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
  • A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
  • A61F2/9517—Instruments specially adapted for placement or removal of stents or stent-grafts handle assemblies therefor
• • 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
  • A61F2/9522—Means for mounting a stent or stent-graft onto or into a placement instrument
• • 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
• • 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
  • A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
  • A61F2210/0004—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof bioabsorbable
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
  • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
  • A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
  • A61F2250/0067—Means for introducing or releasing pharmaceutical products into the body

Definitions

• the present invention relates to medical appliances. More particularly, the present invention relates to a delivery device for a self-expanding stent, a method of using the delivery system, and a method of producing the system.
• medical devices may be coated with materials to provide beneficial surface properties.
• medical devices are often coated with radiopaque materials to allow for fluoroscopic visualization while placed in the body. It is also useful to coat certain devices to achieve enhanced biocompatibility and to improve surface properties such as lubriciousness.
• a DE SE stent loaded in a delivery catheter may apply a compressive force against an inside surface of the delivery catheter.
• This compressive force may be supported directly by the coating, which may consist of a thin, relatively soft polymer carrier of the bioactive substance.
• the compressive force combined with linear displacement may produce an abrasive, scraping action against the DE coating.
• This friction may also be responsible for increasing the stent deployment force, which may be increased to levels higher than are considered acceptable.
• Deployment systems for protecting DE coatings include a rolling sheath or membrane.
• rolling sheaths or membranes may require quite difficult processes to produce and assemble the rolling membrane into the finished delivery system.
• the membrane may turn inside out on itself and cause a load to be added to the retraction force as the outer portion of the membrane is pulled over the inner portion.
• Stents with controlled expansion are apparently discussed in United States Patent No. 6,613,077 to Gilligan et al., entitled “Stent with Controlled Expansion”.
• An activation mechanism for a catheter is discussed in United States Patent No. 6,391,051 to Sullivan, III et al., entitled "Pull Back Stent Delivery System with Pistol Grip Retraction Handle”.
• the extensions may include longitudinal slits of the inner sheath forming a plurality of inner sleeve tails, the inner sleeve tails extending from a distal end of the outer sheath to a distal end of the inner sheath.
• the longitudinal slits of the inner sheath may be biodegradable and detachable from the medical appliance.
• the medical appliance may further include an actuator adapted to move the outer sheath with respect to the inner sheath during deployment of the self-expanding stent.
• the actuator may be adapted to cause the outer sheath to move proximally.
• the medical appliance may further include the self-expanding stent.
• a rate of expansion of the self-expanding stent may include a delay.
• the self-expanding stent may include a coating including a bioactive agent.
• the medical appliance may be deployed in a lumen of a human body and the coating of the self-expanding stent may release the bioactive agent.
• the expandable pusher may be adapted to expand when the self-expanding stent has expanded; abut the self-expanding stent in an expanded state; and oppose a further proximal shear force during retraction of the plurality of extensions.
• a method of deploying a self-expanding stent includes inserting an outer sheath into a lumen of a body. The outer sheath is coupled to a catheter and encloses an inner sheath and a plurality of extensions. The plurality of extensions is coupled to a distal end of the inner sheath and encloses the self-expanding stent.
• the method also includes activating an activator to move the outer sheath relative to the inner sheath and the plurality of extensions.
• the outer sheath moves proximally and the plurality of extensions allows the self-expanding stent to expand to an edge of the lumen.
• the method may include activating the activator to move the inner sheath relative to a pusher abutting the self-expanding stent.
• the inner sheath and the plurality of extensions may move proximally with respect to the self-expanding stent.
• the method may include retracting the catheter.
• a method of loading a delivery mechanism includes inserting an inner sheath into an outer sheath.
• the inner sheath includes a tube having a plurality of longitudinal slits bounded at least distally by a circumferential ring.
• the outer sheath is coupled to a catheter.
• the catheter includes an activation mechanism adapted to move the outer sheath proximally with respect to an expandable pusher.
• the method also includes detaching each of the longitudinal slits from each other of the longitudinal slits at a distal end of the inner sheath.
