Patent Application
20110104228
The invention relates to a coating for medical devices.
Implantable medical articles can be instrumental in saving and/or enhancing the quality of the life of patients. However, a significant barrier to the use of implantable devices is the possibility of adverse reactions of the body such as thrombogenic and immune responses. Common materials used to manufacture implantable medical articles include metals, minerals or ceramics, and polymers. It is generally desirable to modify the surface of such materials in order to provide the surface with properties that are different from the properties of the material, e.g., in terms of infection resistance (i.e., via the delivery of a biologically active agent), thromboresistance, radiopacity, conductivity, and/or biocompatibility.
Various synthetic techniques have been used to impart desired chemical, physical and biological properties to materials used to manufacture implantable medical devices.
One approach, for example, involves application of a parylene coating to devices, wherein a low molecular weight monomer is condensed and polymerized on a substrate, forming a matrix on the surface of the medical device. In another approach, biomaterials, e.g., heparin or albumin, are coupled directly to the surface of the medical device to reduce thrombogenicity (Nicholas A. Peppas et al., Science, 263: 1715 (1994)). Such approaches have a number of limitations. For example, a thick polymer coating, or a surface-coupled polymer coating, when applied to a medical device, such as a stent, will often have different physical properties than the underlying substrate (i.e., a metal) and, consequently, may not respond similarly to tensile, shear, or compression forces, causing the coating to crack, flake, or delaminate. Such instability can have serious adverse consequences when the coating cracks, flakes, or delaminates in vivo. This problem is exacerbated for certain medical devices, such as catheters and stents, which are subjected to deformation in vivo. When the device expands, it is important that the coating is capable of undergoing the same deformation without breaking or coming loose.
The safety of implantable devices can also be compromised by a lack of biocompatibility. Once implanted, a medical device resides in contact with tissue and may produce local inflammation, at the site of implantation, as the host responds to the implant as a foreign body. The design of a drug delivery platform that addresses the host's response to an implantable device has long been desired. Medical implants are excellent platforms for direct and localized drug delivery, however the challenge is with the polymer system used for such applications. For example, although cardiovascular stents revolutionized the management of controlling the re-narrowing of artries, stent-restenosis persists as a clinical risk factor. To address this problem, at the molecular level, a host of polymers as drug delivery platforms have been used. This was captured in the design and implantation of drug eluting stents. However the drug delivery platforms used in “drug eluting stents” are generally durable polymers and remain on the stent platform for an indefinite timeline which in turn initiates a series of un-desired host responses (Perin et al., Review in Cardiovascular Medicine, 6:S13 (2005)). Coating of a pharmaceutically active compound directly on a stent platform has also been investigated. Crystallinity of the deposited pharmaceutically active compound on the surface is often the result. The formation of a crystalline coating produces a dumping effect in which all of the drug on the stent is released at one time. Such a release profile is undesirable because it can result in toxicity leading to necrosis at the site of release.
New coatings that can function as drug delivery matrices, are easy to apply, biocompatible, and have a limited residency time, while allowing for the controlled release of biologically active agents, are needed to address the limitations present in the art.
The invention features the use of a matrix coating consisting of low molecular weight components and comprising an oligomer and a biologically active agent. The matrix coatings are self-eliminating or bioerodible upon implantation into a subject. The matrix coatings can be used to enhance biocompatibility and to control the local delivery of biologically active agents.
In a first aspect, the invention features an implantable medical device having a surface and a matrix coating applied to the surface of the implantable medical device, the matrix coating consisting of components having a molecular weight of less than 20 kDa, the matrix coating including (i) an oligomer and (ii) a biologically active agent, wherein the matrix coating is self-eliminating or bioerodible upon implantation into a subject and wherein the biologically active agent when on the implantable medical device resides solely within the matrix coating.
In a related aspect, the invention features a method for making a coated implantable medical device having a surface by coating the surface with a matrix coating consisting of components having a molecular weight of less than 20 kDa, the matrix coating including (i) an oligomer and (ii) a biologically active agent, wherein the matrix coating is self-eliminating or bioerodible upon implantation into a subject and wherein the biologically active agent when on the implantable medical device resides solely within the matrix coating.
In certain embodiments, the matrix and the biologically active agent are applied to the surface by spray coating, printing, or dip coating the implantable medical device, or using any other application methods described herein.
The biologically active agents can be selected from proteins, peptides, carbohydrates, antibiotics, antiproliferative agents, rapamycin macrolides, analgesics, anesthetics, antiangiogenic agents, antithrombotic agents, vasoactive agents, anticoagulants, immunomodulators, cytotoxic agents, antiviral agents, antibodies, neurotransmitters, psychoactive drugs, oligonucleotides, vitamins, lipids, prodrugs thereof. Biologically active agents useful in the methods and matrix coatings of the invention include any biologically active agent described herein.
In certain embodiments, the biologically active agent is simply mixed with oligomers of the matrix coating. In other embodiments, the biologically active agent is covalently tethered to, or complexed to, an oligomer in the matrix coating.
In still other embodiments, the biologically active agent is uniformly distributed throughout the matrix coating. For example, the biologically active agent can be dissolved in the matrix coating.
In another aspect, the invention features an implantable medical device having a surface and a matrix coating applied to the surface of the implantable medical device, the matrix coating including an oligofluorinated oligomer, wherein the matrix coating is self-eliminating or bioerodible upon implantation into a subject and wherein the oligofluorinated oligomer when on the implantable medical device resides solely within the matrix coating.
In a related aspect, the invention features a method for making a coated implantable medical device having a surface by coating the surface with a matrix coating including an oligofluorinated oligomer, wherein the matrix coating is self-eliminating or bioerodible upon implantation into a subject and wherein the oligofluorinated oligomer when on the implantable medical device resides solely within the matrix coating.
The implantable medical devices of the invention can have a surface material selected from, for example, metals, metal alloys, ceramics, base polymers, and glasses. Implantable medical devices that can be coated using the methods and matrix coatings of the invention include, without limitation, cardiac-assist devices, catheters, stents, prosthetic implants, artificial sphincters, drug delivery devices, and any other implantable devices described herein. In certain embodiments, the implantable medical device is a stent.
