CA2570914A1 - Medical stents - Google Patents
Medical stents Download PDFInfo
- Publication number
- CA2570914A1 CA2570914A1 CA002570914A CA2570914A CA2570914A1 CA 2570914 A1 CA2570914 A1 CA 2570914A1 CA 002570914 A CA002570914 A CA 002570914A CA 2570914 A CA2570914 A CA 2570914A CA 2570914 A1 CA2570914 A1 CA 2570914A1
- Authority
- CA
- Canada
- Prior art keywords
- stent
- polymer
- radiopaque
- strip
- medical
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
- A61F2220/005—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements using adhesives
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
- A61F2250/0067—Means for introducing or releasing pharmaceutical products into the body
- A61F2250/0068—Means for introducing or releasing pharmaceutical products into the body the pharmaceutical product being in a reservoir
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
- A61F2250/0096—Markers and sensors for detecting a position or changes of a position of an implant, e.g. RF sensors, ultrasound markers
- A61F2250/0098—Markers and sensors for detecting a position or changes of a position of an implant, e.g. RF sensors, ultrasound markers radio-opaque, e.g. radio-opaque markers
Abstract
Medical devices, particularly stents, including a polymer body with radiopaque material are disclosed. In some embodiments, a stent (10) can include a stent body (12) including a generally tubular member having a wall that defines at least one void (16), and a radiopaque material (20) bonded to the stent body by a polymer (18). The polymer can span the void, and the radiopaque material can be suspended within the void .
Description
MEDICAL STENTS
TECHNICAL FIELD
This invention relates to medical devices, such as, for example, endoprostheses.
BACKGROUND
The body includes various passageways such as arteries, other blood vessels, and other body lumens. For various treatments and diagnostic techniques, it is often desirable to deliver a medical device into these lumens. For example, these passageways sometimes become occluded or weakened. The passageways can be occluded by, e.g. a tumor, restricted by plaque, or weakened by an aneurysm. When this occurs, the passageway can be reopened or reinforced, or even replaced, with a medical endoprosthesis.
An endoprosthesis is typically a tubular member that is placed in a lumen in the body.
Examples of endoprostheses include stents and covered stents, sometimes called "stent-grafts".
An endoprosthesis can be delivered inside the body by a catheter that supports the endoprosthesis in a compacted or reduced-size form as the endoprosthesis is transported to a desired site. Upon reaching the site, the endoprosthesis is expanded, for example, so that it can contact the walls of the lumen. The expansion mechanism may include forcing the endoprosthesis to expand radially.
For example, the expansion mechanism can include the catheter carrying a balloon, which carries the endoprosthesis. The balloon can be inflated to deform and to fix the expanded endoprosthesis at a predetermined position in contact with the lumen wall. The balloon can then be deflated, and the catheter removed.
In another delivery technique, the endoprosthesis is self-expanding. For example, the endoprosthesis can be formed of an elastic material that can be reversibly compacted and expanded. During introduction into the body, the endoprosthesis is restrained in a compacted condition. Upon reaching the desired implantation site, the restraint is removed, for example, by retracting a restraining device such as an outer sheath, enabling the endoprosthesis to self-expand by its own internal elastic restoring force. Another self-expansion technique uses shape memory metals which can "remember" a particular geometric configuration, e.g. an expanded condition, upon exposure to a trigger, such as an increase in temperature.
SUMMARY
In one aspect, the invention features a medical stent with a stent body including a generally tubular member, the generally tubular member including a wall that defines at least one void, and a radiopaque material bonded to the stent body by a polymer.
In another aspect, the invention features a medical stent with a stent body including a generally tubular member, the generally tubular member having a wall that defines at least one void. The medical stent also includes a radiopaque material that is bonded to the stent body by a polymer. The polymer spans the void, and the radiopaque material is suspended within the void.
In another aspect, the invention features a medical stent with a stent body that defines a generally tubular member and that includes a pattern of voids defined through a tubular stent wall. The geometry and/or location of the voids are selected to facilitate expansion and/or contraction of the stent. The medical stent also includes a radiopaque marker suspended within one of the voids. The radiopaque marker renders the medical stent radiopaque independently of the stent body.
In another aspect, the invention features a method of making a stent, the method including combining a radiopaque material with a first polymer, and attaching the first polymer to an end of a stent body defining a generally tubular member. The generally tubular member has a wall that defines at least one void. The first polymer spans the void, and the radiopaque material is suspended within the void.
In other aspects, the invention features a medical device including a void, and a polymer that e.g. spans the void, and a radiopaque material suspended within the void.
The medical device may include, for example, a plurality of voids. Examples include mesh-forms, such as filters, embolic protection devices, and valves.
Embodiments can include one or more of the following features.
The generally tubular member can include a pattern of voids defined through a tubular stent wall, and radiopaque material can be suspended within a plurality of the voids. The radiopaque material (e.g., the radiopaque marker) can be proximate an end or both ends of the stent body. The medical stent can include a plurality of radiopaque markers, and each radiopaque marker can be suspended within a void and located proximate an end of the stent body. The polymer can include a continuous element that extends over about 50 percent or more of the circumference of the stent body. The polymer can be in the shape of a ring. The ring can have a thickness of about 125 percent of the thickness of the stent body or less, and/or a width of about 25 percent of the length of the stent body or less. The ring can include at least two layers of polymeric material. The polymer can be shaped to complement an edge of the stent body.
The polymer can be a fluoropolymer (e.g., expanded-polytetrafluoroethylene).
The polymer can encapsulate the radiopaque material. The radiopaque material can be dispersed in the polymer.
The radiopaque material can include a body of radiopaque metal. The body of radiopaque metal (e.g., the radiopaque marker) can have a thickness of about 110 percent of the thickness of the stent body or less, and about 75 percent of the thickness of the stent body or more. The body of radiopaque metal can have a thickness of from about 0.001 inch to about 0.01 inch (e.g., from about 0.005 inch to about 0.008 inch). The radiopaque material can be a metal (e.g., tungsten, tantalum, platinum, palladium, lead, gold, titanium, silver), a metal alloy, a metal oxide, bismuth subcarbonate, or barium sulfate. The radiopaque material can have a density of about ten grams per cubic centimeter or greater. The medical stent can further include a therapeutic agent. The generally tubular member and/or the polymer can include the therapeutic agent.
The method can include providing a first strip of the first polymer, positioning a plurality of radiopaque markers on the first strip of the first polymer, and attaching the first strip to the stent body. The method can include positioning the radiopaque markers on the first strip at locations that correspond to voids defined by the stent body. The attachment of the first strip to the stent body can include assembling the first strip in contact with the stent body and bonding the first strip to the stent body. The first strip can be attached to the stent body by an adhesive, by melting, and/or by sintering or partially sintering the first strip. The method can include attaching the first strip to a second strip. The second strip can include a second polymer. The method can include attaching the first strip to the second strip with an adhesive. The method can include melt-bonding the first strip to the second strip. The method can include sintering or partially sintering the first strip to the second strip. The first polymer and the second polymer can be different polymers. The method can further include applying the second strip to at least one radiopaque marker to encapsulate the radiopaque marker. Combining a radiopaque material with a first polymer can include dispersing the radiopaque material in the first polymer.
Combining a radiopaque material with a first polymer can include attaching (e.g., adhering) at least one radiopaque marker to the first polymer. Adhering a radiopaque marker to the first polymer can include spraying the radiopaque marker with a dispersion and/or dipping the radiopaque marker in a dispersion, and placing the radiopaque marker on the first polymer. The dispersion can include tetrafluoroethylene or fluorinated ethylene propylene (FEP). Attaching at least one radiopaque marker to the first polymer can include heating the radiopaque marker and the first polymer. The method can include positioning at least one radiopaque marker in a void that is defined by the stent body. The first polymer can include a fluoropolymer (e.g., expanded-polytetrafluoroethylene). Attaching the first polymer to an end of a stent body can include sintering or partially sintering the first polymer to the end of the stent body. The method can further include contouring an edge of the first polymer.
Embodiments can include one or more of the following advantages.
In some embodiments, the location of an endoprosthesis with a polymer body that includes radiopaque material can be readily ascertained (e.g., by using x-ray fluoroscopy). In certain embodiments (e.g., embodiments in which both ends of an endoprosthesis include polymer rings with T-shaped radiopaque markers), both the location and the orientation of an endoprosthesis can be readily ascertained.
An endoprosthesis with a polymer body that includes radiopaque material can have a low profile. In some embodiments, a polymer body that includes radiopaque markers can be attached to an endoprosthesis without substantially increasing the profile (e.g., the deployment diameter) of the endoprosthesis. In certain embodiments, an endoprosthesis with a polymer body that includes radiopaque material (e.g., radiopaque markers) can provide more space for the radiopaque material than an endoprosthesis that lacks such a polymer body. As a result, the endoprosthesis with the polymer body may be adapted to incorporate more radiopaque material than the endoprosthesis that does not include the polymer body.
Radiopaque material that is incorporated into a polymer body in an endoprosthesis may be less likely to detach from the endoprosthesis than radiopaque material that is not incorporated into a polymer body. Thus, the endoprosthesis with the polymer body may have a relatively low likelihood of inflicting harm during use (e.g., by eliciting emboli formation).
An endoprosthesis with a polymer body incorporating radiopaque material may not require an extra structure or structures within its endoprosthesis body to hold the radiopaque material.
An endoprosthesis with a polymer body (made of, e.g., expanded polytetrafluoroethylene) at one or both of its ends can be less likely to result in stent end effects (harm to the body lumen, such as injury to body tissue, resulting from contact with one or both ends of the stent) than an endoprosthesis that does not have a polymer body at one or both of its ends. The polymer body can cover, e.g., pointed stent ends, making them less likely to harm surrounding tissue. In some embodiments, an endoprosthesis that includes a polymer body can withstand fatigue better than an endoprosthesis without such a polymer body.
An endoprosthesis with a polymer body at one or both of its ends that includes radiopaque material can be quickly and/or inexpensively produced, relative to an endoprosthesis that includes radiopaque material but lacks such a polymer body. In some embodiments, the manufacturing throughput of an endoprosthesis with a polymer body at one or both of its ends that includes radiopaque material can be relatively high.
In embodiments, a polymer body that includes radiopaque material can be relatively easy to assemble. In some embodiments, an endoprosthesis that includes the polymer body can be easier to assemble than, for example, an endoprosthesis with radiopaque markers that require attachment at several locations on and/or within the endoprosthesis body.
Still further aspects, features, and advantages follow.
DESCRIPTION OF DRAWINGS
FIG 1A is a perspective view of a stent.
FIG. 1B is a side view of the stent of FIG. 1A.
FIG 1C is an enlarged view of region 1C in FIG 1B.
FIG 1D is a cross-sectional view of region 1C, taken along line 1D-1D.
FIGS. 2A-2H are schematic views of the assembly of a stent.
FIGS. 3A-3C are schematic views of the assembly of a stent.
FIGS. 4A-4C illustrate delivery of a self-expanding stent.
FIGS. 5A-5C illustrate delivery of a balloon-expandable stent.
FIGS. 6A and 6B illustrate a method of forming a stent.
DETAILED DESCRIPTION
Structure Referring to FIGS. 1A and 1B, a stent 10 includes a generally tubular stent body 12 formed of strand materials 14. Strand materials 14 define a pattern of voids 16 in the wall of stent body 12. Voids 16 facilitate the expansion and contraction of stent 10, and enhance the flexibility of stent 10. At each of its ends, stent 10 includes a polymer body 18 in the shape of a ring that is attached to stent body 12. Radiopaque markers 20, in the form of solid metal slugs, are embedded in polymer body 18. A plurality of markers are spread circumferentially around the stent ends.
Referring as well to FIGS. 1C and 1D, markers 20 are positioned within voids 16 such that markers 20 do not overlap with, or contact, strand materials 14.
Furthermore, markers 20 have approximately the same thickness as strand materials 14. As a result, a relatively thick body of radiopaque material can be provided without substantially increasing the thickness profile of stent 10.
The markers 20 include one or more radiopaque materials to enhance the visibility of stent 10 under x-ray fluoroscopy. A radiopaque material can be, for example, a metal (e.g., tungsten, tantalum, platinum, palladium, lead, gold, titanium, silver); a metal alloy (e.g., stainless steel, an alloy of tungsten, an alloy of tantalum, an alloy of platinum, an alloy of palladium, an alloy of lead, an alloy of gold, an alloy of titanium, an alloy of silver); a metal oxide (e.g., titanium dioxide, zirconium oxide, aluminum oxide); bismuth subcarbonate; or barium sulfate.
In some embodiments, a radiopaque material can be a metal with a density of about ten grams per cubic centimeter or greater (e.g., about 25 grams per cubic centimeter or greater, about 50 grams per cubic centimeter or greater). The radiopaque material is provided as a solid metal slug and/or a radiopaque powder distributed in the polymer body. Suitable radiopaque materials are discussed in Heath, U.S. Patent No. 5,725,570, the entire contents of which are hereby incorporated by reference.
The thickness and width of the markers provide a desirable radiographic image.
In embodiments, the thickness of one or more of the markers is comparable to the thickness of the stent body. For example, the thickness of the marker is about +/-25 percent, about +/- ten percent, about +/- five percent, or less than the thickness of the stent body.
In embodiments, the thickness is from about 0.001 inch to about 0.01 inch (e.g., from about 0.005 inch to about 0.008 inch). In embodiments, the width of the markers is such that the markers can be positioned within the voids of the stent body without contacting or overlapping the stent body when the stent is in an expanded, implanted condition. In embodiments, the markers are sized to be positioned within the voids without contacting or overlapping the stent body when the stent is in a collapsed, delivery condition and an expanded, implanted condition. In particular embodiments, the width of the markers is 90 percent or less, e.g., 50 percent or less or ten percent or less than the width of the voids in the expanded and/or contracted condition. In particular embodiments, the maximum width of the markers is about two millimeters or less, e.g., one millimeter or less or one millimeter to 0.1 millimeter. Preferably, markers located at the ends of the stent do not extend substantially beyond the periphery of the stent body, so that the length of the stent is not increased. In embodiments, the markers extend less than about two millimeters beyond the length of the stent body (e.g., less than about 1.5 millimeters, less than about one millimeter, less than about 0.5 millimeter). In embodiments, the markers are discrete elements (e.g., metal slugs) that provide sufficient radiopacity independently of the stent body (without requiring the presence of the stent body) to provide a desirable radiopaque image.
The location, shape, and number of markers provide a particular radiographic image. To indicate one or both ends of the stent, markers are provided at the ends of the stent. In embodiments, markers are provided along the body of the stent at predetermined distances from the end of the stent. A single marker or multiple markers can be provided along the stent axis and/or circumferentially about the axis. A pattern of markers can provide an indication of stent orientation about the axis. The markers can be shaped to indicate orientation, e.g. cylindrical, disk-shaped or T-shaped markers can be provided. In some embodiments, the markers can be in the form of radiopaque wires (e.g., individual radiopaque wires or bundles of radiopaque wires).
In certain embodiments, the radiopaque wire markers can have a diameter of from about 0.001 inch to about 0.015 inch (e.g., about 0.01 inch), and/or a length of from about 0.5 millimeter to about two millimeters, and/or an aspect ratio (the ratio of the length of the radiopaque wire markers to the diameter of the radiopaque wire markers) of from about 1/1 to about 20/1. In certain embodiments, the radiopaque wire markers can have rounded or tumbled edges. In embodiments, one or more of the radiopaque wire markers can be in the form of a coil. Markers of different shapes can be used on the same stent.
