US20060217696A1 - Multi-modality ablation device - Google Patents
Multi-modality ablation device Download PDFInfo
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- US20060217696A1 US20060217696A1 US11/444,836 US44483606A US2006217696A1 US 20060217696 A1 US20060217696 A1 US 20060217696A1 US 44483606 A US44483606 A US 44483606A US 2006217696 A1 US2006217696 A1 US 2006217696A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/54—Control of the diagnostic device
- A61B8/546—Control of the diagnostic device involving monitoring or regulation of device temperature
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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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
- A61N7/02—Localised ultrasound hyperthermia
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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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
- A61B90/06—Measuring instruments not otherwise provided for
- A61B2090/061—Measuring instruments not otherwise provided for for measuring dimensions, e.g. length
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
- A61B90/36—Image-producing devices or illumination devices not otherwise provided for
- A61B90/37—Surgical systems with images on a monitor during operation
- A61B2090/378—Surgical systems with images on a monitor during operation using ultrasound
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- Heart & Thoracic Surgery (AREA)
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- Plasma & Fusion (AREA)
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- Pathology (AREA)
- Surgical Instruments (AREA)
Abstract
An instrument for ablation of tissue. The instrument including: a body having at least one surface for contacting a tissue surface, the at least one surface being substantially planar; an ultrasonic transducer disposed in the body for generating ultrasonic energy and directing at least a portion of the ultrasonic energy to the tissue surface, the ultrasonic transducer being operatively connected to an ultrasonic generator; at least one radio-frequency electrode disposed on the at least one surface for directing radio frequency energy to the tissue surface, the at least one radio-frequency electrode being operatively connected to a power source; and one or more switches for selectively coupling at least one of the ultrasonic transducer to the ultrasonic generator and the at least one radio-frequency electrode to the power source.
Description
- 1. Field of the Invention
- The present invention relates generally to medical instrumentation, and more particularly, to a multi-modality ablation device.
- 2. Prior Art
- Ultrasonic and radio frequency instruments are well known in the medical arts. Such instrumentation may be used to make lesions in tissue, but are also used to cut and coagulate tissue and blood, respectively. Typically, ultrasonic instrumentation has an ultrasonic transducer at a working end of the instrument, while radio frequency instruments have one or more electrodes at a working end of the instrument. Each of the working ends is typically separated from a handle or other manipulation means by an elongated shaft.
- Instruments utilizing radio frequency energy perform well for single-sided ablation of thin tissue. However, this modality can only ablate thicker tissue at the expense of lesion width. Creating wider lesions with radio frequency energy may result in damage to critical peripheral tissue structures. Beyond 6 mm in tissue depth, radio frequency energy may not achieve lesion transmurality. On the other hand, instruments utilizing ultrasound energy perform well for thick tissue ablation because the energy can be focused into the depth of the tissue. However, for thin tissue, ultrasound may be ineffective as the ultrasound energy is focused in blood, not in the tissue.
- Thus, the surgeon must determine the efficacy of the lesion created with one of the ultrasound or radio frequency instruments and may need to exchange instrumentation to create a proper lesion, all of which significantly increase the time of the procedure (ablation cycle time).
- Therefore it is an object of the present invention to provide ablation devices and methods for their use that overcome the disadvantages of conventional instrumentation known in the art.
- Accordingly, the devices and methods of the present invention utilize one or both ultrasound and radio frequency energy modalities to achieve an efficacious lesion with minimum activation time. Thus, ablation cycle time and adverse effects such as excessive peripheral thermal damage to tissue are minimized when the modalities are used together, when necessary.
- Therefore, an instrument for ablation of tissue is provided. The instrument comprising: a body having at least one surface for contacting a tissue surface, the at least one surface being substantially planar; an ultrasonic transducer disposed in the body for generating ultrasonic energy and directing at least a portion of the ultrasonic energy to the tissue surface, the ultrasonic transducer being operatively connected to an ultrasonic generator; at least one radio-frequency electrode disposed on the at least one surface for directing radio frequency energy to the tissue surface, the at least one radio-frequency electrode being operatively connected to a power source; and one or more switches for selectively coupling at least one of the ultrasonic transducer to the ultrasonic generator and the at least one radio-frequency electrode to the power source.
- The body can comprise a non-conductive head, the non-conductive head having a cavity for housing the ultrasonic transducer. The head can further have a heat exchanger for cooling at least one of the ultrasonic transducer, the at least one radio-frequency electrode, and the tissue surface. The at least one radio-frequency electrode can comprise first and second radio-frequency electrodes, the first radio-frequency electrode being maintained at a first polarity and the second radio-frequency electrode being maintained at a second polarity different from the first polarity. The first and second radio frequency electrodes can comprise first and second conductive surfaces, respectively, disposed on the non-conductive head. The first and second conductive surfaces can be separated by the cavity and the cavity can be enclosed with an acoustic window on the at least one surface.
- Also provided is an instrument for ablation of tissue where the instrument comprises: an ultrasonic transducer for generating ultrasonic energy and directing at least a portion of the ultrasonic energy to a tissue surface; and at least one radio-frequency electrode for directing radio frequency energy to the tissue surface, the at least one radio frequency electrode being disposed substantially in a plane with the ultrasonic transducer.
- The instrument can further comprise one or more switches for selectively powering at least one of the ultrasonic transducer and the at least one radio-frequency electrode.
- Still provided is a system for ablation of tissue, where the system comprises: a tissue thickness measurement means for measuring a thickness of tissue corresponding to a tissue surface to be ablated; and an instrument having an ultrasonic transducer for generating ultrasonic energy and directing at least a portion of the ultrasonic energy to the tissue surface; at least one radio-frequency electrode for directing radio frequency energy to the tissue surface; and one or more switches for selectively powering at least one of the ultrasonic transducer and the at least one radio-frequency electrode based on the measured tissue thickness.
- The system can further comprise an ultrasonic generator selectively coupled to the ultrasonic transducer by the one or more switches. The system can also further comprise a power source selectively coupled to the at least one electrode by the one or more switches.
- Still provided is a method for creating lesions in tissue. The method comprising: providing an instrument capable of selectively directing at least one of ultrasonic and radio-frequency energy to the tissue; measuring a tissue thickness corresponding to the tissue; and applying at least one of ultrasonic and radio-frequency energy from the instrument to the tissue based on the measuring.
- The applying can comprise applying the ultrasonic and radio-frequency energy from the instrument to the tissue surface where the measured tissue thickness is greater than a first predetermined thickness. The first predetermined thickness can be about 6 mm.
- The applying can comprise applying only the radio-frequency energy from the instrument to the tissue surface where the measured tissue thickness is less than a second predetermined thickness. The second predetermined thickness can be about 3-5 mm.
- The applying can comprise applying only the ultrasonic energy from the instrument to the tissue surface where the measured tissue thickness is between the first predetermined thickness and the second predetermined thickness.
- Where the ultrasonic energy is supplied by an ultrasonic transducer and the radio-frequency energy is supplied by at least one electrode, the method can further comprise cooling at least one of the ultrasonic transducer, the at least one electrode, and the tissue.
- Still provided is a method for creating lesions in tissue where the method comprises: measuring a tissue thickness corresponding to the tissue; and applying ultrasonic and radio-frequency energy to the tissue surface where the tissue thickness is greater than a predetermined thickness.
- The applying can comprise applying the ultrasonic energy followed by applying the radio-frequency energy.
