CA2102019C - Device for the implantation of self-expanding endoprostheses - Google Patents
Device for the implantation of self-expanding endoprosthesesInfo
- Publication number
- CA2102019C CA2102019C CA2102019A CA2102019A CA2102019C CA 2102019 C CA2102019 C CA 2102019C CA 2102019 A CA2102019 A CA 2102019A CA 2102019 A CA2102019 A CA 2102019A CA 2102019 C CA2102019 C CA 2102019C
- Authority
- CA
- Canada
- Prior art keywords
- endoprosthesis
- core element
- stamping
- tubular
- contracted state
- 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.)
- Expired - Fee Related
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
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
-
- 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
- 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
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/962—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve
- A61F2/966—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve with relative longitudinal movement between outer sleeve and prosthesis, e.g. using a push rod
- A61F2002/9665—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve with relative longitudinal movement between outer sleeve and prosthesis, e.g. using a push rod with additional retaining means
Abstract
A device for implanting endoprostheses (1) has basically a tubular outer body (2) and an elongated core element (3) placed inside of this. To operate the device, both the core element (3) and the tubular body (2) are provided with handles (5, 6) at their proximal ends. In order to produce a form-locking connection between the endoprosthesis (1) and the core element (3), the core element (3) exhibits a region (10) in which is impressed a relief corresponding to the inner form of the endoprosthesis (1). As a result of this, there are a great number of form- locking meshing sites between the enclosed, folded endoprosthesis (1) and the core element (3). A device with this type of design permits partially released endoprostheses (1) to be folded back up again by pushing the tubular body (2) forward so that the endoprosthesis (1) may be repositioned. In addition, sure and reliable operation is achieved by this type of stamping of the core element (3).
Description
DEVICE FOR THE IMPLANTATION
OF SELF-EXPANDING ENDOPROSTHESES
Backqround of the Invention The invention relates to a device for implanting self-expanding endoprostheses according to the description ofPatent Claim 1.
Endoprostheses of the generic type can be inserted, for example, in veins, bile ducts or urinary tracts to maintain patency. They are also used to prevent recurring stenoses in the sense of an elastic recoiling or a cicatrized constriction following balloon dilation of arteries.
In most known devices, the axial length of the endoprosthesis is considerably longer when it is folded up than when it is expanded. Therefore, positioning in vessels, etc., is relatively difficult, since the exact length and location of the endoprosthesis is not apparent until after it unfolds. In most known devices, the endoprostheses can be released by way of a relative motion between the tubular body and the core element.
A common feature of all the devices currently available on the market, however, is the fact that once the endoprosthesis is partially released, it can no longer be folded back up again. This means that once even just a small piece of the endoprosthesis is released, the device can only be removed from the body by completely releasing the endoprosthesis and leaving it in the body. Moreover, once the endoprosthesis is partially released, it can only be pulled proximally but not pushed, since the expanded distal end ofthe endoprosthesis would inevitably injure the vessel in which it was supposed to be introduced if it were pushed. Also, the shape of the endoprosthesis would be affected by this forcing action; it would be compressed and its supporting elements would buckle.
If it is discovered when the endoprosthesis is released and unfolded that the final location does not correspond to the desired position, the possibility should thus exist of pulling the endoprosthesis back into the 21020~.9 device again after it is partially released so that it can accordingly be repositioned in a folded state.
A device of this type, described as an instrument for inserting a self-expanding implant, is outlined in [design patent] DE-GBM G 90 10 130.8. This device consists basically of an outer casing inside of which is an axial hollow core. The core has a diameter that increases incrementally at its distal end, whereby the distal end of the core strikes against the distal end of the casing.
Around the distal end of the core is-a gripping component that firmly holds a self-expanding implant in such a way that it can be separated. In order to produce a friction-locking connection between the core or the gripping component and the expanding prosthesis, the gripping component is made of a high-friction material. In addition, another type model provides for coating the gripping component with an agent for gluing the expanding implant in such a way that it can be separated.
A disadvantage of this device is the fact that the outer casing must tightly enclose the expanding implant so that a friction-locking connection is ensured between the gripping component and the self-expanding implant as proposed. As a result of this, a relative displacement creates a great deal of friction between the core and the outer casing, and naturally between the expanding implant and the inner wall of the outer casing, so that consequently forces exerted to release the expanding implant and to withdraw it are great. Furthermore, there is a risk that due to the relatively strong forces being exerted, reliability with respect to precise positioning of the implant will be adversely affected accordingly, because in addition to the friction between the expanding implant and the outer casing, there is also the friction between the core and the outer casing along the entire remaining length of the device. Moreover, it is more expensive to ensure by creation of the corresponding friction coefficients that the relative movement actually occurs as intended between the expanding implant and the outer casing, although there the normal force on the friction surfaces is higher by the total expansion force of the expanding implant than the normal force between the core and expanding implant.
With this device it is crucial, in order to achieve a very specific friction between the core and the expanding implant, that a normal force also be required that is just as precise. In this case, the amount of normal force is determined by the elasticity of the outer casing, the elasticity of the expanding implant, and the elasticity of the core, on the one hand, and by the inner diameter of the outer casing, the thickness of the expanding implant and the outer diameter of the core, on the other. Moreover, the expansion force of the expanding implant further determines the amount of normal force; it works against the normal force. The required normal force must be met exactly in order to produce a specific friction force; on the other hand, however, the normal force is very sensitive to the determining factors cited. Mass production of this device therefore presents great problems.
The additional proposal in the aforementioned design patent with respect to coating the gripping component with an agent for gluing the expanding implant in such a way that it can be separated brings with it the risk that the expanding implant, especially when stored for longer periods, will no longer expand on its own after the outer casing is pulled back, since its opening force is too weak, or that the adhesive coat will undergo chemical changes with time and consequently that the desired friction-locking connection will no longer be guaranteed. Applying the adhesive coat also presents problems; every effort must be made to prevent the adhesive coat from getting between elements of the expanding implant, which must move toward one another when the implant expands. Separable adhesive agents derive their properties from the fact that they always retain certain rheological properties; they do not harden. Consequently, the danger exists that adhesive agents that are properly applied originally will begin to run during the time the device is stored and that the 21020 19~
expandlng implant wlll become stuck together.
Another type model of the design patent provides for supplylng the gripplng component wlth a roughened surface.
However, wlth a roughened surface, there is the danger that the expanding implant wlll become deformed and, as a result, that lts shape wlll be affected, particularly when it expands.
Is should be noted in general that a sure method of operation cannot be achieved in every case by means of type models such as those proposed in the aforementioned deslgn patent, since wlth the manufacturlng of expandlng lmplants and, ln particular, wlth the type of compresslon, high tolerances wlth respect to accuracy to gauge and expansion force must be reckoned with.
Summary of the Invention It is therefore the purpose of the invention to provide a slmple device for implanting endoprostheses and folding them back up again in which, compared to devices that do not permit the endoprosthesis to be folded back up again, the operatlng force ls not lncreased and the free and undeformed unfolding of the endoprosthesis is not affected, which can be manufactured easily and inexpensively, which guarantees sure operation even after long storage perlods, and ln whlch even certaln unavoldable manufacturlng tolerances of the endoprosthesls do not have any adverse affect on lts sure operatlon, particularly ln releaslng the endoprosthesls and foldlng lt back agaln.
The lnventlon provldes an lmplantlng devlce ln comblnatlon with a tubular radlally self-expandlng B
OF SELF-EXPANDING ENDOPROSTHESES
Backqround of the Invention The invention relates to a device for implanting self-expanding endoprostheses according to the description ofPatent Claim 1.
Endoprostheses of the generic type can be inserted, for example, in veins, bile ducts or urinary tracts to maintain patency. They are also used to prevent recurring stenoses in the sense of an elastic recoiling or a cicatrized constriction following balloon dilation of arteries.
In most known devices, the axial length of the endoprosthesis is considerably longer when it is folded up than when it is expanded. Therefore, positioning in vessels, etc., is relatively difficult, since the exact length and location of the endoprosthesis is not apparent until after it unfolds. In most known devices, the endoprostheses can be released by way of a relative motion between the tubular body and the core element.
A common feature of all the devices currently available on the market, however, is the fact that once the endoprosthesis is partially released, it can no longer be folded back up again. This means that once even just a small piece of the endoprosthesis is released, the device can only be removed from the body by completely releasing the endoprosthesis and leaving it in the body. Moreover, once the endoprosthesis is partially released, it can only be pulled proximally but not pushed, since the expanded distal end ofthe endoprosthesis would inevitably injure the vessel in which it was supposed to be introduced if it were pushed. Also, the shape of the endoprosthesis would be affected by this forcing action; it would be compressed and its supporting elements would buckle.
If it is discovered when the endoprosthesis is released and unfolded that the final location does not correspond to the desired position, the possibility should thus exist of pulling the endoprosthesis back into the 21020~.9 device again after it is partially released so that it can accordingly be repositioned in a folded state.
A device of this type, described as an instrument for inserting a self-expanding implant, is outlined in [design patent] DE-GBM G 90 10 130.8. This device consists basically of an outer casing inside of which is an axial hollow core. The core has a diameter that increases incrementally at its distal end, whereby the distal end of the core strikes against the distal end of the casing.
Around the distal end of the core is-a gripping component that firmly holds a self-expanding implant in such a way that it can be separated. In order to produce a friction-locking connection between the core or the gripping component and the expanding prosthesis, the gripping component is made of a high-friction material. In addition, another type model provides for coating the gripping component with an agent for gluing the expanding implant in such a way that it can be separated.
A disadvantage of this device is the fact that the outer casing must tightly enclose the expanding implant so that a friction-locking connection is ensured between the gripping component and the self-expanding implant as proposed. As a result of this, a relative displacement creates a great deal of friction between the core and the outer casing, and naturally between the expanding implant and the inner wall of the outer casing, so that consequently forces exerted to release the expanding implant and to withdraw it are great. Furthermore, there is a risk that due to the relatively strong forces being exerted, reliability with respect to precise positioning of the implant will be adversely affected accordingly, because in addition to the friction between the expanding implant and the outer casing, there is also the friction between the core and the outer casing along the entire remaining length of the device. Moreover, it is more expensive to ensure by creation of the corresponding friction coefficients that the relative movement actually occurs as intended between the expanding implant and the outer casing, although there the normal force on the friction surfaces is higher by the total expansion force of the expanding implant than the normal force between the core and expanding implant.
With this device it is crucial, in order to achieve a very specific friction between the core and the expanding implant, that a normal force also be required that is just as precise. In this case, the amount of normal force is determined by the elasticity of the outer casing, the elasticity of the expanding implant, and the elasticity of the core, on the one hand, and by the inner diameter of the outer casing, the thickness of the expanding implant and the outer diameter of the core, on the other. Moreover, the expansion force of the expanding implant further determines the amount of normal force; it works against the normal force. The required normal force must be met exactly in order to produce a specific friction force; on the other hand, however, the normal force is very sensitive to the determining factors cited. Mass production of this device therefore presents great problems.
The additional proposal in the aforementioned design patent with respect to coating the gripping component with an agent for gluing the expanding implant in such a way that it can be separated brings with it the risk that the expanding implant, especially when stored for longer periods, will no longer expand on its own after the outer casing is pulled back, since its opening force is too weak, or that the adhesive coat will undergo chemical changes with time and consequently that the desired friction-locking connection will no longer be guaranteed. Applying the adhesive coat also presents problems; every effort must be made to prevent the adhesive coat from getting between elements of the expanding implant, which must move toward one another when the implant expands. Separable adhesive agents derive their properties from the fact that they always retain certain rheological properties; they do not harden. Consequently, the danger exists that adhesive agents that are properly applied originally will begin to run during the time the device is stored and that the 21020 19~
expandlng implant wlll become stuck together.
Another type model of the design patent provides for supplylng the gripplng component wlth a roughened surface.
However, wlth a roughened surface, there is the danger that the expanding implant wlll become deformed and, as a result, that lts shape wlll be affected, particularly when it expands.
Is should be noted in general that a sure method of operation cannot be achieved in every case by means of type models such as those proposed in the aforementioned deslgn patent, since wlth the manufacturlng of expandlng lmplants and, ln particular, wlth the type of compresslon, high tolerances wlth respect to accuracy to gauge and expansion force must be reckoned with.
Summary of the Invention It is therefore the purpose of the invention to provide a slmple device for implanting endoprostheses and folding them back up again in which, compared to devices that do not permit the endoprosthesis to be folded back up again, the operatlng force ls not lncreased and the free and undeformed unfolding of the endoprosthesis is not affected, which can be manufactured easily and inexpensively, which guarantees sure operation even after long storage perlods, and ln whlch even certaln unavoldable manufacturlng tolerances of the endoprosthesls do not have any adverse affect on lts sure operatlon, particularly ln releaslng the endoprosthesls and foldlng lt back agaln.
