US20090004243A1 - Biodegradable triblock copolymers for implantable devices - Google Patents
Biodegradable triblock copolymers for implantable devices Download PDFInfo
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- US20090004243A1 US20090004243A1 US11/824,011 US82401107A US2009004243A1 US 20090004243 A1 US20090004243 A1 US 20090004243A1 US 82401107 A US82401107 A US 82401107A US 2009004243 A1 US2009004243 A1 US 2009004243A1
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- 0 C.C[1*]OC(C)(C)OC Chemical compound C.C[1*]OC(C)(C)OC 0.000 description 4
- QZWOXAWYWJSRPJ-UHFFFAOYSA-N CC1OC(=O)C(C)OC1=O.O=C1COC(=O)CO1.O=C1OCCCO1.OCO.[H]OC(C)C(=O)OC(C)C(=O)OCC(=O)OCC(=O)OCOC(=O)OCOC(=O)OCOC.[H]OC(C)C(=O)OC(C)C(=O)OCC(=O)OCC(C)=O.[H]OCC(=O)OCC(=O)OCOC(=O)OCOC(=O)OCOC(=O)COC(=O)CO[H].[H]OCOC(=O)OCOC(=O)OCO[H] Chemical compound CC1OC(=O)C(C)OC1=O.O=C1COC(=O)CO1.O=C1OCCCO1.OCO.[H]OC(C)C(=O)OC(C)C(=O)OCC(=O)OCC(=O)OCOC(=O)OCOC(=O)OCOC.[H]OC(C)C(=O)OC(C)C(=O)OCC(=O)OCC(C)=O.[H]OCC(=O)OCC(=O)OCOC(=O)OCOC(=O)OCOC(=O)COC(=O)CO[H].[H]OCOC(=O)OCOC(=O)OCO[H] QZWOXAWYWJSRPJ-UHFFFAOYSA-N 0.000 description 1
Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/08—Materials for coatings
- A61L31/10—Macromolecular materials
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K31/00—Medicinal preparations containing organic active ingredients
- A61K31/33—Heterocyclic compounds
- A61K31/395—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins
- A61K31/435—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins having six-membered rings with one nitrogen as the only ring hetero atom
- A61K31/4353—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins having six-membered rings with one nitrogen as the only ring hetero atom ortho- or peri-condensed with heterocyclic ring systems
- A61K31/436—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins having six-membered rings with one nitrogen as the only ring hetero atom ortho- or peri-condensed with heterocyclic ring systems the heterocyclic ring system containing a six-membered ring having oxygen as a ring hetero atom, e.g. rapamycin
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
- A61L29/04—Macromolecular materials
- A61L29/041—Macromolecular materials obtained by reactions only involving carbon-to-carbon unsaturated bonds
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
- A61L29/14—Materials characterised by their function or physical properties, e.g. lubricating compositions
- A61L29/16—Biologically active materials, e.g. therapeutic substances
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/04—Macromolecular materials
- A61L31/048—Macromolecular materials obtained by reactions only involving carbon-to-carbon unsaturated bonds
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/04—Macromolecular materials
- A61L31/06—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L31/16—Biologically active materials, e.g. therapeutic substances
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
- A61P9/00—Drugs for disorders of the cardiovascular system
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
- C08G81/00—Macromolecular compounds obtained by interreacting polymers in the absence of monomers, e.g. block polymers
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/60—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
- A61L2300/606—Coatings
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2420/00—Materials or methods for coatings medical devices
Definitions
- the present invention is directed to polymeric materials made of biodegradable, bioabsorbable triblock copolymers and implantable devices (e.g., drug-delivery stents) containing such polymeric materials.
- Angioplasty is a well-known procedure for treating heart disease.
- a problem associated with angioplasty includes formation of intimal flaps or torn arterial linings which can collapse and occlude the conduit after the balloon is deflated.
- thrombosis and restenosis of the artery may develop over several months after angioplasty, which may require another angioplasty procedure or a surgical by-pass operation.
- “Stenosis” refers to a narrowing or constriction of the diameter of a bodily passage or orifice
- restenosis refers to the reoccurrence of stenosis in a blood vessel or heart valve after it has been treated (as by balloon angioplasty, stenting, or valvuloplasty) with apparent success.
- Stents are often used in the treatment of atherosclerotic stenoses in blood vessels.
- a stent may be implanted in the lumen to reinforce body vessels and maintain the vascular patency.
- a “lumen” refers to a cavity of a tubular organ such as a blood vessel.
- stents act as scaffoldings, functioning to physically hold open and, if desired, to expand the wall of a passageway, e.g., a blood vessel, urinary tract or bile duct.
- Stents are also used as a vehicle for providing biological therapy.
- Biological therapy can be achieved by medicating the stents.
- Medicated stents provide for the local administration of a therapeutic substance at the diseased site, thereby possibly avoiding side effects associated with systemic administration of such medication.
- One method of medicating stents involves the use of a polymeric carrier coated onto the surface of a stent, in which a therapeutic substance is impregnated in polymer.
- Late stent thrombosis has emerged as a concern for drug-delivery stents.
- the incidence of late stent thrombosis appears to be higher with drug-delivery stents than with the corresponding bare metal stents.
- One potential cause of late thrombosis with drug-delivery stents is a chronic inflammatory or hypersensitivity response to the polymeric coating on the stent.
- the present invention addresses late stent thrombosis and offers other advantageous features.
- the present invention is directed to biodegradable polymeric materials used for implantable devices (e.g., stents) that enable the devices to perform their functions more effectively and avoid adverse effects.
- the polymeric materials are configured to completely or substantially completely erode after the devices accomplish their intended functions (e.g., maintaining vascular patency and locally delivering drugs), thereby avoiding adverse effects such as late stent thrombosis.
- Other advantages of the biodegradable polymeric materials include, among others, good mechanical properties (e.g., strength, rigidity, toughness and flexibility), control of drug-release rates, and enhanced adhesion to metal surfaces.
- One embodiment of the invention is directed to a composition comprising a biodegradable triblock copolymer of the structure A-B-A′, wherein:
- the tensile modulus of the hard A and A′ blocks independently is greater than about 1,000 MPa, and the tensile modulus of the soft B block is less than about 1,000 MPa.
- the weight fraction of the A and A′ blocks is from about 1% to about 99% of the triblock copolymer.
- the A, B and A′ blocks each independently comprise a polymer comprising from one to four different types of monomer, wherein each type of monomer has from about 5 to about 5,000 monomer units.
- the polyketal polymer of the B block has the structure
- R 1 is a poly(caprolactone) diol or a C 2 -C 24 diol of the structure, HO—R 1 —OH, that contains an optionally substituted aliphatic, heteroaliphatic, cycloaliphatic, heterocycloaliphatic, aromatic or heteroaromatic group, or a combination thereof, and n is an integer from about 5 to about 5,000.
- At least one dihydroxyaryl group is conjugated to the polymer ends of the triblock copolymer.
- composition of the invention further comprises at least one biocompatible moiety.
- composition further comprises at least one additional biologically absorbable polymer.
- the composition further comprises at least one biologically active agent.
- the at least one biologically active agent is selected from the group consisting of antiproliferative, antineoplastic, anti-inflammatory, antiplatelet, anticoagulant, antifibrin, antithrombin, antimitotic, antibiotic, antiallergic and antioxidant substances.
- the at least one biologically active agent is selected from the group consisting of paclitaxel, docetaxel, estradiol, nitric oxide donors, super oxide dismutases, super oxide dismutase mimics, 4-amino-2,2,6,6-tetramethylpiperidine-1-oxyl (4-amino-TEMPO), tacrolimus, dexamethasone, rapamycin, rapamycin derivatives, 40-O-(2-hydroxy)ethyl-rapamycin (everolimus), 40-O-(2-ethoxy)ethyl-rapamycin (biolimus), 40-O-(3-hydroxy)propyl-rapamycin, 40-O-[2-(2-hydroxy)ethoxy]ethyl-rapamycin, 40-O-tetrazole-rapamycin, 40-epi-(N-tetrazolyl)-rapamycin (zotarolimus), pimecrolimus, imatinib mesylate
- inventions of the invention are directed to a coating comprising any combination of embodiments of the inventive composition.
- inventions of the invention are directed to an implantable device formed of a material comprising any combination of embodiments of the inventive composition.
- the material comprises any combination of embodiments of the inventive coating, which is disposed over the implantable device.
- the implantable device is a stent, graft, stent-graft, catheter, lead, electrode, clip, shunt, closure device, or valve.
- Still other embodiments of the invention are directed to a method of preparing any combination of embodiments of the inventive composition, e.g., via ring-opening polymerization of the corresponding monomers of the A, B and A′ blocks.
- inventions are directed to a method of fabricating an implantable device.
- the method comprises forming the implantable device of a material comprising any combination of embodiments of the inventive composition.
- the method comprises depositing any combination of embodiments of the inventive coating over at least a portion of the implantable device.
- the implantable device is a stent, graft, stent-graft, catheter, lead, electrode, clip, shunt, closure device, or valve.
- Still further embodiments of the invention are directed to a method of treating or preventing a condition or disorder in a patient, comprising implanting in the patient any combination of embodiments of the inventive implantable device.
- the condition or disorder is selected from the group consisting of atherosclerosis, thrombosis, restenosis, hemorrhage, vascular dissection, vascular perforation, vascular aneurysm, vulnerable plaque, chronic total occlusion, patent foramen ovale, claudication, anastomotic proliferation of vein and artificial grafts, bile duct obstruction, ureter obstruction and tumor obstruction.
- biologically degradable or “biodegradable”
- biologicalcally erodable or “bioerodable”
- biologicalcally absorbable or “bioabsorbable”
- biologicalcally resorbable or “bioresorbable”
- in reference to polymers and coatings are used interchangeably and refer to polymers and coatings that are capable of being completely or substantially completely degraded, dissolved, and/or eroded over time when exposed to bodily fluids such as blood and can be gradually resorbed, absorbed and/or eliminated by the body, or that can be degraded into fragments that can pass through the kidney membrane of a human (e.g., fragments having a molecular weight of about 40,000 Daltons (40 kDa) or less).
- a “biostable” polymer or coating refers to a polymer or coating that is not biodegradable.
- biologically degradable biologically degradable
- biologically erodable biologically absorbable
- biologically resorbable biologically resorbable
- Biodegradability “bioerodability,” “bioabsorbability,” and “bioresorbability” are defined as inherent property of the coating or polymer forming the coating that is biologically degradable, biologically erodable, biologically absorbable, or biologically resorbable.
- biocompatible moieties refer to moieties that are capable of enhancing biological compatibility of the composition, material or structure containing them.
- Physiological conditions refer to conditions to which an implant is exposed within the body of an animal (e.g., a human). Physiological conditions include, but are not limited to, human body temperature (approximately 37° C.) and an aqueous environment of physiologic ionic strength, pH and enzymes.
