WO2003063717A1 - System and method of performing an electrosurgical procedure - Google Patents
System and method of performing an electrosurgical procedure Download PDFInfo
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- WO2003063717A1 WO2003063717A1 PCT/US2003/001036 US0301036W WO03063717A1 WO 2003063717 A1 WO2003063717 A1 WO 2003063717A1 US 0301036 W US0301036 W US 0301036W WO 03063717 A1 WO03063717 A1 WO 03063717A1
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- lesion
- electrosurgical
- power setting
- time period
- electrode
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- 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
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- 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
- A61B2018/00315—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
-
- 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
- A61B2018/00363—Epicardium
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
- A61B2018/00577—Ablation
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- 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
- A61B2018/00738—Depth, e.g. depth of ablation
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/1206—Generators therefor
- A61B2018/1246—Generators therefor characterised by the output polarity
- A61B2018/1253—Generators therefor characterised by the output polarity monopolar
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B2018/1472—Probes or electrodes therefor for use with liquid electrolyte, e.g. virtual electrodes
Definitions
- the present invention relates to a system and method of performing an electrosurgical procedure using an electrosurgical (ablation or electrocautery) device. More particularly, it relates to a method of performing an electrosurgical procedure using an ablation or electrocautery system to create a lesion.
- a wide variety of surgical procedures involve ablation or cauterization of selected tissue. For example, hemorrhoid or varicose vein removal can be accomplished by ablating the tissue in question. Additionally, tissue ablation and/or cauterization is commonly employed for the surgical treatment of cardiac arrhythmia and, in particular, atrial fibrillation.
- cardiac arrhythmia relates to disturbances in the heart's electrical system that causes the heart to beat irregularly, too fast or too slow.
- Irregular heartbeats are caused by psychological or pathological disturbances in the discharged electrical impulses from the sinoatrial node, and the transmission of the signal through the heart tissue, or spontaneous, unexpected electrical signals generated within the heart.
- arrhythmia is tachycardia, which is an abnormal rapidity of heart action.
- atrial tachycardia There are several different forms of atrial tachycardia, including atrial fibrillation and atrial flutter. With atrial fibrillation, instead of a single beat, numerous electrical impulses are generated by depolarizing tissue at one or more locations in the atria (or possibly other locations). These unexpected electrical impulses produce irregular, often rapid heartbeats in the atrial muscles and ventricles.
- ablation of the abnormal tissue or accessory pathway responsible for the atrial fibrillation has proven highly viable.
- ablation or cauterization of tissue is typically achieved by applying a destructive energy source to the target tissue, including radiofrequency electrical energy, direct current electrical energy, and the like.
- the ablative energy source is provided by an electrode and is otherwise placed in contact with the target tissue.
- the electrode can be formed as part of a handheld electrosurgical instrument.
- the term "electrosurgical instrument” includes a handheld instrument capable of ablating or cauterizing tissue.
- the instrument rigidly couples the electrode tip to an instrument handle that is otherwise held and manipulated by the surgeon.
- the rigid construction of the electrosurgical instrument typically requires direct, open access to the target tissue.
- the patient's heart may be opened through one or more incisions, thereby allowing access to the endocardial surface of the heart.
- the surgeon positions the electrode tip of the electrosurgical instrument at the target site.
- the tip is then energized, ablating (or for some applications, cauterizing) the contacted tissue.
- a desired lesion pattern is then created (e.g., portions of a known "Maze" procedure) and moving the tip in a desired fashion along the target site.
- the surgeon can easily control positioning and movement of the tip, as the electrosurgical instrument is rigidly constructed and relatively short.
- Electrosurgical instruments especially those used for treatment of atrial fibrillation, have evolved to include additional features that provide improved results for particular procedures.
- U.S. Patent No. 5,897,553 the teachings of which are incorporated herein by reference, describes a fluid-assisted electrosurgical instrument that delivers a conductive solution to the target site in conjunction with electrical energy, thereby creating a "virtual" electrode.
- the virtual electrode technique has proven highly effective at achieving the desired ablation while minimizing collateral tissue damage.
- Other electrosurgical instrument advancements have likewise optimized system performance. Unfortunately, however, use of the electrosurgical instrument to produce a lesion having desired characteristics has remained a lengthy and intense procedure.
- a lesion is created by repeatedly drawing the electrosurgical instrument across the target tissue site. Before, during, and after each pass of the electrosurgical instrument across the target tissue site, the tissue is carefully monitored and tested to determine the depth of lesion penetration on the target tissue site. Monitoring and testing of the site ensure the proper number of passes of the electrosurgical instrument to create a lesion having the desired depth for a particular procedure.
- Electrosurgical procedures utilizing electrosurgical instruments remain a viable method of lesion production for a variety of surgical treatments, including the surgical treatment of atrial fibrillation.
- typical procedures require prolonged operation time due to the need for constant testing and monitoring of the tissue and lesion depth. Therefore, a need exists for an electrosurgical procedure that reduces reliance upon testing and monitoring during the procedure, and thereby reduces procedure time and the risk of complication.
- the method includes providing an electrosurgical system, determining a desired lesion depth, selecting a desired power setting, and applying electrical energy to the living tissue.
- the electrosurgical system includes an electrosurgical instrument having an electrode at a distal portion thereof, and a power source having multiple available power settings.
- the power source is electrically connected to the electrode.
- the step of applying electrical energy includes energizing the electrode, via the power source, at the selected power setting for a recommended energization time period that is determined by reference to predetermined length of time information and based upon the desired lesion depth and the selected power setting.
- the predetermined length of time information is embodied in a look-up table.
- the electrosurgical system further includes a fluid source maintaining a supply of fluid.
- the fluid source is fluidly connected to the electrosurgical instrument and is configured to irrigate the electrode at an irrigation rate.
- the predetermined length of time information is generated as a function of irrigation rate.
- Another aspect of the present invention relates to an electrosurgical system for performing an electrosurgical procedure on living tissue.
- the electrosurgical system includes an electrosurgical instrument having an electrode at a distal portion thereof, a power source having multiple available power settings, and an energization look-up table.
- the power source is electrically connected to the electrosurgical instrument for selectively energizing the electrode.
- the energization look-up table includes a power setting data set, a lesion depth data set, and a corresponding energization time period information that is organized as a function of the power setting and lesion depth data sets.
- the energization time period information is adapted to identify a recommended energization time period for a particular electrosurgical procedure based upon a cross-reference of a desired power setting relative to the power setting data set and a desired lesion depth relative to the lesion depth data set.
- FIG. 1 is a side view of an electrosurgical system in accordance with the present invention, including the portion shown in block form;
- FIG. 2 is an enlarged, cross-sectional view of a portion of an electrosurgical instrument of FIG. 1 taken along the line 2-2;
- FIG. 3 is an example of an energization look-up table in accordance with the electrosurgical system of FIG. 1;
- FIG. 4 is a flow diagram illustrating a method of use for the electrosurgical system of FIG. 1 in accordance with the present invention;
- FIG. 5 A is a cut-away illustration of a patient's heart depicting use of the electrosurgical system of FIG. 1 during a surgical procedure;
- FIG. 5B is an enlarged illustration of a portion of the view of FIG. 5A. Description of the Preferred Embodiments
- FIG. 1 One preferred embodiment of an electrosurgical system 10 in accordance with the present invention is shown in FIG. 1.
- the system 10 is comprised of an electrosurgical instrument 12, a fluid source 14, a power source 16, an indifferent electrode 17, and an energization look-up table 18.
- the various components are described in greater detail below.
- the fluid source 14 is fluidly connected to the electrosurgical instrument 12.
- the power source 16 is electrically connected to the electrosurgical instrument 12.
- conductive fluid is delivered from the fluid source 14 to a distal portion of the electrosurgical instrument 12.
- the distributed fluid is energized by the electrosurgical instrument 12 via the power source 16 and the indifferent electrode 17.
- the so-energized conductive fluid is capable of forming a virtual electrode, which is capable of ablating or cauterizing tissue.
- the electrosurgical instrument 12 includes a handle 20 and a shaft 22.
- the handle 20 is preferably constructed of a sterilizable, rigid, and non- conductive material, such as polymer or ceramic. Suitable polymers include rigid plastic, rubber, acrylic, nylon, polystyrene, polyvinylchloride, polycarbonate, polyurethane, polyethylene, polypropylene, polyamide, polyether, polyester, polyolefin, polyacrylate, polyisoprene, fluoropolymers, combinations thereof, or the like.
- the handle 20 forms one or more central lumens (not shown).
- the lumen(s) provides a pathway for a line or tubing 24 from the fluid source 14 to the shaft 22, as well as a pathway for a line or wiring 26 from the power source 16 to the shaft 22.
- the shaft 22 is rigidly coupled to the handle 20, and is an elongated, relatively rigid tubular component defining a proximal section 30 and a distal section 32.
- the distal section 32 terminates in an electrically conductive tip (or electrode) 34.
- the tip 34 may be rounded, defining a uniform radius of curvature, or it may have a more angular shape.
- the tip 34 may comprise one or more materials and/or components.
- the tip 34 can have a roller ball configuration. Regardless, the electrically conductive tip 34 shape facilitates sliding movement of the tip 34 along the tissue.
- the shaft 22 defines an internal lumen 28 that is fluidly connected to the tube 24 that is otherwise fluidly connected to the fluid source 14. In this way, fluid is delivered from the fluid source 14 to the distal section 32 via the internal lumen 28.
- the distal section 32 preferably forms at least one passage (referenced generally at 38 in FIG. 1) that is fluidly connected to the internal lumen 28.
- the at least one passage 38 is formed at or proximal to the tip 34.
- the at least one passage 38 provides a relatively uniform disbursement of conductive fluid about tip 34 via the internal lumen 28.
- a plurality of the passages 38 are provided along a circumference of the distal section 32, as well as a passage (not shown) at the tip 34. With this one preferred embodiment, the plurality of passages 38 are circumferentially aligned, and uniformly spaced. Effectively, then, the distal section 32, and in particular the tip 34, is porous.
- the number(s) and locations(s) of the passage(s) 38 can assume any other form sufficient for distributing fluid from the internal lumen 28.
