Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M25/00—Catheters; Hollow probes
  • A61M25/10—Balloon catheters
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M25/00—Catheters; Hollow probes
  • A61M25/10—Balloon catheters
  • A61M25/1027—Making of balloon catheters
  • A61M25/1029—Production methods of the balloon members, e.g. blow-moulding, extruding, deposition or by wrapping a plurality of layers of balloon material around a mandril
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M25/00—Catheters; Hollow probes
  • A61M25/10—Balloon catheters
  • A61M25/1027—Making of balloon catheters
  • A61M25/1029—Production methods of the balloon members, e.g. blow-moulding, extruding, deposition or by wrapping a plurality of layers of balloon material around a mandril
  • A61M2025/1031—Surface processing of balloon members, e.g. coating or deposition; Mounting additional parts onto the balloon member's surface

Definitions

• the present invention relates to the field of insertable and implantable medical devices, in particular, to catheter delivery systems for use therewith.
• Atherosclerotic cardiovascular disease is common, and is caused by a narrowing of the arterial lining due to atherosclerotic plaques. When plaque builds up, this is referred to in the art as stenosis.
• One method commonly employed to relieve arterial stenosis resulting from plaque build-up is percutaneous transluminal coronary angioplasty, or balloon angioplasty.
• PTCA or balloon angioplasty is a non-invasive, non-surgical means of treating coronary arteries.
• This technique consists of inserting a non- inflated balloon catheter into the affected artery. Dilation of the diseased segment of artery is accomplished by inflating the balloon which pushes the atherosclerotic lesion outward, compressing the stenosis and enlarging the arterial diameter.
• a physician can also implant an intravascular prosthesis, or a stent, for maintaining vascular patency inside an artery or other vessel at the lesion.
• Stents are also used for a variety of other purposes including maintaining the patency of any physiological conduit including arteries, veins, vessels, the biliary tree, the urinary tract, the alimentary tract, the tracheobronchial tree, the genitourinary system, and the cerebral aqueduct.
• pharmacologically active therapeutic agents such as those in the form of a drug eluting coating, to reduce the amount of restenosis caused by intimal hyperplasia.
• Stents may be may either be self-expanding or balloon expandable.
• the stent is often delivered on a balloon and the balloon is used to expand the stent.
• the balloon is used for POBA or for stent delivery, one consideration is withdrawal resistance of the balloon after use.
• withdrawal resistance may be Depending on the material used to manufacture the balloon and the stent, and possibly stent coating, there may be friction between the balloon and stent surfaces. Also, if a sufficient amount of time is not allowed for the balloon to fully deflate after use, there may be resistance upon attempts to withdraw the balloon from the treatment site.
• the present invention relates to an expandable medical device having at least one inner layer and at least one outer layer with a lattice formed in the inner surface or the outer surface of the outer layer, the device having at least one static state, at least one expanded state and at least one deflated state, in the expanded state the lattice is open, and in the static state the lattice is closed.
• both the inner and outer layer are polymeric.
• the intermediate layer may include a variety of coatings.
• the intermediate layer includes at least one lubricious polymer material, at least one therapeutic agent(s), or a combination thereof.
• the expandable medical device may be employed in combination with a catheter assembly.
• the expandable medical device may be employed in combination with a stent.
• the present invention relates to a variety of methods of making the expandable medical device including the steps of forming an inner and an outer layer, and forming a lattice in the inner surface or the outer surface of the outer layer.
• the inner and outer layer can be formed simultaneously, or first individually formed prior to assembly.
• the intermediate layer can be formed simultaneously with the inner and outer layer, or, the intermediate layer can be injected between the inner and outer layer as a liquid mixture, after the inner and outer layer have been assembled.
• the lattice can be formed in the inner surface or the outer surface of the outer layer prior to assembly, or can be formed in the outer surface after forming or assembly of the inner and outer layer.
• FIG. 1 is a flat perspective view of one embodiment of a lattice formed in the outer layer of a multilayer medical device according to the invention.
• FIG. 2A is a partial radial cross-section illustrating a tri-layer configuration of an expandable medical device in a static state wherein the lattice is closed.
• FIG. 2B is a partial radial cross-section illustrating a tri-layer configuration of an expandable medical device similar to that shown in FIG. 2A in an expanded state wherein the lattice is open.
