002-03-12 | 2005-08-10 | 帕洛玛医疗技术公司 | Method and apparatus for hair growth management |
US9308043B2 (en) | 2002-04-08 | 2016-04-12 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for monopolar renal neuromodulation |
US7853333B2 (en) | 2002-04-08 | 2010-12-14 | Ardian, Inc. | Methods and apparatus for multi-vessel renal neuromodulation |
US20070129761A1 (en) | 2002-04-08 | 2007-06-07 | Ardian, Inc. | Methods for treating heart arrhythmia |
US20070135875A1 (en) | 2002-04-08 | 2007-06-14 | Ardian, Inc. | Methods and apparatus for thermally-induced renal neuromodulation |
US8131371B2 (en) | 2002-04-08 | 2012-03-06 | Ardian, Inc. | Methods and apparatus for monopolar renal neuromodulation |
US8774922B2 (en) | 2002-04-08 | 2014-07-08 | Medtronic Ardian Luxembourg S.A.R.L. | Catheter apparatuses having expandable balloons for renal neuromodulation and associated systems and methods |
US7620451B2 (en) | 2005-12-29 | 2009-11-17 | Ardian, Inc. | Methods and apparatus for pulsed electric field neuromodulation via an intra-to-extravascular approach |
US20140018880A1 (en) | 2002-04-08 | 2014-01-16 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for monopolar renal neuromodulation |
US8150520B2 (en) | 2002-04-08 | 2012-04-03 | Ardian, Inc. | Methods for catheter-based renal denervation |
US8774913B2 (en) | 2002-04-08 | 2014-07-08 | Medtronic Ardian Luxembourg S.A.R.L. | Methods and apparatus for intravasculary-induced neuromodulation |
US8150519B2 (en) | 2002-04-08 | 2012-04-03 | Ardian, Inc. | Methods and apparatus for bilateral renal neuromodulation |
US9308044B2 (en) | 2002-04-08 | 2016-04-12 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for therapeutic renal neuromodulation |
US8347891B2 (en) | 2002-04-08 | 2013-01-08 | Medtronic Ardian Luxembourg S.A.R.L. | Methods and apparatus for performing a non-continuous circumferential treatment of a body lumen |
US7756583B2 (en) | 2002-04-08 | 2010-07-13 | Ardian, Inc. | Methods and apparatus for intravascularly-induced neuromodulation |
US8145317B2 (en) | 2002-04-08 | 2012-03-27 | Ardian, Inc. | Methods for renal neuromodulation |
US7653438B2 (en) | 2002-04-08 | 2010-01-26 | Ardian, Inc. | Methods and apparatus for renal neuromodulation |
US7617005B2 (en) | 2002-04-08 | 2009-11-10 | Ardian, Inc. | Methods and apparatus for thermally-induced renal neuromodulation |
US9636174B2 (en) | 2002-04-08 | 2017-05-02 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for therapeutic renal neuromodulation |
US6978174B2 (en) | 2002-04-08 | 2005-12-20 | Ardian, Inc. | Methods and devices for renal nerve blocking |
US8145316B2 (en) | 2002-04-08 | 2012-03-27 | Ardian, Inc. | Methods and apparatus for renal neuromodulation |
US7162303B2 (en) | 2002-04-08 | 2007-01-09 | Ardian, Inc. | Renal nerve stimulation method and apparatus for treatment of patients |
US20080213331A1 (en) | 2002-04-08 | 2008-09-04 | Ardian, Inc. | Methods and devices for renal nerve blocking |
US6989009B2 (en) * | 2002-04-19 | 2006-01-24 | Scimed Life Systems, Inc. | Cryo balloon |
ATE371413T1 (en) | 2002-05-06 | 2007-09-15 | Covidien Ag | BLOOD DETECTOR FOR CHECKING AN ELECTROSURGICAL UNIT |
US7294143B2 (en) | 2002-05-16 | 2007-11-13 | Medtronic, Inc. | Device and method for ablation of cardiac tissue |
US7118566B2 (en) | 2002-05-16 | 2006-10-10 | Medtronic, Inc. | Device and method for needle-less interstitial injection of fluid for ablation of cardiac tissue |
US6814731B2 (en) | 2002-05-20 | 2004-11-09 | Scimed Life Systems, Inc. | Methods for RF ablation using jet injection of conductive fluid |
US20070213698A1 (en) * | 2006-03-10 | 2007-09-13 | Palomar Medical Technologies, Inc. | Photocosmetic device |
US7135033B2 (en) | 2002-05-23 | 2006-11-14 | Palomar Medical Technologies, Inc. | Phototreatment device for use with coolants and topical substances |
EP1508051A1 (en) | 2002-05-29 | 2005-02-23 | Surgi-Vision, Inc. | Magnetic resonance probes |
JP2005535370A (en) | 2002-06-19 | 2005-11-24 | パロマー・メディカル・テクノロジーズ・インコーポレイテッド | Method and apparatus for treating skin and subcutaneous conditions |
JP2006500972A (en) | 2002-06-19 | 2006-01-12 | パロマー・メディカル・テクノロジーズ・インコーポレイテッド | Method and apparatus for treating tissue at a depth by radiant heat |
US20040082859A1 (en) | 2002-07-01 | 2004-04-29 | Alan Schaer | Method and apparatus employing ultrasound energy to treat body sphincters |
WO2004004545A2 (en) * | 2002-07-03 | 2004-01-15 | Expanding Concepts, L.L.C. | Ribbon epidural thermal posterior annuloplasty |
US7616985B2 (en) * | 2002-07-16 | 2009-11-10 | Xenogen Corporation | Method and apparatus for 3-D imaging of internal light sources |
US7599731B2 (en) * | 2002-07-16 | 2009-10-06 | Xenogen Corporation | Fluorescent light tomography |
US6887237B2 (en) * | 2002-07-22 | 2005-05-03 | Medtronic, Inc. | Method for treating tissue with a wet electrode and apparatus for using same |
US6929639B2 (en) * | 2002-08-30 | 2005-08-16 | Scimed Life Systems, Inc. | Cryo ablation coil |
KR20050062597A (en) * | 2002-10-07 | 2005-06-23 | 팔로마 메디칼 테크놀로지스, 인코포레이티드 | Apparatus for performing photobiostimulation |
GB0223744D0 (en) * | 2002-10-11 | 2002-11-20 | Aqua Detox Ltd | Electrodes for therapeutic apparatus |
AU2003288945A1 (en) | 2002-10-29 | 2004-05-25 | Tissuelink Medical, Inc. | Fluid-assisted electrosurgical scissors and methods |
US7083620B2 (en) | 2002-10-30 | 2006-08-01 | Medtronic, Inc. | Electrosurgical hemostat |
US7044948B2 (en) | 2002-12-10 | 2006-05-16 | Sherwood Services Ag | Circuit for controlling arc energy from an electrosurgical generator |
US6984232B2 (en) * | 2003-01-17 | 2006-01-10 | St. Jude Medical, Daig Division, Inc. | Ablation catheter assembly having a virtual electrode comprising portholes |
US6960207B2 (en) * | 2003-01-21 | 2005-11-01 | St Jude Medical, Daig Division, Inc. | Ablation catheter having a virtual electrode comprising portholes and a porous conductor |
US7819866B2 (en) * | 2003-01-21 | 2010-10-26 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Ablation catheter and electrode |
US7387629B2 (en) | 2003-01-21 | 2008-06-17 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Catheter design that facilitates positioning at tissue to be diagnosed or treated |
US20040158237A1 (en) * | 2003-02-11 | 2004-08-12 | Marwan Abboud | Multi-energy ablation station |
US20040167466A1 (en) * | 2003-02-21 | 2004-08-26 | Drasler William J. | Delivering cooled fluid to sites inside the body |
US20040186467A1 (en) * | 2003-03-21 | 2004-09-23 | Swanson David K. | Apparatus for maintaining contact between diagnostic and therapeutic elements and tissue and systems including the same |
US7938828B2 (en) * | 2003-03-28 | 2011-05-10 | Boston Scientific Scimed, Inc. | Cooled ablation catheter |
US7497857B2 (en) | 2003-04-29 | 2009-03-03 | Medtronic, Inc. | Endocardial dispersive electrode for use with a monopolar RF ablation pen |
EP1617776B1 (en) | 2003-05-01 | 2015-09-02 | Covidien AG | System for programing and controlling an electrosurgical generator system |
US7235070B2 (en) * | 2003-07-02 | 2007-06-26 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Ablation fluid manifold for ablation catheter |
US7101362B2 (en) | 2003-07-02 | 2006-09-05 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Steerable and shapable catheter employing fluid force |
EP1651127B1 (en) | 2003-07-16 | 2012-10-31 | Arthrocare Corporation | Rotary electrosurgical apparatus |
US7156843B2 (en) * | 2003-09-08 | 2007-01-02 | Medtronic, Inc. | Irrigated focal ablation tip |
US7736362B2 (en) * | 2003-09-15 | 2010-06-15 | Boston Scientific Scimed, Inc. | Catheter balloons |
