Patent Grant
8871883
1. Field of the Invention
This invention is directed to coatings for implantable medical devices, such as drug eluting vascular stents.
2. Description of the State of the Art
Percutaneous transluminal coronary angioplasty (PTCA) is a procedure for treating heart disease. A catheter assembly having a balloon portion is introduced percutaneously into the cardiovascular system of a patient via the brachial or femoral artery. The catheter assembly is advanced through the coronary vasculature until the balloon portion is positioned across the occlusive lesion. Once in position across the lesion, the balloon is inflated to a predetermined size to radially compress against the atherosclerotic plaque of the lesion to remodel the lumen wall. The balloon is then deflated to a smaller profile to allow the catheter to be withdrawn from the patient's vasculature.
A problem associated with the above procedure includes formation of intimal flaps or torn arterial linings which can collapse and occlude the conduit after the balloon is deflated. Moreover, thrombosis and restenosis of the artery may develop over several months after the procedure, which may require another angioplasty procedure or a surgical by-pass operation. To reduce the partial or total occlusion of the artery by the collapse of arterial lining and to reduce the chance of the development of thrombosis and restenosis, a stent is implanted in the lumen to maintain the vascular patency.
Stents are used not only as a mechanical intervention but also as a vehicle for providing biological therapy. As a mechanical intervention, stents act as scaffoldings, functioning to physically hold open and, if desired, to expand the wall of the passageway. Typically, stents are capable of being compressed, so that they can be inserted through small vessels via catheters, and then expanded to a larger diameter once they are at the desired location. Examples in patent literature disclosing stents which have been applied in PTCA procedures include stents illustrated in U.S. Pat. No. 4,733,665 issued to Palmaz, U.S. Pat. No. 4,800,882 issued to Gianturco, and U.S. Pat. No. 4,886,062 issued to Wiktor.
Biological therapy can be achieved by medicating the stents. Medicated stents provide for the local administration of a therapeutic substance at the diseased site. In order to provide an efficacious concentration to the treated site, systemic administration of such medication often produces adverse or toxic side effects for the patient. Local delivery is a preferred method of treatment in that smaller total levels of medication are administered in comparison to systemic dosages, but are concentrated at a specific site. Local delivery thus produces fewer side effects and achieves more favorable results. One proposed method for medicating stents involves the use of a polymeric carrier coated onto the surface of a stent. A solution which includes a solvent, a polymer dissolved in the solvent, and a therapeutic substance dispersed in the blend is applied to the stent. The solvent is allowed to evaporate, leaving on the stent surface a coating of the polymer and the therapeutic substance impregnated in the polymer. Once the stent has been implanted at the treatment site, the therapeutic substance has a sustained release profile from the polymer.
Although local administration of therapeutic agents via stents has shown favorable results in reducing restenosis, improvements can be made to the coatings, more particularly improvements of the biological compatibility of the coatings. The embodiments of the present invention provide for biologically compatible polymers and combination of polymers for coating stents and other implantable medical devices.
A coating for an implantable medical device is provided, the coating includes a copolymer, the copolymer comprising at least one biologically compatible structural moiety and at least one biologically active moiety. The structural moiety can comprise unsubstituted or substituted acrylates, and can be derived from methyl methacrylate, n-butyl methacrylate, lauryl methacrylate, 2-hydroxyethyl methacrylate, or styrene. The biologically active moiety can be derived from superoxide dismutase-mimetics, diazenium diolate type nitric oxide donors, polycationic peptides, polysaccharides, for example, heparin or heparin derivatives, pyrrolidone, poly(ethylene glycol), vitamin E, sulfonated dextrane, 13-phenoxyetanol, N,N-dimethylamino-2-ethanol, mannose-6-phosphate, sulfonic acid and derivatives of sulfonic acid such as propanesulfonic acid, 2-methyl-1 -propanesulfonic acid, benzenesulfonic acid, and 3-methoxy-2-hydroxypropanesulfonic acid. The copolymer can be a block copolymer made by living free radical copolymerization of plurality of monomers with initiation, transfer, termination (iniferter) of the living macro-chains.
A method for coating an implantable medical device is disclosed, the method comprising depositing a copolymer comprising at least one biologically compatible structural moiety and at least one biologically active moiety onto the device.
A biologically compatible copolymer is disclosed, the copolymer having a formula
wherein m1, n1, p1, r1, m2, n2, p2, and r2 is each, independently, an integer and m1≧0, n1≧0, p1≧0, r1>0, m2≧0, n2>0, p2≧0, r2>0;
with the provision that if m1=0, then p1>0; or if p1=0, then m1>0; or if m2=0, then p2>0; or if p2=0, then m2>0;
X, Y, and Z can be each, independently, hydrogen or an alkyl group; M and T can be each, independently, an ester group or a substituted or unsubstituted aryl group; and Q is a biologically active moiety.