The polymer body is biocompatible, compatible with the radiopaque material incorporated in the polymer body, of sufficient strength to retain the markers, and of sufficient flexibility to accommodate stent expansion and flexing during delivery or after implantation.
The polymer body is formed of one or more layers of a polymer such as a fluoropolymer (e.g., expanded-polytetrafluoroethylene), Corethane rt, a polyisobutylene-polystyrene block copolymer such as SIBS (see, e.g., U.S. Patent No. 6,545,097), fluorinated ethylene propylene (FEP), tetrafluoroethylene (TFE), and silicone (e.g., in embodiments of stent 10 that are used for non-vascular applications). The thickness of the polymer body is sufficient to securely retain and bond the marker to the stent body. The polymer body bonds to portions of the stent body adjacent a void in which a marker is positioned. In embodiments, the polymer overlaps the adjacent regions. The thickness of the overlap region is selected to reduce the overall thickness profile of the stent. In embodiments, the thickness of the overlap region on an exterior wall surface of the stent is 25 percent or less, e.g., ten percent or one percent or less than the thickness of the stent wall. In particular embodiments, the thickness of the overlap region is about 200 microns or less. In embodiments, the thickness of the portions of the polymer body overlapping the marker similarly does not greatly increase the thickness profile of the stent. The polymer body extends in particular embodiments into the void between the marker and the stent body to prevent direct contact between the marker and the stent body. The polymer body can include a drug, e.g. an antiproliferative, that elutes from the polymer body into adjacent tissue to, e.g., inhibit restenosis.
In embodiments, the polymer body can extend over from about ten percent to about 100 percent of the circumference of stent body 12, e.g. more than 50 percent. The width of the polymer body along the stent axis extends over about one percent to 100 percent of the length of the stent. In particular embodiments, the width of the polymer body is about ten millimeters or less, e.g., about two millimeters.
The polymer body can be formed and bonded to the stent by solvent casting, or dipping a suitable polymer directly onto the stent. Alternatively, a preformed polymer body can be bonded to the stent. In particular embodiments, the polymer body is formed from one or more preformed polymer strips. In particular embodiments, the markers are sandwiched between the strips, which are bonded together by an adhesive or co-melted, and/or which are sintered or partially sintered together.
In certain embodiments, a stent body can be formed of strands. The strands can be, e.g., woven, knitted, or crocheted. In embodiments, a stent body can be in the form of a sheet-form body with apertures (formed by, e.g., cutting or etching). The stent body can be defined by a metal or a polymer. The stent can be self-expanding or balloon expandable.
Stents are further described in Heath, incorporated supra, and Wang, U.S. Patent No. 6,379,379, the entire contents of which are hereby incorporated by reference.
TECHNICAL FIELD
This invention relates to medical devices, such as, for example, endoprostheses.
BACKGROUND
The body includes various passageways such as arteries, other blood vessels, and other body lumens. For various treatments and diagnostic techniques, it is often desirable to deliver a medical device into these lumens. For example, these passageways sometimes become occluded or weakened. The passageways can be occluded by, e.g. a tumor, restricted by plaque, or weakened by an aneurysm. When this occurs, the passageway can be reopened or reinforced, or even replaced, with a medical endoprosthesis.
An endoprosthesis is typically a tubular member that is placed in a lumen in the body.
Examples of endoprostheses include stents and covered stents, sometimes called "stent-grafts".
An endoprosthesis can be delivered inside the body by a catheter that supports the endoprosthesis in a compacted or reduced-size form as the endoprosthesis is transported to a desired site. Upon reaching the site, the endoprosthesis is expanded, for example, so that it can contact the walls of the lumen. The expansion mechanism may include forcing the endoprosthesis to expand radially.
For example, the expansion mechanism can include the catheter carrying a balloon, which carries the endoprosthesis. The balloon can be inflated to deform and to fix the expanded endoprosthesis at a predetermined position in contact with the lumen wall. The balloon can then be deflated, and the catheter removed.
In another delivery technique, the endoprosthesis is self-expanding. For example, the endoprosthesis can be formed of an elastic material that can be reversibly compacted and expanded. During introduction into the body, the endoprosthesis is restrained in a compacted condition. Upon reaching the desired implantation site, the restraint is removed, for example, by retracting a restraining device such as an outer sheath, enabling the endoprosthesis to self-expand by its own internal elastic restoring force. Another self-expansion technique uses shape memory metals which can "remember" a particular geometric configuration, e.g. an expanded condition, upon exposure to a trigger, such as an increase in temperature.
SUMMARY
In one aspect, the invention features a medical stent with a stent body including a generally tubular member, the generally tubular member including a wall that defines at least one void, and a radiopaque material bonded to the stent body by a polymer.
In another aspect, the invention features a medical stent with a stent body including a generally tubular member, the generally tubular member having a wall that defines at least one void. The medical stent also includes a radiopaque material that is bonded to the stent body by a polymer. The polymer spans the void, and the radiopaque material is suspended within the void.
In another aspect, the invention features a medical stent with a stent body that defines a generally tubular member and that includes a pattern of voids defined through a tubular stent wall. The geometry and/or location of the voids are selected to facilitate expansion and/or contraction of the stent. The medical stent also includes a radiopaque marker suspended within one of the voids. The radiopaque marker renders the medical stent radiopaque independently of the stent body.
In another aspect, the invention features a method of making a stent, the method including combining a radiopaque material with a first polymer, and attaching the first polymer to an end of a stent body defining a generally tubular member. The generally tubular member has a wall that defines at least one void. The first polymer spans the void, and the radiopaque material is suspended within the void.
In other aspects, the invention features a medical device including a void, and a polymer that e.g. spans the void, and a radiopaque material suspended within the void.
The medical device may include, for example, a plurality of voids. Examples include mesh-forms, such as filters, embolic protection devices, and valves.
Embodiments can include one or more of the following features.
The generally tubular member can include a pattern of voids defined through a tubular stent wall, and radiopaque material can be suspended within a plurality of the voids. The radiopaque material (e.g., the radiopaque marker) can be proximate an end or both ends of the stent body. The medical stent can include a plurality of radiopaque markers, and each radiopaque marker can be suspended within a void and located proximate an end of the stent body. The polymer can include a continuous element that extends over about 50 percent or more of the circumference of the stent body. The polymer can be in the shape of a ring. The ring can have a thickness of about 125 percent of the thickness of the stent body or less, and/or a width of about 25 percent of the length of the stent body or less. The ring can include at least two layers of polymeric material. The polymer can be shaped to complement an edge of the stent body.
The polymer can be a fluoropolymer (e.g., expanded-polytetrafluoroethylene).
The polymer can encapsulate the radiopaque material. The radiopaque material can be dispersed in the polymer.
The radiopaque material can include a body of radiopaque metal. The body of radiopaque metal (e.g., the radiopaque marker) can have a thickness of about 110 percent of the thickness of the stent body or less, and about 75 percent of the thickness of the stent body or more. The body of radiopaque metal can have a thickness of from about 0.001 inch to about 0.01 inch (e.g., from about 0.005 inch to about 0.008 inch). The radiopaque material can be a metal (e.g., tungsten, tantalum, platinum, palladium, lead, gold, titanium, silver), a metal alloy, a metal oxide, bismuth subcarbonate, or barium sulfate. The radiopaque material can have a density of about ten grams per cubic centimeter or greater. The medical stent can further include a therapeutic agent. The generally tubular member and/or the polymer can include the therapeutic agent.
The method can include providing a first strip of the first polymer, positioning a plurality of radiopaque markers on the first strip of the first polymer, and attaching the first strip to the stent body. The method can include positioning the radiopaque markers on the first strip at locations that correspond to voids defined by the stent body. The attachment of the first strip to the stent body can include assembling the first strip in contact with the stent body and bonding the first strip to the stent body. The first strip can be attached to the stent body by an adhesive, by melting, and/or by sintering or partially sintering the first strip. The method can include attaching the first strip to a second strip. The second strip can include a second polymer. The method can include attaching the first strip to the second strip with an adhesive. The method can include melt-bonding the first strip to the second strip. The method can include sintering or partially sintering the first strip to the second strip. The first polymer and the second polymer can be different polymers. The method can further include applying the second strip to at least one radiopaque marker to encapsulate the radiopaque marker. Combining a radiopaque material with a first polymer can include dispersing the radiopaque material in the first polymer.
Combining a radiopaque material with a first polymer can include attaching (e.g., adhering) at least one radiopaque marker to the first polymer. Adhering a radiopaque marker to the first polymer can include spraying the radiopaque marker with a dispersion and/or dipping the radiopaque marker in a dispersion, and placing the radiopaque marker on the first polymer. The dispersion can include tetrafluoroethylene or fluorinated ethylene propylene (FEP). Attaching at least one radiopaque marker to the first polymer can include heating the radiopaque marker and the first polymer. The method can include positioning at least one radiopaque marker in a void that is defined by the stent body. The first polymer can include a fluoropolymer (e.g., expanded-polytetrafluoroethylene). Attaching the first polymer to an end of a stent body can include sintering or partially sintering the first polymer to the end of the stent body. The method can further include contouring an edge of the first polymer.
Embodiments can include one or more of the following advantages.
In some embodiments, the location of an endoprosthesis with a polymer body that includes radiopaque material can be readily ascertained (e.g., by using x-ray fluoroscopy). In certain embodiments (e.g., embodiments in which both ends of an endoprosthesis include polymer rings with T-shaped radiopaque markers), both the location and the orientation of an endoprosthesis can be readily ascertained.
An endoprosthesis with a polymer body that includes radiopaque material can have a low profile. In some embodiments, a polymer body that includes radiopaque markers can be attached to an endoprosthesis without substantially increasing the profile (e.g., the deployment diameter) of the endoprosthesis. In certain embodiments, an endoprosthesis with a polymer body that includes radiopaque material (e.g., radiopaque markers) can provide more space for the radiopaque material than an endoprosthesis that lacks such a polymer body. As a result, the endoprosthesis with the polymer body may be adapted to incorporate more radiopaque material than the endoprosthesis that does not include the polymer body.
Radiopaque material that is incorporated into a polymer body in an endoprosthesis may be less likely to detach from the endoprosthesis than radiopaque material that is not incorporated into a polymer body. Thus, the endoprosthesis with the polymer body may have a relatively low likelihood of inflicting harm during use (e.g., by eliciting emboli formation).
An endoprosthesis with a polymer body incorporating radiopaque material may not require an extra structure or structures within its endoprosthesis body to hold the radiopaque material.
An endoprosthesis with a polymer body (made of, e.g., expanded polytetrafluoroethylene) at one or both of its ends can be less likely to result in stent end effects (harm to the body lumen, such as injury to body tissue, resulting from contact with one or both ends of the stent) than an endoprosthesis that does not have a polymer body at one or both of its ends. The polymer body can cover, e.g., pointed stent ends, making them less likely to harm surrounding tissue. In some embodiments, an endoprosthesis that includes a polymer body can withstand fatigue better than an endoprosthesis without such a polymer body.
An endoprosthesis with a polymer body at one or both of its ends that includes radiopaque material can be quickly and/or inexpensively produced, relative to an endoprosthesis that includes radiopaque material but lacks such a polymer body. In some embodiments, the manufacturing throughput of an endoprosthesis with a polymer body at one or both of its ends that includes radiopaque material can be relatively high.
In embodiments, a polymer body that includes radiopaque material can be relatively easy to assemble. In some embodiments, an endoprosthesis that includes the polymer body can be easier to assemble than, for example, an endoprosthesis with radiopaque markers that require attachment at several locations on and/or within the endoprosthesis body.
Still further aspects, features, and advantages follow.
DESCRIPTION OF DRAWINGS
FIG 1A is a perspective view of a stent.
FIG. 1B is a side view of the stent of FIG. 1A.
FIG 1C is an enlarged view of region 1C in FIG 1B.
FIG 1D is a cross-sectional view of region 1C, taken along line 1D-1D.
FIGS. 2A-2H are schematic views of the assembly of a stent.
FIGS. 3A-3C are schematic views of the assembly of a stent.
FIGS. 4A-4C illustrate delivery of a self-expanding stent.
FIGS. 5A-5C illustrate delivery of a balloon-expandable stent.
FIGS. 6A and 6B illustrate a method of forming a stent.
DETAILED DESCRIPTION
Structure Referring to FIGS. 1A and 1B, a stent 10 includes a generally tubular stent body 12 formed of strand materials 14. Strand materials 14 define a pattern of voids 16 in the wall of stent body 12. Voids 16 facilitate the expansion and contraction of stent 10, and enhance the flexibility of stent 10. At each of its ends, stent 10 includes a polymer body 18 in the shape of a ring that is attached to stent body 12. Radiopaque markers 20, in the form of solid metal slugs, are embedded in polymer body 18. A plurality of markers are spread circumferentially around the stent ends.
Referring as well to FIGS. 1C and 1D, markers 20 are positioned within voids 16 such that markers 20 do not overlap with, or contact, strand materials 14.
Furthermore, markers 20 have approximately the same thickness as strand materials 14. As a result, a relatively thick body of radiopaque material can be provided without substantially increasing the thickness profile of stent 10.
The markers 20 include one or more radiopaque materials to enhance the visibility of stent 10 under x-ray fluoroscopy. A radiopaque material can be, for example, a metal (e.g., tungsten, tantalum, platinum, palladium, lead, gold, titanium, silver); a metal alloy (e.g., stainless steel, an alloy of tungsten, an alloy of tantalum, an alloy of platinum, an alloy of palladium, an alloy of lead, an alloy of gold, an alloy of titanium, an alloy of silver); a metal oxide (e.g., titanium dioxide, zirconium oxide, aluminum oxide); bismuth subcarbonate; or barium sulfate.
In some embodiments, a radiopaque material can be a metal with a density of about ten grams per cubic centimeter or greater (e.g., about 25 grams per cubic centimeter or greater, about 50 grams per cubic centimeter or greater). The radiopaque material is provided as a solid metal slug and/or a radiopaque powder distributed in the polymer body. Suitable radiopaque materials are discussed in Heath, U.S. Patent No. 5,725,570, the entire contents of which are hereby incorporated by reference.
The thickness and width of the markers provide a desirable radiographic image.
In embodiments, the thickness of one or more of the markers is comparable to the thickness of the stent body. For example, the thickness of the marker is about +/-25 percent, about +/- ten percent, about +/- five percent, or less than the thickness of the stent body.
In embodiments, the thickness is from about 0.001 inch to about 0.01 inch (e.g., from about 0.005 inch to about 0.008 inch). In embodiments, the width of the markers is such that the markers can be positioned within the voids of the stent body without contacting or overlapping the stent body when the stent is in an expanded, implanted condition. In embodiments, the markers are sized to be positioned within the voids without contacting or overlapping the stent body when the stent is in a collapsed, delivery condition and an expanded, implanted condition. In particular embodiments, the width of the markers is 90 percent or less, e.g., 50 percent or less or ten percent or less than the width of the voids in the expanded and/or contracted condition. In particular embodiments, the maximum width of the markers is about two millimeters or less, e.g., one millimeter or less or one millimeter to 0.1 millimeter. Preferably, markers located at the ends of the stent do not extend substantially beyond the periphery of the stent body, so that the length of the stent is not increased. In embodiments, the markers extend less than about two millimeters beyond the length of the stent body (e.g., less than about 1.5 millimeters, less than about one millimeter, less than about 0.5 millimeter). In embodiments, the markers are discrete elements (e.g., metal slugs) that provide sufficient radiopacity independently of the stent body (without requiring the presence of the stent body) to provide a desirable radiopaque image.