The invention further features a stent having a surface and a matrix coating applied to the surface of the stent, the matrix coating consisting of components having a molecular weight of less than 20 kDa, the matrix coating including (i) an oligomer and (ii) a biologically active agent selected from antiproliferative agents and rapamycin macrolides, wherein the matrix coating is self-eliminating or bioerodible upon implantation into a subject and wherein the biologically active agent when on the stent resides solely within the matrix coating.
The invention also features a stent having a surface and a matrix coating applied to the surface of the stent, the matrix coating including an oligofluorinated oligomer, wherein the matrix coating is self-eliminating or bioerodible upon implantation into a subject and wherein the oligofluorinated oligomer when on the stent resides solely within the matrix coating. In certain embodiments, the matrix coating further includes a biologically active agent selected from antiproliferative agents and rapamycin macrolides.
Antiproliferative agents which can be used on the coated stents of the invention include, without limitation, methotrexate, trimetrexate, gemcitabine, vinblastine, vincristine, etoposide, teniposide, topotecan, irinotecan, camptothecin, 9-aminocamptothecin, paclitaxel, docetaxel, daunorubicin, doxorubicin, dactinomycin, idarubincin, bleomycin, tamoxifen, and any other antiproliferative agent described herein.
Rapamycin macrolides which can be used on the coated stents of the invention include, without limitation, rapamycin, CCI-779, Everolimus, ABT-578, and any other rapamycin macrolide described herein.
In a related aspect, the invention features a method for inhibiting restenosis at a site in a vessel by implanting a stent of the invention at the site.
The invention further features a method for delivering a biologically active agent to a subject by implanting into the subject an implantable medical device having a matrix coating of the invention, where the coating matrix includes a biologically active agent.
Oligomers that can be used in the methods and matrix coatings of the invention include polyurethanes, polyureas, polyamides, polyalkylene oxides, polycarbonates, polyesters, polylactones, polysilicones, polyethersulfones, polyolefins, polyvinyls, polypeptides, polysaccharides, and combinations thereof.
In certain embodiments, an oligomer in the matrix coating is an oligofluorinated oligomer. The oligofluorinated oligomers can be any described herein. In one embodiment, the oligofluorinated oligomer is described by formula (I):
In formula (I), oligo is an oligomeric segment; Bio is a biologically active agent; FT is an oligofluoro group; each Link B is, independently, an organic moiety covalently bound to oligo, FT, or Bio; a is an integer greater than 0; b and c are each, independently, integers greater than or equal to 0; and d is 0 or 1. In another embodiment, the oligofluorinated oligomer is described by formula (II):
F
T
−[B−(oligo)]n−B−(FT)g (II)
In formula (II), B includes a urethane; oligo includes polycarbonate, polypropylene oxide, polyethylene oxide, or polytetramethyleneoxide; FT is an oligofluoro group; g is 0 or 1; and n is an integer from 1 to 10.
Oligofluoro groups include, without limitation, groups having the formula:
CF3(CF2)pX, (CF3)2CF(CF2)pX, or (CF3)3C(CF2)pX,
wherein X is CH2CH2—, (CH2CH2O)n, CH2CH(OH)CH2O—, CH2CH(CH2OH)O—, or a bond; p is an integer between 2 and 20; and n is an integer between 1 and 10.
In any of the above methods and coatings of the invention, the matrix coating can consist of components having a molecular weight of less than 40 kDa, 35 kDa, 30 kDa, 25 kDa, 18 kDa, 16 kDa, 14 kDa, 12 kDa, 10 kDa, 9 kDa, 8 kDa, 7 kDa, 6 kDa, 5 kDa, 4 kDa, or even 3 kDa.
The coatings of the invention can by applied by brushing, printing, spraying, wiping, or dipping the surface with the matrix coating. In certain embodiments, the step of coating includes dissolving the constituents of the matrix coating in a solvent to form a solution and applying the solution to the surface of the implantable medical device. In still other embodiments, the step of coating includes mixing the constituents of the matrix with a diluent to form a fluid mixture and applying the fluid mixture to the surface of the implantable medical device.
In any of the above methods and coatings of the invention, the matrix coating can have a thickness of from 0.01 to 25 microns, 0.05 to 15 microns, 0.1 to 25 microns, 0.1 to 15 microns, 0.1 to 10 microns, 0.1 to 5 microns, 0.1 to 3 microns, or even 0.1 to 1 microns.
In any of the above methods and coatings of the invention, the uncoated implantable medical device is coated to produce a coated implantable medical device, the coated implantable medical device having, upon implantation into an animal, reduced protein deposition, reduced fibrinogene deposition, reduced platelet deposition, or reduced inflammatory cell adhesion in comparison to said uncoated implantable medical device.
By “base polymer” is meant a self supporting polymer having a tensile strength of from about 350 to about 10,000 psi, elongation at break from about 300% to about 1500%, an unsupported thickness of from about 5 to about 100 microns, and a supported thickness of from about 1 to about 100 microns.
As used herein, “LinkB” refers to a coupling segment capable of covalently linking oligomers, biologically active agents, and/or oligofluoro groups. Typically, LinkB molecules have molecular weights ranging from 40 to 700. Preferably the LinkB molecules are selected from the group of functionalized diamines, diisocyanates, disulfonic acids, dicarboxylic acids, diacid chlorides and dialdehydes, wherein the functionalized component has secondary functional chemistry that is accessed for chemical attachment of an oligofluoro group. Such secondary groups include, for example, esters, carboxylic acid salts, sulfonic acid salts, phosphonic acid salts, thiols, vinyls and secondary amines. Terminal hydroxyls, amines or carboxylic acids on the oligo intermediates can react with diamines to form oligo-amides; react with diisocyanates to form oligo-urethanes, oligo-ureas, oligo-amides; react with disulfonic acids to form oligo-sulfonates, oligo-sulfonamides; react with dicarboxylic acids to form oligo-esters, oligo-amides; react with diacid chlorides to form oligo-esters, oligo-amides; and react with dialdehydes to form oligo-acetal, oligo-imines.
By “oligo” or “oligomer” is meant a relatively short length of a repeating unit or units, generally less than about 50 monomeric units and molecular weights less than 10,000 but preferably <5,000 Daltons. Preferably, oligo is selected from the group consisting of polyurethane, polyurea, polyamides, polyalkylene oxide, polycarbonate, polyester, polylactone, polysilicone, polyethersulfone, polyolefin, polyvinyl, polypeptide, polysaccharide; and ether and amine linked segments thereof.