• FIG. 3A is a partial radial cross-section illustrating an alternative tri-layer configuration of an expandable medical device in a static state wherein the lattice is closed similar to that shown in FIG. 1.
• FIG. 3 B is a partial radial cross-section illustrating a tri-layer configuration of an expandable medical device similar to that shown in FIG. 3 A in an expanded state wherein the lattice is open.
• FIG. 4 is a partial perspective view of a tri-layer medical balloon disposed on a dual-layer shaft catheter assembly.
• FIG. 5 is an exploded view taken at section 5 in FIG. 4 illustrating the a lattice formed in the outer layer.
• FIG. 6 is a partial longitudinal cross-section showing a tri-layer balloon.
• FIG. 7 is a longitudinal cross-section of an expandable medical balloon having a tri- layer structure wherein the outer layer is a generic representation of the lattice in the outer layer.
• FIG. 7 A is a radial cross-section taken at section IA-I A in FIG. 7.
• FIGS. 8-10 are longitudinal cross-sections illustrating various embodiments of a tri-layer balloon having different lattices formed into the outer layer.
• FIGS. 8A- 1OA are radial cross-sections taken at 8A-8A, 9A-9A and 10A- 1OA in FIGS. 8, 9 and 10 respectively.
• the present invention is directed to a multilayer expandable medical device having at least one static state, at least one expanded state, and at least one deflated state.
• the outer layer of the multilayer expandable medical device in the at least one static state, has a closed structure, and in the at least one expanded state, the outer layer has a lattice-like open structure. This allows an intermediate layer to be exposed when the medical device is in its at least one expanded state.
• the static state shall refer to the balloon as formed, prior to expansion or deflation.
• the intermediate layer is a lubricious coating layer, a drug- eluting layer, or a combination thereof.
• the expandable medical device herein may find particular utility for delivery of medical devices such implantable medical prosthesis such as stents and stent grafts wherein the intermediate layer is a lubricious coating layer.
• implantable medical prosthesis such as stents and stent grafts wherein the intermediate layer is a lubricious coating layer.
• the outer layer has a closed structure and the intermediate lubricious layer is unexposed.
• the outer layer is in its open lattice-like structure, exposing the lubricious layer which in turn can facilitate withdrawal of the expandable medical device once the implantable prosthesis has been deployed.
• the intermediate layer may include any suitable lubricious material including both hydrophobic and hydrophilic materials, with hydrophilic materials being preferred.
• hydrophilic materials are preferred.
• a hydrophobic material is silicone.
• Hydrophilic polymer materials may also be employed.
• the term "hydrophilic” is used to refer to water having various degrees or water sensitivity including those materials that are water soluble, dispersible, dissolvable, etc.
• water soluble shall include those materials which have partial solubility in water.
• Suitable hydrophilic polymers include those that have non-crosslinked structures having hydrophilic groups thereon, such as -OH, -COOH, -CONH, -COO-, etc.
• the hydrophilic ity of the polymer can be controlled by the number of such groups, as well as the polymer structure.
• hydrophilic materials include, but are not limited to polyalkylene glycols such as polyethylene glycol (PEG), and modified polyalkylene glycols such as polyethylene and polypropylene oxide and hydrophilic block copolymers thereof, poly(N)-vinyl lactams, such as polyvinylpyrrolidone (PVP), polyacrylamides, cellulosics such as methyl cellulose, carboxymethyl cellulose, hydroxyethyl cellulose and hydroxypropyl cellulose, carbohydrates, sugar alcohols such as mannitol, polyols, monosaccharides, oligosaccharides, polysaccharides and modified polysaccharides such as heparin (mucopolysaccharide), polyacrylic acids such as acrylic and methacrylic acids and salts thereof with alkali metal salts with sodium and potassium salts being most common and alkaline earth metal salts, hydroxyl methacrylate (HEMA), polyvinyl alcohols, polyvinyl s
• hydrophilic polymer materials see for example, U.S. Patent No. 5,509,899 and U.S. Patent Publication No. 2006/0212106, each of which is incorporated by reference herein in its entirety.
