CA2488870A1 - Catheter balloon with ultrasonic microscalpel blades - Google Patents
Catheter balloon with ultrasonic microscalpel blades Download PDFInfo
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- CA2488870A1 CA2488870A1 CA002488870A CA2488870A CA2488870A1 CA 2488870 A1 CA2488870 A1 CA 2488870A1 CA 002488870 A CA002488870 A CA 002488870A CA 2488870 A CA2488870 A CA 2488870A CA 2488870 A1 CA2488870 A1 CA 2488870A1
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- Prior art keywords
- balloon
- microscalpel
- cutting
- catheter
- operatively disposed
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/32—Surgical cutting instruments
- A61B17/3205—Excision instruments
- A61B17/3207—Atherectomy devices working by cutting or abrading; Similar devices specially adapted for non-vascular obstructions
- A61B17/320725—Atherectomy devices working by cutting or abrading; Similar devices specially adapted for non-vascular obstructions with radially expandable cutting or abrading elements
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/22—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
- A61B17/22004—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for using mechanical vibrations, e.g. ultrasonic shock waves
- A61B17/22012—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for using mechanical vibrations, e.g. ultrasonic shock waves in direct contact with, or very close to, the obstruction or concrement
- A61B17/2202—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for using mechanical vibrations, e.g. ultrasonic shock waves in direct contact with, or very close to, the obstruction or concrement the ultrasound transducer being inside patient's body at the distal end of the catheter
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/22—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
- A61B2017/22051—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an inflatable part, e.g. balloon, for positioning, blocking, or immobilisation
- A61B2017/22061—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an inflatable part, e.g. balloon, for positioning, blocking, or immobilisation for spreading elements apart
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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
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00214—Expandable means emitting energy, e.g. by elements carried thereon
- A61B2018/0022—Balloons
Abstract
The present invention provides a catheter balloon, and balloon catheter incorporating the catheter balloon, useful in medical dilation procedures. The catheter balloon includes at least one microscalpel operatively disposed on an outer surface thereof. The microscalpel may advantageously be operatively disposed relative to a power source so as to be controllably activatable. Also provided are methods of making the inventive balloon and/or catheter as well as methods of using the inventive catheter in a dilation/incising treatment.
Description
CATHETER BALLOON WITH ULTRASONIC MICROSCALPEL BLADES
Field of the invention The present invention pertains generally to catheter balloons useful in medical dilation. More specifically, the present invention relates to catheter balloons having microscalpel blades operatively disposed relative thereto, which blades may advantageously be provided with controllable ultrasonic energy, if desired.
Background of the Invention Angioplasty is a widely utilized therapeutic treatment in which obstructed intraluminal spaces are reopened or dilated. In a typical procedure, a catheter comprising an inflatable member, such as a balloon, is inserted percutaneously into the patient's luminal passage, such as an arterial passage. Once inserted, the balloon is advanced to the desired treatment site, where the balloon may be inflated to dilate the luminal passage.
Although vascular angioplasty is a widely utilized and largely successful procedure, the procedure can cause collateral trauma to the vessel wall. That is, in order to dilate the area of obstruction, pressure is typically applied, which pressure is realized at the vessel wall. The applied pressure can result in the stretching, or irregular intimal tearing, of layers of the vessel wall, which in turn, can result in restenosis of the treatment site. Any such restenosis that occurs may require further treatment, an outcome that would desirably be avoided.
In order to avoid, or minimize the possibility of such an outcome, devices have been developed that purport to reduce the pressure applied, as well as any potentially resulting collateral damage to the vessel wall. For example, balloons incorporating cutting blades have been provided in conjunction with angioplasty catheters. These cutting balloons, when dilated within a stenosis, provide regular, controlled incisions in the stenosis. It is thought that, unlike irregular intimal tearing, these regular incisions can act to disperse the pressure that otherwise would be realized outwardly at the vessel wall radially about the treatment site, thereby
Field of the invention The present invention pertains generally to catheter balloons useful in medical dilation. More specifically, the present invention relates to catheter balloons having microscalpel blades operatively disposed relative thereto, which blades may advantageously be provided with controllable ultrasonic energy, if desired.
Background of the Invention Angioplasty is a widely utilized therapeutic treatment in which obstructed intraluminal spaces are reopened or dilated. In a typical procedure, a catheter comprising an inflatable member, such as a balloon, is inserted percutaneously into the patient's luminal passage, such as an arterial passage. Once inserted, the balloon is advanced to the desired treatment site, where the balloon may be inflated to dilate the luminal passage.
Although vascular angioplasty is a widely utilized and largely successful procedure, the procedure can cause collateral trauma to the vessel wall. That is, in order to dilate the area of obstruction, pressure is typically applied, which pressure is realized at the vessel wall. The applied pressure can result in the stretching, or irregular intimal tearing, of layers of the vessel wall, which in turn, can result in restenosis of the treatment site. Any such restenosis that occurs may require further treatment, an outcome that would desirably be avoided.
In order to avoid, or minimize the possibility of such an outcome, devices have been developed that purport to reduce the pressure applied, as well as any potentially resulting collateral damage to the vessel wall. For example, balloons incorporating cutting blades have been provided in conjunction with angioplasty catheters. These cutting balloons, when dilated within a stenosis, provide regular, controlled incisions in the stenosis. It is thought that, unlike irregular intimal tearing, these regular incisions can act to disperse the pressure that otherwise would be realized outwardly at the vessel wall radially about the treatment site, thereby
-2-reducing damage to the vessel wall. Although such cutting balloon angioplasty procedures are widely utilized and largely successful procedures, improvements to the same could yet be made.
For example, in some applications, it may be desirable to enhance the precision of the incisions that can be made in a stenosis. Enhanced precision would be advantageous, for example, as it is believed that the sharper and cleaner the cuts provided in a stenosis, the greater the reduction in restenotic response that will be seen. Enhanced precision in the depth of the incision provided would be advantageous as well, inasmuch as such depth precision currently can be difficult to attain, in particular when such cutting elements are provided in conjunction with a compliant balloon.
Summary of the Invention The present invention is generally directed to cutting balloons having at least one microscalpel blade operatively disposed relative thereto. In certain embodiments, the microscalpel may be operatively disposed relative to a power source, preferably a source of ultrasonic energy. Advantageously, the ultrasonic microscalpels, because of their small size and/or the provision of ultrasonic energy thereto, are capable of creating much sharper and cleaner incisions in a stenosis than conventional cutting blades. The ability to selectively activate, deactivate, pulse, or otherwise vary, the source of energy further enhances the cutting precision of the microscalpels and thus, balloon. As a result, the inventive cutting balloons can be used to incise stenosis at lower dilatation pressures, or to incise stenosis that are difficult to incise utilizing other conventional cutting balloons. Trauma to the vessel wall, as well as any subsequent restenosis that can result therefrom, can thus be reduced.
In one aspect then, the present invention provides a dilatation balloon and balloon catheter. Generally, the dilation balloon includes a balloon body having an outer surface and at least one microscalpel operatively disposed on the outer surface of the balloon body. The microscalpel may advantageously be activatable by a source of power, preferable a source of ultrasonic energy. A balloon catheter embodying features of the present invention generally includes the inventive balloon further having an interior, as well as an elongated catheter shaft having a proximal
For example, in some applications, it may be desirable to enhance the precision of the incisions that can be made in a stenosis. Enhanced precision would be advantageous, for example, as it is believed that the sharper and cleaner the cuts provided in a stenosis, the greater the reduction in restenotic response that will be seen. Enhanced precision in the depth of the incision provided would be advantageous as well, inasmuch as such depth precision currently can be difficult to attain, in particular when such cutting elements are provided in conjunction with a compliant balloon.
Summary of the Invention The present invention is generally directed to cutting balloons having at least one microscalpel blade operatively disposed relative thereto. In certain embodiments, the microscalpel may be operatively disposed relative to a power source, preferably a source of ultrasonic energy. Advantageously, the ultrasonic microscalpels, because of their small size and/or the provision of ultrasonic energy thereto, are capable of creating much sharper and cleaner incisions in a stenosis than conventional cutting blades. The ability to selectively activate, deactivate, pulse, or otherwise vary, the source of energy further enhances the cutting precision of the microscalpels and thus, balloon. As a result, the inventive cutting balloons can be used to incise stenosis at lower dilatation pressures, or to incise stenosis that are difficult to incise utilizing other conventional cutting balloons. Trauma to the vessel wall, as well as any subsequent restenosis that can result therefrom, can thus be reduced.
In one aspect then, the present invention provides a dilatation balloon and balloon catheter. Generally, the dilation balloon includes a balloon body having an outer surface and at least one microscalpel operatively disposed on the outer surface of the balloon body. The microscalpel may advantageously be activatable by a source of power, preferable a source of ultrasonic energy. A balloon catheter embodying features of the present invention generally includes the inventive balloon further having an interior, as well as an elongated catheter shaft having a proximal
-3-end, a distal end and an inflation lumen of the catheter shaft extending through at least a portion thereof. The balloon is mounted near the distal end of the catheter shaft so that the inflation lumen is in fluid communication with the interior of the balloon.
Inasmuch as the present invention is based, at least in part, upon the recognition of the advantages that may be attained by the provision of microscalpels smaller than conventional cutting elements on the surface of a cutting balloon, and the further advantages that can be seen when the microscalpels are ultrasonically activatable, the type of balloon and/or catheter, the materials(s) used to manufacture the same, and the configuration of the same once assembled, is not critical.
Rather, the inventive cutting balloon catheters can be provided by utilizing any material, or combination of materials, may be coated or uncoated, cross-linked or uncrosslinked, etc., so long as the balloon has provided thereon at least one microscalpel.
In fact, and due at least in part to the fact that microscalpels can be much sharper than conventional cutting elements, a broader range of materials is suitable for use in the inventive cutting balloon than is appropriate for use in conventional cutting balloons.
In another aspect, the present invention provides a method for producing a balloon catheter. Generally speaking, the method involves the steps of providing a cutting dilation balloon, having an interior and an outer surface having operatively disposed relative thereto at least one microscalpel. In certain embodiments, the microscalpel is desirably controllably ultrasonically activatable. A catheter shaft is also provided having a distal end, a proximal end, and an inflation lumen extending through at least a portion thereof. The cutting balloon is then mounted on the catheter so that the inflation lumen of the catheter shaft is in fluid communication with the balloon interior.
The inventive balloon and balloon catheter can be utilized to dilate a stenosis while doing so at a generally lower dilatation pressure and/or in manner that results in less trauma to the vessel wall. As a result, a reduction in any restenosis that might otherwise occur can be seen. Thus, in yet another aspect of the present invention, a method for incising and/or dilating a stenosis is provided. Generally, the method involves providing balloon catheter having a catheter shaft having a lumen in fluid
Inasmuch as the present invention is based, at least in part, upon the recognition of the advantages that may be attained by the provision of microscalpels smaller than conventional cutting elements on the surface of a cutting balloon, and the further advantages that can be seen when the microscalpels are ultrasonically activatable, the type of balloon and/or catheter, the materials(s) used to manufacture the same, and the configuration of the same once assembled, is not critical.
Rather, the inventive cutting balloon catheters can be provided by utilizing any material, or combination of materials, may be coated or uncoated, cross-linked or uncrosslinked, etc., so long as the balloon has provided thereon at least one microscalpel.
In fact, and due at least in part to the fact that microscalpels can be much sharper than conventional cutting elements, a broader range of materials is suitable for use in the inventive cutting balloon than is appropriate for use in conventional cutting balloons.
In another aspect, the present invention provides a method for producing a balloon catheter. Generally speaking, the method involves the steps of providing a cutting dilation balloon, having an interior and an outer surface having operatively disposed relative thereto at least one microscalpel. In certain embodiments, the microscalpel is desirably controllably ultrasonically activatable. A catheter shaft is also provided having a distal end, a proximal end, and an inflation lumen extending through at least a portion thereof. The cutting balloon is then mounted on the catheter so that the inflation lumen of the catheter shaft is in fluid communication with the balloon interior.
The inventive balloon and balloon catheter can be utilized to dilate a stenosis while doing so at a generally lower dilatation pressure and/or in manner that results in less trauma to the vessel wall. As a result, a reduction in any restenosis that might otherwise occur can be seen. Thus, in yet another aspect of the present invention, a method for incising and/or dilating a stenosis is provided. Generally, the method involves providing balloon catheter having a catheter shaft having a lumen in fluid
-4-communication with the interior of a cutting balloon, the cutting balloon having at least one microscalpel mounted thereon. If desired, the microscalpel may advantageously be operatively disposed relative to a controllable energy source, such as a source of ultrasonic energy. The catheter is inserted into the bodily lumen and directed to the site to be dilated. The balloon is then inflated so that at least one microscalpel at least partially incises the stenosis. The microscalpel may be controllably activated with ultrasonic energy, if an energy source is provided and it's use is desirable, to fuxther enhance the precision of the incisions made.
These and other features and advantages of the present invention will be apparent in the following detailed description of the preferred embodiments when read in conjunction with the accompanying drawings, in which like reference numerals are used to identify the same or similar parts in the several views.
Brief Description of the Drawings The accompanying drawings, which are incorporated in and constitute a part of this application, illustrate several aspects of the invention and together with description of the illustrated embodiments serve to explain the principles of the invention. A brief description of the drawings is as follows:
Figure 1 is a perspective view of a cutting balloon embodying features of the present invention and showing in particular a plurality of microscalpel cutting blades operatively disposed relative thereto;
Figure 2 is a perspective view of a balloon catheter embodying features of the present invention wherein a plurality of microscalpel cutting blades are operatively disposed relative to the balloon and the microscalpel cutting blades are further operatively disposed relative to a power source so as to be controllably activatable;
Figure 3 is a schematic view, in partial cross-section, of the balloon catheter device of Fig. 2, showing in particular the balloon catheter device positioned within a bodily lumen, and wherein the balloon has been inflated so that at least one microscalpel can at least partially incise a stenosis.
Detailed Description The embodiments of the present invention described below are not intended to be exhaustive or to limit the invention to the particular embodiments disclosed in
These and other features and advantages of the present invention will be apparent in the following detailed description of the preferred embodiments when read in conjunction with the accompanying drawings, in which like reference numerals are used to identify the same or similar parts in the several views.