- a “prohealing” drug or agent refers to a drug or agent that has the property that it promotes or enhances re-endothelialization of arterial lumen to promote healing of the vascular tissue.
- a “co-drug” is a drug that is administered concurrently or sequentially with another drug to achieve a particular pharmacological effect.
- the effect may be general or specific.
- the co-drug may exert an effect different from that of the other drug, or it may promote, enhance or potentiate the effect of the other drug.
- prodrug refers to an agent rendered less active by a chemical or biological moiety, which metabolizes into or undergoes in vivo hydrolysis to form a drug or an active ingredient thereof.
- the term “prodrug” can be used interchangeably with terms such as “proagent”, “latentiated drugs”, “bioreversible derivatives”, and “congeners”. N.J. Harper, Drug latentiation, Prog Drug Res., 4: 221-294 (1962); E. B. Roche, Design of Biopharmaceutical Properties through Prodrugs and Analogs, Washington, D.C.: American Pharmaceutical Association (1977); A. A. Sinkula and S. H.
- prodrugs can generally be defined as pharmacologically less active chemical derivatives that can be converted in vivo, enzymatically or nonenzymatically, to the active, or more active, drug molecules that exert a therapeutic, prophylactic or diagnostic effect.
- block copolymer and “graft copolymer” are defined in accordance with the terminology used by the International Union of Pure and Applied Chemistry (IUPAC).
- Block copolymer refers to a copolymer containing a linear arrangement of blocks. The block is defined as a portion of a polymer molecule in which the monomer units have at least one constitutional or configurational feature absent from the adjacent portions.
- “Graft copolymer” refers to a polymer composed of macromolecules with one or more species of block connected to the main chain as side chains, these side chains having constitutional or configurational features that differ from those in the main chain.
- ABA′ triblock copolymer is defined as a block copolymer having moieties A, B and A′ arranged according to the general formula - ⁇ [A-] m -[B] n -[A′] p ⁇ - x , where each of “m,” “n,” “p” and “x” independently is a positive integer ⁇ 1. For example, each of m, n, and p independently may be ⁇ 1 and ⁇ 10,000.
- the blocks of the ABA′ triblock copolymer need not be linked on the ends, since the values of the integers determining the number of A, B and A′ blocks are such as to ensure that the individual blocks are usually long enough to be considered polymers in their own right. Accordingly, the ABA′ triblock copolymer can be named poly A-block-poly B-block-poly A′ block copolymer. Blocks A, B and A′ can be alternating or random.
- a material that is described as a coating “disposed over” an indicated substrate refers to a coating of the material deposited directly or indirectly over at least a portion of the surface of the substrate.
- Direct depositing means that the coating is applied directly to the exposed surface of the substrate.
- Indirect depositing means that the coating is applied to an intervening layer that has been deposited directly or indirectly over the substrate.
- an “implantable device” may be any device that can be implanted in an animal.
- implantable devices include, but are not limited to, self-expandable stents, balloon-expandable stents, coronary stents, peripheral stents, stent-grafts, catheters, other expandable tubular devices for various bodily lumen or orifices, grafts, vascular grafts, arterio-venous grafts, by-pass grafts, pacemakers and defibrillators, leads and electrodes for the preceding, artificial heart valves, anastomotic clips, arterial closure devices, patent foramen ovale closure devices, and cerebrospinal fluid shunts.
- the stents may be intended for any vessel in the body, including neurological, carotid, vein graft, coronary, aortic, renal, iliac, femoral, popliteal vasculature, and urethral passages.
- An implantable device can be designed for the localized delivery of a therapeutic agent.
- a medicated implantable device may be constructed by coating the device or substrate with a coating material containing a therapeutic agent.
- the substrate of the device may also contain a therapeutic agent.
- An implantable device can be fabricated with a coating containing partially or completely a biodegradable/bioabsorbable/bioerodable polymer, a biostable polymer, or a combination thereof.
- An implantable device itself can also be fabricated partially or completely from a biodegradable/bioabsorbable/bioerodable polymer, a biostable polymer, or a combination thereof.
- the “glass transition temperature”, T g is the temperature at which the amorphous domains of a polymer change from a brittle, glassy, vitreous state to a solid deformable, ductile or rubbery state at atmospheric pressure.
- the T g corresponds to the temperature where the onset of segmental motion in the chains of the polymer occurs.
- the increasing heat capacity corresponds to an increase in heat dissipation through movement.
- the T g of a given polymer can be dependent on the heating rate and can be influenced by the thermal history of the polymer. Furthermore, the chemical structure of the polymer heavily influences the glass transition by affecting chain mobility.
- the “melting temperature”, T m is the temperature at which the crystalline domains of a polymer lose their short- and long-term order, changing from a regular, ordered structure of chain packing to that of a disordered structure, resembling an amorphous polymer.
- the disappearance of the polymer crystalline phase is accompanied by changes in physical properties of the polymer.
- the material becomes a viscous solid, with discontinuous changes in the density, refractive index, heat capacity, transparency, and other properties.
- the T m of a given polymer occurs over a finite temperature range. The breadth of the transition is dependent on the size and perfection of the polymer crystallites, as well as their homogeneity and purity.
- the T m of a semi-crystalline polymer is an endothermic transition when the heating rate is positive.
- the ability of the polymer chains to pack into an ordered, repeating structure is heavily influenced by the chemical structure of the polymer.
- Stress refers to force per unit area, as in the force acting through a small area within a plane. Stress can be divided into components, normal and parallel to the plane, called normal stress and shear stress, respectively. True stress denotes the stress where force and area are measured at the same time. Conventional stress, as applied to tension and compression tests, is force divided by the original gauge length.
- “Strength” refers to the maximum stress along an axis which a material will withstand prior to fracture. The ultimate strength is calculated from the maximum load applied during the test divided by the original cross-sectional area.
- Modulus may be defined as the ratio of a component of stress or force per unit area applied to a material divided by the strain along an axis of applied force that results from the applied force.
- a material has both a tensile and a compressive modulus.
- a material with a relatively high modulus tends to be stiff or rigid.
- a material with a relatively low modulus tends to be flexible.
- the modulus of a material depends on the molecular composition and structure, temperature of the material, amount of deformation, and the strain rate or rate of deformation. For example, below its T g , a polymer tends to be brittle with a high modulus. As the temperature of a polymer is increased from below to above its T g , its modulus decreases.
- Stress refers to the amount of elongation or compression that occurs in a material at a given stress or load.
- Elongation may be defined as the increase in length in a material which occurs when subjected to stress. It is typically expressed as a percentage of the original length.
- “Toughness” is the amount of energy absorbed prior to fracture, or equivalently, the amount of work required to fracture a material.
- One measure of toughness is the area under a stress-strain curve from zero strain to the strain at fracture. Thus, a brittle material tends to have a relatively low toughness.
- alkyl and aliphatic group refer to an optionally substituted, straight-chain or branched, saturated or unsaturated hydrocarbon moiety that may contain one or more heteroatoms selected from O, S, and N. If unsaturated, the alkyl or aliphatic group may contain one or more double bonds and/or one or more triple bonds.
- the alkyl or aliphatic group may be monovalent (i.e., —R) or divalent (i.e., —R—) in terms of its attachment to the rest of the compound.
- alkyl and aliphatic groups include, but are not limited to, methyl, ethyl, ethylenyl, ethynyl, n-propyl, isopropyl, propenyl, propynyl, n-butyl, isobutyl, sec-butyl, tertiary-butyl, butenyl, butynyl, n-pentyl, isopentyl, pentenyl, and pentynyl.
- heteroalkyl and “heteroaliphatic group” refer to an alkyl or aliphatic group that contains at least one heteroatom selected from O, S and N, in the main portion and/or the branch(es) of the hydrocarbon moiety.
- heteroalkyl and heteroaliphatic groups include, but are not limited to, alcohols, ethers, oxo compounds, ketones, aldehydes, esters, carbonates, thioesters, thiols, sulfides, sulfoxides, sulfones, sulfonamides, amino compounds, amines, nitriles, N-oxides, imines, oximes, amides, carbamates, ureas, and thioureas.
- cycloalkyl and “cycloaliphatic group” refer to an optionally substituted, saturated or unsaturated, mono- or polycyclic hydrocarbon moiety that may contain one or more heteroatoms selected from O, S, and N. If unsaturated, the cycloalkyl or cycloaliphatic group may contain one or more double bonds and/or one or more triple bonds in and/or off of one or more rings of the cyclic moiety.
- the cycloalkyl or cycloaliphatic group may be monovalent (i.e., -Cyc) or divalent (i.e., -Cyc-) in terms of its attachment to the rest of the compound.
- cycloalkyl and cycloaliphatic groups include, but are not limited to, cyclopropyl, cyclobutyl, cyclopentyl, cyclopentenyl, cyclohexyl, cyclohexenyl, decahydronaphthyl, and octahydroindyl.
- heterocycloalkyl and “heterocycloaliphatic group” refer to a cycloalkyl or cycloaliphatic group in which at least one ring in the cyclic moiety contains one or more heteroatoms selected from O, S, and N.
- heterocycloalkyl and heterocycloaliphatic groups include, but are not limited to, aziridinyl, oxiranyl, oxolanyl, thiolanyl, pyrrolidinyl, 3-pyrrolinyl, dioxalanyl, 1,3-dithiolanyl, oxazolidinyl, imidazolidinyl, oxanyl, piperidinyl, piperazinyl, 1,3-dioxanyl, 1,4-dioxanyl, morpholinyl, octahydroindolyl, octahydroisoindolyl, octahydrobenzofuryl, octahydrobenzothiophene, octahydrochromenyl, and decahydroquinolinyl.
- aryl and “aromatic group” refer to an optionally substituted mono- or polycyclic aromatic moiety in which at least one ring in the moiety is aromatic.
- the ring(s) in the moiety may be carbocyclic or may contain one or more heteroatoms selected from O, S, and N.
- the ring(s) in the moiety may be aromatic or non-aromatic (saturated or unsaturated), but at least one ring in the moiety is aromatic.
- An aryl or aromatic group may be monovalent (i.e., —Ar) or divalent (i.e., —Ar—) in terms of its attachment to the rest of the compound.
- aryl and aromatic groups include, but are not limited to, phenyl, indolinyl, isoindolinyl, 2,3-dihydrobenzofuryl, 2,3-dihydrobenzothiophene, chromanyl, 1,2,3,4-tetrahydroquinolinyl, 1,2,3,4-tetrahydroisoquinolinyl, naphthyl, indenyl, and indanyl.
- heteroaryl and “heteroaromatic group” refer to an aryl or aromatic group in which at least one ring (aromatic or non-aromatic) in the aromatic moiety contains one or more heteroatoms selected from O, S, and N.