A coating for an implantable medical device, such as a stent, according to one embodiment of the present invention, can include an optional primer layer, a drug-polymer layer (also referred to as “reservoir” or “reservoir layer”) or alternatively a polymer free drug layer, and an optional topcoat layer. The drug-polymer layer serves as a reservoir for the drug. The reservoir layer or the polymer free drug layer can be applied directly onto the stent surface. The optional primer layer can be applied on the stent surface to improve the adhesion of the drug-polymer layer or the polymer free drug layer to the stent. The optional topcoat layer, which can be essentially free from any drugs, serves as a rate limiting membrane which helps to control the rate of release of the drug.
According to embodiments of the present invention, biologically compatible copolymers can be used to fabricate the reservoir layer and the optional primer and topcoat layers. To fabricate the coating, the copolymer can be dissolved in a suitable solvent and the solution can be applied onto a stent, for example, by spraying. A variety of solvents or blends thereof can used. Those having ordinary skill in the art can select a suitable solvent or a blend of solvents depending on particular copolymer that is used for making the stent coating. The solvent is allowed to evaporate leaving a coating adhered to the stent. To accelerate the removal of the solvent, the coated stent can be baked.
The biologically compatible copolymers can be either random copolymers or block copolymers. The term “random copolymer” is defined in accordance with terminology used by the International Union of Pure and Applied Chemistry (IUPAC). The IUPAC defines a random copolymer as a copolymer consisting of macromolecules in which the probability of finding a given monomeric unit at any given site in the chain is independent of the nature of the adjacent units. In a random copolymer, the sequence distribution of monomeric units follows Bernoullian statistics.
The term “block copolymer” used in the present invention is defined as a copolymer containing a linear arrangement of blocks, a block being defined as a portion of a polymer molecule in which the monomeric units have at least one constitutional or configurational feature absent from the adjacent portions. For example, a block copolymer of moiety A and moiety B may be written as -A-A-A-B-B-B-B-. Such block copolymer is often referred to as a “AB block copolymer.” The blocks need not be linked on the ends, since the individual blocks are usually long enough to be considered polymers in their own right. The AB block copolymer can be, accordingly, named poly A-block-poly B.
The term “block copolymer” is intended to broadly include two or more types of blocks such as tri-blocks, tetra-blocks, and so on. In addition to AB block copolymers, variations of other available block copolymers include ABA block copolymers (-A-A-A-B-B-B-A-A-A-), ABCBA block copolymers (-A-A-A-B-B-B-C-C-C-B-B-B-B-A-A-A-), ABC block copolymers (-A-A-A-B-B-B-C-C-C-), etc.
Either random copolymers or block copolymers that can be used to fabricate a coating or a layer of a stent coating can include at least one biologically compatible structural moiety and at least one biologically active moiety. For example, in case of random copolymers, some constituent units of the copolymers can include the biologically compatible moiety while other constituent units can include the biologically active moiety. In case of AB block copolymers, either moiety A or moiety B can be a structural moiety, and the other moiety can be a biologically active moiety. As another example, for an ABC block copolymer, either moiety A, B, or C, or any two of A, B, and C can be a structural moiety or moieties, while the remaining moiety or moieties can be a biologically active moiety or moieties.
In general, one example of a structure of block copolymers that can be used can be illustrated by formula (I):
wherein:
(a) m1, n1, p1, r1, m2, n2, p2, and r2 are all integers, wherein m1≧0, n1>0, p1≧0, r1>0, m2≧0, n2>0, p2≧0, r2>0;
each member r1 and r2, etc. of the sequence r1, r2 . . . can be the same or different; m1 and m2 can be the same or different; n1 and n2 can be the same or different; and p1 and p2 can be the same or different;
(b) X, Y, and Z is each, independently, hydrogen or an alkyl group, for example, methyl group, and X, Y, and Z can be the same or different;
(c) M and T is each, independently, an ester group —C(O)—OR, or a substituted or unsubstituted aryl group, where the substitutents in the aryl group include halogens, hydroxyl, carboxyl or amino groups, and M and T can be the same or different;
(d) R in the ester group is a straight-chained or branched substituted or unsubstituted alkyl group, or substituted or unsubstituted aryl group, where the substitutents in the aryl group include halogens, hydroxyl, carboxyl or amino groups; and
(e) Q is a chemical fragment providing the B-units with biologically active properties, which can be attached to the backbone of the block copolymer in a variety of ways, for example via the acyl group or via the methylene bridge.
The structure of a random copolymer is generally similar to the structure of formula (I), except the A-, B-, and C-units in the random copolymer are distributed randomly and not in blocks.
Examples of biologically active fragments that can be incorporated into the random or block copolymer include the fragments derived from superoxide dismutase-mimetics (SODm), diazenium diolate type nitric oxide donors, polycationic peptides, polysaccharides, for example, heparin or heparin derivatives, pyrrolidone, poly(ethylene glycol) (PEG), vitamin E, sulfonated dextrane, β-phenoxyetanol, N,N -dimethylamino-2-ethanol, mannose-6-phosphate, sulfonic acid and derivatives of sulfonic acid such as propanesulfonic acid, 2-methyl- 1-propanesulfonic acid, benzenesulfonic acid, and 3-methoxy-2-hydroxypropanesulfonic acid.