- the shaft 22 includes an elongated electrode body 40 and an electrical insulator covering 42 as shown in FIGS. 1 and 2.
- the electrode body 40 defines the proximal section 30 and the distal section 32 of the shaft 22.
- the proximal section 30 of the electrode body 40 is rigidly coupled to the handle 20.
- the insulator 42 covers a substantial portion of the electrode body 40, preferably leaving the distal section 32 exposed.
- the insulator 42 is positioned to encompass an entirety of the electrode body 40 distal the handle 20 and proximal the distal section 32 (and in particular, proximal the at least one passage 38 and the tip 34).
- the electrode body 40 is tube formed of an electrically conductive, malleable material, preferably stainless steel.
- the insulator 42 is formed of an electrical non-conductive material and serves to electrically insulate the encompassed portion of the electrode body 40.
- the electrosurgical instrument 12 can assume a variety of forms known in the art, varying from that described with respect to FIG. 1.
- the electrosurgical instrument 12 includes an electrode (e.g., the tip 34) at a distal portion thereof.
- the fluid source 14 is preferably fluidly connected to the electrosurgical instrument 12 by the tube or line 24 and maintains a supply of conductive fluid (not shown), such as an energy-conducting fluid, an ionic fluid, a saline solution, saturated saline solution, a Ringers solution, etc. It is preferred that the conductive fluid be sterile.
- the conductive fluid may comprise one or more contrast agents and/or biological agents such as a diagnostic agent, therapeutic agent or drug.
- the fluid source 14 includes a fluid reservoir, such as a bag, bottle or canister, for maintaining a supply of conductive fluid.
- a fluid reservoir such as a bag, bottle or canister
- the fluid reservoir is positioned at an elevated location, thereby gravity feeding the conductive fluid to the electrosurgical instrument 12 via the tube 24.
- the fluid reservoir may be pressurized, thereby pressure feeding the conductive fluid to the electrosurgical instrument 12.
- the fluid source 14 may include, and/or be connected to, a manual or electric pump.
- the power source 16 is electrically connected to the electrosurgical instrument 12 by the wire or line 26 and is of a type known in the art, preferably a radiofirequency (RF) generator.
- the generator may be powered by AC current, DC current, or it may be battery powered either by a disposable or re-chargeable battery.
- the power source 16 can assume a variety of forms, and is provided to selectively energize the electrode tip 34. To this end, the power source 16 is preferably configured to have a multitude of available power settings.
- electrosurgical instrument 12 fluid source 14, and power source 16 are but a few examples of acceptable configurations.
- essentially any electrosurgical instrument can be used with the present invention, and in particular in combination with the energization look-up table 18.
- the first factor (lesion depth) is a function of the remaining three factors that are otherwise controlled by the surgeon. Previously, a surgeon was required to simply guess as to appropriate settings/times for power, irrigation rate and energization time, unnecessarily lengthening the overall procedure time.
- the present invention overcomes this distinct drawback by incorporating the energization look-up table 18, either as a discrete table available for referral by the surgeon, or in electronic form in a manner that assists in controlling operation of the electrosurgical instrument 12, the fluid source 14 and/or the power source 16.
- the energization look-up table 18 provides predetermined length of time information and is preferably an organized collection of previously collected data correlating the interaction between the following four variables: a lesion depth, a power setting, an irrigation rate, and an energization time.
- the predetermined length of time information embodied by the look-up table 18 correlates a plurality of lesion depth values with a plurality of power setting values, and identifies an energization time period value for each lesion depth value and power setting value.
- the preferred look-up table 18 allows a user to apply two, more preferably three, of the four variables to ascertain the fourth. Most commonly, the lesion depth, power setting and the irrigation rate are applied to the look-up table 18 to ascertain the corresponding energization time (or a recommended energization time period for the particular procedure to be performed).
- the look-up table 18 is a graphical representation of the four variables.
- An X-axis 50 of the look-up table 18 corresponds to energization time period information
- a Y-axis 52 corresponds to a lesion depth data set
- a first power setting data set is plotted in series 54 with respect to the X-axis 50 and the Y-axis 52.
- a second power setting data set is also plotted in series 56 and a third power setting data set is plotted in series 58.
- the one exemplary look-up table 18 provides recommended energization time periods for forming a 1 cm long lesion, as described below, to the desired lesion depth at a 95% confidence level.
- a surgeon who has a desired lesion depth and selected power setting can refer to the table 18 and ascertain a correspondingly, recommended energization time and know that the recommended time has proven to achieve the desired results (i.e., desired results (i.e., desired lesion depth) with a 95% confidence level.
- the look-up table 18 is adapted to provide energization time period information that has a 95% confidence bound on an upper limit of lesion depth.
- the one preferred look-up table 18 provided in FIG. 3 incorporates this upper bound, such that a recommended energization time period delivered from the table 18 will not result in too deep a lesion.
- the table 18 can be adapted to correspond to longer or shorter lesion lengths.
- a plurality of different look-up tables 18 are preferably provided, with each corresponding to a different irrigation rate and/or for different types of tissue, such as heart tissue, liver tissue, prostate tissue, etc.
- a first look-up table can be provided that embodies a correlation of lesion depth values with power setting values, along with a second (or third, etc.) look-up table that correlates lesion depth values with power setting values for a second irrigation rate.
- the look-up table 18 may incorporate the variables in other organizational methods (e.g., lesion depth versus power setting; a tabular representation of individual lesion depth, power setting, and time period values, etc.) and/or or need not reflect a particular irrigation rate, and remain within the scope of the present invention.
- other organizational methods e.g., lesion depth versus power setting; a tabular representation of individual lesion depth, power setting, and time period values, etc.
- the look-up table 18 is provided apart from the electrosurgical instrument 12, such as in hard paper form.
- a computer or similar device can be employed to display the desired look-up table 18.
- the electrosurgical system 10 further includes a controller 60.
- the controller 60 is preferably electrically connected to the fluid source 14 by a line or wire 62 and to the power source 16 by a line or wire 64, and is preferably a microprocessor-based computer including associated memory and input/output circuiting.
- a programmable logic controller (PLC) or other controller or equivalent circuitry can be employed. Regardless, the controller 60 stores the look-up table 18 and the corresponding data sets.
- PLC programmable logic controller
- the controller 60 is adapted to convert two, or preferably three variables (i.e., lesion depth, power setting, and/or irrigation rate) inputted by a user (e.g., via a keyboard) into a recommended energization time period value by referencing the internal look-up table 18.
- the controller 60 is further preferably adapted to adjust the irrigation rate of the fluid source 14 and the power setting of the power source 16 as needed or dictated by a user, and control activation/de-activation of the power source 16 in accordance with the determined recommended energization time period.
- the flow diagram of FIG. 4 illustrates one preferred method of forming a lesion on living tissue in accordance with the present invention.
- the above- described electrosurgical system 10, including the electrosurgical instrument 12 is useful for a number of different tissue ablation and cauterization procedures.
- the system 10 can be used to remove hemorrhoids or varicose veins, or stop esophageal bleeding to name but few possible uses.
- the system 10 is highly useful for the surgical treatment of cardiac arrhythmia, and in particular treatment of atrial fibrillation, via ablation of atrial tissue.
- the methodology of FIG. 4 is described in conjunction with an ablation (or lesion forming) procedure performed on atrial tissue as shown in FIG. 5, it being understood that the technique is equally applicable to a variety of other electrosurgical procedures. Prior to performing the electrosurgical procedure, it is assumed that the surgeon has evaluated the patient and determined that the specific procedure to be appropriate for the individual patient.
- FIG. 5A includes a representation of a heart 70 with its left atrium 72 exposed.
- step 100 of FIG. 4 delineates that access to a target site 74 is gained.
- the target site 74 is accessed by splitting the patient's sternum (not shown) and opening the patient's rib cage (not shown) with a retractor.
- Various incision are then made into the heart 70 to expose an interior of the left atrium 72.
- other techniques are available for accessing the target site 74.
- access to a particular target site 74 could be gained, for example, via a thoractomy, sternotomy, percutaneously, • transveneously, arthroscopically, endoscopically, for example through a percutaneous port, stab wound or puncture through a small incision (e.g., in the chest, groin, abdomen, neck, or knee), etc.
- a catheter device may be passed from an interior of the heart 70, through an appendage wall of the heart 70, to an exterior of the heart 70.
- the electrosurgical instrument 12 may then be manipulated to contact an epicardial surface of the heart 70.
- the electrosurgical system 10 is provided. As previously described, the system 10 includes the electrosurgical instrument 12, the power source 16, the fluid source 14, and the look-up table 18. In one preferred embodiment, the system 10 also includes the controller 60.
- a desired lesion depth is determined. To determine the desired lesion depth, the target tissue site 74, such as a portion of an atrial wall 75 of the heart 70 as illustrated in FIG. 5A, is identified and evaluated to determine its thickness. The desired lesion depth is then determined based upon the determined thickness, as the thickness is proportionate to the desired lesion depth. The actual proportion utilized, however, depends upon the requirements of the particular electrosurgical procedure being performed.
- a transmural lesion is required, and consequently, the desired lesion depth will be equal to the thickness of the target site tissue 74.
- other electrosurgical procedures may entail a desired lesion depth that is less than the evaluated thickness of the target site 74, for example, by a prescribed percentage (e.g., 50% of the target site 74 thickness).
- a desired power setting for the power source 16 is selected.
- the power setting mandates how much heat is created within the target tissue site 74 during a subsequent electrosurgical procedure.
- certain recommended protocols have been developed, and are available to the surgeon. These protocols provide guidelines or accepted ranges for certain procedure parameters, including power setting.
- the surgeon will initially refer to recommended power settings. Then, with this prescribed range in mind, to determine the specific power setting for a particular electrosurgical procedure, the risks associated with a probable energization time and a probability of "pops" are considered.
- a shorter ablation time generally corresponds with a lower risk of complications, since lesions can be closed sooner, and consequently, the body can be returned to a relatively natural state in a shorter period of time thereby reducing the chance of infection, thromboembohsm, or other complications. Therefore, since a higher power setting creates the lesion in a shorter period of time, a higher power setting within the recommended range for a particular procedure is preferred in consideration of energization time.