- Still yet provided is a method for creating lesions in tissue where the method comprises: measuring a tissue thickness corresponding to the tissue; applying ultrasonic energy to the tissue surface to create a lesion where the tissue thickness is greater than a predetermined thickness; determining an extent of the lesion created by the applying of the ultrasonic energy; and applying radio-frequency energy to the tissue surface where the extent of the lesion is determined to be unsatisfactory.
- These and other features, aspects, and advantages of the apparatus and methods of the present invention will become better understood with regard to the following description, appended claims, and accompanying drawings where:
-
FIG. 1 illustrates a perspective view of a system for ablating tissue having an embodiment of a tissue ablation instrument according to the present invention. -
FIG. 2 illustrates a sectional view of the instrument ofFIG. 1 as taken along line 2-2 ofFIG. 1 . -
FIG. 3 illustrates a partial bottom view of the instrument ofFIG. 1 . -
FIGS. 4 a-4 c illustrate creation of lesions with the instrument ofFIG. 2 in tissue of varying thickness. - Referring now to
FIGS. 1-3 , therein is illustrated an instrument and system for ablation of tissue, the instrument generally referred to byreference numeral 100 and the system generally referred to byreference numeral 200. Although theinstrument 100 is shown and described as a rigid instrument, it can also be configured in other ways without departing from the scope or spirit of the present invention. For example, theinstrument 100 may be configured as a catheter, a minimally invasive instrument, or a less invasive instrument. Theinstrument 100 has abody 102 having at least onesurface 104 for contacting atissue surface 106. The surface is substantially planar, but may be slightly curved to follow a contour of a curved tissue surface. Thebody 102, as configured by way of example only, is disposed at a distal end of anelongated tube 108. Theelongated tube 108 has ahandle 110 disposed at a proximal end thereof. Thebody 102 preferably comprises anon-conductive head 102 a. - The
body 102 has acavity 102 b for housing at least oneultrasonic transducer 112 for generating ultrasonic energy and directing at least a portion of the ultrasonic energy to thetissue surface 106. Theultrasonic transducer 112 is operatively connected to anultrasonic generator 114, preferably by wiring 116. Thewiring 116 is preferably connected, either hardwired to thehandle 110 or through a releasable connector (not shown) on thehandle 110 and is routed to theultrasonic transducer 112 through theelongated tube 108. Thewiring 116 may also be routed externally to thehandle 110 and/orelongated tube 108. Alternatively, the ultrasonic generator may be integrally formed in theinstrument 100, such as in thehandle 110. Theultrasonic transducer 112 is fixed in thebody 102 by any means known in the art, such as with a bracket orepoxy 118. Anacoustic window 120 fabricated from a material which transmits ultrasonic energy encloses the cavity on the at least onesurface 104. - The
body 102 and/orultrasonic transducer 112 can be configured in any way known in the art for creating lesions in tissue, such as that disclosed in co-pending U.S. application Ser. No. 10/______, (attorney Docket No. 16334), entitled System For Creating Linear Lesions for the Treatment of Atrial Fibrillation, the entire contents of which is incorporated herein by its reference. For example, theultrasonic transducer 112 can be convexly curved such that the resulting ultrasonic energy is focused along a straight or curved line along the length of theultrasonic transducer 112 to create a lesion. Theultrasonic transducer 112 may also have an impedance matching coating (not shown) on the side of theultrasonic transducer 112 that faces theacoustic window 120. Theultrasonic transducer 112 can further provide for circulation of a cooling medium, such as a fluid, through thecavity 102 b. The cooling medium, for example, water or saline, may be re-circulated through thecavity 102 b or through other openings (not shown) in thebody 102 from a cooling medium delivery means 122, such as a pump or a syringe. The cooling medium delivery means 122 can draw cooling medium from a coolingmedium source 124 and deliver the same to theinstrument 100 by way oftubing 126. Thetubing 126 can be routed externally to thehandle 110 andelongated tube 108, as shown inFIG. 1 , or routed internally to thehandle 110 andelongated tube 108. In any configuration, the cooling medium is directed to thecavity 102 b and may be dumped thereafter or re-circulated. The cooling medium acts as a heat exchanger for cooling theultrasonic transducer 112 but may also cool the radio-frequency electrode(s) (discussed below) and the tissue surface (106). Theultrasonic transducer 112 can also be positioned in thecavity 102 b such that an air gap exists between a back surface of the ultrasonic crystal and a front surface of thecavity 102 b. The configuration of theultrasonic transducer 112 is given by way of example only and not to limit the spirit or scope of the present invention. Those skilled in the art will appreciate that theultrasonic transducer 112 can be configured in any manner known in the art for producing ultrasonic energy for its intended purpose. - The
instrument 100 further has at least one radio-frequency electrode 128 disposed on the at least one surface of thebody 102 for directing radio frequency energy to thetissue surface 106. The at least oneradio frequency electrode 128 is preferably disposed substantially in a plane with theultrasonic transducer 112. The radio-frequency electrode(s) 128 are operatively connected to apower source 130, such as an electro-surgical unit, by way ofwiring 132. Thewiring 132 can be hardwired to theinstrument 100 or releasably connected by way of a connector (not shown). Furthermore, thewiring 132 can be routed internally in thehandle 110 and/orelongated tube 108, as shown inFIG. 1 , or external thereto. The radio-frequency electrode(s) 128 can be configured as monopolar or bipolar as is known in the art of electro-surgical instrumentation. In a monopolar configuration, one or more electrodes are at a first polarity and when energized, current flows through the patient and exits through a ground plate attached to the patient. In a bipolar configuration, as shown inFIG. 2 , two or more radio-frequency electrodes 128 are utilized, a first radio-frequency electrode 128 is maintained at a first polarity (+) and a second radio-frequency electrode 128 is maintained at a second polarity (−) different from the first polarity (+). In such a configuration, the first and second radio-frequency electrodes are arranged in a side-by-side relationship with thetransducer 112, with the transducer preferably being positioned in between the first and second radio-frequency electrodes 128 in a substantially planar configuration. In the bipolar configuration, current flows from one electrode to the other, thus, the need for a grounding plate is eliminated. As shown inFIGS. 2 and 3 , the twoelectrodes 128 are separated by thecavity 102 b. The two radio-frequency electrodes 128 preferably are first and secondconductive surfaces non-conductive head 102 a. However, thehead 102 a may also be conductive and coated with a non-conductive coating in all portions except the first and second conductive surfaces. - The
instrument 100 further has one ormore switches 134 for selectively coupling theultrasonic transducer 112 to theultrasonic generator 114 and the radio-frequency electrode(s) 128 to thepower source 130. Theswitches instrument 100, such as formed on thehandle 110 as shown inFIG. 1 , or remote therefrom, such as a footswitch (not shown) or a switch located on theexternal wiring switches 134 comprise a split switch having first andsecond buttons slot 136 formed in thehandle 110. - The system can also include a tissue thickness measurement means 138 for measuring a thickness of tissue corresponding to the