The location, shape, and number of markers provide a particular radiographic image. To indicate one or both ends of the stent, markers are provided at the ends of the stent. In embodiments, markers are provided along the body of the stent at predetermined distances from the end of the stent. A single marker or multiple markers can be provided along the stent axis and/or circumferentially about the axis. A pattern of markers can provide an indication of stent orientation about the axis. The markers can be shaped to indicate orientation, e.g. cylindrical, disk-shaped or T-shaped markers can be provided. In some embodiments, the markers can be in the form of radiopaque wires (e.g., individual radiopaque wires or bundles of radiopaque wires).
In certain embodiments, the radiopaque wire markers can have a diameter of from about 0.001 inch to about 0.015 inch (e.g., about 0.01 inch), and/or a length of from about 0.5 millimeter to about two millimeters, and/or an aspect ratio (the ratio of the length of the radiopaque wire markers to the diameter of the radiopaque wire markers) of from about 1/1 to about 20/1. In certain embodiments, the radiopaque wire markers can have rounded or tumbled edges. In embodiments, one or more of the radiopaque wire markers can be in the form of a coil. Markers of different shapes can be used on the same stent.
The polymer body is biocompatible, compatible with the radiopaque material incorporated in the polymer body, of sufficient strength to retain the markers, and of sufficient flexibility to accommodate stent expansion and flexing during delivery or after implantation.
The polymer body is formed of one or more layers of a polymer such as a fluoropolymer (e.g., expanded-polytetrafluoroethylene), Corethane rt, a polyisobutylene-polystyrene block copolymer such as SIBS (see, e.g., U.S. Patent No. 6,545,097), fluorinated ethylene propylene (FEP), tetrafluoroethylene (TFE), and silicone (e.g., in embodiments of stent 10 that are used for non-vascular applications). The thickness of the polymer body is sufficient to securely retain and bond the marker to the stent body. The polymer body bonds to portions of the stent body adjacent a void in which a marker is positioned. In embodiments, the polymer overlaps the adjacent regions. The thickness of the overlap region is selected to reduce the overall thickness profile of the stent. In embodiments, the thickness of the overlap region on an exterior wall surface of the stent is 25 percent or less, e.g., ten percent or one percent or less than the thickness of the stent wall. In particular embodiments, the thickness of the overlap region is about 200 microns or less. In embodiments, the thickness of the portions of the polymer body overlapping the marker similarly does not greatly increase the thickness profile of the stent. The polymer body extends in particular embodiments into the void between the marker and the stent body to prevent direct contact between the marker and the stent body. The polymer body can include a drug, e.g. an antiproliferative, that elutes from the polymer body into adjacent tissue to, e.g., inhibit restenosis.
In embodiments, the polymer body can extend over from about ten percent to about 100 percent of the circumference of stent body 12, e.g. more than 50 percent. The width of the polymer body along the stent axis extends over about one percent to 100 percent of the length of the stent. In particular embodiments, the width of the polymer body is about ten millimeters or less, e.g., about two millimeters.
The polymer body can be formed and bonded to the stent by solvent casting, or dipping a suitable polymer directly onto the stent. Alternatively, a preformed polymer body can be bonded to the stent. In particular embodiments, the polymer body is formed from one or more preformed polymer strips. In particular embodiments, the markers are sandwiched between the strips, which are bonded together by an adhesive or co-melted, and/or which are sintered or partially sintered together.
In certain embodiments, a stent body can be formed of strands. The strands can be, e.g., woven, knitted, or crocheted. In embodiments, a stent body can be in the form of a sheet-form body with apertures (formed by, e.g., cutting or etching). The stent body can be defined by a metal or a polymer. The stent can be self-expanding or balloon expandable.
Stents are further described in Heath, incorporated supra, and Wang, U.S. Patent No. 6,379,379, the entire contents of which are hereby incorporated by reference.
Manufacture Referring to FIGS. 2A-2G, the manufacture of a stent with radiopaque markers is illustrated. Referring to FIG. 2A, radiopaque markers 20 are attached to one side 50 of a preformed polymer (e.g., expanded-polytetrafluoroethylene) strip 52. The markers 20 are adhered to polymer strip 52, for example, by spraying and/or dipping markers 20 in a low-viscosity dispersion (e.g., TFE, FEP), and then placing markers 20 on polymer strip 52. The strip 52 is heated, e.g., in an oven, such that the dispersion will cure and sinter or partially sinter with polymer strip 52. In embodiments, the temperature during heating is below the melting point of polymer strip 52. Thus, the heat can cause polymer strip 52 to soften and adhere to markers 20, without causing polymer strip 52 to melt. In embodiments, the polymer in the low-viscosity dispersion can be cross-linked and/or sintered or partially sintered to polymer strip 52, thereby securing markers 20 to polymer strip 52. For efficient manufacturing, the polymer strip to which markers 20 are attached can be longer than the circumference of the stent. The strip is then cut to a desired length to accommodate a stent of a desired size.
Referring now to FIG. 2B, the polymer strip 52 is arranged into a ring 54 (shown in FIG.
2C) after markers 20 have been adhered to polymer strip 52. While outer surface 56 of ring 54 includes markers 20, inner surface 58 of ring 54 does not include any markers 20. The diameter of the ring corresponds to the inner diameter of the stent when the stent is in a desired expanded configuration.
Referring to FIG. 2C, ring 54 is inserted onto a mandre160, such that inner surface 58 contacts mandre160. In some embodiments, mandre160 is a coated mandrel (e.g., coated with zirconium-nickel or titanium nitrate). In certain embodiments, a coating can help mandre160 to retain ring 54.
Referring now to FIGS. 2D and 2E, after ring 54 is inserted onto mandre160, a stent body 12 is positioned on mandre160, such that end 62 of stent body 121ies on top of ring 54.
Strand materials 14 are positioned between markers 20, and markers 20 are contained within voids 16. The assembly is heated to attach the ring 54 (e.g., by partial sintering) to the stent body.
Referring to FIGS. 2F and 2G, a securement layer 64 is positioned over the outer surface of the stent body and attached to ring 54. Securement layer 64 covers markers 20. Securement layer 64 can be made of, e.g., a polymer in the form of a preformed strip. The strip is formed of, e.g., the same polymer as the strip 52.
The securement layer 64 can be attached to ring 54 by adhesive-bonding (e.g., using TFE) and/or by sintering or partially sintering securement layer 64. The attachment of securement layer 64 to ring 54 forms polymer body 66, in which markers 20 are embedded. The portion of the stent body covered by the polymer body is likewise sandwiched between strip 52 and layer 64 to securely fix the markers and the polymer body 66 to the stent.
(The polymer strip and the securement layer are attached to minimize gaps between the layers.) Referring to FIG. 2H, polymer body 66 can be cut or trimmed (e.g., laser-trimmed) to reduce flaps of excess polymer material. In embodiments, polymer body 66 can be scalloped (e.g., to decrease stent end effects) and/or contoured or shaped (e.g., to smoothen polymer body 66, to enhance the biocompatibility of polymer body 66, to make polymer body 66 complement the edge of stent body 12).
Referring now to FIGS. 3A-3C, in some embodiments a polymer ring 65 formed of markers 20 sandwiched between polymer strip 52 and securement layer 64 is inserted onto mandrel 60. Thereafter, stent body 12 is inserted onto mandrel 60, such that end 62 of stent body 121ies on top of ring 65. Strand materials 14 of stent body 12 are positioned between the locations of markers 20 within ring 65. A second securement layer 67 is then added over ring 65 and end 62 of stent body 12, such that end 62 is sandwiched between securement layer 64 and securement layer 67.
Stent Delivery FIGS. 4A-4C show the delivery of a self-expanding stent 200. Stent 200 is deployed on a catheter 202 and covered by a sheath 204. When the target site is reached, sheath 204 is retracted and stent 200 self-expands into contact with the body lumen.
Radiopaque markers 206 embedded within polymer bodies 208 at each end of stent 200 allow for determination of the location of stent 200 (e.g., by x-ray radiography).
Referring now to FIGS. 5A-5C, the delivery of a balloon-expandable stent 300 is illustrated. Stent 300 is carried on a catheter 302 over a balloon 304. When the treatment site is reached, balloon 304 is expanded to expand stent 300 into contact with the lumen wall.
Radiopaque markers 306 embedded within polymer bodies 308 at each end of stent 300 allow for determination of the location of stent 300.
Stent 200 and/or stent 300 can be used in vascular and/or non-vascular applications.
Stent 200 and/or stent 300 can be used, for example, to treat stenoses, aneurysms, or emboli. In some embodiments, stent 200 and/or stent 300 can be used in the coronary and/or peripheral vascular system, e.g., for iliac, carotid, superior femoral artery (SFA), renal, and/or popliteal applications. In certain embodiments, stent 200 and/or stent 300 can be used in non-vascular applications. For example, stent 200 and/or stent 300 can be used in tracheal/bronchial, biliary, and/or esophageal applications.
Other Embodiments Referring to FIGS. 6A and 6B, an end 102 of the stent body of a stent 100 is modified to form a larger void volume for accommodating radiopaque markers. In FIG. 6A, forces (indicated by arrows F) are applied against points 104 to deform the stent to increase the void area to accommodate larger radiopaque markers 106 (shown in FIG. 6B).
Alternatively or additionally, strand materials used to form a stent can be manipulated during the stent formation process (e.g., during weaving, knitting, crocheting) to include extra room at the edges of the stent for, e.g., radiopaque markers.
In embodiments, a stent can include a polymer body at only one of its ends, rather than at both of its ends. In certain embodiments, a stent can include a polymer body that is not located at either end of the stent. For example, a polymer body can be located at the middle of the stent body. In such embodiments, the stent can further include a polymer body at one or both of its ends, or can lack polymer bodies at either of its ends.
The polymer body can include more than one form of radiopaque material. For example, a polymer body can include embedded radiopaque markers and can have a radiopaque powder dispersed throughout it.
As a further example, a polymer body that includes radiopaque material can be incorporated into other types of medical devices. For example, the polymer body can be incorporated into various types of endoprostheses, such as a covered stent, an AAA (abdominal aortic aneurysm) stent-graft, an endograft, or a surgical vascular bypass graft, or other devices, including prosthetic venous valves and embolic protection devices and filters.
Other embodiments are within the scope of the following claims.
Referring now to FIG. 2B, the polymer strip 52 is arranged into a ring 54 (shown in FIG.
2C) after markers 20 have been adhered to polymer strip 52. While outer surface 56 of ring 54 includes markers 20, inner surface 58 of ring 54 does not include any markers 20. The diameter of the ring corresponds to the inner diameter of the stent when the stent is in a desired expanded configuration.
Referring to FIG. 2C, ring 54 is inserted onto a mandre160, such that inner surface 58 contacts mandre160. In some embodiments, mandre160 is a coated mandrel (e.g., coated with zirconium-nickel or titanium nitrate). In certain embodiments, a coating can help mandre160 to retain ring 54.
Referring now to FIGS. 2D and 2E, after ring 54 is inserted onto mandre160, a stent body 12 is positioned on mandre160, such that end 62 of stent body 121ies on top of ring 54.
Strand materials 14 are positioned between markers 20, and markers 20 are contained within voids 16. The assembly is heated to attach the ring 54 (e.g., by partial sintering) to the stent body.
Referring to FIGS. 2F and 2G, a securement layer 64 is positioned over the outer surface of the stent body and attached to ring 54. Securement layer 64 covers markers 20. Securement layer 64 can be made of, e.g., a polymer in the form of a preformed strip. The strip is formed of, e.g., the same polymer as the strip 52.
The securement layer 64 can be attached to ring 54 by adhesive-bonding (e.g., using TFE) and/or by sintering or partially sintering securement layer 64. The attachment of securement layer 64 to ring 54 forms polymer body 66, in which markers 20 are embedded. The portion of the stent body covered by the polymer body is likewise sandwiched between strip 52 and layer 64 to securely fix the markers and the polymer body 66 to the stent.
(The polymer strip and the securement layer are attached to minimize gaps between the layers.) Referring to FIG. 2H, polymer body 66 can be cut or trimmed (e.g., laser-trimmed) to reduce flaps of excess polymer material. In embodiments, polymer body 66 can be scalloped (e.g., to decrease stent end effects) and/or contoured or shaped (e.g., to smoothen polymer body 66, to enhance the biocompatibility of polymer body 66, to make polymer body 66 complement the edge of stent body 12).
Referring now to FIGS. 3A-3C, in some embodiments a polymer ring 65 formed of markers 20 sandwiched between polymer strip 52 and securement layer 64 is inserted onto mandrel 60. Thereafter, stent body 12 is inserted onto mandrel 60, such that end 62 of stent body 121ies on top of ring 65. Strand materials 14 of stent body 12 are positioned between the locations of markers 20 within ring 65. A second securement layer 67 is then added over ring 65 and end 62 of stent body 12, such that end 62 is sandwiched between securement layer 64 and securement layer 67.
Stent Delivery FIGS. 4A-4C show the delivery of a self-expanding stent 200. Stent 200 is deployed on a catheter 202 and covered by a sheath 204. When the target site is reached, sheath 204 is retracted and stent 200 self-expands into contact with the body lumen.
Radiopaque markers 206 embedded within polymer bodies 208 at each end of stent 200 allow for determination of the location of stent 200 (e.g., by x-ray radiography).
Referring now to FIGS. 5A-5C, the delivery of a balloon-expandable stent 300 is illustrated. Stent 300 is carried on a catheter 302 over a balloon 304. When the treatment site is reached, balloon 304 is expanded to expand stent 300 into contact with the lumen wall.
Radiopaque markers 306 embedded within polymer bodies 308 at each end of stent 300 allow for determination of the location of stent 300.
Stent 200 and/or stent 300 can be used in vascular and/or non-vascular applications.
Stent 200 and/or stent 300 can be used, for example, to treat stenoses, aneurysms, or emboli. In some embodiments, stent 200 and/or stent 300 can be used in the coronary and/or peripheral vascular system, e.g., for iliac, carotid, superior femoral artery (SFA), renal, and/or popliteal applications. In certain embodiments, stent 200 and/or stent 300 can be used in non-vascular applications. For example, stent 200 and/or stent 300 can be used in tracheal/bronchial, biliary, and/or esophageal applications.
Other Embodiments Referring to FIGS. 6A and 6B, an end 102 of the stent body of a stent 100 is modified to form a larger void volume for accommodating radiopaque markers. In FIG. 6A, forces (indicated by arrows F) are applied against points 104 to deform the stent to increase the void area to accommodate larger radiopaque markers 106 (shown in FIG. 6B).
Alternatively or additionally, strand materials used to form a stent can be manipulated during the stent formation process (e.g., during weaving, knitting, crocheting) to include extra room at the edges of the stent for, e.g., radiopaque markers.
In embodiments, a stent can include a polymer body at only one of its ends, rather than at both of its ends. In certain embodiments, a stent can include a polymer body that is not located at either end of the stent. For example, a polymer body can be located at the middle of the stent body. In such embodiments, the stent can further include a polymer body at one or both of its ends, or can lack polymer bodies at either of its ends.