The lnventlon provldes an lmplantlng devlce ln comblnatlon with a tubular radlally self-expandlng B
2 1 0 2 0 1 9 ~
- 4a -endoprosthesls comprlslng: an elongated lnner core element havlng an outer surface over whlch sald endoprosthesls ls placed and a tubular outer body that can be moved ln relatlon to sald core element and that at least partlally surrounds sald core element and sald endoprosthesls to hold sald endoprosthesls ln a radlally contracted state, the endoprosthesls havlng a longltudlnal length ln a radlally contracted state, whereln sald core element has a stamplng on lts outer surface correspondlng to at least 10% and at most 50% of the longltudinal length of the contracted endoprosthesls, the stamplng essentlally complementlng the shape of an lnner surface of sald endoprosthesls when sald endoprosthesls ls in a radlally contracted state.
The lnventlon also provldes an lmplantlng devlce ln comblnatlon wlth a tubular radlally self-expandlng endoprosthesls comprlslng: an elongated lnner core element havlng a distal end and an outer surface over which sald endoprosthesls ls placed and a tubular outer body that can be moved ln relatlon to sald core element and that at least partially surrounds sald core element and sald endoprosthesls to hold sald endoprosthesls ln a radially contracted state, wherein sald core element has a coating or sheath at least ln a reglon of the dlstal end havlng a stamplng essentlally complementlng an lnner surface of sald endoprosthesls when sald endoprosthesls ls ln a radlally contracted state.
The lnventlon further provldes an lmplantlng devlce ln comblnation with a tubular radially self-expanding endoprosthesls comprlslng: an elongated lnner core element 75420-l B
-- 4b -havlng an outer surface over whlch said endoprosthesls ls placed and a tubular outer body that can be moved ln relation to sald core element and that at least partlally surrounds sald core element and sald endoprosthesls to hold said endoprosthesls ln a radlally contracted state, whereln said core element, at least on part of its outer surface, has a stamplng essentlally complementlng the shape of an lnner surface of sald endoprosthesis when sald endoprosthesls ls ln a radially contracted state and wherein the endoprosthesis comprises several layers and at most 50% of a thickness of an innermost layer of the endoprosthesis meshes with said stamping.
The invention also further provldes an lmplantlng devlce in combination wlth a tubular radlally self-expandlng endoprosthesls comprlslng: an elongated inner core element having an outer surface over which said endoprosthesis ls placed and a tubular outer body that can be moved in relation to sald core element and that at least partlally surrounds said core element and sald endoprosthesls to hold sald endoprosthesls ln a radlally contracted state, whereln said core element, at least on part of lts outer surface, has a stamplng essentlally complementlng the shape of an lnner surface of sald endoprosthesls when sald endoprosthesls ls ln a radlally contracted state, whereln sald core element has a shoulder sltuated proxlmally wlth respect to the endoprosthesls and the shoulder comprlses a rlng made of x-ray opaque material.
B
21û20 ~9 - 4c -The lnvention also provides a process for providlng a locking attachment between the outer surface of an elongate core element and a tubular self-expanding endroprosthesis ln radlally contracted state, said elongate core element being for use in an endroprosthesis implanting device which includes an outer tubular body that at least partially surrounds the core element and is movable longitudinally in relation thereto, the endroprosthesis being held in radially contracted state between the outer body and the core element and in locking engagement with the core element, said process comprising pressing into the surface of the core element a stamping that is essentially complementary to the shape of the inner surface of the endroprosthesis when in contracted state.
The invention also provides the process of preparing an implantable device comprising: providing an elongate inner core element having an outer surface; providing a tubular outer body that can be moved in relation to said core element and that at least partially surrounds said core element;
providlng a stamplng in the core element in accordance with the process of claim 1; insertlng the lndividual prosthesis in folded radlally contracted condltlon around the core element with its proximal end on an area of the core element in whlch there ls no stamplng; pushlng the outer tubular body forwardly until it encloses the proximal end of the folded endroprosthesis so that the latter is secured in positlon by the outer tubular body which presses it into the stamping in the core element; and fully enclosing the folded endroprosthesls by advancing the tubular outer body forwardly B
2 1 ~ 2 o t 9 - 4d -to engage the dlstal end of the core element.
Designlng the endoprosthesls ln such a way that the core element exhlbits on a portlon of lts surface an impressed rellef that corresponds to the structure of the lnner surface of the endoprosthesls guarantees, on the one hand, that the forces exerted to move the core element ln B
. ~ ......
relation to the outer body can be kept to a minimum and, on the other hand, that a sure radial separation of the self-expanding endoprosthesis from the core element is still ensured even after a long storage period. Thus sure and reliable operation is achieved by means of such a design.
This type of endoprosthesis can also be manufactured easily and inexpensively.
A preferred type model of the invention provides for the relief impressed on the core element to be individually adapted to the structure of the inner surface of the endoprosthesis. Such a design ensures that an optimal form-locking connection is achieved between the core element and the endoprosthesis and therefore guarantees the greatest possible operational reliability. In this case, the individual form-locking meshing sites are individually matched to one another with respect to their position, arrangement, and design.
A preferred process provides for using the individual endoprosthesis that is to be inserted in the device to form ~ 20 the relief. An advantage of this process is that great tolerances with respect to accuracy to gauge of the endoprosthesis do not themselves adversely affect the operational reliability of the device.
Brief Descri~tion of the Drawin~s Two examples of the invention~s design are explained in greater detail in the following using the drawings. The drawings show:
Fig. l. A device in a partial cutaway view with a separate representation of a folded endoprosthesis;
Fig. 2. The device in partial cutaway view with an enclosed endoprosthesis;
Fig. 3. An enlarged cross section through a first type model of the device along line A-A in Fig. 2;
Fig. 3a An enlarged cross section through a second type model of the device along line A-A in Fig. 2; and 2102Q l 9 Fig. 4 The device in a partial cutaway view with a partially unfolded endoprosthesis.
Detailed Description of the Invention The device represented in Figure 1 for implanting endoprosthesis 1 has basically a tubular, flexible outer body 2 and an elongated, flexible core element 3.
Tubular outer body 2 is represented in lengthwise section from break line x to its distal end. At its proximal end, tubular body 2 is provided with a handle 5.
Elongated core element 3 is placed in tubular body 2, where core element 3 is designed to be longer than tubular body 2 and also has a handle 6. Toward its distal end, core element 3 exhibits a region B, which serves to receive endoprosthesis 1. This region B exhibits at its proximal end a shoulder 8 made from X-ray opaque material. Distally contiguous to this is a section 9, the diameter of which is reduced. Following section 9 is an area 10 in which a relief in the form of a stamping 11 is impressed and which exhibits a somewhat larger diameter than section 9 preceding it. The form of relief or stamping 11 corresponds to the structure of the inner surface of folded endoprosthesis 1.
Contiguous to area 10 lies a section 13 that exhibits approximately the same diameter as section 9. Following this is a ring 14, which is also made of X-ray opaque material and which is designed to be somewhat larger in diameter than section 13. Finally, at its distal end, core element 3 has a blunt, cone-shaped tip 15.
Extending the entire length of core element 3 is a lumen 16 in which a guide wire 17 can be inserted. For the sake of better clarity, endoprosthesis 1 is depicted outside of the device and folded up in this representation. In this way, the correlation between the form of stamping 11 and that of folded endoprosthesis 1 can be seen. It can also be clearly seen from this representation that the length of area 10, which is provided with stamping 11, is shorter than the length of the endoprosthesis; it preferably totals approximately 10-50% of the length of the endoprosthesis.
As a result of this length of stamping 11, the flexibility of the device in region B of endoprosthesis 1 is affected as little as possible by the piled up material and the form locking in the stamping area. On the other hand, however, a reliable form-locking connection between enclosed endoprosthesis 1 and core element 2 is guaranteed.
Fig. 2 shows the device in a ready-to-use condition.
Here endoprosthesis 1 is enclosed folded up between core element 3 and tubular outer body 2. At the same time, the inner surface of endoprosthesis 1 meshes with core element 3 along stamping 11 impressed in area 10. Stamping 11 corresponds to the structure of the inner surface of endoprosthesis 1, so that a large number of form-locking meshing sites are formed between area 10 of core element 3 and endoprosthesis 1. Since the individual threads of a layer of endoprosthesis 1 diverge when the latter is folded up, differences in the location of the threads with respect to stamping 11 could result in the region of the proximal and distal ends of endoprosthesis 1. For this reason, it is advantageous to provide sections 9 and 13, which have a smaller diameter than area 10, between the latter, which is provided with stamping 11, and the ends of endoprosthesis 1.
A first type model of the device can be seen in Fig.
3 in an enlarged cross section along line A-A of Fig. 2.
Endoprosthesis 1 is enclosed between tubular outer body 2 and core element 3. The distance between the outer diameter of core element 3 and the inner diameter of tubular outer body 2 is chosen in such a way that the inner layer of endoprosthesis 1 is pressed into the recesses resulting from stamping 11. The depth of stamping 11 corresponds to approximately 50~ of the thickness of the inner layer of the semifinished material used in endoprosthesis 1. In this case, a thin wire is used as the semifinished material for manufacturing endoprosthesis 1. However, the same ratio applies if endoprosthesis 1 is punched out, for example, from thin sheet metal or is made of strip metal. The above-mentioned depth of stamping 11 ensures a good form-locking connection between core element 3 and endoprosthesis 1 by means of a large number of form-locking meshing sites 20 and guarantees, in addition, sure radial separation and unfolding of released endoprosthesis 1, because the form-locking connection does not affect the relative motion ofthe layers of semifinished material in relation to one another.
A second type model of the device is illustrated in fig. 3a in an enlarged cross section along line A-A in Fig.
2. In this example, core element 3 has a coating or sheath 3a. The advantage of such a coating or sheath 3a is that it can exhibit properties other than those of core element 3. The change in diameter required in this area can be easily obtained as well by means of this sheath or coating 3a. Thus, for example, the thermoplasticity of core element 3 can be lower than that of coating or sheath 3a.
Consequently, the depth of stamping 11 can be easily influenced by the thickness of coating or sheath 3a. Sheath 3a can be manufactured very easily, for example, by shrinking a contracting tube onto core element 3.
The operation of the device is explained by means of Fig. 4. Using the device, endoprosthesis 1 is inserted folded (Fig. 2) in a body canal 22, which is only indicated schematically, in the known manner and is advanced until the distal end region B of the device is positioned so that enclosed endoprosthesis 1 is at the desired location in body canal 22. At the same time, the advance of folded endoprosthesis 1 in body canal 22 is monitored by means of known processes such as fluoroscopy. The location of endoprosthesis 1 is readily visible due to X-ray opaque rings 8 and 14, which are fitted on core element 3 in the area of the two ends of enclosed endoprosthesis 1.
Once endoprosthesis 1 is in the intended final position, core element 3 is locked into position and endoprosthesis 1 is slowly released by pulling back tubular outer body 2. The two handles 5 and 6 are used for this purpose. Since endoprosthesis 1 is self-expanding, the released portion begins to unfold and rest against the inner 21020~9 wall of body canal 22. In unfolding, the length of endoprosthesis 1 is shortened accordlngly. Since there is a direct connection between the shortening of endoprosthesis 1 and the inner diameter of body canal and the diameter of endoprosthesis 1 in its inserted, unfolded state but the final amount of expansion is not known exactly, the final position of unfolded endoprosthesis 1 cannot be determined with certainty beforehand. Thus the position of endoprosthesis 1 must also be monitored during the unfolding. If monitoring shows that it is positioned correctly, endoprosthesis 1 can be completely released by pulling back tubular body 2 to the area of shoulder 8 of core element 3. If, however, it is discovered during the unfolding that endoprosthesis 1 is not in the correct position, it can be folded back up again in tubular body 2 by moving tubular body 2 forward. This makes it possible for endoprosthesis 1 to then be repositioned accordingly and released again in the new position in the manner described above.
By means of a form-locking connection between endoprosthesis 1 and core element 3, which is achieved via stamping 11, which corresponds to the structure of the inner surface of endoprosthesis 1, and via endoprosthesis 1, which meshes with stamping 11, it can be ensured, on the one hand, that the forces exerted to move core element 3 with respect to outer body 2 can be kept to a minimum and, on the other hand, that sure radial separation of self-expanding endoprosthesis l from core element 3 is still guaranteed even after a long period of storage. In short, sure and reliable operation is achieved by way of a device with this design. It can also be manufactured easily and inexpensively.
The process for producing a stamping for this type of device can go as follows: An endoprosthesis 1 is pushed unfolded onto region B of core element 3. Then endoprosthesis 1 is folded up in the area of section 9 of core element 3 in which there is no stamping. Next, tubular outer body 2 is pushed forward up to the proximal end of 21020~ 9 area l0 of core element 3. Endoprosthesis 1 is secured in position in this way. Endoprosthesis 1 is subsequently folded up in the area where it is exposed by a pressing die, which is in itself known, and pressed by the pressing die on area 10 of core element 3. The pressing die is now warmed with hot air so that endoprosthesis 1, which has been pressed together, is heated and in this way pressed into the thermoplastic material of core element 3 or into its coating or sheath 3a. After removing the pressing die, tubular outer body 2 is pushed forward untiI its distal end lies against the back side of tip 15 of core element 3 and endoprosthesis 1 is thus completely enclosed. A
corresponding process is utilized if a hardened plastic is used instead of the thermoplastic material. While this process is being carried out, it is absolutely imperative that shoulder 8 does not rest against the proximal end of endoprosthesis 1. It automatically rests against the proximal end of endoprosthesis 1 once endoprosthesis 1 comes unmeshed from core element 3 upon release. Shoulder 8 serves then as an abutment for endoprosthesis 1 when the remaining portion of the endoprosthesis still enclosed in tubular body 2 is released.