By “prodrug” is meant a precursor to a biologically active agent which is converted in vivo, e.g., by enzymatic and/or hydrolytic mechanisms, into a biologically active agent. Prodrugs include, without limitation, esterified biologically active agents. Prodrugs useful in the methods and compositions of the invention include, for example, biologically active agents covalently tethered via a hydrolyzable linkage to an oligomer in a matrix coating of the invention.
As used herein, “self-eliminating” refers to the diffusion of a matrix coating from the surface of an implantable medical device. Self-eliminating coatings are those in which greater than 70%, 80%, or even 90% (w/w) of the coating diffuses from the surface over a period of less than 2 months, 1 month, or 15 days under flow conditions in buffer, artificial urine, or plasma as provided in the Examples. It is understood that the self-elimination kinetics of any matrix coating on any particular implantable device will vary with the shape of the device, the constituents of the matrix, and the site of implantation. Of importance is that the matrix coatings of the invention are designed to be transitory in nature, leaving the original uncoated implantable medical device intact at the site of implantation.
As used herein, “bioerodible” refers to the diffusion of a matrix coating from the surface of an implantable medical device. Bioerodible coatings are those in which greater than 30%, 40%, or 50% (w/w) of the coating diffuses from the surface over a period of less than 6 months, 4 months, 3 months, 2 months, or 1 month under sink conditions in buffer, artificial urine, or plasma as provided in the Examples. It is understood that the self-elimination kinetics of any matrix coating on any particular implantable device will vary with the shape of the device, the constituents of the matrix, and the site of implantation. Of importance is that the matrix coatings of the invention are designed to be transitory in nature, leaving the original uncoated implantable medical device intact at the site of implantation.
As used herein, “covalently tethered” refers to moieties separated by one or more covalent bonds. For example, where an oligofluoro group is covalently tethered to an oligomer, tethered includes the moieties separated by a single bond as well as both moieties separated by, for example, a LinkB segment to which both moieties are covalently attached.
As used herein, the term “oligofluorinated” refers to an oligomer covalently linked to an oligofluoro group for use in a matrix coating of the invention.
As used herein, “complexed” or “complexation” refers to an interaction, either non-covalent or via coordination to a metal center, between a complexing moiety in an oligomer contained within a matrix coating of the invention and a biologically active agent. Examples of non-covalent bonding interactions which can be used in accordance with the present invention include, without limitation, hydrogen bonding, ionic interactions (e.g., dipole-dipole interactions, ion pairing, and salt formation), inclusion complexes, clathration, van der Waals interactions (e.g., pi-pi stacking), and combinations thereof. The interaction can also be via coordination to a metal center by both the complexing moiety and the biologically active agent. In some instances, the biologically active agent includes a metal center which is coordinated to the complexing moiety.
As used herein, “complexing moiety” refers to certain embodiments of the invention including a portion of an oligomer contained within a matrix coating of the invention which complexes a biologically active agent either via a non-covalent interaction or coordination to a metal center, forming a polymer complex. The complexing moiety can be a charged moiety, e.g., a moiety which loses a proton at physiological pH thereby becoming negatively charged (e.g., carboxylate, or phosphodiester), a moiety which gains a proton at physiological pH thereby becoming positively charged (e.g., ammonium, guanidinium, or amidinium), a moiety that includes a net formal positive charge without protonation (e.g., quaternary ammonium), or a moiety that includes a net formal negative charge without loss of a proton (e.g., borate, BR4−). Exemplary charged complexing moieties include, without limitation, carboxylate, phosphodiester, phosphoramidate, borate, phosphate, phosphonate, phosphonate ester, sulfonate, sulfate, thiolate, phenolate, ammonium, amidinium, guanidinium, quaternary ammonium, and imidazolium functionalities. The complexing moiety can be designed to physically encapsulate, in whole or in part, the biologically active agent, such as a cyclodextrin. The complexing moiety be designed to ligate a complementary oligonucleotide and/or peptide sequence present in the biologically active agent. The complexing moiety can be designed to coordinate a metal center including the biologically active agent, either as a ligand alone or including the metal center.
A description of how make complexing moieties and complexation with biologically active agents is described in U.S. Patent Publication No. 20070037891, incorporated herein by reference.
Other features and advantages of the invention will be apparent from the following Detailed Description, the Drawings, and the Claims.
The methods and compositions of the invention feature a matrix coating consisting of low molecular weight components and comprising (i) an oligomer and a biologically active agent, or (ii) an oligofluorinated oligomer. The matrix coatings are self-eliminating or bioerodible upon implantation into a subject. The matrix coatings can be used to enhance biocompatibility and to control the local delivery of biologically active agents.
The matrix coating of the invention includes an oligomer. Oligomers which can be used in the matrix coatings of the invention include, without limitation, polyurethanes, polyureas, polyamides, polyaklylene oxides, polycarbonates, polyesters, polylactones, polysilicones, polyethersulfones, polyolefins, polyvinyl derivatives, polypeptides, polysaccharides, polysiloxanes, polydimethylsiloxanes, polyethylene-butylene, polyisobutylenes, polybutadienes, polypropylene oxides, polyethylene oxides, polytetramethyleneoxides, polyethylenebutylenes, polycaprolactone, polylactic, polyethylene glycol, polypropylene glycol, polydiethyleneglycol phthalate, polydiethyleneglycol adipate, polyhydroxybutyrate, polyhydroxyoctanoate, polyhydroxyvalerate, biOH™ soybean oil-derivative (Cargill), and combinations and mixtures thereof.
The matrix coating may optionally contain an oligomer complexed, or covalently tethered, to a biologically active agent, or applied in a mixture including a biologically active agent.
The amount of biologically active agent loaded into the coating will depend upon the design of the oligomer in combination with the desired release profile. The oligomer may be designed for the particular agent being delivered and to provide the biocompatibility necessary for a particular application.
The process by which the polymer complex is formed may be a two or multi-step procedure. In general, oligofluorinated oligomers used in the methods and compositions of the invention can be prepared as described in U.S. Pat. No. 6,127,507, and U.S. Ser. No. 11/404,290, each of which is incorporated herein by reference.