• Bioerodible hydrogels are suitable and in some embodiments, preferred. Examples include, but are not limited to, polyhyaluronic acids, casein, gelatin, glutin, polyanhydrides, polyacrylic acid, alginate, chitosan, poly(methyl methacrylates), poly(ethyl methacrylates), poly(butylmethacrylate), poly (isobutyl methacrylate), poly (hexylmethacrylate), poly (isodecyl methacrylate), poly (lauryl methacrylate), poly (phenyl methacrylate), poly(methyl acrylate), poly(isopropyl acrylate), poly(isobutyl acrylate), and poly(octadecyl acrylate).
• polyhyaluronic acids casein, gelatin, glutin, polyanhydrides
• polyacrylic acid alginate
• chitosan poly(methyl methacrylates), poly(ethyl methacrylates), poly(butyl
• hydrogels include, but are not limited to, polyvinylpyrrolidone, polyethylene oxide (polyethylene glycol), polyvinyl alcohol, etc.
• polyvinylpyrrolidone polyethylene oxide (polyethylene glycol), polyvinyl alcohol, etc.
• polyethylene oxide polyethylene glycol
• polyvinyl alcohol polyvinyl alcohol
• the addition of a the lubricious coating layer can reduce the withdrawal resistance that may occur when the physician attempts to withdraw a balloon from an expanded stent without allowing sufficient time for the balloon to deflate fully. There may be friction between the material employed for forming the balloon and a stent coating, for example.
• the addition of a lubricious coating between the stent and balloon during deployment can aid the withdrawal of the balloon from the stent.
• the lubricious coating remains unexposed beneath the closed lattice of the balloon outer layer. The lubricious coating only becomes exposed upon expansion of the balloon, and breakage of the closed lattice.
• the expandable medical device described herein may find particular utility as a drug delivery device for the controlled delivery of a therapeutic substance(s) wherein the intermediate layer is a drug-eluting layer.
• the therapeutic substance(s) begin to elute following inflation of the medical device and breakage of the closed lattice.
• the intermediate layer be a drug-eluting layer
• any suitable therapeutic agent may be employed therein.
• therapeutic agent include genetic therapeutic agents, non-genetic therapeutic agents and cells.
• a drug may be used singly or in combination with other drugs.
• Drugs include genetic materials, non-genetic materials, and cells including those of human origin, animal origin, and those that are genetically engineered.
• non-genetic materials include, but are not limited to, anti- thrombogenic agents, anti-proliferative agents, anti-inflammatory agents, analgesics, antineoplastic/antiproliferative/anti-miotic agents, anesthetic agents, anti-coagulants, vascular cell growth promoters, vascular cell growth inhibitors, cholesterol-lowering agents; vasodilating agents; and agents which interfere with endogenous vascoactive mechanisms.
• genetic materials include, but are not limited to, anti-sense DNA and RNA and coding DNA, for example.
• therapeutic agents include, but are not limited to, anti-restenosis drugs, such as paclitaxel, sirolimus, everolimus, tacrolimus, dexamethoasone, estradiol, ABT-578 (Abbott Laboratories), trapidil, liprostin,
• anti-restenosis drugs such as paclitaxel, sirolimus, everolimus, tacrolimus, dexamethoasone, estradiol, ABT-578 (Abbott Laboratories), trapidil, liprostin,
• Patent No. 7105175, 7014654, 6899731, 6855770 and 6545097 each of which is incorporated by reference herein in its entirety, and in commonly assigned U.S. Patent
• the drug may be provided in a liquid carrier between the at least one outer layer and the at least one inner layer, or may be provided in a polymer carrier.
• Suitable polymer carriers may include biodegradable/bioresorbable polymer materials.
• polyhydroxyalkanoates such as poly(hydroxybutyrate) (PHB), poly(hydroxyvalerate) (PHV) and poly(hydroxybutyrate-co-valerate), polylactones such as polycapolactone (PCL), poly(L-lactic acid) (PLA), poly(glycolic acid) (PGA), poly(D,L-lactic acid), poly ⁇ actide-co-glycolide) (PLGA), polydioxanone, polyorthoesters, polyanhydrides, poly(glycolic acid-co-trimethylene carbonate), polyphosphoesters, polyphosphoester urethanes, poly(amino acids), cyanoacrylates, poly(trimethylene carbonate), poly(iminocarbonate), copoly(ether-esters) (e.g.