Obviously, processes are also conceivable in which the same endoprosthesis is always used to form the stamping.
Furthermore, it is also possible to impress the stamping by means of a positive cast of an endoprosthesis formed on the pressing die.
- 4a -endoprosthesls comprlslng: an elongated lnner core element havlng an outer surface over whlch sald endoprosthesls ls placed and a tubular outer body that can be moved ln relatlon to sald core element and that at least partlally surrounds sald core element and sald endoprosthesls to hold sald endoprosthesls ln a radlally contracted state, the endoprosthesls havlng a longltudlnal length ln a radlally contracted state, whereln sald core element has a stamplng on lts outer surface correspondlng to at least 10% and at most 50% of the longltudinal length of the contracted endoprosthesls, the stamplng essentlally complementlng the shape of an lnner surface of sald endoprosthesls when sald endoprosthesls ls in a radlally contracted state.
The lnventlon also provldes an lmplantlng devlce ln comblnatlon wlth a tubular radlally self-expandlng endoprosthesls comprlslng: an elongated lnner core element havlng a distal end and an outer surface over which sald endoprosthesls ls placed and a tubular outer body that can be moved ln relatlon to sald core element and that at least partially surrounds sald core element and sald endoprosthesls to hold sald endoprosthesls ln a radially contracted state, wherein sald core element has a coating or sheath at least ln a reglon of the dlstal end havlng a stamplng essentlally complementlng an lnner surface of sald endoprosthesls when sald endoprosthesls ls ln a radlally contracted state.
The lnventlon further provldes an lmplantlng devlce ln comblnation with a tubular radially self-expanding endoprosthesls comprlslng: an elongated lnner core element 75420-l B
-- 4b -havlng an outer surface over whlch said endoprosthesls ls placed and a tubular outer body that can be moved ln relation to sald core element and that at least partlally surrounds sald core element and sald endoprosthesls to hold said endoprosthesls ln a radlally contracted state, whereln said core element, at least on part of its outer surface, has a stamplng essentlally complementlng the shape of an lnner surface of sald endoprosthesis when sald endoprosthesls ls ln a radially contracted state and wherein the endoprosthesis comprises several layers and at most 50% of a thickness of an innermost layer of the endoprosthesis meshes with said stamping.
The invention also further provldes an lmplantlng devlce in combination wlth a tubular radlally self-expandlng endoprosthesls comprlslng: an elongated inner core element having an outer surface over which said endoprosthesis ls placed and a tubular outer body that can be moved in relation to sald core element and that at least partlally surrounds said core element and sald endoprosthesls to hold sald endoprosthesls ln a radlally contracted state, whereln said core element, at least on part of lts outer surface, has a stamplng essentlally complementlng the shape of an lnner surface of sald endoprosthesls when sald endoprosthesls ls ln a radlally contracted state, whereln sald core element has a shoulder sltuated proxlmally wlth respect to the endoprosthesls and the shoulder comprlses a rlng made of x-ray opaque material.
B
21û20 ~9 - 4c -The lnvention also provides a process for providlng a locking attachment between the outer surface of an elongate core element and a tubular self-expanding endroprosthesis ln radlally contracted state, said elongate core element being for use in an endroprosthesis implanting device which includes an outer tubular body that at least partially surrounds the core element and is movable longitudinally in relation thereto, the endroprosthesis being held in radially contracted state between the outer body and the core element and in locking engagement with the core element, said process comprising pressing into the surface of the core element a stamping that is essentially complementary to the shape of the inner surface of the endroprosthesis when in contracted state.
The invention also provides the process of preparing an implantable device comprising: providing an elongate inner core element having an outer surface; providing a tubular outer body that can be moved in relation to said core element and that at least partially surrounds said core element;
providlng a stamplng in the core element in accordance with the process of claim 1; insertlng the lndividual prosthesis in folded radlally contracted condltlon around the core element with its proximal end on an area of the core element in whlch there ls no stamplng; pushlng the outer tubular body forwardly until it encloses the proximal end of the folded endroprosthesis so that the latter is secured in positlon by the outer tubular body which presses it into the stamping in the core element; and fully enclosing the folded endroprosthesls by advancing the tubular outer body forwardly B
2 1 ~ 2 o t 9 - 4d -to engage the dlstal end of the core element.
Designlng the endoprosthesls ln such a way that the core element exhlbits on a portlon of lts surface an impressed rellef that corresponds to the structure of the lnner surface of the endoprosthesls guarantees, on the one hand, that the forces exerted to move the core element ln B
. ~ ......
relation to the outer body can be kept to a minimum and, on the other hand, that a sure radial separation of the self-expanding endoprosthesis from the core element is still ensured even after a long storage period. Thus sure and reliable operation is achieved by means of such a design.
This type of endoprosthesis can also be manufactured easily and inexpensively.
A preferred type model of the invention provides for the relief impressed on the core element to be individually adapted to the structure of the inner surface of the endoprosthesis. Such a design ensures that an optimal form-locking connection is achieved between the core element and the endoprosthesis and therefore guarantees the greatest possible operational reliability. In this case, the individual form-locking meshing sites are individually matched to one another with respect to their position, arrangement, and design.
A preferred process provides for using the individual endoprosthesis that is to be inserted in the device to form ~ 20 the relief. An advantage of this process is that great tolerances with respect to accuracy to gauge of the endoprosthesis do not themselves adversely affect the operational reliability of the device.
Brief Descri~tion of the Drawin~s Two examples of the invention~s design are explained in greater detail in the following using the drawings. The drawings show:
Fig. l. A device in a partial cutaway view with a separate representation of a folded endoprosthesis;
Fig. 2. The device in partial cutaway view with an enclosed endoprosthesis;
Fig. 3. An enlarged cross section through a first type model of the device along line A-A in Fig. 2;
Fig. 3a An enlarged cross section through a second type model of the device along line A-A in Fig. 2; and 2102Q l 9 Fig. 4 The device in a partial cutaway view with a partially unfolded endoprosthesis.
Detailed Description of the Invention The device represented in Figure 1 for implanting endoprosthesis 1 has basically a tubular, flexible outer body 2 and an elongated, flexible core element 3.
Tubular outer body 2 is represented in lengthwise section from break line x to its distal end. At its proximal end, tubular body 2 is provided with a handle 5.
Elongated core element 3 is placed in tubular body 2, where core element 3 is designed to be longer than tubular body 2 and also has a handle 6. Toward its distal end, core element 3 exhibits a region B, which serves to receive endoprosthesis 1. This region B exhibits at its proximal end a shoulder 8 made from X-ray opaque material. Distally contiguous to this is a section 9, the diameter of which is reduced. Following section 9 is an area 10 in which a relief in the form of a stamping 11 is impressed and which exhibits a somewhat larger diameter than section 9 preceding it. The form of relief or stamping 11 corresponds to the structure of the inner surface of folded endoprosthesis 1.
Contiguous to area 10 lies a section 13 that exhibits approximately the same diameter as section 9. Following this is a ring 14, which is also made of X-ray opaque material and which is designed to be somewhat larger in diameter than section 13. Finally, at its distal end, core element 3 has a blunt, cone-shaped tip 15.
Extending the entire length of core element 3 is a lumen 16 in which a guide wire 17 can be inserted. For the sake of better clarity, endoprosthesis 1 is depicted outside of the device and folded up in this representation. In this way, the correlation between the form of stamping 11 and that of folded endoprosthesis 1 can be seen. It can also be clearly seen from this representation that the length of area 10, which is provided with stamping 11, is shorter than the length of the endoprosthesis; it preferably totals approximately 10-50% of the length of the endoprosthesis.
As a result of this length of stamping 11, the flexibility of the device in region B of endoprosthesis 1 is affected as little as possible by the piled up material and the form locking in the stamping area. On the other hand, however, a reliable form-locking connection between enclosed endoprosthesis 1 and core element 2 is guaranteed.
Fig. 2 shows the device in a ready-to-use condition.
Here endoprosthesis 1 is enclosed folded up between core element 3 and tubular outer body 2. At the same time, the inner surface of endoprosthesis 1 meshes with core element 3 along stamping 11 impressed in area 10. Stamping 11 corresponds to the structure of the inner surface of endoprosthesis 1, so that a large number of form-locking meshing sites are formed between area 10 of core element 3 and endoprosthesis 1. Since the individual threads of a layer of endoprosthesis 1 diverge when the latter is folded up, differences in the location of the threads with respect to stamping 11 could result in the region of the proximal and distal ends of endoprosthesis 1. For this reason, it is advantageous to provide sections 9 and 13, which have a smaller diameter than area 10, between the latter, which is provided with stamping 11, and the ends of endoprosthesis 1.
A first type model of the device can be seen in Fig.
3 in an enlarged cross section along line A-A of Fig. 2.
Endoprosthesis 1 is enclosed between tubular outer body 2 and core element 3. The distance between the outer diameter of core element 3 and the inner diameter of tubular outer body 2 is chosen in such a way that the inner layer of endoprosthesis 1 is pressed into the recesses resulting from stamping 11. The depth of stamping 11 corresponds to approximately 50~ of the thickness of the inner layer of the semifinished material used in endoprosthesis 1. In this case, a thin wire is used as the semifinished material for manufacturing endoprosthesis 1. However, the same ratio applies if endoprosthesis 1 is punched out, for example, from thin sheet metal or is made of strip metal. The above-mentioned depth of stamping 11 ensures a good form-locking connection between core element 3 and endoprosthesis 1 by means of a large number of form-locking meshing sites 20 and guarantees, in addition, sure radial separation and unfolding of released endoprosthesis 1, because the form-locking connection does not affect the relative motion ofthe layers of semifinished material in relation to one another.
A second type model of the device is illustrated in fig. 3a in an enlarged cross section along line A-A in Fig.
2. In this example, core element 3 has a coating or sheath 3a. The advantage of such a coating or sheath 3a is that it can exhibit properties other than those of core element 3. The change in diameter required in this area can be easily obtained as well by means of this sheath or coating 3a. Thus, for example, the thermoplasticity of core element 3 can be lower than that of coating or sheath 3a.
Consequently, the depth of stamping 11 can be easily influenced by the thickness of coating or sheath 3a. Sheath 3a can be manufactured very easily, for example, by shrinking a contracting tube onto core element 3.
The operation of the device is explained by means of Fig. 4. Using the device, endoprosthesis 1 is inserted folded (Fig. 2) in a body canal 22, which is only indicated schematically, in the known manner and is advanced until the distal end region B of the device is positioned so that enclosed endoprosthesis 1 is at the desired location in body canal 22. At the same time, the advance of folded endoprosthesis 1 in body canal 22 is monitored by means of known processes such as fluoroscopy. The location of endoprosthesis 1 is readily visible due to X-ray opaque rings 8 and 14, which are fitted on core element 3 in the area of the two ends of enclosed endoprosthesis 1.
Once endoprosthesis 1 is in the intended final position, core element 3 is locked into position and endoprosthesis 1 is slowly released by pulling back tubular outer body 2. The two handles 5 and 6 are used for this purpose. Since endoprosthesis 1 is self-expanding, the released portion begins to unfold and rest against the inner 21020~9 wall of body canal 22. In unfolding, the length of endoprosthesis 1 is shortened accordlngly. Since there is a direct connection between the shortening of endoprosthesis 1 and the inner diameter of body canal and the diameter of endoprosthesis 1 in its inserted, unfolded state but the final amount of expansion is not known exactly, the final position of unfolded endoprosthesis 1 cannot be determined with certainty beforehand. Thus the position of endoprosthesis 1 must also be monitored during the unfolding. If monitoring shows that it is positioned correctly, endoprosthesis 1 can be completely released by pulling back tubular body 2 to the area of shoulder 8 of core element 3. If, however, it is discovered during the unfolding that endoprosthesis 1 is not in the correct position, it can be folded back up again in tubular body 2 by moving tubular body 2 forward. This makes it possible for endoprosthesis 1 to then be repositioned accordingly and released again in the new position in the manner described above.
By means of a form-locking connection between endoprosthesis 1 and core element 3, which is achieved via stamping 11, which corresponds to the structure of the inner surface of endoprosthesis 1, and via endoprosthesis 1, which meshes with stamping 11, it can be ensured, on the one hand, that the forces exerted to move core element 3 with respect to outer body 2 can be kept to a minimum and, on the other hand, that sure radial separation of self-expanding endoprosthesis l from core element 3 is still guaranteed even after a long period of storage. In short, sure and reliable operation is achieved by way of a device with this design. It can also be manufactured easily and inexpensively.