- a pop occurs when the target site tissue 74 is heated so rapidly that intracellular fluid within the target site tissue 74 begins to boil and the target site tissue 74 erupts causing damage to the tissue.
- larger pops can require suturing and may thereby damage the tissue strength and prolong the length of the electrosurgical procedure.
- a goal of the electrosurgical procedure is to minimize, or at least decrease, the occurrence of pops. Since the higher power setting increases the probability of pops, a lower power setting is desired in consideration of the probability of pops.
- a surgeon considers the probable energization time and the probability of pops to determine the power setting that will minimize the combined risks involved in the electrosurgical procedure.
- a desired irrigation rate of the fluid source 16 is selected.
- the irrigation rate affects the amount and rate of heat generated in the target tissue site 74. If the irrigation rate is too low, the tissue will heat too quickly increasing the probability of pops and/or causing dry ablation/electrocauterization that may result in the build-up of excess charred tissue on the electrode tip 34 of the electrosurgical instrument 12, decreasing the overall performance of the electrosurgical system 10. For example, tissue char will raise the impedance of the tissue, thereby preventing the creation of a deep lesion.
- the decreased level of performance requires the tip 34 to be cleaned on a piece of sterile gauze or the like and, consequently, increases the chance of incision contamination.
- the irrigation rate is set too high, it will overcool the target tissue site 74 increasing the time needed to create a lesion and slow the electrosurgical procedure.
- ablation of atrial tissue typically entails an irrigation rate of 3 to 10 cc/minute, more preferably an irrigation rate of 5 ccs per minute.
- other procedures can have varying irrigation rate guidelines.
- step 108 is illustrated in FIG. 4 as following step 106, steps 106 and 108 may be performed in the opposite sequence or relatively simultaneously.
- the predetermined length of time information embodied in the look-up table 18 is referenced to determine a recommended energization time period.
- a surgeon or assistant chooses the look-up table 18 that corresponds with the desired irrigation rate selected at step 108.
- the desired lesion depth, determined at step 104, and the selected power setting, determined at step 106 are then applied to the look-up table 18 to determine the corresponding recommended energization time period needed to create an appropriate lesion 76 (referenced generally in FIG. 5A) in the target site tissue 74.
- the desired lesion depth is 4 mm
- the selected power setting is 25 watts
- the selected irrigation rate is 5 cc/minute.
- reference to the look-up table 18 illustrated in FIG. 3 provides a recommended energization time period of 20.7 seconds.
- the energization time information corresponds with a lesion length of 1 cm.
- the look-up table 18 can be adapted to provide energization time period information corresponding with other lesion lengths. Additionally or alternatively, a surgeon can extrapolate the recommended energization time period information for a 1 cm lesion length to arrive at an appropriate energization time period for the particular procedure/lesion being performed.
- the surgeon determines whether or not the combined risks are acceptable.
- the surgeon compares the selected power setting and irrigation rate previously determined at steps 106 and 108, respectively, to the recommended energization time period determined at step 110 to ensure all values interact in a manner that produces an acceptable combined risk of complication. If the recommended energization time period is not acceptable based upon consideration of the selected power setting and the resultant procedure time, the surgeon repeats steps 106 through 112 until the combined risks are acceptable. Once the combined risks are acceptable, the surgeon continues to step 114.
- step 114 fluid flow from the fluid source 14 is initiated and the power source
- the electrosurgical instrument 12 (in particular the electrode tip 34) is applied to the target tissue site 74 to create the lesion 76, as best shown in FIG. 5B.
- liquid flow from the fluid source 14 is initiated for a short time period prior to activation of the power source 16 to ensure that liquid is being distributed to the target site 74 before energy is applied.
- the electrode tip 34 is then evenly drawn (preferably in a back-and-forth motion) across the target tissue site 74 over the length corresponding to the recommended energization time period (e.g., 1 cm), determined at step 110, to create the lesion 76 with the desired lesion depth.
- the electrosurgical device 12 may be manipulated by a surgeon and/or by a robot.
- the electrosurgical instrument 12 with the selected power setting at 25 watts and the selected irrigation rate at 5 cc/minute is evenly drawn across a 1 cm length of tissue for 20.7 seconds to create the lesion 76 having the lesion depth of 4 mm.
- Step 114 may be repeated from an end of the newly formed lesion 76 to form a second lesion (preferably having a length corresponding with a length of the first lesion 76) until a number of lesions have been created to form a desired pattern 78 for the particular electrosurgical procedure being performed.
- Each lesion, segment is preferably formed at the same selected power setting and recommended irrigation rate, utilizing the recommended energization time period.
- the lesion pattern 78 is formed on a left atrial wall 72 of the heart 70 and encircles two right pulmonary veins 80 as a step in a Maze procedure.
- the procedure described above does not incorporate the optional controller 60 (FIG. 1). If the electrosurgical system 10 includes the controller 60, steps 106 through 112 can be completed by or with the assistance of the controller 60.
- the controller 60 can be adapted to provide varying levels of control over the electrosurgical instrument 12, the fluid source 14, and/or the power source 16.
- the controller 60 may display the applicable look-up table 18, with the surgeon having complete, independent control over the components 12 - 16.
- the controller 60 may be adapted to automatically initiate and/or control fluid flow from the fluid source 14 at the selected irrigation rate. Further, the controller 60 may be adapted to automatically deactivate the power source 16 at the completion of the energization time.
- the controller 60 may be adapted to provide an audible and/or visible signal or warning (e.g., flashing lights, buzzer, etc.) during the procedure, or at or near the expiration of the recommended energization time period.
- the controller 60 may be adapted to operate a sound-producing device in a manner that provides an audible signal in pre-determined increments (e.g., once per second) while power is on, thereby acting like a metronome to aid in timing the preferred back-and-forth motion of the electrosurgical instrument 12, and in particular the tip 34.
- the electrosurgical procedure is highly useful for the surgical treatment of atrial fibrillation, via ablation of atrial tissue, for example as part of the Maze procedure.
- the Maze procedure such as described in Cardiovascular Digest Update, Vol. 1, No. 4, July 1995, pp. 2-3, the teachings of which are incorporated herein by reference, is a well-known technique whereby lesion patterns are created along specified areas of the atria.
- the Maze III procedure a modified version of the original Maze procedure, has been described in Cardiac Surgery Operative Technique, Mosby Inc., 1997, pp. 410-419, the teachings of which are incorporated by referenced.
- the system and method of the present invention may be employed to form one or all of the lesions/lesion patterns required by the above-identified surgical procedures.
- the look-up table 18 may be referenced, and the recommended energization time period employed to form lesions on the tricuspid annulus in the right atrium, the coronary sinus, the mitral valve annulus in the left atrium, etc.
- the electrosurgical system and method of the present invention provides a marked improvement over previous protocols.
- a surgeon can determine a recommended energization time period prior to applying the electrosurgical instrument to the target tissue site.
- Knowledge of the energization time period decreases the requirement of constant measurement and testing during the electrosurgical procedure and, consequently, reduces the time required to create the lesion having the desired properties. Reduction of the surgical time reduces the risk of complication, accordingly.