The polymer body can include more than one form of radiopaque material. For example, a polymer body can include embedded radiopaque markers and can have a radiopaque powder dispersed throughout it.
As a further example, a polymer body that includes radiopaque material can be incorporated into other types of medical devices. For example, the polymer body can be incorporated into various types of endoprostheses, such as a covered stent, an AAA (abdominal aortic aneurysm) stent-graft, an endograft, or a surgical vascular bypass graft, or other devices, including prosthetic venous valves and embolic protection devices and filters.
Other embodiments are within the scope of the following claims.
Claims (26)
1. A medical stent, comprising:
a stent body comprising a generally tubular member, the generally tubular member comprising a wall that defines at least one void; and a radiopaque material bonded to the stent body by a polymer, wherein the polymer spans the at least one void, and the radiopaque material is suspended within the at least one void.
a stent body comprising a generally tubular member, the generally tubular member comprising a wall that defines at least one void; and a radiopaque material bonded to the stent body by a polymer, wherein the polymer spans the at least one void, and the radiopaque material is suspended within the at least one void.
2. The medical stent of claim 1, wherein the generally tubular member includes a pattern of voids defined through a tubular stent wall and radiopaque material is suspended within a plurality of the voids.
3. The medical stent of claim 1, wherein the radiopaque material is proximate an end of the stent body.
4. The medical stent of claim 1, wherein the polymer comprises a continuous element extending over about 50 percent or more of the circumference of the stent body.
5. The medical stent of claim 1, wherein the polymer is in the shape of a ring.
6. The medical stent of claim 5, wherein the ring has a thickness of about 125 percent of the thickness of the stent body or less.
7. The medical stent of claim 5, wherein the ring has a width of about 25 percent of the length of the stent body or less.
8. The medical stent of claim 1, wherein the polymer is a fluoropolymer.
9. The medical stent of claim 1, wherein the polymer is expanded-polytetrafluoroethylene.
10. The medical stent of claim 1, wherein the polymer encapsulates the radiopaque material.
11. The medical stent of claim 1, wherein the radiopaque material comprises a body of radiopaque metal.
12. The medical stent of claim 11, wherein the body of radiopaque metal has a thickness of about 110 percent of the thickness of the stent body or less, and about 75 percent of the thickness of the stent body or more.
13. The medical stent of claim 11, wherein the body of radiopaque metal has a thickness of from about 0.00 1 inch to about 0.01 inch.
14. The medical stent of claim 1, further comprising a therapeutic agent.
15. A medical stent, comprising:
a stent body defining a generally tubular member and including a pattern of voids defined through a tubular stent wall, the geometry and/or location of the voids selected to facilitate expansion and/or contraction of the stent; and a radiopaque marker suspended within one of the voids, wherein the radiopaque marker renders the medical stent radiopaque independently of the stent body.
a stent body defining a generally tubular member and including a pattern of voids defined through a tubular stent wall, the geometry and/or location of the voids selected to facilitate expansion and/or contraction of the stent; and a radiopaque marker suspended within one of the voids, wherein the radiopaque marker renders the medical stent radiopaque independently of the stent body.
16. The medical stent of claim 15, wherein the radiopaque marker is located proximate an end of the stent body.
17. A method of making a stent, the method comprising:
combining a radiopaque material with a first polymer; and attaching the first polymer to an end of a stent body defining a generally tubular member, the generally tubular member comprising a wall that defines at least one void, wherein the first polymer spans the at least one void, and the radiopaque material is suspended within the at least one void.
combining a radiopaque material with a first polymer; and attaching the first polymer to an end of a stent body defining a generally tubular member, the generally tubular member comprising a wall that defines at least one void, wherein the first polymer spans the at least one void, and the radiopaque material is suspended within the at least one void.
18. The method of claim 17, comprising providing a first strip of the first polymer, positioning a plurality of radiopaque markers on the first strip of the first polymer, and attaching the first strip to the stent body.
19. The method of claim 18, comprising positioning the radiopaque markers on the first strip at locations corresponding to voids defined by the stent body.
20. The method of claim 18, wherein attaching the first strip comprises assembling the first strip in contact with the stent body and bonding the first strip to the stent body.
21. The method of claim 20, further comprising bonding the first strip to a second strip, wherein the second strip comprises a second polymer.
22. The method of claim 21, comprising adhesive-bonding, melt-bonding, sintering or partially sintering the first strip to the second strip.
23. The method of claim 21, further comprising applying the second strip to at least one radiopaque marker to encapsulate the at least one radiopaque marker.
24. The method of claim 18, wherein the first strip is attached to the stent body by sintering or partially sintering the first strip, by melting, or by an adhesive.
25. The method of claim 17, comprising positioning at least one radiopaque marker in a void defined by the stent body.
26. The method of claim 17, wherein attaching the first polymer to an end of a stent body comprises partially sintering the first polymer to the end of the stent body.
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/872,164 | 2004-06-18 | ||
US10/872,164 US20050283226A1 (en) | 2004-06-18 | 2004-06-18 | Medical devices |
PCT/US2005/021521 WO2006009867A1 (en) | 2004-06-18 | 2005-06-16 | Medical stents |
Publications (1)
Publication Number | Publication Date |
---|---|
CA2570914A1 true CA2570914A1 (en) | 2006-01-26 |
Family
ID=34979691
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002570914A Abandoned CA2570914A1 (en) | 2004-06-18 | 2005-06-16 | Medical stents |
Country Status (5)
Country | Link |
---|---|
US (1) | US20050283226A1 (en) |
EP (1) | EP1778129A1 (en) |
JP (1) | JP2008503270A (en) |
CA (1) | CA2570914A1 (en) |
WO (1) | WO2006009867A1 (en) |
Families Citing this family (358)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20070084897A1 (en) | 2003-05-20 | 2007-04-19 | Shelton Frederick E Iv | Articulating surgical stapling instrument incorporating a two-piece e-beam firing mechanism |
US9060770B2 (en) | 2003-05-20 | 2015-06-23 | Ethicon Endo-Surgery, Inc. | Robotically-driven surgical instrument with E-beam driver |
US8215531B2 (en) | 2004-07-28 | 2012-07-10 | Ethicon Endo-Surgery, Inc. | Surgical stapling instrument having a medical substance dispenser |
US11896225B2 (en) | 2004-07-28 | 2024-02-13 | Cilag Gmbh International | Staple cartridge comprising a pan |
US20060025852A1 (en) * | 2004-08-02 | 2006-02-02 | Armstrong Joseph R | Bioabsorbable self-expanding endolumenal devices |
EP1791496B1 (en) | 2004-08-31 | 2019-07-31 | C.R. Bard, Inc. | Self-sealing ptfe graft with kink resistance |
US20060210700A1 (en) * | 2005-03-18 | 2006-09-21 | Lachner Thomas F | Flexible and plastic radiopaque laminate composition |
JP2009501027A (en) * | 2005-06-17 | 2009-01-15 | シー・アール・バード・インコーポレイテツド | Vascular graft with kinking resistance after tightening |
US11484312B2 (en) | 2005-08-31 | 2022-11-01 | Cilag Gmbh International | Staple cartridge comprising a staple driver arrangement |
US7669746B2 (en) | 2005-08-31 | 2010-03-02 | Ethicon Endo-Surgery, Inc. | Staple cartridges for forming staples having differing formed staple heights |
US9237891B2 (en) | 2005-08-31 | 2016-01-19 | Ethicon Endo-Surgery, Inc. | Robotically-controlled surgical stapling devices that produce formed staples having different lengths |
US7934630B2 (en) | 2005-08-31 | 2011-05-03 | Ethicon Endo-Surgery, Inc. | Staple cartridges for forming staples having differing formed staple heights |
US10159482B2 (en) | 2005-08-31 | 2018-12-25 | Ethicon Llc | Fastener cartridge assembly comprising a fixed anvil and different staple heights |
US11246590B2 (en) | 2005-08-31 | 2022-02-15 | Cilag Gmbh International | Staple cartridge including staple drivers having different unfired heights |
GB0707671D0 (en) * | 2007-04-20 | 2007-05-30 | Invibio Ltd | Fiducial marker |
US8636794B2 (en) * | 2005-11-09 | 2014-01-28 | C. R. Bard, Inc. | Grafts and stent grafts having a radiopaque marker |
US20070106317A1 (en) | 2005-11-09 | 2007-05-10 | Shelton Frederick E Iv | Hydraulically and electrically actuated articulation joints for surgical instruments |
US20070156230A1 (en) | 2006-01-04 | 2007-07-05 | Dugan Stephen R | Stents with radiopaque markers |
US8186555B2 (en) | 2006-01-31 | 2012-05-29 | Ethicon Endo-Surgery, Inc. | Motor-driven surgical cutting and fastening instrument with mechanical closure system |
US11278279B2 (en) | 2006-01-31 | 2022-03-22 | Cilag Gmbh International | Surgical instrument assembly |
US11224427B2 (en) | 2006-01-31 | 2022-01-18 | Cilag Gmbh International | Surgical stapling system including a console and retraction assembly |
US8708213B2 (en) | 2006-01-31 | 2014-04-29 | Ethicon Endo-Surgery, Inc. | Surgical instrument having a feedback system |
US20110024477A1 (en) | 2009-02-06 | 2011-02-03 | Hall Steven G | Driven Surgical Stapler Improvements |
US8820603B2 (en) | 2006-01-31 | 2014-09-02 | Ethicon Endo-Surgery, Inc. | Accessing data stored in a memory of a surgical instrument |
US11793518B2 (en) | 2006-01-31 | 2023-10-24 | Cilag Gmbh International | Powered surgical instruments with firing system lockout arrangements |
US20110295295A1 (en) | 2006-01-31 | 2011-12-01 | Ethicon Endo-Surgery, Inc. | Robotically-controlled surgical instrument having recording capabilities |
US20120292367A1 (en) | 2006-01-31 | 2012-11-22 | Ethicon Endo-Surgery, Inc. | Robotically-controlled end effector |
US7753904B2 (en) | 2006-01-31 | 2010-07-13 | Ethicon Endo-Surgery, Inc. | Endoscopic surgical instrument with a handle that can articulate with respect to the shaft |
US7845537B2 (en) | 2006-01-31 | 2010-12-07 | Ethicon Endo-Surgery, Inc. | Surgical instrument having recording capabilities |
US8992422B2 (en) | 2006-03-23 | 2015-03-31 | Ethicon Endo-Surgery, Inc. | Robotically-controlled endoscopic accessory channel |
US8752268B2 (en) | 2006-05-26 | 2014-06-17 | Abbott Cardiovascular Systems Inc. | Method of making stents with radiopaque markers |
US8322455B2 (en) | 2006-06-27 | 2012-12-04 | Ethicon Endo-Surgery, Inc. | Manually driven surgical cutting and fastening instrument |
DE102006038232A1 (en) * | 2006-08-07 | 2008-02-14 | Biotronik Vi Patent Ag | Endoprosthesis and method for producing such |
US10568652B2 (en) | 2006-09-29 | 2020-02-25 | Ethicon Llc | Surgical staples having attached drivers of different heights and stapling instruments for deploying the same |
US9198749B2 (en) | 2006-10-12 | 2015-12-01 | C. R. Bard, Inc. | Vascular grafts with multiple channels and methods for making |
US20080102098A1 (en) * | 2006-10-30 | 2008-05-01 | Vipul Bhupendra Dave | Method for making a device having discrete regions |
US8684253B2 (en) | 2007-01-10 | 2014-04-01 | Ethicon Endo-Surgery, Inc. | Surgical instrument with wireless communication between a control unit of a robotic system and remote sensor |
US11291441B2 (en) | 2007-01-10 | 2022-04-05 | Cilag Gmbh International | Surgical instrument with wireless communication between control unit and remote sensor |
US8652120B2 (en) | 2007-01-10 | 2014-02-18 | Ethicon Endo-Surgery, Inc. | Surgical instrument with wireless communication between control unit and sensor transponders |
US11039836B2 (en) | 2007-01-11 | 2021-06-22 | Cilag Gmbh International | Staple cartridge for use with a surgical stapling instrument |
US8701958B2 (en) | 2007-01-11 | 2014-04-22 | Ethicon Endo-Surgery, Inc. | Curved end effector for a surgical stapling device |
US7669747B2 (en) | 2007-03-15 | 2010-03-02 | Ethicon Endo-Surgery, Inc. | Washer for use with a surgical stapling instrument |
US11564682B2 (en) | 2007-06-04 | 2023-01-31 | Cilag Gmbh International | Surgical stapler device |
US8931682B2 (en) | 2007-06-04 | 2015-01-13 | Ethicon Endo-Surgery, Inc. | Robotically-controlled shaft based rotary drive systems for surgical instruments |
US7753245B2 (en) | 2007-06-22 | 2010-07-13 | Ethicon Endo-Surgery, Inc. | Surgical stapling instruments |
US11849941B2 (en) | 2007-06-29 | 2023-12-26 | Cilag Gmbh International | Staple cartridge having staple cavities extending at a transverse angle relative to a longitudinal cartridge axis |
WO2009091968A1 (en) * | 2008-01-18 | 2009-07-23 | Med Institute, Inc. | Intravascular device attachment system having struts |
JP5410110B2 (en) | 2008-02-14 | 2014-02-05 | エシコン・エンド−サージェリィ・インコーポレイテッド | Surgical cutting / fixing instrument with RF electrode |
US8636736B2 (en) | 2008-02-14 | 2014-01-28 | Ethicon Endo-Surgery, Inc. | Motorized surgical cutting and fastening instrument |
US9179912B2 (en) | 2008-02-14 | 2015-11-10 | Ethicon Endo-Surgery, Inc. | Robotically-controlled motorized surgical cutting and fastening instrument |
US7866527B2 (en) | 2008-02-14 | 2011-01-11 | Ethicon Endo-Surgery, Inc. | Surgical stapling apparatus with interlockable firing system |