The process for producing a stamping for this type of device can go as follows: An endoprosthesis 1 is pushed unfolded onto region B of core element 3. Then endoprosthesis 1 is folded up in the area of section 9 of core element 3 in which there is no stamping. Next, tubular outer body 2 is pushed forward up to the proximal end of 21020~ 9 area l0 of core element 3. Endoprosthesis 1 is secured in position in this way. Endoprosthesis 1 is subsequently folded up in the area where it is exposed by a pressing die, which is in itself known, and pressed by the pressing die on area 10 of core element 3. The pressing die is now warmed with hot air so that endoprosthesis 1, which has been pressed together, is heated and in this way pressed into the thermoplastic material of core element 3 or into its coating or sheath 3a. After removing the pressing die, tubular outer body 2 is pushed forward untiI its distal end lies against the back side of tip 15 of core element 3 and endoprosthesis 1 is thus completely enclosed. A
corresponding process is utilized if a hardened plastic is used instead of the thermoplastic material. While this process is being carried out, it is absolutely imperative that shoulder 8 does not rest against the proximal end of endoprosthesis 1. It automatically rests against the proximal end of endoprosthesis 1 once endoprosthesis 1 comes unmeshed from core element 3 upon release. Shoulder 8 serves then as an abutment for endoprosthesis 1 when the remaining portion of the endoprosthesis still enclosed in tubular body 2 is released.
Obviously, processes are also conceivable in which the same endoprosthesis is always used to form the stamping.
Furthermore, it is also possible to impress the stamping by means of a positive cast of an endoprosthesis formed on the pressing die.
Claims (23)
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. An implanting device in combination with a tubular radially self-expanding endoprosthesis comprising: an elongated inner core element having an outer surface over which said endoprosthesis is placed and a tubular outer body that can be moved in relation to said core element and that at least partially surrounds said core element and said endoprosthesis to hold said endoprosthesis in a radially contracted state, the endoprosthesis having a longitudinal length in a radially contracted state, wherein said core element has a stamping on its outer surface corresponding to at least 10% and at most 50% of the longitudinal length of the contracted endoprosthesis, the stamping essentially complementing the shape of an inner surface of said endoprosthesis when said endoprosthesis is in a radially contracted state.
2. The device according to claim 1, wherein said implanting device is configured to be used to implant various endoprostheses, wherein said stamping is individually adapted to complement the structure of the inner surface of each endoprosthesis used.
3. The device according to claim 1, wherein said endoprosthesis has a proximal end and said core element has an area that has no stamping at the proximal end of the endoprosthesis.
4. The device according to claim 1, wherein a depth of said stamping is at least approximately 50% of a thickness of the endoprosthesis.
5. The device according to claim 1, wherein an average distance between an outer diameter of said core element and an inner diameter of said tubular body is less than a thickness of the endoprosthesis in a region of said stamping.
6. The device according to claim 1, wherein said core element has a lumen for receiving as guide wire.
7. The device according to claim 1, wherein said core element has a shoulder situated proximally with respect to the endoprosthesis.
8. The device according to claim 1, wherein said core element has an outer surface in regions bordering said stamping that do not have any stamping.
9. An implanting device in combination with a tubular radially self-expanding endoprosthesis comprising: an elongated inner core element having a distal end and an outer surface over which said endoprosthesis is placed and a tubular outer body that can be moved in relation to said core element and that at least partially surrounds said core element and said endoprosthesis to hold said endoprosthesis in a radially contracted state, wherein said core element has a coating or sheath at least in a region of the distal end having a stamping essentially complementing an inner surface of said endoprosthesis when said endoprosthesis is in a radially contracted state.
10. The device according to claim 9, wherein said coating or sheath is made of a thermoplastic material.
11. The device according to claim 10, wherein said coating or sheath is a sheath comprising a piece of plastic tubing which is shrunk onto said core element.
12. The device according to claim 9, wherein the core element has a thermoplasticity which is lower than a thermoplasticity of the coating or sheath.
13. An implanting device in combination with a tubular radially self-expanding endoprosthesis comprising: an elongated inner core element having an outer surface over which said endoprosthesis is placed and a tubular outer body that can be moved in relation to said core element and that at least partially surrounds said core element and said endoprosthesis to hold said endoprosthesis in a radially contracted state, wherein said core element, at least on part of its outer surface, has a stamping essentially complementing the shape of an inner surface of said endoprosthesis when said endoprosthesis is in a radially contracted state and wherein the endoprosthesis comprises several layers and at most 50% of a thickness of an innermost layer of the endoprosthesis meshes with said stamping.
14. An implanting device in combination with a tubular radially self-expanding endoprosthesis comprising: an elongated inner core element having an outer surface over which said endoprosthesis is placed and a tubular outer body that can be moved in relation to said core element and that at least partially surrounds said core element and said endoprosthesis to hold said endoprosthesis in a radially contracted state, wherein said core element, at least on part of its outer surface, has a stamping essentially complementing the shape of an inner surface of said endoprosthesis when said endoprosthesis is in a radially contracted state, wherein said core element has a shoulder situated proximally with respect to the endoprosthesis and the shoulder comprises a ring made of x-ray opaque material.
15. A process for providing a locking attachment between the outer surface of an elongate core element and a tubular self-expanding endoprosthesis in radially contracted state, said elongate core element being for use in an endoprosthesis implanting device which includes an outer tubular body that at least partially surrounds the core element and is movable longitudinally in relation thereto, the endoprosthesis being held in radially contracted state between the outer body and the core element and in locking engagement with the core element, said process comprising pressing into the surface of the core element a stamping that is essentially complementary to the shape of the inner surface of the endoprosthesis when in contracted state.
16. A process according to claim 15 wherein said stamping is formed on the surface of the core element by casting.
17. A process as claimed in claim 15 wherein said stamping is formed in the surface of the core element by thermal action.
18. A process according to claim 15 wherein said stamping is formed by pressing the endroprosthesis when in contracting condition into the surface.
19. A process according to any one of claims 15 to 18 wherein said stamping is formed in a coating carried by said core element.
20. A process according to claim 19 wherein said coating is provided by a tubular sheet that is shrunk onto said core element.
21. The process of preparing an implantable device comprising:
providing an elongate inner core element having an outer surface; providing a tubular outer body that can be moved in relation to said core element and that at least partially surrounds said core element;
providing a stamping in the core element in accordance with the process of claim 1;
inserting the individual prosthesis in folded radially contracted condition around the core element with its proximal end on an area of the core element in which there is no stamping;
pushing the outer tubular body forwardly until it encloses the proximal end of the folded endroprosthesis so that the latter is secured in position by the outer tubular body which presses it into the stamping in the core element;
and fully enclosing the folded endroprosthesis by advancing the tubular outer body forwardly to engage the distal end of the core element.
providing an elongate inner core element having an outer surface; providing a tubular outer body that can be moved in relation to said core element and that at least partially surrounds said core element;
providing a stamping in the core element in accordance with the process of claim 1;
inserting the individual prosthesis in folded radially contracted condition around the core element with its proximal end on an area of the core element in which there is no stamping;
pushing the outer tubular body forwardly until it encloses the proximal end of the folded endroprosthesis so that the latter is secured in position by the outer tubular body which presses it into the stamping in the core element;
and fully enclosing the folded endroprosthesis by advancing the tubular outer body forwardly to engage the distal end of the core element.
22. A process according to claim 21 wherein said stamping is formed in a coating carried by said core element.
23. A process according to claim 22 wherein said coating is provided by a tubular sheet that is shrunk onto said core element.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP92118671A EP0596145B1 (en) | 1992-10-31 | 1992-10-31 | Disposition for implanting a self-expanding endoprothesis |
EP92118671.4 | 1992-10-31 |
Publications (2)
Publication Number | Publication Date |
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CA2102019A1 CA2102019A1 (en) | 1994-05-01 |
CA2102019C true CA2102019C (en) | 1997-06-03 |
Family
ID=8210200
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA2102019A Expired - Fee Related CA2102019C (en) | 1992-10-31 | 1993-10-29 | Device for the implantation of self-expanding endoprostheses |
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Country | Link |
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US (1) | US5484444A (en) |
EP (1) | EP0596145B1 (en) |
JP (1) | JP2828390B2 (en) |
AT (1) | ATE137656T1 (en) |
AU (1) | AU669007B2 (en) |
CA (1) | CA2102019C (en) |
DE (1) | DE59206251D1 (en) |
ES (1) | ES2089342T3 (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6302893B1 (en) | 1996-07-15 | 2001-10-16 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent delivery system |
Families Citing this family (368)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5683448A (en) | 1992-02-21 | 1997-11-04 | Boston Scientific Technology, Inc. | Intraluminal stent and graft |
US5707376A (en) * | 1992-08-06 | 1998-01-13 | William Cook Europe A/S | Stent introducer and method of use |
ES2059202T3 (en) * | 1992-12-16 | 1994-11-01 | Schneider Europ Ag | DEVICE TO IMPLEMENT A SELF-EXPANDABLE ENDOPROTESIS IN A VESSEL. |
US5989280A (en) * | 1993-10-22 | 1999-11-23 | Scimed Lifesystems, Inc | Stent delivery apparatus and method |
EP0803264B2 (en) | 1996-04-26 | 2011-04-27 | Schneider (Europe) GmbH | Interventional catheter |