• PEO/PLA polyalkylene oxalates
• polyphosphazenes and biomolecules such as fibrin, fibrinogen, cellulose, starch, collagen, hyaluronic acid, etc., and mixtures thereof.
• Bioabsorable polymers are disclosed in U.S. Patent No. 6,790,228, the entire content of which is incorporated by reference herein.
• Other polymer materials include block copolymers of styrene and isoprene (SIS), butadiene (SBS), ethylene/butylene (SEBS), isobutylene (SIBS), ethylene/propylene (SEPS), etc.
• Diblock copolymers may also find utility herein.
• block copolymers which may be employed include polyamide- block-ether copolymers such as those available under the tradename of PEBAX® available from Arkema in Philadelphia, PA, and polyester and copolyester elastomers such as poly(ester-b lock-ether) elastomers available under the tradename of HYTREL® from DuPont de Nemours & Co. and poly(ester-block-ester)
• polystyrene resin examples include, polyolefins, such as ethylene and propylene homopolymers, as well as any copolymers or terpolymers of ethylene and propylene such as ethylene-vinyl acetate copolymers, ethylene (meth)acrylate copolymers, ethylene n-butyl acrylate copolymers, and grafted polyolefins such as maleic anhydride grafted polyethylene or polypropylene, and so forth.
• polyolefins such as ethylene and propylene homopolymers
• any copolymers or terpolymers of ethylene and propylene such as ethylene-vinyl acetate copolymers, ethylene (meth)acrylate copolymers, ethylene n-butyl acrylate copolymers, and grafted polyolefins such as maleic anhydride grafted polyethylene or polypropylene, and so forth.
• polymer carrier materials include, but are not limited to, polyesters, polyamides including nylon 6,6 and nylon 12, polyurethanes, polyethers, polyimides, polycarboxylic acids including polyacrylic acids, (meth)acrylates, cellulosics, polycaprolactams, polyacrylamides, polycarbonates, polyacrylonitriles, polyvinylpyrrolidones, copolymers and terpolymers thereof, etc.
• the therapeutic agent may be mixed with a lubricious material, for example, a hydrogel material, thereby providing an intermediate layer which has both lubriciousness, as well as drug-eluting characteristics.
• a lubricious material for example, a hydrogel material
• lattice shall be used to describe the pattern formed in the outer layer of the multilayer balloon structure through any suitable means such as cutting, scarring, etching, searing, embossing, etc. that weakens the layer. However, the pattern is not formed all the way through the layer.
• the lattice opens at the weakened regions to expose the underlayer.
• FIG. 1 is a partial perspective view of an outer balloon surface illustrating one embodiment of a lattice formed in the surface.
• Channels 2 have been formed using any suitable means such as cutting, embossing, searing, etching either chemically or mechanically, scarring, etc. These channels 2 have a thinner wall than corresponding areas 4 and are weakened as a result.
• FIG. 2 A is a partial radial cross-section of an expandable medical device having a tri-layer structure.
• an inner layer 12 defines the expandable medical balloon.
• Outer layer 16 has a lattice structure with channels 2 formed into the inner surface of the outer layer.
• FIG. 2A the expandable medical device is in a static state.
• FIG. 2B is a partial radial cross-section of an expandable medical device similar to that shown in FIG. 2A, wherein the device is in an expanded state, and the lattice in the outer layer 16, has opened. Openings 8 in the lattice structure expose the inner layer 14 which may be a lubricious layer, a drug eluting layer, or combination thereof as discussed above.
• FIG. 3 A is a partial radial cross-section of an expandable medical device having a tri- layer structure wherein the outer layer 16 has an alternative lattice structure more similar to that shown in FIG. 1 wherein channels 2 are formed in the outer surface of the outer layer as opposed to that shown in FIG. 2A.
• an inner layer 12 defines the expandable medical balloon, hi FIG. 2A, the expandable medical device is in a static state.
• FIG. 3B is a partial radial cross-section of an expandable medical device similar to that shown in FIG. 3A, wherein the device is in an expanded state, and the lattice in the outer layer 16, has opened.
• openings 8 in the lattice structure expose the inner layer 14 which may be a lubricious layer, a drug eluting layer, or combination thereof as discussed above.
• Outer layer 16 may be formed from any polymer material and is suitably, a material that has less elasticity or expansitivity, for example, than that of the inner layer 12.