Abstract
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DE60319341T DE60319341T2 (en) | 2002-01-25 | 2003-01-14 | DEVICE AND METHOD FOR CARRYING OUT AN ELECTRO-SURGERY PROCESS |
EP03702108A EP1467670B1 (en) | 2002-01-25 | 2003-01-14 | System and method of performing an electrosurgical procedure |
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US10/056,806 US6827715B2 (en) | 2002-01-25 | 2002-01-25 | System and method of performing an electrosurgical procedure |
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EP (1) | EP1467670B1 (en) |
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Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN102473996A (en) * | 2009-07-20 | 2012-05-23 | 克里奥医药有限公司 | Surgical antenna and electrosurgical system using the same |
Families Citing this family (193)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
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 |
US5897553A (en) | 1995-11-02 | 1999-04-27 | Medtronic, Inc. | Ball point fluid-assisted electrocautery device |
US7115123B2 (en) * | 1996-01-05 | 2006-10-03 | Thermage, Inc. | Handpiece with electrode and non-volatile memory |
US6033399A (en) * | 1997-04-09 | 2000-03-07 | Valleylab, Inc. | Electrosurgical generator with adaptive power control |
US6096037A (en) | 1997-07-29 | 2000-08-01 | Medtronic, Inc. | Tissue sealing electrosurgery device and methods of sealing tissue |
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 |
US6537248B2 (en) | 1998-07-07 | 2003-03-25 | Medtronic, Inc. | Helical needle apparatus for creating a virtual electrode used for the ablation of tissue |
US7364577B2 (en) | 2002-02-11 | 2008-04-29 | Sherwood Services Ag | Vessel sealing system |
US7901400B2 (en) | 1998-10-23 | 2011-03-08 | Covidien Ag | Method and system for controlling output of RF medical generator |
US7137980B2 (en) | 1998-10-23 | 2006-11-21 | Sherwood Services Ag | Method and system for controlling output of RF medical generator |
US8241274B2 (en) | 2000-01-19 | 2012-08-14 | 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 |
US8221402B2 (en) | 2000-01-19 | 2012-07-17 | Medtronic, Inc. | Method for guiding a medical device |
US8048070B2 (en) | 2000-03-06 | 2011-11-01 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices, systems and methods |
EP1278471B1 (en) | 2000-04-27 | 2005-06-15 | Medtronic, Inc. | Vibration sensitive ablation apparatus |
US6514250B1 (en) | 2000-04-27 | 2003-02-04 | Medtronic, Inc. | Suction stabilized epicardial ablation devices |
US6926669B1 (en) | 2000-10-10 | 2005-08-09 | Medtronic, Inc. | Heart wall ablation/mapping catheter and method |
US7740623B2 (en) | 2001-01-13 | 2010-06-22 | Medtronic, Inc. | Devices and methods for interstitial injection of biologic agents into tissue |
US20040138621A1 (en) | 2003-01-14 | 2004-07-15 | Jahns Scott E. | Devices and methods for interstitial injection of biologic agents into tissue |
US6807968B2 (en) | 2001-04-26 | 2004-10-26 | Medtronic, Inc. | Method and system for treatment of atrial tachyarrhythmias |
US7959626B2 (en) | 2001-04-26 | 2011-06-14 | Medtronic, Inc. | Transmural ablation systems and methods |
US6699240B2 (en) | 2001-04-26 | 2004-03-02 | Medtronic, Inc. | Method and apparatus for tissue ablation |
US6663627B2 (en) | 2001-04-26 | 2003-12-16 | Medtronic, Inc. | Ablation system and method of use |
WO2002094363A2 (en) | 2001-05-21 | 2002-11-28 | Medtronic,Inc. | Trans-septal catheter with retention mechanism |
US7077842B1 (en) * | 2001-08-03 | 2006-07-18 | Cosman Jr Eric R | Over-the-wire high frequency electrode |
EP2275050A1 (en) | 2001-09-05 | 2011-01-19 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices, systems and methods |
US7967816B2 (en) * | 2002-01-25 | 2011-06-28 | Medtronic, Inc. | Fluid-assisted electrosurgical instrument with shapeable electrode |
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 |
US7294143B2 (en) | 2002-05-16 | 2007-11-13 | Medtronic, Inc. | Device and method for ablation of cardiac tissue |
US7258690B2 (en) | 2003-03-28 | 2007-08-21 | Relievant Medsystems, Inc. | Windowed thermal ablation probe |
US6907884B2 (en) | 2002-09-30 | 2005-06-21 | Depay Acromed, Inc. | Method of straddling an intraosseous nerve |
US8361067B2 (en) | 2002-09-30 | 2013-01-29 | Relievant Medsystems, Inc. | Methods of therapeutically heating a vertebral body to treat back pain |
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 |
US7497857B2 (en) | 2003-04-29 | 2009-03-03 | Medtronic, Inc. | Endocardial dispersive electrode for use with a monopolar RF ablation pen |
US8012150B2 (en) | 2003-05-01 | 2011-09-06 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
US7258689B2 (en) * | 2003-05-19 | 2007-08-21 | Matteo Tutino | Silver alloys for use in medical, surgical and microsurgical instruments and process for producing the alloys |
EP1676108B1 (en) | 2003-10-23 | 2017-05-24 | Covidien AG | Thermocouple measurement circuit |
US7396336B2 (en) | 2003-10-30 | 2008-07-08 | Sherwood Services Ag | Switched resonant ultrasonic power amplifier system |
US7131860B2 (en) | 2003-11-20 | 2006-11-07 | Sherwood Services Ag | Connector systems for electrosurgical generator |
US8333764B2 (en) | 2004-05-12 | 2012-12-18 | Medtronic, Inc. | Device and method for determining tissue thickness and creating cardiac ablation lesions |
AU2005244868A1 (en) | 2004-05-14 | 2005-12-01 | Medtronic, Inc. | Method and devices for treating atrial fibrillation by mass ablation |
DE602005021096D1 (en) | 2004-06-02 | 2010-06-17 | Medtronic Inc | COMPOUND BIPOLAR ABLATION DEVICE |
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 |
WO2005120375A2 (en) | 2004-06-02 | 2005-12-22 | Medtronic, Inc. | Loop ablation apparatus and method |
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 |
CA2577986A1 (en) * | 2004-09-01 | 2006-03-09 | Jms Co., Ltd. | Varix treatment system |
US7282049B2 (en) * | 2004-10-08 | 2007-10-16 | Sherwood Services Ag | Electrosurgical system employing multiple electrodes and method thereof |
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 |
US7628786B2 (en) | 2004-10-13 | 2009-12-08 | Covidien Ag | Universal foot switch contact port |
US7862563B1 (en) | 2005-02-18 | 2011-01-04 | Cosman Eric R | Integral high frequency electrode |
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 |
US8696662B2 (en) | 2005-05-12 | 2014-04-15 | Aesculap Ag | Electrocautery method and apparatus |
US7862565B2 (en) | 2005-05-12 | 2011-01-04 | Aragon Surgical, Inc. | Method for tissue cauterization |
US9339323B2 (en) | 2005-05-12 | 2016-05-17 | Aesculap Ag | Electrocautery method and apparatus |
US7803156B2 (en) * | 2006-03-08 | 2010-09-28 | Aragon Surgical, Inc. | Method and apparatus for surgical electrocautery |
US8728072B2 (en) * | 2005-05-12 | 2014-05-20 | Aesculap Ag | Electrocautery method and apparatus |
US20070066971A1 (en) * | 2005-09-21 | 2007-03-22 | Podhajsky Ronald J | Method and system for treating pain during an electrosurgical procedure |
US7879031B2 (en) * | 2005-09-27 | 2011-02-01 | Covidien Ag | Cooled RF ablation needle |
US8550743B2 (en) * | 2005-09-30 | 2013-10-08 | Medtronic, Inc. | Sliding lock device |
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 |
US7947039B2 (en) | 2005-12-12 | 2011-05-24 | Covidien Ag | Laparoscopic apparatus for performing electrosurgical procedures |
US7513896B2 (en) | 2006-01-24 | 2009-04-07 | Covidien Ag | Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling |
US8685016B2 (en) | 2006-01-24 | 2014-04-01 | 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 |
US9186200B2 (en) | 2006-01-24 | 2015-11-17 | 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 |
US8216223B2 (en) | 2006-01-24 | 2012-07-10 | Covidien Ag | System and method for tissue sealing |
EP1810634B8 (en) | 2006-01-24 | 2015-06-10 | Covidien AG | System for tissue sealing |
US10098618B2 (en) * | 2006-01-27 | 2018-10-16 | Medtronic, Inc. | Method of surgical dissection and/or guidance of other medical devices into body |
US20070203483A1 (en) * | 2006-01-27 | 2007-08-30 | David Kim | Ablation device with lockout feature |
US7976542B1 (en) * | 2006-03-02 | 2011-07-12 | Cosman Eric R | Adjustable high frequency electrode |
US7651493B2 (en) | 2006-03-03 | 2010-01-26 | Covidien Ag | System and method for controlling electrosurgical snares |
US7651492B2 (en) | 2006-04-24 | 2010-01-26 | Covidien Ag | Arc based adaptive control system for an electrosurgical unit |
US8574229B2 (en) | 2006-05-02 | 2013-11-05 | Aesculap Ag | Surgical tool |
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 |
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 |
EP2218479A3 (en) | 2006-06-28 | 2013-06-05 | Medtronic Ardian Luxembourg S.à.r.l. | Methods and systems for thermally-induced renal neuromodulation |
US7763018B2 (en) * | 2006-07-28 | 2010-07-27 | Covidien Ag | Cool-tip thermocouple including two-piece hub |
US7794457B2 (en) | 2006-09-28 | 2010-09-14 | Covidien Ag | Transformer for RF voltage sensing |
US8048069B2 (en) * | 2006-09-29 | 2011-11-01 | Medtronic, Inc. | User interface for ablation therapy |
US8211099B2 (en) | 2007-01-31 | 2012-07-03 | Tyco Healthcare Group Lp | Thermal feedback systems and methods of using the same |
US10166066B2 (en) | 2007-03-13 | 2019-01-01 | University Of Virginia Patent Foundation | Epicardial ablation catheter and method of use |