EP1675499B1 (en) | 2003-10-23 | 2011-10-19 | Covidien AG | Redundant temperature monitoring in electrosurgical systems for safety mitigation |
WO2005050151A1 (en) | 2003-10-23 | 2005-06-02 | Sherwood Services Ag | Thermocouple measurement circuit |
US7396336B2 (en) | 2003-10-30 | 2008-07-08 | Sherwood Services Ag | Switched resonant ultrasonic power amplifier system |
US7326195B2 (en) * | 2003-11-18 | 2008-02-05 | Boston Scientific Scimed, Inc. | Targeted cooling of tissue within a body |
US7131860B2 (en) | 2003-11-20 | 2006-11-07 | Sherwood Services Ag | Connector systems for electrosurgical generator |
US7608072B2 (en) | 2003-12-02 | 2009-10-27 | Boston Scientific Scimed, Inc. | Surgical methods and apparatus for maintaining contact between tissue and electrophysiology elements and confirming whether a therapeutic lesion has been formed |
US8052676B2 (en) | 2003-12-02 | 2011-11-08 | Boston Scientific Scimed, Inc. | Surgical methods and apparatus for stimulating tissue |
US7347859B2 (en) * | 2003-12-18 | 2008-03-25 | Boston Scientific, Scimed, Inc. | Tissue treatment system and method for tissue perfusion using feedback control |
US7220254B2 (en) | 2003-12-31 | 2007-05-22 | Palomar Medical Technologies, Inc. | Dermatological treatment with visualization |
US20050267467A1 (en) * | 2004-01-16 | 2005-12-01 | Saurav Paul | Bipolar conforming electrode catheter and methods for ablation |
US7727232B1 (en) | 2004-02-04 | 2010-06-01 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices and methods |
US7766905B2 (en) | 2004-02-12 | 2010-08-03 | Covidien Ag | Method and system for continuity testing of medical electrodes |
US7632266B2 (en) | 2004-02-17 | 2009-12-15 | Boston Scientific Scimed, Inc. | Endoscopic devices and related methods of use |
US7371233B2 (en) * | 2004-02-19 | 2008-05-13 | Boston Scientific Scimed, Inc. | Cooled probes and apparatus for maintaining contact between cooled probes and tissue |
US7157213B2 (en) * | 2004-03-01 | 2007-01-02 | Think Laboratory Co., Ltd. | Developer agent for positive type photosensitive compound |
US7780662B2 (en) | 2004-03-02 | 2010-08-24 | Covidien Ag | Vessel sealing system using capacitive RF dielectric heating |
US7775087B2 (en) * | 2004-03-16 | 2010-08-17 | Northwestern University | Microchannel forming method and nanotipped dispensing device having a microchannel |
US7582050B2 (en) * | 2004-03-31 | 2009-09-01 | The Regents Of The University Of California | Apparatus for hyperthermia and brachytherapy delivery |
US7824394B2 (en) | 2004-04-01 | 2010-11-02 | The General Hospital Corporation | Method and apparatus for dermatological treatment and tissue reshaping |
US8333764B2 (en) | 2004-05-12 | 2012-12-18 | Medtronic, Inc. | Device and method for determining tissue thickness and creating cardiac ablation lesions |
ES2308505T3 (en) | 2004-05-14 | 2008-12-01 | Medtronic, Inc. | ULTRASONIC ENERGY USE SYSTEM FOCUSED ON HIGH INTENS IDAD TO FORM A CUTTED FABRIC AREA. |
US8894642B2 (en) | 2004-05-17 | 2014-11-25 | Boston Scientific Scimed, Inc. | Irrigated catheter |
US20050261571A1 (en) * | 2004-05-21 | 2005-11-24 | Willis Nathaniel P | 3-D ultrasound navigation during radio-frequency ablation |
US7087053B2 (en) * | 2004-05-27 | 2006-08-08 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Catheter with bifurcated, collapsible tip for sensing and ablating |
US7311704B2 (en) * | 2004-05-27 | 2007-12-25 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Spring-tip, flexible electrode catheter for tissue ablation |
EP1750607A2 (en) | 2004-06-02 | 2007-02-14 | Medtronic, Inc. | Loop ablation apparatus and method |
WO2005120376A2 (en) | 2004-06-02 | 2005-12-22 | Medtronic, Inc. | Ablation device with jaws |
WO2005120377A1 (en) | 2004-06-02 | 2005-12-22 | Medtronic, Inc. | Clamping ablation tool |
ATE466536T1 (en) | 2004-06-02 | 2010-05-15 | Medtronic Inc | COMPOSITE BIPOLAR ABLATION DEVICE |
US8361063B2 (en) * | 2004-06-10 | 2013-01-29 | Kimberly-Clark Inc. | System and method for controlling energy delivery |
US8409219B2 (en) | 2004-06-18 | 2013-04-02 | Medtronic, Inc. | Method and system for placement of electrical lead inside heart |
US8926635B2 (en) * | 2004-06-18 | 2015-01-06 | Medtronic, Inc. | Methods and devices for occlusion of an atrial appendage |
US8663245B2 (en) | 2004-06-18 | 2014-03-04 | Medtronic, Inc. | Device for occlusion of a left atrial appendage |
US7226447B2 (en) * | 2004-06-23 | 2007-06-05 | Smith & Nephew, Inc. | Electrosurgical generator |
EP1773227B1 (en) | 2004-06-24 | 2016-04-13 | ArthroCare Corporation | Electrosurgical device having planar vertical electrodes |
US20060025840A1 (en) * | 2004-08-02 | 2006-02-02 | Martin Willard | Cooling tissue inside the body |
US7799021B2 (en) * | 2004-08-04 | 2010-09-21 | Kimberly-Clark Inc. | Electrosurgical treatment in conjunction with monitoring |
US7824408B2 (en) * | 2004-08-05 | 2010-11-02 | Tyco Healthcare Group, Lp | Methods and apparatus for coagulating and/or constricting hollow anatomical structures |
US7322974B2 (en) * | 2004-08-10 | 2008-01-29 | Medtronic, Inc. | TUNA device with integrated saline reservoir |
US8911438B2 (en) * | 2004-08-10 | 2014-12-16 | Medtronic, Inc. | Tuna device with integrated saline reservoir |
PL1639956T3 (en) * | 2004-09-27 | 2007-11-30 | Vibratech Ab | Arrangement for therapy of tumours |
US7553309B2 (en) * | 2004-10-08 | 2009-06-30 | Covidien Ag | Electrosurgical system employing multiple electrodes and method thereof |
US7776035B2 (en) * | 2004-10-08 | 2010-08-17 | Covidien Ag | Cool-tip combined electrode introducer |
US7282049B2 (en) * | 2004-10-08 | 2007-10-16 | Sherwood Services Ag | Electrosurgical system employing multiple electrodes and method thereof |
US7628786B2 (en) | 2004-10-13 | 2009-12-08 | Covidien Ag | Universal foot switch contact port |
US20060089637A1 (en) | 2004-10-14 | 2006-04-27 | Werneth Randell L | Ablation catheter |
US7937143B2 (en) | 2004-11-02 | 2011-05-03 | Ardian, Inc. | Methods and apparatus for inducing controlled renal neuromodulation |
US8617152B2 (en) | 2004-11-15 | 2013-12-31 | Medtronic Ablation Frontiers Llc | Ablation system with feedback |
US7429261B2 (en) | 2004-11-24 | 2008-09-30 | Ablation Frontiers, Inc. | Atrial ablation catheter and method of use |
US7468062B2 (en) * | 2004-11-24 | 2008-12-23 | Ablation Frontiers, Inc. | Atrial ablation catheter adapted for treatment of septal wall arrhythmogenic foci and method of use |
US7731712B2 (en) | 2004-12-20 | 2010-06-08 | Cytyc Corporation | Method and system for transcervical tubal occlusion |
US7467075B2 (en) * | 2004-12-23 | 2008-12-16 | Covidien Ag | Three-dimensional finite-element code for electrosurgery and thermal ablation simulations |
US20070156209A1 (en) * | 2005-01-14 | 2007-07-05 | Co-Repair, Inc. | System for the treatment of heart tissue |
US7455670B2 (en) * | 2005-01-14 | 2008-11-25 | Co-Repair, Inc. | System and method for the treatment of heart tissue |
US7114197B2 (en) * | 2005-01-14 | 2006-10-03 | Louis Garneau Sport Inc. | Adjustable stabilization strap apparatus |
US20070156210A1 (en) * | 2005-01-14 | 2007-07-05 | Co-Repair, Inc., A California Corporation | Method for the treatment of heart tissue |
US7789846B2 (en) * | 2005-01-25 | 2010-09-07 | Thermopeutix, Inc. | System and methods for selective thermal treatment |
US7860556B2 (en) | 2005-02-02 | 2010-12-28 | Voyage Medical, Inc. | Tissue imaging and extraction systems |
US20080015569A1 (en) | 2005-02-02 | 2008-01-17 | Voyage Medical, Inc. | Methods and apparatus for treatment of atrial fibrillation |