Brief Description of the Drawings The accompanying drawings, which are incorporated in and constitute a part of this application, illustrate several aspects of the invention and together with description of the illustrated embodiments serve to explain the principles of the invention. A brief description of the drawings is as follows:
Figure 1 is a perspective view of a cutting balloon embodying features of the present invention and showing in particular a plurality of microscalpel cutting blades operatively disposed relative thereto;
Figure 2 is a perspective view of a balloon catheter embodying features of the present invention wherein a plurality of microscalpel cutting blades are operatively disposed relative to the balloon and the microscalpel cutting blades are further operatively disposed relative to a power source so as to be controllably activatable;
Figure 3 is a schematic view, in partial cross-section, of the balloon catheter device of Fig. 2, showing in particular the balloon catheter device positioned within a bodily lumen, and wherein the balloon has been inflated so that at least one microscalpel can at least partially incise a stenosis.
Detailed Description The embodiments of the present invention described below are not intended to be exhaustive or to limit the invention to the particular embodiments disclosed in
-5-the following detailed description. Rather, the embodiments are described so that others skilled in the art can understand the principles and practices of the present invention.
The present invention provides a cutting balloon, and dilation catheter incorporating the same, wherein the cutting balloon has at least one microscalpel blade operatively disposed relative thereto. Advantageously, a source of energy, preferably ultrasonic energy, may be operatively disposed relative to the microscalpel. The inventive cutting balloon, incorporating such microscalpels, or energizable microscalpels, and when provided in conjunction with an angioplasty catheter, can provide advantages not attainable, or for the enhancement of advantages attainable, from a conventional cutting balloon catheter.
Generally speaking, cutting balloons embodying features of the present invention include a balloon having provided operatively disposed thereto at least one microscalpel blade which microscalpel may be further advantageously operatively disposed relative to a power source. The present invention further generally provides a cutting balloon catheter further including, in addition to the inventive cutting balloon, a catheter shaft in fluid communication with the cutting balloon.
Inasmuch as the invention is based at least in part upon the discovery that microscalpels that comprise a much smaller cutting surface or edge than conventional cutting elements can be provided in connection with an angioplasty balloon, that these microscalpels can advantageously be supplied with energy, and further, the advantages that could be obtained by using such device in a dilation procedure, the particular type of balloon or catheter shaft utilized in the inventive balloon and/or balloon catheter are not critical. Rather, any type of catheter shaft and/or balloon, arranged in any configuration, can be employed to provide the inventive balloon or device.
For example, the cutting balloon may be any balloon, of any size or geometry, made of any material or combination of materials, by any method, coated or uncoated, and may be crosslinked or uncrosslinked, having at least one microscalpel blade operatively disposed in connection therewith.
In fact, and due at least in part to the fact that microscalpels can be much sharper than conventional cutting elements, a broader range of materials is suitable
The present invention provides a cutting balloon, and dilation catheter incorporating the same, wherein the cutting balloon has at least one microscalpel blade operatively disposed relative thereto. Advantageously, a source of energy, preferably ultrasonic energy, may be operatively disposed relative to the microscalpel. The inventive cutting balloon, incorporating such microscalpels, or energizable microscalpels, and when provided in conjunction with an angioplasty catheter, can provide advantages not attainable, or for the enhancement of advantages attainable, from a conventional cutting balloon catheter.
Generally speaking, cutting balloons embodying features of the present invention include a balloon having provided operatively disposed thereto at least one microscalpel blade which microscalpel may be further advantageously operatively disposed relative to a power source. The present invention further generally provides a cutting balloon catheter further including, in addition to the inventive cutting balloon, a catheter shaft in fluid communication with the cutting balloon.
Inasmuch as the invention is based at least in part upon the discovery that microscalpels that comprise a much smaller cutting surface or edge than conventional cutting elements can be provided in connection with an angioplasty balloon, that these microscalpels can advantageously be supplied with energy, and further, the advantages that could be obtained by using such device in a dilation procedure, the particular type of balloon or catheter shaft utilized in the inventive balloon and/or balloon catheter are not critical. Rather, any type of catheter shaft and/or balloon, arranged in any configuration, can be employed to provide the inventive balloon or device.
For example, the cutting balloon may be any balloon, of any size or geometry, made of any material or combination of materials, by any method, coated or uncoated, and may be crosslinked or uncrosslinked, having at least one microscalpel blade operatively disposed in connection therewith.
In fact, and due at least in part to the fact that microscalpels can be much sharper than conventional cutting elements, a broader range of materials is suitable
6 PCT/US03/16141 for use in the inventive cutting balloon than is appropriate for use in conventional cutting balloons. For example, and in addition to materials conventionally used in cutting balloons, Pebax~, polyurethanes, latex, polyethylene, Hytrel~ and ionomers can be utilized in the formation of a cutting balloon embodying features of the present invention.
Likewise, the catheter shaft may be any of those used to provide any of the various designs for balloon catheters known in the art. Examples include over-the-wire catheters, single operator or rapid exchange catheters, to name a few.
Additionally, the catheter shaft can be made from any material, by any method, may be coated or uncoated. Further, the catheter shaft, including any components thereof, can have the dimensions of any conventional dilatation catheter, and inner and outer tubular members as may be incorporated into the same.
As mentioned above, the inventive cutting balloon includes at least one microscalpel blade. As used herein, the phrase "microscalpel blade" or term "microscalpel" is meant to indicate any cutting blade, surface, element, edge or the like, that comprise a cutting edge or surface that is generally smaller and/or sharper than any conventional cutting blade used in conjunction with angioplasty balloons.
Generally speaking, microscalpel blades embodying features of the present invention have a cutting surface that is advantageously at least 2 times sharper than any associated with any conventional cutting blade, preferably at least 5 times sharper, and most optimally at least 10 times sharper than cutting edges of conventional cutting blades.
One way of quantifying sharpness is via measurement of the radius of curvature of the cutting edge or surface. For example, one known conventional cutting blade used in conjunction with angioplasty balloons is made from stainless steel and has a radius of curvature of greater than about 100 nm. A
microscalpel blade embodying features of the present invention would thus be sharper than this conventional cutting element by including a cutting edge having a radius of curvature of less than about 100 nm, advantageously less than about 50 nm, more advantageously less than about 20 nm and most optimally, less than about 10 nm.
The microscalpel blades may be formed from any material, or combination of materials, capable of being manufactured to form a cutting blade includes a 7_ cutting surface that is smaller and/or sharper than a conventional cutting blade. One example of a material suitable for use in the production of such microscalpels is a crystalline material, including either monocrystalline or polycrystalline materials.
Such materials are easily manufactured into small structures, while yet providing structures having sufficient strength so as to be useful as a cutting blade.
Examples of such materials include, but are not limited to, silicon, quartz sapphire, diamond (such as diamond-like-carbon), and the like.
The microscalpel cutting blades may further be formed from a combination of materials. The utilization of a combination of materials may be desirable, for example, when the base material is capable of being manufactured to have the desired sharper cutting surface relative to a conventional cutting blade, but wherein the resulting microscalpel may lack the desired strength for use in this capacity. The microscalpel cutting blades may thus be formed from any material, including noncrystalline materials such as glasses, metals, polymers etc, and have provided in combination therewith an additional material or materials to provide the microscalpel with the desired strength or with a desired edge having the desired radius of curvature.
The microscalpel cutting blades may optionally be coated. If desired, any coating, applied in any thickness and by any method, for any desired purpose, may be used, so long it is suitable for use in conjunction with a medical device.
Coatings may desirably be provided to, e.g., enhance lubricity, impart radioopacity, to deliver therapeutic agents therefrom, etc. A coating may further be applied to enhance the strength, or to otherwise protect, the microscalpel cutting blades. Strength enhancing coatings or thin films include, but are not limited to, silicon dioxide, silicon nitride, titanium diboride, diamond like carbon, and silicon carbide.
The method used to form the microscalpel cutting blades is not critical.
Rather, the microscalpel cutting blades may be formed by any method of manufacture appropriate for the chosen material, so long as the microscalpels produced by such a method have a sharper cutting edge or surface than conventional cutting elements. Such methods include, of course, those methods currently utilized to produce conventional cutting elements. Examples of such methods include, but _g_ are not limited to, oxidation sharpening processes or mechanical techniques, such as mechanical cleavage.
Advantageously, when the microscalpels are desirably formed from crystalline materials, the microscalpel blades may be formed by methods commonly utilized to manufacture semiconductor devices. Such techniques are capable of producing large volumes of microscalpel blades inexpensively and further capable of producing incredibly small microscalpels having intricate features, if desired.
Exemplary techniques include etching, such as anisotropic or isotropic etching techniques, further including ion etching (RIE), ion beam milling or chemical etching via the application of chemical agents.
The provision of energy to the microscalpel blades can provide further advantages to the inventive cutting balloon and catheter. For example, the application of energy to the microscalpel cutting blades can further reduce the pressure required to incise a stenosis, i.e. beyond the reduction already provided by the enhanced sharpness of the microscalpels relative to conventional cutting elements. Advantageously, the energy provided to the microscalpel cutting blades may be controllable, so that the energy may be turned on, off, pulsed, or otherwise varied in type, strength, etc., further enhancing the control and precision that may be exercised over incising a stenosis using the inventive cutting balloon and catheter.
Thus, the microscalpel blades are desirably and advantageously operatively disposed relative to a power source that supplies energy, such as thermal, RF, electric, or oscillatory energy, to the microscalpels. Preferably, oscillatory energy, more preferably, ultrasonic energy, is provided by a power source to the microscalpel blades.
Energy may be supplied to the microscalpel cutting blades by any method, using any componentry, arranged in any configuration, so long as however supplied, the energy is capable of at least partially activating at least a portion of at least one microscalpel blade. Methods of providing energy from a source to a remote area are well known to those of ordinary skill in the electrical engineering arts, and any of these may be used.
For exemplary purposes only then, one such configuration might have the power source provided as a component separate from the balloon catheter and connected to the microscalpels via one or more conductors capable of conducting or transmitting the energy provided by the power source. Any such conductors) may be connected directly to the microscalpel blades, or may be operatively disposed to a transducer that is in turn operatively disposed relative to the microscalpel blades. If the conductors) are desirably connected directly to the microscalpels, the conductors themselves are desirably operatively disposed relative to a transducer.
The transducer is desirably provided in any configuration wherein the transducer is capable of supplying energy provided by the power source to the microscalpel blades in order to activate at least a portion of at least one microscalpel.
For example, the transducer may be provided in connection with the balloon and operatively disposed relative to the microscalpel blades. Indeed, microscalpel cutting blades can be attached to the transducer which is in turn, attached to a surface of the cutting balloon, if desired. The transducer may also be an integral part of the microscalpel cutting blades, i.e., as would be the case if a thin film transducer were formed directly on at least a portion of a surface of at least one microscalpel blade. Such transducer structures are generally well-known and comprise multilayer thin film structures including piezoelectric layers and contact layers.
Clearly, given the above, the type of balloon and catheter to which the inventive concept, the provision of ultrasonically activatable microscapels in connection therewith, is not particularly limited and such a construction is not intended. For illustration and exemplary purposes only, then the following figures and description thereof is provided.
Referring now to Figure 1, there is illustrated an exemplary cutting balloon 100 embodying features of the present invention. Generally, cutting balloon comprises a substantially cylindrical body 102 having an outer surface 104, a distal cone section 106, a proximal cone section 108, a distal waist section 110 and proximal waist section 112. Distal waist section 110 and proximal waist section 112 include openings 114 and 116, respectively, for operatively positioning balloon 100 with respect to a catheter shaft (not shown). A plurality of microscalpel blades 120 are disposed on outer surface 104 of body 102. It is noted that the representation of Figure 1 may or may not be to scale, given the nature of microscalpel blades 120.
Microscalpel blades 120 include an edge 122 having a radius of curvature less than that of conventional cutting elements, i.e., less than about 100 nm.
Although microscalpel blades 120 are shown in Figure 1 having a certain shape and configuration, these are not critical, and microscalpel blades 120 can be provided in any shape and configuration so long as at least a portion of one edge 122 of microscalpel cutting blades 120 has a radius of curvature smaller than that of conventional cutting elements provided in connection with angioplasty balloons.
For example, although Figure 1 illustrates microscalpel blades 120 as a single contiguous structure extending in a substantially parallel fashion along substantially the entirety of the longitudinal axis of balloon 100, this configuration is not required. Rather, microscalpel blades 120 can be provided in connection with outer surface 104 of balloon body 102 in any configuration, such as in the form of individual units, each substantially shorter in length than the body 102 of balloon 100, and may be provided in, e.g., a helical configuration, in relation to the outer surface 104 of balloon body 102. Microscalpel blades 120 may also have disruptions, such as serrations provided on edge 122 thereof. Finally, although two microscalpel blades 120 are illustrated in Figure 1, any number of microscalpel blades 120 may be provided on the surface 104 of balloon body 102.
Microscalpels 120 are mounted to the outer surface 104 of the balloon body 102 via mounting elements 124. Mounting elements 124 may be comprised of any material capable of adhering microscalpels 120 to the outer surface 104 of balloon body 102. For example, mounting elements 124 may comprise an elastomeric polymer, such as polyurethane, or may comprise an effective amount of an adhesive, such as a cyanoacrylate or polyurethane adhesive. Although illustrated as such in Figure 1, microscalpel blades 120 need not be indirectly adhered to the outer surface 104 of balloon body 102 via such mounting elements 124. Rather, microscalpel blades 120 can be formed to be an integral component of balloon 100 during the balloon molding process.
Referring now to Figure 2, a balloon catheter embodying features of the present invention, generally designated number 200, is illustrated. Balloon catheter 200 generally includes an elongated catheter shaft 226, having proximal section 228 and distal section 230, balloon 201, microscalpels 220, transducers 250 and conductors 236. Cutting balloon 201 is disposed on the distal section 230 of catheter shaft 226, and manifold 232 is mounted on proximal section 228 of shaft 226 to permit controllable sliding over guidewire 234 and conductor 236, and for fluid introduction within shaft 226. Conductors 236 have a proximal end operatively disposed relative to a power source (not shown), and a distal end operatively disposed relative to transducers 250, which transducers 250 are, in turn, operatively disposed to microscalpels 220. In Figure 2, balloon catheter 200 is illustrated with balloon 201 in an expanded state.