US11058354B2 (en) | 2007-03-19 | 2021-07-13 | University Of Virginia Patent Foundation | Access needle with direct visualization and related methods |
US9468396B2 (en) | 2007-03-19 | 2016-10-18 | University Of Virginia Patent Foundation | Systems and methods for determining location of an access needle in a subject |
WO2008115745A2 (en) | 2007-03-19 | 2008-09-25 | University Of Virginia Patent Foundation | Access needle pressure sensor device and method of use |
US9211405B2 (en) | 2007-03-22 | 2015-12-15 | University Of Virginia Patent Foundation | Electrode catheter for ablation purposes and related method thereof |
US8777941B2 (en) | 2007-05-10 | 2014-07-15 | Covidien Lp | Adjustable impedance electrosurgical electrodes |
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 |
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 |
US20100241185A1 (en) | 2007-11-09 | 2010-09-23 | University Of Virginia Patent Foundation | Steerable epicardial pacing catheter system placed via the subxiphoid process |
EP2197377B1 (en) * | 2007-11-16 | 2017-11-01 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Device for real-time lesion estimation during ablation |
US8292880B2 (en) | 2007-11-27 | 2012-10-23 | Vivant Medical, Inc. | Targeted cooling of deployable microwave antenna |
US8106829B2 (en) * | 2007-12-12 | 2012-01-31 | Broadcom Corporation | Method and system for an integrated antenna and antenna management |
JP5443386B2 (en) | 2007-12-28 | 2014-03-19 | サリエント・サージカル・テクノロジーズ・インコーポレーテッド | Fluid-assisted electrosurgical device, method and system |
US8870867B2 (en) | 2008-02-06 | 2014-10-28 | Aesculap Ag | Articulable electrosurgical instrument with a stabilizable articulation actuator |
EP2881050B1 (en) | 2008-03-31 | 2023-02-22 | Applied Medical Resources Corporation | Electrosurgical system with means for determining the end of a treatment based on a phase angle |
EP2303171A2 (en) | 2008-05-13 | 2011-04-06 | 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 |
US8608739B2 (en) * | 2008-07-22 | 2013-12-17 | Covidien Lp | Electrosurgical devices, systems and methods of using the same |
EP3406210A1 (en) | 2008-09-26 | 2018-11-28 | Relievant Medsystems, Inc. | Systems and for navigating an instrument through bone |
US10028753B2 (en) | 2008-09-26 | 2018-07-24 | Relievant Medsystems, Inc. | Spine treatment kits |
US10695126B2 (en) | 2008-10-06 | 2020-06-30 | Santa Anna Tech Llc | Catheter with a double balloon structure to generate and apply a heated ablative zone to tissue |
US9629678B2 (en) * | 2008-12-30 | 2017-04-25 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Controlled irrigated catheter ablation systems and methods thereof |
US8262652B2 (en) | 2009-01-12 | 2012-09-11 | Tyco Healthcare Group Lp | Imaginary impedance process monitoring and intelligent shut-off |
WO2010082146A1 (en) * | 2009-01-14 | 2010-07-22 | Koninklijke Philips Electronics N.V. | Monitoring apparatus for monitoring an ablation procedure |
US9254168B2 (en) | 2009-02-02 | 2016-02-09 | Medtronic Advanced Energy Llc | Electro-thermotherapy of tissue using penetrating microelectrode array |
US8632533B2 (en) | 2009-02-23 | 2014-01-21 | Medtronic Advanced Energy Llc | Fluid-assisted electrosurgical device |
US20100256735A1 (en) * | 2009-04-03 | 2010-10-07 | Board Of Regents, The University Of Texas System | Intraluminal stent with seam |
US20100280508A1 (en) * | 2009-05-01 | 2010-11-04 | Joseph Charles Eder | Method and Apparatus for RF Anastomosis |
US9345541B2 (en) | 2009-09-08 | 2016-05-24 | Medtronic Advanced Energy Llc | Cartridge assembly for electrosurgical devices, electrosurgical unit and methods of use thereof |
US9642534B2 (en) | 2009-09-11 | 2017-05-09 | University Of Virginia Patent Foundation | Systems and methods for determining location of an access needle in a subject |
WO2011097469A2 (en) | 2010-02-04 | 2011-08-11 | Aragon Surgical, Inc. | Laparoscopic radiofrequency surgical device |
EP2537149B1 (en) | 2010-02-18 | 2017-10-25 | University Of Virginia Patent Foundation | System, method, and computer program product for simulating epicardial electrophysiology procedures |
US9592090B2 (en) | 2010-03-11 | 2017-03-14 | Medtronic Advanced Energy Llc | Bipolar electrosurgical cutter with position insensitive return electrode contact |
US8827992B2 (en) | 2010-03-26 | 2014-09-09 | Aesculap Ag | Impedance mediated control of power delivery for electrosurgery |
US8419727B2 (en) | 2010-03-26 | 2013-04-16 | Aesculap Ag | Impedance mediated power delivery for electrosurgery |
US20110238058A1 (en) * | 2010-03-29 | 2011-09-29 | Estech, Inc. (Endoscopic Technologies, Inc.) | Indifferent electrode pad systems and methods for tissue ablation |
US9179968B2 (en) | 2010-05-10 | 2015-11-10 | St. Jude Medical Luxembourg Holding S.À.R.L. | Irrigated finned ablation head |
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 |
US8840609B2 (en) | 2010-07-23 | 2014-09-23 | Conmed Corporation | Tissue fusion system and method of performing a functional verification test |
US9173698B2 (en) | 2010-09-17 | 2015-11-03 | Aesculap Ag | Electrosurgical tissue sealing augmented with a seal-enhancing composition |
ES2912092T3 (en) | 2010-10-01 | 2022-05-24 | Applied Med Resources | Electrosurgical instruments and connections thereto |
TWI513451B (en) | 2010-10-25 | 2015-12-21 | Medtronic Ardian Luxembourg | 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 |
US9427281B2 (en) | 2011-03-11 | 2016-08-30 | Medtronic Advanced Energy Llc | Bronchoscope-compatible catheter provided with electrosurgical device |
CN102106755A (en) * | 2011-03-15 | 2011-06-29 | 李刚 | Minimally invasive endoscopic electrode |
US9339327B2 (en) | 2011-06-28 | 2016-05-17 | Aesculap Ag | Electrosurgical tissue dissecting device |
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 |
US9131980B2 (en) | 2011-12-19 | 2015-09-15 | Medtronic Advanced Energy Llc | Electrosurgical devices |
US10390877B2 (en) | 2011-12-30 | 2019-08-27 | Relievant Medsystems, Inc. | Systems and methods for treating back pain |
US20130204243A1 (en) * | 2012-02-02 | 2013-08-08 | John Jordan Newkirk | Handheld electrosurgical generator |
US9226792B2 (en) | 2012-06-12 | 2016-01-05 | Medtronic Advanced Energy Llc | Debridement device and method |
US10588691B2 (en) | 2012-09-12 | 2020-03-17 | Relievant Medsystems, Inc. | Radiofrequency ablation of tissue within a vertebral body |
KR102174907B1 (en) | 2012-09-26 | 2020-11-05 | 아에스쿨랍 아게 | Apparatus for tissue cutting and sealing |
US11234760B2 (en) | 2012-10-05 | 2022-02-01 | Medtronic Advanced Energy Llc | Electrosurgical device for cutting and removing tissue |
WO2014071161A1 (en) | 2012-11-05 | 2014-05-08 | Relievant Medsystems, Inc. | System and methods for creating curved paths through bone and modulating nerves within the bone |
US9204921B2 (en) | 2012-12-13 | 2015-12-08 | Cook Medical Technologies Llc | RF energy controller and method for electrosurgical medical devices |
US9364277B2 (en) | 2012-12-13 | 2016-06-14 | Cook Medical Technologies Llc | RF energy controller and method for electrosurgical medical devices |
US9489785B2 (en) | 2013-03-14 | 2016-11-08 | Covidien Lp | RFID secure authentication |
US9775665B2 (en) | 2013-03-15 | 2017-10-03 | Alan G Ellman | Fixed position RF electrode |
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 |
US9724151B2 (en) | 2013-08-08 | 2017-08-08 | Relievant Medsystems, Inc. | Modulating nerves within bone using bone fasteners |
US10631914B2 (en) | 2013-09-30 | 2020-04-28 | Covidien Lp | Bipolar electrosurgical instrument with movable electrode and related systems and methods |
US10433902B2 (en) | 2013-10-23 | 2019-10-08 | Medtronic Ardian Luxembourg S.A.R.L. | Current control methods and systems |
WO2015073397A1 (en) | 2013-11-13 | 2015-05-21 | Thixos Llc | Devices, kits and methods relating to treatment of facet joints |
US10314647B2 (en) | 2013-12-23 | 2019-06-11 | Medtronic Advanced Energy Llc | Electrosurgical cutting instrument |
US10813686B2 (en) | 2014-02-26 | 2020-10-27 | Medtronic Advanced Energy Llc | Electrosurgical cutting instrument |
US10130382B2 (en) | 2014-03-27 | 2018-11-20 | Medtronic Xomed, Inc. | Powered surgical handpiece having a surgical tool with an RFID tag |
US10610292B2 (en) | 2014-04-25 | 2020-04-07 | Medtronic Ardian Luxembourg S.A.R.L. | Devices, systems, and methods for monitoring and/or controlling deployment of a neuromodulation element within a body lumen and related technology |
KR20230076143A (en) | 2014-05-16 | 2023-05-31 | 어플라이드 메디컬 리소시스 코포레이션 | Electrosurgical system |
EP3148465B1 (en) | 2014-05-30 | 2018-05-16 | Applied Medical Resources Corporation | Electrosurgical system with an instrument comprising a jaw with a central insulative pad |
US9974599B2 (en) | 2014-08-15 | 2018-05-22 | Medtronic Ps Medical, Inc. | Multipurpose electrosurgical device |
US9956029B2 (en) | 2014-10-31 | 2018-05-01 | Medtronic Advanced Energy Llc | Telescoping device with saline irrigation line |
CA2967824A1 (en) | 2014-11-19 | 2016-05-26 | Advanced Cardiac Therapeutics, Inc. | Ablation devices, systems and methods of using a high-resolution electrode assembly |
WO2016081611A1 (en) | 2014-11-19 | 2016-05-26 | Advanced Cardiac Therapeutics, Inc. | High-resolution mapping of tissue with pacing |