US5961765A (en) | 1994-09-20 | 1999-10-05 | Schneider (Europe) A. G. | Method of making a catheter |
US6659977B2 (en) | 1993-10-27 | 2003-12-09 | Schneider (Europe) A.G. | Multilayer interventional catheter |
US6039749A (en) | 1994-02-10 | 2000-03-21 | Endovascular Systems, Inc. | Method and apparatus for deploying non-circular stents and graftstent complexes |
US6165210A (en) | 1994-04-01 | 2000-12-26 | Gore Enterprise Holdings, Inc. | Self-expandable helical intravascular stent and stent-graft |
US6001123A (en) | 1994-04-01 | 1999-12-14 | Gore Enterprise Holdings Inc. | Folding self-expandable intravascular stent-graft |
US5456694A (en) * | 1994-05-13 | 1995-10-10 | Stentco, Inc. | Device for delivering and deploying intraluminal devices |
DK63894A (en) * | 1994-06-06 | 1996-01-08 | Meadox Medicals Inc | Stent catheter and method for making such a stent catheter |
DE4419792C1 (en) * | 1994-06-06 | 1996-02-01 | Alfons Prof Dr Med Hofstetter | Endoscope for surgical operations |
US5683451A (en) * | 1994-06-08 | 1997-11-04 | Cardiovascular Concepts, Inc. | Apparatus and methods for deployment release of intraluminal prostheses |
US5824041A (en) * | 1994-06-08 | 1998-10-20 | Medtronic, Inc. | Apparatus and methods for placement and repositioning of intraluminal prostheses |
EP1520557A3 (en) * | 1994-06-08 | 2010-07-21 | Cardiovascular Concepts, Inc. | Apparatus and methods for endoluminal graft placement |
EP1051953A3 (en) * | 1994-06-17 | 2001-02-28 | Terumo Kabushiki Kaisha | Indwelling stent and the method for manufacturing the same |
US5743874A (en) * | 1994-08-29 | 1998-04-28 | Fischell; Robert E. | Integrated catheter for balloon angioplasty and stent delivery |
US6331188B1 (en) | 1994-08-31 | 2001-12-18 | Gore Enterprise Holdings, Inc. | Exterior supported self-expanding stent-graft |
US6015429A (en) | 1994-09-08 | 2000-01-18 | Gore Enterprise Holdings, Inc. | Procedures for introducing stents and stent-grafts |
WO1996013228A1 (en) * | 1994-10-27 | 1996-05-09 | Schneider (Usa) Inc. | Stent delivery device |
US5662675A (en) * | 1995-02-24 | 1997-09-02 | Intervascular, Inc. | Delivery catheter assembly |
DE29507519U1 (en) * | 1995-05-05 | 1995-08-10 | Angiomed Ag | Endosphincter and set for releasable closing of the urethra |
US5639274A (en) * | 1995-06-02 | 1997-06-17 | Fischell; Robert E. | Integrated catheter system for balloon angioplasty and stent delivery |
US5700269A (en) * | 1995-06-06 | 1997-12-23 | Corvita Corporation | Endoluminal prosthesis deployment device for use with prostheses of variable length and having retraction ability |
US20110077672A1 (en) * | 1995-06-07 | 2011-03-31 | Fleischman Sidney D | Devices For Installing Stasis Reducing Means In Body Tissue |
US6132438A (en) | 1995-06-07 | 2000-10-17 | Ep Technologies, Inc. | Devices for installing stasis reducing means in body tissue |
US5702418A (en) * | 1995-09-12 | 1997-12-30 | Boston Scientific Corporation | Stent delivery system |
CA2231471C (en) * | 1995-09-18 | 2003-07-08 | W.L. Gore & Associates, Inc. | A delivery system for intraluminal vascular grafts |
ATE177928T1 (en) * | 1995-11-14 | 1999-04-15 | Schneider Europ Gmbh | DEVICE FOR STENT IMPLANTATION |
US6042605A (en) | 1995-12-14 | 2000-03-28 | Gore Enterprose Holdings, Inc. | Kink resistant stent-graft |
EP0950385A3 (en) | 1995-12-14 | 1999-10-27 | Prograft Medical, Inc. | Stent-graft deployment apparatus and method |
FR2748197A1 (en) * | 1996-05-02 | 1997-11-07 | Braun Celsa Sa | Surgical implant positioning device |
US5669932A (en) * | 1996-05-29 | 1997-09-23 | Isostent, Inc. | Means for accurately positioning an expandable stent |
US5772669A (en) | 1996-09-27 | 1998-06-30 | Scimed Life Systems, Inc. | Stent deployment catheter with retractable sheath |
US5843090A (en) * | 1996-11-05 | 1998-12-01 | Schneider (Usa) Inc. | Stent delivery device |
US6395017B1 (en) * | 1996-11-15 | 2002-05-28 | C. R. Bard, Inc. | Endoprosthesis delivery catheter with sequential stage control |
US6551350B1 (en) | 1996-12-23 | 2003-04-22 | Gore Enterprise Holdings, Inc. | Kink resistant bifurcated prosthesis |
US6352561B1 (en) | 1996-12-23 | 2002-03-05 | W. L. Gore & Associates | Implant deployment apparatus |
US5925061A (en) | 1997-01-13 | 1999-07-20 | Gore Enterprise Holdings, Inc. | Low profile vascular stent |
US5957974A (en) * | 1997-01-23 | 1999-09-28 | Schneider (Usa) Inc | Stent graft with braided polymeric sleeve |
US6254633B1 (en) | 1997-02-12 | 2001-07-03 | Corvita Corporation | Delivery device for a medical device having a constricted region |
US6090128A (en) * | 1997-02-20 | 2000-07-18 | Endologix, Inc. | Bifurcated vascular graft deployment device |
US6951572B1 (en) | 1997-02-20 | 2005-10-04 | Endologix, Inc. | Bifurcated vascular graft and method and apparatus for deploying same |
US6425915B1 (en) * | 1997-03-18 | 2002-07-30 | Endotex Interventional Systems, Inc. | Helical mesh endoprosthesis and methods of use |
US6059812A (en) | 1997-03-21 | 2000-05-09 | Schneider (Usa) Inc. | Self-expanding medical device for centering radioactive treatment sources in body vessels |
US5792144A (en) * | 1997-03-31 | 1998-08-11 | Cathco, Inc. | Stent delivery catheter system |
US6165166A (en) | 1997-04-25 | 2000-12-26 | Schneider (Usa) Inc. | Trilayer, extruded medical tubing and medical devices incorporating such tubing |
CA2235911C (en) | 1997-05-27 | 2003-07-29 | Schneider (Usa) Inc. | Stent and stent-graft for treating branched vessels |
US5906641A (en) * | 1997-05-27 | 1999-05-25 | Schneider (Usa) Inc | Bifurcated stent graft |
EP1477134A3 (en) | 1997-05-27 | 2007-05-16 | Schneider (Usa) Inc. | Stent and stent-graft for treating branched vessels |
ATE265247T1 (en) * | 1997-06-10 | 2004-05-15 | Schneider Europ Gmbh | CATHETER SYSTEM |
US6045498A (en) * | 1997-06-12 | 2000-04-04 | Uromedica, Inc. | Method for adjustably restricting a body lumen |
ATE286687T1 (en) * | 1997-07-17 | 2005-01-15 | Schneider Europ Gmbh | STENT AND PRODUCTION METHOD THEREOF |
US6340367B1 (en) | 1997-08-01 | 2002-01-22 | Boston Scientific Scimed, Inc. | Radiopaque markers and methods of using the same |
US6245103B1 (en) | 1997-08-01 | 2001-06-12 | Schneider (Usa) Inc | Bioabsorbable self-expanding stent |
US5980564A (en) * | 1997-08-01 | 1999-11-09 | Schneider (Usa) Inc. | Bioabsorbable implantable endoprosthesis with reservoir |
US6174330B1 (en) | 1997-08-01 | 2001-01-16 | Schneider (Usa) Inc | Bioabsorbable marker having radiopaque constituents |
US6070589A (en) | 1997-08-01 | 2000-06-06 | Teramed, Inc. | Methods for deploying bypass graft stents |
US6340356B1 (en) | 1997-09-23 | 2002-01-22 | NAVIA JOSé ANTONIO | Intraluminal catheter with expandable tubular open-walled element |
US6626939B1 (en) * | 1997-12-18 | 2003-09-30 | Boston Scientific Scimed, Inc. | Stent-graft with bioabsorbable structural support |
US6296633B1 (en) | 1998-01-09 | 2001-10-02 | Schneider (Usa) Inc. | Medical device tubing assembly and method of making the same |
US6149996A (en) * | 1998-01-15 | 2000-11-21 | Schneider (Usa) Inc. | Molded tip and tubing and method of making same |
US6077296A (en) * | 1998-03-04 | 2000-06-20 | Endologix, Inc. | Endoluminal vascular prosthesis |
DE59812219D1 (en) * | 1998-03-04 | 2004-12-09 | Schneider Europ Gmbh Buelach | Device for inserting an endoprosthesis into a catheter shaft |
US7500988B1 (en) | 2000-11-16 | 2009-03-10 | Cordis Corporation | Stent for use in a stent graft |
US6290731B1 (en) | 1998-03-30 | 2001-09-18 | Cordis Corporation | Aortic graft having a precursor gasket for repairing an abdominal aortic aneurysm |
US6520983B1 (en) | 1998-03-31 | 2003-02-18 | Scimed Life Systems, Inc. | Stent delivery system |
US6264689B1 (en) | 1998-03-31 | 2001-07-24 | Scimed Life Systems, Incorporated | Low profile medical stent |
US6146389A (en) | 1998-04-23 | 2000-11-14 | Boston Scientific Corporation | Stent deployment device and method for deploying a stent |
WO1999062428A1 (en) * | 1998-06-04 | 1999-12-09 | Scimed Life Systems, Inc. | Stent loading tool |
WO1999065419A1 (en) | 1998-06-19 | 1999-12-23 | Endologix, Inc. | Self expanding bifurcated endovascular prosthesis |
US6325824B2 (en) | 1998-07-22 | 2001-12-04 | Advanced Cardiovascular Systems, Inc. | Crush resistant stent |
NL1009738C2 (en) * | 1998-07-24 | 2000-01-25 | Cordis Europ | Balloon catheter with filler for stent delivery. |
US7004962B2 (en) | 1998-07-27 | 2006-02-28 | Schneider (Usa), Inc. | Neuroaneurysm occlusion and delivery device and method of using same |
US6120522A (en) * | 1998-08-27 | 2000-09-19 | Scimed Life Systems, Inc. | Self-expanding stent delivery catheter |
EP1447057A1 (en) * | 1998-09-30 | 2004-08-18 | Bard Peripheral Vascular, Inc. | Delivery mechanism for implantable stent |
US20020007145A1 (en) * | 1998-10-23 | 2002-01-17 | Timothy Stivland | Catheter having improved bonding region |
US6214036B1 (en) | 1998-11-09 | 2001-04-10 | Cordis Corporation | Stent which is easily recaptured and repositioned within the body |
US6660030B2 (en) * | 1998-12-11 | 2003-12-09 | Endologix, Inc. | Bifurcation graft deployment catheter |
ATE303107T1 (en) | 1998-12-11 | 2005-09-15 | Endologix Inc | ENDOLUMINAL VASCULAR PROSTHESIS |
US6733523B2 (en) * | 1998-12-11 | 2004-05-11 | Endologix, Inc. | Implantable vascular graft |
US6187036B1 (en) | 1998-12-11 | 2001-02-13 | Endologix, Inc. | Endoluminal vascular prosthesis |
US7018401B1 (en) | 1999-02-01 | 2006-03-28 | Board Of Regents, The University Of Texas System | Woven intravascular devices and methods for making the same and apparatus for delivery of the same |
US6261316B1 (en) | 1999-03-11 | 2001-07-17 | Endologix, Inc. | Single puncture bifurcation graft deployment system |
US8034100B2 (en) * | 1999-03-11 | 2011-10-11 | Endologix, Inc. | Graft deployment system |
US6899730B1 (en) * | 1999-04-15 | 2005-05-31 | Scimed Life Systems, Inc. | Catheter-stent device |
EP1173110B1 (en) * | 1999-04-15 | 2009-07-08 | Smart Therapeutics, Inc. | Intravascular stent for treating neurovascular vessel lesion |
US6375676B1 (en) * | 1999-05-17 | 2002-04-23 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent with enhanced delivery precision and stent delivery system |
JP4299973B2 (en) * | 1999-05-20 | 2009-07-22 | ボストン サイエンティフィック リミテッド | Stent delivery system with a shrink stabilizer |
US6858034B1 (en) | 1999-05-20 | 2005-02-22 | Scimed Life Systems, Inc. | Stent delivery system for prevention of kinking, and method of loading and using same |
US6221078B1 (en) * | 1999-06-25 | 2001-04-24 | Stephen S. Bylsma | Surgical implantation apparatus |
US6402779B1 (en) | 1999-07-26 | 2002-06-11 | Endomed, Inc. | Balloon-assisted intraluminal stent graft |
KR100341019B1 (en) * | 1999-08-18 | 2002-06-20 | 신경민 | The flexible self- expandable stent foundation device |
US6183493B1 (en) | 1999-08-24 | 2001-02-06 | Pharmasys International, Llc | Method and apparatus for the treatment of sleep apnea and related breathing disorders |
US6183481B1 (en) * | 1999-09-22 | 2001-02-06 | Endomed Inc. | Delivery system for self-expanding stents and grafts |
US6270525B1 (en) | 1999-09-23 | 2001-08-07 | Cordis Corporation | Precursor stent gasket for receiving bilateral grafts having controlled contralateral guidewire access |
US7758624B2 (en) | 2000-11-13 | 2010-07-20 | C. R. Bard, Inc. | Implant delivery device |
US6443979B1 (en) | 1999-12-20 | 2002-09-03 | Advanced Cardiovascular Systems, Inc. | Expandable stent delivery sheath and method of use |
US6280465B1 (en) | 1999-12-30 | 2001-08-28 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for delivering a self-expanding stent on a guide wire |
US6322586B1 (en) | 2000-01-10 | 2001-11-27 | Scimed Life Systems, Inc. | Catheter tip designs and method of manufacture |