Superoxide dismutase-mimetics are oxidoreductases-based complexes that contain cations of copper, iron, or manganese. SOD-mimetics are major intracellular enzymes that protect the cell against oxygen toxicity by dismutating the radical oxygen superoxide, O2—, to oxygen and hydrogen peroxide. A complex seven-ligand manganese-based SOD,m, manganese(II)dichloro-aminoethylthiolated pentaazatetracyclohexacosatriene (SOD-40470) manufactured by Metaphore Pharmaceuticals, Inc., St. Louis, Missouri is one example of SODm that can be used in preparing the B-units of the block copolymer of formula (I). Other types of SODm can be also used, if desired.
Diazenium diolate type nitric oxide donors are adducts of nitric oxide (NO) with nucleophilic amines. Diazenium diolates, also known as NONOates, are highly biologically compatible and possess valuable medicinal properties. In slightly acidic medium they spontaneously release NO which has excellent therapeutical properties. One example of diazenium diolate that can be used for making the B-units of block copolymers of formula (I) is an aliphatic NONOate 1,3-propanediamine, N-{4-[1-(3-aminopropyl)-2-hydroxy-2-nitrosohydrazino]butyl}-diazen-1-ium-1,2-diolate also known as spermine diazenium diolate (SDD) and having the formula NH2—(CH2)3—N[N+(O)—(N—OH)]—(CH2)4—NH—(CH2)3—NH2. SDD is manufactured by Molecular Probes, Inc., Eugene, Oreg. Alternatively, other diazenium diolate-type NO donors can be used. One example of a suitable alternative diazenium diolate-type NO donor can be 1-{N-methyl-N-[6-(N-methylammonio)hexyl]amino}diazen-1-ium-1,2-diolate having the formula CH3—N+H2—(CH2)6—N(CH3)—N+(O−)═N—O− (MAHMA-NO). Another example of a suitable alternative NONOate can be and Z-1-[N-(2-aminoethyl)-N-(2-ammonioethyl)amino]diazen-1-ium-1,2-diolate having the formula O−—N+[N(CH2—CH2—NH2)CH2—CH2—N+H3]═N—O− (DETA-NO). MAHMA-NO and DETA-NO can be obtained from Cayman Chemical Co., Ann Arbor, Mich.
Examples of suitable polycationic peptides that can be used to make the B-units of the block copolymer of formula (I) include poly(L-arginine), poly(D-arginine), poly(D,L-arginine), poly(L-lysine), poly(D-lysine), poly(δ-guanidino-α-aminobutyric acid), and a racemic mixture of poly(L-arginine) or poly(D-arginine). The terms “poly(L-arginine),” “poly(D-arginine),” “poly(D,L-arginine)” are intended to include L-, D-, and/or D,L-arginine in both its polymeric and oligomeric form. Arginine (R or 2-amino-5-guanidinovaleric acid), is an amino acid having a formula
Polymers and/or oligomers of L-, D-, and/or D, L-arginine that can be used comprise a plurality of repeating monomeric amino acid units connected with peptide bonds, each unit including 1-guanidinopropyl radical having the structure —CH2—CH2—CH2—NH—C(NH2)═NH. For example, a heptamer (R7) (p=7), or a nonamer (R9) (p=9) of L-arginine, can be used.
Heparin is derived from a mixture of sulfated polysaccharide chains based on D-glucosamine and D-glucoronic or L-iduronic acid. “Heparin derivative” is intended to include any functional or structural variation of heparin. Representative variations include heparinoids, heparin having a hydrophobic counter-ion, heparan sulfate, alkali metal or alkaline-earth metal salts of heparin, for example, sodium heparin (also known as hepsal or pularin), potassium heparin (formerly known as clarin), lithium heparin, calcium heparin (also known as calciparine), magnesium heparin (also known as cutheparine), low molecular weight heparin (also known as ardeparin sodium), and blends thereof. Examples of other suitable polysaccharides that can be included in the B-units of the block copolymer of formula (I) are glycosaminoglycans (or mucopolysaccharides) such as keratan sulfate, chondroitin sulfate, dermatan sulfate (also known as chondroitin sulfate B), hyaluronic acid, hyaluronates and blends thereof.
As seen from formula (I), the block copolymer can have three types of units A, B, and C to include block copolymers such as ABC or ABCBA block copolymers (if M and T are different), or two types of units A and B to include block copolymers such as AB or ABA. A-units or C-units or both A- and C-units are the structural moiety or moieties, and B-units are the biologically active moiety.