US8137333B2 (en) | 2005-10-25 | 2012-03-20 | Voyage Medical, Inc. | Delivery of biological compounds to ischemic and/or infarcted tissue |
US7860555B2 (en) | 2005-02-02 | 2010-12-28 | Voyage Medical, Inc. | Tissue visualization and manipulation system |
US8078266B2 (en) | 2005-10-25 | 2011-12-13 | Voyage Medical, Inc. | Flow reduction hood systems |
US9510732B2 (en) | 2005-10-25 | 2016-12-06 | Intuitive Surgical Operations, Inc. | Methods and apparatus for efficient purging |
US8050746B2 (en) | 2005-02-02 | 2011-11-01 | Voyage Medical, Inc. | Tissue visualization device and method variations |
US10064540B2 (en) | 2005-02-02 | 2018-09-04 | Intuitive Surgical Operations, Inc. | Visualization apparatus for transseptal access |
US7930016B1 (en) | 2005-02-02 | 2011-04-19 | Voyage Medical, Inc. | Tissue closure system |
US11478152B2 (en) | 2005-02-02 | 2022-10-25 | Intuitive Surgical Operations, Inc. | Electrophysiology mapping and visualization system |
US7918787B2 (en) | 2005-02-02 | 2011-04-05 | Voyage Medical, Inc. | Tissue visualization and manipulation systems |
US7625372B2 (en) * | 2005-02-23 | 2009-12-01 | Vnus Medical Technologies, Inc. | Methods and apparatus for coagulating and/or constricting hollow anatomical structures |
US7674256B2 (en) | 2005-03-17 | 2010-03-09 | Boston Scientific Scimed, Inc. | Treating internal body tissue |
US9474564B2 (en) | 2005-03-31 | 2016-10-25 | Covidien Ag | Method and system for compensating for external impedance of an energy carrying component when controlling an electrosurgical generator |
US7856985B2 (en) | 2005-04-22 | 2010-12-28 | Cynosure, Inc. | Method of treatment body tissue using a non-uniform laser beam |
US7674260B2 (en) | 2005-04-28 | 2010-03-09 | Cytyc Corporation | Emergency hemostasis device utilizing energy |
US8044996B2 (en) * | 2005-05-11 | 2011-10-25 | Xenogen Corporation | Surface construction using combined photographic and structured light information |
US20080091193A1 (en) * | 2005-05-16 | 2008-04-17 | James Kauphusman | Irrigated ablation catheter having magnetic tip for magnetic field control and guidance |
US8016822B2 (en) | 2005-05-28 | 2011-09-13 | Boston Scientific Scimed, Inc. | Fluid injecting devices and methods and apparatus for maintaining contact between fluid injecting devices and tissue |
US7776034B2 (en) * | 2005-06-15 | 2010-08-17 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Ablation catheter with adjustable virtual electrode |
US7419486B2 (en) * | 2005-06-15 | 2008-09-02 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Treatment and diagnostic catheters with hydrogel electrodes |
AU2006262447A1 (en) | 2005-06-20 | 2007-01-04 | Medtronic Ablation Frontiers Llc | Ablation catheter |
US7819868B2 (en) | 2005-06-21 | 2010-10-26 | St. Jude Medical, Atrial Fibrilation Division, Inc. | Ablation catheter with fluid distribution structures |
US7655003B2 (en) | 2005-06-22 | 2010-02-02 | Smith & Nephew, Inc. | Electrosurgical power control |
US8080009B2 (en) | 2005-07-01 | 2011-12-20 | Halt Medical Inc. | Radio frequency ablation device for the destruction of tissue masses |
US8512333B2 (en) * | 2005-07-01 | 2013-08-20 | Halt Medical Inc. | Anchored RF ablation device for the destruction of tissue masses |
AU2006268238A1 (en) | 2005-07-11 | 2007-01-18 | Medtronic Ablation Frontiers Llc | Low power tissue ablation system |
US7879030B2 (en) | 2005-07-27 | 2011-02-01 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Multipolar, virtual-electrode catheter with at least one surface electrode and method for ablation |
US7416552B2 (en) | 2005-08-22 | 2008-08-26 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Multipolar, multi-lumen, virtual-electrode catheter with at least one surface electrode and method for ablation |
US8657814B2 (en) | 2005-08-22 | 2014-02-25 | Medtronic Ablation Frontiers Llc | User interface for tissue ablation system |
CN101309631A (en) | 2005-09-15 | 2008-11-19 | 帕洛玛医疗技术公司 | Skin optical characterization device |
US7879031B2 (en) * | 2005-09-27 | 2011-02-01 | Covidien Ag | Cooled RF ablation needle |
AU2005215926B2 (en) * | 2005-09-27 | 2012-09-13 | Covidien Ag | Cooled RF ablation needle |
US20070078454A1 (en) * | 2005-09-30 | 2007-04-05 | Mcpherson James W | System and method for creating lesions using bipolar electrodes |
US20070078453A1 (en) * | 2005-10-04 | 2007-04-05 | Johnson Kristin D | System and method for performing cardiac ablation |
US8734438B2 (en) | 2005-10-21 | 2014-05-27 | Covidien Ag | Circuit and method for reducing stored energy in an electrosurgical generator |
US8221310B2 (en) | 2005-10-25 | 2012-07-17 | Voyage Medical, Inc. | Tissue visualization device and method variations |
US7842031B2 (en) * | 2005-11-18 | 2010-11-30 | Medtronic Cryocath Lp | Bioimpedance measurement system and method |
US8696656B2 (en) | 2005-11-18 | 2014-04-15 | Medtronic Cryocath Lp | System and method for monitoring bioimpedance and respiration |
US7947039B2 (en) | 2005-12-12 | 2011-05-24 | Covidien Ag | Laparoscopic apparatus for performing electrosurgical procedures |
US7691101B2 (en) | 2006-01-06 | 2010-04-06 | Arthrocare Corporation | Electrosurgical method and system for treating foot ulcer |
US8876746B2 (en) | 2006-01-06 | 2014-11-04 | Arthrocare Corporation | Electrosurgical system and method for treating chronic wound tissue |
US9827437B2 (en) | 2006-01-17 | 2017-11-28 | Endymed Medical Ltd | Skin treatment devices and methods |
US9844682B2 (en) | 2006-01-17 | 2017-12-19 | Endymed Medical Ltd. | Skin treatment devices and methods |
US9186200B2 (en) | 2006-01-24 | 2015-11-17 | Covidien Ag | System and method for tissue sealing |
CA2574935A1 (en) | 2006-01-24 | 2007-07-24 | Sherwood Services Ag | A method and system for controlling an output of a radio-frequency medical generator having an impedance based control algorithm |
US7972328B2 (en) | 2006-01-24 | 2011-07-05 | Covidien Ag | System and method for tissue sealing |
US8147485B2 (en) | 2006-01-24 | 2012-04-03 | Covidien Ag | System and method for tissue sealing |
CA2574934C (en) | 2006-01-24 | 2015-12-29 | Sherwood Services Ag | System and method for closed loop monitoring of monopolar electrosurgical apparatus |
US7513896B2 (en) | 2006-01-24 | 2009-04-07 | Covidien Ag | Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling |
US8216223B2 (en) | 2006-01-24 | 2012-07-10 | Covidien Ag | System and method for tissue sealing |
US8685016B2 (en) | 2006-01-24 | 2014-04-01 | Covidien Ag | System and method for tissue sealing |
US20100191306A1 (en) * | 2006-01-25 | 2010-07-29 | Greatbatch Ltd. | Transient voltage suppression circuit for an implanted rfid chip |
WO2007092610A2 (en) | 2006-02-07 | 2007-08-16 | Tivamed, Inc. | Vaginal remodeling device and methods |
US7651493B2 (en) | 2006-03-03 | 2010-01-26 | Covidien Ag | System and method for controlling electrosurgical snares |
US7648499B2 (en) | 2006-03-21 | 2010-01-19 | Covidien Ag | System and method for generating radio frequency energy |
US8795270B2 (en) * | 2006-04-24 | 2014-08-05 | Covidien Ag | System and method for ablating tissue |
US7651492B2 (en) | 2006-04-24 | 2010-01-26 | Covidien Ag | Arc based adaptive control system for an electrosurgical unit |
US20070258838A1 (en) * | 2006-05-03 | 2007-11-08 | Sherwood Services Ag | Peristaltic cooling pump system |
US20070260240A1 (en) | 2006-05-05 | 2007-11-08 | Sherwood Services Ag | Soft tissue RF transection and resection device |
US8753334B2 (en) | 2006-05-10 | 2014-06-17 | Covidien Ag | System and method for reducing leakage current in an electrosurgical generator |