• Suitable outer layer materials include, but are not limited to, polyalkylene terephthalates such as polyethylene terephthalate and polybutylene terephthalate, polyethylene, polypropylene, polyamides, polycarbonate, poly(ether-block-amide) such as PEBAX® 72D available from Arkema, North America, located in Philadelphia, PA.
• PEBAX® 72D available from Arkema, North America, located in Philadelphia, PA.
• the inner layer 12 has superior mechanical properties to that of the outer layer 16, such as more elasticity and expansivity.
• Suitable materials for the inner layer 12 include, for example, any block copolymer that is more elastomeric or elastic than that of the outer layer 16.
• the inner layer 12 may be formed from a more elastic PEBAX® material, for example, PEBAX® 62D, also available from Arkema.
• block copolymer materials need not be employed for the inner layer 12, provided that it has more elasticity than that of the outer layer 16.
• the outer layer 16 may be formed from any suitable material that protects the intermediate layer and allows/controls when the intermediate layer is released.
• suitable material that protects the intermediate layer and allows/controls when the intermediate layer is released.
• Other examples include, but are not limited to, block copolymers such as styrenic block copolymers having styrene endb locks and midblocks of butadiene, isoprene, ethylene/butylene, ethylene/propylene, etc., copolyesters, polyester-polyether block copolymers such as those available under the tradename of Hytrel®, polyurethanes, etc.
• the inner layer 12 may be formed from any material suitable for POBA
• thermoplastic ionomers such as those available under the tradename of Surlyn® (also referred to as polyolefin copolymers), polyesters such as polyethylene terephthalate and polybutylene terephthalate, polyamides including nylon 6,6, nylon 12 and nylon 6, polyurethanes, copolyesters, polyester-polyethers such as those available under the tradename of
• Arnitel® or Hytrel® polyether-b lock-amides available under the tradename of Pebax®, polyolefins including polyethylene and polypropylene and copolymers and terpolymers thereof such as ethylene vinyl acetate, etc.
• the inner layer is selected so as to exhibit more elasticity than the outer layer.
• Combinations of materials from the same family can be employed, providing that the material selected for each layer exhibit different properties.
• a Pebax® resin that is more rigid can be employed for the outer layer
• a Pebax® resin that is more elastic for the inner layer for example, Pebax® 7233 exhibits a higher flexural modulus than does Pebax® 7033 or Pebax® 6333.
• the outer layer 16 may be highly elastic and the inner layer 12 is less elastic.
• the material selected may be microporous/nanoporous material wherein the pores open when the balloon is inflated.
• the elasticity of the outer layer could also assist the balloon to re-wrap upon deflation allowing easier withdrawal.
• the outer layer may be either rigid or elastic providing that it protects the intermediate layer and controls/allows when the intermediate layer is released.
• Micro fluidic channels also could be employed wherein movement of the intermediate layer is allowed with pressure driven flow upon balloon inflation or osmotic material that allows movement of the coating in one direction only upon balloon inflation could also be employed for use in forming the outer layer.
• FIG. 4 illustrates a partial perspective view of a medical balloon disposed about a dual-shaft catheter assembly having an inner shaft 22 and an outer shaft 24.
• Balloon 10 has a tri-layer design including an outer layer 16 having a diamond lattice formed therein, an intermediate layer 14, and an inner layer 12 which defines the expandable medical balloon structure.
• intermediate layer 14 can be lubricious, drug-eluting, or a combination thereof.
• other types of coatings can be employed as well depending on the end result desired.
• Lubricious coatings on the outer surface of a balloon may have an adverse impact on stent delivery due to slippage of the stent on the balloon.
• lubricious coatings decrease withdrawal resistance of the balloon once the stent has been deployed. Therefore, exposing the lubricious coating only during deployment of the stent, provides a desirable combination of properties to the balloon.
• FIGS. 2 and 3 may be referred back to for illustration on opening of the lattice once the expandable medical balloon has been expanded.
• FIG. 5 is a partial exploded view of the tri- layer balloon structure taken at section 5 in FIG. 4.
• FIG. 6 is a partial longitudinal cross-section of a balloon as shown in FIGS. 4 and 5.
• FIGS. 7- 1OA illustrate various embodiments of a balloon according to the present invention and include a variety of lattices (patterns) which may be formed into the outer balloon layer.