US8573465B2 (en) | 2008-02-14 | 2013-11-05 | Ethicon Endo-Surgery, Inc. | Robotically-controlled surgical end effector system with rotary actuated closure systems |
US7819298B2 (en) | 2008-02-14 | 2010-10-26 | Ethicon Endo-Surgery, Inc. | Surgical stapling apparatus with control features operable with one hand |
US20130153641A1 (en) | 2008-02-15 | 2013-06-20 | Ethicon Endo-Surgery, Inc. | Releasable layer of material and surgical end effector having the same |
US9962523B2 (en) | 2008-06-27 | 2018-05-08 | Merit Medical Systems, Inc. | Catheter with radiopaque marker |
WO2010031060A1 (en) | 2008-09-15 | 2010-03-18 | Medtronic Ventor Technologies Ltd. | Prosthetic heart valve having identifiers for aiding in radiographic positioning |
US8210411B2 (en) | 2008-09-23 | 2012-07-03 | Ethicon Endo-Surgery, Inc. | Motor-driven surgical cutting instrument |
US9386983B2 (en) | 2008-09-23 | 2016-07-12 | Ethicon Endo-Surgery, Llc | Robotically-controlled motorized surgical instrument |
US9005230B2 (en) | 2008-09-23 | 2015-04-14 | Ethicon Endo-Surgery, Inc. | Motorized surgical instrument |
US11648005B2 (en) | 2008-09-23 | 2023-05-16 | Cilag Gmbh International | Robotically-controlled motorized surgical instrument with an end effector |
US8608045B2 (en) | 2008-10-10 | 2013-12-17 | Ethicon Endo-Sugery, Inc. | Powered surgical cutting and stapling apparatus with manually retractable firing system |
US20130331928A1 (en) * | 2008-11-13 | 2013-12-12 | Chen Yang | Dialysis Graft with Thromboses Prevention Arrangement |
US8517239B2 (en) | 2009-02-05 | 2013-08-27 | Ethicon Endo-Surgery, Inc. | Surgical stapling instrument comprising a magnetic element driver |
EP2393430A1 (en) | 2009-02-06 | 2011-12-14 | Ethicon Endo-Surgery, Inc. | Driven surgical stapler improvements |
EP2429636B1 (en) * | 2009-04-30 | 2014-08-27 | Medtronic, Inc | Shielding an implantable medical lead |
US8851354B2 (en) | 2009-12-24 | 2014-10-07 | Ethicon Endo-Surgery, Inc. | Surgical cutting instrument that analyzes tissue thickness |
US8808353B2 (en) | 2010-01-30 | 2014-08-19 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer scaffolds having a low crossing profile |
US8568471B2 (en) | 2010-01-30 | 2013-10-29 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer scaffolds |
EP2399619B1 (en) * | 2010-06-25 | 2015-08-05 | Biotronik AG | Implant and Method for Manufacturing Same |
US8783543B2 (en) | 2010-07-30 | 2014-07-22 | Ethicon Endo-Surgery, Inc. | Tissue acquisition arrangements and methods for surgical stapling devices |
US11849952B2 (en) | 2010-09-30 | 2023-12-26 | Cilag Gmbh International | Staple cartridge comprising staples positioned within a compressible portion thereof |
US9566061B2 (en) | 2010-09-30 | 2017-02-14 | Ethicon Endo-Surgery, Llc | Fastener cartridge comprising a releasably attached tissue thickness compensator |
US8746535B2 (en) | 2010-09-30 | 2014-06-10 | Ethicon Endo-Surgery, Inc. | Tissue thickness compensator comprising detachable portions |
US9839420B2 (en) | 2010-09-30 | 2017-12-12 | Ethicon Llc | Tissue thickness compensator comprising at least one medicament |
US11812965B2 (en) | 2010-09-30 | 2023-11-14 | Cilag Gmbh International | Layer of material for a surgical end effector |
US10945731B2 (en) | 2010-09-30 | 2021-03-16 | Ethicon Llc | Tissue thickness compensator comprising controlled release and expansion |
US11298125B2 (en) | 2010-09-30 | 2022-04-12 | Cilag Gmbh International | Tissue stapler having a thickness compensator |
US9629814B2 (en) | 2010-09-30 | 2017-04-25 | Ethicon Endo-Surgery, Llc | Tissue thickness compensator configured to redistribute compressive forces |
US9386988B2 (en) | 2010-09-30 | 2016-07-12 | Ethicon End-Surgery, LLC | Retainer assembly including a tissue thickness compensator |
US8695866B2 (en) | 2010-10-01 | 2014-04-15 | Ethicon Endo-Surgery, Inc. | Surgical instrument having a power control circuit |
AU2012250197B2 (en) | 2011-04-29 | 2017-08-10 | Ethicon Endo-Surgery, Inc. | Staple cartridge comprising staples positioned within a compressible portion thereof |
US9072535B2 (en) | 2011-05-27 | 2015-07-07 | Ethicon Endo-Surgery, Inc. | Surgical stapling instruments with rotatable staple deployment arrangements |
US11207064B2 (en) | 2011-05-27 | 2021-12-28 | Cilag Gmbh International | Automated end effector component reloading system for use with a robotic system |
US8726483B2 (en) | 2011-07-29 | 2014-05-20 | Abbott Cardiovascular Systems Inc. | Methods for uniform crimping and deployment of a polymer scaffold |
RU2639857C2 (en) | 2012-03-28 | 2017-12-22 | Этикон Эндо-Серджери, Инк. | Tissue thickness compensator containing capsule for medium with low pressure |
MX358135B (en) | 2012-03-28 | 2018-08-06 | Ethicon Endo Surgery Inc | Tissue thickness compensator comprising a plurality of layers. |
RU2644272C2 (en) | 2012-03-28 | 2018-02-08 | Этикон Эндо-Серджери, Инк. | Limitation node with tissue thickness compensator |
US9233015B2 (en) | 2012-06-15 | 2016-01-12 | Trivascular, Inc. | Endovascular delivery system with an improved radiopaque marker scheme |
US9101358B2 (en) | 2012-06-15 | 2015-08-11 | Ethicon Endo-Surgery, Inc. | Articulatable surgical instrument comprising a firing drive |
EP2866686A1 (en) | 2012-06-28 | 2015-05-06 | Ethicon Endo-Surgery, Inc. | Empty clip cartridge lockout |
US9289256B2 (en) | 2012-06-28 | 2016-03-22 | Ethicon Endo-Surgery, Llc | Surgical end effectors having angled tissue-contacting surfaces |
US9226751B2 (en) | 2012-06-28 | 2016-01-05 | Ethicon Endo-Surgery, Inc. | Surgical instrument system including replaceable end effectors |
BR112014032776B1 (en) | 2012-06-28 | 2021-09-08 | Ethicon Endo-Surgery, Inc | SURGICAL INSTRUMENT SYSTEM AND SURGICAL KIT FOR USE WITH A SURGICAL INSTRUMENT SYSTEM |
US9649111B2 (en) | 2012-06-28 | 2017-05-16 | Ethicon Endo-Surgery, Llc | Replaceable clip cartridge for a clip applier |
US11202631B2 (en) | 2012-06-28 | 2021-12-21 | Cilag Gmbh International | Stapling assembly comprising a firing lockout |
US20140001231A1 (en) | 2012-06-28 | 2014-01-02 | Ethicon Endo-Surgery, Inc. | Firing system lockout arrangements for surgical instruments |
US20140018663A1 (en) * | 2012-07-16 | 2014-01-16 | Endomagnetics Ltd. | Magnetic Marker for Surgical Localization |
RU2672520C2 (en) | 2013-03-01 | 2018-11-15 | Этикон Эндо-Серджери, Инк. | Hingedly turnable surgical instruments with conducting ways for signal transfer |
RU2669463C2 (en) | 2013-03-01 | 2018-10-11 | Этикон Эндо-Серджери, Инк. | Surgical instrument with soft stop |
US20140255298A1 (en) * | 2013-03-08 | 2014-09-11 | Medtronic, Inc. | Radiopaque markers for implantable medical leads |
IN2014DE00462A (en) * | 2013-03-11 | 2015-06-12 | Depuy Synthes Products Llc | |
US9332987B2 (en) | 2013-03-14 | 2016-05-10 | Ethicon Endo-Surgery, Llc | Control arrangements for a drive member of a surgical instrument |
US9629629B2 (en) | 2013-03-14 | 2017-04-25 | Ethicon Endo-Surgey, LLC | Control systems for surgical instruments |
US9867612B2 (en) | 2013-04-16 | 2018-01-16 | Ethicon Llc | Powered surgical stapler |
BR112015026109B1 (en) | 2013-04-16 | 2022-02-22 | Ethicon Endo-Surgery, Inc | surgical instrument |
CA2919536C (en) * | 2013-08-09 | 2018-01-02 | Boston Scientific Scimed, Inc. | Atraumatic stents including radiopaque connectors and methods |
US9775609B2 (en) | 2013-08-23 | 2017-10-03 | Ethicon Llc | Tamper proof circuit for surgical instrument battery pack |
MX369362B (en) | 2013-08-23 | 2019-11-06 | Ethicon Endo Surgery Llc | Firing member retraction devices for powered surgical instruments. |
US9962161B2 (en) | 2014-02-12 | 2018-05-08 | Ethicon Llc | Deliverable surgical instrument |
US20150272557A1 (en) | 2014-03-26 | 2015-10-01 | Ethicon Endo-Surgery, Inc. | Modular surgical instrument system |
US9826977B2 (en) | 2014-03-26 | 2017-11-28 | Ethicon Llc | Sterilization verification circuit |
BR112016021943B1 (en) | 2014-03-26 | 2022-06-14 | Ethicon Endo-Surgery, Llc | SURGICAL INSTRUMENT FOR USE BY AN OPERATOR IN A SURGICAL PROCEDURE |
JP6612256B2 (en) | 2014-04-16 | 2019-11-27 | エシコン エルエルシー | Fastener cartridge with non-uniform fastener |
US20150297223A1 (en) | 2014-04-16 | 2015-10-22 | Ethicon Endo-Surgery, Inc. | Fastener cartridges including extensions having different configurations |
CN106456176B (en) | 2014-04-16 | 2019-06-28 | 伊西康内外科有限责任公司 | Fastener cartridge including the extension with various configuration |
US9844369B2 (en) | 2014-04-16 | 2017-12-19 | Ethicon Llc | Surgical end effectors with firing element monitoring arrangements |
JP6532889B2 (en) | 2014-04-16 | 2019-06-19 | エシコン エルエルシーEthicon LLC | Fastener cartridge assembly and staple holder cover arrangement |
US20160066913A1 (en) | 2014-09-05 | 2016-03-10 | Ethicon Endo-Surgery, Inc. | Local display of tissue parameter stabilization |
BR112017004361B1 (en) | 2014-09-05 | 2023-04-11 | Ethicon Llc | ELECTRONIC SYSTEM FOR A SURGICAL INSTRUMENT |
US11311294B2 (en) | 2014-09-05 | 2022-04-26 | Cilag Gmbh International | Powered medical device including measurement of closure state of jaws |
US10105142B2 (en) | 2014-09-18 | 2018-10-23 | Ethicon Llc | Surgical stapler with plurality of cutting elements |
US11523821B2 (en) | 2014-09-26 | 2022-12-13 | Cilag Gmbh International | Method for creating a flexible staple line |
JP6648119B2 (en) | 2014-09-26 | 2020-02-14 | エシコン エルエルシーEthicon LLC | Surgical stapling buttress and accessory materials |
US9924944B2 (en) | 2014-10-16 | 2018-03-27 | Ethicon Llc | Staple cartridge comprising an adjunct material |
US10517594B2 (en) | 2014-10-29 | 2019-12-31 | Ethicon Llc | Cartridge assemblies for surgical staplers |
US11141153B2 (en) | 2014-10-29 | 2021-10-12 | Cilag Gmbh International | Staple cartridges comprising driver arrangements |
US9844376B2 (en) | 2014-11-06 | 2017-12-19 | Ethicon Llc | Staple cartridge comprising a releasable adjunct material |
US10736636B2 (en) | 2014-12-10 | 2020-08-11 | Ethicon Llc | Articulatable surgical instrument system |
US9987000B2 (en) | 2014-12-18 | 2018-06-05 | Ethicon Llc | Surgical instrument assembly comprising a flexible articulation system |
US9844374B2 (en) | 2014-12-18 | 2017-12-19 | Ethicon Llc | Surgical instrument systems comprising an articulatable end effector and means for adjusting the firing stroke of a firing member |
US10004501B2 (en) | 2014-12-18 | 2018-06-26 | Ethicon Llc | Surgical instruments with improved closure arrangements |
US9844375B2 (en) | 2014-12-18 | 2017-12-19 | Ethicon Llc | Drive arrangements for articulatable surgical instruments |
RU2703684C2 (en) | 2014-12-18 | 2019-10-21 | ЭТИКОН ЭНДО-СЕРДЖЕРИ, ЭлЭлСи | Surgical instrument with anvil which is selectively movable relative to staple cartridge around discrete fixed axis |
US10085748B2 (en) | 2014-12-18 | 2018-10-02 | Ethicon Llc | Locking arrangements for detachable shaft assemblies with articulatable surgical end effectors |
US9999527B2 (en) | 2015-02-11 | 2018-06-19 | Abbott Cardiovascular Systems Inc. | Scaffolds having radiopaque markers |
US11154301B2 (en) | 2015-02-27 | 2021-10-26 | Cilag Gmbh International | Modular stapling assembly |
JP2020121162A (en) | 2015-03-06 | 2020-08-13 | エシコン エルエルシーEthicon LLC | Time dependent evaluation of sensor data to determine stability element, creep element and viscoelastic element of measurement |
US9993248B2 (en) | 2015-03-06 | 2018-06-12 | Ethicon Endo-Surgery, Llc | Smart sensors with local signal processing |
US10441279B2 (en) | 2015-03-06 | 2019-10-15 | Ethicon Llc | Multiple level thresholds to modify operation of powered surgical instruments |
US10245033B2 (en) | 2015-03-06 | 2019-04-02 | Ethicon Llc | Surgical instrument comprising a lockable battery housing |
US10052044B2 (en) | 2015-03-06 | 2018-08-21 | Ethicon Llc | Time dependent evaluation of sensor data to determine stability, creep, and viscoelastic elements of measures |
US10433844B2 (en) | 2015-03-31 | 2019-10-08 | Ethicon Llc | Surgical instrument with selectively disengageable threaded drive systems |
US9700443B2 (en) | 2015-06-12 | 2017-07-11 | Abbott Cardiovascular Systems Inc. | Methods for attaching a radiopaque marker to a scaffold |
US10835249B2 (en) | 2015-08-17 | 2020-11-17 | Ethicon Llc | Implantable layers for a surgical instrument |
US10238386B2 (en) | 2015-09-23 | 2019-03-26 | Ethicon Llc | Surgical stapler having motor control based on an electrical parameter related to a motor current |
US10105139B2 (en) | 2015-09-23 | 2018-10-23 | Ethicon Llc | Surgical stapler having downstream current-based motor control |
US10299878B2 (en) | 2015-09-25 | 2019-05-28 | Ethicon Llc | Implantable adjunct systems for determining adjunct skew |
US10980539B2 (en) | 2015-09-30 | 2021-04-20 | Ethicon Llc | Implantable adjunct comprising bonded layers |
US10603039B2 (en) * | 2015-09-30 | 2020-03-31 | Ethicon Llc | Progressively releasable implantable adjunct for use with a surgical stapling instrument |
US10271849B2 (en) | 2015-09-30 | 2019-04-30 | Ethicon Llc | Woven constructs with interlocked standing fibers |
US11890015B2 (en) | 2015-09-30 | 2024-02-06 | Cilag Gmbh International | Compressible adjunct with crossing spacer fibers |
US10292704B2 (en) | 2015-12-30 | 2019-05-21 | Ethicon Llc | Mechanisms for compensating for battery pack failure in powered surgical instruments |
US10368865B2 (en) | 2015-12-30 | 2019-08-06 | Ethicon Llc | Mechanisms for compensating for drivetrain failure in powered surgical instruments |
US10265068B2 (en) | 2015-12-30 | 2019-04-23 | Ethicon Llc | Surgical instruments with separable motors and motor control circuits |
US11213293B2 (en) | 2016-02-09 | 2022-01-04 | Cilag Gmbh International | Articulatable surgical instruments with single articulation link arrangements |
BR112018016098B1 (en) | 2016-02-09 | 2023-02-23 | Ethicon Llc | SURGICAL INSTRUMENT |