WO2007140331A2 (en) | 2006-05-25 | 2007-12-06 | Medtronic, Inc. | Methods of using high intensity focused ultrasound to form an ablated tissue area containing a plurality of lesions |
EP2020943B1 (en) | 2006-05-30 | 2015-07-08 | ArthroCare Corporation | Hard tissue ablation system |
US8903505B2 (en) | 2006-06-08 | 2014-12-02 | Greatbatch Ltd. | Implantable lead bandstop filter employing an inductive coil with parasitic capacitance to enhance MRI compatibility of active medical devices |
US9055906B2 (en) | 2006-06-14 | 2015-06-16 | Intuitive Surgical Operations, Inc. | In-vivo visualization systems |
US7763018B2 (en) * | 2006-07-28 | 2010-07-27 | Covidien Ag | Cool-tip thermocouple including two-piece hub |
US7586957B2 (en) | 2006-08-02 | 2009-09-08 | Cynosure, Inc | Picosecond laser apparatus and methods for its operation and use |
US7731717B2 (en) | 2006-08-08 | 2010-06-08 | Covidien Ag | System and method for controlling RF output during tissue sealing |
US8034049B2 (en) | 2006-08-08 | 2011-10-11 | Covidien Ag | System and method for measuring initial tissue impedance |
US10775308B2 (en) * | 2006-08-24 | 2020-09-15 | Xenogen Corporation | Apparatus and methods for determining optical tissue properties |
US10335038B2 (en) | 2006-08-24 | 2019-07-02 | Xenogen Corporation | Spectral unmixing for in-vivo imaging |
US10004388B2 (en) | 2006-09-01 | 2018-06-26 | Intuitive Surgical Operations, Inc. | Coronary sinus cannulation |
US20080097476A1 (en) | 2006-09-01 | 2008-04-24 | Voyage Medical, Inc. | Precision control systems for tissue visualization and manipulation assemblies |
WO2008028149A2 (en) | 2006-09-01 | 2008-03-06 | Voyage Medical, Inc. | Electrophysiology mapping and visualization system |
US8486060B2 (en) | 2006-09-18 | 2013-07-16 | Cytyc Corporation | Power ramping during RF ablation |
US7637907B2 (en) * | 2006-09-19 | 2009-12-29 | Covidien Ag | System and method for return electrode monitoring |
US7794457B2 (en) | 2006-09-28 | 2010-09-14 | Covidien Ag | Transformer for RF voltage sensing |
US10335131B2 (en) | 2006-10-23 | 2019-07-02 | Intuitive Surgical Operations, Inc. | Methods for preventing tissue migration |
US20080183036A1 (en) | 2006-12-18 | 2008-07-31 | Voyage Medical, Inc. | Systems and methods for unobstructed visualization and ablation |
US8758229B2 (en) | 2006-12-21 | 2014-06-24 | Intuitive Surgical Operations, Inc. | Axial visualization systems |
US7846160B2 (en) | 2006-12-21 | 2010-12-07 | Cytyc Corporation | Method and apparatus for sterilization |
US8131350B2 (en) | 2006-12-21 | 2012-03-06 | Voyage Medical, Inc. | Stabilization of visualization catheters |
CN100574719C (en) * | 2006-12-26 | 2009-12-30 | 上海导向医疗系统有限公司 | Gas throttling cooling type radio frequency ablation electrode |
US7766907B2 (en) * | 2006-12-28 | 2010-08-03 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Ablation catheter with sensor array and discrimination circuit to minimize variation in power density |
US20080161743A1 (en) * | 2006-12-28 | 2008-07-03 | Crowe John E | Ablation device having a piezoelectric pump |
GB2452103B (en) * | 2007-01-05 | 2011-08-31 | Arthrocare Corp | Electrosurgical system with suction control apparatus and system |
US8211099B2 (en) | 2007-01-31 | 2012-07-03 | Tyco Healthcare Group Lp | Thermal feedback systems and methods of using the same |
EP2112908B1 (en) * | 2007-02-25 | 2013-11-20 | Kimberly-Clark Inc. | Control of energy delivery to multiple energy delivery devices |
US20090187183A1 (en) * | 2007-03-13 | 2009-07-23 | Gordon Epstein | Temperature responsive ablation rf driving for moderating return electrode temperature |
US20090138011A1 (en) * | 2007-03-13 | 2009-05-28 | Gordon Epstein | Intermittent ablation rf driving for moderating return electrode temperature |
US7862560B2 (en) | 2007-03-23 | 2011-01-04 | Arthrocare Corporation | Ablation apparatus having reduced nerve stimulation and related methods |
US9155452B2 (en) | 2007-04-27 | 2015-10-13 | Intuitive Surgical Operations, Inc. | Complex shape steerable tissue visualization and manipulation catheter |
US8657805B2 (en) | 2007-05-08 | 2014-02-25 | Intuitive Surgical Operations, Inc. | Complex shape steerable tissue visualization and manipulation catheter |
US8777941B2 (en) | 2007-05-10 | 2014-07-15 | Covidien Lp | Adjustable impedance electrosurgical electrodes |
US8641704B2 (en) | 2007-05-11 | 2014-02-04 | Medtronic Ablation Frontiers Llc | Ablation therapy system and method for treating continuous atrial fibrillation |
US8709008B2 (en) | 2007-05-11 | 2014-04-29 | Intuitive Surgical Operations, Inc. | Visual electrode ablation systems |
US7777130B2 (en) * | 2007-06-18 | 2010-08-17 | Vivant Medical, Inc. | Microwave cable cooling |
US9486269B2 (en) * | 2007-06-22 | 2016-11-08 | Covidien Lp | Electrosurgical systems and cartridges for use therewith |
US7834484B2 (en) | 2007-07-16 | 2010-11-16 | Tyco Healthcare Group Lp | Connection cable and method for activating a voltage-controlled generator |
US8235985B2 (en) | 2007-08-31 | 2012-08-07 | Voyage Medical, Inc. | Visualization and ablation system variations |
US8181995B2 (en) * | 2007-09-07 | 2012-05-22 | Tyco Healthcare Group Lp | Cool tip junction |
US8216220B2 (en) | 2007-09-07 | 2012-07-10 | Tyco Healthcare Group Lp | System and method for transmission of combined data stream |
US8512332B2 (en) | 2007-09-21 | 2013-08-20 | Covidien Lp | Real-time arc control in electrosurgical generators |
US9579148B2 (en) * | 2007-11-13 | 2017-02-28 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Irrigated ablation electrode having recessed surface portions |
US8128620B2 (en) * | 2007-11-13 | 2012-03-06 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Irrigated ablation electrode having proximal direction flow |
US8251991B2 (en) | 2007-11-14 | 2012-08-28 | Halt Medical Inc. | Anchored RF ablation device for the destruction of tissue masses |
US8241276B2 (en) * | 2007-11-14 | 2012-08-14 | Halt Medical Inc. | RF ablation device with jam-preventing electrical coupling member |
US8292880B2 (en) | 2007-11-27 | 2012-10-23 | Vivant Medical, Inc. | Targeted cooling of deployable microwave antenna |
US8221409B2 (en) * | 2007-12-21 | 2012-07-17 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Thermally insulated irrigation catheter assembly |
US8998892B2 (en) | 2007-12-21 | 2015-04-07 | Atricure, Inc. | Ablation device with cooled electrodes and methods of use |
US8273082B2 (en) | 2007-12-21 | 2012-09-25 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Irrigated ablation catheter assembly having a flow member to create parallel external flow |
US8353907B2 (en) * | 2007-12-21 | 2013-01-15 | Atricure, Inc. | Ablation device with internally cooled electrodes |
US8216225B2 (en) * | 2007-12-21 | 2012-07-10 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Irrigated ablation electrode assembly having a polygonal electrode |
US8118809B2 (en) * | 2007-12-21 | 2012-02-21 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Flexible conductive polymer electrode and method for ablation |
US8882756B2 (en) | 2007-12-28 | 2014-11-11 | Medtronic Advanced Energy Llc | Fluid-assisted electrosurgical devices, methods and systems |
US8858609B2 (en) | 2008-02-07 | 2014-10-14 | Intuitive Surgical Operations, Inc. | Stent delivery under direct visualization |
US9358063B2 (en) | 2008-02-14 | 2016-06-07 | Arthrocare Corporation | Ablation performance indicator for electrosurgical devices |
CN102065775B (en) * | 2008-02-20 | 2015-01-07 | 梅约医学教育与研究基金会 | Ultrasound guided systems and methods |