Catheter shaft 226 has an outer tubular member 238 and an inner tubular member 240 disposed within outer tubular member 238, and defining along with outer tubular member 238, inflation lumen 242. Inflation lumen 242 is in fluid communication with the interior (not shown) of cutting balloon 201. The distal extremity 210 of cutting balloon 201 is sealingly secured to the distal extremity of inner tubular member 240 and the proximal extremity 212 of the balloon 201 is sealingly secured to the distal extremity of the outer tubular member 238.
Balloon 201 can be inflated by any fluid, e.g., radiopaque, injected through inflation port 248, or otherwise provided through inflation lumen 244, or by other means, such as from a passageway formed between the outside of the catheter shaft and the member forming balloon 201, depending on the particular design of the catheter. The details and mechanics of fluid transfer and introduction within balloons vary according to the specific design of the catheter, and are well know in the art.
Inner tubular member 240 has an inner lumen 244 extending therethrough and connected with the exterior of outer tubular member 238 via ports 246.
Inner lumen 244 can slidably receive a guidewire 234 suitable for advancement through a patient's bodily lumen (not shown) as well as conductors 236 to provide conductors 236 in operative disposition relative to transducers 250.
Although two conductors 236 are shown, it is noted that any number of conductors can be provided in order to supply energy as provided by a power source (not shown) to any number of transducers 250 and then to microscalpel 220.
Furthermore, although conductors 236 are shown extending through inner lumen 244, conductors 236 may be provided in operative disposition relative to microscalpel cutting blades 220 in any fashion. For exemplary purposes only, such configurations might include, but are not limited to, conductors 236 extending through inflation lumen 242, or extending through an additional lumen, as may be provided within catheter shaft 226 by providing an additional tubular member within outer tubular member 238.
Ultrasonic transducers 250 are fixedly positioned on outer surface 204 of cutting balloon 201 and extend in a generally parallel fashion along the longitudinal axis thereof. Transducers 250 are operatively disposed relative to microscalpel blades 220, more particularly, microscalpel blades are mounted on top of transducers 250. Microscalpel blades 220 and transducers 250 may be so disposed by any known connection method, such as by the use of conventional adhesives or by non-adhesive based techniques, such as fusion bonding.
As but one example of an alternative configuration within the scope of the present invention, conductors 236 may be ultrasonic transmission elements, which may be operatively attached, at a distal end thereof, directly to microscalpel blades 220. In such a configuration, transducers 250 could be operatively disposed at the proximal ends of conductors 236. As such, the ultrasonic vibrations may be transmitted by the conductors 236 to the microscalpel blades 220 thereby ultrasonically activating the same.
In those embodiments of the invention where ultrasonic energy microscapels 220 are provided with conductors 236, conductors 236 are preferably formed from a metal alloy or other material which exhibits superelastic properties within the range of operating temperature that is normally encountered by the conductors 236 during use. In particular, one preferred superelastic metal alloy of which the conductors 236 may be formed is a nickel-titanium alloy wire made up of 55.8 weight percent nickel (NiTi containing 55.8 weight percent nickel and the balance as titanium). It is understood that the conductors 236, when used as ultrasonic transmission elements, may be tapered, narrowed, or otherwise reduced or changed in cross-sectional dimension so as to decrease the rigidity of the conductors 236 and/or to cause amplification of the ultrasound transmitted to and from a distal end thereof.
The inventive balloon catheter, including at least one microscalpel cutting blade that may optionally be ultrasonically activatable, provides many advantages when used to perform a cutting dilation. Firstly, due at least in part to the small size and enhanced sharpness of the microscalpels and at least in part to the ability to activate the microscalpels with a form of energy, the cutting balloon, when inflated, is capable of creating much sharper and cleaner incisions in a stenosis than a balloon including conventional cutting blades. The ability to selectively activate, deactivate, pulse, or otherwise vary, e.g., as by varying the frequency or amplitude of an oscillatory power source, the source of energy further enhances the cutting precision that can be seen when utilizing the inventive balloon catheter in a treatment.
As a result of these advantages, the inventive cutting balloons and balloon catheters can be used to incise stenosis at lower dilatation pressures, or to incise stenosis that are difficult to incise utilizing conventional cutting balloons. As such, trauma to the vessel wall, as well as any subsequent restenosis that can result therefrom, can be reduced.
In this regard, the present invention further provides a method of dilating and incising a stenosis using the inventive balloon catheter, which method can generally be described with reference to Figure 3. Generally, the method comprises the steps of providing a balloon catheter 300, wherein the balloon catheter 300 comprises at least a cutting balloon 301 including at least one microscalpel blade 320, which may further optionally be operatively disposed relative to a power source (not shown) so that the microscalpels 320 may be activated thereby. The balloon catheter may be inserted within a bodily lumen 360, as by advancing the catheter over a guide wire (not shown) placed prior to the insertion of the catheter 300, and advanced to the desired treatment site 362. The balloon 301 may then be inflated to cause the radial expansion thereof so that at least a portion of at least one of the microscalpel blades 320 contacts the stenosis 362 thereby at least partially incising the stenosis 362. If desired, during any portion of the inflation or any other period that any portion of microscalpel 320 is disposed within stenosis 362 so as to be capable of incising stenosis 362, microscalpel 320 may be activated with ultrasonic energy as provide to microscalpel 320 by transducer 350 and/or conductor 336. The balloon may then be deflated and withdrawn from the lumen.
The present invention provides apparatus and methods for the treatment of luminal conditions and diseases of body systems including the vascular, pulmonary, lymphatic, and urinary, as well as other body systems that include one or more body lumens. In particular, the present invention provides balloon catheters that may be advantageously utilized for the treatment of diseases of the coronary and peripheral vasculature. Specific conditions generally include coronary and peripheral arterial disease and thrombosis. Such catheters advantageously provide treatment by generally non-invasive techniques by permitting manipulation of distal features of such catheters from their proximal ends.
Numerous characteristics and advantages of the invention meant to be described by this document have been set forth in the foregoing description.
It is to be understood, however, that while particular forms or embodiments of the invention have been illustrated, various modifications, including modifications to shape, and arrangement of parts, and the like, can be made without departing from the spirit and scope of the invention.
Likewise, the catheter shaft may be any of those used to provide any of the various designs for balloon catheters known in the art. Examples include over-the-wire catheters, single operator or rapid exchange catheters, to name a few.
Additionally, the catheter shaft can be made from any material, by any method, may be coated or uncoated. Further, the catheter shaft, including any components thereof, can have the dimensions of any conventional dilatation catheter, and inner and outer tubular members as may be incorporated into the same.
As mentioned above, the inventive cutting balloon includes at least one microscalpel blade. As used herein, the phrase "microscalpel blade" or term "microscalpel" is meant to indicate any cutting blade, surface, element, edge or the like, that comprise a cutting edge or surface that is generally smaller and/or sharper than any conventional cutting blade used in conjunction with angioplasty balloons.
Generally speaking, microscalpel blades embodying features of the present invention have a cutting surface that is advantageously at least 2 times sharper than any associated with any conventional cutting blade, preferably at least 5 times sharper, and most optimally at least 10 times sharper than cutting edges of conventional cutting blades.
One way of quantifying sharpness is via measurement of the radius of curvature of the cutting edge or surface. For example, one known conventional cutting blade used in conjunction with angioplasty balloons is made from stainless steel and has a radius of curvature of greater than about 100 nm. A
microscalpel blade embodying features of the present invention would thus be sharper than this conventional cutting element by including a cutting edge having a radius of curvature of less than about 100 nm, advantageously less than about 50 nm, more advantageously less than about 20 nm and most optimally, less than about 10 nm.
The microscalpel blades may be formed from any material, or combination of materials, capable of being manufactured to form a cutting blade includes a 7_ cutting surface that is smaller and/or sharper than a conventional cutting blade. One example of a material suitable for use in the production of such microscalpels is a crystalline material, including either monocrystalline or polycrystalline materials.
Such materials are easily manufactured into small structures, while yet providing structures having sufficient strength so as to be useful as a cutting blade.
Examples of such materials include, but are not limited to, silicon, quartz sapphire, diamond (such as diamond-like-carbon), and the like.
The microscalpel cutting blades may further be formed from a combination of materials. The utilization of a combination of materials may be desirable, for example, when the base material is capable of being manufactured to have the desired sharper cutting surface relative to a conventional cutting blade, but wherein the resulting microscalpel may lack the desired strength for use in this capacity. The microscalpel cutting blades may thus be formed from any material, including noncrystalline materials such as glasses, metals, polymers etc, and have provided in combination therewith an additional material or materials to provide the microscalpel with the desired strength or with a desired edge having the desired radius of curvature.
The microscalpel cutting blades may optionally be coated. If desired, any coating, applied in any thickness and by any method, for any desired purpose, may be used, so long it is suitable for use in conjunction with a medical device.
Coatings may desirably be provided to, e.g., enhance lubricity, impart radioopacity, to deliver therapeutic agents therefrom, etc. A coating may further be applied to enhance the strength, or to otherwise protect, the microscalpel cutting blades. Strength enhancing coatings or thin films include, but are not limited to, silicon dioxide, silicon nitride, titanium diboride, diamond like carbon, and silicon carbide.
The method used to form the microscalpel cutting blades is not critical.
Rather, the microscalpel cutting blades may be formed by any method of manufacture appropriate for the chosen material, so long as the microscalpels produced by such a method have a sharper cutting edge or surface than conventional cutting elements. Such methods include, of course, those methods currently utilized to produce conventional cutting elements. Examples of such methods include, but _g_ are not limited to, oxidation sharpening processes or mechanical techniques, such as mechanical cleavage.
Advantageously, when the microscalpels are desirably formed from crystalline materials, the microscalpel blades may be formed by methods commonly utilized to manufacture semiconductor devices. Such techniques are capable of producing large volumes of microscalpel blades inexpensively and further capable of producing incredibly small microscalpels having intricate features, if desired.
Exemplary techniques include etching, such as anisotropic or isotropic etching techniques, further including ion etching (RIE), ion beam milling or chemical etching via the application of chemical agents.
The provision of energy to the microscalpel blades can provide further advantages to the inventive cutting balloon and catheter. For example, the application of energy to the microscalpel cutting blades can further reduce the pressure required to incise a stenosis, i.e. beyond the reduction already provided by the enhanced sharpness of the microscalpels relative to conventional cutting elements. Advantageously, the energy provided to the microscalpel cutting blades may be controllable, so that the energy may be turned on, off, pulsed, or otherwise varied in type, strength, etc., further enhancing the control and precision that may be exercised over incising a stenosis using the inventive cutting balloon and catheter.
Thus, the microscalpel blades are desirably and advantageously operatively disposed relative to a power source that supplies energy, such as thermal, RF, electric, or oscillatory energy, to the microscalpels. Preferably, oscillatory energy, more preferably, ultrasonic energy, is provided by a power source to the microscalpel blades.
Energy may be supplied to the microscalpel cutting blades by any method, using any componentry, arranged in any configuration, so long as however supplied, the energy is capable of at least partially activating at least a portion of at least one microscalpel blade. Methods of providing energy from a source to a remote area are well known to those of ordinary skill in the electrical engineering arts, and any of these may be used.
For exemplary purposes only then, one such configuration might have the power source provided as a component separate from the balloon catheter and connected to the microscalpels via one or more conductors capable of conducting or transmitting the energy provided by the power source. Any such conductors) may be connected directly to the microscalpel blades, or may be operatively disposed to a transducer that is in turn operatively disposed relative to the microscalpel blades. If the conductors) are desirably connected directly to the microscalpels, the conductors themselves are desirably operatively disposed relative to a transducer.
The transducer is desirably provided in any configuration wherein the transducer is capable of supplying energy provided by the power source to the microscalpel blades in order to activate at least a portion of at least one microscalpel.
For example, the transducer may be provided in connection with the balloon and operatively disposed relative to the microscalpel blades. Indeed, microscalpel cutting blades can be attached to the transducer which is in turn, attached to a surface of the cutting balloon, if desired. The transducer may also be an integral part of the microscalpel cutting blades, i.e., as would be the case if a thin film transducer were formed directly on at least a portion of a surface of at least one microscalpel blade. Such transducer structures are generally well-known and comprise multilayer thin film structures including piezoelectric layers and contact layers.
Clearly, given the above, the type of balloon and catheter to which the inventive concept, the provision of ultrasonically activatable microscapels in connection therewith, is not particularly limited and such a construction is not intended. For illustration and exemplary purposes only, then the following figures and description thereof is provided.
Referring now to Figure 1, there is illustrated an exemplary cutting balloon 100 embodying features of the present invention. Generally, cutting balloon comprises a substantially cylindrical body 102 having an outer surface 104, a distal cone section 106, a proximal cone section 108, a distal waist section 110 and proximal waist section 112. Distal waist section 110 and proximal waist section 112 include openings 114 and 116, respectively, for operatively positioning balloon 100 with respect to a catheter shaft (not shown). A plurality of microscalpel blades 120 are disposed on outer surface 104 of body 102. It is noted that the representation of Figure 1 may or may not be to scale, given the nature of microscalpel blades 120.
Microscalpel blades 120 include an edge 122 having a radius of curvature less than that of conventional cutting elements, i.e., less than about 100 nm.
Although microscalpel blades 120 are shown in Figure 1 having a certain shape and configuration, these are not critical, and microscalpel blades 120 can be provided in any shape and configuration so long as at least a portion of one edge 122 of microscalpel cutting blades 120 has a radius of curvature smaller than that of conventional cutting elements provided in connection with angioplasty balloons.
For example, although Figure 1 illustrates microscalpel blades 120 as a single contiguous structure extending in a substantially parallel fashion along substantially the entirety of the longitudinal axis of balloon 100, this configuration is not required. Rather, microscalpel blades 120 can be provided in connection with outer surface 104 of balloon body 102 in any configuration, such as in the form of individual units, each substantially shorter in length than the body 102 of balloon 100, and may be provided in, e.g., a helical configuration, in relation to the outer surface 104 of balloon body 102. Microscalpel blades 120 may also have disruptions, such as serrations provided on edge 122 thereof. Finally, although two microscalpel blades 120 are illustrated in Figure 1, any number of microscalpel blades 120 may be provided on the surface 104 of balloon body 102.