- heteroaryl and heteroaromatic groups include, but are not limited to, pyrrolyl, pyrazolyl, imidazolyl, furyl, isoxazolyl, oxazolyl, thiophenyl, thiazolyl, isothiazolyl, triazolyl, oxadiazolyl, thiadiazolyl, tetrazolyl, pyridyl, pyridazinyl, pyrimidinyl, pyrazinyl, 1,3,5-triazinyl, indolyl, isoindolyl, benzofuranyl, benzothiophenyl, indazolyl, benzimidazolyl, benzothiazolyl, [1,7]naphthyridinyl, chromenyl, quinolinyl, isoquinolinyl, cinnolinyl, quinazolinyl, quinoxalinyl, phthalazinyl,
- alkyl, aliphatic, heteroalkyl, heteroaliphatic, cycloalkyl, cycloaliphatic, heterocycloalkyl, heterocycloaliphatic, aryl, aromatic, heteroaryl and heteroaromatic groups may be substituted or unsubstituted. If substituted, they may contain from 1 to 5 substituents.
- the substituents include, but are not limited to: optionally substituted carbon-containing groups, e.g., alkyl, cycloalkyl and aryl (e.g., benzyl); halogen atoms (i.e., F, Cl, Br and I) and optionally substituted halogen-containing groups, e.g., haloalkyl (e.g., trifluoromethyl); optionally substituted oxygen-containing groups, e.g., oxo, alcohols (e.g., hydroxyl, hydroxyalkyl, aryl(hydroxyl)alkyl), and ethers (e.g., alkoxy, aryloxy, alkoxyalkyl, aryloxyalkyl); optionally substituted carbonyl-containing groups, e.g., aldehydes (e.g., carboxaldehyde), ketones (e.g., alkylcarbonyl, alkylcarbonylalkyl, ary
- sulfhydryl alkylthio, alkylsulfinyl, alkylsulfonyl, alkylthioalkyl, alkylsulfinylalkyl, alkylsulfonylalkyl, arylthio, arylsulfinyl, arylsulfonyl, arylthioalkyl, arylsulfinylalkyl, arylsulfonylalkyl); and optionally substituted aromatic or non-aromatic heterocyclic groups containing one or more heteroatoms selected from O, S and N (e.g., thienyl, furanyl, pyrrolyl, imidazolyl, pyrazolyl, thiazolyl, isothiazolyl, oxazolyl, oxadiazolyl, thiadiazolyl, aziridinyl, azetidinyl, pyrrolidinyl, pyr
- the embodiments of the present invention are designed to possess certain advantages over conventional biodegradable polymers used to make implantable devices.
- the degradation rate of a polymer may be enhanced by the appropriate selection of monomers and ratio thereof for the “hard” and “soft” blocks of the polymer.
- the relatively high T g or T m of the “hard” blocks, above body temperature, increases the strength and rigidity of the polymer.
- the fracture toughness, flexibility and drug permeability of the polymer may be increased by incorporation, with the hard block polymers, of a “soft” block polymer having a T g less than the T g or T m of the hard block polymers.
- the hard and/or soft blocks may comprise another polymer that may be miscible or immiscible with the soft and/or hard block polymers, respectively.
- adhesion of a polymeric coating to a metal surface can be promoted by appropriate (e.g., chemical) modification of the polymer. Such modification could lead to a single polymer, which could be used as a drug reservoir, with no primer.
- one embodiment of the present invention is directed to a composition comprising a biodegradable triblock copolymer of the structure A-B-A′, wherein:
- the A and A′ blocks each independently have a T g or T m above body temperature when the A and A′ blocks are hydrated, and the B block has a T g less than the T g or T m of the A and A′ blocks when the B block is hydrated.
- the A and A′ blocks each independently have a T g or T m above body temperature when the A and A′ blocks are not hydrated, and the B block has a T g less than the T g or T m of the A and A′ blocks when the B block is not hydrated.
- the A and A′ blocks in the triblock copolymer may be the same or different from one another. In an embodiment, optionally in combination with one or more other embodiments described herein, the A and A′ blocks are the same. In another embodiment, optionally in combination with one or more other embodiments described herein, the A and A′ blocks are different.
- the B block may or may not be miscible with the A and A′ blocks. In one embodiment, optionally in combination with one or more other embodiments described herein, the B block is partially or completely miscible with the A and A′ blocks. In another embodiment, optionally in combination with one or more other embodiments described herein, the B block is partially or completely immiscible with the A and A′ blocks.
- the hard A and A′ blocks are formulated so that their T g or T m is above body temperature.
- the T g or T m of the A and A′ blocks can be tuned to a desired value by appropriate selection of component monomers and adjustment of their ratios and numbers.
- the T g or T m of the A and A′ blocks independently ranges from about 35° C. to about 300° C., or from about 40° C. to about 250° C., or from about 50° C. to about 200° C., or from about 60° C. to about 150° C., or from about 70° C. to about 100° C.
- High rigidity and strength may be important for implantable devices fabricated with a polymeric material, e.g., for a stent so that the stent can support the walls of a vessel.
- the degradation rate of the triblock copolymers may be increased by formulating the A and A′ blocks as polymers containing appropriate monomer(s), e.g., poly(glycolide) (PGA) or a glycolide-containing copolymer, as further described below.
- Some conventional polymers may have a lower toughness and flexibility than desired, e.g., for use in stent applications.
- certain glassy, semicrystalline polymers can have a T g above human body temperature and tend to be brittle under physiological conditions, exhibiting low elongation.
- Glassy refers to a polymer that exhibits a brittle fracture mechanism, in which there is little or no plastic deformation prior to failure.
- a stent coating fabricated from such polymers can have insufficient toughness and flexibility for the range of aggressive applications of a coated stent, such as overlapped stents, stent through stent delivery, and bifurcations.
- Some conventional polymers may also be unable to control drug release.
- a high drug/polymer ratio must be employed to get the drug to release.
- a high drug/polymer ratio can lead to a drug-release profile in which most of the drug is released as a burst, and the remaining portion of the drug is released very slowly.
- a low drug/polymer ratio may result in no drug release at all.
- the B block of the inventive triblock copolymer is formulated to have a T g less than the T g or T m of the hard A and A′ blocks.
- the T g of the B block can be tuned to a desired value by appropriate selection of component monomers and adjustment of their ratios and numbers.
- the B block has a T g below body temperature.
- the T g of the B block ranges from about ⁇ 70° C. to about 150° C., or from about ⁇ 50° C. to about 100° C., or from about ⁇ 25° C. to about 75° C., or from about 0° C.
- the B block may have a T m rather than a T g , and the scope of the present invention encompasses cases where the B block has a T m rather than a T g .
- the soft block may have greater flexibility, a lower modulus, and higher fracture toughness than the hard blocks at physiological conditions. It is believed that when a device is placed under stress, the soft block tends to absorb energy when a fracture starts to propagate through the device. Crack propagation through the hard blocks may then be reduced or inhibited. As a consequence, the fracture toughness of the polymeric material, and thus that of the device fabricated therewith, tend to be increased.
- the tensile modulus of the hard A and A′ blocks independently is greater than about 1,000 MPa, and the tensile modulus of the soft B block is less than about 1,000 MPa.
- the tensile modulus of the hard A and A′ blocks independently is greater than about 1,500 MPa, and the tensile modulus of the soft B block is less than about 750 MPa.
- the tensile modulus of the hard A and A′ blocks independently is greater than about 2,000 MPa, and the tensile modulus of the soft B block is less than about 500 MPa.
- the soft B block of the triblock copolymer may be composed of a rubbery or elastomeric polymer.
- An “elastomeric” or “rubbery” polymer refers to a polymer that exhibits elastic deformation through all or most of a range of deformation.
- the soft B block may also be substantially or completely amorphous.
- the B block can have a degree of crystallinity of about 10% or less.
- biodegradable polymers having a relatively high fracture toughness at body temperature include, but are not limited to, polycaprolactone (PCL), poly(trimethylene carbonate) (PTMC), polydioxanone, poly(propiolactone), poly(valerolactone) and polyacetal.
- PCL polycaprolactone
- PTMC poly(trimethylene carbonate)
- polydioxanone poly(propiolactone)
- poly(valerolactone) polyacetal
- some embodiments of the soft B block of the triblock copolymer can include caprolactone (CL), trimethylene carbonate (TMC), dioxanone, propiolactone, valerolactone or acetal monomer units, or a combination thereof.
- the hard blocks are anchored to the soft block through covalent bonds.
- A, A′ and B blocks have some degree of immiscibility, different domains, rich in soft blocks or hard blocks, form within the bulk polymer. These domains are bound to each other via the polymer chains they share.
- the high degree of adhesion provided by the covalent bonding facilitates energy transfer between the hard and soft blocks, and thus increases the fracture toughness of the triblock copolymer. It is believed that without the anchoring or adhesion provided by the covalent bonding, a propagating crack may go around the soft block, reducing the effectiveness of the soft block in absorbing energy imparted to a device.
- the hard and soft blocks phase-separate, various morphologies may be formed.
- the specific morphology formed depends on the relative amounts of the hard and soft blocks, as well as their chemical nature.
- the soft block comprises a small volume fraction of the polymer, it tends to exist as a dispersed phase in a continuous phase of the hard block(s).
- the hard block comprises a small volume fraction, it tends to exist as a dispersed phase in a continuous phase of soft block.
- Variations of the ratio of soft to hard blocks allow one to tune/modify the properties of the polymeric material, e.g., the drug permeability and drug-release rate of the material.
- the degradation rate of the triblock copolymers can be influenced by the physical state of the hard and soft blocks. Since the diffusion rate of fluids through an amorphous structure is generally faster than through a crystalline structure, the hard blocks and/or soft block may exhibit a higher degree of amorphousness to increase the degradation rate. The faster degrading hard blocks and/or soft block increase water penetration and content in those blocks. The increased water penetration and content causes an increase in the degradation rate of the polymeric material and thus the device.
- the degradation rate of the triblock copolymers can also be influenced by the identity of the monomer units making up the hard and soft blocks.
- the hard blocks and/or soft block may include units that are hydrophilic and/or hydrolytically active. These two characteristics increase the moisture content of the polymeric material, which increases the degradation rate of the polymer.
- the hard blocks and/or soft block may also contain units that have acidic or hydrophilic degradation products. Since the rate of the hydrolysis reaction tends to increase as the pH decreases, acidic degradation products can increase the degradation rate of the polymeric material and hence the device.
- faster degrading polymers may contain the glycolide (GA) monomer.
- G glycolide
- glycolic acid hydrolyzes faster than L-lactic acid or D-lactic acid, for the ester bond formed from glycolic acid is less sterically hindered than that formed from lactic acid.
- glycolide units have acidic degradation products that can increase the degradation rate of a glycolide-containing polymeric material.
- glycolic acid is a low molecular weight monomer, so that an appreciable level of glycolic acid means that there is a substantial number of ester bonds formed from glycolic acid in a glycolide-containing polymer, any or all of which can hydrolyze.
- a fast degrading polymer is poly(glycolide-co-trimethylene carbonate) (P(GA-co-TMC)).
- the soft B block can include toughness-enhancing units and fast degrading units.