US10448948B2 (en) | 2016-02-12 | 2019-10-22 | Ethicon Llc | Mechanisms for compensating for drivetrain failure in powered surgical instruments |
US11224426B2 (en) | 2016-02-12 | 2022-01-18 | Cilag Gmbh International | Mechanisms for compensating for drivetrain failure in powered surgical instruments |
KR101761713B1 (en) * | 2016-03-28 | 2017-07-26 | 주식회사 시브이바이오 | The Biodegradable polymer vascular stent having markers |
US10492783B2 (en) | 2016-04-15 | 2019-12-03 | Ethicon, Llc | Surgical instrument with improved stop/start control during a firing motion |
US10357247B2 (en) | 2016-04-15 | 2019-07-23 | Ethicon Llc | Surgical instrument with multiple program responses during a firing motion |
US10456137B2 (en) | 2016-04-15 | 2019-10-29 | Ethicon Llc | Staple formation detection mechanisms |
US11179150B2 (en) | 2016-04-15 | 2021-11-23 | Cilag Gmbh International | Systems and methods for controlling a surgical stapling and cutting instrument |
US10828028B2 (en) | 2016-04-15 | 2020-11-10 | Ethicon Llc | Surgical instrument with multiple program responses during a firing motion |
US11607239B2 (en) | 2016-04-15 | 2023-03-21 | Cilag Gmbh International | Systems and methods for controlling a surgical stapling and cutting instrument |
US10426467B2 (en) | 2016-04-15 | 2019-10-01 | Ethicon Llc | Surgical instrument with detection sensors |
US10335145B2 (en) | 2016-04-15 | 2019-07-02 | Ethicon Llc | Modular surgical instrument with configurable operating mode |
US11317917B2 (en) | 2016-04-18 | 2022-05-03 | Cilag Gmbh International | Surgical stapling system comprising a lockable firing assembly |
US20170296173A1 (en) | 2016-04-18 | 2017-10-19 | Ethicon Endo-Surgery, Llc | Method for operating a surgical instrument |
US10426469B2 (en) | 2016-04-18 | 2019-10-01 | Ethicon Llc | Surgical instrument comprising a primary firing lockout and a secondary firing lockout |
MX2019007311A (en) | 2016-12-21 | 2019-11-18 | Ethicon Llc | Surgical stapling systems. |
US10856868B2 (en) | 2016-12-21 | 2020-12-08 | Ethicon Llc | Firing member pin configurations |
US10610224B2 (en) | 2016-12-21 | 2020-04-07 | Ethicon Llc | Lockout arrangements for surgical end effectors and replaceable tool assemblies |
US11134942B2 (en) | 2016-12-21 | 2021-10-05 | Cilag Gmbh International | Surgical stapling instruments and staple-forming anvils |
JP6983893B2 (en) | 2016-12-21 | 2021-12-17 | エシコン エルエルシーEthicon LLC | Lockout configuration for surgical end effectors and replaceable tool assemblies |
US10568624B2 (en) | 2016-12-21 | 2020-02-25 | Ethicon Llc | Surgical instruments with jaws that are pivotable about a fixed axis and include separate and distinct closure and firing systems |
US20180168598A1 (en) | 2016-12-21 | 2018-06-21 | Ethicon Endo-Surgery, Llc | Staple forming pocket arrangements comprising zoned forming surface grooves |
US20180168615A1 (en) | 2016-12-21 | 2018-06-21 | Ethicon Endo-Surgery, Llc | Method of deforming staples from two different types of staple cartridges with the same surgical stapling instrument |
US11090048B2 (en) | 2016-12-21 | 2021-08-17 | Cilag Gmbh International | Method for resetting a fuse of a surgical instrument shaft |
US10568625B2 (en) | 2016-12-21 | 2020-02-25 | Ethicon Llc | Staple cartridges and arrangements of staples and staple cavities therein |
US10675025B2 (en) | 2016-12-21 | 2020-06-09 | Ethicon Llc | Shaft assembly comprising separately actuatable and retractable systems |
US10588630B2 (en) | 2016-12-21 | 2020-03-17 | Ethicon Llc | Surgical tool assemblies with closure stroke reduction features |
JP7010956B2 (en) | 2016-12-21 | 2022-01-26 | エシコン エルエルシー | How to staple tissue |
US11191540B2 (en) | 2016-12-21 | 2021-12-07 | Cilag Gmbh International | Protective cover arrangements for a joint interface between a movable jaw and actuator shaft of a surgical instrument |
US20180168625A1 (en) | 2016-12-21 | 2018-06-21 | Ethicon Endo-Surgery, Llc | Surgical stapling instruments with smart staple cartridges |
US11419606B2 (en) | 2016-12-21 | 2022-08-23 | Cilag Gmbh International | Shaft assembly comprising a clutch configured to adapt the output of a rotary firing member to two different systems |
US10888321B2 (en) | 2017-06-20 | 2021-01-12 | Ethicon Llc | Systems and methods for controlling velocity of a displacement member of a surgical stapling and cutting instrument |
US10980537B2 (en) | 2017-06-20 | 2021-04-20 | Ethicon Llc | Closed loop feedback control of motor velocity of a surgical stapling and cutting instrument based on measured time over a specified number of shaft rotations |
US10779820B2 (en) | 2017-06-20 | 2020-09-22 | Ethicon Llc | Systems and methods for controlling motor speed according to user input for a surgical instrument |
US11071554B2 (en) | 2017-06-20 | 2021-07-27 | Cilag Gmbh International | Closed loop feedback control of motor velocity of a surgical stapling and cutting instrument based on magnitude of velocity error measurements |
US10881399B2 (en) | 2017-06-20 | 2021-01-05 | Ethicon Llc | Techniques for adaptive control of motor velocity of a surgical stapling and cutting instrument |
US11090046B2 (en) | 2017-06-20 | 2021-08-17 | Cilag Gmbh International | Systems and methods for controlling displacement member motion of a surgical stapling and cutting instrument |
US10307170B2 (en) | 2017-06-20 | 2019-06-04 | Ethicon Llc | Method for closed loop control of motor velocity of a surgical stapling and cutting instrument |
US11382638B2 (en) | 2017-06-20 | 2022-07-12 | Cilag Gmbh International | Closed loop feedback control of motor velocity of a surgical stapling and cutting instrument based on measured time over a specified displacement distance |
US11517325B2 (en) | 2017-06-20 | 2022-12-06 | Cilag Gmbh International | Closed loop feedback control of motor velocity of a surgical stapling and cutting instrument based on measured displacement distance traveled over a specified time interval |
US11653914B2 (en) | 2017-06-20 | 2023-05-23 | Cilag Gmbh International | Systems and methods for controlling motor velocity of a surgical stapling and cutting instrument according to articulation angle of end effector |
US10993716B2 (en) | 2017-06-27 | 2021-05-04 | Ethicon Llc | Surgical anvil arrangements |
US11324503B2 (en) | 2017-06-27 | 2022-05-10 | Cilag Gmbh International | Surgical firing member arrangements |
US10631859B2 (en) | 2017-06-27 | 2020-04-28 | Ethicon Llc | Articulation systems for surgical instruments |
US11266405B2 (en) | 2017-06-27 | 2022-03-08 | Cilag Gmbh International | Surgical anvil manufacturing methods |
US10903685B2 (en) | 2017-06-28 | 2021-01-26 | Ethicon Llc | Surgical shaft assemblies with slip ring assemblies forming capacitive channels |
US11246592B2 (en) | 2017-06-28 | 2022-02-15 | Cilag Gmbh International | Surgical instrument comprising an articulation system lockable to a frame |
US11259805B2 (en) | 2017-06-28 | 2022-03-01 | Cilag Gmbh International | Surgical instrument comprising firing member supports |
US11564686B2 (en) | 2017-06-28 | 2023-01-31 | Cilag Gmbh International | Surgical shaft assemblies with flexible interfaces |
US10765427B2 (en) | 2017-06-28 | 2020-09-08 | Ethicon Llc | Method for articulating a surgical instrument |
US20190000461A1 (en) | 2017-06-28 | 2019-01-03 | Ethicon Llc | Surgical cutting and fastening devices with pivotable anvil with a tissue locating arrangement in close proximity to an anvil pivot axis |
USD906355S1 (en) | 2017-06-28 | 2020-12-29 | Ethicon Llc | Display screen or portion thereof with a graphical user interface for a surgical instrument |
EP4070740A1 (en) | 2017-06-28 | 2022-10-12 | Cilag GmbH International | Surgical instrument comprising selectively actuatable rotatable couplers |
US11678880B2 (en) | 2017-06-28 | 2023-06-20 | Cilag Gmbh International | Surgical instrument comprising a shaft including a housing arrangement |
US10932772B2 (en) | 2017-06-29 | 2021-03-02 | Ethicon Llc | Methods for closed loop velocity control for robotic surgical instrument |
US11944300B2 (en) | 2017-08-03 | 2024-04-02 | Cilag Gmbh International | Method for operating a surgical system bailout |
US11304695B2 (en) | 2017-08-03 | 2022-04-19 | Cilag Gmbh International | Surgical system shaft interconnection |
US11471155B2 (en) | 2017-08-03 | 2022-10-18 | Cilag Gmbh International | Surgical system bailout |
USD907647S1 (en) | 2017-09-29 | 2021-01-12 | Ethicon Llc | Display screen or portion thereof with animated graphical user interface |
US11399829B2 (en) | 2017-09-29 | 2022-08-02 | Cilag Gmbh International | Systems and methods of initiating a power shutdown mode for a surgical instrument |
USD907648S1 (en) | 2017-09-29 | 2021-01-12 | Ethicon Llc | Display screen or portion thereof with animated graphical user interface |
US11090075B2 (en) | 2017-10-30 | 2021-08-17 | Cilag Gmbh International | Articulation features for surgical end effector |
US11134944B2 (en) | 2017-10-30 | 2021-10-05 | Cilag Gmbh International | Surgical stapler knife motion controls |
US10842490B2 (en) | 2017-10-31 | 2020-11-24 | Ethicon Llc | Cartridge body design with force reduction based on firing completion |
US11071543B2 (en) | 2017-12-15 | 2021-07-27 | Cilag Gmbh International | Surgical end effectors with clamping assemblies configured to increase jaw aperture ranges |
US11197670B2 (en) | 2017-12-15 | 2021-12-14 | Cilag Gmbh International | Surgical end effectors with pivotal jaws configured to touch at their respective distal ends when fully closed |
US10828033B2 (en) | 2017-12-15 | 2020-11-10 | Ethicon Llc | Handheld electromechanical surgical instruments with improved motor control arrangements for positioning components of an adapter coupled thereto |
US10966718B2 (en) | 2017-12-15 | 2021-04-06 | Ethicon Llc | Dynamic clamping assemblies with improved wear characteristics for use in connection with electromechanical surgical instruments |
US11033267B2 (en) | 2017-12-15 | 2021-06-15 | Ethicon Llc | Systems and methods of controlling a clamping member firing rate of a surgical instrument |
US10779826B2 (en) | 2017-12-15 | 2020-09-22 | Ethicon Llc | Methods of operating surgical end effectors |
US10779825B2 (en) | 2017-12-15 | 2020-09-22 | Ethicon Llc | Adapters with end effector position sensing and control arrangements for use in connection with electromechanical surgical instruments |
US10869666B2 (en) | 2017-12-15 | 2020-12-22 | Ethicon Llc | Adapters with control systems for controlling multiple motors of an electromechanical surgical instrument |
USD910847S1 (en) | 2017-12-19 | 2021-02-16 | Ethicon Llc | Surgical instrument assembly |
US10835330B2 (en) | 2017-12-19 | 2020-11-17 | Ethicon Llc | Method for determining the position of a rotatable jaw of a surgical instrument attachment assembly |
US11020112B2 (en) | 2017-12-19 | 2021-06-01 | Ethicon Llc | Surgical tools configured for interchangeable use with different controller interfaces |
US11129680B2 (en) | 2017-12-21 | 2021-09-28 | Cilag Gmbh International | Surgical instrument comprising a projector |
US11337691B2 (en) | 2017-12-21 | 2022-05-24 | Cilag Gmbh International | Surgical instrument configured to determine firing path |
US11311290B2 (en) | 2017-12-21 | 2022-04-26 | Cilag Gmbh International | Surgical instrument comprising an end effector dampener |
US11076853B2 (en) | 2017-12-21 | 2021-08-03 | Cilag Gmbh International | Systems and methods of displaying a knife position during transection for a surgical instrument |
US11291440B2 (en) | 2018-08-20 | 2022-04-05 | Cilag Gmbh International | Method for operating a powered articulatable surgical instrument |
US11039834B2 (en) | 2018-08-20 | 2021-06-22 | Cilag Gmbh International | Surgical stapler anvils with staple directing protrusions and tissue stability features |
US11324501B2 (en) | 2018-08-20 | 2022-05-10 | Cilag Gmbh International | Surgical stapling devices with improved closure members |
US11253256B2 (en) | 2018-08-20 | 2022-02-22 | Cilag Gmbh International | Articulatable motor powered surgical instruments with dedicated articulation motor arrangements |
US11207065B2 (en) | 2018-08-20 | 2021-12-28 | Cilag Gmbh International | Method for fabricating surgical stapler anvils |
US11045192B2 (en) | 2018-08-20 | 2021-06-29 | Cilag Gmbh International | Fabricating techniques for surgical stapler anvils |
US10856870B2 (en) | 2018-08-20 | 2020-12-08 | Ethicon Llc | Switching arrangements for motor powered articulatable surgical instruments |
US10912559B2 (en) | 2018-08-20 | 2021-02-09 | Ethicon Llc | Reinforced deformable anvil tip for surgical stapler anvil |
USD914878S1 (en) | 2018-08-20 | 2021-03-30 | Ethicon Llc | Surgical instrument anvil |
US11083458B2 (en) | 2018-08-20 | 2021-08-10 | Cilag Gmbh International | Powered surgical instruments with clutching arrangements to convert linear drive motions to rotary drive motions |
CN109498210B (en) * | 2018-11-08 | 2021-01-26 | 深圳市先健畅通医疗有限公司 | Lumen stent |
AU2020209654A1 (en) * | 2019-01-16 | 2021-07-29 | Edwards Lifesciences Corporation | Apparatus and method for monitoring valve expansion |
US11172929B2 (en) | 2019-03-25 | 2021-11-16 | Cilag Gmbh International | Articulation drive arrangements for surgical systems |
US11147551B2 (en) | 2019-03-25 | 2021-10-19 | Cilag Gmbh International | Firing drive arrangements for surgical systems |
US11147553B2 (en) | 2019-03-25 | 2021-10-19 | Cilag Gmbh International | Firing drive arrangements for surgical systems |
US11696761B2 (en) | 2019-03-25 | 2023-07-11 | Cilag Gmbh International | Firing drive arrangements for surgical systems |
US11903581B2 (en) | 2019-04-30 | 2024-02-20 | Cilag Gmbh International | Methods for stapling tissue using a surgical instrument |
US11426251B2 (en) | 2019-04-30 | 2022-08-30 | Cilag Gmbh International | Articulation directional lights on a surgical instrument |