Biologically active agents can be incorporated in the coatings of the invention. The incorporation can be achieved either by mixing the matrix coating components and the biologically active agent together and applying the mixture to the surface of the article prior to implantation. In some instances, the biologically active agent is covalently tethered or complexed to an oligomer in the matrix coating. A detailed description of how biologically active agents may be covalently tethered or complexed to an oligofluorinated oligomeris provided in U.S. Pat. No. 6,770,725 and U.S. Ser. No. 11/404,290, each of which is incorporated herein by reference. Biologically active agents that can be used in the methods and compositions of the invention include therapeutic, diagnostic, and prophylactic agents. They can be naturally occurring compounds, synthetic organic compounds, or inorganic compounds. Biologically active agents that can be used in the methods and compositions of the invention include, but are not limited to, proteins, peptides, carbohydrates, antibiotics, antiproliferative agents, rapamycin macrolides, analgesics, anesthetics, antiangiogenic agents, vasoactive agents, anticoagulants, immunomodulators, cytotoxic agents, antiviral agents, antithrombotic drugs, such as terbrogrel and ramatroban, antibodies, neurotransmitters, psychoactive drugs, oligonucleotides, proteins, lipids, and any biologically active agent described herein.
Exemplary therapeutic agents include growth hormone, for example human growth hormone, calcitonin, granulocyte macrophage colony stimulating factor (GMCSF), ciliary neurotrophic factor, and parathyroid hormone. Other specific therapeutic agents include parathyroid hormone-related peptide, somatostatin, testosterone, progesterone, estradiol, nicotine, fentanyl, norethisterone, clonidine, scopolomine, salicylate, salmeterol, formeterol, albeterol, valium, heparin, dermatan, ferrochrome A, erythropoetins, diethylstilbestrol, lupron, estrogen estradiol, androgen halotestin, 6-thioguanine, 6-mercaptopurine, zolodex, taxol, lisinopril/zestril, streptokinase, aminobutylric acid, hemostatic aminocaproic acid, parlodel, tacrine, potaba, adipex, memboral, phenobarbital, insulin, gamma globulin, azathioprine, papein, acetaminophen, ibuprofen, acetylsalicylic acid, epinephrine, flucloronide, oxycodone percoset, dalgan, phreniline butabital, procaine, novocain, morphine, oxycodone, aloxiprin, brofenac, ketoprofen, ketorolac, hemin, vitamin B-12, folic acid, magnesium salts, vitamin D, vitamin C, vitamin E, vitamin A, Vitamin U, vitamin L, vitamin K, pantothenic acid, aminophenylbutyric acid, penicillin, acyclovir, oflaxacin, amoxicillin, tobramycin, retrovior, epivir, nevirapine, gentamycin, duracef, ablecet, butoxycaine, benoxinate, tropenzile, diponium salts, butaverine, apoatropine, feclemine, leiopyrrole, octamylamine, oxybutynin, albuterol, metaproterenol, beclomethasone dipropionate, triamcinolone acetamide, budesonide acetonide, ipratropium bromide, flunisolide, cromolyn sodium, ergotamine tartrate, and protein or peptide drugs such as TNF antagonists or interleukin antagonists. For example, the biologically active agent can be an antiinflammatory agent, such as an NSAID, corticosteriod, or COX-2 inhibitor, e.g., rofecoxib, celecoxib, valdecoxib, or lumiracoxib.
Exemplary diagnostic agents include imaging agents, such as those that are used in positron emission tomography (PET), computer assisted tomography (CAT), single photon emission computerized tomography, X-ray, fluoroscopy, and magnetic resonance imaging (MRI). Suitable materials for use as contrast agents in MRI include gadolinium chelates, as well as iron, magnesium, manganese, copper, and chromium chelates. Examples of materials useful for CAT and X-rays include iodine based materials.
A preferred biologically active agent is a substantially purified peptide or protein. Proteins are generally defined as consisting of 100 amino acid residues or more; peptides are less than 100 amino acid residues. Unless otherwise stated, the term protein, as used herein, refers to both proteins and peptides. The proteins may be produced, for example, by isolation from natural sources, recombinantly, or through peptide synthesis. Examples include growth hormones, such as human growth hormone and bovine growth hormone; enzymes, such as DNase, proteases, urate oxidase, alronidase, alpha galactosidase, and alpha glucosidase; antibodies, such as trastuzumab.
Rapamycin Macrolides
Rapamycin (Sirolimus) is an immunosuppressive lactam macrolide that is produced by Streptomyces hygroscopicus. See, for example, McAlpine, J. B., et al., J. Antibiotics 44: 688 (1991); Schreiber, S. L., et al., J. Am. Chem. Soc. 113: 7433 (1991); and U.S. Pat. No. 3,929,992, incorporated herein by reference. Exemplary rapamycin macrolides which can be used in the methods and compositions of the invention include, without limitation, rapamycin, CCI-779, Everolimus (also known as RAD001), and ABT-578. CCI-779 is an ester of rapamycin (42-ester with 3-hydroxy-2-hydroxymethyl-2-methylpropionic acid), disclosed in U.S. Pat. No. 5,362,718. Everolimus is an alkylated rapamycin (40-O-(2-hydroxyethyl)-rapamycin, disclosed in U.S. Pat. No. 5,665,772.