• FIG. 7 is a longitudinal cross-section of a balloon 10 having a tri- layer structure.
• the outer layer 16 which includes the lattice, is shown generically in this figure, as the lattice could be formed of an endless array of patterns.
• Balloon 10 is shown with an intermediate layer 14 and an inner layer 12.
• Balloon 10 has waist portions 26, 28, cone portions 27, 29 and a body portion 30.
• the outer layer 16 maybe formed on any portion or combination of these portions. For example, it may be desirable to form the outer layer 16 on only the body portion 30.
• FIG. 7A is a radial cross-section taken at section IA-I A in FIG. 7.
• FIG. 8 is a longitudinal cross-section illustrating one embodiment of a balloon having a lattice formed of longitudinal channels 18 in the balloon body 30 only.
• FIG. 8 A is a radial cross-section taken at section 8A-8A in FIG. 8.
• FIG. 9 is longitudinal cross-section of illustrating another embodiment of a balloon having a different lattice formed into balloon body 30.
• This lattice includes a plurality of channels 18 that are discontinuous on the balloon body 30.
• FIG. 9 A is a radial cross-section taken at section 9A-9A in FIG. 9.
• FIG. 10 is longitudinal cross-section of illustrating another embodiment of a balloon having a different lattice formed into balloon body 30.
• This lattice includes a plurality of marks 18 in the form of crosses 18 formed into the surface of the outer layer 16 on the balloon body 30.
• FIG. 1OA is a radial cross-section taken at section lOA-lOA in FIG. 10.
• the lattice pattern may be a defined repeatable pattern or may be non-regular and random.
• the balloons may be formed using any suitable balloon forming process.
• the inner layer, defining the balloon structure maybe extruded as a tubular balloon preform.
• the intermediate layer can be applied in a variety of ways including co-extrusion with the inner layer, by spraying, dipping, brushing, etc.
• the intermediate layer can be applied to the whole balloon structure, or to any portion thereof as desired.
• the tubular member is stretched, and the ends then dipped in glycerin leaving the ends crystallized and leaving a predetermined length of the central portion of the tubular preform balloon uncrystallized.
• the preform is then inserted into a balloon forming mold and radially expanded using nitrogen, for example.
• One method of adding the outer layer having the lattice is to first radially expand this outer layer in a mold that has blades inside the mold, the blades cutting the lattice pattern in the outer surface of the outer layer as desired.
• this layer can be formed in a standard balloon mold, no blades, and then the lattice can be cut, etched, embossed, seared, etc. on the inner surface of the outer layer.
• the inner layer with the intermediate layer suitably an intermediate layer with some adhesive characteristics, can be radially expanded in the same mold. Heat treating can then facilitate adhesively bonding the inner layer to the outer layer via the intermediate layer.
• the balloon can be formed with the inner and outer layer only, and the intermediate layer injected between the inner and outer layer.
• This process may be more readily employed wherein the lattice pattern is formed on the inner surface of the outer layer. See FIGS. 2 and 3, for example, wherein there are more spaces via channels 2, that exist between the inner layer 12 and outer layer 16.
• the coating can then be cured such as by drying if the coating is applied from a solvent.
• Balloon folds can then be formed in the balloon, the balloon deflated and a stent crimped thereon if the balloon is employed for stent delivery.
• all three layers can be simultaneously coextruded as well wherein the three different materials are combined using three different extruders.
• Tooling can be made to the correct dimension you require for your product.
• Intermittent coextrusion or via use of a quick shut-off valve at the crosshead can be employed to provide the outer layer on only those portions of the balloon, such as the balloon body, as desired.
• the lattice can be formed in the outer surface of the outer layer such as through etching, cutting, ablating, via a laser, embossing, searing, etc
• the coating can alternatively be injected between a coextruded inner and outer layer as well through interstices, which is more readily employed wherein the lattice is formed in the inner surface of the outer layer.
• the inner layer may optionally include an adhesive for securement to the outer layer.
• the adhesive may be coextruded as well.
• the present invention allows for the localized controlled delivery of a variety of substances to a specific target site within a patient such as during POBA (plain old balloon angioplasty) and stent delivery.
• POBA plain old balloon angioplasty
• stent delivery

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