US6808534B1 (en) | 2000-02-16 | 2004-10-26 | Endovascular Technologies, Inc. | Collapsible jacket guard |
US7722663B1 (en) | 2000-04-24 | 2010-05-25 | Scimed Life Systems, Inc. | Anatomically correct endoluminal prostheses |
US6743219B1 (en) | 2000-08-02 | 2004-06-01 | Cordis Corporation | Delivery apparatus for a self-expanding stent |
US20020016597A1 (en) * | 2000-08-02 | 2002-02-07 | Dwyer Clifford J. | Delivery apparatus for a self-expanding stent |
EP1745761A1 (en) | 2000-08-23 | 2007-01-24 | LeMaitre Acquisition LLC | Method of manufacturing custom intravascular devices |
US6945989B1 (en) * | 2000-09-18 | 2005-09-20 | Endotex Interventional Systems, Inc. | Apparatus for delivering endoluminal prostheses and methods of making and using them |
US6589273B1 (en) * | 2000-10-02 | 2003-07-08 | Impra, Inc. | Apparatus and method for relining a blood vessel |
US6786918B1 (en) * | 2000-10-17 | 2004-09-07 | Medtronic Vascular, Inc. | Stent delivery system |
US7727253B2 (en) * | 2000-11-03 | 2010-06-01 | Cook Incorporated | Medical grasping device having embolic protection |
US7713275B2 (en) * | 2000-11-03 | 2010-05-11 | Cook Incorporated | Medical grasping device |
US7753917B2 (en) * | 2000-11-03 | 2010-07-13 | Cook Incorporated | Medical grasping device |
EP1330194B1 (en) * | 2000-11-03 | 2006-10-18 | Cook Incorporated | Medical grasping device |
WO2002039888A2 (en) * | 2000-11-15 | 2002-05-23 | Endologix, Inc. | Implantable vascular graft |
US7314483B2 (en) * | 2000-11-16 | 2008-01-01 | Cordis Corp. | Stent graft with branch leg |
US20020095203A1 (en) * | 2001-01-18 | 2002-07-18 | Intra Therapeutics, Inc. | Catheter system with spacer member |
US6699274B2 (en) | 2001-01-22 | 2004-03-02 | Scimed Life Systems, Inc. | Stent delivery system and method of manufacturing same |
US6623518B2 (en) | 2001-02-26 | 2003-09-23 | Ev3 Peripheral, Inc. | Implant delivery system with interlock |
US6592549B2 (en) | 2001-03-14 | 2003-07-15 | Scimed Life Systems, Inc. | Rapid exchange stent delivery system and associated components |
KR100457630B1 (en) * | 2001-04-04 | 2004-11-18 | (주) 태웅메디칼 | Flexible self-expandable stent and methods for making the stent for lumen |
US7011675B2 (en) * | 2001-04-30 | 2006-03-14 | Boston Scientific Scimed, Inc. | Endoscopic stent delivery system and method |
US8075606B2 (en) * | 2001-07-06 | 2011-12-13 | Angiomed Gmbh & Co. Medizintechnik Kg | Delivery system having a rapid pusher assembly for self-expanding stent, and stent exchange configuration |
GB0121980D0 (en) | 2001-09-11 | 2001-10-31 | Cathnet Science Holding As | Expandable stent |
US20030050648A1 (en) | 2001-09-11 | 2003-03-13 | Spiration, Inc. | Removable lung reduction devices, systems, and methods |
GB0123633D0 (en) * | 2001-10-02 | 2001-11-21 | Angiomed Ag | Stent delivery system |
US7572287B2 (en) * | 2001-10-25 | 2009-08-11 | Boston Scientific Scimed, Inc. | Balloon expandable polymer stent with reduced elastic recoil |
US6592594B2 (en) | 2001-10-25 | 2003-07-15 | Spiration, Inc. | Bronchial obstruction device deployment system and method |
US20030135266A1 (en) | 2001-12-03 | 2003-07-17 | Xtent, Inc. | Apparatus and methods for delivery of multiple distributed stents |
US7351255B2 (en) | 2001-12-03 | 2008-04-01 | Xtent, Inc. | Stent delivery apparatus and method |
US7309350B2 (en) | 2001-12-03 | 2007-12-18 | Xtent, Inc. | Apparatus and methods for deployment of vascular prostheses |
US7137993B2 (en) * | 2001-12-03 | 2006-11-21 | Xtent, Inc. | Apparatus and methods for delivery of multiple distributed stents |
US7182779B2 (en) | 2001-12-03 | 2007-02-27 | Xtent, Inc. | Apparatus and methods for positioning prostheses for deployment from a catheter |
US7892273B2 (en) | 2001-12-03 | 2011-02-22 | Xtent, Inc. | Custom length stent apparatus |
US7294146B2 (en) | 2001-12-03 | 2007-11-13 | Xtent, Inc. | Apparatus and methods for delivery of variable length stents |
US20040186551A1 (en) | 2003-01-17 | 2004-09-23 | Xtent, Inc. | Multiple independent nested stent structures and methods for their preparation and deployment |
US8080048B2 (en) | 2001-12-03 | 2011-12-20 | Xtent, Inc. | Stent delivery for bifurcated vessels |
US7147656B2 (en) | 2001-12-03 | 2006-12-12 | Xtent, Inc. | Apparatus and methods for delivery of braided prostheses |
US8308797B2 (en) | 2002-01-04 | 2012-11-13 | Colibri Heart Valve, LLC | Percutaneously implantable replacement heart valve device and method of making same |
US7326237B2 (en) * | 2002-01-08 | 2008-02-05 | Cordis Corporation | Supra-renal anchoring prosthesis |
US20040068314A1 (en) * | 2002-01-16 | 2004-04-08 | Jones Donald K. | Detachable self -expanding aneurysm cover device |
US6929637B2 (en) | 2002-02-21 | 2005-08-16 | Spiration, Inc. | Device and method for intra-bronchial provision of a therapeutic agent |
US7169170B2 (en) | 2002-02-22 | 2007-01-30 | Cordis Corporation | Self-expanding stent delivery system |
US6989024B2 (en) * | 2002-02-28 | 2006-01-24 | Counter Clockwise, Inc. | Guidewire loaded stent for delivery through a catheter |
US6866679B2 (en) | 2002-03-12 | 2005-03-15 | Ev3 Inc. | Everting stent and stent delivery system |
US20030181922A1 (en) * | 2002-03-20 | 2003-09-25 | Spiration, Inc. | Removable anchored lung volume reduction devices and methods |
US20030212412A1 (en) * | 2002-05-09 | 2003-11-13 | Spiration, Inc. | Intra-bronchial obstructing device that permits mucus transport |
US20040006380A1 (en) * | 2002-07-05 | 2004-01-08 | Buck Jerrick C. | Stent delivery system |
US20060129227A1 (en) * | 2002-08-02 | 2006-06-15 | Auxetica Limited | Auxetic tubular liners |
US6814746B2 (en) * | 2002-11-01 | 2004-11-09 | Ev3 Peripheral, Inc. | Implant delivery system with marker interlock |
US7965719B2 (en) * | 2002-12-11 | 2011-06-21 | Broadcom Corporation | Media exchange network supporting multiple broadband network and service provider infrastructures |
CA2513082C (en) * | 2003-01-15 | 2010-11-02 | Angiomed Gmbh & Co. Medizintechnik Kg | Trans-luminal surgical device |
GB0327306D0 (en) * | 2003-11-24 | 2003-12-24 | Angiomed Gmbh & Co | Catheter device |
JP2006518625A (en) * | 2003-02-14 | 2006-08-17 | サルヴィアック・リミテッド | Stent delivery and placement system |
US7771463B2 (en) * | 2003-03-26 | 2010-08-10 | Ton Dai T | Twist-down implant delivery technologies |
US20050209672A1 (en) * | 2004-03-02 | 2005-09-22 | Cardiomind, Inc. | Sliding restraint stent delivery systems |
ES2346059T3 (en) | 2003-03-26 | 2010-10-08 | Biosensors International Group Ltd. | IMPLANT SUPPLY CATHETER WITH ELECTROLYTICALLY EROSIONABLE JOINTS. |
US8016869B2 (en) * | 2003-03-26 | 2011-09-13 | Biosensors International Group, Ltd. | Guidewire-less stent delivery methods |
US7527632B2 (en) * | 2003-03-31 | 2009-05-05 | Cordis Corporation | Modified delivery device for coated medical devices |
US7100616B2 (en) * | 2003-04-08 | 2006-09-05 | Spiration, Inc. | Bronchoscopic lung volume reduction method |
US20040267348A1 (en) | 2003-04-11 | 2004-12-30 | Gunderson Richard C. | Medical device delivery systems |
US7473271B2 (en) * | 2003-04-11 | 2009-01-06 | Boston Scientific Scimed, Inc. | Stent delivery system with securement and deployment accuracy |
GB0309616D0 (en) | 2003-04-28 | 2003-06-04 | Angiomed Gmbh & Co | Loading and delivery of self-expanding stents |
ES2364555T3 (en) | 2003-05-23 | 2011-09-06 | Boston Scientific Limited | CANNULAS WITH INCORPORATED LOOP TERMINATIONS. |
US7241308B2 (en) | 2003-06-09 | 2007-07-10 | Xtent, Inc. | Stent deployment systems and methods |
US20040260377A1 (en) * | 2003-06-17 | 2004-12-23 | Medinol, Ltd. | Shape memory alloy endoprosthesis delivery system |
US7470282B2 (en) * | 2003-06-30 | 2008-12-30 | Boston Scientific Scimed, Inc. | Stent grip and system for use therewith |
US8206320B2 (en) * | 2003-07-31 | 2012-06-26 | Cook Medical Technologies Llc | System and method for introducing multiple medical devices |
US7533671B2 (en) | 2003-08-08 | 2009-05-19 | Spiration, Inc. | Bronchoscopic repair of air leaks in a lung |
EP1670390B1 (en) * | 2003-09-02 | 2008-12-24 | Abbott Laboratories | Delivery system for a medical device |
US7780716B2 (en) * | 2003-09-02 | 2010-08-24 | Abbott Laboratories | Delivery system for a medical device |
US7794489B2 (en) * | 2003-09-02 | 2010-09-14 | Abbott Laboratories | Delivery system for a medical device |
US7651519B2 (en) * | 2003-09-16 | 2010-01-26 | Cook Incorporated | Prosthesis deployment system |
US7867268B2 (en) * | 2003-09-24 | 2011-01-11 | Boston Scientific Scimed, Inc. | Stent delivery system for self-expanding stent |
GB0322511D0 (en) | 2003-09-25 | 2003-10-29 | Angiomed Ag | Lining for bodily lumen |
US20050125050A1 (en) * | 2003-12-04 | 2005-06-09 | Wilson Cook Medical Incorporated | Biliary stent introducer system |
US7162030B2 (en) | 2003-12-23 | 2007-01-09 | Nokia Corporation | Communication device with rotating housing |
US7887574B2 (en) * | 2003-12-23 | 2011-02-15 | Scimed Life Systems, Inc. | Stent delivery catheter |
US7326236B2 (en) | 2003-12-23 | 2008-02-05 | Xtent, Inc. | Devices and methods for controlling and indicating the length of an interventional element |
US7468070B2 (en) * | 2004-01-23 | 2008-12-23 | Boston Scientific Scimed, Inc. | Stent delivery catheter |
US7651521B2 (en) * | 2004-03-02 | 2010-01-26 | Cardiomind, Inc. | Corewire actuated delivery system with fixed distal stent-carrying extension |
US7323006B2 (en) | 2004-03-30 | 2008-01-29 | Xtent, Inc. | Rapid exchange interventional devices and methods |
EP1732470B1 (en) * | 2004-03-31 | 2010-05-26 | Wilson-Cook Medical Inc. | Stent introducer system |
WO2010120926A1 (en) | 2004-05-25 | 2010-10-21 | Chestnut Medical Technologies, Inc. | Vascular stenting for aneurysms |
US8628564B2 (en) | 2004-05-25 | 2014-01-14 | Covidien Lp | Methods and apparatus for luminal stenting |
JP2008502378A (en) | 2004-05-25 | 2008-01-31 | チェストナット メディカル テクノロジーズ インコーポレイテッド | Flexible vascular closure device |
US8267985B2 (en) | 2005-05-25 | 2012-09-18 | Tyco Healthcare Group Lp | System and method for delivering and deploying an occluding device within a vessel |
US20060206200A1 (en) | 2004-05-25 | 2006-09-14 | Chestnut Medical Technologies, Inc. | Flexible vascular occluding device |
US8617234B2 (en) | 2004-05-25 | 2013-12-31 | Covidien Lp | Flexible vascular occluding device |
US7846171B2 (en) | 2004-05-27 | 2010-12-07 | C.R. Bard, Inc. | Method and apparatus for delivering a prosthetic fabric into a patient |
US8317859B2 (en) | 2004-06-28 | 2012-11-27 | J.W. Medical Systems Ltd. | Devices and methods for controlling expandable prostheses during deployment |
US20050288766A1 (en) | 2004-06-28 | 2005-12-29 | Xtent, Inc. | Devices and methods for controlling expandable prostheses during deployment |
US7303580B2 (en) * | 2004-07-26 | 2007-12-04 | Cook Incorporated | Stent delivery system allowing controlled release of a stent |
US20060085057A1 (en) * | 2004-10-14 | 2006-04-20 | Cardiomind | Delivery guide member based stent anti-jumping technologies |
US8337543B2 (en) * | 2004-11-05 | 2012-12-25 | Boston Scientific Scimed, Inc. | Prosthesis anchoring and deploying device |
US20060206187A1 (en) * | 2005-03-09 | 2006-09-14 | Cook Incorporated | Stent delivery system |
US20070118207A1 (en) * | 2005-05-04 | 2007-05-24 | Aga Medical Corporation | System for controlled delivery of stents and grafts |
US20060253184A1 (en) * | 2005-05-04 | 2006-11-09 | Kurt Amplatz | System for the controlled delivery of stents and grafts |
US8652193B2 (en) | 2005-05-09 | 2014-02-18 | Angiomed Gmbh & Co. Medizintechnik Kg | Implant delivery device |
US9480589B2 (en) * | 2005-05-13 | 2016-11-01 | Boston Scientific Scimed, Inc. | Endoprosthesis delivery system |