Block copolymers of formula (I) are expected to evince not only good biocompatibility (e.g., blood compatibility) but also good physical, chemical and mechanical properties suitable for making medicated stent coatings. In addition, due to the presence of the biologically active moiety, the block copolymers are expected to elicit favorable biological effects such as, for example, preventing significant platelet aggregation or inflammation, being non-supportive to smooth muscular cells on the surface, and causing endothelialization (self-healing) on the surface.
The block copolymers used in the coatings of the present invention can also have a potential for synergistic biological effect when used together with at least some drugs used in the reservoir layer or the drug layer of the coating.
The random or block copolymers represented by formula (I) can be obtained by common synthetic methods, for example, by radical copolymerization of monomers forming A-, B-, and/or C-units in bulk, solution, suspension, or emulsion, in the presence of suitable initiators. For preparing the block copolymers, one synthetic method that can be used is the method of living free radical copolymerization with initiation, transfer, termination (iniferter) of the living macro-chains (the iniferter process). The iniferter process utilizes an initiator capable of undergoing thermal and/or photolytic free radical decomposition. Examples of suitable initiators include benzyl-N,N-diethyldithiocarbamate (BDC) or p-xylylene-N,N-diethyldithiocarbamate (XDC). BDC is a derivative of toluene and has the formula C6H5—CH2—S—C(S)—N—(C2H5)2. XDC is a derivative of p-xylene and has the formula (C2H5)2—N—C(S)—S—CH2—C6H4—CH2—S—C(S)—N—(C2H5)2. One possible path of the process of decomposition of an initiator is shown for BDC by scheme (II):
As a result of decomposition of BDC, two types of radicals are generated: the benzylic radical (species A), which undergoes free-radical addition to a monomer molecule initiating polymerization, and the dithiocarbamate radical which terminates by heterolytic radical combination. One possible path of polymerization is shown by reaction schemes (III) and (IV):
In reaction (III), radical A serves as a free-radical initiator reacting with the monomer 1 creating reactive species (2), which can further react with radical B acting as a transfer agent terminator. The reactive species (3) shown by reaction (IV) below, in the presence of monomer and light will undergo heterolytic cleavage yielding the reactive polymer chain and the chain transfer agent, species B. The process is propagated until monomer (1) has been consumed:
Following the completion of polymerization, another monomer can be added and the process analogous to the process described by reactions (II)-(IV) can be repeated, resulting in formation of an AB block copolymer. If a difunctional or multifunctional iniferter is used, an ABA, ABCBA, etc., block or star-block copolymers can be obtained in a similar fashion.
1. Monomers Forming the Structural Moiety
The structural moiety forming the random or block copolymer (A- and/or C-units in formula I) can be derived from unsaturated monomers, for example, unsubstituted or substituted acrylates or a general formula CH2═CX-M, where X is hydrogen or methyl and M is a substituted or unsubstituted aryl group or an ester group O═C(OR)—, where R is an alkyl or aryl.
Some monomers that can be used to form the structural moiety are summarized in Table 1. Other monomers described by the formula CH2═CX-M can be used, if desired.
2. Monomers Forming the Biologically Active Moiety
The biologically active moiety forming the random or block copolymer (B-units in formula I) can be derived from unsaturated monomers and/or oligomers. The choice of the monomer and/or oligomer depends on the kind of biological response that the biologically active moiety is designed to elicit. For example, the biologically active moiety can provide anti-restenotic effect (to treat restenosis), or to ensure better blood compatibility, or to promote cell adhesion.
Examples of the monomers and/or oligomers from which anti-restenotic moiety can be derived include acryloyl-, methacryloyl-, vinyl or allyl-modified adducts of SODm, acryloyl-, methacryloyl-, vinyl or allyl-modified donors of NO (examples of the NO donors include DETA or speramine), and acryloyl-, methacryloyl-, vinyl or allyl-modified polycationic peptides such as poly-L-arginine.
Examples of some particular monomers that can be used to form the biologically active moiety include 2-acrylamido-2-methyl-1-propanesulfonic acid, poly(ethylene glycol) methacrylate, 3-sulfopropyl acrylate, 3-sulfopropyl methacrylate, N-vinylpyrrolidone, vinylsulfonic acid, 4-styrenesulfonic acid and 3-allyloxy-2-hydroxypropanesulfonic acid. All monomers based on sulfonic acid can be either in a form of an acid or in a form of an alkali metal salt (e.g., K+ or Na+).
3. Initiators
For synthesis of random block copolymers, standard initiators of radical homo- or copolymerization can be used, for example, 2,2-dimethoxy-2-phenol acetophenone. Benzophenone can be optionally added to 2,2-dimethoxy-2-phenol acetophenone as a photosensitizer.