tissue surface 106 to be ablated. An imaging modality, such as ultrasound imaging, or other measurement, such as electrical characteristics, can be used to determine the tissue thickness. Tissue thickness measurement is well known in the art, such as that disclosed in U.S. Pat. No. 6,524,250, the entire contents of which is incorporated herein by its reference. InFIG. 1 , theprobe 138 a is meant to schematically illustrate structure, such as an ultrasound transducer, for measuring tissue thickness, such as that disclosed in U.S. Pat. No. 6,524,250. Although the tissue thickness measurement means 138 is shown separate from theinstrument 100, the same can also be integrally formed with theinstrument 100 and may even utilize the radio-frequency electrode(s) 128 and/orultrasonic transducer 112 for such purposes. Furthermore, as discussed below, the mode of operation of theinstrument 100 can depend upon the thickness of the tissue corresponding to thetissue surface 106 to be ablated. Thus, the tissue thickness measurement means 138 may output a value to the user of theinstrument 100 and the user manually select a mode of operation based thereon. Alternatively, the tissue thickness measurement means 138 can automatically input one or both of theultrasonic generator 114 and power source 130 (either directly (shown by dashed lines) or through a common processor-not shown) and control the same to automatically select a mode of operation. - The operation and use of the
instrument 100 andsystem 200 will now be described with regard toFIGS. 1-3 as well asFIGS. 4 a-4 c. Thetissue surface 106 is first accessed by any means known in the art and thesurface 104 of thebody 102 is positioned over thetissue surface 106 to be ablated. The thickness of the tissue corresponding to thetissue surface 106 is then measured either manually by a user or automatically with the tissue thickness measurement means 138. At least one of ultrasonic and radio-frequency energy from theinstrument 100 is then applied to thetissue surface 106 based on the measured thickness. As discussed above, the user may manually select one or both of the ultrasound energy or radio frequency energy throughswitches FIGS. 4 a-4 c, the lesion created by the ultrasonic energy is referred to byreference numeral 142 while the lesion created with radio frequency energy is referred to byreference numeral 140. - As shown in
FIG. 4 a, both the ultrasonic and radio frequency energy can be applied from theinstrument 100 to thetissue surface 106 where the measured tissue thickness is greater than a first predetermined thickness t1. The first predetermined thickness t1 is preferably about 6 mm. In this case the focal spot of the ultrasonic energy is located in the tissue, which leads to most efficient heating of the tissue because heat is conducted to other areas of the tissue from the focal spot. As the tissue is ablated by the ultrasonic energy, it becomes more opaque to ultrasound, heating more on a side of the tissue closer to the ultrasonic transducer. Concurrently energy from the ultrasonic beam is absorbed as it is transmitted through the tissue so the tissue will heat more from the focal point to the transducer and will fill a “wedge-shaped lesion” when a focused ultrasound transducer is used. Preferably, the ultrasonic transducer is in direct contact with the tissue surface. Since the ultrasonic transducer is preferably cooled, it acts as a heat sink on the tissue surface. The tissue in contact with the ultrasonic transducer has a relatively small energy input because the ultrasonic beam is not focused there and the intensity is low. As a result, approximately the last ¼ to ½ mm of tissue on the surface is sometimes not sufficiently ablated. Thus, radio-frequency energy can be applied to ablate the top portion of the tissue (if the surgeon decides that it is necessary). - As shown in
FIG. 4 b, the measured tissue thickness is less than a second predetermined thickness t2. The second predetermined thickness t2 is about 3-5 mm. In this case the tissue is relatively thin and ablating using only ultrasound is not the most efficient because the beam is not focused in the tissue. Therefore, radio-frequency energy is used to speed up the ablation process and also to ablate the upper portion of the tissue, e.g., the upper 0.5 mm of the tissue. However, only the radio-frequency energy may also be used to ablate thin tissue. - As shown in
FIG. 4 c, the measured tissue thickness t3 is between the first predetermined thickness and the second predetermined thickness. Thus, in moderately thick tissue, the focal spot of the ultrasonic energy may still be outside of the tissue, so the efficient heating mechanism discussed above may be missing and the conduction mechanism discussed above is minimized. Therefore, ablation of the tissue can be provided by a somewhat focused ultrasonic beam and radio-frequency energy can be applied to speed up the ablation process. However, in moderately thick tissue, only the ultrasonic energy may be applied to create an efficacious lesion. - Therefore, in all three cases discussed above, ultrasonic energy can be used to create a lesion in tissue, however, the use of radio-frequency energy in combination with the ultrasonic energy provides a good visual indication of the lesion created for the surgeon, both in terms of the location of the lesion and whether there is a gap in the lesion at the tissue surface. The imaging modality or other measurement such as electrical characteristics used for measuring tissue thickness can also be used to determine an extent of the
lesion 142 created by applying the ultrasonic energy. Where the extent of thelesion 142 is determined to be unsatisfactory, the instrument can also apply radio-frequency energy to thetissue surface 106 until it is determined that the extent of the lesion is satisfactory. - While there has been shown and described what is considered to be preferred embodiments of the invention, it will, of course, be understood that various modifications and changes in form or detail could readily be made without departing from the spirit of the invention. It is therefore intended that the invention be not limited to the exact forms described and illustrated, but should be constructed to cover all modifications that may fall within the scope of the appended claims.
Claims (12)
1-12. (canceled)
13. A method for creating lesions in tissue, the method comprising:
providing an instrument capable of selectively directing at least one of ultrasonic and radio-frequency energy to the tissue;
measuring a tissue thickness corresponding to the tissue; and
applying at least one of ultrasonic and radio-frequency energy from the instrument to the tissue based on the measuring.
14. The method of claim 13 , wherein the applying comprises applying the ultrasonic and radio-frequency energy from the instrument to the tissue surface where the measured tissue thickness is greater than a first predetermined thickness.
15. The method of claim 14 , wherein the first predetermined thickness is about 6 mm.
16. The method of claim 14 , wherein the applying comprises applying only the radio-frequency energy from the instrument to the tissue surface where the measured tissue thickness is less than a second predetermined thickness.
17. The method of claim 16 , wherein the second predetermined thickness is about 3-5 mm.
18. The method of claim 16 , wherein the applying comprises applying only the ultrasonic energy from the instrument to the tissue surface where the measured tissue thickness is between the first predetermined thickness and the second predetermined thickness.
19. The method of claim 13 , wherein the ultrasonic energy is supplied by an ultrasonic transducer and the radio-frequency energy is supplied by at least one electrode, the method further comprising cooling at least one of the ultrasonic transducer, the at least one electrode, and the tissue.
20. The method of claim 13 , wherein the ultrasonic energy is first applied to the tissue followed by application of the radio-frequency energy to the tissue where the measured thickness is greater than a predetermined thickness.
21. A method for creating lesions in tissue, the method comprising:
measuring a tissue thickness corresponding to the tissue; and
applying ultrasonic and radio-frequency energy to the tissue surface where the tissue thickness is greater than a predetermined thickness.
22. The method of claim 21 , wherein the applying comprises applying the ultrasonic energy followed by applying the radio-frequency energy.
23. A method for creating lesions in tissue, the method comprising:
measuring a tissue thickness corresponding to the tissue;
applying ultrasonic energy to the tissue surface to create a lesion where the tissue thickness is greater than a predetermined thickness;
determining an extent of the lesion created by the applying of the ultrasonic energy; and
applying radio-frequency energy to the tissue surface where the extent of the lesion is determined to be unsatisfactory.