- the soft block may include GA, CL, TMC, valerolactone, propiolactone or acetal units, or a combination thereof.
- the B block can have alternating or random GA, CL, TMC, valerolactone, propiolactone and acetal units.
- the B block can be poly(GA-co-CL), poly(GA-co-TMC), or poly(GA-co-TMC-co-CL).
- the flexibility, toughness and degradation rate of the soft B block can also be adjusted by the ratio of fast degrading and toughness-enhancing units. For example, as the ratio of CL increases in poly(GA-co-CL), the block copolymer becomes more flexible and tougher.
- the degradation rate of the B block, and hence that of the polymeric material can be increased by increasing the fraction of GA in the B block.
- the poly(GA-co-CL) or poly(GA-co-TMC) segments can have greater than 1 wt %, 5 wt %, 20 wt %, 50 wt %, 70 wt % or 80 wt % GA units.
- the mechanical properties (e.g., rigidity, strength, toughness and flexibility), degradation rate and drug permeability of the inventive triblock copolymer can be tuned by appropriate selection of the monomer units of the hard and soft blocks, the ratio of the monomers within the blocks, the length or molecular weight of the blocks, the weight ratio of the blocks, and any other substances chemically or non-chemically incorporated with the triblock copolymer.
- the entire polymer needs to have sufficient molecular weight. Accordingly, in some embodiments, optionally in combination with one or more other embodiments described herein, the triblock copolymers have a polymer number-average molecular weight (M n ) of at least about 20 kDa. In other embodiments, the triblock copolymers have an M n of at least about 40 kDa.
- M n polymer number-average molecular weight
- the triblock copolymers range in M n from about 20 kDa to about 1,000 kDa. In another embodiment, the triblock copolymers range in M n from about 20 kDa to about 500 kDa. A polymer with an M n from about 20 kDa to about 500 kDa may be more amenable to being processed into a coating. In yet another embodiment, the triblock copolymers range in M n from about 40 kDa to about 500 kDa.
- the blocks to form discrete phases which are indicative of an immiscible system they need to be of a certain minimal size.
- each phase is saturated with the other phase, although these saturated concentrations may be very small.
- the A, A′ and B blocks each independently have an M n of at least about 1 kDa.
- the A, A′ and B blocks each independently range in M n from about 1 kDa to about 500 kDa, or from about 10 kDa to about 400 kDa, or from about 20 kDa to about 300 kDa, or from about 30 kDa to about 200 kDa, or from about 40 kDa to about 100 kDa.
- the ratio of the molecular weight of each of the A and A′ blocks to the B block is between about 20:1 and about 1:20, more narrowly between about 10:1 and about 1:10, and still more narrowly between about 5:1 and about 1:5.
- the weight fraction of the A and A′ blocks with respect to the total triblock copolymer is from about 1% to about 99%, more narrowly from about 10% to about 90%, still more narrowly from about 20% to about 80%, even more narrowly from about 30% to about 70%, and still even more narrowly from about 40% to about 60%.
- the triblock copolymer can contain about 1-30 wt %, or more narrowly about 2-20 wt %, of the B block and about 70-99% wt %, or 80-98 wt %, of the A and A′ blocks.
- the A, B and A′ blocks each independently comprise a polymer comprising from one to four different types of monomer, wherein each type of monomer has from about 5 to about 5,000 monomer units.
- each type of monomer in the polymer of the A, B or A′ block independently has from about 10 to about 4,500 monomer units, or from about 20 to about 4,000 monomer units, or from about 30 to about 3,500 monomer units, or from about 40 to about 3,000 monomer units, or from about 50 to about 2,500 monomer units.
- the A, A′ and B blocks specifically cannot comprise one or more of any of the aforementioned polymers.
- the A and A′ blocks can comprise PGA or a glycolide-containing copolymer to achieve fast degradation.
- the hard A and A′ blocks are formulated so that their T g or T m is above body temperature.
- the B block comprises a glycolide-containing polymer.
- the B block is formulated to have a T g less than the T g or T m of the A and A′ blocks.
- the B block has a T g below body temperature.
- poly(TMC) has a T g of ⁇ 15° C.
- poly(dioxanone) has a T g of ⁇ 10° C. to 0° C.
- the B block may be formulated to be miscible or immiscible with the A and A′ blocks. In some embodiments, the B block is immiscible with the A and A′ blocks.
- the polyketal polymer of the B block has the structure of
- R 1 is a poly(caprolactone) diol or a C 2 -C 24 diol of the structure, HO—R 1 —OH, that contains an optionally substituted aliphatic, heteroaliphatic, cycloaliphatic, heterocycloaliphatic, aromatic or heteroaromatic group, or a combination thereof, and n is an integer from about 5 to about 5,000.
- n for the polyketal polymer is an integer from about 10 to about 4,500, or from about 20 to about 4,000, or from about 30 to about 3,500, or from about 40 to about 3,000, or from about 50 to about 2,500.
- the polyketal polymer has a polymer number-average molecular weight (M n ) from about 0.5 kDa to about 500 kDa.
- M n polymer number-average molecular weight
- the polyketal polymer has an M n in the range from about 1 kDa to about 500 kDa, or from about 10 kDa to about 400 kDa, or from about 20 kDa to about 300 kDa, or from about 30 kDa to about 200 kDa, or from about 40 kDa to about 100 kDa.
- R 1 is a poly(caprolactone) diol. In other embodiments, R 1 is a C 2 -C 24 diol, more narrowly a C 2 -C 16 diol, or even more narrowly a C 2 -C 8 diol.
- R 1 diol specifically cannot be any particular one of the various diols that fall within the genus of the R 1 diol, as defined herein. In a particular embodiment, the R 1 diol specifically cannot be a poly(caprolactone) diol.
- the polyketal polymer of the B block possesses properties that make it a suitable component of the inventive biodegradable triblock copolymer.
- the ketal linkages in the backbone of the polyketal polymer undergo rapid acid-catalyzed hydrolysis.
- the degradation products, C 2 -C 24 HO—R 1 —OH and acetone are low molecular weight, excretable compounds that in many cases are water-soluble and not acidic.
- the polyketal polymer is an acid-sensitive, biodegradable polymer that is expected to release an incorporated drug at an accelerated rate in acidic environments.
- the polyketal polymer may degrade faster than some polymers (e.g., PLGA), but more slowly than other polymers (e.g., poly(ortho esters) and poly( ⁇ -amino esters)), thereby permitting the tuning of drug-release rates to a particular application.
- some polymers e.g., PLGA
- other polymers e.g., poly(ortho esters) and poly( ⁇ -amino esters)
- R 1 group gives a polyketal polymer having a different T g , and thus allows for the tuning of the flexibility and toughness of the polymer. Further, selection of different R 1 groups differing in their degree of lipophilicity and steric bulkiness yields polyketal polymers differing in hydrophobicity/hydrophilicity and steric hindrance around the ketal linkages. This would affect the degradation rate and the drug-release rate of the triblock copolymer containing the polyketal polymer.
- Poly(caprolactone) can be a flexible polymer having a T g of about ⁇ 60° C. (the T g /T m of PCL is tunable depending on, e.g., its molecular weight). PCL may also be tuned to degrade more slowly, e.g., in about 1-2 years. Therefore, the use of poly(caprolactone) diol as the R 1 diol can result in a polyketal that is softer and more flexible, but degrades more slowly, than polyketals based on an aromatic R 1 diol (e.g., 1,4-benzenedimethanol).
- an aromatic R 1 diol e.g., 1,4-benzenedimethanol
- the polyketal polymer may be synthesized by any of various methods known in the art.
- the polyketal polymer may be synthesized by acid-catalyzed polycondensation of the diol, HO—R 1 —OH, with an acetone source such as acetone or 2,2-dimethoxypropane.
- the synthesis may be done in the presence of excess diol, which would result in a hydroxyl-terminated polymer segment that may be used to initiate growth of other segments of the B block or growth of the A and A′ blocks by ring-opening polymerization.
- A-B-A′ triblock copolymers of the present invention e.g., poly(GA-ran-LLA)-block-poly(TMC)-block-poly(GA-ran-LLA)
- TMC block-poly(GA-ran-LLA)
- An additional advantage of the inventive triblock copolymers is their compatibility with terminal sterilization techniques.
- Various terminal sterilization processes are available for sterilizing implantable devices such as drug-delivery stents. Many of these processes, such as electron beam and gamma irradiation, can cause degradation of the drug. Ethylene oxide gas (EOG) tends to cause less drug degradation.
- EOG sterilization the drug-delivery coating is exposed to a combination of heat, humidity and EOG. With many conventional biodegradable polymers, such a combination of conditions softens the coating, leading to coating flow and deformation.
- the triblock copolymers of the invention are compatible with EOG sterilization.
- a primer of that pure polymer may have to be used to achieve optimum adhesion to metal stents.
- the triblock copolymers of the invention have characteristics that improve their adhesion to metal surfaces.
- the B block with a lower T g is expected to interact favorably with a metal substrate at body temperature.
- the different polarity of the hard A and A′ blocks and the soft B block increases the chance of favorable non-covalent adhesive interactions with metal substrates.
- At least one dihydroxyaryl group could be conjugated to the polymer ends of the triblock copolymers.
- the dihydroxyaryl group(s) may contain a dihydroxyphenyl moiety.
- Ortho-dihydroxyphenyl groups in 3,4-dihydroxyphenyl alanine have been shown to be responsible for the bonding of mussel adhesive proteins to a variety of metallic substrates. B. P. Lee et al., Biomacromolecules, 3: 1038-1047 (2002).
- 3,4-dihydroxyphenyl-containing compounds that may be conjugated to the polymer ends of the triblock copolymers to increase their adhesion to metal surfaces include, e.g., dopamine and 3,4-dihydroxyhydrocinnamic acid.
- At least one dihydroxyaryl group is conjugated to the polymer ends of the triblock copolymer.
- the at least one dihydroxyaryl group contains an ortho-dihydroxyphenyl moiety.
- the at least one dihydroxyaryl group contains a 1,2-dihydroxyphenyl moiety.
- the at least one dihydroxyaryl group contains a 3,4-dihydroxyphenyl moiety.
- 3,4-Dihydroxyphenyl-containing compounds that could be conjugated to the polymer ends of a triblock copolymer include, e.g., dopamine and 3,4-dihydroxyhydrocinnamic acid.
- compositions comprising an A-B-A′ triblock copolymer of the invention and at least one biologically compatible (or “biocompatible”) moiety.
- the at least one biocompatible moiety may be blended or bonded with the triblock copolymer. If bonded with the triblock copolymer, the biocompatible moiety may be included in the A, B and/or A′ bocks, providing the ABA′ triblock copolymer with biological, e.g., blood, compatibility.
- the biocompatible moieties may be selected in such a way as to make the entire ABA′ triblock copolymer biologically degradable.