Microscalpels 120 are mounted to the outer surface 104 of the balloon body 102 via mounting elements 124. Mounting elements 124 may be comprised of any material capable of adhering microscalpels 120 to the outer surface 104 of balloon body 102. For example, mounting elements 124 may comprise an elastomeric polymer, such as polyurethane, or may comprise an effective amount of an adhesive, such as a cyanoacrylate or polyurethane adhesive. Although illustrated as such in Figure 1, microscalpel blades 120 need not be indirectly adhered to the outer surface 104 of balloon body 102 via such mounting elements 124. Rather, microscalpel blades 120 can be formed to be an integral component of balloon 100 during the balloon molding process.
Referring now to Figure 2, a balloon catheter embodying features of the present invention, generally designated number 200, is illustrated. Balloon catheter 200 generally includes an elongated catheter shaft 226, having proximal section 228 and distal section 230, balloon 201, microscalpels 220, transducers 250 and conductors 236. Cutting balloon 201 is disposed on the distal section 230 of catheter shaft 226, and manifold 232 is mounted on proximal section 228 of shaft 226 to permit controllable sliding over guidewire 234 and conductor 236, and for fluid introduction within shaft 226. Conductors 236 have a proximal end operatively disposed relative to a power source (not shown), and a distal end operatively disposed relative to transducers 250, which transducers 250 are, in turn, operatively disposed to microscalpels 220. In Figure 2, balloon catheter 200 is illustrated with balloon 201 in an expanded state.
Catheter shaft 226 has an outer tubular member 238 and an inner tubular member 240 disposed within outer tubular member 238, and defining along with outer tubular member 238, inflation lumen 242. Inflation lumen 242 is in fluid communication with the interior (not shown) of cutting balloon 201. The distal extremity 210 of cutting balloon 201 is sealingly secured to the distal extremity of inner tubular member 240 and the proximal extremity 212 of the balloon 201 is sealingly secured to the distal extremity of the outer tubular member 238.
Balloon 201 can be inflated by any fluid, e.g., radiopaque, injected through inflation port 248, or otherwise provided through inflation lumen 244, or by other means, such as from a passageway formed between the outside of the catheter shaft and the member forming balloon 201, depending on the particular design of the catheter. The details and mechanics of fluid transfer and introduction within balloons vary according to the specific design of the catheter, and are well know in the art.
Inner tubular member 240 has an inner lumen 244 extending therethrough and connected with the exterior of outer tubular member 238 via ports 246.
Inner lumen 244 can slidably receive a guidewire 234 suitable for advancement through a patient's bodily lumen (not shown) as well as conductors 236 to provide conductors 236 in operative disposition relative to transducers 250.
Although two conductors 236 are shown, it is noted that any number of conductors can be provided in order to supply energy as provided by a power source (not shown) to any number of transducers 250 and then to microscalpel 220.
Furthermore, although conductors 236 are shown extending through inner lumen 244, conductors 236 may be provided in operative disposition relative to microscalpel cutting blades 220 in any fashion. For exemplary purposes only, such configurations might include, but are not limited to, conductors 236 extending through inflation lumen 242, or extending through an additional lumen, as may be provided within catheter shaft 226 by providing an additional tubular member within outer tubular member 238.
Ultrasonic transducers 250 are fixedly positioned on outer surface 204 of cutting balloon 201 and extend in a generally parallel fashion along the longitudinal axis thereof. Transducers 250 are operatively disposed relative to microscalpel blades 220, more particularly, microscalpel blades are mounted on top of transducers 250. Microscalpel blades 220 and transducers 250 may be so disposed by any known connection method, such as by the use of conventional adhesives or by non-adhesive based techniques, such as fusion bonding.
As but one example of an alternative configuration within the scope of the present invention, conductors 236 may be ultrasonic transmission elements, which may be operatively attached, at a distal end thereof, directly to microscalpel blades 220. In such a configuration, transducers 250 could be operatively disposed at the proximal ends of conductors 236. As such, the ultrasonic vibrations may be transmitted by the conductors 236 to the microscalpel blades 220 thereby ultrasonically activating the same.
In those embodiments of the invention where ultrasonic energy microscapels 220 are provided with conductors 236, conductors 236 are preferably formed from a metal alloy or other material which exhibits superelastic properties within the range of operating temperature that is normally encountered by the conductors 236 during use. In particular, one preferred superelastic metal alloy of which the conductors 236 may be formed is a nickel-titanium alloy wire made up of 55.8 weight percent nickel (NiTi containing 55.8 weight percent nickel and the balance as titanium). It is understood that the conductors 236, when used as ultrasonic transmission elements, may be tapered, narrowed, or otherwise reduced or changed in cross-sectional dimension so as to decrease the rigidity of the conductors 236 and/or to cause amplification of the ultrasound transmitted to and from a distal end thereof.
The inventive balloon catheter, including at least one microscalpel cutting blade that may optionally be ultrasonically activatable, provides many advantages when used to perform a cutting dilation. Firstly, due at least in part to the small size and enhanced sharpness of the microscalpels and at least in part to the ability to activate the microscalpels with a form of energy, the cutting balloon, when inflated, is capable of creating much sharper and cleaner incisions in a stenosis than a balloon including conventional cutting blades. The ability to selectively activate, deactivate, pulse, or otherwise vary, e.g., as by varying the frequency or amplitude of an oscillatory power source, the source of energy further enhances the cutting precision that can be seen when utilizing the inventive balloon catheter in a treatment.
As a result of these advantages, the inventive cutting balloons and balloon catheters can be used to incise stenosis at lower dilatation pressures, or to incise stenosis that are difficult to incise utilizing conventional cutting balloons. As such, trauma to the vessel wall, as well as any subsequent restenosis that can result therefrom, can be reduced.
In this regard, the present invention further provides a method of dilating and incising a stenosis using the inventive balloon catheter, which method can generally be described with reference to Figure 3. Generally, the method comprises the steps of providing a balloon catheter 300, wherein the balloon catheter 300 comprises at least a cutting balloon 301 including at least one microscalpel blade 320, which may further optionally be operatively disposed relative to a power source (not shown) so that the microscalpels 320 may be activated thereby. The balloon catheter may be inserted within a bodily lumen 360, as by advancing the catheter over a guide wire (not shown) placed prior to the insertion of the catheter 300, and advanced to the desired treatment site 362. The balloon 301 may then be inflated to cause the radial expansion thereof so that at least a portion of at least one of the microscalpel blades 320 contacts the stenosis 362 thereby at least partially incising the stenosis 362. If desired, during any portion of the inflation or any other period that any portion of microscalpel 320 is disposed within stenosis 362 so as to be capable of incising stenosis 362, microscalpel 320 may be activated with ultrasonic energy as provide to microscalpel 320 by transducer 350 and/or conductor 336. The balloon may then be deflated and withdrawn from the lumen.
The present invention provides apparatus and methods for the treatment of luminal conditions and diseases of body systems including the vascular, pulmonary, lymphatic, and urinary, as well as other body systems that include one or more body lumens. In particular, the present invention provides balloon catheters that may be advantageously utilized for the treatment of diseases of the coronary and peripheral vasculature. Specific conditions generally include coronary and peripheral arterial disease and thrombosis. Such catheters advantageously provide treatment by generally non-invasive techniques by permitting manipulation of distal features of such catheters from their proximal ends.
Numerous characteristics and advantages of the invention meant to be described by this document have been set forth in the foregoing description.
It is to be understood, however, that while particular forms or embodiments of the invention have been illustrated, various modifications, including modifications to shape, and arrangement of parts, and the like, can be made without departing from the spirit and scope of the invention.
Claims (32)
1. A cutting dilation balloon comprising:
a balloon body having an outer surface; and at least one microscalpel operatively disposed relative to the outer surface of the body.
a balloon body having an outer surface; and at least one microscalpel operatively disposed relative to the outer surface of the body.
2. The cutting dilation balloon of claim 1, wherein the microscalpel comprises a crystalline material.
3. The cutting dilation balloon of claim 2, wherein the crystalline material comprises a monocrystalline material.
4. The cutting dilation balloon of claim 3, wherein the monocrystalline material is silicon.
5. The cutting dilation balloon of claim 1, wherein the microscalpel has a radius of curvature of between about 0.5 nm and about 100 nm.
6. The cutting dilation balloon of claim 1, wherein the microscalpel has a radius of curvature between about 1 nm and about 50 nm.
7. The cutting dilation balloon of claim 1, wherein at least a portion of the microscalpel includes a thin-film coating.
8. The cutting dilation balloon of claim 7, wherein the thin-film coating comprises silicon dioxide, silicon nitride, titanium diboride, diamond like carbon, silicon carbide or combinations thereof.
9. The cutting dilation balloon of claim 7, wherein at least one microscalpel is operatively disposed relative to a source of power so as to be controllably activatable.
10. The cutting dilation balloon of claim 9, wherein the power source is capable of being controlled so as to controllably activate, deactivate, pulse, or otherwise vary the power supplied to the microscalpel.
11. The cutting dilation balloon of claim 9, wherein the power source provides oscillatory, thermal, RF, electric energy, or a combination of these, to the microscalpel.
12. The cutting dilation balloon of claim 11, wherein the power source is a source of ultrasonic energy.
13. The cutting dilation balloon of claim 12, wherein the microscalpel is ultrasonically activatable by the provision of a transducer operatively disposed relative to the microscalpel.
I4. The cutting dilation balloon of claim 13, wherein the transducer is a thin-film transducer formed on at least a portion of a surface of the microscalpel.
15. The cutting dilation balloon of claim 14, wherein the thin-film transducer includes at least one piezoelectric material.
16. The cutting dilation balloon of claim 13, wherein the transducer oscillates at a frequency in the range from about 1 kHz to about 300 kHz.
17. The cutting dilatation balloon of claim 13, wherein the transducer oscillates at a frequency in the range from about 20 kHz to about 80 kHz.
18. A cutting balloon catheter comprising:
an elongated catheter shaft having a proximal end, a distal end, and an inflation lumen extending through at least a section thereof; and a cutting dilation balloon comprising a balloon body having an outer surface and an interior in fluid communication with the inflation lumen; and at least one microscalpel operatively disposed relative to the outer surface of the body.
an elongated catheter shaft having a proximal end, a distal end, and an inflation lumen extending through at least a section thereof; and a cutting dilation balloon comprising a balloon body having an outer surface and an interior in fluid communication with the inflation lumen; and at least one microscalpel operatively disposed relative to the outer surface of the body.
19. The cutting balloon catheter of claim 18, wherein at least one microscalpel is operatively disposed relative to a source of power so as to be controllably activatable.
20. The cutting balloon catheter of claim 19, wherein the power source is capable of being controlled so as to controllably activate, deactivate, pulse, or otherwise vary the power supplied to the microscalpel.
21. The cutting balloon catheter of claim 19, wherein the power source provides oscillatory, thermal, RF, electric energy, or a combination of these, to the microscalpel.
22. The cutting balloon catheter of claim 2I, wherein the power source is a source of ultrasonic energy.
23. A method of forming a cutting balloon comprising the steps of providing a balloon having an outer surface;
providing at least one microscalpel; and mounting the at least one microscalpel onto the outer surface of the balloon.
providing at least one microscalpel; and mounting the at least one microscalpel onto the outer surface of the balloon.
24. The method of claim 23, wherein the microscalpel is ultrasonically activatable.
25. A method of forming a cutting balloon catheter comprising the steps of:
providing a balloon having an outer surface, an interior, and at least one microscalpel operatively disposed on the outer surface;
providing an elongated catheter shaft having a proximal end, a distal end and an inflation lumen extending through at least a portion thereof; and mounting the balloon on the catheter shaft so that the interior of the balloon is in fluid communication with the inflation lumen.
providing a balloon having an outer surface, an interior, and at least one microscalpel operatively disposed on the outer surface;
providing an elongated catheter shaft having a proximal end, a distal end and an inflation lumen extending through at least a portion thereof; and mounting the balloon on the catheter shaft so that the interior of the balloon is in fluid communication with the inflation lumen.
26. The method of claim 25, wherein the microscalpel is ultrasonically activatable.
27. A method for incising a stenosis comprising the steps of providing a balloon catheter, comprising:
an elongated catheter shaft having an inflation lumen extending through at least a portion thereof;
a balloon having an interior, an outer surface, and at least one microscalpel operatively disposed on the outer surface, wherein the interior of the balloon is in fluid communication with the inflation lumen;
inserting the balloon catheter into the bodily lumen and directing the balloon to the site to be dilated; and inflating the balloon so that at least one microscalpel at least partially incises the stenosis.
an elongated catheter shaft having an inflation lumen extending through at least a portion thereof;
a balloon having an interior, an outer surface, and at least one microscalpel operatively disposed on the outer surface, wherein the interior of the balloon is in fluid communication with the inflation lumen;
inserting the balloon catheter into the bodily lumen and directing the balloon to the site to be dilated; and inflating the balloon so that at least one microscalpel at least partially incises the stenosis.
28. The method of claim 27, wherein at least one microscalpel is operatively disposed relative to a source of power so as to be controllably activatable.
29. The method of claim 28, wherein the power source is capable of being controlled so as to controllably activate, deactivate, pulse, or otherwise vary the power supplied to the microscalpel.
30. The method of claim 29, wherein the power source provides oscillatory, thermal, RF, electric energy, or a combination of these, to the microscalpel.
31. The method of claim 30, wherein the power source is a source of ultrasonic energy.
32. The method of claim 31 wherein the microscalpel is activated with ultrasonic energy for at least a portion of the time that the balloon is inflated.