US8273101B2 (en) | 2005-05-25 | 2012-09-25 | Tyco Healthcare Group Lp | System and method for delivering and deploying an occluding device within a vessel |
AU2005332044B2 (en) | 2005-05-25 | 2012-01-19 | Covidien Lp | System and method for delivering and deploying and occluding device within a vessel |
US8157851B2 (en) | 2005-06-08 | 2012-04-17 | Xtent, Inc. | Apparatus and methods for deployment of multiple custom-length prostheses |
US20070073379A1 (en) * | 2005-09-29 | 2007-03-29 | Chang Jean C | Stent delivery system |
US20070027522A1 (en) * | 2005-06-14 | 2007-02-01 | Chang Jean C | Stent delivery and guidewire systems |
WO2007005799A1 (en) * | 2005-06-30 | 2007-01-11 | Abbott Laboratories | Delivery system for a medical device |
US8118852B2 (en) * | 2005-07-13 | 2012-02-21 | Cook Medical Technologies Llc | Introducer for self-expandable medical device |
US20070043420A1 (en) * | 2005-08-17 | 2007-02-22 | Medtronic Vascular, Inc. | Apparatus and method for stent-graft release using a cap |
US20070100414A1 (en) * | 2005-11-02 | 2007-05-03 | Cardiomind, Inc. | Indirect-release electrolytic implant delivery systems |
US20070213813A1 (en) | 2005-12-22 | 2007-09-13 | Symetis Sa | Stent-valves for valve replacement and associated methods and systems for surgery |
US11026822B2 (en) | 2006-01-13 | 2021-06-08 | C. R. Bard, Inc. | Stent delivery system |
CA2936205C (en) | 2006-01-13 | 2018-08-21 | C.R. Bard, Inc. | Stent delivery system |
WO2007095031A2 (en) * | 2006-02-13 | 2007-08-23 | Bay Street Medical, Inc. | System for delivering a stent |
WO2007100556A1 (en) | 2006-02-22 | 2007-09-07 | Ev3 Inc. | Embolic protection systems having radiopaque filter mesh |
US20070219618A1 (en) * | 2006-03-17 | 2007-09-20 | Cully Edward H | Endoprosthesis having multiple helically wound flexible framework elements |
JP2009530060A (en) | 2006-03-20 | 2009-08-27 | エックステント・インコーポレーテッド | Apparatus and method for deploying connected prosthetic segments |
US7699884B2 (en) * | 2006-03-22 | 2010-04-20 | Cardiomind, Inc. | Method of stenting with minimal diameter guided delivery systems |
US7691151B2 (en) | 2006-03-31 | 2010-04-06 | Spiration, Inc. | Articulable Anchor |
US20070281117A1 (en) * | 2006-06-02 | 2007-12-06 | Xtent, Inc. | Use of plasma in formation of biodegradable stent coating |
US20070288183A1 (en) * | 2006-06-07 | 2007-12-13 | Cherik Bulkes | Analog signal transition detector |
US20070288077A1 (en) * | 2006-06-07 | 2007-12-13 | Cherik Bulkes | Self-anchoring electrical lead with multiple electrodes |
US20070288076A1 (en) * | 2006-06-07 | 2007-12-13 | Cherik Bulkes | Biological tissue stimulator with flexible electrode carrier |
GB0615658D0 (en) | 2006-08-07 | 2006-09-13 | Angiomed Ag | Hand-held actuator device |
US20080071343A1 (en) * | 2006-09-15 | 2008-03-20 | Kevin John Mayberry | Multi-segmented graft deployment system |
JP2010504820A (en) * | 2006-09-28 | 2010-02-18 | クック・インコーポレイテッド | Apparatus and method for repairing a thoracic aortic aneurysm |
MX2009004292A (en) | 2006-10-22 | 2009-08-12 | Idev Technologies Inc | Devices and methods for stent advancement. |
EP3329882B1 (en) | 2006-10-22 | 2023-09-20 | IDEV Technologies, INC. | Methods for securing strand ends and the resulting devices |
JP5319546B2 (en) * | 2006-12-15 | 2013-10-16 | カーディオマインド, インコーポレイテッド | Stent system |
US8523931B2 (en) * | 2007-01-12 | 2013-09-03 | Endologix, Inc. | Dual concentric guidewire and methods of bifurcated graft deployment |
CA2676787A1 (en) * | 2007-02-05 | 2008-08-14 | Boston Scientific Limited | System with catheter system and an adaptor comprising a friction reducing sleeve, and methods of use |
US7815601B2 (en) | 2007-02-05 | 2010-10-19 | Boston Scientific Scimed, Inc. | Rapid exchange enteral stent delivery system |
US20080199510A1 (en) | 2007-02-20 | 2008-08-21 | Xtent, Inc. | Thermo-mechanically controlled implants and methods of use |
US20080255654A1 (en) * | 2007-03-22 | 2008-10-16 | Bay Street Medical | System for delivering a stent |
US8486132B2 (en) | 2007-03-22 | 2013-07-16 | J.W. Medical Systems Ltd. | Devices and methods for controlling expandable prostheses during deployment |
US20080300667A1 (en) * | 2007-05-31 | 2008-12-04 | Bay Street Medical | System for delivering a stent |
US8366628B2 (en) * | 2007-06-07 | 2013-02-05 | Kenergy, Inc. | Signal sensing in an implanted apparatus with an internal reference |
GB0713497D0 (en) | 2007-07-11 | 2007-08-22 | Angiomed Ag | Device for catheter sheath retraction |
US9144508B2 (en) * | 2007-07-19 | 2015-09-29 | Back Bay Medical Inc. | Radially expandable stent |
US9393137B2 (en) * | 2007-09-24 | 2016-07-19 | Boston Scientific Scimed, Inc. | Method for loading a stent into a delivery system |
US8043301B2 (en) * | 2007-10-12 | 2011-10-25 | Spiration, Inc. | Valve loader method, system, and apparatus |
EP2194933B1 (en) | 2007-10-12 | 2016-05-04 | Spiration, Inc. | Valve loader method, system, and apparatus |
US8114144B2 (en) * | 2007-10-17 | 2012-02-14 | Abbott Cardiovascular Systems Inc. | Rapid-exchange retractable sheath self-expanding delivery system with incompressible inner member and flexible distal assembly |
US20090105806A1 (en) * | 2007-10-23 | 2009-04-23 | Endologix, Inc | Stent |
WO2009065087A1 (en) | 2007-11-14 | 2009-05-22 | Biosensors International Group, Ltd. | Automated coating apparatus and method |
EP2240121B1 (en) | 2008-01-16 | 2019-05-22 | St. Jude Medical, Inc. | Delivery and retrieval systems for collapsible/expandable prosthetic heart valves |
US8114116B2 (en) * | 2008-01-18 | 2012-02-14 | Cook Medical Technologies Llc | Introduction catheter set for a self-expandable implant |
US8758421B2 (en) * | 2008-01-30 | 2014-06-24 | Boston Scientific Scimed, Inc. | Medical systems and related methods |
US8221494B2 (en) | 2008-02-22 | 2012-07-17 | Endologix, Inc. | Apparatus and method of placement of a graft or graft system |
US9101503B2 (en) | 2008-03-06 | 2015-08-11 | J.W. Medical Systems Ltd. | Apparatus having variable strut length and methods of use |
US8313525B2 (en) * | 2008-03-18 | 2012-11-20 | Medtronic Ventor Technologies, Ltd. | Valve suturing and implantation procedures |
US8236040B2 (en) | 2008-04-11 | 2012-08-07 | Endologix, Inc. | Bifurcated graft deployment systems and methods |
EP2633823B1 (en) | 2008-04-21 | 2016-06-01 | Covidien LP | Braid-ball embolic devices and delivery systems |
US9675482B2 (en) * | 2008-05-13 | 2017-06-13 | Covidien Lp | Braid implant delivery systems |
US9750625B2 (en) * | 2008-06-11 | 2017-09-05 | C.R. Bard, Inc. | Catheter delivery device |
GB0810749D0 (en) | 2008-06-11 | 2008-07-16 | Angiomed Ag | Catherter delivery device |
US20090318892A1 (en) * | 2008-06-20 | 2009-12-24 | Maria Aboytes | Removable Core Implant Delivery Catheter |
EP2293838B1 (en) | 2008-07-01 | 2012-08-08 | Endologix, Inc. | Catheter system |
CA2731735A1 (en) * | 2008-07-22 | 2010-01-28 | Microtherapeutics, Inc. | Vascular remodeling device |
US8678008B2 (en) * | 2008-07-30 | 2014-03-25 | Ethicon, Inc | Methods and devices for forming an auxiliary airway for treating obstructive sleep apnea |
US8556797B2 (en) * | 2008-07-31 | 2013-10-15 | Ethicon, Inc. | Magnetic implants for treating obstructive sleep apnea and methods therefor |
US8413661B2 (en) | 2008-08-14 | 2013-04-09 | Ethicon, Inc. | Methods and devices for treatment of obstructive sleep apnea |
US8408212B2 (en) * | 2008-08-18 | 2013-04-02 | Glenveigh Medical, Llc | Cervical occluder |
US8216498B2 (en) | 2008-09-10 | 2012-07-10 | Boston Scientific Scimed, Inc. | Catheter having a coextruded fluoropolymer layer |
GB0816965D0 (en) * | 2008-09-16 | 2008-10-22 | Angiomed Ag | Stent device adhesively bonded to a stent device pusher |
US8597454B2 (en) | 2008-09-23 | 2013-12-03 | Cook Medical Technologies Llc | Catheter tip assembly |
US8769796B2 (en) | 2008-09-25 | 2014-07-08 | Advanced Bifurcation Systems, Inc. | Selective stent crimping |
US8821562B2 (en) | 2008-09-25 | 2014-09-02 | Advanced Bifurcation Systems, Inc. | Partially crimped stent |
CN102215780B (en) | 2008-09-25 | 2015-10-14 | 高级分支系统股份有限公司 | Part crimped stent |
US11298252B2 (en) | 2008-09-25 | 2022-04-12 | Advanced Bifurcation Systems Inc. | Stent alignment during treatment of a bifurcation |
US8795347B2 (en) | 2008-09-25 | 2014-08-05 | Advanced Bifurcation Systems, Inc. | Methods and systems for treating a bifurcation with provisional side branch stenting |
US8561616B2 (en) * | 2008-10-24 | 2013-10-22 | Ethicon, Inc. | Methods and devices for the indirect displacement of the hyoid bone for treating obstructive sleep apnea |
US8561617B2 (en) * | 2008-10-30 | 2013-10-22 | Ethicon, Inc. | Implant systems and methods for treating obstructive sleep apnea |
US8800567B2 (en) | 2008-12-01 | 2014-08-12 | Ethicon, Inc. | Implant systems and methods for treating obstructive sleep apnea |
US8783258B2 (en) | 2008-12-01 | 2014-07-22 | Ethicon, Inc. | Implant systems and methods for treating obstructive sleep apnea |
FR2939637B1 (en) * | 2008-12-17 | 2012-01-13 | Newco | DEVICE FOR DELIVERING STENT AND METHOD FOR MANUFACTURING THE SAME |
GB0901496D0 (en) | 2009-01-29 | 2009-03-11 | Angiomed Ag | Delivery device for delivering a stent device |
US8371308B2 (en) | 2009-02-17 | 2013-02-12 | Ethicon, Inc. | Magnetic implants and methods for treating an oropharyngeal condition |
WO2010127040A1 (en) | 2009-04-28 | 2010-11-04 | Endologix, Inc. | Apparatus and method of placement of a graft or graft system |
US10772717B2 (en) | 2009-05-01 | 2020-09-15 | Endologix, Inc. | Percutaneous method and device to treat dissections |
JP2012525239A (en) | 2009-05-01 | 2012-10-22 | エンドロジックス、インク | Transcutaneous methods and devices for treating dissociation (priority information and incorporation by reference) |
GB0909319D0 (en) | 2009-05-29 | 2009-07-15 | Angiomed Ag | Transluminal delivery system |
US8657870B2 (en) * | 2009-06-26 | 2014-02-25 | Biosensors International Group, Ltd. | Implant delivery apparatus and methods with electrolytic release |
US8491646B2 (en) | 2009-07-15 | 2013-07-23 | Endologix, Inc. | Stent graft |
WO2011017123A2 (en) | 2009-07-27 | 2011-02-10 | Endologix, Inc. | Stent graft |
WO2011034010A1 (en) * | 2009-09-16 | 2011-03-24 | テルモ株式会社 | Stent delivery system |
US8771335B2 (en) * | 2009-09-21 | 2014-07-08 | Boston Scientific Scimed, Inc. | Rapid exchange stent delivery system |
US9877862B2 (en) * | 2009-10-29 | 2018-01-30 | Ethicon, Inc. | Tongue suspension system with hyoid-extender for treating obstructive sleep apnea |
US9326886B2 (en) | 2009-10-29 | 2016-05-03 | Ethicon, Inc. | Fluid filled implants for treating obstructive sleep apnea |
US9974683B2 (en) * | 2009-10-30 | 2018-05-22 | Ethicon, Inc. | Flexible implants having internal volume shifting capabilities for treating obstructive sleep apnea |
US20110202085A1 (en) | 2009-11-09 | 2011-08-18 | Siddharth Loganathan | Braid Ball Embolic Device Features |
US8632488B2 (en) * | 2009-12-15 | 2014-01-21 | Ethicon, Inc. | Fluid filled implants for treating medical conditions |
EP2528541B1 (en) * | 2010-01-28 | 2016-05-18 | Covidien LP | Vascular remodeling device |
US9468442B2 (en) * | 2010-01-28 | 2016-10-18 | Covidien Lp | Vascular remodeling device |
CN102933161A (en) * | 2010-02-08 | 2013-02-13 | 萨帕斯医药有限公司 | Method and device for treating cerebrovascular pathologies and delivery system therefor |
US20110218617A1 (en) * | 2010-03-02 | 2011-09-08 | Endologix, Inc. | Endoluminal vascular prosthesis |
CA2794080A1 (en) | 2010-03-24 | 2011-09-29 | Advanced Bifurcation Systems, Inc. | System and methods for treating a bifurcation |
WO2011119883A1 (en) | 2010-03-24 | 2011-09-29 | Advanced Bifurcation Systems, Inc. | Stent alignment during treatment of a bifurcation |