- biocompatible moieties include, but are not limited to, poly(alkylene glycols), e.g., poly(ethylene glycol) (PEG), poly(ethylene oxide), poly(propylene glycol) (PPG), poly(tetramethylene glycol) and poly(ethylene oxide-co-propylene oxide); lactones and lactides, e.g., ⁇ -caprolactone, ⁇ -butyrolactone, ⁇ -valerolactone and glycolide; poly(N-vinyl pyrrolidone); poly(acrylamide methyl propane sulfonic acid) and salts thereof (AMPS and salts thereof); poly(styrene sulfonate); sulfonated dextran; polyphosphazenes; poly(orthoesters); poly(tyrosine carbonate); sialic acid; hyaluronic acid; hyaluronic acid having a stearoyl or palmitoyl substitutent group; copo
- the molecular weight of a biocompatible polymeric moiety may be below 40 kDa to ensure renal clearance of the compound, e.g., between about 300 and about 40,000 Daltons, or between about 8,000 and about 30,000 Daltons, e.g., about 15,000 Daltons.
- the at least one biocompatible moiety is selected from the group consisting of poly(ethylene oxide), poly(propylene glycol), poly(tetramethylene glycol), polyethylene oxide-co-propylene oxide), ⁇ -caprolactone, ⁇ -butyrolactone, ⁇ -valerolactone, glycolide, poly(N-vinyl pyrrolidone), poly(acrylamide methyl propane sulfonic acid) and salts thereof, poly(styrene sulfonate), sulfonated dextran, polyphosphazenes, poly(orthoesters), poly(tyrosine carbonate), sialic acid, hyaluronic acid or derivatives thereof, copolymers of poly(ethylene glycol) with hyaluronic acid or derivatives thereof, heparin, copolymers of polyethylene glycol with heparin, a graft copolymer of poly(L-lysine) and poly(ethylene glycol),
- the at least one biocompatible moiety specifically cannot be one or more of any of the biocompatible moieties described herein.
- Yet another embodiment of the invention is directed to a composition comprising an A-B-A′ triblock copolymer of the invention and at least one additional biologically absorbable polymer.
- the at least one additional bioabsorbable polymer may impart desired properties to the composition.
- Such a polymer may be blended or bonded with the triblock copolymer.
- biologically absorbable polymers include, but are not limited to:
- PEG-PBT and PEG-PBT-PEG block copolymers are known under the trade name POLYACTIVETM and are available from IsoTis Corp. of Holland. These polymers can be obtained, e.g., by trans-esterification of dibutyleneterephthalate with PEG.
- POLYACTIVETM the ratio between the units derived from ethylene glycol and the units derived from butylene terephthalate can be between about 0.67:1 and about 9:1.
- the molecular weight of the units derived from ethylene glycol can be between about 300 and about 4,000 Daltons, and the molecular weight of the units derived from butylene terephthalate can be between about 50,000 and about 250,000, e.g., about 100,000 Daltons.
- DLPLA-PEG-DLPLA, PEG-DLPLA-PEG, PEG-PBT, PEG-PBT-PEG, PBT-PEG-PBT, PEG-PCL, PEG-PCL-PEG, and PCL-PEG-PCL block copolymers all contain fragments with ester bonds.
- Ester bonds are known to be water-labile bonds. When in contact with slightly alkaline blood, ester bonds are subject to base-catalyzed hydrolysis, thus ensuring biological degradability of the block copolymers.
- One product of degradation of every block polymer belonging to the group of DLPLA-PEG-DLPLA, PEG-DLPLA-PEG, PEG-PBT, PEG-PBT-PEG, PBT-PEG-PBT, PEG-PCL, PEG-PCL-PEG, and PCL-PEG-PCL is expected to be PEG, which is highly biologically compatible.
- the at least one additional biologically absorbable polymer is selected from the group consisting of poly(hydroxybutyrate), poly(hydroxyvalerate), poly(hydroxybutyrate-co-valerate), poly(caprolactone), poly(lactide-co-glycolide), poly(ethylene-glycol)-block-poly(butyleneterephthalate), poly(ethylene-glycol)-block-poly(butylene terephthalate)-block-polyethylene-glycol), poly(butyleneterephthalate)-block-poly(ethylene-glycol)-block poly(butyleneterephthalate), poly(ethylene-glycol)-block-poly(caprolactone), poly(ethylene-glycol)-block-poly(caprolactone)-block-poly(ethylene-glycol), poly(caprolactone)-block-poly(ethylene-glycol)-block-poly(caprolactone), and blends thereof.
- the at least one additional biologically absorbable polymer specifically cannot be one or more of any of the bioabsorbable polymers described herein.
- a further embodiment of the invention is directed to a composition comprising an A-B-A′ triblock copolymer of the invention and at least one biologically active (or “bioactive”) agent.
- the at least one biologically active agent may include any substance capable of exerting a therapeutic, prophylactic or diagnostic effect for a patient.
- bioactive agents include, but are not limited to, synthetic inorganic and organic compounds, proteins and peptides, polysaccharides and other sugars, lipids, and DNA and RNA nucleic acid sequences having therapeutic, prophylactic or diagnostic activities.
- Nucleic acid sequences include genes, antisense molecules that bind to complementary DNA to inhibit transcription, and ribozymes.
- bioactive agents include antibodies, receptor ligands, enzymes, adhesion peptides, blood clotting factors, inhibitors or clot dissolving agents such as streptokinase and tissue plasminogen activator, antigens for immunization, hormones and growth factors, oligonucleotides such as antisense oligonucleotides and ribozymes and retroviral vectors for use in gene therapy.
- the bioactive agents could be designed, e.g., to inhibit the activity of vascular smooth muscle cells. They could be directed at inhibiting abnormal or inappropriate migration and/or proliferation of smooth muscle cells to inhibit restenosis.
- the inventive composition comprises at least one biologically active agent selected from the group consisting of antiproliferative, antineoplastic, antimitotic, anti-inflammatory, antiplatelet, anticoagulant, antifibrin, antithrombin, antibiotic, antiallergic and antioxidant substances.
- An antiproliferative agent can be a natural proteineous agent such as a cytotoxin or a synthetic molecule.
- antiproliferative substances include, but are not limited to, actinomycin D or derivatives and analogs thereof (manufactured by Sigma-Aldrich, or COSMEGEN available from Merck) (synonyms of actinomycin D include dactinomycin, actinomycin IV, actinomycin I 1 , actinomycin X 1 , and actinomycin C 1 ); all taxoids such as taxols, docetaxel, and paclitaxel and derivatives thereof, all olimus drugs such as macrolide antibiotics, rapamycin, everolimus, structural derivatives and functional analogues of rapamycin, structural derivatives and functional analogues of everolimus, FKBP-12 mediated mTOR inhibitors, biolimus, perfenidone, prodrugs thereof, co-drugs thereof, and combinations thereof.
- rapamycin derivatives include, but are not limited to, 40-O-(2-hydroxy)ethyl-rapamycin (trade name everolimus from Novartis), 40-O-(2-ethoxy)ethyl-rapamycin (biolimus), 40-O-(3-hydroxy)propyl-rapamycin, 40-O-[2-(2-hydroxy)ethoxy]ethyl-rapamycin, 40-O-tetrazole-rapamycin, 40-epi-(N1-tetrazolyl)-rapamycin (zotarolimus, manufactured by Abbott Labs.), prodrugs thereof, co-drugs thereof, and combinations thereof.
- An anti-inflammatory drug can be a steroidal anti-inflammatory drug, a nonsteroidal anti-inflammatory drug (NSAID), or a combination thereof.
- anti-inflammatory drugs include, but are not limited to, alclofenac, alclometasone dipropionate, algestone acetonide, alpha amylase, amcinafal, amcinafide, amfenac sodium, amiprilose hydrochloride, anakinra, anirolac, anitrazafen, apazone, balsalazide disodium, bendazac, benoxaprofen, benzydamine hydrochloride, bromelains, broperamole, budesonide, carprofen, cicloprofen, cintazone, cliprofen, clobetasol, clobetasol propionate, clobetasone butyrate, clopirac, cloticasone propionate, cormethasone acetate, cortodoxone, de
- the anti-inflammatory agent may be a biological inhibitor of pro-inflammatory signaling molecules.
- Anti-inflammatory biological agents include antibodies to such biological inflammatory signaling molecules.
- bioactive agents can be other than antiproliferative or anti-inflammatory agents.
- the bioactive agents can be any agent that is a therapeutic, prophylactic or diagnostic agent. In some embodiments, such agents may be used in combination with antiproliferative or anti-inflammatory agents.
- These bioactive agents can also have antiproliferative and/or anti-inflammmatory properties or can have other properties such as antineoplastic, antimitotic, cystostatic, antiplatelet, anticoagulant, antifibrin, antithrombin, antibiotic, antiallergic, and/or antioxidant properties.
- antineoplastics and/or antimitotics include, but are not limited to, paclitaxel (e.g., TAXOL® available from Bristol-Myers Squibb), docetaxel (e.g., Taxotere® from Aventis), methotrexate, azathioprine, vincristine, vinblastine, fluorouracil, doxorubicin hydrochloride (e.g., Adriamycin® from Pfizer), and mitomycin (e.g., Mutamycin® from Bristol-Myers Squibb).
- paclitaxel e.g., TAXOL® available from Bristol-Myers Squibb
- docetaxel e.g., Taxotere® from Aventis
- methotrexate e.g., azathioprine, vincristine, vinblastine, fluorouracil, doxorubicin hydrochloride (e.g., Adriamycin® from Pfizer), and
- antiplatelet, anticoagulant, antifibrin, and antithrombin agents that may also have cytostatic or antiproliferative properties include, but are not limited to, sodium heparin, low molecular weight heparins, heparinoids, hirudin, argatroban, forskolin, vapiprost, prostacyclin and prostacyclin analogues, dextran, D-phe-pro-arg-chloromethylketone (synthetic antithrombin), dipyridamole, glycoprotein IIb/IIIa platelet membrane receptor antagonist antibody, recombinant hirudin, thrombin inhibitors such as ANGIOMAX (from Biogen), calcium channel blockers (e.g., nifedipine), colchicine, fibroblast growth factor (FGF) antagonists, fish oil (e.g., omega 3-fatty acid), histamine antagonists, lovastatin (a cholesterol-lowering drug that inhibits HMG-CoA reducta
- cytostatic substances include, but are not limited to, angiopeptin, angiotensin converting enzyme inhibitors such as captopril (e.g., Capoten® and Capozide® from Bristol-Myers Squibb), cilazapril and lisinopril (e.g., Prinivil® and Prinzide® from Merck).
- angiopeptin angiotensin converting enzyme inhibitors
- captopril e.g., Capoten® and Capozide® from Bristol-Myers Squibb
- cilazapril e.g., Prinivil® and Prinzide® from Merck
- antiallergic agents include, but are not limited to, permirolast potassium.
- antioxidant substances include, but are not limited to, 4-amino-2,2,6,6-tetramethylpiperidine-1-oxyl (4-amino-TEMPO).