Antiproliferative Agents
Exemplary antiproliferative agents which can be used in the methods and compositions of the invention include, without limitation, mechlorethamine, cyclophosphamide, iosfamide, melphalan, chlorambucil, uracil mustard, estramustine, mitomycin C, AZQ, thiotepa, busulfan, hepsulfam, carmustine, lomustine, semustine, streptozocin, dacarbazine, cisplatin, carboplatin, procarbazine, methotrexate, trimetrexate, fluouracil, floxuridine, cytarabine, fludarabine, capecitabine, azacitidine, thioguanine, mercaptopurine, allopurine, cladribine, gemcitabine, pentostatin, vinblastine, vincristine, etoposide, teniposide, topotecan, irinotecan, camptothecin, 9-aminocamptothecin, paclitaxel, docetaxel, daunorubicin, doxorubicin, dactinomycin, idarubincin, plicamycin, mitomycin, amsacrine, bleomycin, aminoglutethimide, anastrozole, finasteride, ketoconazole, tamoxifen, flutamide, leuprolide, goserelin, Gleevec™ (Novartis), leflunomide (Pharmacia), SU5416 (Pharmacia), SU6668 (Pharmacia), PTK787 (Novartis), Iressa™ (AstraZeneca), Tarceva™, (Oncogene Science), trastuzumab (Genentech), Erbitux™ (ImClone), PKI166 (Novartis), GW2016 (GlaxoSmithKline), EKB-509 (Wyeth), EKB-569 (Wyeth), MDX-H210 (Medarex), 2C4 (Genentech), MDX-447 (Medarex), ABX-EGF (Abgenix), CI-1033 (Pfizer), Avastin™ (Genentech), IMC-1C11 (ImClone), ZD4190 (AstraZeneca), ZD6474 (AstraZeneca), CEP-701 (Cephalon), CEP-751 (Cephalon), MLN518 (Millenium), PKC412 (Novartis), 13-cis-retinoic acid, isotretinoin, retinyl palmitate, 4-(hydroxycarbophenyl) retinamide, misonidazole, nitracrine, mitoxantrone, hydroxyurea, L-asparaginase, interferon alfa, AP23573, Cerivastatin, Troglitazone, CRx-026DHA-paclitaxel, Taxoprexin, TPI-287, Sphingosine-based lipids, and mitotane.
Corticosteroids
Exemplary corticosteroids which can be used in the methods and compositions of the invention include, without limitation, 21-acetoxypregnenolone, alclomerasone, algestone, amcinonide, beclomethasone, betamethasone, betamethasone valerate, budesonide, chloroprednisone, clobetasol, clobetasol propionate, clobetasone, clobetasone butyrate, clocortolone, cloprednol, corticosterone, cortisone, cortivazol, deflazacon, desonide, desoximerasone, dexamethasone, diflorasone, diflucortolone, difluprednate, enoxolone, fluazacort, flucloronide, flumethasone, flumethasone pivalate, flunisolide, flucinolone acetonide, fluocinonide, fluorocinolone acetonide, fluocortin butyl, fluocortolone, fluorocortolone hexanoate, diflucortolone valerate, fluorometholone, fluperolone acetate, fluprednidene acetate, fluprednisolone, flurandenolide, formocortal, halcinonide, halometasone, halopredone acetate, hydrocortamate, hydrocortisone, hydrocortisone acetate, hydrocortisone butyrate, hydrocortisone phosphate, hydrocortisone 21-sodium succinate, hydrocortisone tebutate, mazipredone, medrysone, meprednisone, methylprednicolone, mometasone furoate, paramethasone, prednicarbate, prednisolone, prednisolone 21-diedryaminoacetate, prednisolone sodium phosphate, prednisolone sodium succinate, prednisolone sodium 21-m-sulfobenzoate, prednisolone sodium 21-stearoglycolate, prednisolone tebutate, prednisolone 21-trimethylacetate, prednisone, prednival, prednylidene, prednylidene 21-diethylaminoacetate, tixocortol, triamcinolone, triamcinolone acetonide, triamcinolone benetonide and triamcinolone hexacetonide. Structurally related corticosteroids having similar anti-inflammatory properties are also intended to be encompassed by this group.
NSAIDs
Exemplary non-steroidal antiinflammatory drugs (NSAIDs) which can be used in the methods and compositions of the invention include, without limitation, naproxen sodium, diclofenac sodium, diclofenac potassium, aspirin, sulindac, diflunisal, piroxicam, indomethacin, ibuprofen, nabumetone, choline magnesium trisalicylate, sodium salicylate, salicylsalicylic acid (salsalate), fenoprofen, flurbiprofen, ketoprofen, meclofenamate sodium, meloxicam, oxaprozin, sulindac, and tolmetin.
Analgesics
Exemplary analgesics which can be used in the methods and compositions of the invention include, without limitation, morphine, codeine, heroin, ethylmorphine, O-carboxymethylmorphine, O-acetylmorphine, hydrocodone, hydromorphone, oxymorphone, oxycodone, dihydrocodeine, thebaine, metopon, ethorphine, acetorphine, diprenorphine, buprenorphine, phenomorphan, levorphanol, ethoheptazine, ketobemidone, dihydroetorphine and dihydroacetorphine.
Antimicrobials
Exemplary antimicrobials which can be used in the methods and compositions of the invention include, without limitation, penicillin G, penicillin V, methicillin, oxacillin, cloxacillin, dicloxacillin, nafcillin, ampicillin, amoxicillin, carbenicillin, ticarcillin, mezlocillin, piperacillin, azlocillin, temocillin, cepalothin, cephapirin, cephradine, cephaloridine, cefazolin, cefamandole, cefuroxime, cephalexin, cefprozil, cefaclor, loracarbef, cefoxitin, cefmatozole, cefotaxime, ceftizoxime, ceftriaxone, cefoperazone, ceftazidime, cefixime, cefpodoxime, ceftibuten, cefdinir, cefpirome, cefepime, BAL5788, BAL9141, imipenem, ertapenem, meropenem, astreonam, clavulanate, sulbactam, tazobactam, streptomycin, neomycin, kanamycin, paromycin, gentamicin, tobramycin, amikacin, netilmicin, spectinomycin, sisomicin, dibekalin, isepamicin, tetracycline, chlortetracycline, demeclocycline, minocycline, oxytetracycline, methacycline, doxycycline, erythromycin, azithromycin, clarithromycin, telithromycin, ABT-773, lincomycin, clindamycin, vancomycin, oritavancin, dalbavancin, teicoplanin, quinupristin and dalfopristin, sulphanilamide, para-aminobenzoic acid, sulfadiazine, sulfisoxazole, sulfamethoxazole, sulfathalidine, linezolid, nalidixic acid, oxolinic acid, norfloxacin, perfloxacin, enoxacin, ofloxacin, ciprofloxacin, temafloxacin, lomefloxacin, fleroxacin, grepafloxacin, sparfloxacin, trovafloxacin, clinafloxacin, gatifloxacin, moxifloxacin, gemifloxacin, sitafloxacin, metronidazole, daptomycin, garenoxacin, ramoplanin, faropenem, polymyxin, tigecycline, AZD2563, and trimethoprim.