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US11/444,836 US20060217696A1 (en) | 2003-06-30 | 2006-06-01 | Multi-modality ablation device |
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US10/609,694 US7074218B2 (en) | 2003-06-30 | 2003-06-30 | Multi-modality ablation device |
US11/444,836 US20060217696A1 (en) | 2003-06-30 | 2006-06-01 | Multi-modality ablation device |
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US11/444,836 Abandoned US20060217696A1 (en) | 2003-06-30 | 2006-06-01 | Multi-modality ablation device |
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---|---|---|---|---|
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US20090228003A1 (en) * | 2008-03-04 | 2009-09-10 | Prorhythm, Inc. | Tissue ablation device using radiofrequency and high intensity focused ultrasound |
US20100211060A1 (en) * | 2009-02-13 | 2010-08-19 | Cutera, Inc. | Radio frequency treatment of subcutaneous fat |
US20110218464A1 (en) * | 2010-03-01 | 2011-09-08 | Lumenis Ltd. | System, Device and Methods of Tissue Treatment for Achieving Tissue Specific Effects |
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Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6104959A (en) | 1997-07-31 | 2000-08-15 | Microwave Medical Corp. | Method and apparatus for treating subcutaneous histological features |
US6050943A (en) | 1997-10-14 | 2000-04-18 | Guided Therapy Systems, Inc. | Imaging, therapy, and temperature monitoring ultrasonic system |
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US20050043726A1 (en) * | 2001-03-07 | 2005-02-24 | Mchale Anthony Patrick | Device II |
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US7244257B2 (en) | 2002-11-05 | 2007-07-17 | Sherwood Services Ag | Electrosurgical pencil having a single button variable control |
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US7503917B2 (en) * | 2003-11-20 | 2009-03-17 | Covidien Ag | Electrosurgical pencil with improved controls |
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US20120165668A1 (en) | 2010-08-02 | 2012-06-28 | Guided Therapy Systems, Llc | Systems and methods for treating acute and/or chronic injuries in soft tissue |
US10864385B2 (en) | 2004-09-24 | 2020-12-15 | Guided Therapy Systems, Llc | Rejuvenating skin by heating tissue for cosmetic treatment of the face and body |
US8444562B2 (en) | 2004-10-06 | 2013-05-21 | Guided Therapy Systems, Llc | System and method for treating muscle, tendon, ligament and cartilage tissue |
US7758524B2 (en) | 2004-10-06 | 2010-07-20 | Guided Therapy Systems, L.L.C. | Method and system for ultra-high frequency ultrasound treatment |
US8690779B2 (en) | 2004-10-06 | 2014-04-08 | Guided Therapy Systems, Llc | Noninvasive aesthetic treatment for tightening tissue |
US9827449B2 (en) | 2004-10-06 | 2017-11-28 | Guided Therapy Systems, L.L.C. | Systems for treating skin laxity |
US11235179B2 (en) | 2004-10-06 | 2022-02-01 | Guided Therapy Systems, Llc | Energy based skin gland treatment |
US11883688B2 (en) | 2004-10-06 | 2024-01-30 | Guided Therapy Systems, Llc | Energy based fat reduction |
KR20130080477A (en) | 2004-10-06 | 2013-07-12 | 가이디드 테라피 시스템스, 엘.엘.씨. | System of ultrasound treatment |
US8133180B2 (en) | 2004-10-06 | 2012-03-13 | Guided Therapy Systems, L.L.C. | Method and system for treating cellulite |
US8663112B2 (en) | 2004-10-06 | 2014-03-04 | Guided Therapy Systems, Llc | Methods and systems for fat reduction and/or cellulite treatment |
US9694212B2 (en) | 2004-10-06 | 2017-07-04 | Guided Therapy Systems, Llc | Method and system for ultrasound treatment of skin |
KR101328103B1 (en) | 2004-10-06 | 2013-11-13 | 가이디드 테라피 시스템스, 엘.엘.씨. | Method and system for noninvasive cosmetic enhancement |
US20060111744A1 (en) | 2004-10-13 | 2006-05-25 | Guided Therapy Systems, L.L.C. | Method and system for treatment of sweat glands |
US11724133B2 (en) | 2004-10-07 | 2023-08-15 | Guided Therapy Systems, Llc | Ultrasound probe for treatment of skin |
US11207548B2 (en) | 2004-10-07 | 2021-12-28 | Guided Therapy Systems, L.L.C. | Ultrasound probe for treating skin laxity |
MX2007004151A (en) | 2004-10-08 | 2007-09-11 | Johnson & Johnson | Ultrasonic surgical instrument. |
JP4695188B2 (en) | 2005-04-25 | 2011-06-08 | アーデント サウンド, インコーポレイテッド | Method and apparatus for improving the safety of computer peripherals |
US7500974B2 (en) | 2005-06-28 | 2009-03-10 | Covidien Ag | Electrode with rotatably deployable sheath |
US7828794B2 (en) | 2005-08-25 | 2010-11-09 | Covidien Ag | Handheld electrosurgical apparatus for controlling operating room equipment |
US20070191713A1 (en) | 2005-10-14 | 2007-08-16 | Eichmann Stephen E | Ultrasonic device for cutting and coagulating |
US8167805B2 (en) | 2005-10-20 | 2012-05-01 | Kona Medical, Inc. | Systems and methods for ultrasound applicator station keeping |
US8998890B2 (en) | 2005-12-06 | 2015-04-07 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Assessment of electrode coupling for tissue ablation |
US9492226B2 (en) | 2005-12-06 | 2016-11-15 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Graphical user interface for real-time RF lesion depth display |
US9254163B2 (en) | 2005-12-06 | 2016-02-09 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Assessment of electrode coupling for tissue ablation |
US10362959B2 (en) | 2005-12-06 | 2019-07-30 | St. Jude Medical, Atrial Fibrillation Division, Inc. | System and method for assessing the proximity of an electrode to tissue in a body |
US8603084B2 (en) | 2005-12-06 | 2013-12-10 | St. Jude Medical, Atrial Fibrillation Division, Inc. | System and method for assessing the formation of a lesion in tissue |
US8406866B2 (en) | 2005-12-06 | 2013-03-26 | St. Jude Medical, Atrial Fibrillation Division, Inc. | System and method for assessing coupling between an electrode and tissue |
US8403925B2 (en) | 2006-12-06 | 2013-03-26 | St. Jude Medical, Atrial Fibrillation Division, Inc. | System and method for assessing lesions in tissue |
BRPI0619725A2 (en) | 2005-12-06 | 2011-10-11 | St Jude Medical Atrial Fibrill | tissue ablation electrode junction evaluation |
US7621930B2 (en) | 2006-01-20 | 2009-11-24 | Ethicon Endo-Surgery, Inc. | Ultrasound medical instrument having a medical ultrasonic blade |
US8133191B2 (en) * | 2006-02-16 | 2012-03-13 | Syneron Medical Ltd. | Method and apparatus for treatment of adipose tissue |
US20070260240A1 (en) | 2006-05-05 | 2007-11-08 | Sherwood Services Ag | Soft tissue RF transection and resection device |
US9566454B2 (en) | 2006-09-18 | 2017-02-14 | Guided Therapy Systems, Llc | Method and sysem for non-ablative acne treatment and prevention |