- bioactive agents may include anti-infectives such as antiviral agents; analgesics and analgesic combinations; anorexics; antihelmintics; antiarthritics, antiasthmatic agents; anticonvulsants; antidepressants; antidiuretic agents; antidiarrheals; antihistamines; antimigrain preparations; antinauseants; antiparkinsonism drugs; antipruritics; antipsychotics; antipyretics; antispasmodics; anticholinergics; sympathomimetics; xanthine derivatives; cardiovascular preparations including calcium channel blockers and beta-blockers such as pindolol and antiarrhythmics; antihypertensives; diuretics; vasodilators including general coronary vasodilators; peripheral and cerebral vasodilators; central nervous system stimulants; cough and cold preparations, including decongestants; hypnotics; immunosuppressives; muscle relaxants; parasympatho
- Other biologically active agents include alpha-interferon, genetically engineered epithelial cells, tacrolimus and dexamethasone.
- a “prohealing” drug or agent in the context of a blood-contacting implantable device, refers to a drug or agent that has the property that it promotes or enhances re-endothelialization of arterial lumen to promote healing of the vascular tissue.
- the portion(s) of an implantable device (e.g., a stent) containing a prohealing drug or agent can attract, bind and eventually become encapsulated by endothelial cells (e.g., endothelial progenitor cells).
- endothelial cells e.g., endothelial progenitor cells.
- the attraction, binding, and encapsulation of the cells will reduce or prevent the formation of emboli or thrombi due to the loss of the mechanical properties that could occur if the stent was insufficiently encapsulated.
- the enhanced re-endothelialization may promote the endothelialization at a rate faster than the loss of mechanical properties of the stent.
- the prohealing drug or agent can be dispersed in the body of the bioabsorbable polymer substrate or scaffolding.
- the prohealing drug or agent can also be dispersed within a bioabsorbable polymer coating over a surface of an implantable device (e.g., a stent).
- Endothelial progenitor cells refer to primitive cells made in the bone marrow that can enter the bloodstream and go to areas of blood vessel injury to help repair the damage. Endothelial progenitor cells circulate in adult human peripheral blood and are mobilized from bone marrow by cytokines, growth factors, and ischemic conditions. Vascular injury is repaired by both angiogenesis and vasculogenesis mechanisms. Circulating endothelial progenitor cells contribute to repair of injured blood vessels mainly via a vasculogenesis mechanism.
- the prohealing drug or agent can be an endothelial cell (EDC)-binding agent.
- EDC-binding agent can be a protein, peptide or antibody, which can be, e.g., one of collagen type 1, a 23 peptide fragment known as single chain Fv fragment (scFv A5), a junction membrane protein vascular endothelial (VE)-cadherin, and combinations thereof.
- Collagen type 1 when bound to osteopontin, has been shown to promote adhesion of endothelial cells and modulate their viability by the down regulation of apoptotic pathways.
- S. M. Martin et al., J. Biomed. Mater. Res., 70A:10-19 (2004).
- Endothelial cells can be selectively targeted (for the targeted delivery of immunoliposomes) using scFv A5.
- scFv A5. T. Volkel, et al., Biochimica et Biophysica Acta, 1663:158-166 (2004).
- Junction membrane protein vascular endothelial (VE)-cadherin has been shown to bind to endothelial cells and down regulate apoptosis of the endothelial cells.
- VE vascular endothelial
- the EDC-binding agent can be the active fragment of osteopontin, (Asp-Val-Asp-Val-Pro-Asp-Gly-Asp-Ser-Leu-Ala-Try-Gly).
- Other EDC-binding agents include, but are not limited to, EPC (epithelial cell) antibodies, RGD peptide sequences, RGD mimetics, and combinations thereof.
- the prohealing drug or agent may be a substance or agent that attracts and binds endothelial progenitor cells.
- Representative substances or agents that attract and bind endothelial progenitor cells include antibodies such as CD-34, CD-133 and vegf type 2 receptor.
- An agent that attracts and binds endothelial progenitor cells can include a polymer having nitric oxide donor groups.
- biologically active agents are listed by way of example and are not meant to be limiting. Other biologically active agents that are currently available or that may be developed in the future are equally applicable.
- the composition of the invention comprises at least one biologically active agent selected from the group consisting of paclitaxel, docetaxel, estradiol, nitric oxide donors, super oxide dismutases, super oxide dismutase mimics, 4-amino-2,2,6,6-tetramethylpiperidine-1-oxyl (4-amino-TEMPO), tacrolimus, dexamethasone, rapamycin, rapamycin derivatives, 40-O-(2-hydroxy)ethyl-rapamycin (everolimus), 40-O-(2-ethoxy)ethyl-rapamycin (biolimus), 40-O-(3-hydroxy)propyl-rapamycin, 40-O-[2-(2-hydroxy)ethoxy]ethyl-rapamycin, 40-O-tetrazole-raparnycin, 40-epi-(N1-tetrazolyl)-
- the at least one biologically active agent specifically cannot be one or more of any of the bioactive drugs or agents described herein.
- inventive composition comprising a biodegradable ABA′ triblock copolymer may be used to make a material of which an implantable device is formed.
- a material may comprise any combination of embodiments of the inventive composition described herein.
- an embodiment of the invention is drawn to a material containing any combination of embodiments of the composition comprising a biodegradable ABA′ triblock copolymer.
- the composition forming the material may optionally have at least one dihydroxyaryl group conjugated to the polymer ends of the triblock copolymer and optionally contain at least one biocompatible moiety, at least one additional biologically absorbable polymer, and/or at least one biologically active agent.
- the material of the invention may be used to make a portion of an implantable device or the whole device itself. Moreover, the material may be used to make a coating that is disposed over at least a portion of an implantable device.
- a embodiment of the invention is directed to a coating containing any combination of embodiments of the composition comprising a biodegradable ABA′ triblock copolymer.
- the composition forming the coating may optionally have at least one dihydroxyaryl group conjugated to the polymer ends of the triblock copolymer and optionally contain at least one biocompatible moiety, at least one additional biologically absorbable polymer, and/or at least one biologically active agent.
- the coating may have a variety of thickness and biodegradation rates.
- the coating has a thickness of ⁇ bout 30 micron, or ⁇ about 20 micron, or ⁇ about 10 micron.
- the biodegradation rate of the coating is characterized by loss of about 100% mass within about two years, or loss of about 100% mass within about 12 months, or loss of at least about 70% mass within about six months.
- inventive material containing any combination of embodiments of the composition comprising a biodegradable ABA′ copolymer may be used to form an implantable device.
- one embodiment of the invention optionally in combination with one or more other embodiments described herein, is drawn to an implantable device formed of a material containing any combination of embodiments of the composition comprising a biodegradable ABA′ copolymer.
- the implantable device may be formed of a material comprising a composition that optionally has at least one dihydroxyaryl group conjugated to the polymer ends of the triblock copolymer and optionally contains at least one biocompatible moiety, at least one additional biologically absorbable polymer, and/or at least one biologically active agent.
- a portion of the implantable device or the whole device itself may be formed of the material containing any combination of embodiments of the composition comprising a biodegradable ABA′ copolymer. Further, at least a portion of the implantable device may be coated by a coating containing any combination of embodiments of the composition comprising a biodegradable ABA′ copolymer.
- an embodiment of the invention is directed to an implantable device formed of a coating containing any combination of embodiments of the composition comprising a biodegradable ABA′ copolymer.
- the implantable device may be formed of a coating comprising a composition that optionally has at least one dihydroxyaryl group conjugated to the polymer ends of the triblock copolymer and optionally contains at least one biocompatible moiety, at least one additional biologically absorbable polymer, and/or at least one biologically active agent.
- the implantable device may be formed of a coating that may have a variety of thickness and biodegradation rates. In some embodiments, optionally in combination with one or more other embodiments described herein, the implantable device is formed of a coating that has a thickness of ⁇ about 30 micron, or ⁇ about 20 micron, or ⁇ about 10 micron. In further embodiments, optionally in combination with one or more other embodiments described herein, the implantable device is formed of a coating whose biodegradation rate is characterized by loss of about 100% mass within about two years, or loss of about 100% mass within about 12 months, or loss of at least about 70% mass within about six months.
- the present invention also encompasses implantable devices formed of bioabsorbable and/or biostable polymers.
- implantable devices formed of bioabsorbable and/or biostable polymers.
- a portion of the device or the whole device itself can be formed of such polymers and any other substances described herein.
- implantable devices can be formed of the inventive material or coating.
- implantable devices include, but are not limited to, stents (e.g., coronary stents and peripheral stents), grafts (e.g., aortic grafts, arterio-venous grafts and by-pass grafts), stent-grafts, catheters, leads and electrodes for pacemakers and defibrillators, endocardial leads (e.g., FINELINE and ENDOTAK, available from Abbott Vascular, Santa Clara, Calif.), clips (e.g., anastomotic clips), shunts (e.g., cerebrospinal fluid and axius coronary shunts), closure devices (e.g., arterial and patent foramen ovale closure devices), and valves (e.g., artificial heart valves).
- stents e.g., coronary stents and peripheral stents
- grafts e.g
- the implantable device is selected from the group consisting of stents, grafts, stent-grafts, catheters, leads and electrodes, clips, shunts, closure devices, and valves.
- the implantable device is a stent.
- the stent may be balloon-expandable or self-expandable.
- the stent may be intended for any vessel in the body, e.g., neurological, carotid, vein graft, coronary, aortic renal, iliac, femoral, popliteal vasculature and urethral passages.
- the underlying structure of the implantable device can be of virtually any design.
- the device can be made of a metallic material or an alloy such as, but not limited to, cobalt-chromium alloys (e.g., ELGILOY), “L-605”, stainless steel (316L), “MP35N,” “MP20N,” ELASTINITE (Nitinol), tantalum, tantalum-based alloys, nickel-titanium alloys, platinum, platinum-based alloys (e.g., platinum-iridium alloy), iridium, gold, magnesium, titanium, titanium-based alloys, zirconium-based alloys, or combinations thereof.
- L-605 is a trade name for an alloy of cobalt, chromium, tungsten, nickel and iron available as Haynes 25 from Haynes International (Kokomo, Ind.). “L-605” consists of 51% cobalt, 20% chromium, 15% tungsten, 10% nickel and 3% iron. “MP35N” and “MP20N” are trade names for alloys of cobalt, nickel, chromium and molybdenum available from Standard Press Steel Co. (Jenkintown, Pa.). “MP35N” consists of 35% cobalt, 35% nickel, 20% chromium and 10% molybdenum. “MP20N” consists of 50% cobalt, 20% nickel, 20% chromium and 10% molybdenum.
- a coating for an implantable device can be a multi-layer structure that may include any of the following four layers or combination thereof:
- Each layer of a stent coating can be disposed over the stent by dissolving the polymer or a blend of polymers in a solvent, or a mixture of solvents, and disposing the resulting polymer solution over the stent by spraying or immersing the stent in the solution. After the solution has been disposed over the stent, the coating is dried by allowing the solvent to evaporate. The process of drying can be accelerated if the drying is conducted at an elevated temperature.
