the present invention as shown in fig1 a - 1c is a delivery catheter ( 10 ) for delivering a stent device ( 20 ) percutaneously to a vessel lumen . the use of this invention can be for delivering a stent device ( 20 ) following angioplasty or during the angioplasty procedure . the stent device ( 20 ) can be a drug eluting stent such as a balloon expandable stent or a self - expanding stent or it can be a stent graft or covered stent . one of the more advantageous applications for the delivery catheter ( 10 ) of the present invention is for the closure of a large arteriotomy site such as one made in the femoral artery for delivery of a large catheter such as a tavi device or an aaa device . since the standard introducer sheath used in these procedures are approximately the same size as the vessel diameter , i . e ., 16 - 21 french , the normal vascular closure devices and methods do not work well . the present delivery catheter ( 10 ) is intended to gain access in the same femoral artery or other artery that is typically entered for the tavi procedure only at a new access site that is just a small distance distal to the tavi access site . since the present invention has a very small profile , providing this new second access site does not create a significant drawback and provides a definite device and method for sealing the large tavi access opening easily , quickly , and consistently which currently is a source of vascular complications using existing sealing devices and methods . an embodiment of the delivery catheter ( 10 ) is shown in fig1 a - 2b . a balloon tube or shaft ( 30 ) with a balloon inflation lumen ( 40 ) extends from the balloon manifold ( 50 ) through the delivery catheter ( 10 ) to the balloon ( 60 ). the distal end of the balloon ( 60 ) is closed by thermal methods , adhesive , solvent , bonding a plastic filler or other method . the balloon ( 60 ) can be formed from polyethylene terephthalate , polyethylene , or any material commonly used for making an angioplasty balloon . it is anticipated but not required that the same tubing that is use to form the balloon ( 60 ) can be used for the balloon tube or shaft ( 30 ). on the outside of the balloon ( 60 ) is mounted a stent device ( 20 ); the stent device ( 20 ) can be a stent ( 80 ) or a covered stent ( 90 ). in the preferred embodiment for providing a vascular closure device the stent device ( 20 ) can be a self - expanding stent that has a covering ( 100 ); alternately the stent ( 80 ) can be either balloon expandable or self - expanding and it does not require a covering ( 100 ). the distal end of the balloon ( 60 ) is bonded to a conical dilator or cone ( 110 ) that is formed from a hard plastic , or metal , or other nondeformable material that is generally lubricious and can serve as a dilator . materials for the cone ( 110 ) include polyethylene , delrin , fluorinated polymers , and other plastics , composites , or metals . at the distal end of the cone ( 110 ) is an attachment feature or attachment element ( 120 ). the attachment element ( 120 ) can be a stud that has a locking feature , a plastic or metal stud that has a lock snap that springs shut on a receiving element ( 130 ), a threaded stud ( 140 ) ( as shown in fig1 a ) that can be used to form a threaded joint ( 150 ) as shown in fig1 b , a metal stud that can receive a mating cylinder that can be swaged upon to form a swage joint ( 160 ) as shown in fig1 c , or an indented receptacle that has a non - slip material on its surface , a threaded receptacle ( 180 ), or other locking receptacle . another element of the invention is a guidewire ( 170 ) having a receiving element ( 130 ) that is able to be attached to the attachment element ( 120 ) at the distal end of the cone ( 110 ). the receiving element ( 130 ) of the guidewire ( 170 ) can be a stud , a threaded joint ( 150 ), a threaded receptacle ( 180 ) as shown in fig1 a and 1b and can be used to form a threaded joint ( 150 ) as shown in fig1 b , a snapping feature that mates with the attachment element ( 120 ) of the cone ( 110 ) or other mating member that allows the guidewire ( 170 ) to be readily but securely joined to the cone ( 110 ) of the delivery catheter ( 10 ). providing the guidewire ( 170 ) as a separate but connectable element allows the guidewire ( 170 ) to be advanced into the vessel through an initial needle puncture and allows removal of the needle ; this obviates the need for a separate dilator and introducer sheath . the guidewire ( 170 ) can range in diameter from 0 . 014 - 0 . 