US20090248011A1 (en) * | 2008-02-28 | 2009-10-01 | Hlavka Edwin J | Chronic venous insufficiency treatment |
US10080889B2 (en) | 2009-03-19 | 2018-09-25 | Greatbatch Ltd. | Low inductance and low resistance hermetically sealed filtered feedthrough for an AIMD |
US9108066B2 (en) | 2008-03-20 | 2015-08-18 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
WO2009140359A2 (en) | 2008-05-13 | 2009-11-19 | Medtronic, Inc. | Tissue lesion evaluation |
US8226639B2 (en) | 2008-06-10 | 2012-07-24 | Tyco Healthcare Group Lp | System and method for output control of electrosurgical generator |
DE102008050635A1 (en) * | 2008-10-07 | 2010-04-15 | Erbe Elektromedizin Gmbh | Method and apparatus for controlling a cooled RF ablation probe |
US9101735B2 (en) | 2008-07-07 | 2015-08-11 | Intuitive Surgical Operations, Inc. | Catheter control systems |
US8608739B2 (en) | 2008-07-22 | 2013-12-17 | Covidien Lp | Electrosurgical devices, systems and methods of using the same |
US8747400B2 (en) | 2008-08-13 | 2014-06-10 | Arthrocare Corporation | Systems and methods for screen electrode securement |
US8454599B2 (en) * | 2008-08-13 | 2013-06-04 | Olympus Medical Systems Corp. | Treatment apparatus and electro-surgical device |
US8133219B2 (en) | 2008-10-07 | 2012-03-13 | Olympus Medical Systems Corp. | High frequency operation apparatus and high frequency operation method |
US8894643B2 (en) | 2008-10-10 | 2014-11-25 | Intuitive Surgical Operations, Inc. | Integral electrode placement and connection systems |
US8734444B2 (en) | 2008-10-10 | 2014-05-27 | Covidien Lp | System and method for delivering high current to electrosurgical device |
US8333012B2 (en) | 2008-10-10 | 2012-12-18 | Voyage Medical, Inc. | Method of forming electrode placement and connection systems |
US8852179B2 (en) * | 2008-10-10 | 2014-10-07 | Covidien Lp | Apparatus, system and method for monitoring tissue during an electrosurgical procedure |
US9468364B2 (en) | 2008-11-14 | 2016-10-18 | Intuitive Surgical Operations, Inc. | Intravascular catheter with hood and image processing systems |
US8355799B2 (en) | 2008-12-12 | 2013-01-15 | Arthrocare Corporation | Systems and methods for limiting joint temperature |
US8447414B2 (en) | 2008-12-17 | 2013-05-21 | Greatbatch Ltd. | Switched safety protection circuit for an AIMD system during exposure to high power electromagnetic fields |
US8652129B2 (en) | 2008-12-31 | 2014-02-18 | Medtronic Ardian Luxembourg S.A.R.L. | Apparatus, systems, and methods for achieving intravascular, thermally-induced renal neuromodulation |
US8974445B2 (en) | 2009-01-09 | 2015-03-10 | Recor Medical, Inc. | Methods and apparatus for treatment of cardiac valve insufficiency |
US8262652B2 (en) | 2009-01-12 | 2012-09-11 | Tyco Healthcare Group Lp | Imaginary impedance process monitoring and intelligent shut-off |
US9254168B2 (en) | 2009-02-02 | 2016-02-09 | Medtronic Advanced Energy Llc | Electro-thermotherapy of tissue using penetrating microelectrode array |
EP2395934B1 (en) | 2009-02-11 | 2019-04-17 | Boston Scientific Scimed, Inc. | Insulated ablation catheter devices |
US8632533B2 (en) | 2009-02-23 | 2014-01-21 | Medtronic Advanced Energy Llc | Fluid-assisted electrosurgical device |
US8574187B2 (en) | 2009-03-09 | 2013-11-05 | Arthrocare Corporation | System and method of an electrosurgical controller with output RF energy control |
US8095224B2 (en) * | 2009-03-19 | 2012-01-10 | Greatbatch Ltd. | EMI shielded conduit assembly for an active implantable medical device |
US8257350B2 (en) | 2009-06-17 | 2012-09-04 | Arthrocare Corporation | Method and system of an electrosurgical controller with wave-shaping |
WO2011008444A1 (en) * | 2009-06-30 | 2011-01-20 | Boston Scientific Scimed, Inc. | Map and ablate open irrigated hybrid catheter |
US9919168B2 (en) | 2009-07-23 | 2018-03-20 | Palomar Medical Technologies, Inc. | Method for improvement of cellulite appearance |
US9345541B2 (en) | 2009-09-08 | 2016-05-24 | Medtronic Advanced Energy Llc | Cartridge assembly for electrosurgical devices, electrosurgical unit and methods of use thereof |
EP2477695B1 (en) | 2009-09-18 | 2015-10-21 | Viveve Inc. | Vaginal remodeling device |
US20110112529A1 (en) | 2009-09-22 | 2011-05-12 | Mederi Therapeutics Inc. | Systems and methods for controlling use and operation of a family of different treatment devices |
US9775664B2 (en) | 2009-09-22 | 2017-10-03 | Mederi Therapeutics, Inc. | Systems and methods for treating tissue with radiofrequency energy |
US9750563B2 (en) | 2009-09-22 | 2017-09-05 | Mederi Therapeutics, Inc. | Systems and methods for treating tissue with radiofrequency energy |
US10386990B2 (en) | 2009-09-22 | 2019-08-20 | Mederi Rf, Llc | Systems and methods for treating tissue with radiofrequency energy |
US9474565B2 (en) | 2009-09-22 | 2016-10-25 | Mederi Therapeutics, Inc. | Systems and methods for treating tissue with radiofrequency energy |
US8317786B2 (en) | 2009-09-25 | 2012-11-27 | AthroCare Corporation | System, method and apparatus for electrosurgical instrument with movable suction sheath |
US8323279B2 (en) | 2009-09-25 | 2012-12-04 | Arthocare Corporation | System, method and apparatus for electrosurgical instrument with movable fluid delivery sheath |
US9113926B2 (en) * | 2009-09-29 | 2015-08-25 | Covidien Lp | Management of voltage standing wave ratio at skin surface during microwave ablation |
TWI423602B (en) * | 2009-12-07 | 2014-01-11 | Mediatek Inc | Method of reducing interference between two communication systems operating in adjacent frequency bands |
US8372067B2 (en) | 2009-12-09 | 2013-02-12 | Arthrocare Corporation | Electrosurgery irrigation primer systems and methods |
US8920415B2 (en) * | 2009-12-16 | 2014-12-30 | Biosense Webster (Israel) Ltd. | Catheter with helical electrode |
US8936631B2 (en) * | 2010-01-04 | 2015-01-20 | Covidien Lp | Apparatus and methods for treating hollow anatomical structures |
US8882763B2 (en) | 2010-01-12 | 2014-11-11 | Greatbatch Ltd. | Patient attached bonding strap for energy dissipation from a probe or a catheter during magnetic resonance imaging |
US8694071B2 (en) | 2010-02-12 | 2014-04-08 | Intuitive Surgical Operations, Inc. | Image stabilization techniques and methods |
US8556891B2 (en) * | 2010-03-03 | 2013-10-15 | Medtronic Ablation Frontiers Llc | Variable-output radiofrequency ablation power supply |
US9592090B2 (en) | 2010-03-11 | 2017-03-14 | Medtronic Advanced Energy Llc | Bipolar electrosurgical cutter with position insensitive return electrode contact |
US9814522B2 (en) | 2010-04-06 | 2017-11-14 | Intuitive Surgical Operations, Inc. | Apparatus and methods for ablation efficacy |
US8747399B2 (en) | 2010-04-06 | 2014-06-10 | Arthrocare Corporation | Method and system of reduction of low frequency muscle stimulation during electrosurgical procedures |
US8696659B2 (en) | 2010-04-30 | 2014-04-15 | Arthrocare Corporation | Electrosurgical system and method having enhanced temperature measurement |
US20110295249A1 (en) * | 2010-05-28 | 2011-12-01 | Salient Surgical Technologies, Inc. | Fluid-Assisted Electrosurgical Devices, and Methods of Manufacture Thereof |
US9138289B2 (en) | 2010-06-28 | 2015-09-22 | Medtronic Advanced Energy Llc | Electrode sheath for electrosurgical device |
US8906012B2 (en) | 2010-06-30 | 2014-12-09 | Medtronic Advanced Energy Llc | Electrosurgical devices with wire electrode |
US8920417B2 (en) | 2010-06-30 | 2014-12-30 | Medtronic Advanced Energy Llc | Electrosurgical devices and methods of use thereof |
US8685018B2 (en) | 2010-10-15 | 2014-04-01 | Arthrocare Corporation | Electrosurgical wand and related method and system |