Examples of suitable initiators for synthesis of block copolymers include BDC or XDC described above. The initiators can be prepared synthetically. To synthesize BDC, sodium N,N-diethyldithiocarbamate can be combined with benzyl bromide in an anhydrous methanol solution. The ratio between sodium N,N-diethyldithiocarbamate and benzyl bromide can be close to equimolar. The mixture can be stirred for about 24 hours at about room temperature to yield BDC. The process can be completed by evaporating methanol at a reduced pressure and vacuum distillation. The synthesis of XDC is similar, except instead of benzyl bromide, α,α-dibromo-p-xylene is used, and the molar ratio between sodium N,N-diethyldithiocarbamate and α,α-dibromo-p-xylene can be about 1:2.3. The product of reaction is XDC which can be purified by re-crystallization in methanol.
The coating can be used as a reservoir layer containing an active agent or a drug, or a topcoat layer for reducing the rate of release of the drug. The block copolymers can be used alone or in combination with other suitable polymers. In other words, the copolymer can be blended or layered with other polymers Poly(ethylene-co-vinyl alcohol) (EVAL) is one example of a polymer than can be employed. EVAL is a product of hydrolysis of ethylene-vinyl acetate copolymers and may also be a terpolymer including up to 5 molar % of units derived from styrene, propylene and other suitable unsaturated monomers.
Representative examples of other suitable polymers include poly(hydroxyvalerate), poly(L-lactic acid), polycaprolactone, poly(lactide-co-glycolide), poly(hydroxybutyrate), poly(hydroxybutyrate-co-valerate), polydioxanone, polyorthoester, polyanhydride, poly(glycolic acid), poly(D,L-lactic acid), poly(glycolic acid-co-trimethylene carbonate), poly(glycerol-sebacate), polyphosphoester, polyphosphoester urethane; poly(amino acids), cyanoacrylates, poly(trimethylene carbonate), poly(iminocarbonate), co-poly(ether-esters) (e.g. PEO/PLA), polyalkylene oxalates, polyphosphazenes, biomolecules (such as fibrin, fibrinogen, cellulose, starch, collagen and hyaluronic acid), polyurethanes, silicones, polyesters, polyolefins, polyisobutylene and ethylene-alphaolefin copolymers, acrylic polymers and copolymers, vinyl halide polymers and copolymers (such as polyvinyl chloride), polyvinyl ethers (such as polyvinyl methyl ether), polyvinylidene halides (such as polyvinylidene fluoride and polyvinylidene chloride), polyacrylonitrile, polyvinyl ketones, polyvinyl aromatics (such as polystyrene), polyvinyl esters (such as polyvinyl acetate), copolymers of vinyl monomers with each other and olefins (such as ethylene-methyl methacrylate copolymers, acrylonitrile-styrene copolymers, ABS resins, and ethylene-vinyl acetate copolymers), polyamides (such as Nylon 66 and polycaprolactam), alkyd resins, other polycarbonates, polyoxymethylenes, polyimides, polyethers, epoxy resins, other polyurethanes, rayon, rayon-triacetate, cellulose, cellulose acetate, cellulose butyrate, cellulose acetate butyrate, cellophane, cellulose nitrate, cellulose propionate, cellulose ethers, soluble fluorinated polymers and carboxymethyl cellulose.
The embodiments of the present invention are described in connection with a stent, e.g., balloon expandable or self-expandable stents; however, other implantable medical devices can also be coated with the described block copolymers. Examples of such implantable devices include stent-grafts, grafts (e.g., aortic grafts), artificial heart valves, cerebrospinal fluid shunts, pacemaker electrodes, and endocardial leads (e.g., FINELINE and ENDOTAK, available from Guidant Corp. of Santa Clara, Calif.). The underlying structure of the 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 alloy (ELGILOY), stainless steel (316L), “MP35N,” “MP20N,” ELASTINITE (Nitinol), tantalum, nickel-titanium alloy, platinum-iridium alloy, gold, magnesium, or combinations thereof. “MP35N” and “MP20N” are trade names for alloys of cobalt, nickel, chromium and molybdenum available from Standard Press Steel Co. of 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. Devices made from bioabsorbable or biostable polymers could also be used with the embodiments of the present invention.
For the reservoir layer, the coating can include an active agent or a drug. The drug can include any substance capable of exerting a therapeutic or prophylactic effect for a patient. The drug may include small molecule drugs, peptides, proteins, oligonucleotides, and the like. The drug could be designed, for example, to inhibit the activity of vascular smooth muscle cells. It can be directed at inhibiting abnormal or inappropriate migration and/or proliferation of smooth muscle cells to inhibit restenosis.