US11432816B2 (en) | 2019-04-30 | 2022-09-06 | Cilag Gmbh International | Articulation pin for a surgical instrument |
US11648009B2 (en) | 2019-04-30 | 2023-05-16 | Cilag Gmbh International | Rotatable jaw tip for a surgical instrument |
US11253254B2 (en) | 2019-04-30 | 2022-02-22 | Cilag Gmbh International | Shaft rotation actuator on a surgical instrument |
US11471157B2 (en) | 2019-04-30 | 2022-10-18 | Cilag Gmbh International | Articulation control mapping for a surgical instrument |
US11452528B2 (en) | 2019-04-30 | 2022-09-27 | Cilag Gmbh International | Articulation actuators for a surgical instrument |
US11553971B2 (en) | 2019-06-28 | 2023-01-17 | Cilag Gmbh International | Surgical RFID assemblies for display and communication |
US11523822B2 (en) | 2019-06-28 | 2022-12-13 | Cilag Gmbh International | Battery pack including a circuit interrupter |
US11771419B2 (en) | 2019-06-28 | 2023-10-03 | Cilag Gmbh International | Packaging for a replaceable component of a surgical stapling system |
US11684434B2 (en) | 2019-06-28 | 2023-06-27 | Cilag Gmbh International | Surgical RFID assemblies for instrument operational setting control |
US11399837B2 (en) | 2019-06-28 | 2022-08-02 | Cilag Gmbh International | Mechanisms for motor control adjustments of a motorized surgical instrument |
US11497492B2 (en) | 2019-06-28 | 2022-11-15 | Cilag Gmbh International | Surgical instrument including an articulation lock |
US11376098B2 (en) | 2019-06-28 | 2022-07-05 | Cilag Gmbh International | Surgical instrument system comprising an RFID system |
US11051807B2 (en) | 2019-06-28 | 2021-07-06 | Cilag Gmbh International | Packaging assembly including a particulate trap |
US11638587B2 (en) | 2019-06-28 | 2023-05-02 | Cilag Gmbh International | RFID identification systems for surgical instruments |
US11291451B2 (en) | 2019-06-28 | 2022-04-05 | Cilag Gmbh International | Surgical instrument with battery compatibility verification functionality |
US11219455B2 (en) | 2019-06-28 | 2022-01-11 | Cilag Gmbh International | Surgical instrument including a lockout key |
US11298127B2 (en) | 2019-06-28 | 2022-04-12 | Cilag GmbH Interational | Surgical stapling system having a lockout mechanism for an incompatible cartridge |
US11627959B2 (en) | 2019-06-28 | 2023-04-18 | Cilag Gmbh International | Surgical instruments including manual and powered system lockouts |
US11464601B2 (en) | 2019-06-28 | 2022-10-11 | Cilag Gmbh International | Surgical instrument comprising an RFID system for tracking a movable component |
US11259803B2 (en) | 2019-06-28 | 2022-03-01 | Cilag Gmbh International | Surgical stapling system having an information encryption protocol |
US11478241B2 (en) | 2019-06-28 | 2022-10-25 | Cilag Gmbh International | Staple cartridge including projections |
US11246678B2 (en) | 2019-06-28 | 2022-02-15 | Cilag Gmbh International | Surgical stapling system having a frangible RFID tag |
US11224497B2 (en) | 2019-06-28 | 2022-01-18 | Cilag Gmbh International | Surgical systems with multiple RFID tags |
US11241235B2 (en) | 2019-06-28 | 2022-02-08 | Cilag Gmbh International | Method of using multiple RFID chips with a surgical assembly |
US11298132B2 (en) | 2019-06-28 | 2022-04-12 | Cilag GmbH Inlernational | Staple cartridge including a honeycomb extension |
US11426167B2 (en) | 2019-06-28 | 2022-08-30 | Cilag Gmbh International | Mechanisms for proper anvil attachment surgical stapling head assembly |
US11660163B2 (en) | 2019-06-28 | 2023-05-30 | Cilag Gmbh International | Surgical system with RFID tags for updating motor assembly parameters |
US11504122B2 (en) | 2019-12-19 | 2022-11-22 | Cilag Gmbh International | Surgical instrument comprising a nested firing member |
US11529137B2 (en) | 2019-12-19 | 2022-12-20 | Cilag Gmbh International | Staple cartridge comprising driver retention members |
US11446029B2 (en) | 2019-12-19 | 2022-09-20 | Cilag Gmbh International | Staple cartridge comprising projections extending from a curved deck surface |
US11559304B2 (en) | 2019-12-19 | 2023-01-24 | Cilag Gmbh International | Surgical instrument comprising a rapid closure mechanism |
US11304696B2 (en) | 2019-12-19 | 2022-04-19 | Cilag Gmbh International | Surgical instrument comprising a powered articulation system |
US11576672B2 (en) | 2019-12-19 | 2023-02-14 | Cilag Gmbh International | Surgical instrument comprising a closure system including a closure member and an opening member driven by a drive screw |
US11931033B2 (en) | 2019-12-19 | 2024-03-19 | Cilag Gmbh International | Staple cartridge comprising a latch lockout |
US11844520B2 (en) | 2019-12-19 | 2023-12-19 | Cilag Gmbh International | Staple cartridge comprising driver retention members |
US11464512B2 (en) | 2019-12-19 | 2022-10-11 | Cilag Gmbh International | Staple cartridge comprising a curved deck surface |
US11291447B2 (en) | 2019-12-19 | 2022-04-05 | Cilag Gmbh International | Stapling instrument comprising independent jaw closing and staple firing systems |
US11911032B2 (en) | 2019-12-19 | 2024-02-27 | Cilag Gmbh International | Staple cartridge comprising a seating cam |
US11529139B2 (en) | 2019-12-19 | 2022-12-20 | Cilag Gmbh International | Motor driven surgical instrument |
US11607219B2 (en) | 2019-12-19 | 2023-03-21 | Cilag Gmbh International | Staple cartridge comprising a detachable tissue cutting knife |
US11234698B2 (en) | 2019-12-19 | 2022-02-01 | Cilag Gmbh International | Stapling system comprising a clamp lockout and a firing lockout |
US11701111B2 (en) | 2019-12-19 | 2023-07-18 | Cilag Gmbh International | Method for operating a surgical stapling instrument |
USD966512S1 (en) | 2020-06-02 | 2022-10-11 | Cilag Gmbh International | Staple cartridge |
USD975850S1 (en) | 2020-06-02 | 2023-01-17 | Cilag Gmbh International | Staple cartridge |
USD974560S1 (en) | 2020-06-02 | 2023-01-03 | Cilag Gmbh International | Staple cartridge |
USD967421S1 (en) | 2020-06-02 | 2022-10-18 | Cilag Gmbh International | Staple cartridge |
USD975278S1 (en) | 2020-06-02 | 2023-01-10 | Cilag Gmbh International | Staple cartridge |
USD976401S1 (en) | 2020-06-02 | 2023-01-24 | Cilag Gmbh International | Staple cartridge |
USD975851S1 (en) | 2020-06-02 | 2023-01-17 | Cilag Gmbh International | Staple cartridge |
US11883024B2 (en) | 2020-07-28 | 2024-01-30 | Cilag Gmbh International | Method of operating a surgical instrument |
US11517390B2 (en) | 2020-10-29 | 2022-12-06 | Cilag Gmbh International | Surgical instrument comprising a limited travel switch |
USD1013170S1 (en) | 2020-10-29 | 2024-01-30 | Cilag Gmbh International | Surgical instrument assembly |
US11452526B2 (en) | 2020-10-29 | 2022-09-27 | Cilag Gmbh International | Surgical instrument comprising a staged voltage regulation start-up system |
US11534259B2 (en) | 2020-10-29 | 2022-12-27 | Cilag Gmbh International | Surgical instrument comprising an articulation indicator |
US11844518B2 (en) | 2020-10-29 | 2023-12-19 | Cilag Gmbh International | Method for operating a surgical instrument |
USD980425S1 (en) | 2020-10-29 | 2023-03-07 | Cilag Gmbh International | Surgical instrument assembly |
US11779330B2 (en) | 2020-10-29 | 2023-10-10 | Cilag Gmbh International | Surgical instrument comprising a jaw alignment system |
US11617577B2 (en) | 2020-10-29 | 2023-04-04 | Cilag Gmbh International | Surgical instrument comprising a sensor configured to sense whether an articulation drive of the surgical instrument is actuatable |
US11931025B2 (en) | 2020-10-29 | 2024-03-19 | Cilag Gmbh International | Surgical instrument comprising a releasable closure drive lock |
US11896217B2 (en) | 2020-10-29 | 2024-02-13 | Cilag Gmbh International | Surgical instrument comprising an articulation lock |
US11717289B2 (en) | 2020-10-29 | 2023-08-08 | Cilag Gmbh International | Surgical instrument comprising an indicator which indicates that an articulation drive is actuatable |
KR102528141B1 (en) * | 2020-11-13 | 2023-05-09 | 주식회사 시브이바이오 | Graft stent with different skin lengths for each location in preparation for the curve of blood vessels |
US11627960B2 (en) | 2020-12-02 | 2023-04-18 | Cilag Gmbh International | Powered surgical instruments with smart reload with separately attachable exteriorly mounted wiring connections |
US11678882B2 (en) | 2020-12-02 | 2023-06-20 | Cilag Gmbh International | Surgical instruments with interactive features to remedy incidental sled movements |
US11653920B2 (en) | 2020-12-02 | 2023-05-23 | Cilag Gmbh International | Powered surgical instruments with communication interfaces through sterile barrier |
US11849943B2 (en) | 2020-12-02 | 2023-12-26 | Cilag Gmbh International | Surgical instrument with cartridge release mechanisms |
US11744581B2 (en) | 2020-12-02 | 2023-09-05 | Cilag Gmbh International | Powered surgical instruments with multi-phase tissue treatment |
US11653915B2 (en) | 2020-12-02 | 2023-05-23 | Cilag Gmbh International | Surgical instruments with sled location detection and adjustment features |
US11944296B2 (en) | 2020-12-02 | 2024-04-02 | Cilag Gmbh International | Powered surgical instruments with external connectors |
US11890010B2 (en) | 2020-12-02 | 2024-02-06 | Cllag GmbH International | Dual-sided reinforced reload for surgical instruments |
US11737751B2 (en) | 2020-12-02 | 2023-08-29 | Cilag Gmbh International | Devices and methods of managing energy dissipated within sterile barriers of surgical instrument housings |
US11793514B2 (en) | 2021-02-26 | 2023-10-24 | Cilag Gmbh International | Staple cartridge comprising sensor array which may be embedded in cartridge body |
US11751869B2 (en) | 2021-02-26 | 2023-09-12 | Cilag Gmbh International | Monitoring of multiple sensors over time to detect moving characteristics of tissue |
US11925349B2 (en) | 2021-02-26 | 2024-03-12 | Cilag Gmbh International | Adjustment to transfer parameters to improve available power |
US11812964B2 (en) | 2021-02-26 | 2023-11-14 | Cilag Gmbh International | Staple cartridge comprising a power management circuit |
US11730473B2 (en) | 2021-02-26 | 2023-08-22 | Cilag Gmbh International | Monitoring of manufacturing life-cycle |
US11749877B2 (en) | 2021-02-26 | 2023-09-05 | Cilag Gmbh International | Stapling instrument comprising a signal antenna |
US11701113B2 (en) | 2021-02-26 | 2023-07-18 | Cilag Gmbh International | Stapling instrument comprising a separate power antenna and a data transfer antenna |
US11950779B2 (en) | 2021-02-26 | 2024-04-09 | Cilag Gmbh International | Method of powering and communicating with a staple cartridge |
US11723657B2 (en) | 2021-02-26 | 2023-08-15 | Cilag Gmbh International | Adjustable communication based on available bandwidth and power capacity |
US11696757B2 (en) | 2021-02-26 | 2023-07-11 | Cilag Gmbh International | Monitoring of internal systems to detect and track cartridge motion status |
US11744583B2 (en) | 2021-02-26 | 2023-09-05 | Cilag Gmbh International | Distal communication array to tune frequency of RF systems |
US11950777B2 (en) | 2021-02-26 | 2024-04-09 | Cilag Gmbh International | Staple cartridge comprising an information access control system |
US11826012B2 (en) | 2021-03-22 | 2023-11-28 | Cilag Gmbh International | Stapling instrument comprising a pulsed motor-driven firing rack |
US11826042B2 (en) | 2021-03-22 | 2023-11-28 | Cilag Gmbh International | Surgical instrument comprising a firing drive including a selectable leverage mechanism |
US11759202B2 (en) | 2021-03-22 | 2023-09-19 | Cilag Gmbh International | Staple cartridge comprising an implantable layer |
US11717291B2 (en) | 2021-03-22 | 2023-08-08 | Cilag Gmbh International | Staple cartridge comprising staples configured to apply different tissue compression |
US11723658B2 (en) | 2021-03-22 | 2023-08-15 | Cilag Gmbh International | Staple cartridge comprising a firing lockout |
US11806011B2 (en) | 2021-03-22 | 2023-11-07 | Cilag Gmbh International | Stapling instrument comprising tissue compression systems |
US11737749B2 (en) | 2021-03-22 | 2023-08-29 | Cilag Gmbh International | Surgical stapling instrument comprising a retraction system |
US11786243B2 (en) | 2021-03-24 | 2023-10-17 | Cilag Gmbh International | Firing members having flexible portions for adapting to a load during a surgical firing stroke |
US11903582B2 (en) | 2021-03-24 | 2024-02-20 | Cilag Gmbh International | Leveraging surfaces for cartridge installation |
US11793516B2 (en) | 2021-03-24 | 2023-10-24 | Cilag Gmbh International | Surgical staple cartridge comprising longitudinal support beam |
US11786239B2 (en) | 2021-03-24 | 2023-10-17 | Cilag Gmbh International | Surgical instrument articulation joint arrangements comprising multiple moving linkage features |
US11896219B2 (en) | 2021-03-24 | 2024-02-13 | Cilag Gmbh International | Mating features between drivers and underside of a cartridge deck |
US11849945B2 (en) | 2021-03-24 | 2023-12-26 | Cilag Gmbh International | Rotary-driven surgical stapling assembly comprising eccentrically driven firing member |
US11744603B2 (en) | 2021-03-24 | 2023-09-05 | Cilag Gmbh International | Multi-axis pivot joints for surgical instruments and methods for manufacturing same |
US11857183B2 (en) | 2021-03-24 | 2024-01-02 | Cilag Gmbh International | Stapling assembly components having metal substrates and plastic bodies |
US11832816B2 (en) | 2021-03-24 | 2023-12-05 | Cilag Gmbh International | Surgical stapling assembly comprising nonplanar staples and planar staples |
US11849944B2 (en) | 2021-03-24 | 2023-12-26 | Cilag Gmbh International | Drivers for fastener cartridge assemblies having rotary drive screws |
US11944336B2 (en) | 2021-03-24 | 2024-04-02 | Cilag Gmbh International | Joint arrangements for multi-planar alignment and support of operational drive shafts in articulatable surgical instruments |