US8568405B2 (en) | 2010-10-15 | 2013-10-29 | Arthrocare Corporation | Electrosurgical wand and related method and system |
USD658760S1 (en) | 2010-10-15 | 2012-05-01 | Arthrocare Corporation | Wound care electrosurgical wand |
US10448992B2 (en) | 2010-10-22 | 2019-10-22 | Arthrocare Corporation | Electrosurgical system with device specific operational parameters |
US9066720B2 (en) | 2010-10-25 | 2015-06-30 | Medtronic Ardian Luxembourg S.A.R.L. | Devices, systems and methods for evaluation and feedback of neuromodulation treatment |
US9023040B2 (en) | 2010-10-26 | 2015-05-05 | Medtronic Advanced Energy Llc | Electrosurgical cutting devices |
CN106264720A (en) * | 2010-12-28 | 2017-01-04 | 西比姆公司 | Method for the sympathetic reequilibrate of patient |
US9486275B2 (en) | 2010-12-30 | 2016-11-08 | Avent, Inc. | Electrosurgical apparatus having a sensor |
US8747401B2 (en) | 2011-01-20 | 2014-06-10 | Arthrocare Corporation | Systems and methods for turbinate reduction |
US9131597B2 (en) | 2011-02-02 | 2015-09-08 | Arthrocare Corporation | Electrosurgical system and method for treating hard body tissue |
US8974450B2 (en) | 2011-02-03 | 2015-03-10 | Covidien Lp | System and method for ablation procedure monitoring using electrodes |
US9271784B2 (en) | 2011-02-09 | 2016-03-01 | Arthrocare Corporation | Fine dissection electrosurgical device |
US9168082B2 (en) | 2011-02-09 | 2015-10-27 | Arthrocare Corporation | Fine dissection electrosurgical device |
US9931514B2 (en) | 2013-06-30 | 2018-04-03 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
US9427596B2 (en) | 2013-01-16 | 2016-08-30 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
US11198014B2 (en) | 2011-03-01 | 2021-12-14 | Greatbatch Ltd. | Hermetically sealed filtered feedthrough assembly having a capacitor with an oxide resistant electrical connection to an active implantable medical device housing |
US10272252B2 (en) | 2016-11-08 | 2019-04-30 | Greatbatch Ltd. | Hermetic terminal for an AIMD having a composite brazed conductive lead |
US10350421B2 (en) | 2013-06-30 | 2019-07-16 | Greatbatch Ltd. | Metallurgically bonded gold pocket pad for grounding an EMI filter to a hermetic terminal for an active implantable medical device |
US10596369B2 (en) | 2011-03-01 | 2020-03-24 | Greatbatch Ltd. | Low equivalent series resistance RF filter for an active implantable medical device |
US9011428B2 (en) | 2011-03-02 | 2015-04-21 | Arthrocare Corporation | Electrosurgical device with internal digestor electrode |
US20120232549A1 (en) * | 2011-03-09 | 2012-09-13 | Vivant Medical, Inc. | Systems for thermal-feedback-controlled rate of fluid flow to fluid-cooled antenna assembly and methods of directing energy to tissue using same |
US10335230B2 (en) | 2011-03-09 | 2019-07-02 | Covidien Lp | Systems for thermal-feedback-controlled rate of fluid flow to fluid-cooled antenna assembly and methods of directing energy to tissue using same |
US9427281B2 (en) | 2011-03-11 | 2016-08-30 | Medtronic Advanced Energy Llc | Bronchoscope-compatible catheter provided with electrosurgical device |
US9220433B2 (en) | 2011-06-30 | 2015-12-29 | Biosense Webster (Israel), Ltd. | Catheter with variable arcuate distal section |
US9662169B2 (en) | 2011-07-30 | 2017-05-30 | Biosense Webster (Israel) Ltd. | Catheter with flow balancing valve |
US9033973B2 (en) | 2011-08-30 | 2015-05-19 | Covidien Lp | System and method for DC tissue impedance sensing |
US9788882B2 (en) | 2011-09-08 | 2017-10-17 | Arthrocare Corporation | Plasma bipolar forceps |
CA2847846A1 (en) | 2011-09-14 | 2013-03-21 | Boston Scientific Scimed, Inc. | Ablation device with multiple ablation modes |
EP2755588B1 (en) | 2011-09-14 | 2016-05-18 | Boston Scientific Scimed, Inc. | Ablation device with ionically conductive balloon |
US9750565B2 (en) | 2011-09-30 | 2017-09-05 | Medtronic Advanced Energy Llc | Electrosurgical balloons |
US8870864B2 (en) | 2011-10-28 | 2014-10-28 | Medtronic Advanced Energy Llc | Single instrument electrosurgery apparatus and its method of use |
WO2013106557A1 (en) | 2012-01-10 | 2013-07-18 | Boston Scientific Scimed, Inc. | Electrophysiology system |
WO2013115941A1 (en) | 2012-01-31 | 2013-08-08 | Boston Scientific Scimed, Inc. | Ablation probe with fluid-based acoustic coupling for ultrasonic tissue imaging |
US9750568B2 (en) | 2012-03-08 | 2017-09-05 | Medtronic Ardian Luxembourg S.A.R.L. | Ovarian neuromodulation and associated systems and methods |
EP3348220A1 (en) | 2012-03-08 | 2018-07-18 | Medtronic Ardian Luxembourg S.à.r.l. | Biomarker sampling in the context of neuromodulation devices and associated systems |
CN105919666A (en) | 2012-03-16 | 2016-09-07 | 女康乐公司 | Therapy equipment for repairing female vaginal tissue |
US8945113B2 (en) | 2012-04-05 | 2015-02-03 | Covidien Lp | Electrosurgical tissue ablation systems capable of detecting excessive bending of a probe and alerting a user |
US20130274737A1 (en) * | 2012-04-16 | 2013-10-17 | Boston Scientific Scimed, Inc. | Renal nerve modulation catheter design |
KR102183581B1 (en) | 2012-04-18 | 2020-11-27 | 싸이노슈어, 엘엘씨 | Picosecond laser apparatus and methods for treating target tissues with same |
DE112013002175T5 (en) | 2012-04-24 | 2015-01-22 | Cibiem, Inc. | Endovascular catheters and procedures for ablation of the carotid body |
KR101415900B1 (en) * | 2012-05-18 | 2014-07-08 | 신경민 | Reiterating type bipolar electrode for high frequency thermotherapy |
US9770293B2 (en) | 2012-06-04 | 2017-09-26 | Boston Scientific Scimed, Inc. | Systems and methods for treating tissue of a passageway within a body |
JP6301926B2 (en) | 2012-08-09 | 2018-03-28 | ユニバーシティ オブ アイオワ リサーチ ファウンデーション | Catheter, catheter system, and method for piercing tissue structure |
WO2014047068A1 (en) | 2012-09-18 | 2014-03-27 | Boston Scientific Scimed, Inc. | Map and ablate closed-loop cooled ablation catheter |
US20140110296A1 (en) | 2012-10-19 | 2014-04-24 | Medtronic Ardian Luxembourg S.A.R.L. | Packaging for Catheter Treatment Devices and Associated Devices, Systems, and Methods |
USRE46699E1 (en) | 2013-01-16 | 2018-02-06 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
US9254166B2 (en) | 2013-01-17 | 2016-02-09 | Arthrocare Corporation | Systems and methods for turbinate reduction |
US9717551B2 (en) | 2013-02-21 | 2017-08-01 | Carefusion 2200, Inc. | Intravertebral tissue ablation device and method |
US9693818B2 (en) | 2013-03-07 | 2017-07-04 | Arthrocare Corporation | Methods and systems related to electrosurgical wands |
US9713489B2 (en) | 2013-03-07 | 2017-07-25 | Arthrocare Corporation | Electrosurgical methods and systems |
US10076384B2 (en) | 2013-03-08 | 2018-09-18 | Symple Surgical, Inc. | Balloon catheter apparatus with microwave emitter |
US9801678B2 (en) | 2013-03-13 | 2017-10-31 | Arthrocare Corporation | Method and system of controlling conductive fluid flow during an electrosurgical procedure |
WO2014145707A2 (en) | 2013-03-15 | 2014-09-18 | Cynosure, Inc. | Picosecond optical radiation systems and methods of use |
US9439723B2 (en) | 2013-06-20 | 2016-09-13 | Abhimanyu Beri | Variable stiffness catheter |
US9872719B2 (en) | 2013-07-24 | 2018-01-23 | Covidien Lp | Systems and methods for generating electrosurgical energy using a multistage power converter |
US9636165B2 (en) | 2013-07-29 | 2017-05-02 | Covidien Lp | Systems and methods for measuring tissue impedance through an electrosurgical cable |
EP3091921B1 (en) | 2014-01-06 | 2019-06-19 | Farapulse, Inc. | Apparatus for renal denervation ablation |