Examples of drugs include antiproliferative substances such as actinomycin D, or derivatives and analogs thereof (manufactured by Sigma-Aldrich of Milwaukee, Wis., or COSMEGEN available from Merck). Synonyms of actinomycin D include dactinomycin, actinomycin IV, actinomycin I1, actinomycin X1, and actinomycin C1. The active agent can also fall under the genus of antineoplastic, anti-inflammatory, antiplatelet, anticoagulant, antifibrin, antithrombin, antimitotic, antibiotic, antiallergic and antioxidant substances. Examples of such antineoplastics and/or antimitotics include paclitaxel (e.g. TAXOL® by Bristol-Myers Squibb Co., Stamford, Conn.), docetaxel (e.g. Taxotere®, from Aventis S.A., Frankfurt, Germany) methotrexate, azathioprine, vincristine, vinblastine, fluorouracil, doxorubicin hydrochloride (e.g. Adriamycin® from Pharmacia & Upjohn, Peapack N.J.), and mitomycin (e.g. Mutamycin® from Bristol-Myers Squibb Co., Stamford, Conn.). Examples of such antiplatelets, anticoagulants, antifibrin, and antithrombins include 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, and thrombin inhibitors such as Angiomax™ (Biogen, Inc., Cambridge, Mass.). Examples of such cytostatic or antiproliferative agents include angiopeptin, angiotensin converting enzyme inhibitors such as captopril (e.g. Capoten® and Capozide® from Bristol-Myers Squibb Co., Stamford, Conn.), cilazapril or lisinopril (e.g. Prinivil® and Prinzide® from Merck & Co., Inc., Whitehouse Station, N.J.); calcium channel blockers (such as nifedipine), colchicine, fibroblast growth factor (FGF) antagonists, fish oil (omega 3-fatty acid), histamine antagonists, lovastatin (an inhibitor of HMG-CoA reductase, a cholesterol lowering drug, brand name Mevacor® from Merck & Co., Inc., Whitehouse Station, N.J.), monoclonal antibodies (such as those specific for Platelet-Derived Growth Factor (PDGF) receptors), nitroprusside, phosphodiesterase inhibitors, prostaglandin inhibitors, suramin, serotonin blockers, steroids, thioprotease inhibitors, triazolopyrimidine (a PDGF antagonist), and donors of nitric oxide. An example of an antiallergic agent is permirolast potassium. Other therapeutic substances or agents which may be appropriate include alpha-interferon, genetically engineered epithelial cells, tacrolimus, dexamethasone, and rapamycin and structural derivatives or functional analogs thereof, such as 40-O-(2-hydroxy)ethyl-rapamycin (known by the trade name of EVEROLIMUS available from Novartis), 40-O-(3-hydroxy)propyl-rapamycin, 40-O-[2-(2-hydroxy)ethoxy]ethyl-rapamycin, and 40-O-tetrazole-rapamycin.
Embodiments of the present invention are further illustrated by the following examples
As a first step, a monomer BMA was dissolved in 2-butanone (also known as methyl ethyl ketone) and an initiator XDC was added. The amounts of components are summarized in Table 2.
The solution of BMA and XDC in 2-butanone was placed into a borosilicate vial, purged with dry nitrogen for about 30 minutes and the vial was sealed. The contents of vial were subjected to UV radiation at a wavelength within a range of between about 310 nm and about 400 nm, for about 12 hours. The vial was then opened and the contents were added dropwise to ethanol cooled to a temperature of about −76° C. As a result, poly(butylmethacrylate)-XDC (PBMA-XDC) was precipitated. The precipitate was collected using a vacuum funnel and vacuum-dried.
As a second step, PBMA-XDC obtained as described above was combined with 3-sulfopropylmethacrylate and aqueous 2-butanone in the amounts shown in Table 3.
The blend of PBMA-XDC, 3-sulfopropylmethacrylate, and 2-butanone was placed into a borosilicate vial, purged with dry nitrogen for about 10 minutes and the vial was sealed. The contents of vial were subjected to UV radiation at a wavelength within a range of between about 310 nm and about 400 nm, for about 12 hours. The vial was then opened and the contents were added dropwise to water and vigorously stirred causing precipitation of a poly(3-sulfopropyl methacrylate-block-butylmethacrylate-block-3-sulfopropylmethacrylate)-XDC. The precipitate was collected using a vacuum funnel and vacuum-dried followed by hydrolysis in the presence of potassium ethoxide to remove the N,N-diethyl-dithiocarbamate functionality. As a result of the described process, poly(3-sulfopropylmethacrylate-block-butylmethacrylate-block-3-sulfopropyl methacrylate), which is an ABA block copolymer, was precipitated, the ABA block copolymer (V):
The molecular weight of the BMA-based mid-blocks (B blocks) was about 66,700 Daltons as measured by the method of gel-permeation chromatography (GPC) corresponding to the value of n˜470, and the molecular weight of the 3-sulfopropylmethacrylate-based end blocks (A blocks) was about 11,100 Daltons, corresponding to values of m˜54 and p˜54.
As a first step, PBMA-XDC was synthesized as described in Example 1. As a second step, PBMA-XDC was combined with methacrylic acid (MAA) and 2-butanone in the amounts shown in Table 4.