US11896218B2 (en) | 2021-03-24 | 2024-02-13 | Cilag Gmbh International | Method of using a powered stapling device |
US11826047B2 (en) | 2021-05-28 | 2023-11-28 | Cilag Gmbh International | Stapling instrument comprising jaw mounts |
US11957337B2 (en) | 2021-10-18 | 2024-04-16 | Cilag Gmbh International | Surgical stapling assembly with offset ramped drive surfaces |
US11877745B2 (en) | 2021-10-18 | 2024-01-23 | Cilag Gmbh International | Surgical stapling assembly having longitudinally-repeating staple leg clusters |
US11937816B2 (en) | 2021-10-28 | 2024-03-26 | Cilag Gmbh International | Electrical lead arrangements for surgical instruments |
Family Cites Families (91)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2857915A (en) * | 1956-04-02 | 1958-10-28 | David S Sheridan | X-ray catheter |
US3605750A (en) * | 1969-04-07 | 1971-09-20 | David S Sheridan | X-ray tip catheter |
US3618614A (en) * | 1969-05-06 | 1971-11-09 | Scient Tube Products Inc | Nontoxic radiopaque multiwall medical-surgical tubings |
US4027659A (en) * | 1975-11-21 | 1977-06-07 | Krandex Corporation | Radiographic opaque and conductive stripped medical tubes |
US4173228A (en) * | 1977-05-16 | 1979-11-06 | Applied Medical Devices | Catheter locating device |
US4202349A (en) * | 1978-04-24 | 1980-05-13 | Jones James W | Radiopaque vessel markers |
JPS5582884A (en) * | 1978-12-19 | 1980-06-21 | Olympus Optical Co | Flexible tube and its manufacture |
US4588399A (en) * | 1980-05-14 | 1986-05-13 | Shiley Incorporated | Cannula with radiopaque tip |
US4571240A (en) * | 1983-08-12 | 1986-02-18 | Advanced Cardiovascular Systems, Inc. | Catheter having encapsulated tip marker |
US4547193A (en) * | 1984-04-05 | 1985-10-15 | Angiomedics Incorporated | Catheter having embedded multi-apertured film |
US4572198A (en) * | 1984-06-18 | 1986-02-25 | Varian Associates, Inc. | Catheter for use with NMR imaging systems |
US4581390A (en) * | 1984-06-29 | 1986-04-08 | Flynn Vincent J | Catheters comprising radiopaque polyurethane-silicone network resin compositions |
US4577637A (en) * | 1984-07-13 | 1986-03-25 | Argon Medical Corp. | Flexible metal radiopaque indicator and plugs for catheters |
US5045071A (en) * | 1985-12-17 | 1991-09-03 | Mbo Laboratories, Inc. | Double wall catheter with internal printing and embedded marker |
US5170789A (en) * | 1987-06-17 | 1992-12-15 | Perinchery Narayan | Insertable NMR coil probe |
US5154179A (en) * | 1987-07-02 | 1992-10-13 | Medical Magnetics, Inc. | Device construction and method facilitating magnetic resonance imaging of foreign objects in a body |
US4989608A (en) * | 1987-07-02 | 1991-02-05 | Ratner Adam V | Device construction and method facilitating magnetic resonance imaging of foreign objects in a body |
AU623100B2 (en) * | 1987-10-08 | 1992-05-07 | Terumo Kabushiki Kaisha | Instrument and apparatus for securing inner diameter of lumen of tubular organ |
US4938608A (en) * | 1988-04-25 | 1990-07-03 | Daniel Espinosa | Double-section plastic produce bag |
FI80585C (en) * | 1988-11-11 | 1990-07-10 | Instrumentarium Oy | ARRANGEMANG FOER UNDERSOEKNING AV ETT OBJEKT. |
US5348010A (en) * | 1989-02-24 | 1994-09-20 | Medrea, Inc., Pennsylvania Corp., Pa. | Intracavity probe and interface device for MRI imaging and spectroscopy |
US5147315A (en) * | 1990-04-06 | 1992-09-15 | C. R. Bard, Inc. | Access catheter and system for use in the female reproductive system |
US5034005A (en) * | 1990-07-09 | 1991-07-23 | Appling William M | Radiopaque marker |
US5247103A (en) * | 1990-09-20 | 1993-09-21 | Union Carbide Chemicals & Plastics Technology Corporation | Processes for the preparation of cyclic ethers |
US5256158A (en) * | 1991-05-17 | 1993-10-26 | Act Medical, Inc. | Device having a radiopaque marker for endoscopic accessories and method of making same |
GB9120508D0 (en) * | 1991-09-26 | 1991-11-06 | Nycomed As | Diagnostic agents |
US5669878A (en) * | 1992-01-30 | 1997-09-23 | Intravascular Research Limited | Guide wire for a catheter with position indicating means |
US5683448A (en) * | 1992-02-21 | 1997-11-04 | Boston Scientific Technology, Inc. | Intraluminal stent and graft |
US5203777A (en) * | 1992-03-19 | 1993-04-20 | Lee Peter Y | Radiopaque marker system for a tubular device |
JPH07505316A (en) * | 1992-03-31 | 1995-06-15 | ボストン サイエンティフィック コーポレーション | medical wire |
US5271400A (en) * | 1992-04-01 | 1993-12-21 | General Electric Company | Tracking system to monitor the position and orientation of a device using magnetic resonance detection of a sample contained within the device |
US5427103A (en) * | 1992-06-29 | 1995-06-27 | Olympus Optical Co., Ltd. | MRI apparatus for receiving nuclear-magnetic resonance signals of a living body |
US5647361A (en) * | 1992-09-28 | 1997-07-15 | Fonar Corporation | Magnetic resonance imaging method and apparatus for guiding invasive therapy |
US5383926A (en) * | 1992-11-23 | 1995-01-24 | Children's Medical Center Corporation | Re-expandable endoprosthesis |
US5347221A (en) * | 1993-03-09 | 1994-09-13 | Rubinson Kenneth A | Truncated nuclear magnetic imaging probe |
DE4310993A1 (en) * | 1993-04-03 | 1994-10-06 | Philips Patentverwaltung | MR imaging method and arrangement for carrying out the method |
US5427115A (en) * | 1993-09-13 | 1995-06-27 | Boston Scientific Corporation | Apparatus for stricture diagnosis and treatment |
US5855598A (en) * | 1993-10-21 | 1999-01-05 | Corvita Corporation | Expandable supportive branched endoluminal grafts |
US5429617A (en) * | 1993-12-13 | 1995-07-04 | The Spectranetics Corporation | Radiopaque tip marker for alignment of a catheter within a body |
US5609627A (en) * | 1994-02-09 | 1997-03-11 | Boston Scientific Technology, Inc. | Method for delivering a bifurcated endoluminal prosthesis |
US5520646A (en) * | 1994-03-03 | 1996-05-28 | D'andrea; Mark A. | Diagnostic marking catheter system for use in radiation diagnosis procedure |
US5948489A (en) * | 1994-03-03 | 1999-09-07 | Cordis Corporation | Catheter having extruded, flexible, pliable and compliant marker band |
JPH07303625A (en) * | 1994-03-18 | 1995-11-21 | Olympus Optical Co Ltd | Instrument for magnetic resonance tomography device |
EP0679372B1 (en) * | 1994-04-25 | 1999-07-28 | Advanced Cardiovascular Systems, Inc. | Radiopaque stent markers |
US5522881A (en) * | 1994-06-28 | 1996-06-04 | Meadox Medicals, Inc. | Implantable tubular prosthesis having integral cuffs |
US5728079A (en) * | 1994-09-19 | 1998-03-17 | Cordis Corporation | Catheter which is visible under MRI |
US5773419A (en) * | 1995-03-03 | 1998-06-30 | Falcon; Juan | Method of treating cancer with tannic acid |
DE19531117C2 (en) * | 1995-08-24 | 1999-05-12 | Daum Gmbh | Use of a titanium alloy for instruments for interventional magnetic resonance imaging and methods for the treatment of such instruments |
GB9521009D0 (en) * | 1995-10-13 | 1995-12-13 | Marconi Gec Ltd | Magnetic resonance methods and apparatus` |
US5607442A (en) * | 1995-11-13 | 1997-03-04 | Isostent, Inc. | Stent with improved radiopacity and appearance characteristics |
NL1001736C2 (en) * | 1995-11-23 | 1997-05-27 | Cordis Europ | Medical device visible in magnetic resonance imaging (MRI). |
WO1997019362A1 (en) * | 1995-11-24 | 1997-05-29 | Philips Electronics N.V. | Mri-system and catheter for interventional procedures |
US5727552A (en) * | 1996-01-11 | 1998-03-17 | Medtronic, Inc. | Catheter and electrical lead location system |
US5727553A (en) * | 1996-03-25 | 1998-03-17 | Saad; Saad A. | Catheter with integral electromagnetic location identification device |
NL1002898C2 (en) * | 1996-04-18 | 1997-10-21 | Cordis Europ | Catheter with marker sleeve. |
US5669932A (en) * | 1996-05-29 | 1997-09-23 | Isostent, Inc. | Means for accurately positioning an expandable stent |
JP4053091B2 (en) * | 1996-09-02 | 2008-02-27 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Invasive device used in magnetic resonance imaging apparatus |
US5824046A (en) * | 1996-09-27 | 1998-10-20 | Scimed Life Systems, Inc. | Covered stent |
US5938601A (en) * | 1996-11-21 | 1999-08-17 | Picker International, Inc. | Nuclear magnetic resonance imaging apparatus |
GB9626070D0 (en) * | 1996-12-16 | 1997-02-05 | Marconi Gec Ltd | Nuclear magnetic resonance imaging apparatus |
US5779731A (en) * | 1996-12-20 | 1998-07-14 | Cordis Corporation | Balloon catheter having dual markers and method |
US5759174A (en) * | 1997-01-29 | 1998-06-02 | Cathco, Inc. | Angioplasty balloon with an expandable external radiopaque marker band |
ATE287679T1 (en) * | 1997-03-05 | 2005-02-15 | Boston Scient Ltd | COMPLIANT MULTI-LAYER STENT DEVICE |
US6019737A (en) * | 1997-03-31 | 2000-02-01 | Terumo Kabushiki Kaisha | Guide wire |
US5919126A (en) * | 1997-07-07 | 1999-07-06 | Implant Sciences Corporation | Coronary stent with a radioactive, radiopaque coating |
US6174330B1 (en) * | 1997-08-01 | 2001-01-16 | Schneider (Usa) Inc | Bioabsorbable marker having radiopaque constituents |
US5908413A (en) * | 1997-10-03 | 1999-06-01 | Scimed Life Systems, Inc. | Radiopaque catheter and method of manufacture thereof |
NO311781B1 (en) * | 1997-11-13 | 2002-01-28 | Medinol Ltd | Metal multilayer stents |
US6179811B1 (en) * | 1997-11-25 | 2001-01-30 | Medtronic, Inc. | Imbedded marker and flexible guide wire shaft |
US6036682A (en) * | 1997-12-02 | 2000-03-14 | Scimed Life Systems, Inc. | Catheter having a plurality of integral radiopaque bands |
US6022374A (en) * | 1997-12-16 | 2000-02-08 | Cardiovasc, Inc. | Expandable stent having radiopaque marker and method |
US6228072B1 (en) * | 1998-02-19 | 2001-05-08 | Percusurge, Inc. | Shaft for medical catheters |
US6238340B1 (en) * | 1998-05-19 | 2001-05-29 | Eckhard Alt | Composite materials for avoidance of unwanted radiation amplification |
US6139511A (en) * | 1998-06-29 | 2000-10-31 | Advanced Cardiovascular Systems, Inc. | Guidewire with variable coil configuration |
US6171297B1 (en) * | 1998-06-30 | 2001-01-09 | Schneider (Usa) Inc | Radiopaque catheter tip |
US6126650A (en) * | 1998-06-30 | 2000-10-03 | Cordis Corporation | Flow directed catheter having radiopaque strain relief segment |
US6210396B1 (en) * | 1999-06-24 | 2001-04-03 | Medtronic, Inc. | Guiding catheter with tungsten loaded band |
US6520934B1 (en) * | 1999-12-29 | 2003-02-18 | Advanced Cardiovascular Systems, Inc. | Catheter assemblies with flexible radiopaque marker |
JP2001327609A (en) * | 2000-05-19 | 2001-11-27 | Terumo Corp | Stent for staying in vivo |
US6620114B2 (en) * | 2000-10-05 | 2003-09-16 | Scimed Life Systems, Inc. | Guidewire having a marker segment for length assessment |
US7077837B2 (en) * | 2000-11-20 | 2006-07-18 | Implant Sciences Corporation | Multi-layered radiopaque coating on intravascular devices |
US6545097B2 (en) * | 2000-12-12 | 2003-04-08 | Scimed Life Systems, Inc. | Drug delivery compositions and medical devices containing block copolymer |
US20020095205A1 (en) * | 2001-01-12 | 2002-07-18 | Edwin Tarun J. | Encapsulated radiopaque markers |
US6636758B2 (en) * | 2001-05-01 | 2003-10-21 | Concentric Medical, Inc. | Marker wire and process for using it |
US8197535B2 (en) * | 2001-06-19 | 2012-06-12 | Cordis Corporation | Low profile improved radiopacity intraluminal medical device |
US7052512B2 (en) * | 2001-07-18 | 2006-05-30 | Boston Scientific Scimed, Inc. | Fluorescent dyed lubricant for medical devices |
JP4398244B2 (en) * | 2001-10-04 | 2010-01-13 | ネオヴァスク メディカル リミテッド | Flow reduction implant |
US20030125711A1 (en) * | 2001-10-04 | 2003-07-03 | Eidenschink Tracee E.J. | Flexible marker band |
US7147661B2 (en) * | 2001-12-20 | 2006-12-12 | Boston Scientific Santa Rosa Corp. | Radially expandable stent |
US7331986B2 (en) * | 2002-10-09 | 2008-02-19 | Boston Scientific Scimed, Inc. | Intraluminal medical device having improved visibility |
US8088158B2 (en) * | 2002-12-20 | 2012-01-03 | Boston Scientific Scimed, Inc. | Radiopaque ePTFE medical devices |
-
2004
- 2004-06-18 US US10/872,164 patent/US20050283226A1/en not_active Abandoned
-
2005
- 2005-06-16 WO PCT/US2005/021521 patent/WO2006009867A1/en active Application Filing
- 2005-06-16 EP EP05762261A patent/EP1778129A1/en not_active Withdrawn
- 2005-06-16 JP JP2007516792A patent/JP2008503270A/en active Pending
- 2005-06-16 CA CA002570914A patent/CA2570914A1/en not_active Abandoned
Also Published As
Publication number | Publication date |
---|---|
US20050283226A1 (en) | 2005-12-22 |
WO2006009867A1 (en) | 2006-01-26 |
EP1778129A1 (en) | 2007-05-02 |
JP2008503270A (en) | 2008-02-07 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US20050283226A1 (en) | Medical devices | |
US20230093376A1 (en) | Stent | |
US6143022A (en) | Stent-graft assembly with dual configuration graft component and method of manufacture | |
EP3445283B1 (en) | Stent-graft prosthesis and method of manufacture | |
AU762169B2 (en) | Wire reinforced vascular prosthesis | |
EP3445282B1 (en) | Diametrically adjustable endoprostheses | |
EP1011529B1 (en) | Conformal laminate stent device | |
US6673105B1 (en) | Metal prosthesis coated with expandable ePTFE | |
US20020095205A1 (en) | Encapsulated radiopaque markers | |
JP2020505984A (en) | Pre-strained stent elements | |
EP0938879A2 (en) | Stent-graft assembly and method of manufacture | |
EP2037848A1 (en) | Endoprosthesis delivery system with stent holder | |
WO1996028115A1 (en) | Endoluminal encapsulated stent and methods of manufacture and endoluminal delivery | |
JP2009514656A (en) | Graft and stent graft with radiopaque beading | |
US8221486B2 (en) | Laminated stent graft edge binding | |
WO2015168016A1 (en) | Method for producing radiopaque medical implants | |
US20230076862A1 (en) | Encapsulated devices with separation layers |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
EEER | Examination request | ||
FZDE | Discontinued |
Effective date: 20130522 |