US9526556B2 (en) | 2014-02-28 | 2016-12-27 | Arthrocare Corporation | Systems and methods systems related to electrosurgical wands with screen electrodes |
WO2015138795A1 (en) | 2014-03-12 | 2015-09-17 | Cibiem, Inc. | Carotid body ablation with a transvenous ultrasound imaging and ablation catheter |
US10194980B1 (en) | 2014-03-28 | 2019-02-05 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for catheter-based renal neuromodulation |
US9980766B1 (en) | 2014-03-28 | 2018-05-29 | Medtronic Ardian Luxembourg S.A.R.L. | Methods and systems for renal neuromodulation |
US10194979B1 (en) | 2014-03-28 | 2019-02-05 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for catheter-based renal neuromodulation |
WO2015153815A1 (en) | 2014-04-01 | 2015-10-08 | Gregory Brucker | Temperature-responsive irrigated ablation electrode with reduced coolant flow and related methods for making and using |
EP3495018B1 (en) | 2014-05-07 | 2023-09-06 | Farapulse, Inc. | Apparatus for selective tissue ablation |
WO2015192027A1 (en) * | 2014-06-12 | 2015-12-17 | Iowa Approach Inc. | Method and apparatus for rapid and selective transurethral tissue ablation |
EP3154464A4 (en) | 2014-06-12 | 2018-01-24 | Iowa Approach Inc. | Method and apparatus for rapid and selective tissue ablation with cooling |
US9597142B2 (en) | 2014-07-24 | 2017-03-21 | Arthrocare Corporation | Method and system related to electrosurgical procedures |
US9649148B2 (en) | 2014-07-24 | 2017-05-16 | Arthrocare Corporation | Electrosurgical system and method having enhanced arc prevention |
US9974599B2 (en) | 2014-08-15 | 2018-05-22 | Medtronic Ps Medical, Inc. | Multipurpose electrosurgical device |
CN106793968A (en) | 2014-10-13 | 2017-05-31 | 波士顿科学医学有限公司 | Organizational diagnosis and treatment using microelectrode |
EP3206613B1 (en) | 2014-10-14 | 2019-07-03 | Farapulse, Inc. | Apparatus for rapid and safe pulmonary vein cardiac ablation |
EP3209234B1 (en) | 2014-10-24 | 2023-11-29 | Boston Scientific Scimed Inc. | Medical devices with a flexible electrode assembly coupled to an ablation tip |
WO2016070013A1 (en) | 2014-10-31 | 2016-05-06 | Medtronic Advanced Energy Llc | Fingerswitch circuitry to reduce rf leakage current |
WO2016081611A1 (en) | 2014-11-19 | 2016-05-26 | Advanced Cardiac Therapeutics, Inc. | High-resolution mapping of tissue with pacing |
EP3220843B1 (en) | 2014-11-19 | 2020-01-01 | EPiX Therapeutics, Inc. | Ablation devices and methods of using a high-resolution electrode assembly |
CA2967829A1 (en) | 2014-11-19 | 2016-05-26 | Advanced Cardiac Therapeutics, Inc. | Systems and methods for high-resolution mapping of tissue |
US20160143686A1 (en) * | 2014-11-19 | 2016-05-26 | Stereotaxis, Inc. | Inter-electrode impedance for detecting tissue distance, orientation, contact and contact quality |
WO2016100917A1 (en) | 2014-12-18 | 2016-06-23 | Boston Scientific Scimed Inc. | Real-time morphology analysis for lesion assessment |
US9636164B2 (en) | 2015-03-25 | 2017-05-02 | Advanced Cardiac Therapeutics, Inc. | Contact sensing systems and methods |
US10806512B2 (en) | 2015-03-26 | 2020-10-20 | Garner B. Meads, JR. | Nasal coagulation suction device and methods |
US9775673B2 (en) * | 2015-03-26 | 2017-10-03 | Garner B. Meads, JR. | Nasal coagulation suction device and methods |
EP3288478B1 (en) | 2015-04-29 | 2019-12-25 | Innoblative Designs, Inc. | Cavitary tissue ablation |
US11389227B2 (en) | 2015-08-20 | 2022-07-19 | Medtronic Advanced Energy Llc | Electrosurgical device with multivariate control |
US11051875B2 (en) | 2015-08-24 | 2021-07-06 | Medtronic Advanced Energy Llc | Multipurpose electrosurgical device |
US20170106199A1 (en) | 2015-10-16 | 2017-04-20 | Brady L. WOOLFORD | Integrated pump control for dynamic control of plasma field |
ES2779627T3 (en) | 2015-10-29 | 2020-08-18 | Innoblative Designs Inc | Spherical Screen Tissue Ablation Devices |
WO2017091335A1 (en) * | 2015-11-25 | 2017-06-01 | Smith And Nephew, Inc. | System and methods of controlling temperature related to electrosurgical procedures |
US11324442B1 (en) | 2015-11-25 | 2022-05-10 | Maquet Cardiovascular Llc | Broadband impedance spectroscopy and its use for tissue welding |
US10716612B2 (en) | 2015-12-18 | 2020-07-21 | Medtronic Advanced Energy Llc | Electrosurgical device with multiple monopolar electrode assembly |
US10172673B2 (en) | 2016-01-05 | 2019-01-08 | Farapulse, Inc. | Systems devices, and methods for delivery of pulsed electric field ablative energy to endocardial tissue |
US20170189097A1 (en) | 2016-01-05 | 2017-07-06 | Iowa Approach Inc. | Systems, apparatuses and methods for delivery of ablative energy to tissue |
US10660702B2 (en) | 2016-01-05 | 2020-05-26 | Farapulse, Inc. | Systems, devices, and methods for focal ablation |
US10130423B1 (en) | 2017-07-06 | 2018-11-20 | Farapulse, Inc. | Systems, devices, and methods for focal ablation |
US20170215947A1 (en) | 2016-02-02 | 2017-08-03 | Innoblative Designs, Inc. | Cavitary tissue ablation system |
US10869714B2 (en) | 2016-03-01 | 2020-12-22 | Innoblative Designs, Inc. | Resecting and coagulating tissue |
KR20180124070A (en) | 2016-03-15 | 2018-11-20 | 에픽스 테라퓨틱스, 인크. | Improved apparatus, systems and methods for irrigation ablation |
GB2550375B (en) | 2016-05-17 | 2021-12-01 | Creo Medical Ltd | Electrosurgical cutting tool |
GB2550414A (en) * | 2016-05-20 | 2017-11-22 | Creo Medical Ltd | Antenna structure |
WO2017218734A1 (en) | 2016-06-16 | 2017-12-21 | Iowa Approach, Inc. | Systems, apparatuses, and methods for guide wire delivery |
JP2019536509A (en) | 2016-10-17 | 2019-12-19 | イノブレイティブ デザインズ, インコーポレイテッド | Treatment device and method |
EP3538000A4 (en) | 2016-11-08 | 2020-04-01 | Innoblative Designs, Inc. | Electrosurgical tissue and vessel sealing device |
US10249415B2 (en) | 2017-01-06 | 2019-04-02 | Greatbatch Ltd. | Process for manufacturing a leadless feedthrough for an active implantable medical device |
US11511110B2 (en) | 2018-06-27 | 2022-11-29 | Viveve, Inc. | Methods for treating urinary stress incontinence |
US11896823B2 (en) | 2017-04-04 | 2024-02-13 | Btl Healthcare Technologies A.S. | Method and device for pelvic floor tissue treatment |
US9987081B1 (en) | 2017-04-27 | 2018-06-05 | Iowa Approach, Inc. | Systems, devices, and methods for signal generation |
EP3614946B1 (en) | 2017-04-27 | 2024-03-20 | EPiX Therapeutics, Inc. | Determining nature of contact between catheter tip and tissue |
US10617867B2 (en) | 2017-04-28 | 2020-04-14 | Farapulse, Inc. | Systems, devices, and methods for delivery of pulsed electric field ablative energy to esophageal tissue |
US10194975B1 (en) | 2017-07-11 | 2019-02-05 | Medtronic Advanced Energy, Llc | Illuminated and isolated electrosurgical apparatus |
EP3658053B1 (en) | 2017-07-26 | 2023-09-13 | Innoblative Designs, Inc. | Minimally invasive articulating assembly having ablation capabilities |
CN115844523A (en) | 2017-09-12 | 2023-03-28 | 波士顿科学医学有限公司 | Systems, devices, and methods for ventricular focal ablation |
US20190090948A1 (en) * | 2017-09-26 | 2019-03-28 | Covidien Lp | Flexible ablation catheter with stiff section around radiator |
US11103308B2 (en) | 2017-12-11 | 2021-08-31 | Covidien Lp | Reusable transmission network for dividing energy and monitoring signals between surgical devices |
CN112042066A (en) | 2018-02-26 | 2020-12-04 | 赛诺秀股份有限公司 | Q-switched cavity-tilting subnanosecond laser |
US10912945B2 (en) | 2018-03-22 | 2021-02-09 | Greatbatch Ltd. | Hermetic terminal for an active implantable medical device having a feedthrough capacitor partially overhanging a ferrule for high effective capacitance area |