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US10/167,214 US7153315B2 (en) | 2002-06-11 | 2002-06-11 | Catheter balloon with ultrasonic microscalpel blades |
US10/167,214 | 2002-06-11 | ||
PCT/US2003/016141 WO2003103516A1 (en) | 2002-06-11 | 2003-05-21 | Catheter balloon with ultrasonic microscalpel blades |
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CA2488870A1 true CA2488870A1 (en) | 2003-12-18 |
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CA002488870A Abandoned CA2488870A1 (en) | 2002-06-11 | 2003-05-21 | Catheter balloon with ultrasonic microscalpel blades |
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---|---|---|---|---|
US8328829B2 (en) | 1999-08-19 | 2012-12-11 | Covidien Lp | High capacity debulking catheter with razor edge cutting window |
US6299622B1 (en) | 1999-08-19 | 2001-10-09 | Fox Hollow Technologies, Inc. | Atherectomy catheter with aligned imager |
US7713279B2 (en) | 2000-12-20 | 2010-05-11 | Fox Hollow Technologies, Inc. | Method and devices for cutting tissue |
US7708749B2 (en) | 2000-12-20 | 2010-05-04 | Fox Hollow Technologies, Inc. | Debulking catheters and methods |
US8241274B2 (en) | 2000-01-19 | 2012-08-14 | Medtronic, Inc. | Method for guiding a medical device |
EP2353526B1 (en) | 2000-12-20 | 2013-09-04 | Covidien LP | Catheter for removing atheromatous or thrombotic occlusive material |
US10835307B2 (en) | 2001-06-12 | 2020-11-17 | Ethicon Llc | Modular battery powered handheld surgical instrument containing elongated multi-layered shaft |
US8150519B2 (en) | 2002-04-08 | 2012-04-03 | Ardian, Inc. | Methods and apparatus for bilateral renal neuromodulation |
US7756583B2 (en) | 2002-04-08 | 2010-07-13 | Ardian, Inc. | Methods and apparatus for intravascularly-induced neuromodulation |
US8347891B2 (en) | 2002-04-08 | 2013-01-08 | Medtronic Ardian Luxembourg S.A.R.L. | Methods and apparatus for performing a non-continuous circumferential treatment of a body lumen |
US7617005B2 (en) | 2002-04-08 | 2009-11-10 | Ardian, Inc. | Methods and apparatus for thermally-induced renal neuromodulation |
US7494497B2 (en) * | 2003-01-02 | 2009-02-24 | Boston Scientific Scimed, Inc. | Medical devices |
US7763043B2 (en) * | 2003-01-09 | 2010-07-27 | Boston Scientific Scimed, Inc. | Dilatation catheter with enhanced distal end for crossing occluded lesions |
US8246640B2 (en) | 2003-04-22 | 2012-08-21 | Tyco Healthcare Group Lp | Methods and devices for cutting tissue at a vascular location |
US8012136B2 (en) | 2003-05-20 | 2011-09-06 | Optimyst Systems, Inc. | Ophthalmic fluid delivery device and method of operation |
WO2004103478A1 (en) | 2003-05-20 | 2004-12-02 | Collins James F | Ophthalmic drug delivery system |
EP3045136B1 (en) | 2003-09-12 | 2021-02-24 | Vessix Vascular, Inc. | Selectable eccentric remodeling and/or ablation of atherosclerotic material |
US8048093B2 (en) * | 2003-12-19 | 2011-11-01 | Boston Scientific Scimed, Inc. | Textured balloons |
US7258697B1 (en) * | 2003-12-22 | 2007-08-21 | Advanced Cardiovascular Systems, Inc. | Stent with anchors to prevent vulnerable plaque rupture during deployment |
US8182501B2 (en) | 2004-02-27 | 2012-05-22 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical shears and method for sealing a blood vessel using same |
US7976557B2 (en) * | 2004-06-23 | 2011-07-12 | Boston Scientific Scimed, Inc. | Cutting balloon and process |
US8920414B2 (en) | 2004-09-10 | 2014-12-30 | Vessix Vascular, Inc. | Tuned RF energy and electrical tissue characterization for selective treatment of target tissues |
US9713730B2 (en) | 2004-09-10 | 2017-07-25 | Boston Scientific Scimed, Inc. | Apparatus and method for treatment of in-stent restenosis |
US8396548B2 (en) | 2008-11-14 | 2013-03-12 | Vessix Vascular, Inc. | Selective drug delivery in a lumen |
EP1802245B8 (en) | 2004-10-08 | 2016-09-28 | Ethicon Endo-Surgery, LLC | Ultrasonic surgical instrument |
US7753907B2 (en) * | 2004-10-29 | 2010-07-13 | Boston Scientific Scimed, Inc. | Medical device systems and methods |
US8038691B2 (en) * | 2004-11-12 | 2011-10-18 | Boston Scientific Scimed, Inc. | Cutting balloon catheter having flexible atherotomes |
US7291158B2 (en) * | 2004-11-12 | 2007-11-06 | Boston Scientific Scimed, Inc. | Cutting balloon catheter having a segmented blade |
DK1830915T3 (en) * | 2004-12-30 | 2009-02-16 | Cook Inc | Catheter construction with plaque cutting balloon |
US20060247674A1 (en) * | 2005-04-29 | 2006-11-02 | Roman Ricardo D | String cutting balloon |
US10076641B2 (en) | 2005-05-11 | 2018-09-18 | The Spectranetics Corporation | Methods and systems for delivering substances into luminal walls |
US8052703B2 (en) * | 2005-06-29 | 2011-11-08 | Boston Scientific Scimed, Inc. | Medical devices with cutting elements |
US7708753B2 (en) | 2005-09-27 | 2010-05-04 | Cook Incorporated | Balloon catheter with extendable dilation wire |
US20070191713A1 (en) | 2005-10-14 | 2007-08-16 | Eichmann Stephen E | Ultrasonic device for cutting and coagulating |
US20070198047A1 (en) * | 2005-12-20 | 2007-08-23 | Medical Components, Inc. | Cutting balloon catheter assembly |
US7621930B2 (en) | 2006-01-20 | 2009-11-24 | Ethicon Endo-Surgery, Inc. | Ultrasound medical instrument having a medical ultrasonic blade |
US8019435B2 (en) | 2006-05-02 | 2011-09-13 | Boston Scientific Scimed, Inc. | Control of arterial smooth muscle tone |
US20080039746A1 (en) | 2006-05-25 | 2008-02-14 | Medtronic, Inc. | Methods of using high intensity focused ultrasound to form an ablated tissue area containing a plurality of lesions |
US20070276419A1 (en) | 2006-05-26 | 2007-11-29 | Fox Hollow Technologies, Inc. | Methods and devices for rotating an active element and an energy emitter on a catheter |
AU2007261016A1 (en) * | 2006-06-20 | 2007-12-27 | Aortx, Inc. | Prosthetic valve implant site preparation techniques |
EP2076194B1 (en) | 2006-10-18 | 2013-04-24 | Vessix Vascular, Inc. | System for inducing desirable temperature effects on body tissue |
EP2992850A1 (en) | 2006-10-18 | 2016-03-09 | Vessix Vascular, Inc. | Inducing desirable temperature effects on body tissue |
US8226675B2 (en) | 2007-03-22 | 2012-07-24 | Ethicon Endo-Surgery, Inc. | Surgical instruments |
US20080234709A1 (en) | 2007-03-22 | 2008-09-25 | Houser Kevin L | Ultrasonic surgical instrument and cartilage and bone shaping blades therefor |
US8142461B2 (en) | 2007-03-22 | 2012-03-27 | Ethicon Endo-Surgery, Inc. | Surgical instruments |
US8057498B2 (en) | 2007-11-30 | 2011-11-15 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instrument blades |
US8911460B2 (en) | 2007-03-22 | 2014-12-16 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments |
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 |
US8348967B2 (en) | 2007-07-27 | 2013-01-08 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments |
US8808319B2 (en) | 2007-07-27 | 2014-08-19 | Ethicon Endo-Surgery, Inc. | Surgical instruments |
US8257377B2 (en) | 2007-07-27 | 2012-09-04 | Ethicon Endo-Surgery, Inc. | Multiple end effectors ultrasonic surgical instruments |
US8252012B2 (en) | 2007-07-31 | 2012-08-28 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instrument with modulator |
US9044261B2 (en) | 2007-07-31 | 2015-06-02 | Ethicon Endo-Surgery, Inc. | Temperature controlled ultrasonic surgical instruments |
US8512365B2 (en) | 2007-07-31 | 2013-08-20 | Ethicon Endo-Surgery, Inc. | Surgical instruments |
US8430898B2 (en) | 2007-07-31 | 2013-04-30 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments |
AU2008308606B2 (en) | 2007-10-05 | 2014-12-18 | Ethicon Endo-Surgery, Inc. | Ergonomic surgical instruments |
USD594983S1 (en) | 2007-10-05 | 2009-06-23 | Ethicon Endo-Surgery, Inc. | Handle assembly for surgical instrument |
US7901423B2 (en) | 2007-11-30 | 2011-03-08 | Ethicon Endo-Surgery, Inc. | Folded ultrasonic end effectors with increased active length |
US10010339B2 (en) | 2007-11-30 | 2018-07-03 | Ethicon Llc | Ultrasonic surgical blades |
US7815687B2 (en) * | 2007-12-18 | 2010-10-19 | Med Institute, Inc. | Method of promoting cell proliferation and ingrowth by injury to the native tissue |
US20090171283A1 (en) * | 2007-12-27 | 2009-07-02 | Cook Incorporated | Method of bonding a dilation element to a surface of an angioplasty balloon |
US8784440B2 (en) | 2008-02-25 | 2014-07-22 | Covidien Lp | Methods and devices for cutting tissue |
WO2009114425A1 (en) | 2008-03-13 | 2009-09-17 | Cook Incorporated | Cutting balloon with connector and dilation element |
US11229777B2 (en) | 2008-03-21 | 2022-01-25 | Cagent Vascular, Inc. | System and method for plaque serration |
CA2718067C (en) | 2008-03-21 | 2014-07-08 | Innovasc Llc | Device and method for opening blood vessels by pre-angioplasty serration and dilatation of atherosclerotic plaque |
US9480826B2 (en) | 2008-03-21 | 2016-11-01 | Cagent Vascular, Llc | Intravascular device |
US20100036294A1 (en) | 2008-05-07 | 2010-02-11 | Robert Mantell | Radially-Firing Electrohydraulic Lithotripsy Probe |
US8956371B2 (en) | 2008-06-13 | 2015-02-17 | Shockwave Medical, Inc. | Shockwave balloon catheter system |
US9072534B2 (en) | 2008-06-13 | 2015-07-07 | Shockwave Medical, Inc. | Non-cavitation shockwave balloon catheter system |
US10702293B2 (en) | 2008-06-13 | 2020-07-07 | Shockwave Medical, Inc. | Two-stage method for treating calcified lesions within the wall of a blood vessel |
EP2326264B1 (en) * | 2008-07-27 | 2017-11-15 | Pi-R-Squared Ltd. | Fracturing calcifications in heart valves |
US9089360B2 (en) | 2008-08-06 | 2015-07-28 | Ethicon Endo-Surgery, Inc. | Devices and techniques for cutting and coagulating tissue |
US8058771B2 (en) | 2008-08-06 | 2011-11-15 | Ethicon Endo-Surgery, Inc. | Ultrasonic device for cutting and coagulating with stepped output |
US20100069837A1 (en) * | 2008-09-16 | 2010-03-18 | Boston Scientific Scimed, Inc. | Balloon Assembly and Method for Therapeutic Agent Delivery |
KR101645754B1 (en) | 2008-10-13 | 2016-08-04 | 코비디엔 엘피 | Devices and methods for manipulating a catheter shaft |
US9180280B2 (en) * | 2008-11-04 | 2015-11-10 | Shockwave Medical, Inc. | Drug delivery shockwave balloon catheter system |
US9044618B2 (en) | 2008-11-05 | 2015-06-02 | Shockwave Medical, Inc. | Shockwave valvuloplasty catheter system |
CA2743992A1 (en) | 2008-11-17 | 2010-05-20 | Minnow Medical, Inc. | Selective accumulation of energy with or without knowledge of tissue topography |
BRPI1014721A2 (en) | 2009-04-29 | 2016-04-12 | Tyco Healthcare | methods and devices for cutting and scraping fabric |
CA2761774C (en) | 2009-05-14 | 2014-09-16 | Tyco Healthcare Group Lp | Easily cleaned atherectomy catheters and methods of use |
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 |
US8461744B2 (en) | 2009-07-15 | 2013-06-11 | Ethicon Endo-Surgery, Inc. | Rotating transducer mount for ultrasonic surgical instruments |
US8663220B2 (en) | 2009-07-15 | 2014-03-04 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments |
US9017326B2 (en) | 2009-07-15 | 2015-04-28 | Ethicon Endo-Surgery, Inc. | Impedance monitoring apparatus, system, and method for ultrasonic surgical instruments |
USRE47996E1 (en) | 2009-10-09 | 2020-05-19 | Ethicon Llc | Surgical generator for ultrasonic and electrosurgical devices |
US9039695B2 (en) | 2009-10-09 | 2015-05-26 | Ethicon Endo-Surgery, Inc. | Surgical generator for ultrasonic and electrosurgical devices |
US10172669B2 (en) | 2009-10-09 | 2019-01-08 | Ethicon Llc | Surgical instrument comprising an energy trigger lockout |
US9168054B2 (en) | 2009-10-09 | 2015-10-27 | 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 |
US10441345B2 (en) | 2009-10-09 | 2019-10-15 | Ethicon Llc | Surgical generator for ultrasonic and electrosurgical devices |
BR112012013389A2 (en) | 2009-12-02 | 2018-03-06 | Tyco Healthcare | methods and devices for cutting a fabric |
CA2783301C (en) | 2009-12-11 | 2015-02-24 | Tyco Healthcare Group Lp | Material removal device having improved material capture efficiency and methods of use |
US8382782B2 (en) | 2010-02-11 | 2013-02-26 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments with partially rotating blade and fixed pad arrangement |
US8419759B2 (en) | 2010-02-11 | 2013-04-16 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instrument with comb-like tissue trimming device |
US8961547B2 (en) | 2010-02-11 | 2015-02-24 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments with moving cutting implement |