KR20230093365A (en) | 2014-12-23 | 2023-06-27 | 어플라이드 메디컬 리소시스 코포레이션 | Bipolar electrosurgical sealer and divider |
USD748259S1 (en) | 2014-12-29 | 2016-01-26 | Applied Medical Resources Corporation | Electrosurgical instrument |
US10376302B2 (en) | 2015-02-18 | 2019-08-13 | Medtronic Xomed, Inc. | Rotating electrical connector for RF energy enabled tissue debridement device |
US10188456B2 (en) | 2015-02-18 | 2019-01-29 | Medtronic Xomed, Inc. | Electrode assembly for RF energy enabled tissue debridement device |
AU2016219980B2 (en) | 2015-02-18 | 2020-09-03 | Medtronic Xomed, Inc. | RF energy enabled tissue debridement device |
US9636164B2 (en) | 2015-03-25 | 2017-05-02 | Advanced Cardiac Therapeutics, Inc. | Contact sensing systems and methods |
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 |
US10716612B2 (en) | 2015-12-18 | 2020-07-21 | Medtronic Advanced Energy Llc | Electrosurgical device with multiple monopolar electrode assembly |
WO2017160808A1 (en) | 2016-03-15 | 2017-09-21 | Advanced Cardiac Therapeutics, Inc. | Improved devices, systems and methods for irrigated ablation |
US11331140B2 (en) | 2016-05-19 | 2022-05-17 | Aqua Heart, Inc. | Heated vapor ablation systems and methods for treating cardiac conditions |
US11497507B2 (en) | 2017-02-19 | 2022-11-15 | Orpheus Ventures, Llc | Systems and methods for closing portions of body tissue |
US11197709B2 (en) * | 2017-03-13 | 2021-12-14 | Medtronic Advanced Energy Llc | Electrosurgical system |
CN110809448B (en) | 2017-04-27 | 2022-11-25 | Epix疗法公司 | Determining properties of contact between catheter tip and tissue |
US10194975B1 (en) | 2017-07-11 | 2019-02-05 | Medtronic Advanced Energy, Llc | Illuminated and isolated electrosurgical apparatus |
US11259860B2 (en) | 2017-09-25 | 2022-03-01 | Covidien Lp | Systems and methods for providing sensory feedback with an ablation system |
US11864812B2 (en) | 2018-09-05 | 2024-01-09 | Applied Medical Resources Corporation | Electrosurgical generator control system |
CA3120182A1 (en) | 2018-11-16 | 2020-05-22 | Applied Medical Resources Corporation | Electrosurgical system |
US11779391B2 (en) * | 2019-02-28 | 2023-10-10 | Biosense Webster (Israel) Ltd. | Forming a lesion based on pre-determined amount of abaltive energy vs lesion size curve |
WO2021050767A1 (en) | 2019-09-12 | 2021-03-18 | Relievant Medsystems, Inc. | Systems and methods for tissue modulation |
US20210290301A1 (en) * | 2020-03-19 | 2021-09-23 | Biosense Webster (Israel) Ltd. | Measuring thickness of cardiac wall tissue during ablation |
Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1996034567A1 (en) * | 1995-05-02 | 1996-11-07 | Heart Rhythm Technologies, Inc. | System for controlling the energy delivered to a patient for ablation |
US5897553A (en) | 1995-11-02 | 1999-04-27 | Medtronic, Inc. | Ball point fluid-assisted electrocautery device |
US5925038A (en) * | 1996-01-19 | 1999-07-20 | Ep Technologies, Inc. | Expandable-collapsible electrode structures for capacitive coupling to tissue |
US6113592A (en) * | 1995-06-09 | 2000-09-05 | Engineering & Research Associates, Inc. | Apparatus and method for controlling ablation depth |
US6175768B1 (en) * | 1996-04-17 | 2001-01-16 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | In vivo simulator for microwave treatment |
US6217573B1 (en) * | 1998-12-03 | 2001-04-17 | Cordis Webster | System and method for measuring surface temperature of tissue during ablation |
WO2001068173A2 (en) * | 2000-03-15 | 2001-09-20 | Boston Scientific Limited | Ablation and imaging catheter |
WO2001080757A2 (en) * | 2000-04-27 | 2001-11-01 | Medtronic, Inc. | Vibration sensitive ablation device and method |
Family Cites Families (183)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1735271A (en) * | 1928-03-14 | 1929-11-12 | Sutten H Groff | Diathermy knife |
US3823575A (en) | 1971-06-07 | 1974-07-16 | Univ Melbourne | Cryogenic apparatus |
US3736936A (en) | 1971-12-13 | 1973-06-05 | Hughes Aircraft Co | Cryogenic heat transfer device |
GB1438759A (en) | 1972-06-02 | 1976-06-09 | Spembly Ltd | Cryo-surgical apparatus |
US3807403A (en) | 1972-06-14 | 1974-04-30 | Frigitronics Of Conn Inc | Cryosurgical apparatus |
US3886945A (en) | 1972-06-14 | 1975-06-03 | Frigitronics Of Conn Inc | Cryosurgical apparatus |
US3830239A (en) | 1972-09-12 | 1974-08-20 | Frigitronics Of Conn Inc | Cryosurgical device |
US3823718A (en) | 1972-09-15 | 1974-07-16 | T Tromovitch | Portable cryosurgical apparatus |
US3827436A (en) | 1972-11-10 | 1974-08-06 | Frigitronics Of Conn Inc | Multipurpose cryosurgical probe |
US3924628A (en) | 1972-12-01 | 1975-12-09 | William Droegemueller | Cyrogenic bladder for necrosing tissue cells |
NL176833C (en) | 1973-04-26 | 1985-06-17 | Draegerwerk Ag | HEAT-INSULATING FLEXIBLE PIPE. |
US3859986A (en) | 1973-06-20 | 1975-01-14 | Jiro Okada | Surgical device |
US3907339A (en) | 1973-07-23 | 1975-09-23 | Frigitronics Of Conn Inc | Cryogenic delivery line |
US3862627A (en) | 1973-08-16 | 1975-01-28 | Sr Wendel J Hans | Suction electrode |
US4022215A (en) | 1973-12-10 | 1977-05-10 | Benson Jerrel W | Cryosurgical system |
GB1513565A (en) | 1975-04-22 | 1978-06-07 | Spembly Ltd | Cryosurgical instruments |
US4018227A (en) | 1975-10-09 | 1977-04-19 | Cryomedics, Inc. | Cryosurgical instrument |
US4072152A (en) | 1976-02-23 | 1978-02-07 | Linehan John H | Orthopedic cryosurgical apparatus |
GB1534162A (en) | 1976-07-21 | 1978-11-29 | Lloyd J | Cyosurgical probe |
US4061135A (en) | 1976-09-27 | 1977-12-06 | Jerrold Widran | Binocular endoscope |
US4275734A (en) | 1977-08-12 | 1981-06-30 | Valleylab, Inc. | Cryosurgical apparatus and method |
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 |
DE2831199C3 (en) | 1978-07-15 | 1981-01-08 | Erbe Elektromedizin Gmbh & Co Kg, 7400 Tuebingen | Cryosurgical device |
US4248224A (en) | 1978-08-01 | 1981-02-03 | Jones James W | Double venous cannula |
CA1129015A (en) | 1980-06-11 | 1982-08-03 | Timofei S. Gudkin | Thermoelectric cryoprobe |
US4377168A (en) | 1981-02-27 | 1983-03-22 | Wallach Surgical Instruments, Inc. | Cryosurgical instrument |
US4598698A (en) | 1983-01-20 | 1986-07-08 | Warner-Lambert Technologies, Inc. | Diagnostic device |
US4601290A (en) | 1983-10-11 | 1986-07-22 | Cabot Medical Corporation | Surgical instrument for cutting body tissue from a body area having a restricted space |
US5143073A (en) | 1983-12-14 | 1992-09-01 | Edap International, S.A. | Wave apparatus system |
US4664110A (en) | 1985-03-18 | 1987-05-12 | University Of Southern California | Controlled rate freezing for cryorefractive surgery |
SE8502048D0 (en) | 1985-04-26 | 1985-04-26 | Astra Tech Ab | VACUUM FIXED HALLS FOR MEDICAL USE |
US4917095A (en) | 1985-11-18 | 1990-04-17 | Indianapolis Center For Advanced Research, Inc. | Ultrasound location and therapy method and apparatus for calculi in the body |
US4872346A (en) | 1986-07-18 | 1989-10-10 | Indianapolis Center For Advanced Research | Multiple frequencies from single crystal |
US5231995A (en) | 1986-11-14 | 1993-08-03 | Desai Jawahar M | Method for catheter mapping and ablation |
US5044165A (en) | 1986-12-03 | 1991-09-03 | Board Of Regents, The University Of Texas | Cryo-slammer |
US4779611A (en) | 1987-02-24 | 1988-10-25 | Grooters Ronald K | Disposable surgical scope guide |
US4802475A (en) | 1987-06-22 | 1989-02-07 | Weshahy Ahmed H A G | Methods and apparatus of applying intra-lesional cryotherapy |
US4815470A (en) | 1987-11-13 | 1989-03-28 | Advanced Diagnostic Medical Systems, Inc. | Inflatable sheath for ultrasound probe |
US5029574A (en) | 1988-04-14 | 1991-07-09 | Okamoto Industries, Inc. | Endoscopic balloon with a protective film thereon |
US4920982A (en) * | 1988-06-27 | 1990-05-01 | Vastech Medical Products Inc. | Percutaneous vasectomy method |
US5147355A (en) | 1988-09-23 | 1992-09-15 | Brigham And Womens Hospital | Cryoablation catheter and method of performing cryoablation |
US5108390A (en) | 1988-11-14 | 1992-04-28 | Frigitronics, Inc. | Flexible cryoprobe |
GB2226497B (en) | 1988-12-01 | 1992-07-01 | Spembly Medical Ltd | Cryosurgical probe |
GB8829525D0 (en) | 1988-12-17 | 1989-02-01 | Spembly Medical Ltd | Cryosurgical apparatus |
US4936281A (en) | 1989-04-13 | 1990-06-26 | Everest Medical Corporation | Ultrasonically enhanced RF ablation catheter |
US4946460A (en) | 1989-04-26 | 1990-08-07 | Cryo Instruments, Inc. | Apparatus for cryosurgery |
US4916922A (en) | 1989-05-09 | 1990-04-17 | Mullens Patrick L | Rapid freezing apparatus |
US5151102A (en) * | 1989-05-31 | 1992-09-29 | Kyocera Corporation | Blood vessel coagulation/stanching device |
US5100388A (en) | 1989-09-15 | 1992-03-31 | Interventional Thermodynamics, Inc. | Method and device for thermal ablation of hollow body organs |
US5364394A (en) * | 1989-12-21 | 1994-11-15 | Mehl Thomas L | Method of removing hair from the body and inhibiting future growth |
GB9004427D0 (en) | 1990-02-28 | 1990-04-25 | Nat Res Dev | Cryogenic cooling apparatus |
US5013312A (en) | 1990-03-19 | 1991-05-07 | Everest Medical Corporation | Bipolar scalpel for harvesting internal mammary artery |
US5080660A (en) | 1990-05-11 | 1992-01-14 | Applied Urology, Inc. | Electrosurgical electrode |