Local Anesthetics
Exemplary local anesthetics which can be used in the methods and compositions of the invention include, without limitation, cocaine, procaine, lidocaine, prilocalne, mepivicaine, bupivicaine, articaine, tetracaine, chloroprocaine, etidocaine, and ropavacaine.
Antispasmodic
Exemplary antispasmodics which can be used in the methods and compositions of the invention include, without limitation, atropine, belladonna, bentyl, cystospaz, detrol (tolterodine), dicyclomine, ditropan, donnatol, donnazyme, fasudil, flexeril, glycopyrrolate, homatropine, hyoscyamine, levsin, levsinex, librax, malcotran, novartin, oxyphencyclimine, oxybutynin, pamine, tolterodine, tiquizium, prozapine, and pinaverium.
Matrix Coating
The matrix coatings of the invention can be designed to vary in adhesion to a surface by varying the size of oligomers, their solubility in physiological media, and/or employing oligomers which favorably interact with the surface on which the coating is placed. Such favorable interactions can include, for example, coordinatation (i.e., carboxylate groups coordinating to a metal surface), and/or hydrogen bonding between the oligomers and the device surface. In certain embodiments, the matrix coating is applied to the surface of the implantable medical device to form a thin coating (i.e., 0.5-5.0 microns in thickness). Because the matrix coatings of the invention do not have the properties of a base polymer, they are not susceptible to flaking or cracking during the physical manipulation of the device, such as the crimping and deployment of a stent. The matrix coatings of the invention control the release of biologically active agents incorporated within the matrix by limiting the rate of diffusion of the agent from the matrix. The modified release profile is achieved despite the low molecular weight of the matrix component and the self-eliminating or bioerodible nature of the coating.
A primary function of such coating can be to locally deliver a biologically active agent for a defined period of time and leave the device surface intact once the therapy period is completed. The matrix coating is optionally complexed, or covalently tethered, or physically combined with a biologically active agent, or applied in a mixture including a biologically active agent. The amount of biologically active agent loaded into the matrix coating will depend upon the desired local concentration and release profile from the matrix coating.
The matrix coating of the invention is significantly different from biodegradable and bioabsorbable polymers as the oligomers of the matrix remain intact during elimination from the surface of the device. In certain embodiments, a biologically active agent is covalently bound to an oligomer in the matrix via a hydrolyzable linker. In these embodiments, it is understood that the hydrolysis of the linker can occur either within the matrix or after diffusion of the biologically active agent from the surface of the device. It is desirable to limit hydrolytic degradation near the site of implantation to avoid localized changes in pH and the generation of inflammatory side products.
The matrix coatings of the invention can be applied to the surface of a medical device in any number of ways including, but not limited, to dipping, spraying, brushing, printing, or spin coating of the matrix coating material from a solution or suspension followed by solvent removal step as needed. Further description of how the matrix coatings can be applied is found in the Examples.
Coated Medical Devices
A wide variety of implantable medical devices can be coated using the compositions and methods of the invention. Implantable medical devices can be coated to improve their biocompatibility and to deliver biologically active agents at the site of implantation. The medical devices include, without limitation, catheters, guide wires, vascular stents, micro-particles, probes, sensors, drug depots, transdermal patches, vascular patches, and tubing. The medical device can be an implanted device, percutaneous device, or cutaneous device. Implanted devices include articles that are fully implanted in a patient, i.e., are completely internal. Percutaneous devices include items that penetrate the skin, thereby extending from outside the body into the body. Cutaneous devices are used superficially. Implanted devices include, without limitation, prostheses such as pacemakers, electrical leads such as pacing leads, defibrillators, artificial hearts, ventricular assist devices, anatomical reconstruction prostheses such as breast implants, artificial heart valves, heart valve stents, pericardial patches, surgical patches, coronary stents, vascular grafts, vascular and structural stents, vascular or cardiovascular shunts, biological conduits, pledges, sutures, annuloplasty rings, stents, staples, valved grafts, dermal grafts for wound healing, orthopedic spinal implants, orthopedic pins, intrauterine devices, urinary stents, maxial facial reconstruction plating, dental implants, intraocular lenses, clips, sternal wires, bone, skin, ligaments, tendons, and combination thereof. Percutaneous devices include, without limitation, catheters or various types, cannulas, drainage tubes such as chest tubes, surgical instruments such as forceps, retractors, needles, and catheter cuffs. Cutaneous devices include, without limitation, burn dressings, wound dressings and dental hardware, such as bridge supports and bracing components.
The following examples are put forth so as to provide those of ordinary skill in the art with a complete disclosure and description of how the methods and compounds claimed herein are performed, made, and evaluated, and are intended to be purely exemplary of the invention and are not intended to limit the scope of what the inventors regard as their invention.
The following acronyms denote the listed compounds.
ACD acid citrate dextrose
BAL poly(difluoromethylene), α-fluoro-ω-(2-hydroxyethyl)
BPH neopentyl glycol phthalic anhydride based polyester diol
CDCl3 deuterated chloroform
DBDL dibutyltin dilaurate
DCM dichloromethane
DIC diisopropylcarbodiimide
DL-PLGA DL-polylactic-co-glycolic acid polymer
DMAc dimethylacetamide
DMAP 4-(dimethylamino)pyridine
DMF dimethylformamide
DMSO dimethylsuiphoxide
EtO ethylene oxide
HCAEC human coronary artery endothelial cells
HCl hydrochloric acid
HLB hydroxy terminated polybutadiene
HPCN hexamethylene polycarbonate diol
KBr potassium bromide
KD dansyl labelled lysine
LDI lysine diisocyanate
MeOH methanol
NaOH sodium hydroxideExam
N2 nitrogen gas
OPCN methyl polycarbonate diol
PBS phosphate buffer solution
PCAEC porcine coronary artery endothelial cells
PEB polyethylene-co-butadiene diol
PET polyethylene terephthalate
PCL polycaprolactone
PTT partial thromboplastin time
PTMO polytetramethylene oxide
PTX paclitaxel
RBC red blood cell
SA salicylic acid
TEA triethylamine
THF tetrahydrofuran
TMX m-tetramethylxylene diisocyanate
Tween PBS 0.05% Tween 20 in phosphate buffer solution
Cationic Solid Phase Extraction (SCX-SPE): A pre-packed cationic silica gel column (plastic) is used to remove small cationic compounds from the reaction mixtures.