038 inch diameter and can have a length ranging from 3 cm to 40 cm . once the guidewire ( 170 ) is attached to the cone ( 110 ), the delivery catheter ( 10 ), which includes the guidewire ( 170 ), can then be advanced together to the site of interest in the vessel . the delivery catheter ( 10 ) of the invention has a movable external sheath or case ( 190 ) that extends over the stent device ( 20 ) and holds the stent device ( 20 ) down onto the balloon ( 60 ). the case ( 190 ) comes into contact with the cone ( 110 ) to form a smooth surface such that the combination of the cone ( 110 ) and the case ( 190 ) act in a manner similar to a standard dilator and introducer sheath . thus with the guidewire ( 170 ) attached to the cone ( 110 ), the delivery catheter ( 10 ) can be advanced through an arteriotomy site by holding onto the case ( 190 ) and advancing the delivery catheter ( 10 ) distally . when the case ( 190 ) is retracted in a proximal direction toward the balloon manifold ( 50 ) as shown in fig1 b , the stent device ( 20 ) is exposed to the vessel wall . in the case of a self - expanding stent device ( 20 ), the stent device ( 20 ) can be deployed immediately upon retraction of the case ( 190 ). the stent device ( 20 ) can then be post dilated by inflating the balloon ( 60 ) as shown in fig1 c to ensure definite contact of the stent device ( 20 ) and the vessel wall . the present invention provides that a self - expanding stent device ( 20 ) can remain attached to the balloon ( 60 ) even after retraction of the case ( 190 ) as shown in fig1 b ; this feature will be described further in fig2 a - 2d . in the femoral artery and many regions of the leg and the carotid arteries of the neck , a self - expanding stent device ( 20 ) is preferred to reduce the chances for crush deformation of the stent device ( 20 ) due to external forces applied to the stent device ( 20 ) through the skin or from muscle groups . for the case where external crush is not a significant detriment , such as for coronary stenting , a balloon expandable stent device ( 20 ) can be used ; the balloon expandable stent device ( 20 ) is mounted onto the balloon ( 60 ) and is deployed upon inflation of the balloon ( 60 ). the case ( 190 ) can be used for the balloon expandable stent ( 80 ) or stent device ( 20 ) but is not required if a standard introduce sheath is used to provide entry for the stent device ( 20 ) mounted on a standard balloon dilation catheter such as used in the medical device industry . the stent device ( 20 ) of the present invention can include any stent ( 80 ) or covered stent ( 90 ) that is currently found in the industry . the stent ( 80 ), for example , can be formed of zigzag rings or a zigzag spiral , or it can be formed from any open or close cell patterns used in stent design , some of which are shown in fig2 a - 2d . the stent struts ( 200 ) can have overlapped struts ( 210 ) to help gain a lower profile as shown in fig2 c . the connectors ( 220 ) or links of various patterns can connect individual ringlets ( 225 ) to provide a stent device ( 20 ) with multiple connected ringlets . ringlets ( 225 ) can overlap neighboring ringlets ( 225 ) as described in the cross - referenced patent application . the self - expanding stent ( 80 ) can be formed from nitinol , elgiloy , or other elastic metals , composites , biodegradable materials , or elastomeric plastics . the balloon expandable stent ( 80 ) can be formed from stainless steel , cobalt - chrome , or other materials commonly used for stents including biodegradable materials . biodegradable polymeric materials or biodegradable metals can be used for the stent ( 80 ) or stent device ( 20 ) construction ; such materials include polyglycolic acid , polylactic acid , polyethylene glycol , tissue or collagen materials , magnesium , or other biodegradable materials used in the medical device industry . the stent device ( 20 ) can have a thin covering ( 100 ) placed on the inside surface ( 230 ), outside surface ( 240 ) or both . one embodiment as shown in fig2 b has an eptfe cover with a thickness of approximately 0 . 