US8579928B2 (en) | 2010-02-11 | 2013-11-12 | Ethicon Endo-Surgery, Inc. | Outer sheath and blade arrangements for ultrasonic surgical instruments |
US9259234B2 (en) | 2010-02-11 | 2016-02-16 | Ethicon Endo-Surgery, Llc | Ultrasonic surgical instruments with rotatable blade and hollow sheath arrangements |
US8531064B2 (en) | 2010-02-11 | 2013-09-10 | Ethicon Endo-Surgery, Inc. | Ultrasonically powered surgical instruments with rotating cutting implement |
US8486096B2 (en) | 2010-02-11 | 2013-07-16 | Ethicon Endo-Surgery, Inc. | Dual purpose surgical instrument for cutting and coagulating tissue |
US8951272B2 (en) | 2010-02-11 | 2015-02-10 | Ethicon Endo-Surgery, Inc. | Seal arrangements for ultrasonically powered surgical instruments |
US8323302B2 (en) * | 2010-02-11 | 2012-12-04 | Ethicon Endo-Surgery, Inc. | Methods of using ultrasonically powered surgical instruments with rotatable cutting implements |
US8469981B2 (en) | 2010-02-11 | 2013-06-25 | Ethicon Endo-Surgery, Inc. | Rotatable cutting implement arrangements for ultrasonic surgical instruments |
CN103068330B (en) | 2010-04-09 | 2016-06-29 | Vessix血管股份有限公司 | Power for treating tissue occurs and controls device |
US9192790B2 (en) | 2010-04-14 | 2015-11-24 | Boston Scientific Scimed, Inc. | Focused ultrasonic renal denervation |
US8211354B2 (en) | 2010-05-18 | 2012-07-03 | Cook Medical Technologies Llc | Balloon with integral retention of a dilation element |
GB2480498A (en) | 2010-05-21 | 2011-11-23 | Ethicon Endo Surgery Inc | Medical device comprising RF circuitry |
US8473067B2 (en) | 2010-06-11 | 2013-06-25 | Boston Scientific Scimed, Inc. | Renal denervation and stimulation employing wireless vascular energy transfer arrangement |
EP2742881B1 (en) | 2010-06-14 | 2015-10-07 | Covidien LP | Material removal device |
CA2805425C (en) | 2010-07-15 | 2019-07-23 | Corinthian Ophthalmic, Inc. | Ophthalmic drug delivery |
US10154923B2 (en) | 2010-07-15 | 2018-12-18 | Eyenovia, Inc. | Drop generating device |
EA201390121A8 (en) | 2010-07-15 | 2014-02-28 | Коринтиан Офтэлмик, Инк. | METHOD AND SYSTEM FOR PERFORMING REMOTE TREATMENT AND CONTROL |
JP5964826B2 (en) | 2010-07-15 | 2016-08-03 | アイノビア,インコーポレイティド | Drop generation device |
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 |
US9358365B2 (en) | 2010-07-30 | 2016-06-07 | Boston Scientific Scimed, Inc. | Precision electrode movement control for renal nerve ablation |
US9463062B2 (en) | 2010-07-30 | 2016-10-11 | Boston Scientific Scimed, Inc. | Cooled conductive balloon RF catheter for renal nerve ablation |
US9084609B2 (en) | 2010-07-30 | 2015-07-21 | Boston Scientific Scime, Inc. | Spiral balloon catheter for renal nerve ablation |
US9155589B2 (en) | 2010-07-30 | 2015-10-13 | Boston Scientific Scimed, Inc. | Sequential activation RF electrode set for renal nerve ablation |
US9408661B2 (en) | 2010-07-30 | 2016-08-09 | Patrick A. Haverkost | RF electrodes on multiple flexible wires for renal nerve ablation |
US8888809B2 (en) | 2010-10-01 | 2014-11-18 | Ethicon Endo-Surgery, Inc. | Surgical instrument with jaw member |
US8979890B2 (en) | 2010-10-01 | 2015-03-17 | Ethicon Endo-Surgery, Inc. | Surgical instrument with jaw member |
US9282991B2 (en) | 2010-10-06 | 2016-03-15 | Rex Medical, L.P. | Cutting wire assembly with coating for use with a catheter |
US8685050B2 (en) | 2010-10-06 | 2014-04-01 | Rex Medical L.P. | Cutting wire assembly for use with a catheter |
US8685049B2 (en) | 2010-11-18 | 2014-04-01 | Rex Medical L.P. | Cutting wire assembly for use with a catheter |
US9084610B2 (en) | 2010-10-21 | 2015-07-21 | Medtronic Ardian Luxembourg S.A.R.L. | Catheter apparatuses, systems, and methods for renal neuromodulation |
US8974451B2 (en) | 2010-10-25 | 2015-03-10 | Boston Scientific Scimed, Inc. | Renal nerve ablation using conductive fluid jet and RF energy |
US9220558B2 (en) | 2010-10-27 | 2015-12-29 | Boston Scientific Scimed, Inc. | RF renal denervation catheter with multiple independent electrodes |
JP5636114B2 (en) | 2010-10-28 | 2014-12-03 | コヴィディエン リミテッド パートナーシップ | Substance removal device and method of use |
CN103281964B (en) | 2010-11-11 | 2015-09-30 | 科维蒂恩有限合伙公司 | The flexibility possessing imaging capability subtracts the method for go out conduit and manufacture conduit |
US9028485B2 (en) | 2010-11-15 | 2015-05-12 | Boston Scientific Scimed, Inc. | Self-expanding cooling electrode for renal nerve ablation |
US9089350B2 (en) | 2010-11-16 | 2015-07-28 | Boston Scientific Scimed, Inc. | Renal denervation catheter with RF electrode and integral contrast dye injection arrangement |
US9668811B2 (en) | 2010-11-16 | 2017-06-06 | Boston Scientific Scimed, Inc. | Minimally invasive access for renal nerve ablation |
US9326751B2 (en) | 2010-11-17 | 2016-05-03 | Boston Scientific Scimed, Inc. | Catheter guidance of external energy for renal denervation |
US9060761B2 (en) | 2010-11-18 | 2015-06-23 | Boston Scientific Scime, Inc. | Catheter-focused magnetic field induced renal nerve ablation |
US9023034B2 (en) | 2010-11-22 | 2015-05-05 | Boston Scientific Scimed, Inc. | Renal ablation electrode with force-activatable conduction apparatus |
US8702736B2 (en) | 2010-11-22 | 2014-04-22 | Rex Medical L.P. | Cutting wire assembly for use with a catheter |
US9192435B2 (en) | 2010-11-22 | 2015-11-24 | Boston Scientific Scimed, Inc. | Renal denervation catheter with cooled RF electrode |
US20120157993A1 (en) | 2010-12-15 | 2012-06-21 | Jenson Mark L | Bipolar Off-Wall Electrode Device for Renal Nerve Ablation |
CN203354638U (en) | 2010-12-21 | 2013-12-25 | 泰尔茂株式会社 | Balloon catheter and electrification system |
US8491615B2 (en) * | 2010-12-29 | 2013-07-23 | Boston Scientific Scimed, Inc. | Cutting balloon catheter |
US9220561B2 (en) | 2011-01-19 | 2015-12-29 | Boston Scientific Scimed, Inc. | Guide-compatible large-electrode catheter for renal nerve ablation with reduced arterial injury |
CA2832311A1 (en) | 2011-04-08 | 2012-11-29 | Covidien Lp | Iontophoresis drug delivery system and method for denervation of the renal sympathetic nerve and iontophoretic drug delivery |
US8968293B2 (en) | 2011-04-12 | 2015-03-03 | Covidien Lp | Systems and methods for calibrating power measurements in an electrosurgical generator |
CN103930061B (en) | 2011-04-25 | 2016-09-14 | 美敦力阿迪安卢森堡有限责任公司 | Relevant low temperature sacculus for restricted conduit wall cryogenic ablation limits the device and method disposed |
CN103813745B (en) | 2011-07-20 | 2016-06-29 | 波士顿科学西美德公司 | In order to visualize, be directed at and to melt transcutaneous device and the method for nerve |
US9259265B2 (en) | 2011-07-22 | 2016-02-16 | Ethicon Endo-Surgery, Llc | Surgical instruments for tensioning tissue |
CN103813829B (en) | 2011-07-22 | 2016-05-18 | 波士顿科学西美德公司 | There is the neuromodulation system of the neuromodulation element that can be positioned in spiral guiding piece |
USD691265S1 (en) | 2011-08-23 | 2013-10-08 | Covidien Ag | Control assembly for portable surgical device |
WO2013033426A2 (en) | 2011-09-01 | 2013-03-07 | Covidien Lp | Catheter with helical drive shaft and methods of manufacture |
WO2013055826A1 (en) | 2011-10-10 | 2013-04-18 | Boston Scientific Scimed, Inc. | Medical devices including ablation electrodes |
US10085799B2 (en) | 2011-10-11 | 2018-10-02 | Boston Scientific Scimed, Inc. | Off-wall electrode device and methods for nerve modulation |
US9420955B2 (en) | 2011-10-11 | 2016-08-23 | Boston Scientific Scimed, Inc. | Intravascular temperature monitoring system and method |
US9364284B2 (en) | 2011-10-12 | 2016-06-14 | Boston Scientific Scimed, Inc. | Method of making an off-wall spacer cage |
EP2768563B1 (en) | 2011-10-18 | 2016-11-09 | Boston Scientific Scimed, Inc. | Deflectable medical devices |
EP2768568B1 (en) | 2011-10-18 | 2020-05-06 | Boston Scientific Scimed, Inc. | Integrated crossing balloon catheter |
JP6234932B2 (en) | 2011-10-24 | 2017-11-22 | エシコン・エンド−サージェリィ・インコーポレイテッドEthicon Endo−Surgery,Inc. | Medical instruments |
USD687549S1 (en) | 2011-10-24 | 2013-08-06 | Ethicon Endo-Surgery, Inc. | Surgical instrument |
US8574247B2 (en) | 2011-11-08 | 2013-11-05 | Shockwave Medical, Inc. | Shock wave valvuloplasty device with moveable shock wave generator |
CN108095821B (en) | 2011-11-08 | 2021-05-25 | 波士顿科学西美德公司 | Orifice renal nerve ablation |
US9119600B2 (en) | 2011-11-15 | 2015-09-01 | Boston Scientific Scimed, Inc. | Device and methods for renal nerve modulation monitoring |
US9119632B2 (en) | 2011-11-21 | 2015-09-01 | Boston Scientific Scimed, Inc. | Deflectable renal nerve ablation catheter |
WO2013090468A1 (en) | 2011-12-12 | 2013-06-20 | Corinthian Ophthalmic, Inc. | High modulus polymeric ejector mechanism, ejector device, and methods of use |
US9265969B2 (en) | 2011-12-21 | 2016-02-23 | Cardiac Pacemakers, Inc. | Methods for modulating cell function |
EP2793724B1 (en) | 2011-12-23 | 2016-10-12 | Vessix Vascular, Inc. | Apparatuses for remodeling tissue of or adjacent to a body passage |
CN104135958B (en) | 2011-12-28 | 2017-05-03 | 波士顿科学西美德公司 | By the apparatus and method that have the new ablation catheter modulation nerve of polymer ablation |
US9050106B2 (en) | 2011-12-29 | 2015-06-09 | Boston Scientific Scimed, Inc. | Off-wall electrode device and methods for nerve modulation |
WO2013119545A1 (en) | 2012-02-10 | 2013-08-15 | Ethicon-Endo Surgery, Inc. | Robotically controlled surgical instrument |
US9226766B2 (en) | 2012-04-09 | 2016-01-05 | Ethicon Endo-Surgery, Inc. | Serial communication protocol for medical device |
US9724118B2 (en) | 2012-04-09 | 2017-08-08 | Ethicon Endo-Surgery, Llc | Techniques for cutting and coagulating tissue for ultrasonic surgical instruments |
US9241731B2 (en) | 2012-04-09 | 2016-01-26 | Ethicon Endo-Surgery, Inc. | Rotatable electrical connection for ultrasonic surgical instruments |
US9237921B2 (en) | 2012-04-09 | 2016-01-19 | Ethicon Endo-Surgery, Inc. | Devices and techniques for cutting and coagulating tissue |
US9439668B2 (en) | 2012-04-09 | 2016-09-13 | Ethicon Endo-Surgery, Llc | Switch arrangements for ultrasonic surgical instruments |
WO2013169927A1 (en) | 2012-05-08 | 2013-11-14 | Boston Scientific Scimed, Inc. | Renal nerve modulation devices |
US9642673B2 (en) | 2012-06-27 | 2017-05-09 | Shockwave Medical, Inc. | Shock wave balloon catheter with multiple shock wave sources |
US20140005705A1 (en) | 2012-06-29 | 2014-01-02 | Ethicon Endo-Surgery, Inc. | Surgical instruments with articulating shafts |
US9820768B2 (en) | 2012-06-29 | 2017-11-21 | Ethicon Llc | Ultrasonic surgical instruments with control mechanisms |
US9408622B2 (en) | 2012-06-29 | 2016-08-09 | Ethicon Endo-Surgery, Llc | Surgical instruments with articulating shafts |
US20140005702A1 (en) | 2012-06-29 | 2014-01-02 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments with distally positioned transducers |
US9351754B2 (en) | 2012-06-29 | 2016-05-31 | Ethicon Endo-Surgery, Llc | Ultrasonic surgical instruments with distally positioned jaw assemblies |
US9283045B2 (en) | 2012-06-29 | 2016-03-15 | Ethicon Endo-Surgery, Llc | Surgical instruments with fluid management system |
US9198714B2 (en) | 2012-06-29 | 2015-12-01 | Ethicon Endo-Surgery, Inc. | Haptic feedback devices for surgical robot |
US9326788B2 (en) | 2012-06-29 | 2016-05-03 | Ethicon Endo-Surgery, Llc | Lockout mechanism for use with robotic electrosurgical device |
US9226767B2 (en) | 2012-06-29 | 2016-01-05 | Ethicon Endo-Surgery, Inc. | Closed feedback control for electrosurgical device |
US9393037B2 (en) | 2012-06-29 | 2016-07-19 | Ethicon Endo-Surgery, Llc | Surgical instruments with articulating shafts |
WO2014025397A1 (en) | 2012-08-06 | 2014-02-13 | Shockwave Medical, Inc. | Low profile electrodes for an angioplasty shock wave catheter |
EP2879597B1 (en) | 2012-08-06 | 2016-09-21 | Shockwave Medical, Inc. | Shockwave catheter |
US9138249B2 (en) | 2012-08-17 | 2015-09-22 | Shockwave Medical, Inc. | Shock wave catheter system with arc preconditioning |
CN104540465A (en) | 2012-08-24 | 2015-04-22 | 波士顿科学西美德公司 | Intravascular catheter with a balloon comprising separate microporous regions |
US9333000B2 (en) | 2012-09-13 | 2016-05-10 | Shockwave Medical, Inc. | Shockwave catheter system with energy control |
US9579157B2 (en) | 2012-09-13 | 2017-02-28 | Covidien Lp | Cleaning device for medical instrument and method of use |
US9522012B2 (en) | 2012-09-13 | 2016-12-20 | Shockwave Medical, Inc. | Shockwave catheter system with energy control |