• the expandable pusher may be adapted to abut the inner sheath when the outer sheath moves proximally with respect to the expandable pusher.
• the activation mechanism may include a dual action activator, a first activation adapted to move the outer sheath proximally with respect to the expandable pusher, a second activation adapted to move the inner sheath proximally with respect to the expandable pusher.
• the method may include contracting a self-expanding stent and inserting the self- expanding stent into the inner sheath.
• the contracting of the self-expanding stent and the inserting of the self-expanding stent into the inner sheath may be performed before the inserting of the inner sheath in the outer sheath and the detaching of each of the longitudinal slits.
• the inserting of the inner sheath into the outer sheath further may include inserting the self-expanding stent and the inner sheath into the outer sheath.
• the contracting of the self-expanding stent and the inserting of the self-expanding stent into the inner sheath may be performed after the inserting of the inner sheath in the outer sheath and the detaching of each of the longitudinal slits.
• Figure 1 is a schematic cross-sectional representation of an exemplary embodiment of the present invention showing a self-expanding stent loaded in a delivery system that includes a two-piece sheath.
• Figure 4 shows the schematic cross-sectional representation of the exemplary embodiment of the present invention of Figure 3 in the lumen in a fully expanded state after the retraction of the inner sheath.
• Figure 5 is a schematic cross-sectional representation of an alternative exemplary embodiment of the present invention showing a self-expanding stent loaded in a delivery system that includes a two-piece sheath and an alternative pusher design.
• Figure 6 shows the schematic cross-sectional representation of an exemplary embodiment of the present invention of Figure 5 after a partial retraction of the outer sheath and showing the SE stent partially expanded and the inner sheath partially expanded.
• Figure 7 is a schematic cross-sectional representation of an exemplary embodiment showing a catheter delivery mechanism in a loaded state and an activation mechanism with a portion of the catheter cut away.
• Figure 10 shows a zoomed in view of the schematic cross-sectional representation of the exemplary embodiment of Figure 8 showing a section of the expanded pusher spring.
• Figure 12 shows a schematic cross-sectional representation of another exemplary embodiment of the present invention after a partial retraction of the outer sheath showing the SE stent partially expanded and looped wires attached to a proximal inner sheath.
• Figure 14 shows a zoomed in view of a schematic cross-sectional representation of another exemplary embodiment showing the molded tip of the medical appliance and the wires of an inner sheath.
• the polymer base of the DE coating may thus be subjected to a continuous compressive force, which during deployment may cause a scuffing and/or abrasive action at the interface of the coating and the catheter. There may also be an increase in the stent deployment force.
• an inner sheath also referred to herein as an inner sleeve
• the inner sheath may open freely into the body lumen. During deployment, the inner sleeve may then be retracted, followed by the normal withdrawal from the vessel of the delivery system.
• An exemplary embodiment of the present invention may utilize an inner protective sleeve with longitudinal slits.
• the exemplary embodiment of the present invention may utilize this non-rolling protective sleeve, which may be retracted linearly within the outer sheath and after the retraction of the outer sheath.
• the inner, coating protection sleeve may be made from a low friction material and may be cut longitudinally, possibly with between 2 and 6 slits.
• a retraction mechanism may connect the sheath and sleeve and may pull back the outer sheath fully before retracting the inner sleeve.
• the inner sleeve may then be retracted past the deployed, expanded stent, in which position the coating abrasion forces may be reduced.
• an inner sleeve of external diameter 2mm may be cut longitudinally into 4 equally spaced, 90 degree arcs.
• each of the 4 inner sleeve tails may now cover an arc of approximately 18 degrees, and an arc length of 1.6mm.
• An expandable stent pusher may be included in the system to ensure that the stent is deployed with a sufficient degree of linear positional precision.
• the design of a sequential, double sheath (also referred to herein as a sheath/sleeve combination) deployment mechanism may reduce and/or eliminate sheath retraction over a folly loaded, contracted stent.