0005 inches placed on both the outside and inside surface ( 230 ) s of the stent struts ( 200 ) and bonded together around the stent struts ( 200 ) to hold it in place . the eptfe covering ( 100 ) or other fibrous covering ( 100 ) such as polypropylene , polyurethane , or other fibrous or porous polymeric structure is porous to allow cellular penetration to enhance tissue healing but not allow significant bleeding to occur through the cover . alternately , a tissue covering ( 100 ) such as a porcine pericardium or other biodegradable material can be used , including collagen , fibrin , or other tissue materials . the pore size for a polymeric covering should range between 2 - 30 microns , but this pore size is dependent upon the wall thickness . the coverering ( 100 ) can extend along the entire surface of the stent ( 80 ) or it can cover only a portion of the stent ( 80 ) leaving the strut end ( 250 ) uncovered by the eptfe or other cover material . allowing the strut end ( 250 ) to remain uncovered allows the stent device ( 20 ) to be attached to the balloon ( 60 ) as shown in fig3 a - 3d . the stent ringlets ( 225 ) can be located , for example , at each end of the covering ( 100 ) leaving the central portion of the covering ( 100 ) without support from a stent ( 80 ), thereby having the flexibility that is desired and having the ability to be punctured again at a later time for vascular access . the balloon ( 60 ) of the present invention is shown in a nondeployed configuration in fig3 a and 3b . the balloon ( 60 ) can be wrapped around a portion of the stent strut ( 200 ) such as a strut end ( 250 ) to form a wrap attachment ( 260 ) as shown in fig3 a - 3d . this wrapping feature is not required by the present invention but provides a potential benefit for holding the self - expanding stent device ( 20 ) in position with respect to the balloon ( 60 ) such that the stent device ( 20 ) cannot embolize or become displaced in the vessel . in fig3 a a portion of the balloon ( 60 ) is wrapped around a stent strut . as the balloon ( 60 ) wraps around the strut , it can form a balloon bond ( 270 ) to another portion of the balloon ( 60 ) and form a wrap attachment ( 260 ). when the balloon ( 60 ) becomes partially inflated as shown in fig3 c and 3d , the stent device ( 20 ) is still attached to the balloon ( 60 ). further inflation of the balloon ( 60 ) as shown in fig3 e and 3f causes the stent device ( 20 ) to become released from the balloon ( 60 ) as the balloon wrap attachments ( 260 ) are forced to let go of the strut ends ( 250 ). for the case where the stent device ( 20 ) is a covered stent ( 90 ), the strut ends ( 250 ) are held by the wrap attachments ( 260 ) and are released as shown in fig3 f . a small amount of thrombin , blood coagulant , or clotting agent ( 280 ) can be placed on the outside of the covering ( 100 ) or between the layers of the cover as shown in fig3 f if desired to assist in forming a clot when the stent device ( 20 ) is a covered stent ( 90 ) use to provide vascular closure . the method of use of the delivery catheter ( 10 ) for vascular closure is shown in fig4 a - 4f . the method for delivery of a stent ( 80 ) or covered stent ( 90 ) to the vasculature for a different purpose is identical to this except that the site of delivery for the stent device ( 20 ) may not be for the closure of a large diameter arteriotomy site from a large catheter . access is made with a needle to the femoral artery at a site approximately 1 - 10 cm ( preferably 1 - 3 cm ) distal to a large introducer sheath , is , being used for passage of a large diameter interventional catheter such as a tavi or aaa catheter . the small diameter access site , sas , for the delivery catheter ( 10 ) of the present invention could be greater than 3 cm from the large introducer for the large interventional catheter without deviating from the present invention . a guidewire ( 170 ) of the present invention having a receiving element ( 130 ) at its proximal end is advanced through the needle and past the site of the large diameter introducer sheath , is , as shown in fig4 a . the needle is removed and the receiving element ( 130 ) of the guidewire ( 170 ) is firmly attached to the attachment element ( 120 ) at the distal end of the cone ( 110 ) of the delivery catheter ( 10 ). this attachment can be via screwing , swaging , via a snap fit , a one - way joint , or other joint . the cone ( 110 ) acts as a dilator to enter the arteriotomy and the case ( 190 ) acts as an introducer to hold the arteriotomy site outwards . the delivery catheter ( 10 ) is advanced along with the guidewire ( 170 ) into the vessel until the cone ( 110 ) comes into contact with the large diameter introducer . the large diameter introducer sheath , is , can then be removed and the delivery catheter ( 10 ) is advanced a small prescribed distance if necessary to place the stent device ( 20 ) adjacent to the arteriotomy site as shown in fig4 c . the case ( 190 ) is then retracted in a proximal direction as shown in fig4 d thereby exposing the stent device ( 20 ) to the vessel , v , and the balloon ( 60 ) is inflated to press the self - expanding stent device ( 20 ) up against the vessel wall thereby covering the arteriotomy site as shown in fig4 e . the covering ( 100 ) on the stent device ( 20 ) covers the opening causing the blood leakage out of the arteriotomy site to cease . a small amount of thrombin or other clotting agent placed on the surface of the covering ( 100 ) or between layers of the eptfe covering ( 100 ) can help to ensure that the blood clots quickly and leakage is maintained at a minimum . the balloon ( 60 ) is deflated and the delivery catheter ( 10 ) is then removed as shown in fig4 f . in an alternate embodiment , a guidewire tube ( 290 ) with a separate guidewire lumen ( 300 ) can be placed through the balloon tube ( 30 ), the balloon ( 60 ), and through the cone ( 110 ) as shown in fig5 a . this device allows a standard guidewire ( 310 ) to be placed into the vessel , v , using a standard seldinger approach . a guidewire ( 170 ) could range from 0 . 010 to − 0 . 038 inches but it would be preferred to use the smaller diameter guidewire ( 170 ) to minimize the profile of the delivery catheter ( 10 ). after the standard guidewire ( 310 ) is in place across the arteriotomy site , as , the delivery catheter ( 10 ) can be advanced over the standard guidewire ( 310 ) with cone ( 110 ) dilating the small diameter arteriotomy site , sas , and the case ( 190 ) holding the small arteriotomy site , sas , outwards . the delivery catheter ( 10 ) is advanced until the cone ( 110 ) comes into contact with the large diameter introducer sheath that is being used for passage of a large therapeutic device such as the tavi or aaa catheters as shown in fig5 b . the large diameter introducer is removed and the delivery catheter ( 10 ) is positioned adjacent to the large diameter arteriotomy site , as , and the stent device ( 20 ) is delivered in a manner that is similar to that described for the previous embodiment . the present invention does not require that a balloon ( 60 ) ( as shown in fig1 a ) be used to deliver a self - expanding stent device ( 20 ). as seen in fig6 a self - expanding stent device ( 20 ) can be positioned toward the distal end of a catheter shaft ( 320 ) having a cone ( 110 ) positioned at its distal end . the stent device ( 20 ) is contained by an external sheath or case ( 190 ) that can be withdrawn to release the stent device ( 20 ). a pusher tube ( 330 ) located on the catheter shaft ( 320 ) can be used to hold the stent device ( 20 ) in place along the catheter shaft ( 320 ) while the case ( 190 ) is being withdrawn . a control fiber ( 340 ) can form a loop ( 350 ) around one of the struts ( 200 ) of the stent ( 80 ) of the stent device ( 20 ) to hold the stent device ( 20 ) from embolizing or moving out of position within the blood vessel after it has been released . a secondary step could be implemented after the stent device ( 20 ) has been released and the catheter shaft ( 320 ) has been removed from the vessel . a standard balloon dilatation catheter can be introduced into the external sheath or case ( 190 ) to provide a post dilatation to the self - expanding stent device ( 20 ) to ensure that it is in full apposition with the vessel wall . in another embodiment a stent ( 80 ) or stent device ( 20 ) can have a stent structure with a hinge ( 360 ) and strut ( 200 ) geometry as described in the cross referenced us patents and us patent application indicated earlier in this application . a balloon expandable hinge ( 360 ) and strut ( 200 ) structure is shown in fig7 a and 7b . the hinge ( 360 ) is the portion of the stent ( 80 ) that undergoes deformation as the stent ( 80 ) is expanded from nondeployed state to a deployed expanded diameter state . the hinge ( 360 ) has a short hinge length ( 380 ) that undergoes all of the deformation as the hinge ( 360 ) is bent along the hinge length ( 380 ) during expansion deformation . the hinge length ( 380 ) for the balloon expandable stent is very short ranging from 1 - 3 times a hinge width . the hinge length ( 380 ) should be shorter than the hinge width to provide the maximum focus for hinge ( 360 ) deformation during the expansion deformation . the hinge length ( 380 ) is also smaller than the hinge radial dimension ( 400 ). the hinge radial dimension ( 400 ) extends in the radial direction of the stent ( 80 ) and is larger than the strut radial dimension ( 410 ) such that the hinge ( 360 ) will not bend if the stent ( 80 ) of the stent device ( 20 ) is placed into an oval cross section