US9241683B2 (en) | 2006-10-04 | 2016-01-26 | Ardent Sound Inc. | Ultrasound system and method for imaging and/or measuring displacement of moving tissue and fluid |
US8057498B2 (en) | 2007-11-30 | 2011-11-15 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instrument blades |
US8142461B2 (en) | 2007-03-22 | 2012-03-27 | Ethicon Endo-Surgery, Inc. | Surgical instruments |
US8911460B2 (en) | 2007-03-22 | 2014-12-16 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments |
US8226675B2 (en) | 2007-03-22 | 2012-07-24 | Ethicon Endo-Surgery, Inc. | Surgical instruments |
WO2008131306A1 (en) | 2007-04-19 | 2008-10-30 | The Foundry, Inc. | Systems and methods for creating an effect using microwave energy to specified tissue |
EP3391844A1 (en) | 2007-04-19 | 2018-10-24 | Miramar Labs, Inc. | Apparatus for reducing sweat production |
EP2767308B1 (en) | 2007-04-19 | 2016-04-13 | Miramar Labs, Inc. | Devices, and systems for non-invasive delivery of microwave therapy |
US9241763B2 (en) | 2007-04-19 | 2016-01-26 | Miramar Labs, Inc. | Systems, apparatus, methods and procedures for the noninvasive treatment of tissue using microwave energy |
US8688228B2 (en) | 2007-04-19 | 2014-04-01 | Miramar Labs, Inc. | Systems, apparatus, methods and procedures for the noninvasive treatment of tissue using microwave energy |
CN101711134B (en) | 2007-04-19 | 2016-08-17 | 米勒玛尔实验室公司 | Tissue is applied the system of microwave energy and in organized layer, produces the system of tissue effect |
US20150174388A1 (en) | 2007-05-07 | 2015-06-25 | Guided Therapy Systems, Llc | Methods and Systems for Ultrasound Assisted Delivery of a Medicant to Tissue |
TWI526233B (en) | 2007-05-07 | 2016-03-21 | 指導治療系統股份有限公司 | Methods and systems for modulating medicants using acoustic energy |
ES2699477T3 (en) | 2007-05-07 | 2019-02-11 | Guided Therapy Systems Llc | Methods and systems for coupling and focusing acoustic energy using a coupling member |
US8702609B2 (en) * | 2007-07-27 | 2014-04-22 | Meridian Cardiovascular Systems, Inc. | Image-guided intravascular therapy catheters |
US8523889B2 (en) | 2007-07-27 | 2013-09-03 | Ethicon Endo-Surgery, Inc. | Ultrasonic end effectors with increased active length |
US8882791B2 (en) | 2007-07-27 | 2014-11-11 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments |
US8808319B2 (en) | 2007-07-27 | 2014-08-19 | Ethicon Endo-Surgery, Inc. | Surgical instruments |
US9044261B2 (en) | 2007-07-31 | 2015-06-02 | Ethicon Endo-Surgery, Inc. | Temperature controlled ultrasonic surgical instruments |
US8430898B2 (en) | 2007-07-31 | 2013-04-30 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments |
US8512365B2 (en) | 2007-07-31 | 2013-08-20 | Ethicon Endo-Surgery, Inc. | Surgical instruments |
US8506565B2 (en) | 2007-08-23 | 2013-08-13 | Covidien Lp | Electrosurgical device with LED adapter |
AU2008308606B2 (en) | 2007-10-05 | 2014-12-18 | Ethicon Endo-Surgery, Inc. | Ergonomic surgical instruments |
US10010339B2 (en) | 2007-11-30 | 2018-07-03 | Ethicon Llc | Ultrasonic surgical blades |
US8425545B2 (en) * | 2007-12-03 | 2013-04-23 | Covidien Ag | Cordless hand-held ultrasonic cautery cutting device and method |
US8663262B2 (en) | 2007-12-03 | 2014-03-04 | Covidien Ag | Battery assembly for battery-powered surgical instruments |
US8338726B2 (en) | 2009-08-26 | 2012-12-25 | Covidien Ag | Two-stage switch for cordless hand-held ultrasonic cautery cutting device |
US9107690B2 (en) | 2007-12-03 | 2015-08-18 | Covidien Ag | Battery-powered hand-held ultrasonic surgical cautery cutting device |
US20090143800A1 (en) * | 2007-12-03 | 2009-06-04 | Derek Dee Deville | Cordless Hand-Held Ultrasonic Cautery Cutting Device |
US8061014B2 (en) | 2007-12-03 | 2011-11-22 | Covidien Ag | Method of assembling a cordless hand-held ultrasonic cautery cutting device |
US9017355B2 (en) | 2007-12-03 | 2015-04-28 | Covidien Ag | Battery-powered hand-held ultrasonic surgical cautery cutting device |
US9314261B2 (en) | 2007-12-03 | 2016-04-19 | Covidien Ag | Battery-powered hand-held ultrasonic surgical cautery cutting device |
US8235987B2 (en) | 2007-12-05 | 2012-08-07 | Tyco Healthcare Group Lp | Thermal penetration and arc length controllable electrosurgical pencil |
ES2471971T3 (en) | 2007-12-12 | 2014-06-27 | Miramar Labs, Inc. | System and apparatus for non-invasive treatment of tissue using microwave energy |
US9204927B2 (en) | 2009-05-13 | 2015-12-08 | St. Jude Medical, Atrial Fibrillation Division, Inc. | System and method for presenting information representative of lesion formation in tissue during an ablation procedure |
US8290578B2 (en) | 2007-12-28 | 2012-10-16 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Method and apparatus for complex impedance compensation |
EP2561819B1 (en) | 2008-01-17 | 2015-01-07 | Syneron Medical Ltd. | Hair removal apparatus for personal use |
WO2009093230A2 (en) | 2008-01-24 | 2009-07-30 | Syneron Medical Ltd. | A device, apparatus, and method of adipose tissue treatment |
WO2010029529A1 (en) * | 2008-09-11 | 2010-03-18 | Syneron Medical Ltd. | A device, apparatus, and method of adipose tissue treatment |
US20120022512A1 (en) * | 2008-01-24 | 2012-01-26 | Boris Vaynberg | Device, apparatus, and method of adipose tissue treatment |
US8636733B2 (en) | 2008-03-31 | 2014-01-28 | Covidien Lp | Electrosurgical pencil including improved controls |
EP2265196B9 (en) | 2008-03-31 | 2013-10-02 | Applied Medical Resources Corporation | Electrosurgical system with means for measuring permittivity and conductivity of tissue |
US8597292B2 (en) | 2008-03-31 | 2013-12-03 | Covidien Lp | Electrosurgical pencil including improved controls |
US8632536B2 (en) | 2008-03-31 | 2014-01-21 | Covidien Lp | Electrosurgical pencil including improved controls |
US8133222B2 (en) * | 2008-05-28 | 2012-03-13 | Medwaves, Inc. | Tissue ablation apparatus and method using ultrasonic imaging |
CA3206234A1 (en) | 2008-06-06 | 2009-12-10 | Ulthera, Inc. | A system and method for cosmetic treatment and imaging |
US8162937B2 (en) | 2008-06-27 | 2012-04-24 | Tyco Healthcare Group Lp | High volume fluid seal for electrosurgical handpiece |
US9314293B2 (en) | 2008-07-16 | 2016-04-19 | Syneron Medical Ltd | RF electrode for aesthetic and body shaping devices and method of using same |
US20100017750A1 (en) | 2008-07-16 | 2010-01-21 | Avner Rosenberg | User interface |
US9089360B2 (en) | 2008-08-06 | 2015-07-28 | Ethicon Endo-Surgery, Inc. | Devices and techniques for cutting and coagulating tissue |
WO2010032235A1 (en) | 2008-09-21 | 2010-03-25 | Syneron Medical Ltd. | A method and apparatus for personal skin treatment |
US8231620B2 (en) | 2009-02-10 | 2012-07-31 | Tyco Healthcare Group Lp | Extension cutting blade |
US9278230B2 (en) | 2009-02-25 | 2016-03-08 | Syneron Medical Ltd | Electrical skin rejuvenation |