The blend of PBMA-XDC, methacrylic acid and 2-butanone was subjected to UV radiation at a wavelength within a range of between about 310 nm and about 400 nm, for about 32.5 hours. The vial was then opened, the solvent was removed by evaporation, the contents were dissolved in tetrahydrofuran and the solution was added dropwise to water and vigorously stirred causing precipitation of a poly(methacrylic acid-block-butylmethacrylate-block-methacrylic acid)-XDC. The precipitate was collected using a vacuum funnel and vacuum-dried followed by hydrolysis in the presence of a strong base to remove XDC. As a result of the described process, poly(methacrylic acid-block-butylmethacrylate-block-methacrylic acid), which is an ABA block copolymer, was precipitated, the ABA block copolymer having the general formula (VI):
The molecular weight of the BMA-based mid-blocks (B blocks) in block-copolymer (VI) was about 85,000 Daltons as measured by GPC corresponding to the value of n˜599, and the molecular weight of the methacrylic acid-based end blocks (A blocks) was about 10,020 Daltons, corresponding to values of m˜116 and p˜116, resulting in molar ratio between units derived from MAA and BMA of about 14:72:14.
As a first step, PBMA-XDC was synthesized as described in Example 1. As a second step, PBMA-XDC was combined with acryloyl poly(ethylene glycol) (acryloyl-PEG) and 2-butanone in the amounts shown in Table 5.
Acryloyl-PEG is a product of esterification of acrylic acid by PEG and has a formula (VII):
A low molecular weight acryloyl-PEG oligomer with the number-averaged molecular weight (Mn) of about 375 was used, corresponding to the value “x” in formula of (VII) of about 7. The blend of PBMA-XDC, acryloyl-PEG and 2-butanone was subjected to UV radiation as described in Example 2, for about 43 hours. The vial was then opened, the contents were added dropwise to water and vigorously stirred at a temperature of about 70° C. for about 2 hours, causing evaporation of 2-butanone and forming a suspension of poly(acryloyl-PEG-block-butylmethacrylate-block-acryloyl-PEG)-XDC. The suspension was cooled to the room temperature and the precipitate was collected using a vacuum funnel and vacuum-dried followed by hydrolysis in the presence of a strong base to remove XDC. As a result of the described process, poly(acryloyl-PEG-block-butylmethacrylate-block-acryloyl-PEG), which is a ABA block copolymer, was precipitated, the ABA block copolymer having the general formula (VIII):
Poly(3-sulfopropylmethacrylate-block-butylmethacrylate-block-3-sulfopropylmethacrylate)-XDC obtained as described in Example 1 was combined in a borosilicate vial with PEG-methacrylate and 2-butanone in the amounts shown in Table 6.
A low molecular weight acryloyl-PEG oligomer with Mn of about 375 was used, corresponding to the value “x” in formula of (VII) of about 7. The mixture in the vial was purged with dry nitrogen for about 10 minutes and the vial was sealed. The contents of vial were subjected to UV radiation at a wavelength within a range of between about 310 nm and about 400 nm, for about 12 hours. The vial was then opened and the contents were added dropwise to water and vigorously stirred causing precipitation of a polymeric matter.
The precipitate was collected using a vacuum funnel and vacuum-dried followed by hydrolysis in the presence of a strong base to remove XDC. As a result of the described process, poly(acryloyl{poly[ethylene glycol]}-block-3-sulfopropylmethacrylate-block-butylmethacrylate-block-3-sulfopropylmethacrylate-block-acryloyl{poly[ethylene glycol]}), which is an ABCBA block copolymer, was precipitated, the ABCBA block copolymer having the general formula (IX):
The molecular weight of the BMA-based center blocks (C blocks) was about 66,700 Daltons as measured by GPC corresponding to the value of p˜470, the molecular weight of the 3-sulfopropylmethacrylate-based blocks (B blocks) was about 11,100 Daltons, corresponding to values of n˜54 and q˜54, and the molecular weight of terminal PEG-containing blocks (A blocks) was about 4,400 Daltons, corresponding to values of m˜12 and r˜12.
As a first step, a monomer BMA was dissolved in 2-butanone and an initiator BDC was added. The amounts of components are summarized in Table 7.
The solution of BMA and BDC in 2-butanone was placed into a borosilicate vial, purged with dry nitrogen for about 30 minutes and the vial was sealed. The contents of vial were subjected to UV radiation at a wavelength within a range of between about 310 nm and about 400 nm, for about 12 hours. The vial was then opened and the contents were added dropwise to ethanol cooled to a temperature of about −76° C. As a result, poly(butylmethacrylate)-BDC (PBMA-BDC) was precipitated. The molecular weight of the PBMA-BDC was about 200,000 Daltons as measured by GPC. The precipitate was collected using a vacuum funnel and vacuum-dried.