or crush deformation due to exposure to an external force or due to exposure imposed by neighboring muscle groups of the body . the strut radial dimension ( 410 ) is smaller than the hinge radial dimension ( 400 ) such that the strut ( 200 ) will flex easily to allow the stent ( 80 ) to form an oval shape during a crush deformation and will return elastically to its normal shape to provide the stent ( 80 ) with a round shape when the crush deformation force has been removed . the strut width ( 420 ) is larger than the hinge width such that during the expansion deformation , the strut ( 200 ) does not bend and instead forces all of the expansion deformation to occur at the hinges ( 360 ). in fig7 a the hinge ( 360 ) is connected to two struts ( 200 ) via two transition regions ( 430 ). the transition regions ( 430 ) do not flex in either the expansion deformation or a crush deformation . the transition region radial dimension for this embodiment tapers from the strut radial dimension ( 410 ) to the hinge radial dimension ( 400 ). the cross sectional area ( defined by the radial direction and width direction ) of the transition region ( 430 ) is larger than that of the strut ( 200 ) or the hinge ( 360 ). the embodiment of fig7 b has two hinges ( 360 ) each of which connect to a strut ( 200 ) via a transition region ( 430 ). each hinge ( 360 ) of this embodiment connect to the other hinge ( 360 ) via a node ( 440 ) that does not bend during the expansion deformation and does not bend in the radial direction during a crush deformation . the other reference numerals used in fig7 b represent similar components as found in fig7 a . the use of a balloon expandable stent device ( 20 ) of the present embodiment either with or without a covering ( 100 ) allows the stent device ( 20 ) to be crimped onto the balloon ( 60 ) of the present invention as described in fig1 a - 1c . upon removal of the external sheath or case ( 190 ), the stent ( 80 ) will remain in position adjacent to the arteriotomy site and held onto the balloon via a crimping mechanism . expansion of the balloon ( 60 ) will place the stent device ( 20 ) into direct apposition with the vessel wall such that the stent ( 80 ) or stent device ( 20 ) will generate hemostasis . if the femoral artery is exposed to external forces , the stent ( 80 ) will bend elastically along the struts ( 200 ) to an oval shape and will return to a round shape . the wall structure for the stent ( 80 ) of the stent device ( 20 ) of this embodiment can be an open structure , closed structure , a zigzag structure ; it can have individual zigzag ringlets ( 225 ), or connectors ( 220 ) that join individual stent ringlets ( 225 ), or a spiral shaped zigzag structure ; the stent ( 80 ) can be formed from a single ringlet ( 225 ) located and attached to each end of the covering ( 100 ), or it can extend throughout most or all of the covered stent device ( 20 ). a self - expanding stent device ( 20 ) of still another embodiment provides a stent ( 80 ) that has a self - expanding hinge structure as shown in fig8 . the difference in this embodiment from that described in fig7 a and 7b is that the hinge length ( 380 ) is longer . the expansion deformation of this embodiment is not focused as it was in the balloon expandable hinge geometry shown in fig7 a and 7b . instead the expansion deformation is spread along a hinge length ( 380 ) that extends from the junction of the hinge ( 360 ) from one transition region ( 430 ) to another transition region ( 430 ) as shown in fig8 . the hinge length ( 380 ) for the self - expanding stent device ( 20 ) is larger than 3 times the hinge width ( 390 ). the hinge length ( 380 ) for materials such as stainless steel or other generally plastically deformable metals is greater than twice the strut width ( 420 ). the long hinge length ( 380 ) allows the hinge ( 360 ) to undergo a deformation during compression for delivery within the external sheath in a smaller diameter state and undergo expansion deformation elastically to an enlarged expanded diameter upon release into the blood vessel . thus the long hinge length ( 380 ) provides the stent device ( 20 ) with its self - expanding character . other reference numerals describe similar components described in fig7 a and 7b . the self - expanding hinge stent ( 80 ) of fig8 can be used in the stent device ( 20 ) of the present invention to provide a stent ( 80 ) that has very soft flex in a crush deformation by forming a strut ( 200 ) with a strut radial dimension ( 410 ) that is relatively small ( i . e ., 0 . 002 - 0 . 