JPH0734805B2 (en) * | 1990-05-16 | 1995-04-19 | アロカ株式会社 | Blood coagulator |
ZA917281B (en) | 1990-09-26 | 1992-08-26 | Cryomedical Sciences Inc | Cryosurgical instrument and system and method of cryosurgery |
US5269291A (en) | 1990-12-10 | 1993-12-14 | Coraje, Inc. | Miniature ultrasonic transducer for plaque ablation |
US5324255A (en) | 1991-01-11 | 1994-06-28 | Baxter International Inc. | Angioplasty and ablative devices having onboard ultrasound components and devices and methods for utilizing ultrasound to treat or prevent vasopasm |
US5156613A (en) * | 1991-02-13 | 1992-10-20 | Interface Biomedical Laboratories Corp. | Collagen welding rod material for use in tissue welding |
US5316000A (en) | 1991-03-05 | 1994-05-31 | Technomed International (Societe Anonyme) | Use of at least one composite piezoelectric transducer in the manufacture of an ultrasonic therapy apparatus for applying therapy, in a body zone, in particular to concretions, to tissue, or to bones, of a living being and method of ultrasonic therapy |
US5300087A (en) * | 1991-03-22 | 1994-04-05 | Knoepfler Dennis J | Multiple purpose forceps |
US5217460A (en) * | 1991-03-22 | 1993-06-08 | Knoepfler Dennis J | Multiple purpose forceps |
US5178133A (en) | 1991-03-26 | 1993-01-12 | Pena Louis T | Laparoscopic retractor and sheath |
US5207674A (en) | 1991-05-13 | 1993-05-04 | Hamilton Archie C | Electronic cryogenic surgical probe apparatus and method |
US5370134A (en) | 1991-05-29 | 1994-12-06 | Orgin Medsystems, Inc. | Method and apparatus for body structure manipulation and dissection |
US5361752A (en) | 1991-05-29 | 1994-11-08 | Origin Medsystems, Inc. | Retraction apparatus and methods for endoscopic surgery |
US5232516A (en) | 1991-06-04 | 1993-08-03 | Implemed, Inc. | Thermoelectric device with recuperative heat exchangers |
US5217860A (en) | 1991-07-08 | 1993-06-08 | The American National Red Cross | Method for preserving organs for transplantation by vitrification |
US5735290A (en) * | 1993-02-22 | 1998-04-07 | Heartport, Inc. | Methods and systems for performing thoracoscopic coronary bypass and other procedures |
US5254116A (en) | 1991-09-06 | 1993-10-19 | Cryomedical Sciences, Inc. | Cryosurgical instrument with vent holes and method using same |
US5395312A (en) * | 1991-10-18 | 1995-03-07 | Desai; Ashvin | Surgical tool |
US5383874A (en) * | 1991-11-08 | 1995-01-24 | Ep Technologies, Inc. | Systems for identifying catheters and monitoring their use |
US5217001A (en) | 1991-12-09 | 1993-06-08 | Nakao Naomi L | Endoscope sheath and related method |
US5228923A (en) | 1991-12-13 | 1993-07-20 | Implemed, Inc. | Cylindrical thermoelectric cells |
FR2685872A1 (en) | 1992-01-07 | 1993-07-09 | Edap Int | APPARATUS OF EXTRACORPOREAL ULTRASONIC HYPERTHERMIA WITH VERY HIGH POWER AND ITS OPERATING METHOD. |
US5400770A (en) | 1992-01-15 | 1995-03-28 | Nakao; Naomi L. | Device utilizable with endoscope and related method |
US5626599A (en) * | 1992-01-22 | 1997-05-06 | C. R. Bard | Method for the percutaneous transluminal front-end loading delivery of a prosthetic occluder |
US5222501A (en) | 1992-01-31 | 1993-06-29 | Duke University | Methods for the diagnosis and ablation treatment of ventricular tachycardia |
US5263493A (en) | 1992-02-24 | 1993-11-23 | Boaz Avitall | Deflectable loop electrode array mapping and ablation catheter for cardiac chambers |
US5555883A (en) * | 1992-02-24 | 1996-09-17 | Avitall; Boaz | Loop electrode array mapping and ablation catheter for cardiac chambers |
US5318525A (en) | 1992-04-10 | 1994-06-07 | Medtronic Cardiorhythm | Steerable electrode catheter |
AU4026793A (en) | 1992-04-10 | 1993-11-18 | Cardiorhythm | Shapable handle for steerable electrode catheter |
WO1993020768A1 (en) * | 1992-04-13 | 1993-10-28 | Ep Technologies, Inc. | Steerable microwave antenna systems for cardiac ablation |
US5318589A (en) * | 1992-04-15 | 1994-06-07 | Microsurge, Inc. | Surgical instrument for endoscopic surgery |
US5281213A (en) | 1992-04-16 | 1994-01-25 | Implemed, Inc. | Catheter for ice mapping and ablation |
US5281215A (en) | 1992-04-16 | 1994-01-25 | Implemed, Inc. | Cryogenic catheter |
US5443470A (en) * | 1992-05-01 | 1995-08-22 | Vesta Medical, Inc. | Method and apparatus for endometrial ablation |
US5277201A (en) | 1992-05-01 | 1994-01-11 | Vesta Medical, Inc. | Endometrial ablation apparatus and method |
US5295484A (en) | 1992-05-19 | 1994-03-22 | Arizona Board Of Regents For And On Behalf Of The University Of Arizona | Apparatus and method for intra-cardiac ablation of arrhythmias |
US5324284A (en) | 1992-06-05 | 1994-06-28 | Cardiac Pathways, Inc. | Endocardial mapping and ablation system utilizing a separately controlled ablation catheter and method |
US5275595A (en) | 1992-07-06 | 1994-01-04 | Dobak Iii John D | Cryosurgical instrument |
WO1994002077A2 (en) * | 1992-07-15 | 1994-02-03 | Angelase, Inc. | Ablation catheter system |
GB2269107B (en) | 1992-07-31 | 1996-05-08 | Spembly Medical Ltd | Cryosurgical ablation |
US5401272A (en) * | 1992-09-25 | 1995-03-28 | Envision Surgical Systems, Inc. | Multimodality probe with extendable bipolar electrodes |
US5322520A (en) | 1992-11-12 | 1994-06-21 | Implemed, Inc. | Iontophoretic structure for medical devices |
US5334193A (en) | 1992-11-13 | 1994-08-02 | American Cardiac Ablation Co., Inc. | Fluid cooled ablation catheter |
DE4338758C2 (en) * | 1992-11-13 | 2001-08-09 | Scimed Life Systems Inc | Catheter assembly |
US5348554A (en) * | 1992-12-01 | 1994-09-20 | Cardiac Pathways Corporation | Catheter for RF ablation with cooled electrode |
US5403312A (en) | 1993-07-22 | 1995-04-04 | Ethicon, Inc. | Electrosurgical hemostatic device |
US5324286A (en) | 1993-01-21 | 1994-06-28 | Arthur A. Fowle, Inc. | Entrained cryogenic droplet transfer method and cryosurgical instrument |
US5409483A (en) * | 1993-01-22 | 1995-04-25 | Jeffrey H. Reese | Direct visualization surgical probe |
US5645082A (en) * | 1993-01-29 | 1997-07-08 | Cardima, Inc. | Intravascular method and system for treating arrhythmia |
US5797960A (en) * | 1993-02-22 | 1998-08-25 | Stevens; John H. | Method and apparatus for thoracoscopic intracardiac procedures |
US5403311A (en) | 1993-03-29 | 1995-04-04 | Boston Scientific Corporation | Electro-coagulation and ablation and other electrotherapeutic treatments of body tissue |
US5395363A (en) * | 1993-06-29 | 1995-03-07 | Utah Medical Products | Diathermy coagulation and ablation apparatus and method |
US5487757A (en) * | 1993-07-20 | 1996-01-30 | Medtronic Cardiorhythm | Multicurve deflectable catheter |
US5385148A (en) | 1993-07-30 | 1995-01-31 | The Regents Of The University Of California | Cardiac imaging and ablation catheter |
WO1995005212A2 (en) * | 1993-08-11 | 1995-02-23 | Electro-Catheter Corporation | Improved ablation electrode |
US5405376A (en) * | 1993-08-27 | 1995-04-11 | Medtronic, Inc. | Method and apparatus for ablation |
US5431649A (en) * | 1993-08-27 | 1995-07-11 | Medtronic, Inc. | Method and apparatus for R-F ablation |
US5396887A (en) | 1993-09-23 | 1995-03-14 | Cardiac Pathways Corporation | Apparatus and method for detecting contact pressure |
US5607462A (en) * | 1993-09-24 | 1997-03-04 | Cardiac Pathways Corporation | Catheter assembly, catheter and multi-catheter introducer for use therewith |
US5496312A (en) * | 1993-10-07 | 1996-03-05 | Valleylab Inc. | Impedance and temperature generator control |
US5400783A (en) | 1993-10-12 | 1995-03-28 | Cardiac Pathways Corporation | Endocardial mapping apparatus with rotatable arm and method |
US5545193A (en) * | 1993-10-15 | 1996-08-13 | Ep Technologies, Inc. | Helically wound radio-frequency emitting electrodes for creating lesions in body tissue |
US5497774A (en) * | 1993-11-03 | 1996-03-12 | Daig Corporation | Guiding introducer for left atrium |
US5722400A (en) * | 1995-02-16 | 1998-03-03 | Daig Corporation | Guiding introducers for use in the treatment of left ventricular tachycardia |
US5472441A (en) * | 1993-11-08 | 1995-12-05 | Zomed International | Device for treating cancer and non-malignant tumors and methods |
US5458598A (en) * | 1993-12-02 | 1995-10-17 | Cabot Technology Corporation | Cutting and coagulating forceps |
US5730127A (en) * | 1993-12-03 | 1998-03-24 | Avitall; Boaz | Mapping and ablation catheter system |
US5487385A (en) | 1993-12-03 | 1996-01-30 | Avitall; Boaz | Atrial mapping and ablation catheter system |
US5458596A (en) * | 1994-05-06 | 1995-10-17 | Dorsal Orthopedic Corporation | Method and apparatus for controlled contraction of soft tissue |
US5617854A (en) * | 1994-06-22 | 1997-04-08 | Munsif; Anand | Shaped catheter device and method |
US5505730A (en) * | 1994-06-24 | 1996-04-09 | Stuart D. Edwards | Thin layer ablation apparatus |
US5575788A (en) * | 1994-06-24 | 1996-11-19 | Stuart D. Edwards | Thin layer ablation apparatus |
US6009877A (en) * | 1994-06-24 | 2000-01-04 | Edwards; Stuart D. | Method for treating a sphincter |
US5609151A (en) * | 1994-09-08 | 1997-03-11 | Medtronic, Inc. | Method for R-F ablation |
US5885278A (en) * | 1994-10-07 | 1999-03-23 | E.P. Technologies, Inc. | Structures for deploying movable electrode elements |
US5722402A (en) * | 1994-10-11 | 1998-03-03 | Ep Technologies, Inc. | Systems and methods for guiding movable electrode elements within multiple-electrode structures |