- the complete stent coating can be optionally annealed at a temperature between about 40° C. and about 150° C. for a period of time between about 5 minutes and about 60 minutes, if desired, to improve the thermodynamic stability of the coating.
- the drug can be combined with the polymer solution that is disposed over the stent as described above.
- a polymer-free reservoir can be made.
- the drug can be dissolved in a suitable solvent or mixture of solvents, and the resulting drug solution can be disposed over the stent by spraying or immersing the stent in the drug-containing solution.
- the drug can be introduced as a colloid system, such as a suspension in an appropriate solvent phase.
- the drug can be dispersed in the solvent phase using conventional techniques used in colloid chemistry.
- solvent to form the solvent phase of the suspension, as well as the quantity of the drug to be dispersed in the solvent phase.
- a surfactant may be added to stabilize the suspension.
- the suspension can be mixed with a polymer solution and the mixture can be disposed over the stent as described above. Alternatively, the drug suspension can be disposed over the stent without being mixed with the polymer solution.
- the drug-polymer layer can be applied directly onto at least a part of the stent surface to serve as a reservoir for at least one bioactive agent or drug that is incorporated into the reservoir layer.
- the optional primer layer can be applied between the stent and the reservoir to improve the adhesion of the drug-polymer layer to the stent.
- the optional topcoat layer can be applied over at least a portion of the reservoir layer and serves as a rate-limiting membrane that helps to control the rate of release of the drug. In one embodiment, the topcoat layer can be essentially free from any bioactive agents or drugs. If the topcoat layer is used, the optional finishing coat layer can be applied over at least a portion of the topcoat layer for further control of the drug-release rate and for improving the biocompatibility of the coating. Without the topcoat layer, the finishing coat layer can be deposited directly on the reservoir layer.
- the process of the release of a drug from a coating having both topcoat and finishing coat layers includes at least three steps. First, the drug is absorbed by the polymer of the topcoat layer on the drug-polymer layer/topcoat layer interface. Next, the drug diffuses through the topcoat layer using the void volume between the macromolecules of the topcoat layer polymer as pathways for migration. Next, the drug arrives at the topcoat layer/finishing layer interface. Finally, the drug diffuses through the finishing coat layer in a similar fashion, arrives at the outer surface of the finishing coat layer, and desorbs from the outer surface. At this point, the drug is released into the surrounding tissue. Consequently, a combination of the topcoat and finishing coat layers, if used, can serve as a rate-limiting barrier. The drug can be released through the degradation, dissolution, and/or erosion of the layer.
- any or all of the layers of the stent coating can be made of a biologically degradable, erodable, absorbable, and/or resorbable polymer.
- the outermost layer of the coating can be limited to such a polymer.
- the outermost layer is the finishing coat layer, which is made of a polymer that is biologically degradable, erodable, absorbable, and/or resorbable.
- the remaining layers i.e., the primer, the reservoir layer and the topcoat layer
- the polymer may be the same or different in each layer.
- the topcoat layer can be the outermost layer and is made of a biologically degradable polymer.
- the remaining layers i.e., the primer and the reservoir layer
- the polymer may be the same or different in each of the three layers.
- the stent coating could have only two layers, the primer and the reservoir.
- the reservoir is the outermost layer of the stent coating and is made of a biologically degradable polymer.
- the primer optionally can also be fabricated of a biologically degradable polymer.
- the two layers may be made from the same or different materials.
- a stent coating can be engineered to provide either fast or slow release of a drug, as desired.
- fast release may be recommended for stent coatings loaded with antimigratory drugs, which often need to be released within 1 to 2 weeks.
- slow release may be desired (e.g., up to 30-day release time).
- Any layer of a stent coating may contain any amount of the at least one additional biologically absorbable polymer described above, or a blend of more than one such polymer. If less than 100% of the layer is made of the bioabsorbable polymer(s), other alternative polymers can comprise the balance.
- polyacrylates e.g., poly(butyl methacrylate), poly(ethyl methacrylate), poly(ethyl methacrylate-co-butyl methacrylate), poly(acrylonitrile), poly(ethylene-co-methyl methacrylate), poly(acrylonitrile-co-styrene) and poly(cyanoacrylates); fluorinated polymers and/or copolymers, e.g., poly(vinylidene fluoride) and poly(vinylidene fluoride-co-hexafluoro propylene); poly(N-vinyl pyrrolidone); polydioxanone; polyorthoester; polyanhydride; poly(glycolic acid); poly(glycolic acid-co-trimethylene carbonate); polyphosphoester; polyphosphoester urethane; poly(amino acids); poly(trimethylene carbonate); poly(
- the method comprises forming the implantable device of a material containing any combination of embodiments of the composition comprising a biodegradable ABA′ copolymer.
- the method comprises forming the implantable device of a material comprising a composition that optionally has at least one dihydroxyaryl group conjugated to the polymer ends of the triblock copolymer and optionally contains at least one biocompatible moiety, at least one additional biologically absorbable polymer, and/or at least one biologically active agent.
- a portion of the implantable device or the whole device itself may be formed of the material containing any combination of embodiments of the composition comprising a biodegradable ABA′ copolymer.
- the method may comprise depositing over at least a portion of the implantable device a coating containing any combination of embodiments of the composition comprising a biodegradable ABA′ copolymer.
- the method comprises disposing over at least a portion of an implantable device a coating containing any combination of embodiments of the composition comprising a biodegradable ABA′ copolymer.
- the method comprises disposing over at least a portion of an implantable device a coating comprising a composition that optionally has at least one dihydroxyaryl group conjugated to the polymer ends of the triblock copolymer and optionally contains at least one biocompatible moiety, at least one additional biologically absorbable polymer, and/or at least one biologically active agent.
- the method may deposit a coating having a variety of thickness over an implantable device.
- the method deposits over at least a portion of the implantable device a coating that has a thickness of about 30 micron, or ⁇ about 20 micron, or ⁇ about 10 micron.
- the method is used to fabricate an implantable device selected from the group consisting of stents, grafts, stent-grafts, catheters, leads and electrodes, clips, shunts, closure devices, and valves.
- the method is used to fabricate a stent.
- the triblock copolymer of the invention may be formed into a polymer construct, such as a tube or sheet that can be rolled or bonded to form a construct such as a tube.
- An implantable device may then be fabricated from the construct.
- a stent can be fabricated from a tube by laser machining a pattern into the tube.
- a polymer construct may be formed from the polymeric material of the invention using an injection-molding apparatus.
- EVAL ethylene vinyl alcohol copolymer
- poly(vinylidene fluoride-co-hexafluoropropylene) e.g., SOLEF 2150
- An implantable device formed of a material or coating containing any combination of embodiments of the composition comprising a biodegradable ABA′ copolymer can be used to treat, prevent or diagnose conditions or disorders.
- conditions or disorders include, but are not limited to, atherosclerosis, thrombosis, restenosis, hemorrhage, vascular dissection, vascular perforation, vascular aneurysm, vulnerable plaque, chronic total occlusion, patent foramen ovale, claudication, anastomotic proliferation of vein and artificial grafts, bile duct obstruction, ureter obstruction and tumor obstruction.
- an embodiment of the invention is drawn to a method of treating, preventing or diagnosing a condition or disorder in a patient, comprising implanting in the patient an implantable device formed of a material or coating containing any combination of embodiments of the composition comprising a biodegradable ABA′ copolymer.
- the implantable device may be formed of a material or coating comprising a composition that optionally has at least one dihydroxyaryl group conjugated to the polymer ends of the triblock copolymer and optionally contains at least one biocompatible moiety, at least one additional biologically absorbable polymer, and/or at least one biologically active agent.
- the implantable device is formed of a material or coating containing at least one biologically active agent selected from the group consisting of paclitaxel, docetaxel, estradiol, nitric oxide donors, super oxide dismutases, super oxide dismutase mimics, 4-amino-2,2,6,6-tetramethylpiperidine-1-oxyl (4-amino-TEMPO), tacrolimus, dexamethasone, rapamycin, rapamycin derivatives, 40-O-(2-hydroxy)ethyl-rapamycin (everolimus), 40-O-(2-ethoxy)ethyl-rapamycin (biolimus), 40-O-(3-hydroxy)propyl-rapamycin, 40-O-[2-(2-hydroxy)ethoxy]ethyl-rapamycin, 40-O-tetrazole-rapamycin, 40-epi-(N-1-tetrazolyl)-rapamycin (zotarolimus), pimecro
- the implantable device used in the method is selected from the group consisting of stents, grafts, stent-grafts, catheters, leads and electrodes, clips, shunts, closure devices, and valves.
- the implantable device is a stent.
- the condition or disorder treated, prevented or diagnosed by the implantable device is selected from the group consisting of atherosclerosis, thrombosis, restenosis, hemorrhage, vascular dissection, vascular perforation, vascular aneurysm, vulnerable plaque, chronic total occlusion, patent foramen ovale, claudication, anastomotic proliferation of vein and artificial grafts, bile duct obstruction, ureter obstruction and tumor obstruction.
- the triblock copolymers of the invention can be prepared by any method of polymerization known in the art. Methods of polymerization include, but are not limited to, solution-based polymerization and melt-phase polymerization. In solution-based polymerization, all the reactive components involved in the polymerization reaction are dissolved in a solvent.
- the first step generally involves forming a precursor block, e.g., the B block.
- Monomer units of the precursor block, a suitable initiator and a suitable catalyst are added to a suitable solvent to form a polymerization solution.
- monomer units of the second block e.g., the A block, or the A and A′ blocks if these two blocks are the same
- a catalyst which may be the same or different than the catalyst used in the first reaction
- a third reaction to form the A′ block may proceed in a similar manner as the second reaction to form the A block.
- the solvent(s) in the reaction(s) for forming the A and A′ blocks can be selected so that the precursor block is soluble in the solvent(s) for the second reaction and the AB diblock is soluble in the solvent(s) for the third reaction, which would facilitate copolymerization of the precursor block and AB diblock with the added units of the A block and the A′ block, respectively.
- the B block is formed first in the synthesis of a triblock copolymer.
- Triblock copolymers can be synthesized by standard methods known to those having ordinary skill in the art, e.g., by ring-opening polymerization (ROP) with the corresponding monomers of the blocks.
- ROP can be catalyzed by an organic or inorganic acid (including a Lewis acid), an organic or inorganic base (including a Lewis base), an organometallic reagent, and/or heat, if necessary.
- One method of synthesizing A-B-A′ triblock copolymers of the invention is to conduct ring-opening polymerization (ROP) with the corresponding monomer(s) of the A, B and A′ blocks.
- ROP ring-opening polymerization
- triblock copolymers in which the A and A′ blocks are the same may be produced by performing ROP with the corresponding monomer(s) of the B block, and then performing ROP with the corresponding monomer(s) of the A and A′ blocks.