CN104780859B (en) | 2012-09-17 | 2017-07-25 | 波士顿科学西美德公司 | Self-positioning electrode system and method for renal regulation |
US10549127B2 (en) | 2012-09-21 | 2020-02-04 | Boston Scientific Scimed, Inc. | Self-cooling ultrasound ablation catheter |
WO2014047411A1 (en) | 2012-09-21 | 2014-03-27 | Boston Scientific Scimed, Inc. | System for nerve modulation and innocuous thermal gradient nerve block |
WO2014052181A1 (en) | 2012-09-28 | 2014-04-03 | Ethicon Endo-Surgery, Inc. | Multi-function bi-polar forceps |
US10835305B2 (en) | 2012-10-10 | 2020-11-17 | Boston Scientific Scimed, Inc. | Renal nerve modulation devices and methods |
US9044575B2 (en) | 2012-10-22 | 2015-06-02 | Medtronic Adrian Luxembourg S.a.r.l. | Catheters with enhanced flexibility and associated devices, systems, and methods |
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 |
US9943329B2 (en) | 2012-11-08 | 2018-04-17 | Covidien Lp | Tissue-removing catheter with rotatable cutter |
US20140135804A1 (en) | 2012-11-15 | 2014-05-15 | Ethicon Endo-Surgery, Inc. | Ultrasonic and electrosurgical devices |
CN105188830B (en) * | 2012-12-28 | 2019-06-07 | 巴德血管外围设备公司 | Pass through the drug delivery of mechanical oscillation sacculus |
WO2014122788A1 (en) * | 2013-02-08 | 2014-08-14 | テルモ株式会社 | Medical instrument |
WO2014140715A2 (en) | 2013-03-11 | 2014-09-18 | Northgate Technologies Inc. | Unfocused electrohydraulic lithotripter |
WO2014163987A1 (en) | 2013-03-11 | 2014-10-09 | Boston Scientific Scimed, Inc. | Medical devices for modulating nerves |
US9693821B2 (en) | 2013-03-11 | 2017-07-04 | Boston Scientific Scimed, Inc. | Medical devices for modulating nerves |
US10842567B2 (en) | 2013-03-13 | 2020-11-24 | The Spectranetics Corporation | Laser-induced fluid filled balloon catheter |
US9808311B2 (en) | 2013-03-13 | 2017-11-07 | Boston Scientific Scimed, Inc. | Deflectable medical devices |
US9320530B2 (en) * | 2013-03-13 | 2016-04-26 | The Spectranetics Corporation | Assisted cutting balloon |
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 |
JP6220044B2 (en) | 2013-03-15 | 2017-10-25 | ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. | Medical device for renal nerve ablation |
US9297845B2 (en) | 2013-03-15 | 2016-03-29 | Boston Scientific Scimed, Inc. | Medical devices and methods for treatment of hypertension that utilize impedance compensation |
US10265122B2 (en) | 2013-03-15 | 2019-04-23 | Boston Scientific Scimed, Inc. | Nerve ablation devices and related methods of use |
EP2996754B1 (en) | 2013-05-18 | 2023-04-26 | Medtronic Ardian Luxembourg S.à.r.l. | Neuromodulation catheters with shafts for enhanced flexibility and control and associated devices and systems |
JP2016523147A (en) | 2013-06-21 | 2016-08-08 | ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. | Renal denervation balloon catheter with a riding-type electrode support |
US10022182B2 (en) | 2013-06-21 | 2018-07-17 | Boston Scientific Scimed, Inc. | Medical devices for renal nerve ablation having rotatable shafts |
US9707036B2 (en) | 2013-06-25 | 2017-07-18 | Boston Scientific Scimed, Inc. | Devices and methods for nerve modulation using localized indifferent electrodes |
WO2015002787A1 (en) | 2013-07-01 | 2015-01-08 | Boston Scientific Scimed, Inc. | Medical devices for renal nerve ablation |
US10413357B2 (en) | 2013-07-11 | 2019-09-17 | Boston Scientific Scimed, Inc. | Medical device with stretchable electrode assemblies |
EP3019105B1 (en) | 2013-07-11 | 2017-09-13 | Boston Scientific Scimed, Inc. | Devices for nerve modulation |
EP3019107A1 (en) * | 2013-07-12 | 2016-05-18 | Boston Scientific Scimed, Inc. | Apparatus and methods for renal denervation |
CN105682594B (en) | 2013-07-19 | 2018-06-22 | 波士顿科学国际有限公司 | Helical bipolar electrodes renal denervation dominates air bag |
EP3024406B1 (en) | 2013-07-22 | 2019-06-19 | Boston Scientific Scimed, Inc. | Medical devices for renal nerve ablation |
EP3024405A1 (en) | 2013-07-22 | 2016-06-01 | Boston Scientific Scimed, Inc. | Renal nerve ablation catheter having twist balloon |
WO2015027096A1 (en) | 2013-08-22 | 2015-02-26 | Boston Scientific Scimed, Inc. | Flexible circuit having improved adhesion to a renal nerve modulation balloon |
US9895194B2 (en) | 2013-09-04 | 2018-02-20 | Boston Scientific Scimed, Inc. | Radio frequency (RF) balloon catheter having flushing and cooling capability |
US9814514B2 (en) | 2013-09-13 | 2017-11-14 | Ethicon Llc | Electrosurgical (RF) medical instruments for cutting and coagulating tissue |
EP3043733A1 (en) | 2013-09-13 | 2016-07-20 | Boston Scientific Scimed, Inc. | Ablation balloon with vapor deposited cover layer |
US11246654B2 (en) | 2013-10-14 | 2022-02-15 | Boston Scientific Scimed, Inc. | Flexible renal nerve ablation devices and related methods of use and manufacture |
US9687166B2 (en) | 2013-10-14 | 2017-06-27 | Boston Scientific Scimed, Inc. | High resolution cardiac mapping electrode array catheter |
US9770606B2 (en) | 2013-10-15 | 2017-09-26 | Boston Scientific Scimed, Inc. | Ultrasound ablation catheter with cooling infusion and centering basket |
AU2013403325B2 (en) | 2013-10-15 | 2019-07-18 | Stryker Corporation | Device for creating a void space in a living tissue, the device including a handle with a control knob that can be set regardless of the orientation of the handle |
US9962223B2 (en) | 2013-10-15 | 2018-05-08 | Boston Scientific Scimed, Inc. | Medical device balloon |
EP3057521B1 (en) | 2013-10-18 | 2020-03-25 | Boston Scientific Scimed, Inc. | Balloon catheters with flexible conducting wires |
US10271898B2 (en) | 2013-10-25 | 2019-04-30 | Boston Scientific Scimed, Inc. | Embedded thermocouple in denervation flex circuit |
EP2870936B1 (en) * | 2013-11-07 | 2016-10-26 | Cook Medical Technologies LLC | Balloon catheter with lithotripsy amplification system |
US9265926B2 (en) | 2013-11-08 | 2016-02-23 | Ethicon Endo-Surgery, Llc | Electrosurgical devices |
US10286190B2 (en) | 2013-12-11 | 2019-05-14 | Cook Medical Technologies Llc | Balloon catheter with dynamic vessel engaging member |
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 |
EP3091922B1 (en) | 2014-01-06 | 2018-10-17 | Boston Scientific Scimed, Inc. | Tear resistant flex circuit assembly |
US9795436B2 (en) | 2014-01-07 | 2017-10-24 | Ethicon Llc | Harvesting energy from a surgical generator |
US9956384B2 (en) | 2014-01-24 | 2018-05-01 | Cook Medical Technologies Llc | Articulating balloon catheter and method for using the same |
EP3099377B1 (en) | 2014-01-27 | 2022-03-02 | Medtronic Ireland Manufacturing Unlimited Company | Neuromodulation catheters having jacketed neuromodulation elements and related devices |
US11000679B2 (en) | 2014-02-04 | 2021-05-11 | Boston Scientific Scimed, Inc. | Balloon protection and rewrapping devices and related methods of use |
EP3424453A1 (en) | 2014-02-04 | 2019-01-09 | Boston Scientific Scimed, Inc. | Alternative placement of thermal sensors on bipolar electrode |
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 |
US20150297763A1 (en) * | 2014-04-17 | 2015-10-22 | Boston Scientific Scimed, Inc. | Devices and methods for therapeutic heat treatment |
WO2015164280A1 (en) | 2014-04-24 | 2015-10-29 | Medtronic Ardian Luxembourg S.A.R.L. | Neuromodulation catheters having braided shafts and associated systems and methods |
US10709490B2 (en) | 2014-05-07 | 2020-07-14 | Medtronic Ardian Luxembourg S.A.R.L. | Catheter assemblies comprising a direct heating element for renal neuromodulation and associated systems and methods |
US9730715B2 (en) | 2014-05-08 | 2017-08-15 | Shockwave Medical, Inc. | Shock wave guide wire |
US10463842B2 (en) | 2014-06-04 | 2019-11-05 | Cagent Vascular, Llc | Cage for medical balloon |
WO2015200702A1 (en) | 2014-06-27 | 2015-12-30 | Covidien Lp | Cleaning device for catheter and catheter including the same |
US9700333B2 (en) | 2014-06-30 | 2017-07-11 | Ethicon Llc | Surgical instrument with variable tissue compression |
US10285724B2 (en) | 2014-07-31 | 2019-05-14 | Ethicon Llc | Actuation mechanisms and load adjustment assemblies for surgical instruments |
US9655998B2 (en) * | 2014-08-07 | 2017-05-23 | Cook Medical Technologies Llc | Encapsulated drug compositions and methods of use thereof |
WO2016073490A1 (en) | 2014-11-03 | 2016-05-12 | Cagent Vascular, Llc | Serration balloon |
WO2016090122A1 (en) | 2014-12-03 | 2016-06-09 | PAVmed Inc. | Systems and methods for percutaneous division of fibrous structures |
US10639092B2 (en) | 2014-12-08 | 2020-05-05 | Ethicon Llc | Electrode configurations for surgical instruments |
US10159524B2 (en) | 2014-12-22 | 2018-12-25 | Ethicon Llc | High power battery powered RF amplifier topology |
US11058492B2 (en) | 2014-12-30 | 2021-07-13 | The Spectranetics Corporation | Laser-induced pressure wave emitting catheter sheath |
WO2016109737A1 (en) | 2014-12-30 | 2016-07-07 | The Spectranetics Corporation | Electrically-induced fluid filled balloon catheter |
EP3240600B1 (en) | 2014-12-30 | 2019-05-08 | The Spectranetics Corporation | Electrically-induced pressure wave emitting catheter sheath |
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 |
US10350341B2 (en) * | 2015-03-20 | 2019-07-16 | Drexel University | Impellers, blood pumps, and methods of treating a subject |
US10595929B2 (en) | 2015-03-24 | 2020-03-24 | Ethicon Llc | Surgical instruments with firing system overload protection mechanisms |
US10314667B2 (en) | 2015-03-25 | 2019-06-11 | Covidien Lp | Cleaning device for cleaning medical instrument |
US10314638B2 (en) | 2015-04-07 | 2019-06-11 | Ethicon Llc | Articulating radio frequency (RF) tissue seal with articulating state sensing |
EP3281669B1 (en) * | 2015-04-10 | 2020-05-27 | Goodman Co., Ltd. | Balloon catheter |
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 |
US10357303B2 (en) | 2015-06-30 | 2019-07-23 | Ethicon Llc | Translatable outer tube for sealing using shielded lap chole dissector |
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 |
US10034704B2 (en) | 2015-06-30 | 2018-07-31 | Ethicon Llc | Surgical instrument with user adaptable algorithms |
US11129669B2 (en) | 2015-06-30 | 2021-09-28 | Cilag Gmbh International | Surgical system with user adaptable techniques based on tissue type |
US11141213B2 (en) | 2015-06-30 | 2021-10-12 | Cilag Gmbh International | Surgical instrument with user adaptable techniques |
US10154852B2 (en) | 2015-07-01 | 2018-12-18 | Ethicon Llc | Ultrasonic surgical blade with improved cutting and coagulation features |
US10799287B2 (en) | 2015-07-07 | 2020-10-13 | Boston Scientific Scimed, Inc. | Medical device having extenable members |
US10292721B2 (en) | 2015-07-20 | 2019-05-21 | Covidien Lp | Tissue-removing catheter including movable distal tip |
CN108348734B (en) | 2015-09-17 | 2021-11-09 | 开金血管公司 | Wedge-shaped cutter of medical air bag |
US10194973B2 (en) | 2015-09-30 | 2019-02-05 | Ethicon Llc | Generator for digitally generating electrical signal waveforms for electrosurgical and ultrasonic surgical instruments |
US10314664B2 (en) | 2015-10-07 | 2019-06-11 | Covidien Lp | Tissue-removing catheter and tissue-removing element with depth stop |
US10959771B2 (en) | 2015-10-16 | 2021-03-30 | Ethicon Llc | Suction and irrigation sealing grasper |
US10595930B2 (en) | 2015-10-16 | 2020-03-24 | Ethicon Llc | Electrode wiping surgical device |
WO2017087195A1 (en) | 2015-11-18 | 2017-05-26 | Shockwave Medical, Inc. | Shock wave electrodes |
US10179022B2 (en) | 2015-12-30 | 2019-01-15 | Ethicon Llc | Jaw position impedance limiter for electrosurgical instrument |
US10959806B2 (en) | 2015-12-30 | 2021-03-30 | Ethicon Llc | Energized medical device with reusable handle |
US10575892B2 (en) | 2015-12-31 | 2020-03-03 | Ethicon Llc | Adapter for electrical surgical instruments |
US11051840B2 (en) | 2016-01-15 | 2021-07-06 | Ethicon Llc | Modular battery powered handheld surgical instrument with reusable asymmetric handle housing |
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 |
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 |
US10555769B2 (en) | 2016-02-22 | 2020-02-11 | Ethicon Llc | Flexible circuits for electrosurgical instrument |
US10226265B2 (en) | 2016-04-25 | 2019-03-12 | Shockwave Medical, Inc. | Shock wave device with polarity switching |
US10485607B2 (en) | 2016-04-29 | 2019-11-26 | Ethicon Llc | Jaw structure with distal closure for electrosurgical instruments |
US10987156B2 (en) | 2016-04-29 | 2021-04-27 | Ethicon Llc | Electrosurgical instrument with electrically conductive gap setting member and electrically insulative tissue engaging members |