US9700339B2 (en) | 2009-05-20 | 2017-07-11 | Ethicon Endo-Surgery, Inc. | Coupling arrangements and methods for attaching tools to ultrasonic surgical instruments |
US8334635B2 (en) | 2009-06-24 | 2012-12-18 | Ethicon Endo-Surgery, Inc. | Transducer arrangements for ultrasonic surgical instruments |
US8663220B2 (en) | 2009-07-15 | 2014-03-04 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments |
US9168054B2 (en) | 2009-10-09 | 2015-10-27 | Ethicon Endo-Surgery, Inc. | Surgical generator for ultrasonic and electrosurgical devices |
US10441345B2 (en) | 2009-10-09 | 2019-10-15 | Ethicon Llc | Surgical generator for ultrasonic and electrosurgical devices |
USRE47996E1 (en) | 2009-10-09 | 2020-05-19 | Ethicon Llc | Surgical generator for ultrasonic and electrosurgical devices |
US8951248B2 (en) | 2009-10-09 | 2015-02-10 | Ethicon Endo-Surgery, Inc. | Surgical generator for ultrasonic and electrosurgical devices |
US11090104B2 (en) | 2009-10-09 | 2021-08-17 | Cilag Gmbh International | Surgical generator for ultrasonic and electrosurgical devices |
US8986231B2 (en) | 2009-10-12 | 2015-03-24 | Kona Medical, Inc. | Energetic modulation of nerves |
US20110092880A1 (en) | 2009-10-12 | 2011-04-21 | Michael Gertner | Energetic modulation of nerves |
US8469904B2 (en) | 2009-10-12 | 2013-06-25 | Kona Medical, Inc. | Energetic modulation of nerves |
US9174065B2 (en) | 2009-10-12 | 2015-11-03 | Kona Medical, Inc. | Energetic modulation of nerves |
US8517962B2 (en) | 2009-10-12 | 2013-08-27 | Kona Medical, Inc. | Energetic modulation of nerves |
US20160059044A1 (en) | 2009-10-12 | 2016-03-03 | Kona Medical, Inc. | Energy delivery to intraparenchymal regions of the kidney to treat hypertension |
US8295912B2 (en) | 2009-10-12 | 2012-10-23 | Kona Medical, Inc. | Method and system to inhibit a function of a nerve traveling with an artery |
US8986211B2 (en) | 2009-10-12 | 2015-03-24 | Kona Medical, Inc. | Energetic modulation of nerves |
US20110118600A1 (en) | 2009-11-16 | 2011-05-19 | Michael Gertner | External Autonomic Modulation |
US9119951B2 (en) | 2009-10-12 | 2015-09-01 | Kona Medical, Inc. | Energetic modulation of nerves |
WO2011046879A1 (en) * | 2009-10-12 | 2011-04-21 | Kona Medical, Inc. | Energetic modulation of nerves |
US8715186B2 (en) | 2009-11-24 | 2014-05-06 | Guided Therapy Systems, Llc | Methods and systems for generating thermal bubbles for improved ultrasound imaging and therapy |
US20110196438A1 (en) * | 2010-02-10 | 2011-08-11 | Lukas Mnozil | Therapy device and method for treating underlying tissue using electrical and acoustic energies |
US8579928B2 (en) | 2010-02-11 | 2013-11-12 | Ethicon Endo-Surgery, Inc. | Outer sheath and blade arrangements for ultrasonic surgical instruments |
US8961547B2 (en) | 2010-02-11 | 2015-02-24 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments with moving cutting implement |
US8469981B2 (en) | 2010-02-11 | 2013-06-25 | Ethicon Endo-Surgery, Inc. | Rotatable cutting implement arrangements for ultrasonic surgical instruments |
US8951272B2 (en) | 2010-02-11 | 2015-02-10 | Ethicon Endo-Surgery, Inc. | Seal arrangements for ultrasonically powered surgical instruments |
US8486096B2 (en) | 2010-02-11 | 2013-07-16 | Ethicon Endo-Surgery, Inc. | Dual purpose surgical instrument for cutting and coagulating tissue |
GB2480498A (en) | 2010-05-21 | 2011-11-23 | Ethicon Endo Surgery Inc | Medical device comprising RF circuitry |
US8795327B2 (en) | 2010-07-22 | 2014-08-05 | Ethicon Endo-Surgery, Inc. | Electrosurgical instrument with separate closure and cutting members |
US9192431B2 (en) | 2010-07-23 | 2015-11-24 | Ethicon Endo-Surgery, Inc. | Electrosurgical cutting and sealing instrument |
US9504446B2 (en) | 2010-08-02 | 2016-11-29 | Guided Therapy Systems, Llc | Systems and methods for coupling an ultrasound source to tissue |
EP2621389B1 (en) | 2010-10-01 | 2015-03-18 | Applied Medical Resources Corporation | Electrosurgical instrument with jaws and with an electrode |
US8857438B2 (en) | 2010-11-08 | 2014-10-14 | Ulthera, Inc. | Devices and methods for acoustic shielding |
WO2012156944A1 (en) * | 2011-05-19 | 2012-11-22 | Alma Lasers Ltd. | Apparatus for concurrent treatment with thermal and ultrasonic energy |
WO2013009784A2 (en) | 2011-07-10 | 2013-01-17 | Guided Therapy Systems, Llc | Systems and method for accelerating healing of implanted material and/or native tissue |
WO2013012641A1 (en) | 2011-07-11 | 2013-01-24 | Guided Therapy Systems, Llc | Systems and methods for coupling an ultrasound source to tissue |
US9259265B2 (en) | 2011-07-22 | 2016-02-16 | Ethicon Endo-Surgery, Llc | Surgical instruments for tensioning tissue |
US9314301B2 (en) | 2011-08-01 | 2016-04-19 | Miramar Labs, Inc. | Applicator and tissue interface module for dermatological device |
EP2564894B1 (en) * | 2011-09-05 | 2015-11-18 | Venus Concept Ltd | A device for cosmetic improvement of the skin |
EP2811932B1 (en) | 2012-02-10 | 2019-06-26 | Ethicon LLC | Robotically controlled surgical instrument |
US9439668B2 (en) | 2012-04-09 | 2016-09-13 | Ethicon Endo-Surgery, Llc | Switch arrangements for ultrasonic surgical instruments |
US9237921B2 (en) | 2012-04-09 | 2016-01-19 | Ethicon Endo-Surgery, Inc. | Devices and techniques for cutting and coagulating tissue |
US9241731B2 (en) | 2012-04-09 | 2016-01-26 | Ethicon Endo-Surgery, Inc. | Rotatable electrical connection for ultrasonic surgical instruments |
US9724118B2 (en) | 2012-04-09 | 2017-08-08 | Ethicon Endo-Surgery, Llc | Techniques for cutting and coagulating tissue for ultrasonic surgical instruments |
US9226766B2 (en) | 2012-04-09 | 2016-01-05 | Ethicon Endo-Surgery, Inc. | Serial communication protocol for medical device |
US9263663B2 (en) | 2012-04-13 | 2016-02-16 | Ardent Sound, Inc. | Method of making thick film transducer arrays |
US20140005705A1 (en) | 2012-06-29 | 2014-01-02 | Ethicon Endo-Surgery, Inc. | Surgical instruments with articulating shafts |
US9393037B2 (en) | 2012-06-29 | 2016-07-19 | Ethicon Endo-Surgery, Llc | Surgical instruments with articulating shafts |
US9326788B2 (en) | 2012-06-29 | 2016-05-03 | Ethicon Endo-Surgery, Llc | Lockout mechanism for use with robotic electrosurgical device |
US9351754B2 (en) | 2012-06-29 | 2016-05-31 | Ethicon Endo-Surgery, Llc | Ultrasonic surgical instruments with distally positioned jaw assemblies |
US9408622B2 (en) | 2012-06-29 | 2016-08-09 | Ethicon Endo-Surgery, Llc | Surgical instruments with articulating shafts |
US9198714B2 (en) | 2012-06-29 | 2015-12-01 | Ethicon Endo-Surgery, Inc. | Haptic feedback devices for surgical robot |
US9226767B2 (en) | 2012-06-29 | 2016-01-05 | Ethicon Endo-Surgery, Inc. | Closed feedback control for electrosurgical device |