• the inner DE coating protection sleeve may be a thin- walled (possibly 0.001 inch to 0.0015 inch) cylindrical tube with a diameter provided to give a close sliding fit inside the main catheter delivery sheath. This sleeve may provide a protection wall or barrier for the DE coating.
• the outer sheath may now freely slide off this new inner sleeve. Because the material of the inner sleeve may be selected for low sliding friction properties (for instance, PTFE), the stent deployment force may now be significantly lower than if the outer sheath were retracted over the polymer based DE coating.
• Extruded tubing as in some catheter delivery tubes, may have a dense, homogenous structure with a highly polished surface.
• the spray-deposited polymer coating may have a relatively soft and textured surface, which renders it more liable to scuffing and tearing damage.
• the inner sleeve may function more effectively if it is able to separate and allow the ,5 stent to expand freely into the body lumen as the outer sheath is retracted.
• An exemplary embodiment of the inner sleeve enabling radial opening includes multiple (for instance, between two and six) equally spaced slits, disposed in a longitudinal direction over a distance slightly longer than the stent. Due to a potentially large difference in diameter of the stent between its loaded (contracted) and deployed (expanded) conditions, the 0 individual segments of the folly opened, slit portion of the inner sleeve may occupy a relatively small arc of the total expanded stent circumference. Thus, immediately after the retraction of the outer sheath, these inner sleeve tails may offer little resistance to their own, secondary retraction since most of the radial spring force of the deployed stent may now be supported directly by the vessel wall.
• An exemplary embodiment of the present invention may include an expandable stent pusher.
• the operation of the inner expandable sleeve may require a compatible expandable stent pusher.
• a pusher provides a buttress and shoulder against which the proximal end of the stent is held during the retraction of the outer sheath.
• a significant portion of the sheath retraction force may be generated from the friction force present between the compressed stent and the retracting outer sheath.
• the purpose of the stent pusher is therefore to supply this reaction force against the stent. Also, as the stent is being deployed, for instance by a physician at a particular vessel lesion site, the stent must be held without further movement relative to the vessel wall while the outer sheath is retracted relative to the stent and vessel wall.
• the stent pusher may be expandable.
• the expansion function may ensure that the retraction of the inner sleeve does not permit any migration of the stent in the body lumen.
• there may be a reduced retraction force due to the relative ease with which the several inner sleeve tails may be retracted through the stent- vessel interface.
• the stent may bed down into the lining of the vessel wall.
• an expandable pusher may be provided.
• the pusher when self-expanded to approximately the same size as the deployed stent, may supply the reaction force between the proximal end of the stent and the inner sleeve during the retraction of the inner sleeve.
• a plurality of fine, superelastic Nitinol wire springs may be securely mounted on the catheter inner shaft. When the stent is loaded, these springs may be contracted and loaded to occupy a space inside the inner expandable sheath.
• a rigid molded buttress also referred to herein as a pusher may be secured immediately behind the springs to support the fully opened springs and carry some of the reaction force.
• each of the wire springs may expand so that, as the inner sleeve begins to be retracted, the enlarged pusher may supply the reaction force between the stent and the inner sheath.
• an embolic particle protection filter may be of use in stenting procedures that may give rise to the production of loose particles of plaque from the artery lesion site.
• An exemplary embodiment of an embolic filter may trap particles and be effective when blood flow is towards the proximal end of the catheter. The filter may also remove trapped emboli with the withdrawal of the catheter from the artery during or after the procedure.
• a short portion of the distal end of inner sleeve may be continuous, i.e., not slit, in order to facilitate stent loading.
• the distal ends of the slits may be completed, forming the inner sleeve tails. This final cut may allow the inner sleeve tails to open and pass over the deployed stent.
• Roll-flattening of each inner sheath tail before assembly may assist in promoting the conforming shape change. Additionally, shape-memory components may be utilized to facilitate the adaptation of the inner sleeve tails from covering the contracted SE stent to covering the expanded SE stent.
• FIG. 1 is a schematic cross-sectional representation of an exemplary embodiment of the present invention showing SE stent 12 loaded in delivery system 10.