US9023095B2 (en) | 2010-05-27 | 2015-05-05 | Idev Technologies, Inc. | Stent delivery system with pusher assembly |
AU2011276503B2 (en) | 2010-06-28 | 2015-09-17 | Colibri Heart Value LLC | Method and apparatus for the endoluminal delivery of intravascular devices |
US9039759B2 (en) | 2010-08-24 | 2015-05-26 | St. Jude Medical, Cardiology Division, Inc. | Repositioning of prosthetic heart valve and deployment |
WO2012039753A2 (en) | 2010-09-20 | 2012-03-29 | St. Jude Medical, Cardiology Division, Inc. | Valve leaflet attachment in collapsible prosthetic valves |
GB201017834D0 (en) | 2010-10-21 | 2010-12-01 | Angiomed Ag | System to deliver a bodily implant |
JP6261339B2 (en) | 2010-11-02 | 2018-01-17 | エンドロジックス、インク | Apparatus and method for placement of a graft or graft system |
EP2450010B1 (en) | 2010-11-09 | 2013-11-20 | Biotronik AG | Balloon catheter, in particular for delivering drugs or stents in the region of a stenosis |
US8756789B2 (en) * | 2010-11-16 | 2014-06-24 | W. L. Gore & Associates, Inc. | Method of manufacturing a catheter assembly |
WO2012068298A1 (en) | 2010-11-17 | 2012-05-24 | Endologix, Inc. | Devices and methods to treat vascular dissections |
SG10201601962WA (en) | 2010-12-14 | 2016-04-28 | Colibri Heart Valve Llc | Percutaneously deliverable heart valve including folded membrane cusps with integral leaflets |
US9717593B2 (en) | 2011-02-01 | 2017-08-01 | St. Jude Medical, Cardiology Division, Inc. | Leaflet suturing to commissure points for prosthetic heart valve |
WO2012109382A2 (en) | 2011-02-08 | 2012-08-16 | Advanced Bifurcation Systems, Inc. | Multi-stent and multi-balloon apparatus for treating bifurcations and methods of use |
EP2672932B1 (en) | 2011-02-08 | 2018-09-19 | Advanced Bifurcation Systems, Inc. | System for treating a bifurcation with a fully crimped stent |
CN103442653B (en) | 2011-02-11 | 2016-06-01 | 柯惠有限合伙公司 | Two benches launches aneurysma embolization device |
WO2012118901A1 (en) | 2011-03-01 | 2012-09-07 | Endologix, Inc. | Catheter system and methods of using same |
WO2012132508A1 (en) * | 2011-03-25 | 2012-10-04 | テルモ株式会社 | Stent delivery system |
WO2012134990A1 (en) | 2011-03-25 | 2012-10-04 | Tyco Healthcare Group Lp | Vascular remodeling device |
US8795241B2 (en) | 2011-05-13 | 2014-08-05 | Spiration, Inc. | Deployment catheter |
US9101507B2 (en) | 2011-05-18 | 2015-08-11 | Ralph F. Caselnova | Apparatus and method for proximal-to-distal endoluminal stent deployment |
US10849771B2 (en) | 2011-06-27 | 2020-12-01 | Boston Scientific Scimed, Inc. | Stent delivery systems and methods for making and using stent delivery systems |
US9119716B2 (en) | 2011-07-27 | 2015-09-01 | Edwards Lifesciences Corporation | Delivery systems for prosthetic heart valve |
US8905033B2 (en) | 2011-09-28 | 2014-12-09 | Ethicon, Inc. | Modular tissue securement systems |
WO2013049448A1 (en) | 2011-09-29 | 2013-04-04 | Covidien Lp | Vascular remodeling device |
US9161855B2 (en) | 2011-10-24 | 2015-10-20 | Ethicon, Inc. | Tissue supporting device and method |
US8973582B2 (en) | 2011-11-30 | 2015-03-10 | Ethicon, Inc. | Tongue suspension device and method |
US10470760B2 (en) | 2011-12-08 | 2019-11-12 | Ethicon, Inc. | Modified tissue securement fibers |
US9072624B2 (en) | 2012-02-23 | 2015-07-07 | Covidien Lp | Luminal stenting |
US20130226278A1 (en) * | 2012-02-23 | 2013-08-29 | Tyco Healthcare Group Lp | Methods and apparatus for luminal stenting |
WO2013128016A1 (en) | 2012-03-01 | 2013-09-06 | Medical Device Works Nv | Kit and devices for organ perfusion |
US9078659B2 (en) | 2012-04-23 | 2015-07-14 | Covidien Lp | Delivery system with hooks for resheathability |
US9173766B2 (en) | 2012-06-01 | 2015-11-03 | Ethicon, Inc. | Systems and methods to treat upper pharyngeal airway of obstructive sleep apnea patients |
US9155647B2 (en) | 2012-07-18 | 2015-10-13 | Covidien Lp | Methods and apparatus for luminal stenting |
US9724222B2 (en) | 2012-07-20 | 2017-08-08 | Covidien Lp | Resheathable stent delivery system |
US9114001B2 (en) | 2012-10-30 | 2015-08-25 | Covidien Lp | Systems for attaining a predetermined porosity of a vascular device |
US9452070B2 (en) | 2012-10-31 | 2016-09-27 | Covidien Lp | Methods and systems for increasing a density of a region of a vascular device |
US9314248B2 (en) | 2012-11-06 | 2016-04-19 | Covidien Lp | Multi-pivot thrombectomy device |
US9943427B2 (en) | 2012-11-06 | 2018-04-17 | Covidien Lp | Shaped occluding devices and methods of using the same |
US9295571B2 (en) | 2013-01-17 | 2016-03-29 | Covidien Lp | Methods and apparatus for luminal stenting |
US9157174B2 (en) | 2013-02-05 | 2015-10-13 | Covidien Lp | Vascular device for aneurysm treatment and providing blood flow into a perforator vessel |
US9463105B2 (en) | 2013-03-14 | 2016-10-11 | Covidien Lp | Methods and apparatus for luminal stenting |
US9855160B2 (en) | 2013-03-14 | 2018-01-02 | W. L. Gore & Associates, Inc. | Endoprosthesis delivery systems with deployment aids |
CN108433769B (en) | 2013-03-15 | 2021-06-08 | 柯惠有限合伙公司 | Occlusion device |
US10130500B2 (en) | 2013-07-25 | 2018-11-20 | Covidien Lp | Methods and apparatus for luminal stenting |
US9474639B2 (en) | 2013-08-27 | 2016-10-25 | Covidien Lp | Delivery of medical devices |
US9782186B2 (en) | 2013-08-27 | 2017-10-10 | Covidien Lp | Vascular intervention system |
CN103431926B (en) * | 2013-09-04 | 2015-09-30 | 杭州启明医疗器械有限公司 | For intervention apparatus conveying sheath core and there is the induction system of this sheath core |
EP3043755B1 (en) | 2013-09-12 | 2022-10-19 | St. Jude Medical, Cardiology Division, Inc. | Atraumatic interface in an implant delivery device |
WO2015179140A1 (en) | 2014-05-21 | 2015-11-26 | Boston Scientific Scimed, Inc. | Stent delivery system |
US9855140B2 (en) | 2014-06-10 | 2018-01-02 | St. Jude Medical, Cardiology Division, Inc. | Stent cell bridge for cuff attachment |
WO2016153635A1 (en) | 2015-03-24 | 2016-09-29 | Spiration, Inc.D/B/A Olympus Respiratory America | Airway stent |
JP2018524025A (en) | 2015-06-30 | 2018-08-30 | エンドロジックス、インク | Lock assembly for coupling guidewire to delivery system |
US10850064B2 (en) | 2015-09-03 | 2020-12-01 | St. Jude Medical, Cardiology Division, Inc. | Introducer sheath having expandable portions |
US10478194B2 (en) | 2015-09-23 | 2019-11-19 | Covidien Lp | Occlusive devices |
US10953204B2 (en) | 2017-01-09 | 2021-03-23 | Boston Scientific Scimed, Inc. | Guidewire with tactile feel |
US10376396B2 (en) | 2017-01-19 | 2019-08-13 | Covidien Lp | Coupling units for medical device delivery systems |
US10842624B2 (en) | 2017-03-10 | 2020-11-24 | St. Jude Medical, Cardiology Division, Inc. | Transseptal mitral valve delivery system |
US10660752B2 (en) | 2017-03-16 | 2020-05-26 | St. Jude Medical, Cardiology Division, Inc. | Retainers for transcatheter heart valve delivery systems |
WO2018204736A1 (en) | 2017-05-05 | 2018-11-08 | St. Jude Medical, Cardiology Division, Inc. | Introducer sheath having expandable portions |
WO2019051476A1 (en) | 2017-09-11 | 2019-03-14 | Incubar, LLC | Conduit vascular implant sealing device for reducing endoleak |
US11006939B2 (en) | 2017-12-08 | 2021-05-18 | Tendyne Holdings, Inc. | Introducer sheath with seal and methods of using the same |
US10898326B2 (en) | 2018-02-20 | 2021-01-26 | St. Jude Medical, Cardiology Division, Inc. | Crimping heart valve with nitinol braid |
US11413176B2 (en) | 2018-04-12 | 2022-08-16 | Covidien Lp | Medical device delivery |
US10786377B2 (en) | 2018-04-12 | 2020-09-29 | Covidien Lp | Medical device delivery |
US11123209B2 (en) | 2018-04-12 | 2021-09-21 | Covidien Lp | Medical device delivery |
US11071637B2 (en) | 2018-04-12 | 2021-07-27 | Covidien Lp | Medical device delivery |
US10441449B1 (en) | 2018-05-30 | 2019-10-15 | Vesper Medical, Inc. | Rotary handle stent delivery system and method |
US10449073B1 (en) | 2018-09-18 | 2019-10-22 | Vesper Medical, Inc. | Rotary handle stent delivery system and method |
EP3902597B1 (en) | 2018-12-28 | 2023-06-28 | St. Jude Medical, Cardiology Division, Inc. | Operating handle for selective deflection or rotation of a catheter |
US11413174B2 (en) | 2019-06-26 | 2022-08-16 | Covidien Lp | Core assembly for medical device delivery systems |
US11219541B2 (en) | 2020-05-21 | 2022-01-11 | Vesper Medical, Inc. | Wheel lock for thumbwheel actuated device |
US20220265448A1 (en) * | 2021-02-22 | 2022-08-25 | Stryker Corporation | Implant delivery devices and methods of making the same |
US11944558B2 (en) | 2021-08-05 | 2024-04-02 | Covidien Lp | Medical device delivery devices, systems, and methods |
Family Cites Families (14)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4572186A (en) * | 1983-12-07 | 1986-02-25 | Cordis Corporation | Vessel dilation |
US4580568A (en) * | 1984-10-01 | 1986-04-08 | Cook, Incorporated | Percutaneous endovascular stent and method for insertion thereof |
ES8705239A1 (en) * | 1984-12-05 | 1987-05-01 | Medinvent Sa | A device for implantation and a method of implantation in a vessel using such device. |
US4681110A (en) * | 1985-12-02 | 1987-07-21 | Wiktor Dominik M | Catheter arrangement having a blood vessel liner, and method of using it |
US4665918A (en) * | 1986-01-06 | 1987-05-19 | Garza Gilbert A | Prosthesis system and method |
EP0257091B1 (en) * | 1986-02-24 | 1993-07-28 | Robert E. Fischell | An intravascular stent and percutaneous insertion system |
SE454482B (en) * | 1986-09-30 | 1988-05-09 | Medinvent Sa | DEVICE FOR IMPLANTATION |
JPS63238872A (en) * | 1987-03-25 | 1988-10-04 | テルモ株式会社 | Instrument for securing inner diameter of cavity of tubular organ and catheter equipped therewith |
DE9010130U1 (en) * | 1989-07-13 | 1990-09-13 | American Medical Systems, Inc., Minnetonka, Minn., Us | |
US5034001A (en) * | 1989-09-08 | 1991-07-23 | Advanced Cardiovascular Systems, Inc. | Method of repairing a damaged blood vessel with an expandable cage catheter |
US5002560A (en) * | 1989-09-08 | 1991-03-26 | Advanced Cardiovascular Systems, Inc. | Expandable cage catheter with a rotatable guide |
US5234457A (en) * | 1991-10-09 | 1993-08-10 | Boston Scientific Corporation | Impregnated stent |
US5201757A (en) * | 1992-04-03 | 1993-04-13 | Schneider (Usa) Inc. | Medial region deployment of radially self-expanding stents |
US5290295A (en) * | 1992-07-15 | 1994-03-01 | Querals & Fine, Inc. | Insertion tool for an intraluminal graft procedure |
-
1992
- 1992-10-31 DE DE59206251T patent/DE59206251D1/en not_active Expired - Lifetime
- 1992-10-31 ES ES92118671T patent/ES2089342T3/en not_active Expired - Lifetime
- 1992-10-31 EP EP92118671A patent/EP0596145B1/en not_active Expired - Lifetime
- 1992-10-31 AT AT92118671T patent/ATE137656T1/en not_active IP Right Cessation
-
1993
- 1993-10-14 US US08/137,676 patent/US5484444A/en not_active Expired - Lifetime
- 1993-10-27 AU AU50320/93A patent/AU669007B2/en not_active Ceased
- 1993-10-29 CA CA2102019A patent/CA2102019C/en not_active Expired - Fee Related
- 1993-10-29 JP JP5272440A patent/JP2828390B2/en not_active Expired - Lifetime
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6302893B1 (en) | 1996-07-15 | 2001-10-16 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent delivery system |
Also Published As
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AU5032093A (en) | 1994-05-12 |
EP0596145B1 (en) | 1996-05-08 |
DE59206251D1 (en) | 1996-06-13 |
AU669007B2 (en) | 1996-05-23 |
EP0596145A1 (en) | 1994-05-11 |
CA2102019A1 (en) | 1994-05-01 |
US5484444A (en) | 1996-01-16 |
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ATE137656T1 (en) | 1996-05-15 |
JP2828390B2 (en) | 1998-11-25 |
JPH06197985A (en) | 1994-07-19 |
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