003 inches ) in comparison to existing femoral stents , ( i . e ., 0 . 004 - 0 . 005 inches ). the hinge radial dimension ( 400 ) can be relatively larger ( i . e ., 0 . 006 inches ) than existing femoral stent ( 0 . 004 - 0 . 005 inches ) to provide a stronger stent that resists reduction in diameter . the balloon expandable hinge stent ( 80 ) of fig7 a and 7b can be combined with any self - expanding stent including the self - expanding hinge stent ( 80 ) of fig8 to form a stent having both a self - expanding portion ( 450 ) and a balloon expandable portion ( 460 ) as shown in fig9 a and 9b . balloon expandable ringlets ( 225 ) can be placed at each end of the stent device ( 20 ) such that the stent device ( 20 ) is firmly attached to the balloon ( 60 ) as shown in fig9 b ; the central stent portion of the stent device ( 20 ) can be formed from self - expanding ringlets ( 225 ). the ringlets ( 225 ) can be attached directly to the covering ( 100 ) or can be attached to each other via connectors ( 220 ) or via one or more biodegradable fibers ( 480 ). alternately , one or more balloon expandable ringlets ( 225 ) can be place in the central portion of the stent device ( 20 ) and one or more self - expanding ringlets ( 225 ) can be placed at the end portions of the stent device ( 20 ) as shown in fig9 a . the self - expanding ringlets ( 225 ) provide a soft and flexible deformation that is desirable in the femoral artery near the arteriotomy site . in a further embodiment a locator balloon ( 490 ) is placed into the large introducer sheath , is , prior to introduction of the delivery catheter ( 10 ) of the present invention to help position the delivery catheter ( 10 ) as shown in fig1 a - 10d . the locator balloon ( 490 ) is placed into the blood vessel , v , and inflated via a locator balloon inflation port ( 495 ) with an inflation medium that can include saline , air , co2 , contrast medium , or a cross - linkable polymer . the locator balloon ( 490 ) is pulled back to the arteriotomy site , as , along with the large introducer sheath , is . the locator balloon ( 490 ) provides hemostasis to the arteriotomy site and also can be used to occlude or partially occlude the vessel lumen , vl , as shown in fig1 b . as the delivery catheter ( 10 ) is introduced into the vessel lumen , vl , as shown in fig4 a - 4d , the delivery catheter ( 10 ) impinges upon the locator balloon ( 490 ), thereby stopping the delivery catheter ( 10 ) from further advancement past the locator balloon ( 490 ). a tether fiber ( 500 ) of one embodiment is attached to the distal end ( 510 ) of the locator balloon ( 490 ). applying tenstion to the tether fiber ( 500 ) via a tensioning spool ( 515 ) will cause the locator balloon ( 490 ) to form inward folds ( 520 ) and advance inside of the locator balloon shaft ( 525 ) thereby providing a passage for the delivery catheter ( 10 ) at a location adjacent to the arteriotomy site , as , as shown in fig1 c . the locator balloon ( 490 ) still provides hemostasis of blood at the arteriotomy site . the stent device ( 20 ) of the delivery catheter ( 10 ) is then released adjacent to the arteriotomy site , as , and into contact with the locator balloon ( 490 ). the locator balloon ( 490 ) can fully withdrawn into the locator balloon ( 490 ) shaft and out of the arteriotomy site , as , as the balloon ( 60 ) from the delivery catheter ( 10 ) is delivered into apposition with the vessel wall at the arteriotomy site as shown in fig1 d . the locator balloon ( 490 ) can be formed with more than one tether or with a shape that enhances its ability to provide positioning for the delivery catheter ( 10 ) and also to provide hemostasis for the arteriotomy site . the locator balloon ( 490 ) can alternately be partially implanted and serve as a plug for the arteriotomy site as shown in fig1 a and 11b . in fig1 a the locator balloon ( 490 ) has been filled with a cross - linking polymer such as polyurethane , silicone , or a biodegradable material such as polyethylene glycol , or other biodegradable gel or fluid including saline . a balloon valve ( 530 ) is located near the junction of the locator balloon ( 490 ) with the locator balloon ( 490 ) distal shaft such that the inflation fluid can enter but cannot leak out of the locator balloon ( 490 ) and through the locator balloon shaft ( 525 ). a temporary passage ( not shown ) can be provided to allow inflation fluid to leak out of the locator balloon ( 490 ) and through a temporarily placed passage tube that extends through the balloon valve ( 530 ), for example . as the