• Delivery system 10 includes tip 11, outer protective sheath 13, inner protective sheath 16, pusher 14, and pusher springs 15. Pusher 14 and pusher springs 15 may collectively be referred to herein as an expandable pusher.
• Delivery system 10 also includes activator shaft 17 and central shaft 18 positioned on a central axis of delivery system 10. Delivery system 10 is shown with SE stent 12 in a contracted (i.e., loaded) state ready to be inserted into a lumen of a body.
• Slits 21a, 21b, 21c, 21 d expand as SE stent 12 expands. Since outer protective sheath 13 is withdrawn across the surface of tails 20a, 20b, 20c, 20d, which are coated with a lubricious coating (for instance, PTFE), damage to the coating on SE stent 12 is reduced and/or eliminated.
• a lubricious coating for instance, PTFE
• Figure 3 shows the schematic cross-sectional representation of the exemplary embodiment of the present invention of Figure 2 in a lumen bounded by lumen wall 30.
• Figure 3 shows SE stent 12 partially expanded and inner protective sheath 16 partially expanded after a partial retraction of outer protective sheath 13.
• SE stent 12 is adapted to expand to press against lumen wall surface 31.
• SE stent 12 is partially expanded causing tails 2Oa 5 20b, 20c, 2Od of inner protective sheath 16 to press against lumen wall surface 31.
• Figure 4 shows the schematic cross-sectional representation of the exemplary embodiment of the present invention of Figure 3 in the lumen bounded by lumen wall 30 in a 5 fully expanded state after the complete retraction of outer protective sheath 13 and after the retraction of inner protective sheath 16.
• SE stent 12 is fully expanded and inner protective sheath 16 is fully retracted.
• SE stent 12 presses against lumen wall surface 31.
• Pusher spring arms 15a, 15b, 15c, 15d pressed against the edge of SE stent 12 during the retraction of tails 20a, 20b, 20c, 2Od to maintain SE stent 12 in position against lumen wall surface 31.
• Robust pusher 51 may be a longer, cylindrical pusher buttress, and may provide a stable support for robust pusher springs 52.
• the longer design of robust pusher 51 may assist 0 in preventing the collapse and buckling of the ends of pusher springs 52 (distal of robust pusher 51) during retraction of outer sheath 13.
• Robust pusher springs 52 may be more robust than pusher springs 15, or alternatively may be similar to pusher springs 52.
• Figure 6 shows the schematic cross-sectional representation of an exemplary embodiment of the present invention of Figure 5 after a partial retraction of outer protective 5 sheath 13 and showing SE stent 12 partially expanded and inner protective sheath 16 partially expanded.
• Activation of expanded pusher delivery system 50 is accomplished by moving outer protective sheath 13 in a proximal direction relative to a distal motion of activator shaft 17 connected to robust pusher 51.
• SE stent 12 is able to expand, since tails 20a, 20b, 20c, 2Od are
• slits 21a, 21b, 21c, 21d expand as SE stent 12 expands. Since outer protective sheath 13 is withdrawn across the surface of tails 20a, 20b, 20c, 2Od 5 which are coated with a lubricious coating, damage to the coating on SE stent 12 is reduced and/or eliminated.
• Robust pusher springs 52 may provide greater stability to SE stent 12 in maintaining position during the retraction of inner protective sheath 16. The function of a longer, close-fitting pusher buttress may prevent the collapse of the tails at the start of the outer sheath retraction. In the fully assembled system, the inner slits should not extend beyond the proximal end face of the pusher buttress. This may ensure that the light compressive/shear forces transmitted to the sleeve tails do not cause the tails to buckle.
• FIG. 7 is a schematic cross-sectional representation of an exemplary embodiment showing delivery system 10 in a loaded state and activation mechanism 70 with a portion of the catheter cut away by break 79.
• Delivery system 10 includes tip 11, outer protective sheath 13, inner protective sheath 16, and activator shaft 17.
• Activation mechanism 70 includes lever 71 that activates gear 72 to rotate screw 73 a.
• Gear 72 may incorporate a rotary ratchet that allows the screw drive mechanism to advance without a corresponding reverse rotation produced by the return stroke of lever 71.