As a second step, PBMA-BDC obtained as described above was combined with 3-sulfopropylmethacrylate and a 2% (mass) solution of PEG having weight average molecular weight of about 750 in aqueous 2-butanone. The amounts of components are shown in Table 8
The blend of PBMA-BDC, 3-sulfopropylmethacrylate, and the PEG solution in aqueous 2-butanone was placed into a borosilicate vial, purged with dry nitrogen for about 10 minutes and the vial was sealed. The contents of vial were subjected to UV radiation at a wavelength within a range of between about 310 nm and about 400 nm, for about 12 hours. The vial was then opened and the contents were added dropwise to water and vigorously stirred causing precipitation of a poly(3-sulfopropylmethacrylate-block-butylmethacrylate)-BDC, having molecular weight of about 266,700 Daltons. The precipitate was collected using a vacuum funnel and vacuum-dried followed by hydrolysis in the presence of a strong base to remove BDC. As a result of the described process, poly(3-sulfopropylmethacrylate-block-butylmethacrylate), which is an AB block copolymer, was precipitated, the AB block copolymer having the general formula (X):
The molecular weight of the BMA-based blocks (B blocks) was about 200,000 Daltons as measured by GPC corresponding to the value of n˜1,400, the molecular weight of the 3-sulfopropylmethacrylate-based blocks (A blocks) was about 66,700 Daltons, corresponding to values of m˜324. Overall molecular weight of the block copolymer was about 266,700 Daltons.
Poly(3-sulfopropylmethacrylate-block-butylmethacrylate)-BDC obtained as described in Example 5 was combined in a borosilicate vial with PEG-methacrylate and 2-butanone in the amounts shown in Table 9.
PEG-methacrylate is a product of esterification of methacrylic acid by PEG and has a formula (XI):
A brand of PEG-methacrylate with the number-averaged molecular weight (Mn) of about 520 was used, corresponding to the value “y” in formula of (XI) of about 10. The mixture in the vial was purged with dry nitrogen for about 10 minutes and the vial was sealed. The contents of vial were subjected to UV radiation for about 12 hours. The vial was then opened and the contents were added dropwise to water and vigorously stirred causing precipitation of a polymeric matter. The precipitate was collected using a vacuum funnel and vacuum-dried followed by hydrolysis in the presence of a strong base to remove BDC. As a result of the described process, poly(acryloyl{poly[ethylene glycol]}-block-3-sulfopropyl methacrylate-block-butylmethacrylate), which is a ABC block copolymer (XII) was precipitated:
The molecular weight of the BMA-based blocks (C blocks) was about 200,000 Daltons as measured by GPC corresponding to the value of p˜1,400, the molecular weight of the 3-sulfopropylmethacrylate-based mid-blocks (B blocks) was about 66,700 Daltons, corresponding to value of n˜324, and the molecular weight of the PEG-methacrylate blocks (A blocks) was about 29,600 Daltons, corresponding to value of m˜57. Overall molecular weight of the block copolymer was about 296,300 Daltons.
A solution can be prepared by thoroughly mixing the following components:
(a) about 15 mass % of MMA;
(b) about 9 mass % of BMA;
(c) about 8 mass % of PEG-methacrylate (PEGMA), where PEG can have weight-average molecular weight of about 6,000;
(d) about 20 mass % of acrylic acid (AA);
(e) about 3 mass % of initiator 2,2-dimethoxy-2-phenol acetophenone; and
(f) the balance of benzene serving as a solvent.
An inert atmosphere can be created by bubbling nitrogen gas through the solution for about 30 minutes. The solution can then be exposed to UV radiation for about 10 minutes at a wavelength of 360 nm while being continuously stirred causing formation of a random copolymer, P(MMA-BMA-AA-PEGMA).
SODm can then be grafted to the P(MMA-BMA-AA-PEGMA) copolymer. About 1:1 mole ratio between SODm and the amount of acrylic acid can be used. Grafting of SODm to the P(MMA-BMA-AA-PEGMA) copolymer can be conducted in the presence of 1-ethyl-3(3-dimethylaminopropyl)carbodiimide, also known as carbodiimide or EDC, having the formula CH3—CH2—N═C═N—CH2—CH2—CH2—N(CH3)2. EDC is manufactured by Pierce Corp., of Rockford, Ill. Instead of EDC, 1,3-dicyclohexylcarbodiimide (DCC) can be used.
The final P(MMA-BMA-AA-PEGMA)-SODm random copolymer can be precipitated with a non-solvent such as hexane and vacuum dried. The copolymer can then be mixed with EVAL in a mass ratio of about 2:3 and the mixture can be applied onto a stent to form a reservoir layer or a topcoat layer.
While particular embodiments of the present invention have been shown and described, it will be obvious to those skilled in the art that changes and modifications can be made without departing from this invention in its broader aspects. Therefore, the appended claims are to encompass within their scope all such changes and modifications as fall within the true spirit and scope of this invention.
This is a divisional application of U.S. patent application Ser. No. 10/317,435, filed Dec. 11, 2002, now U.S. Pat. No. 7,776,926 the teaching of which is incorporated herein in its entirety by reference.
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| Number | Date | Country | |
|---|---|---|---|
| 20100292426 A1 | Nov 2010 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 10317435 | Dec 2002 | US |
| Child | 12844734 | US |