Fluorous Solid Phase Extraction (F-SPE): SPE substrates modified with perfluorinated ligands (F-SPE) are used to selectively retain perfluorinated oligomers, allowing the separation of non-fluorinated compounds.
Elemental analysis: samples are combusted, and the liberated fluorine is absorbed into water and analyzed by ion-selective electrode.
FTIR analysis: a sample is dissolved as a 20 mg/mL solution in a suitable volatile solvent and 50 μL of this solution is cast on a KBr disk. Once dried, the sample is analyzed.
GPC analysis: samples are dissolved as a 20 mg/mL solution in a suitable solvent (THF, dioxane, DMF) and are analyzed using a polystyrene column calibrated with polystyrene standards.
NMR: samples are dissolved at 20 mg/mL in a suitable solvent and are analyzed using a 300 or 400 MHz NMR spectrometer.
SEM: surfaces are coated with gold and images taken with an accelerating volatage of 20 kV.
XPS analysis: films are analyzed using a 90° take-off angle.
Oligomers: fluorinated and non fluorinated oligomers of different chemical compositions are made to evaluate their coating, residency time and compatibility with pharmaceutical compounds.
Pharmaceuticals: these compounds are selected according to mode of cellular interactions and functional groups available for interactions with drug delivery matrix.
Coating: coating methods are developed to demonstrate and establish thin coating of oligomers.
Residency time: flow and sink conditions (artificial urine, porcine blood, bovine blood, porcine plasma and cardiac muscle) are used to measure residency time
PTMO (15.0 g, 14 mmol) was reacted with LDI (5.9 g, 28 mmol) in DMAc (80 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. Perfluoroalcohol (13.15 g, 31 mmol) was dissolved in DMAc (25 mL), added to the reaction, and stirred at room temperature overnight under N2. The product (Compound 1) was purified by solvent extraction and cationic SPE. GPC (dioxane mobile phase): retention time of 25 minutes. 1H NMR (400 MHz, CDCl3) δ (ppm) 4.24-4.46 (—CH2—O, BAL), 3.94-4.13 (—CH2—O—CO, PTMO), 3.74 (CH3, LDI), 3.28-3.50 (CH2—O, PTMO), 2.98-3.28 (CH2—NH, LDI), 2.29-2.60 (—CH2—CF2—, BAL), 1.16-1.96 (PTMO and LDI CH2). IR analysis was in accordance with the chemical structure: 3318 cm−1 v(N—H) H-bonded, 2930 cm−1 v(C—H), 2848 cm−1 v(C—H), 1712 cm−1 v(C═O) urethane amide, 1524 cm−1 v(C—N), 1438 cm−1 v(C—N), 1356 cm−1 v(C—O), 1400-1000 cm−1 v(C—F). Elemental analysis: 20% F. DSC analysis: Tg=−69° C. Compound 1 was further purified by dissolving in MeOH and dialyzing for three days using 1000 MWCO regenerated cellulose membranes (Compound 1-D).
Compound 1 was dissolved in MeOH and treated with 1N NaOH. The product (Compound 2) was neutralized with 1N HCl, precipitated in water, and dried. GPC (dioxane mobile phase): retention time of 25 minutes. 1H NMR (400 MHz, CDCl3) δ (ppm) 4.26-4.48 (—CH2—O, BAL), 3.96-4.23 (—CH2—O—CO, PTMO), 3.30-3.52 (CH2—O, PTMO), 3.07-3.22 (CH2—NH, LDI), 2.36-2.55 (—CH2—CF2—, BAL), 1.14-1.94 (PTMO and LDI CH2). IR analysis was in accordance with the chemical structure: 3318 cm−1 v(N—H) H-bonded, 2930 cm−1 v(C—H), 2848 cm−1 v(C—H), 1712 cm−1 v(C═O) urethane amide, 1524 cm−1 v(C—N), 1438 cm−1 v(C—N), 1356 cm−1 v(C—O), 1400-1000 cm−1 v(C—F). Compound 2 was further purified by dissolving in MeOH and dialyzing for three days using 1000 MWCO regenerated cellulose membranes (Compound 2-D).
Compound 2-D (2.0 g, 1.71 mmol acid) was dissolved in anhydrous DMF (25 mL). The solution was chilled, DIC (0.215 g, 1.71 mmol) was added and the solution was stirred for 2 hours at room temperature under N2. TEA (0.345 g, 3.41 mmol) and dansyl-labelled lysine (KD) (0.718 g, 1.71 mmol) in anhydrous DMF (9 mL) were added to the activated Compound 2-D, and the solution was kept well stirred for 12 hours at room temperature under N2. The product (Compound 3) was purified with cationic and fluorous SPE, and recovered by rotary evaporation. GPC (dioxane mobile phase): no free KD was detected, and the polymer peak had strong UV absorbance. 1H NMR (400 MHz, CDCl3) δ (ppm) 7.14-8.59 (aromatic H, KD) 4.46-4.66 (CH2—N, KD), 4.28-4.48 (—CH2—O, BAL), 3.90-4.17 (—CH2—O—CO, PTMO), 3.31-3.54 (CH2—O, PTMO), 3.06-3.26 (CH2—NH, LDI), 2.81-3.00 (CH3, KD) 2.32-2.58 (—CH2—CF2—, BAL), 1.08-1.94 (CH2, PTMO, LDI and KD). High performance liquid chromatography (HPLC) analysis of Compound 3: samples ranging in concentration from 0.0005 to 50 mg/mL in MeOH were injected and analyzed using an MeOH/pH 9 buffer mobile phase. Free KD (standard solution) eluted at 21 minutes, and Compound 3 eluted at 35 minutes with no evidence of free KD contamination (
Compound 2-D (1.5 g, 1.36 mmol acid) was dissolved in anhydrous DCM (150 mL). The solution was chilled, DIC (0.342 g, 2.71 mmol) was added and the solution was stirred for 2 hours at room temperature under N2. DMAP (0.496 g, 4.07 mmol) and PTX (2.31 g, 2.71 mmol) in anhydrous DCM (75 mL) were added to the activated Compound 2-D, and the solution was kept well stirred for three days at room temperature under N2. The product (Compound 4) was purified with fluorous SPE, and recovered by rotary evaporation. GPC (dioxane mobile phase): no free PTX was detected, and the polymer peak had a strong UV absorbance. 1H NMR (300 MHz, DMSO) δ (ppm) 7.11-8.15 (aromatic H, PTX), 6.24-6.30 (C10), 5.79-5.88 (C3′), 5.53-5.63 (C2′ conjugated), 5.32-5.44 (C2), 4.81-4.93 (C5), 4.56-4.62 (C7), 4.16-4.35 (—CH2—O, BAL), 3.84-3.96 (—CH2—O—CO, PTMO), 3.13-3.40 (CH2—O, PTMO), 2.21-2.27 (OAc, C4), 2.02-2.09 (OAc, C10), 1.68-1.70 (C18), 1.04-1.60 (CH2, PTMO, LDI), 0.90-1.02 (C16, C17).