• Screw 73a is continuous with screw 73b.
• Anchor 75 on screw 73a anchors wire 74 which attaches to outer protective sheath 13.
• Anchor 77 on screw 73b provides a delayed stop for wire 76 by stopping stop 78.
• Wire 76 attaches to inner protective sheath 16.
• Figure 8 shows a zoomed in view of a schematic cross-sectional representation of an exemplary embodiment of the present invention after a partial retraction of outer protective sheath 13 showing SE stent 12 and inner protective sheath 16 expanded before the retraction of inner protective sheath 16.
• Delivery system 10 including tip 11, outer protective sheath 13, inner protective sheath 16, and activator shaft 17, is shown in lumen wall 30 having lumen wall surface 31.
• Tails 20a, 20b, 20c, 2Od, of inner protective sheath 16 are pressed by SE stent 12 against lumen wall surface 31 of lumen wall 30.
• Zone 80 includes pusher spring 15 and represents a zoomed-in view shown in Figure 10.
• Figure 10 shows a zoomed in view of the schematic cross-sectional representation of the exemplary embodiment of Figure 8 showing zone 80 including pusher spring 15.
• Pusher spring 15 abuts SE stent 12 to maintain SE stent 12 in position against lumen wall surface 31.
• Pusher spring 15 is shown in Figure 10 having depression 100 to prevent SE stent 12 from moving between pusher spring 15 and lumen wall surface 31 during a retraction of the tails of an inner protective sheath.
• the outer sheath may be coupled to a catheter. From action 114 the flow proceeds to action 115, which indicates to sever the circumferential ring from each of the longitudinal slits to make the inner sheath include a set of loose tails. From action 115 the flow proceeds to end circle 116.
• Figure 12 shows a schematic cross-sectional representation of another exemplary embodiment of the present invention after a partial retraction of the outer sheath showing the SE stent partially expanded.
• Delivery system 10 includes tip 11 and looped wires 121a, 121b, 121c, 12 Id, 12 Ie, 12 If attached to proximal inner sheath 120. More or fewer looped wires may also be provided. Looped wires 121c, 121d are attached at a distal end at loop 122. Loop 122 may be a tight loop.
• Proximal inner sheath 120 includes anchor points 123a, 123b, which may anchor looped wires 121a, 121b, 121c, 121d, 121e, 121f to proximal inner sheath 120.
• Anchor points 123a, 123b may include a laser weld, a heat bond, or any other appropriate method of attachment.
• Looped wires 121a, 121b, 121c, 121d, 121e, 121f may be stainless steel, nitinol, elgiloy-typical metals, or any other appropriate material.
• Looped wires 121a, 121b, 121c, 12 Id, 12Ie 5 12 may be roll-flattened to increase the load-bearing area of the wires, to increase the radial flexibility of the loops, and/or to reduce the cross-sectional area of delivery system 10. Increasing the radial flexibility of the wires of the loops may facilitate the complete opening and/or expansion of the stent upon deployment.
• loop 122 may be absent and looped wires 121c, 12 Id may not be connected at a distal- end.
• looped wires 121c, 12 Id, as well as the other wires may terminate at a point or another appropriate shape.
• Figure 13 shows the schematic cross-sectional representation of the exemplary embodiment of Figure 12 cut along line XIII-XIII. Looped wires 121 e, 12 If are shown in cross-section and are roll-flattened. Width 130 of looped wire 12 If may therefore be larger than depth 131 of looped wire 121f. In particular width 130 may be 0.004 inches and depth 131 may be 0.001 inches.
• therapeutic agent includes one or more "therapeutic agents” or “drugs”.
• therapeutic agents include pharmaceutically active compounds, nucleic acids with and without carrier vectors such as lipids, compacting agents (such as histones), virus (such as adenovirus, andenoassociated virus, retrovirus, lentivirus and ⁇ -virus), polymers, hyaluronic acid, proteins, cells and the like, with or without targeting sequences.