US10702329B2 (en) | 2016-04-29 | 2020-07-07 | Ethicon Llc | Jaw structure with distal post for electrosurgical instruments |
US10646269B2 (en) | 2016-04-29 | 2020-05-12 | Ethicon Llc | Non-linear jaw gap for electrosurgical instruments |
US10856934B2 (en) | 2016-04-29 | 2020-12-08 | Ethicon Llc | Electrosurgical instrument with electrically conductive gap setting and tissue engaging members |
US10456193B2 (en) | 2016-05-03 | 2019-10-29 | Ethicon Llc | Medical device with a bilateral jaw configuration for nerve stimulation |
US10245064B2 (en) | 2016-07-12 | 2019-04-02 | Ethicon Llc | Ultrasonic surgical instrument with piezoelectric central lumen transducer |
US10893883B2 (en) | 2016-07-13 | 2021-01-19 | Ethicon Llc | Ultrasonic assembly for use with ultrasonic surgical instruments |
US10842522B2 (en) | 2016-07-15 | 2020-11-24 | Ethicon Llc | Ultrasonic surgical instruments having offset blades |
US10376305B2 (en) | 2016-08-05 | 2019-08-13 | Ethicon Llc | Methods and systems for advanced harmonic energy |
US10285723B2 (en) | 2016-08-09 | 2019-05-14 | Ethicon Llc | Ultrasonic surgical blade with improved heel portion |
USD847990S1 (en) | 2016-08-16 | 2019-05-07 | Ethicon Llc | Surgical instrument |
US10828056B2 (en) | 2016-08-25 | 2020-11-10 | Ethicon Llc | Ultrasonic transducer to waveguide acoustic coupling, connections, and configurations |
US10952759B2 (en) | 2016-08-25 | 2021-03-23 | Ethicon Llc | Tissue loading of a surgical instrument |
US10751117B2 (en) | 2016-09-23 | 2020-08-25 | Ethicon Llc | Electrosurgical instrument with fluid diverter |
US10646240B2 (en) | 2016-10-06 | 2020-05-12 | Shockwave Medical, Inc. | Aortic leaflet repair using shock wave applicators |
EP3534808A4 (en) | 2016-11-04 | 2020-06-10 | Les Solutions Médicales Soundbite Inc. | Device for delivering mechanical waves through a balloon catheter |
WO2018094077A1 (en) | 2016-11-16 | 2018-05-24 | Cagent Vascular, Llc | Systems and methods of depositing drug into tissue through serrations |
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 |
US10357264B2 (en) | 2016-12-06 | 2019-07-23 | Shockwave Medical, Inc. | Shock wave balloon catheter with insertable electrodes |
US11033325B2 (en) | 2017-02-16 | 2021-06-15 | Cilag Gmbh International | Electrosurgical instrument with telescoping suction port and debris cleaner |
US10799284B2 (en) | 2017-03-15 | 2020-10-13 | Ethicon Llc | Electrosurgical instrument with textured jaws |
US11497546B2 (en) | 2017-03-31 | 2022-11-15 | Cilag Gmbh International | Area ratios of patterned coatings on RF electrodes to reduce sticking |
US10441300B2 (en) | 2017-04-19 | 2019-10-15 | Shockwave Medical, Inc. | Drug delivery shock wave balloon catheter system |
US11020135B1 (en) | 2017-04-25 | 2021-06-01 | Shockwave Medical, Inc. | Shock wave device for treating vascular plaques |
KR20240034855A (en) | 2017-06-10 | 2024-03-14 | 아이노비아 인코포레이티드 | Methods and devices for handling a fluid and delivering the fluid to the eye |
US10966737B2 (en) | 2017-06-19 | 2021-04-06 | Shockwave Medical, Inc. | Device and method for generating forward directed shock waves |
US10603117B2 (en) | 2017-06-28 | 2020-03-31 | Ethicon Llc | Articulation state detection mechanisms |
US10820920B2 (en) | 2017-07-05 | 2020-11-03 | Ethicon Llc | Reusable ultrasonic medical devices and methods of their use |
US11033323B2 (en) | 2017-09-29 | 2021-06-15 | Cilag Gmbh International | Systems and methods for managing fluid and suction in electrosurgical systems |
US11490951B2 (en) | 2017-09-29 | 2022-11-08 | Cilag Gmbh International | Saline contact with electrodes |
US11484358B2 (en) | 2017-09-29 | 2022-11-01 | Cilag Gmbh International | Flexible electrosurgical instrument |
US10709462B2 (en) | 2017-11-17 | 2020-07-14 | Shockwave Medical, Inc. | Low profile electrodes for a shock wave catheter |
WO2019199672A1 (en) | 2018-04-09 | 2019-10-17 | Boston Scientific Scimed, Inc. | Cutting balloon basket |
CN112367934A (en) | 2018-06-21 | 2021-02-12 | 冲击波医疗公司 | System for treating an occlusion in a body lumen |
CN112203713B (en) * | 2018-07-09 | 2023-06-02 | 株式会社戈德曼 | Balloon catheter |
CN112739406A (en) | 2018-07-25 | 2021-04-30 | 开金血管有限公司 | Medical balloon catheter with enhanced pushability |
US11849986B2 (en) | 2019-04-24 | 2023-12-26 | Stryker Corporation | Systems and methods for off-axis augmentation of a vertebral body |
EP4034006A1 (en) | 2019-09-24 | 2022-08-03 | Shockwave Medical, Inc. | System for treating thrombus in body lumens |
US11812987B2 (en) | 2019-11-27 | 2023-11-14 | Boston Scientific Scimed, Inc. | Cutting balloon catheter |
US11786294B2 (en) | 2019-12-30 | 2023-10-17 | Cilag Gmbh International | Control program for modular combination energy device |
US11944366B2 (en) | 2019-12-30 | 2024-04-02 | Cilag Gmbh International | Asymmetric segmented ultrasonic support pad for cooperative engagement with a movable RF electrode |
US11786291B2 (en) | 2019-12-30 | 2023-10-17 | Cilag Gmbh International | Deflectable support of RF energy electrode with respect to opposing ultrasonic blade |
US11707318B2 (en) | 2019-12-30 | 2023-07-25 | Cilag Gmbh International | Surgical instrument with jaw alignment features |
US11812957B2 (en) | 2019-12-30 | 2023-11-14 | Cilag Gmbh International | Surgical instrument comprising a signal interference resolution system |
US20210196349A1 (en) | 2019-12-30 | 2021-07-01 | Ethicon Llc | Electrosurgical instrument with flexible wiring assemblies |
US11696776B2 (en) | 2019-12-30 | 2023-07-11 | Cilag Gmbh International | Articulatable surgical instrument |
US11937866B2 (en) | 2019-12-30 | 2024-03-26 | Cilag Gmbh International | Method for an electrosurgical procedure |
US20210196362A1 (en) | 2019-12-30 | 2021-07-01 | Ethicon Llc | Electrosurgical end effectors with thermally insulative and thermally conductive portions |
US11660089B2 (en) | 2019-12-30 | 2023-05-30 | Cilag Gmbh International | Surgical instrument comprising a sensing 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 |
US11779387B2 (en) | 2019-12-30 | 2023-10-10 | Cilag Gmbh International | Clamp arm jaw to minimize tissue sticking and improve tissue control |
US11779329B2 (en) | 2019-12-30 | 2023-10-10 | Cilag Gmbh International | Surgical instrument comprising a flex circuit including a sensor 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 |
US11950797B2 (en) | 2019-12-30 | 2024-04-09 | Cilag Gmbh International | Deflectable electrode with higher distal bias relative to proximal bias |
US11452525B2 (en) | 2019-12-30 | 2022-09-27 | Cilag Gmbh International | Surgical instrument comprising an adjustment system |
CN113425380A (en) * | 2021-06-01 | 2021-09-24 | 青岛博泰医疗器械有限责任公司 | Balloon catheter for linear segmentation of glandular tissue |
US11957342B2 (en) | 2021-11-01 | 2024-04-16 | Cilag Gmbh International | Devices, systems, and methods for detecting tissue and foreign objects during a surgical operation |
US20230248386A1 (en) * | 2022-02-10 | 2023-08-10 | Boston Scientific Scimed, Inc. | Methods of treating vascular lesions |
Family Cites Families (33)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4273128A (en) * | 1980-01-14 | 1981-06-16 | Lary Banning G | Coronary cutting and dilating instrument |
US5000185A (en) * | 1986-02-28 | 1991-03-19 | Cardiovascular Imaging Systems, Inc. | Method for intravascular two-dimensional ultrasonography and recanalization |
US4838853A (en) * | 1987-02-05 | 1989-06-13 | Interventional Technologies Inc. | Apparatus for trimming meniscus |
US4860744A (en) * | 1987-11-02 | 1989-08-29 | Raj K. Anand | Thermoelectrically controlled heat medical catheter |
US5904679A (en) * | 1989-01-18 | 1999-05-18 | Applied Medical Resources Corporation | Catheter with electrosurgical cutter |
US5057107A (en) * | 1989-04-13 | 1991-10-15 | Everest Medical Corporation | Ablation catheter with selectively deployable electrodes |
US5046503A (en) * | 1989-04-26 | 1991-09-10 | Advanced Cardiovascular Systems, Inc. | Angioplasty autoperfusion catheter flow measurement method and apparatus |
US5059203A (en) * | 1989-05-17 | 1991-10-22 | Husted Royce Hill | Powered microsurgical tool |
US5064994A (en) * | 1989-10-18 | 1991-11-12 | Urban Paul L | Fast-heating high-temperature fiber cutting tool |
US5085662A (en) * | 1989-11-13 | 1992-02-04 | Scimed Life Systems, Inc. | Atherectomy catheter and related components |
US5181920A (en) * | 1990-06-08 | 1993-01-26 | Devices For Vascular Intervention, Inc. | Atherectomy device with angioplasty balloon and method |
US5320634A (en) * | 1990-07-03 | 1994-06-14 | Interventional Technologies, Inc. | Balloon catheter with seated cutting edges |
US5196024A (en) * | 1990-07-03 | 1993-03-23 | Cedars-Sinai Medical Center | Balloon catheter with cutting edge |
US5916192A (en) * | 1991-01-11 | 1999-06-29 | Advanced Cardiovascular Systems, Inc. | Ultrasonic angioplasty-atherectomy catheter and method of use |
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 |
US5695510A (en) * | 1992-02-20 | 1997-12-09 | Hood; Larry L. | Ultrasonic knife |
EP0820728B1 (en) | 1992-05-05 | 2000-09-13 | Advanced Cardiovascular Systems, Inc. | Ultrasonic angioplasty catheter device |
US5243997A (en) * | 1992-09-14 | 1993-09-14 | Interventional Technologies, Inc. | Vibrating device for a guide wire |
CA2114988A1 (en) * | 1993-02-05 | 1994-08-06 | Matthew O'boyle | Ultrasonic angioplasty balloon catheter |
CA2118886C (en) | 1993-05-07 | 1998-12-08 | Dennis Vigil | Method and apparatus for dilatation of a stenotic vessel |
US5728089A (en) * | 1993-06-04 | 1998-03-17 | The Regents Of The University Of California | Microfabricated structure to be used in surgery |
US5549604A (en) * | 1994-12-06 | 1996-08-27 | Conmed Corporation | Non-Stick electroconductive amorphous silica coating |
US5665062A (en) * | 1995-01-23 | 1997-09-09 | Houser; Russell A. | Atherectomy catheter and RF cutting method |
US5980518A (en) * | 1995-10-27 | 1999-11-09 | Carr; William N. | Microcautery surgical tool |
US5846218A (en) * | 1996-09-05 | 1998-12-08 | Pharmasonics, Inc. | Balloon catheters having ultrasonically driven interface surfaces and methods for their use |
US6464660B2 (en) * | 1996-09-05 | 2002-10-15 | Pharmasonics, Inc. | Balloon catheters having ultrasonically driven interface surfaces and methods for their use |
US6083232A (en) * | 1996-09-27 | 2000-07-04 | Advanced Cardivascular Systems, Inc. | Vibrating stent for opening calcified lesions |
DE19645107C2 (en) * | 1996-11-01 | 1999-06-24 | Leica Ag | Microtome with an oscillating knife |
US5882329A (en) * | 1997-02-12 | 1999-03-16 | Prolifix Medical, Inc. | Apparatus and method for removing stenotic material from stents |
US5944717A (en) * | 1997-05-12 | 1999-08-31 | The Regents Of The University Of California | Micromachined electrical cauterizer |
US6306151B1 (en) * | 1998-03-31 | 2001-10-23 | Interventional Technologies Inc. | Balloon with reciprocating stent incisor |
US6383183B1 (en) * | 1998-04-09 | 2002-05-07 | Olympus Optical Co., Ltd. | High frequency treatment apparatus |
EP1169970A1 (en) | 2000-07-04 | 2002-01-09 | Transgene S.A. | Device for the administration of a composition in a conduit of a human or animal body |
-
2002
- 2002-06-11 US US10/167,214 patent/US7153315B2/en not_active Expired - Fee Related
-
2003
- 2003-05-21 AT AT03734122T patent/ATE456935T1/en not_active IP Right Cessation
- 2003-05-21 AU AU2003239557A patent/AU2003239557A1/en not_active Abandoned
- 2003-05-21 EP EP03734122A patent/EP1524943B1/en not_active Expired - Lifetime
- 2003-05-21 JP JP2004510642A patent/JP2005529652A/en active Pending
- 2003-05-21 DE DE60331191T patent/DE60331191D1/en not_active Expired - Lifetime
- 2003-05-21 CA CA002488870A patent/CA2488870A1/en not_active Abandoned
- 2003-05-21 WO PCT/US2003/016141 patent/WO2003103516A1/en active Application Filing
Also Published As
Publication number | Publication date |
---|---|
EP1524943B1 (en) | 2010-02-03 |
EP1524943A1 (en) | 2005-04-27 |
ATE456935T1 (en) | 2010-02-15 |
JP2005529652A (en) | 2005-10-06 |
AU2003239557A1 (en) | 2003-12-22 |
DE60331191D1 (en) | 2010-03-25 |
WO2003103516A1 (en) | 2003-12-18 |
US7153315B2 (en) | 2006-12-26 |
US20030229370A1 (en) | 2003-12-11 |
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Legal Events
Date | Code | Title | Description |
---|---|---|---|
EEER | Examination request | ||
FZDE | Discontinued |
Effective date: 20131105 |