US9283045B2 (en) | 2012-06-29 | 2016-03-15 | Ethicon Endo-Surgery, Llc | Surgical instruments with fluid management system |
US9820768B2 (en) | 2012-06-29 | 2017-11-21 | Ethicon Llc | Ultrasonic surgical instruments with control mechanisms |
US20140005702A1 (en) | 2012-06-29 | 2014-01-02 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments with distally positioned transducers |
US9510802B2 (en) | 2012-09-21 | 2016-12-06 | Guided Therapy Systems, Llc | Reflective ultrasound technology for dermatological treatments |
US9492224B2 (en) | 2012-09-28 | 2016-11-15 | EthiconEndo-Surgery, LLC | Multi-function bi-polar forceps |
US10201365B2 (en) | 2012-10-22 | 2019-02-12 | Ethicon Llc | Surgeon feedback sensing and display methods |
US9095367B2 (en) | 2012-10-22 | 2015-08-04 | Ethicon Endo-Surgery, Inc. | Flexible harmonic waveguides/blades for surgical instruments |
US20140135804A1 (en) | 2012-11-15 | 2014-05-15 | Ethicon Endo-Surgery, Inc. | Ultrasonic and electrosurgical devices |
CN204017181U (en) | 2013-03-08 | 2014-12-17 | 奥赛拉公司 | Aesthstic imaging and processing system, multifocal processing system and perform the system of aesthetic procedure |
US10226273B2 (en) | 2013-03-14 | 2019-03-12 | Ethicon Llc | Mechanical fasteners for use with surgical energy devices |
US9241728B2 (en) | 2013-03-15 | 2016-01-26 | Ethicon Endo-Surgery, Inc. | Surgical instrument with multiple clamping mechanisms |
WO2014146022A2 (en) | 2013-03-15 | 2014-09-18 | Guided Therapy Systems Llc | Ultrasound treatment device and methods of use |
US10779885B2 (en) | 2013-07-24 | 2020-09-22 | Miradry. Inc. | Apparatus and methods for the treatment of tissue using microwave energy |
US9814514B2 (en) | 2013-09-13 | 2017-11-14 | Ethicon Llc | Electrosurgical (RF) medical instruments for cutting and coagulating tissue |
US9265926B2 (en) | 2013-11-08 | 2016-02-23 | Ethicon Endo-Surgery, Llc | Electrosurgical devices |
GB2521228A (en) | 2013-12-16 | 2015-06-17 | Ethicon Endo Surgery Inc | Medical device |
GB2521229A (en) | 2013-12-16 | 2015-06-17 | Ethicon Endo Surgery Inc | Medical device |
US9795436B2 (en) | 2014-01-07 | 2017-10-24 | Ethicon Llc | Harvesting energy from a surgical generator |
US9554854B2 (en) | 2014-03-18 | 2017-01-31 | Ethicon Endo-Surgery, Llc | Detecting short circuits in electrosurgical medical devices |
US10092310B2 (en) | 2014-03-27 | 2018-10-09 | Ethicon Llc | Electrosurgical devices |
US10463421B2 (en) | 2014-03-27 | 2019-11-05 | Ethicon Llc | Two stage trigger, clamp and cut bipolar vessel sealer |
US9737355B2 (en) | 2014-03-31 | 2017-08-22 | Ethicon Llc | Controlling impedance rise in electrosurgical medical devices |
US9913680B2 (en) | 2014-04-15 | 2018-03-13 | Ethicon Llc | Software algorithms for electrosurgical instruments |
WO2015160708A1 (en) | 2014-04-18 | 2015-10-22 | Ulthera, Inc. | Band transducer ultrasound therapy |
AU2015258819B2 (en) | 2014-05-16 | 2019-12-12 | Applied Medical Resources Corporation | Electrosurgical system |
EP3369392A1 (en) | 2014-05-30 | 2018-09-05 | Applied Medical Resources Corporation | Electrosurgical seal and dissection systems |
US10285724B2 (en) | 2014-07-31 | 2019-05-14 | Ethicon Llc | Actuation mechanisms and load adjustment assemblies for surgical instruments |
US10925579B2 (en) | 2014-11-05 | 2021-02-23 | Otsuka Medical Devices Co., Ltd. | Systems and methods for real-time tracking of a target tissue using imaging before and during therapy delivery |
US10639092B2 (en) | 2014-12-08 | 2020-05-05 | Ethicon Llc | Electrode configurations for surgical instruments |
US10420603B2 (en) | 2014-12-23 | 2019-09-24 | Applied Medical Resources Corporation | Bipolar electrosurgical sealer and divider |
USD748259S1 (en) | 2014-12-29 | 2016-01-26 | Applied Medical Resources Corporation | Electrosurgical instrument |
US10245095B2 (en) | 2015-02-06 | 2019-04-02 | Ethicon Llc | Electrosurgical instrument with rotation and articulation mechanisms |
US10321950B2 (en) | 2015-03-17 | 2019-06-18 | Ethicon Llc | Managing tissue treatment |
US10342602B2 (en) | 2015-03-17 | 2019-07-09 | Ethicon Llc | Managing tissue treatment |
US10595929B2 (en) | 2015-03-24 | 2020-03-24 | Ethicon Llc | Surgical instruments with firing system overload protection mechanisms |
US10034684B2 (en) | 2015-06-15 | 2018-07-31 | Ethicon Llc | Apparatus and method for dissecting and coagulating tissue |
US11020140B2 (en) | 2015-06-17 | 2021-06-01 | Cilag Gmbh International | Ultrasonic surgical blade for use with ultrasonic surgical instruments |
US10898256B2 (en) | 2015-06-30 | 2021-01-26 | Ethicon Llc | Surgical system with user adaptable techniques based on tissue impedance |
US11051873B2 (en) | 2015-06-30 | 2021-07-06 | Cilag Gmbh International | Surgical system with user adaptable techniques employing multiple energy modalities based on tissue parameters |
US11129669B2 (en) | 2015-06-30 | 2021-09-28 | Cilag Gmbh International | Surgical system with user adaptable techniques based on tissue type |
US10034704B2 (en) | 2015-06-30 | 2018-07-31 | Ethicon Llc | Surgical instrument with user adaptable algorithms |
US10357303B2 (en) | 2015-06-30 | 2019-07-23 | Ethicon Llc | Translatable outer tube for sealing using shielded lap chole dissector |
US10765470B2 (en) | 2015-06-30 | 2020-09-08 | Ethicon Llc | Surgical system with user adaptable techniques employing simultaneous energy modalities based on tissue parameters |
US10154852B2 (en) | 2015-07-01 | 2018-12-18 | Ethicon Llc | Ultrasonic surgical blade with improved cutting and coagulation features |
US10687884B2 (en) | 2015-09-30 | 2020-06-23 | Ethicon Llc | Circuits for supplying isolated direct current (DC) voltage to surgical instruments |
US10595930B2 (en) | 2015-10-16 | 2020-03-24 | Ethicon Llc | Electrode wiping surgical device |
US10179022B2 (en) | 2015-12-30 | 2019-01-15 | Ethicon Llc | Jaw position impedance limiter for electrosurgical instrument |
US10575892B2 (en) | 2015-12-31 | 2020-03-03 | Ethicon Llc | Adapter for electrical surgical instruments |
US10716615B2 (en) | 2016-01-15 | 2020-07-21 | Ethicon Llc | Modular battery powered handheld surgical instrument with curved end effectors having asymmetric engagement between jaw and blade |
US11229471B2 (en) | 2016-01-15 | 2022-01-25 | Cilag Gmbh International | Modular battery powered handheld surgical instrument with selective application of energy based on tissue characterization |
US11129670B2 (en) | 2016-01-15 | 2021-09-28 | Cilag Gmbh International | Modular battery powered handheld surgical instrument with selective application of energy based on button displacement, intensity, or local tissue characterization |