• the therapeutic agent may be any pharmaceutically acceptable agent such as a non- genetic therapeutic agent, a biomolecule, a small molecule, or cells.
• biomolecules include peptides, polypeptides and proteins; oligonucleotides; nucleic acids such as double or single stranded DNA (including naked and cDNA), RNA 5 antisense nucleic acids such as antisense DNA and RNA, small interfering RNA (siRNA), and ribozymes; genes; carbohydrates; angiogenic factors including growth factors; cell cycle inhibitors; and anti-restenosis agents.
• Nucleic acids may be incorporated into delivery systems such as, for example, vectors (including viral vectors), plasmids or liposomes.
• Non-limiting examples of proteins include serca-2 protein, monocyte chemoattractant proteins ("MCP-I) and bone morphogenic proteins ("BMP's”), such as, for example, BMP-2, BMP-3, BMP-4, BMP-5, BMP-6 (VgM), BMP-7 (OP-I), BMP-8, BMP-9, BMP-IO, BMP- 11, BMP-12, BMP-13, BMP-14, BMP-15.
• Preferred BMPS are any of BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, and BMP-7. These BMPs can be provided as homdimers, heterodimers, or combinations thereof, alone or together with other molecules.
• molecules capable of inducing an upstream or downstream effect of a BMP can be provided.
• Such molecules include any of the "hedghog" proteins, or the DNA's encoding them.
• genes include survival genes that protect against cell death, such as anti-apoptotic Bcl-2 family factors and Akt kinase; serca 2 gene; and combinations thereof.
• Non-limiting examples of angiogenic factors include acidic and basic fibroblast growth factors, vascular endothelial growth factor, epidermal growth factor, transforming growth factor ⁇ and ⁇ , platelet-derived endothelial growth factor, platelet- derived growth factor, tumor necrosis factor ⁇ , hepatocyte growth factor, and insulin like growth factor.
• a non-limiting example of a cell cycle inhibitor is a cathespin D (CD) inhibitor.
• Non-limiting examples of anti-restenosis agents include pi 5, pi 6, pl8, pl9. p21, ⁇ 27, p53, p57, Rb, nFkB and E2F decoys, thymidine kinase ("TK”) and combinations thereof and other agents useful for interfering with cell proliferation.
• TK thymidine kinase
• Exemplary small molecules include hormones, nucleotides, amino acids, sugars, and lipids and compounds have a molecular weight of less than 10OkD.
• Exemplary cells include stem cells, progenitor cells, endothelial cells, adult cardiomyocytes, and smooth muscle cells.
• Cells can be of human origin (autologous or allogenic) or from an animal source (xenogenic), or genetically engineered.
• Non-limiting examples of cells include side population (SP) cells, lineage negative (Lin-) cells including LU1-CD34-, Lin-CD34+, Lin-cKit+, mesenchymal stem cells including mesenchymal stem cells with 5-aza, cord blood cells, cardiac or other tissue derived stem cells, whole bone marrow, bone marrow mononuclear cells, endothelial progenitor cells, skeletal myoblasts or satellite cells, muscle derived cells, go cells, endothelial cells, adult cardiomyocytes, fibroblasts, smooth muscle cells, adult cardiac fibroblasts + 5-aza, genetically modified cells, tissue engineered grafts, MyoD scar fibroblasts, pacing cells, embryonic stem cell clo
• Any of the therapeutic agents may be combined to the extent such combination is biologically compatible.
• any of the above mentioned therapeutic agents may be incorporated into a polymeric coating on the medical device or applied onto a polymeric coating on a medical device.
• the polymers of the polymeric coatings may be biodegradable or non-biodegradable.