US10905888B2 (en) | 2018-03-22 | 2021-02-02 | Greatbatch Ltd. | Electrical connection for an AIMD EMI filter utilizing an anisotropic conductive layer |
CN112118798A (en) | 2018-05-07 | 2020-12-22 | 法拉普尔赛股份有限公司 | Systems, devices, and methods for filtering high voltage noise induced by pulsed electric field ablation |
JP7399881B2 (en) | 2018-05-07 | 2023-12-18 | ファラパルス,インコーポレイテッド | epicardial ablation catheter |
EP3790486A1 (en) | 2018-05-07 | 2021-03-17 | Farapulse, Inc. | Systems, apparatuses and methods for delivery of ablative energy to tissue |
CN110074860B (en) * | 2018-09-14 | 2024-02-27 | 杭州堃博生物科技有限公司 | Radio frequency ablation catheter beneficial to distribution of heat exchange medium, lung radio frequency ablation system, control method and control device |
EP3852661A1 (en) | 2018-09-20 | 2021-07-28 | Farapulse, Inc. | Systems, apparatuses, and methods for delivery of pulsed electric field ablative energy to endocardial tissue |
US20200155228A1 (en) * | 2018-11-20 | 2020-05-21 | Boston Scientific Scimed Inc. | Sheath detection using local impedance information |
US11648053B2 (en) | 2018-12-20 | 2023-05-16 | Biosense Webster (Israel) Ltd. | Catheter with flex circuit distal assembly |
US10625080B1 (en) | 2019-09-17 | 2020-04-21 | Farapulse, Inc. | Systems, apparatuses, and methods for detecting ectopic electrocardiogram signals during pulsed electric field ablation |
US11497541B2 (en) | 2019-11-20 | 2022-11-15 | Boston Scientific Scimed, Inc. | Systems, apparatuses, and methods for protecting electronic components from high power noise induced by high voltage pulses |
US11065047B2 (en) | 2019-11-20 | 2021-07-20 | Farapulse, Inc. | Systems, apparatuses, and methods for protecting electronic components from high power noise induced by high voltage pulses |
US10842572B1 (en) | 2019-11-25 | 2020-11-24 | Farapulse, Inc. | Methods, systems, and apparatuses for tracking ablation devices and generating lesion lines |
CN112791262B (en) * | 2020-12-31 | 2023-02-03 | 杭州堃博生物科技有限公司 | Radio frequency operation data regulation and control method and device and injection pump |
CN112716594B (en) * | 2020-12-31 | 2022-08-12 | 杭州堃博生物科技有限公司 | Method for protecting data exception of radio frequency operation object, radio frequency host and storage medium |
EP4349288A1 (en) | 2022-10-07 | 2024-04-10 | Erbe Elektromedizin GmbH | Ablation probe with internal cooling |
EP4349287A1 (en) | 2022-10-07 | 2024-04-10 | Erbe Elektromedizin GmbH | Ablation instrument |
Family Cites Families (23)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3572344A (en) * | 1968-12-31 | 1971-03-23 | Medtronic Inc | Electrode apparatus with lead construction |
DE2504280C3 (en) * | 1975-02-01 | 1980-08-28 | Hans Heinrich Prof. Dr. 8035 Gauting Meinke | Device for cutting and / or coagulating human tissue with high frequency current |
US4326529A (en) * | 1978-05-26 | 1982-04-27 | The United States Of America As Represented By The United States Department Of Energy | Corneal-shaping electrode |
DE3050386C2 (en) * | 1980-05-13 | 1987-06-25 | American Hospital Supply Corp | Multipolar electrosurgical device |
US4328806A (en) * | 1980-06-18 | 1982-05-11 | American Hospital Supply Corporation | Catheter with trans-luminal gas pathway |
US4381007A (en) * | 1981-04-30 | 1983-04-26 | The United States Of America As Represented By The United States Department Of Energy | Multipolar corneal-shaping electrode with flexible removable skirt |
DE3120102A1 (en) * | 1981-05-20 | 1982-12-09 | F.L. Fischer GmbH & Co, 7800 Freiburg | ARRANGEMENT FOR HIGH-FREQUENCY COAGULATION OF EGG WHITE FOR SURGICAL PURPOSES |
US4559951A (en) * | 1982-11-29 | 1985-12-24 | Cardiac Pacemakers, Inc. | Catheter assembly |
US4658836A (en) * | 1985-06-28 | 1987-04-21 | Bsd Medical Corporation | Body passage insertable applicator apparatus for electromagnetic |
US4785815A (en) * | 1985-10-23 | 1988-11-22 | Cordis Corporation | Apparatus for locating and ablating cardiac conduction pathways |
US4641649A (en) * | 1985-10-30 | 1987-02-10 | Rca Corporation | Method and apparatus for high frequency catheter ablation |
EP0249823B1 (en) * | 1986-06-16 | 1991-12-18 | Pacesetter AB | Device for the control of a heart pacer using impedance measurement at body tissues |
JPS6323676A (en) * | 1986-07-17 | 1988-01-30 | オリンパス光学工業株式会社 | High frequency heating method and apparatus |
US4785812A (en) * | 1986-11-26 | 1988-11-22 | First Medical Devices Corporation | Protection system for preventing defibrillation with incorrect or improperly connected electrodes |
US4869248A (en) * | 1987-04-17 | 1989-09-26 | Narula Onkar S | Method and apparatus for localized thermal ablation |
US4943290A (en) * | 1987-06-23 | 1990-07-24 | Concept Inc. | Electrolyte purging electrode tip |
US4907589A (en) * | 1988-04-29 | 1990-03-13 | Cosman Eric R | Automatic over-temperature control apparatus for a therapeutic heating device |
US4896671A (en) * | 1988-08-01 | 1990-01-30 | C. R. Bard, Inc. | Catheter with contoured ablation electrode |
US4966597A (en) * | 1988-11-04 | 1990-10-30 | Cosman Eric R | Thermometric cardiac tissue ablation electrode with ultra-sensitive temperature detection |
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 |
US4945912A (en) * | 1988-11-25 | 1990-08-07 | Sensor Electronics, Inc. | Catheter with radiofrequency heating applicator |
US5006119A (en) * | 1989-05-25 | 1991-04-09 | Engineering & Research Associates, Inc. | Hollow core coaxial catheter |
US5156151A (en) * | 1991-02-15 | 1992-10-20 | Cardiac Pathways Corporation | Endocardial mapping and ablation system and catheter probe |
-
1992
- 1992-11-13 US US07/975,662 patent/US5334193A/en not_active Expired - Fee Related
-
1993
- 1993-11-01 CA CA002149310A patent/CA2149310A1/en not_active Abandoned
- 1993-11-01 WO PCT/US1993/010465 patent/WO1994011059A1/en not_active Application Discontinuation
- 1993-11-01 JP JP6512145A patent/JPH08505544A/en active Pending
- 1993-11-01 AU AU54563/94A patent/AU5456394A/en not_active Abandoned
- 1993-11-01 EP EP93925138A patent/EP0703803A1/en not_active Withdrawn
Also Published As
Publication number | Publication date |
---|---|
EP0703803A1 (en) | 1996-04-03 |
WO1994011059A1 (en) | 1994-05-26 |
JPH08505544A (en) | 1996-06-18 |
EP0703803A4 (en) | 1995-11-02 |
US5334193A (en) | 1994-08-02 |
AU5456394A (en) | 1994-06-08 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA2149310A1 (en) | Fluid cooled ablation catheter | |
US5342357A (en) | Fluid cooled electrosurgical cauterization system | |
EP3158961B1 (en) | System and method for controlling catheter power based on renal ablation response | |
US8702693B2 (en) | Apparatus and methods for supplying fluid to an electrophysiology apparatus | |
US6017338A (en) | Fluid cooled and perfused tip for a catheter | |
US5681282A (en) | Methods and apparatus for ablation of luminal tissues | |
EP1280467B1 (en) | Multi-channel rf energy delivery with coagulum reduction | |
US7252664B2 (en) | System and method for multi-channel RF energy delivery with coagulum reduction | |
AU676329B2 (en) | Methods and apparatus for surgical cutting | |
US20210236200A1 (en) | System and method for adjusting available power per probe during an ablation procedure | |
WO1996000040A1 (en) | Tissue ablation systems using temperature curve control | |
CA2194072C (en) | Tissue heating and ablation system | |
US20220015814A1 (en) | Flow rate control for a cooled medical probe assembly | |
WO2019231960A1 (en) | Fiber optic temperature sensor for cooled radiofrequency probe |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
FZDE | Discontinued |