US10251664B2 (en) | 2016-01-15 | 2019-04-09 | Ethicon Llc | Modular battery powered handheld surgical instrument with multi-function motor via shifting gear assembly |
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US10555769B2 (en) | 2016-02-22 | 2020-02-11 | Ethicon Llc | Flexible circuits for electrosurgical instrument |
US10702329B2 (en) | 2016-04-29 | 2020-07-07 | Ethicon Llc | Jaw structure with distal post for electrosurgical instruments |
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AU2017278615B2 (en) | 2016-06-06 | 2022-06-16 | Sofwave Medical Ltd. | Ultrasound transducer and system |
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US10603064B2 (en) | 2016-11-28 | 2020-03-31 | Ethicon Llc | Ultrasonic transducer |
US11266430B2 (en) | 2016-11-29 | 2022-03-08 | Cilag Gmbh International | End effector control and calibration |
AU2018257642B2 (en) | 2017-04-28 | 2024-03-21 | Stryker Corporation | Control console and accessories for RF nerve ablation and methods of operating the same |
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US20190059978A1 (en) * | 2017-08-29 | 2019-02-28 | Sea-Quan Su | Non-invasive radio-frequency ablation system |
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WO2019164836A1 (en) | 2018-02-20 | 2019-08-29 | Ulthera, Inc. | Systems and methods for combined cosmetic treatment of cellulite with ultrasound |
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US11779329B2 (en) | 2019-12-30 | 2023-10-10 | Cilag Gmbh International | Surgical instrument comprising a flex circuit including a sensor system |
US11911063B2 (en) | 2019-12-30 | 2024-02-27 | Cilag Gmbh International | Techniques for detecting ultrasonic blade to electrode contact and reducing power to ultrasonic blade |
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US11779387B2 (en) | 2019-12-30 | 2023-10-10 | Cilag Gmbh International | Clamp arm jaw to minimize tissue sticking and improve tissue control |
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US11786291B2 (en) | 2019-12-30 | 2023-10-17 | Cilag Gmbh International | Deflectable support of RF energy electrode with respect to opposing ultrasonic blade |
US11660089B2 (en) | 2019-12-30 | 2023-05-30 | Cilag Gmbh International | Surgical instrument comprising a sensing system |
US11937863B2 (en) | 2019-12-30 | 2024-03-26 | Cilag Gmbh International | Deflectable electrode with variable compression bias along the length of the deflectable electrode |
US11937866B2 (en) | 2019-12-30 | 2024-03-26 | Cilag Gmbh International | Method for an electrosurgical procedure |
US20220117623A1 (en) | 2020-10-15 | 2022-04-21 | Covidien Lp | Ultrasonic surgical instrument |
US11717312B2 (en) | 2021-10-01 | 2023-08-08 | Covidien Lp | Surgical system including blade visualization markings |
Citations (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4936281A (en) * | 1989-04-13 | 1990-06-26 | Everest Medical Corporation | Ultrasonically enhanced RF ablation catheter |
US5013312A (en) * | 1990-03-19 | 1991-05-07 | Everest Medical Corporation | Bipolar scalpel for harvesting internal mammary artery |
US5282799A (en) * | 1990-08-24 | 1994-02-01 | Everest Medical Corporation | Bipolar electrosurgical scalpel with paired loop electrodes |
US5295494A (en) * | 1991-05-17 | 1994-03-22 | Rodriguez Andres C | Support for a therapeutic magnet |
US5893848A (en) * | 1996-10-24 | 1999-04-13 | Plc Medical Systems, Inc. | Gauging system for monitoring channel depth in percutaneous endocardial revascularization |
US6032674A (en) * | 1992-01-07 | 2000-03-07 | Arthrocare Corporation | Systems and methods for myocardial revascularization |
US6235024B1 (en) * | 1999-06-21 | 2001-05-22 | Hosheng Tu | Catheters system having dual ablation capability |
US20040116921A1 (en) * | 2002-12-11 | 2004-06-17 | Marshall Sherman | Cold tip rf/ultrasonic ablation catheter |
US7226448B2 (en) * | 2001-12-04 | 2007-06-05 | Estech, Inc. (Endoscopic Technologies, Inc.) | Cardiac treatment devices and methods |
Family Cites Families (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
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 |
US6229153B1 (en) * | 1996-06-21 | 2001-05-08 | Wisconsin Alumni Research Corporation | High peak current density resonant tunneling diode |
-
2003
- 2003-06-30 US US10/609,694 patent/US7074218B2/en not_active Expired - Lifetime
-
2006
- 2006-06-01 US US11/444,836 patent/US20060217696A1/en not_active Abandoned
Patent Citations (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4936281A (en) * | 1989-04-13 | 1990-06-26 | Everest Medical Corporation | Ultrasonically enhanced RF ablation catheter |
US5013312A (en) * | 1990-03-19 | 1991-05-07 | Everest Medical Corporation | Bipolar scalpel for harvesting internal mammary artery |
US5282799A (en) * | 1990-08-24 | 1994-02-01 | Everest Medical Corporation | Bipolar electrosurgical scalpel with paired loop electrodes |
US5295494A (en) * | 1991-05-17 | 1994-03-22 | Rodriguez Andres C | Support for a therapeutic magnet |
US6032674A (en) * | 1992-01-07 | 2000-03-07 | Arthrocare Corporation | Systems and methods for myocardial revascularization |
US5893848A (en) * | 1996-10-24 | 1999-04-13 | Plc Medical Systems, Inc. | Gauging system for monitoring channel depth in percutaneous endocardial revascularization |
US6235024B1 (en) * | 1999-06-21 | 2001-05-22 | Hosheng Tu | Catheters system having dual ablation capability |
US7226448B2 (en) * | 2001-12-04 | 2007-06-05 | Estech, Inc. (Endoscopic Technologies, Inc.) | Cardiac treatment devices and methods |
US20040116921A1 (en) * | 2002-12-11 | 2004-06-17 | Marshall Sherman | Cold tip rf/ultrasonic ablation catheter |
Cited By (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2007013072A1 (en) | 2005-07-26 | 2007-02-01 | Syneron Medical Ltd. | Method and apparatus for treatment of skin using rf and ultrasound energies |
US20090228003A1 (en) * | 2008-03-04 | 2009-09-10 | Prorhythm, Inc. | Tissue ablation device using radiofrequency and high intensity focused ultrasound |
US20100211060A1 (en) * | 2009-02-13 | 2010-08-19 | Cutera, Inc. | Radio frequency treatment of subcutaneous fat |
US20110218464A1 (en) * | 2010-03-01 | 2011-09-08 | Lumenis Ltd. | System, Device and Methods of Tissue Treatment for Achieving Tissue Specific Effects |
WO2011107885A3 (en) * | 2010-03-01 | 2011-12-01 | Yoni Iger | System, device and methods of tissue treatment for achieving tissue specific effects |
US10006804B2 (en) | 2013-05-09 | 2018-06-26 | Reach Surgical Inc. | Method and system for searching for resonant frequency of transducer |
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US20040267252A1 (en) | 2004-12-30 |
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