stent device ( 20 ) is dilated via the delivery catheter ( 10 ) to provide apposition of the stent device ( 20 ) with the vessel wall , the inflation fluid within the locator balloon ( 490 ) is forced to push the locator balloon ( 490 ) into forming a seal with the arteriotomy site . the locator balloon proximal shaft ( 550 ) is separated from the locator balloon distal shaft ( 540 ) via a threaded uncoupling or any other uncoupling mechanism that can be used to uncouple two tubings with a common lumen . the balloon valve ( 530 ) remains implanted in the arteriotomy site along with the locator balloon ( 490 ). the stent device ( 20 ) in this embodiment could include the stent ( 80 ) either with or alone without a covering ( 100 ) and depend upon the locator balloon ( 490 ) to provide the seal for the arteriotomy site . the material of construction for the locator balloon ( 490 ) include nylon , pebax , polyethylene terephthalate ( pet ), polyurethane , silicone , or other compliant , semicompliant , or noncompliant materials used for balloon , stent ( 80 ), or implanted medical device manufacture in the medical device industry . the locator balloon ( 490 ) can also be formed from thin - walled eptfe , a thin tissue material , or a flexible biodegradable tissue or film . the tether fiber ( 500 ) can be formed from a thin metal or polymeric fiber and can also be formed from a biodegradable material . the locator balloon distal shaft ( 540 ) can be formed from a polymeric material including a biodegradable materials indicated for the locator balloon ( 490 ). the tether valve can be a standard duck - billed valve formed from a thin polymeric leaflets or tissue leaflets ; the tether valve can also be formed from biodegradable materials indicated for the locator balloon ( 490 ). the dimensions for the locator balloon ( 490 ) as it is being used is further described during the following method steps . the locator balloon ( 490 ) is folded during entry into the large introducer sheath , is , and into the vessel lumen , vl , of the blood vessel , v . the locator balloon ( 490 ) is then inflated via the locator balloon inflation port ( 495 ) with inflation medium to a volume or pressure that causes it to expand to a diameter that is 10 - 50 % larger than the arteriotomy site , as , and the inside diameter of the is ; this diameter can range from 4 - 11 mm ; the locator balloon inflated diameter is approximately 6 - 9 mm for a tavi procedure access site arteriotomy . the locator balloon shaft ( 525 ) is withdrawn proximally until the locator balloon ( 490 ) is in full contact with the arteriotomy site and the is has its distal end adjacent the locator balloon ( 490 ). the locator balloon ( 490 ) is then inflated to a diameter that fills the lumen of the femoral artery , approximately 7 - 10 mm to provide an inflated locator balloon ( 490 ) into which the delivery catheter ( 10 ) will contact when it is inserted . the locator balloon ( 490 ) can have traction applied to the tether fiber ( 500 ) to cause the distal end of the locator balloon ( 490 ) to inwardly fold into the locator balloon shaft ( 525 ) and provide a space in the lumen of the blood vessel , v , for passage of the delivery catheter ( 10 ). the embodiments of the present invention include both self - expanding and balloon expandable stents and covered stents ( 90 ) that form the stent device ( 20 ). the stents ( 80 ) can be formed from single ringlets ( 225 ) located at the end of the covering ( 100 ) or can extend throughout the stent device ( 20 ). the delivery catheter ( 10 ) and stent device ( 20 ) can be used with a balloon dilatation catheter or without , and can be used with or without the locator balloon ( 490 ). each of the embodiments can be interchanged with other aspect of other embodiments and still are included in the present invention .
a low profile stent device consisting of a stent plus an optional covering is placed percutaneously into a blood vessel to provide vascular closure to a nearby large diameter arteriotomy site . a self - expanding stent device is mounted onto a balloon for postdilitation and is held in a small diameter configuration by an outer case . a balloon expandable stent device has hinge and strut features that provide it with crush resistance . the cone and sheath of the deliver catheter serves as a dilator and introducer sheath to assist in delivery . an attachable guidewire reduces profile by eliminating a guidewire lumen . a locator balloon placed through the large diameter arteriotomy introducer sheath assists positioning .