• suitable non-biodegradable polymers include polystrene; polyisobutylene copolymers and styrene-isobutylene-styrene block copolymers such as styrene-isobutylene-styrene tert-block copolymers (SIBS); polyvinylpyrrolidone including cross-linked polyvinylpyrrolidone; polyvinyl alcohols, copolymers of vinyl monomers such as EVA; polyvinyl ethers; polyvinyl aromatics; polyethylene oxides; polyesters including polyethylene terephthalate; polyamides; polyacrylamides; polyethers including polyether sulfone; polyalkylenes including polypropylene, poly
• BAYHDROL® squalene emulsions
• suitable biodegradable polymers include polycarboxylic acid, polyanhydrides including maleic anhydride polymers; polyorthoesters; poly-amino acids; polyethylene oxide; polyphosphazenes; polylactic acid, polyglycolic acid and copolymers and mixtures thereof such as poly(L-lactic acid) (PLLA), poly(D,L,-lactide), poly(lactic acid-co-glycolic acid), 50/50 (DL-lactide-co-glycolide); polydioxanone; polypropylene fumarate; polydepsipeptides; polycaprolactone and co-polymers and mixtures thereof such as poly(D,L-lactide-co-caprolactone) and polycaprolactone co-butylacrylate; polyhydroxybutyrate valerate and blends; polycarbonates such as tyrosine-derived polycarbonates and arylates, polyiminocarbonates, and polydimethyltrimethylcarbonates;
• the biodegradable polymer may also be a surface erodable polymer such as polyhydroxybutyrate and its copolymers, polycaprolactone, polyanhydrides (both crystalline and amorphous), maleic anhydride copolymers, and zinc- calcium phosphate.
• a surface erodable polymer such as polyhydroxybutyrate and its copolymers, polycaprolactone, polyanhydrides (both crystalline and amorphous), maleic anhydride copolymers, and zinc- calcium phosphate.
• Such coatings used with the present invention may be formed by any method known to one in the art.
• an initial polymer/solvent mixture can be formed and then the therapeutic agent added to the polymer/solvent mixture.
• the polymer, solvent, and therapeutic agent can be added simultaneously to form the mixture.
• the polymer/solvent mixture may be a dispersion, suspension or a solution.
• the therapeutic agent may also be mixed with the polymer in the absence of a solvent.
• the coating can be applied to the medical device by any known method in the art including dipping, spraying, rolling, brushing, electrostatic plating or spinning, vapor deposition, air spraying including atomized spray coating, and spray coating using an ultrasonic nozzle.
• the coating is typically from about 1 to about 50 microns thick. In the case of balloon catheters, the thickness is preferably from about 1 to about 10 microns, and more preferably from about 2 to about 5 microns. Very thin polymer coatings, such as about 0.2-0.3 microns and much thicker coatings, such as more than 10 microns, are also possible. It is also within the scope of the present invention to apply multiple layers of polymer coatings onto the medical device. Such multiple layers may contain the same or different therapeutic agents and/or the same or different polymers. Methods of choosing the type, thickness and other properties of the polymer and/or therapeutic agent to create different release kinetics are well known to one in the art.
• the medical device may also contain a radio-opacifying agent within its structure to facilitate viewing the medical device during insertion and at any point while the device is implanted.
• radio-opacifying agents are bismuth subcarbonate, bismuth oxychloride, bismuth trioxide, barium sulfate, tungsten, and mixtures thereof.
• Non-limiting examples of medical devices according to the present invention include catheters, guide wires, balloons, filters (e.g., vena cava filters), stents, stent grafts, vascular grafts, intraluminal paving systems, implants and other devices used in connection with drug- loaded polymer coatings.
• Such medical devices may be implanted or otherwise utilized in body lumina and organs such as the coronary vasculature, esophagus, trachea, colon, biliary tract, urinary tract, prostate, brain, lung, liver, heart, skeletal muscle, kidney, bladder, intestines, stomach, pancreas, ovary, cartilage, eye, bone, and the like.

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• 2005
  • 2005-02-16 US US11/059,240 patent/US7918880B2/en active Active
• 2006
  • 2006-02-01 EP EP06734111.5A patent/EP1858456B1/en active Active
  • 2006-02-01 WO PCT/US2006/003377 patent/WO2006088638A1/en not_active Ceased
  • 2006-02-01 CA CA2599054A patent/CA2599054C/en not_active Expired - Fee Related
  • 2006-02-01 JP JP2007556159A patent/JP2008529719A/ja active Pending

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