US5951546A (en) * | 1994-12-13 | 1999-09-14 | Lorentzen; Torben | Electrosurgical instrument for tissue ablation, an apparatus, and a method for providing a lesion in damaged and diseased tissue from a mammal |
US5595183A (en) * | 1995-02-17 | 1997-01-21 | Ep Technologies, Inc. | Systems and methods for examining heart tissue employing multiple electrode structures and roving electrodes |
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 |
US6063081A (en) * | 1995-02-22 | 2000-05-16 | Medtronic, Inc. | Fluid-assisted electrocautery device |
US5647871A (en) * | 1995-03-10 | 1997-07-15 | Microsurge, Inc. | Electrosurgery with cooled electrodes |
US5688267A (en) * | 1995-05-01 | 1997-11-18 | Ep Technologies, Inc. | Systems and methods for sensing multiple temperature conditions during tissue ablation |
US5735280A (en) * | 1995-05-02 | 1998-04-07 | Heart Rhythm Technologies, Inc. | Ultrasound energy delivery system and method |
US5718241A (en) * | 1995-06-07 | 1998-02-17 | Biosense, Inc. | Apparatus and method for treating cardiac arrhythmias with no discrete target |
US5827271A (en) * | 1995-09-19 | 1998-10-27 | Valleylab | Energy delivery system for vessel sealing |
US5590657A (en) * | 1995-11-06 | 1997-01-07 | The Regents Of The University Of Michigan | Phased array ultrasound system and method for cardiac ablation |
US5716389A (en) * | 1995-11-13 | 1998-02-10 | Walinsky; Paul | Cardiac ablation catheter arrangement with movable guidewire |
US5733280A (en) * | 1995-11-15 | 1998-03-31 | Avitall; Boaz | Cryogenic epicardial mapping and ablation |
US5853411A (en) * | 1996-01-19 | 1998-12-29 | Ep Technologies, Inc. | Enhanced electrical connections for electrode structures |
US5895417A (en) * | 1996-03-06 | 1999-04-20 | Cardiac Pathways Corporation | Deflectable loop design for a linear lesion ablation apparatus |
NL1003024C2 (en) * | 1996-05-03 | 1997-11-06 | Tjong Hauw Sie | Stimulus conduction blocking instrument. |
US5730074A (en) * | 1996-06-07 | 1998-03-24 | Farmer Fabrications, Inc. | Liquid dispenser for seed planter |
US5882346A (en) * | 1996-07-15 | 1999-03-16 | Cardiac Pathways Corporation | Shapable catheter using exchangeable core and method of use |
US5720775A (en) * | 1996-07-31 | 1998-02-24 | Cordis Corporation | Percutaneous atrial line ablation catheter |
US6237605B1 (en) * | 1996-10-22 | 2001-05-29 | Epicor, Inc. | Methods of epicardial ablation |
US5893848A (en) * | 1996-10-24 | 1999-04-13 | Plc Medical Systems, Inc. | Gauging system for monitoring channel depth in percutaneous endocardial revascularization |
US5782828A (en) * | 1996-12-11 | 1998-07-21 | Irvine Biomedical, Inc. | Ablation catheter with multiple flexible curves |
US5897554A (en) * | 1997-03-01 | 1999-04-27 | Irvine Biomedical, Inc. | Steerable catheter having a loop electrode |
US5873845A (en) * | 1997-03-17 | 1999-02-23 | General Electric Company | Ultrasound transducer with focused ultrasound refraction plate |
US5879295A (en) * | 1997-04-02 | 1999-03-09 | Medtronic, Inc. | Enhanced contact steerable bowing electrode catheter assembly |
US6012457A (en) * | 1997-07-08 | 2000-01-11 | The Regents Of The University Of California | Device and method for forming a circumferential conduction block in a pulmonary vein |
US6217576B1 (en) * | 1997-05-19 | 2001-04-17 | Irvine Biomedical Inc. | Catheter probe for treating focal atrial fibrillation in pulmonary veins |
US5876399A (en) * | 1997-05-28 | 1999-03-02 | Irvine Biomedical, Inc. | Catheter system and methods thereof |
US6096037A (en) * | 1997-07-29 | 2000-08-01 | Medtronic, Inc. | Tissue sealing electrosurgery device and methods of sealing tissue |
US6527767B2 (en) * | 1998-05-20 | 2003-03-04 | New England Medical Center | Cardiac ablation system and method for treatment of cardiac arrhythmias and transmyocardial revascularization |
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 |
US6302903B1 (en) * | 1998-07-07 | 2001-10-16 | Medtronic, Inc. | Straight needle apparatus for creating 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 |
US6016811A (en) * | 1998-09-01 | 2000-01-25 | Fidus Medical Technology Corporation | Method of using a microwave ablation catheter with a loop configuration |
US6042556A (en) * | 1998-09-04 | 2000-03-28 | University Of Washington | Method for determining phase advancement of transducer elements in high intensity focused ultrasound |
US6245062B1 (en) * | 1998-10-23 | 2001-06-12 | Afx, Inc. | Directional reflector shield assembly for a microwave ablation instrument |
US6217528B1 (en) * | 1999-02-11 | 2001-04-17 | Scimed Life Systems, Inc. | Loop structure having improved tissue contact capability |
US6702811B2 (en) * | 1999-04-05 | 2004-03-09 | Medtronic, Inc. | Ablation catheter assembly with radially decreasing helix and method of use |
US20050010095A1 (en) * | 1999-04-05 | 2005-01-13 | Medtronic, Inc. | Multi-purpose catheter apparatus and method of use |
US20010007070A1 (en) * | 1999-04-05 | 2001-07-05 | Medtronic, Inc. | Ablation catheter assembly and method for isolating a pulmonary vein |
US6371955B1 (en) * | 1999-08-10 | 2002-04-16 | Biosense Webster, Inc. | Atrial branding iron catheter and a method for treating atrial fibrillation |
US6368275B1 (en) * | 1999-10-07 | 2002-04-09 | Acuson Corporation | Method and apparatus for diagnostic medical information gathering, hyperthermia treatment, or directed gene therapy |
US6692450B1 (en) * | 2000-01-19 | 2004-02-17 | Medtronic Xomed, Inc. | Focused ultrasound ablation devices having selectively actuatable ultrasound emitting elements and methods of using the same |
US6361531B1 (en) * | 2000-01-21 | 2002-03-26 | Medtronic Xomed, Inc. | Focused ultrasound ablation devices having malleable handle shafts and methods of using the same |
WO2001082811A1 (en) * | 2000-04-27 | 2001-11-08 | Medtronic, Inc. | System and method for assessing transmurality of ablation lesions |
US6514250B1 (en) * | 2000-04-27 | 2003-02-04 | Medtronic, Inc. | Suction stabilized epicardial ablation devices |
US6663627B2 (en) * | 2001-04-26 | 2003-12-16 | Medtronic, Inc. | Ablation system and method of use |
US6699240B2 (en) * | 2001-04-26 | 2004-03-02 | Medtronic, Inc. | Method and apparatus for tissue ablation |
US7250048B2 (en) * | 2001-04-26 | 2007-07-31 | 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 |
US6648883B2 (en) * | 2001-04-26 | 2003-11-18 | Medtronic, Inc. | Ablation system and method of use |
US6656175B2 (en) * | 2001-12-11 | 2003-12-02 | Medtronic, Inc. | Method and system for treatment of atrial tachyarrhythmias |
US7294143B2 (en) * | 2002-05-16 | 2007-11-13 | Medtronic, Inc. | Device and method for ablation of cardiac tissue |
AU2005244868A1 (en) * | 2004-05-14 | 2005-12-01 | Medtronic, Inc. | Method and devices for treating atrial fibrillation by mass ablation |
WO2005120375A2 (en) * | 2004-06-02 | 2005-12-22 | Medtronic, Inc. | Loop ablation apparatus and method |
-
2002
- 2002-01-25 US US10/056,806 patent/US6827715B2/en not_active Expired - Lifetime
-
2003
- 2003-01-14 AT AT03702108T patent/ATE387150T1/en not_active IP Right Cessation
- 2003-01-14 EP EP03702108A patent/EP1467670B1/en not_active Expired - Lifetime
- 2003-01-14 DE DE60319341T patent/DE60319341T2/en not_active Expired - Lifetime
- 2003-01-14 WO PCT/US2003/001036 patent/WO2003063717A1/en active IP Right Grant
-
2004
- 2004-12-03 US US11/003,451 patent/US7364578B2/en not_active Expired - Lifetime
Patent Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1996034567A1 (en) * | 1995-05-02 | 1996-11-07 | Heart Rhythm Technologies, Inc. | System for controlling the energy delivered to a patient for ablation |
US6113592A (en) * | 1995-06-09 | 2000-09-05 | Engineering & Research Associates, Inc. | Apparatus and method for controlling ablation depth |
US5897553A (en) | 1995-11-02 | 1999-04-27 | Medtronic, Inc. | Ball point fluid-assisted electrocautery device |
US5925038A (en) * | 1996-01-19 | 1999-07-20 | Ep Technologies, Inc. | Expandable-collapsible electrode structures for capacitive coupling to tissue |
US6175768B1 (en) * | 1996-04-17 | 2001-01-16 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | In vivo simulator for microwave treatment |
US6217573B1 (en) * | 1998-12-03 | 2001-04-17 | Cordis Webster | System and method for measuring surface temperature of tissue during ablation |
WO2001068173A2 (en) * | 2000-03-15 | 2001-09-20 | Boston Scientific Limited | Ablation and imaging catheter |
WO2001080757A2 (en) * | 2000-04-27 | 2001-11-01 | Medtronic, Inc. | Vibration sensitive ablation device and method |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN102473996A (en) * | 2009-07-20 | 2012-05-23 | 克里奥医药有限公司 | Surgical antenna and electrosurgical system using the same |
US9033971B2 (en) | 2009-07-20 | 2015-05-19 | Creo Medical Limited | Surgical antenna and electrosurgical system using the same |
Also Published As
Publication number | Publication date |
---|---|
US20050165392A1 (en) | 2005-07-28 |
US20030144653A1 (en) | 2003-07-31 |
ATE387150T1 (en) | 2008-03-15 |
US6827715B2 (en) | 2004-12-07 |
EP1467670B1 (en) | 2008-02-27 |
US7364578B2 (en) | 2008-04-29 |
DE60319341T2 (en) | 2008-07-31 |
DE60319341D1 (en) | 2008-04-10 |
EP1467670A1 (en) | 2004-10-20 |
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