- An initiating compound containing two active end groups is employed to initiate ROP with the first monomer of the B block.
- the two active end groups on the initiating compound are independently a hydroxyl, amino or thiol group.
- A-B-A′ triblock copolymers in which the A and A′ blocks are different may be synthesized by:
- the initiating compounds employed in the synthesis of the triblock copolymers have at least one active end group that is a hydroxyl, amino or thiol group.
- the initiating compound is a diol, in which one of the hydroxyl end groups may optionally be protected.
- the initiating compound is a diamine, in which one of the amino end groups may optionally be protected.
- the initiating compound is a dithiol, in which one of the thiol end groups may optionally be protected.
- the diamino, dithiol or dihydroxy initiating compound is C 2 -C 24 and contains an optionally substituted aliphatic, heteroaliphatic, cycloaliphatic, heterocycloaliphatic, aromatic or heteroaromatic group, or a combination thereof.
- the initiating compound is a diol selected from diethylene glycol, triethylene glycol, tetraethylene glycol, poly(ethylene glycol), poly(propylene glycol), poly(tetramethylene glycol), and poly(caprolactone) diol.
- A-B-A′ triblock copolymers in which the A and A′ blocks are the same, via ROP is illustrated by the synthesis of poly(D,L-lactide-co-glycolide-bl-trimethylene carbonate-bl-glycolide-co-D,L-lactide) via ROP in Scheme 1 below.
- 1,6-hexanediol is employed to initiate ROP with TMC.
- the resulting bis(hydroxyl)-terminated B block, PTMC can then be used to initiate ROP with glycolide, leading to the formation of bis(hydroxyl)-terminated PGA-bl-PTMC-bl-PGA.
- the A and A′ blocks are further elaborated via ROP of this intermediate with a different type of monomer, D,L-lactide, resulting in the triblock copolymer, poly(D,L-lactide-co-glycolide)-block-poly-(trimethylene carbonate)-block-poly(glycolide-co-D,L-lactide).
- the A and A′ blocks are the same (i.e., poly(glycolide-co-D,L-lactide)), and m, n and p each independently are integers from about 5 to about 5,000.
- a person of ordinary skill in the art would understand that the synthetic procedure in the above example could also be modified to generate poly(D,L-lactide-ran-glycolide)-block-poly-(trimethylene carbonate)-block-poly(glycolide-ran-D,L-lactide) by conducting ROP in the presence of glycolide and D,L-lactide in the same pot.
- triblock copolymers are often done neat, in the absence of a solvent. However, the blocks are not always miscible with each other. For example, in the melt the glycolide may not dissolve in the PTMC polymer. In such a case, polymerization would be conducted in a solvent. If done properly, the intermediate bis(hydroxyl)-terminated PTMC polymer would not need to be isolated and could be used to initiate the next ROP with glycolide.
- a strong or exotic solvent may be needed to initially dissolve the monomer(s).
- a solvent can usually be employed to dissolve a mixture of monomers into a mixture of monomers and then be evaporated off before an initiating catalyst is added to start the polymerization.
- the soft B block may also assist in the dissolution of the monomers of the A and A′ blocks.
- various organo and organometallic catalysts may influence the structure of the polymer by providing different release kinetics and minimize or maximize the polymerization rate of the various monomers incorporated into the A, B or A′ block.
- compositions comprising an A-B-A′ triblock copolymer, whether the A and A′ blocks are the same or different, may be prepared by optionally:
- the at least one dihydroxyaryl group may contain, e.g., an ortho-dihydroxyphenyl moiety such as 1,2-dihydroxyphenyl and 3,4-dihydroxyphenyl.
- 3,4-Dihydroxyphenyl-containing compounds include, e.g., dopamine and 3,4-dihydroxyhydrocinnamic acid. Dopamine could be conjugated to hydroxyl end groups of a triblock copolymer via coupling with 1,1′-carbonyldiimidazole.
- 3,4-Dihydroxy-hydrocinnamic acid could be conjugated to hydroxyl end groups by conversion of the cinnamic acid to the N-succidimyl ester or by use of dicyclohexylcarbodiimide (DCC) and 4-(dimethylamino)pyridinium (DPTS).
- DCC dicyclohexylcarbodiimide
- DPTS 4-(dimethylamino)pyridinium
- conjugation of the cinnamic acid could be effected via a Mitsunobu reaction using triphenylphosphine and diethyl azodicarboxylate (DEAD) or diisopropyl azodicarboxylate (DIAD).
- a flame-dried, three-neck 250 ml round-bottom flask is charged with 46.41 g (0.455 mole) trimethylene carbonate, 0.123 g (1.16 mmol) distilled diethylene glycol, and 0.053 ml of stannous octoate (0.33 M in toluene) (60,000:1 molar ratio monomer:catalyst).
- the flask is equipped with a flame-dried mechanical stirrer and adapter for argon purge and vacuum.
- the reaction vessel is purged by evacuating the flask, followed by venting with argon; this is repeated three times.
- the reaction flask, under an argon pressure of one atmosphere is heated to 190° C. and maintained at this temperature for about 16 hours with slow stirring.
- a flame-dried, three-neck, 250 ml round-bottom flask is charged with 36.0 g (0.316 mole) caprolactone and 24.0 g (0.207 mole) glycolide.
- the flask is equipped with a flame-dried mechanical stirrer and adapter for argon purge and vacuum.
- the contents are heated to 120° C. and stirred under vacuum for four hours.
- 0.11 gm (1.4 mmol) distilled diethylene glycol, and 0.097 ml of stannous octoate (0.33 M in toluene) (25,000:1 molar ratio monomer:catalyst) are added.
- the reaction vessel is purged by evacuating the flask followed by venting with argon; this is repeated three times.
- the reaction flask, under an argon pressure of one atmosphere, is heated to 180° C. and maintained at this temperature for about 24 hours with slow stirring.
- an optional primer coating is applied to a stent.
- a primer solution containing between about 0.1 mass % and about 15 mass %, (e.g., about 2.0 mass %) of the copolymer of Example 1 or 2, and the balance being a solvent mixture of chloroform and 1,1,1-trichloroethane (having about 50 mass % of chloroform and about 50 mass % of 1,1,1-trichloroethane) is prepared.
- the solution is applied onto the stent to form a primer layer.
- a spray apparatus e.g., Sono-Tek MicroMist spray nozzle, manufactured by Sono-Tek Corp. of Milton, N.Y.
- the spray apparatus is an ultrasonic atomizer with a gas entrainment stream.
- a syringe pump is used to supply the coating solution to the nozzle.
- the composition is atomized by ultrasonic energy and applied to the stent surfaces.
- a useful nozzle-to-stent distance is about 20 mm to about 40 mm at an ultrasonic power of about one watt to about two watts.
- the stent is optionally rotated about its longitudinal axis, at a speed of about 100 to about 600 rpm, e.g., about 400 rpm.
- the stent is also linearly moved along the same axis during the application.
- the primer solution is applied to a 3.0 ⁇ 12 mm VISIONTM stent (available from Abbott Vascular Corp.) in a series of 20-second passes, to deposit, e.g., 20 ⁇ g of coating per spray pass. Between the spray passes, the stent is allowed to dry for about 10 seconds to about 30 seconds at ambient temperature. Four spray passes can be applied, followed by baking the primer layer at about 80° C. for about 1 hour. As a result, a primer layer can be formed having a solids content of about 80 ⁇ g.
- solids means the amount of the dry residue deposited on the stent after all volatile organic compounds (e.g., the solvent) have been removed.
- the drug-containing formulation is applied to the stent in a manner similar to the application of the copolymer primer layer.
- the process results in the formation of a drug-polymer reservoir layer having a solids content between about 30 ⁇ g and about 750 ⁇ g, (e.g., about 175 ⁇ g) and a drug content of between about 10 ⁇ g and about 250 ⁇ g, (e.g., about 55 ⁇ g).
- the coating is baked at 50° C. for two hours to remove any remaining solvent.
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Priority Applications (7)
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US11/824,011 US20090004243A1 (en) | 2007-06-29 | 2007-06-29 | Biodegradable triblock copolymers for implantable devices |
JP2010514912A JP5585841B2 (ja) | 2007-06-29 | 2008-05-22 | ステントのための生体分解性トリブロックコポリマー |
PCT/US2008/064585 WO2009005909A2 (en) | 2007-06-29 | 2008-05-22 | Biodegradable triblock copolymers for implantable devices |
EP08769646A EP2173398B1 (en) | 2007-06-29 | 2008-05-22 | Biodegradable triblock copolymers for implantable devices |
ES08769646T ES2400252T3 (es) | 2007-06-29 | 2008-05-22 | Copolímeros tribloque biodegradables para dispositivos implantables |
US14/081,287 US9090745B2 (en) | 2007-06-29 | 2013-11-15 | Biodegradable triblock copolymers for implantable devices |
US14/752,637 US9468707B2 (en) | 2007-06-29 | 2015-06-26 | Biodegradable triblock copolymers for implantable devices |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
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US11/824,011 US20090004243A1 (en) | 2007-06-29 | 2007-06-29 | Biodegradable triblock copolymers for implantable devices |
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US14/081,287 Continuation US9090745B2 (en) | 2007-06-29 | 2013-11-15 | Biodegradable triblock copolymers for implantable devices |
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US20090004243A1 true US20090004243A1 (en) | 2009-01-01 |
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US14/081,287 Expired - Fee Related US9090745B2 (en) | 2007-06-29 | 2013-11-15 | Biodegradable triblock copolymers for implantable devices |
US14/752,637 Expired - Fee Related US9468707B2 (en) | 2007-06-29 | 2015-06-26 | Biodegradable triblock copolymers for implantable devices |
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Application Number | Title | Priority Date | Filing Date |
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US14/081,287 Expired - Fee Related US9090745B2 (en) | 2007-06-29 | 2013-11-15 | Biodegradable triblock copolymers for implantable devices |
US14/752,637 Expired - Fee Related US9468707B2 (en) | 2007-06-29 | 2015-06-26 | Biodegradable triblock copolymers for implantable devices |
Country Status (5)
Country | Link |
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US (3) | US20090004243A1 (es) |
EP (1) | EP2173398B1 (es) |
JP (1) | JP5585841B2 (es) |
ES (1) | ES2400252T3 (es) |
WO (1) | WO2009005909A2 (es) |
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EP2173398B1 (en) | 2012-11-21 |
US20150374885A1 (en) | 2015-12-31 |
JP5585841B2 (ja) | 2014-09-10 |
ES2400252T3 (es) | 2013-04-08 |
JP2010532216A (ja) | 2010-10-07 |
EP2173398A2 (en) | 2010-04-14 |
US9090745B2 (en) | 2015-07-28 |
US20140072609A1 (en) | 2014-03-13 |
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WO2009005909A2 (en) | 2009-01-08 |
US9468707B2 (en) | 2016-10-18 |
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