PTMO (15.0 g, 14 mmol) was reacted with LDI (5.9 g, 28 mmol) in DMAc (60 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. MeOH (0.9 g, 28 mmol) was dissolved in DMAc (25 mL), added to the reaction, and stirred at room temperature overnight under N2. The product (Compound 5) was purified by solvent extraction and cationic SPE. GPC (dioxane mobile phase): 26 minutes. 1H NMR (300 MHz, CDCl3) δ (ppm) 4.27-4.39 (—CH—, LDI), 4.02-4.14 (—CH2—O—CO, PTMO), 3.73-3.78 (CH3, LDI), 3.60-3.70 (—OCH3, MeOH), 3.30-3.53 (CH2—O, PTMO), 3.09-3.21 (CH2—NH, LDI), 1.22-1.91 (PTMO and LDI CH2).
PTMO (15.0 g, 14 mmol) was reacted with TMX (6.79 g, 28 mmol) in DMAc (60 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. Perfluoroalcohol (12.85 g, 30 mmol) was dissolved in DMAc (20 mL), added to the reaction, and stirred at room temperature overnight under N2. The product (Compound 6) was purified by solvent extraction. GPC (dioxane mobile phase): retention time of 26.5 minutes. 1H NMR (300 MHz, CDCl3) δ (ppm) 7.2-7.4 (—CH—, TMX), 4.23-4.37 (—CH2—O—, BAL), 3.9-4.06 (—CH2—O—CO, PTMO), 3.32-3.52 (CH2—O, PTMO), 2.29-2.57 (—CH2—CF2—, BAL), 1.16-1.96 (—CH2—PTMO and —CH3 TMX). IR analysis was in accordance with the chemical structure: 3308 cm−1 v(N—H) H-bonded, 2936 cm−1 v(C—H), 2852 cm−1 v(C—H), 1716 cm−1 v(C═O) urethane amide, 1520 cm−1 v(C—N), 1456 cm−1 v(C—N), 1362 cm−1 v(C—O), 1400-1000 cm−1 v(C—F). DSC analysis: Tg=−55° C. Compound 6 was further purified by dissolving in MeOH and dialyzing for three days using 1000 MWCO regenerated cellulose membranes (Compound 6-D).
PCL diol (10 g, 8 mmol) was reacted with LDI (3.39 g, 16 mmol) in DMAc (17 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. Perfluoroalcohol (7.39 g, 18 mmol) was dissolved in DMAc (20 mL), added to the reaction, and stirred at room temperature overnight under N2. The product (Compound 7) was purified by solvent extraction and cationic SPE. GPC (dioxane mobile phase): retention time of 26.8 minutes, no free PCL diol detected. 1H NMR (400 MHz, CDCl3) δ (ppm) 4.27-4.48 (—CH2—O, BAL), 4.17-4.26 (—CH2—O—CO—N, PCL), 3.96-4.12 (—CH2—O—CO—, PCL), 3.71-3.76 (CH3, LDI), 3.09-3.22 (CH2—NH, LDI), 2.39-2.53 (—CH2—CF2—, BAL), 2.26-2.38 (CO—CH2—, PCL), 1.13-1.76 (PCL and LDI CH2). DSC analysis: Tg=−53° C., Tm=39° C. Compound 7 was further purified by dissolving in acetone and dialyzing for three days using 1000 MWCO regenerated cellulose membranes (Compound 7-D).
Methyl polycarbonate diol (OPCN, 10.0 g, 10 mmol) was reacted with LDI (4.24 g, 20 mmol) in anhydrous DMAc (70 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. Perfluoroalcohol (9.24 g, 22 mmol) was dissolved in anhydrous DMAc (25 mL), added to the reaction, and stirred at room temperature overnight under N2. The product (Compound 8) was purified by solvent extraction and cationic SPE. GPC (dioxane mobile phase): retention time of 24.7 minutes. 1H NMR (400 MHz, CDCl3) δ (ppm) 4.27-4.51 (—CH2—O, BAL), 3.82-4.07 (—CH2—O, OPCN), 3.65-3.80 (—CH3, LDI), 3.07-3.27 (CH2—NH, LDI), 2.32-2.59 (—CH2—CF2—, BAL), 1.18-1.94 (CH2, LDI), 0.84-1.09 (—CH3, OPCN). DSC analysis: Tg=−3° C. Compound 8 was further purified by dissolving in acetone and dialyzing for three days using 1000 MWCO regenerated cellulose membranes (Compound 8-D).
Hexamethylene polycarbonate diol (HPCN, 10.0 g, 5 mmol) was reacted with LDI (2.12 g, 10 mmol) in anhydrous DMAc (65 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. Perfluoroalcohol (4.62 g, 11 mmol) was dissolved in anhydrous DMAc (15 mL), added to the reaction, and stirred at room temperature overnight under N2. The product (Compound 9) was purified by solvent extraction and cationic SPE. GPC (dioxane mobile phase): retention time of 24.2 minutes. 1H NMR (400 MHz, CDCl3) δ (ppm) 4.30-4.43 (—CH2—O, BAL), 3.97-4.22 (—CH2—O, HPCN), 3.69-3.78 (—CH3, LDI), 3.10-3.23 (CH2—NH, LDI), 2.37-2.55 (—CH2—CF2—, BAL), 1.13-1.89 (CH2, LDI and HPCN). DSC analysis: Tg=−40° C. Compound 9 was further purified by dissolving in acetone and dialyzing for three days using 1000 MWCO regenerated cellulose membranes (Compound 9-D).
PEB diol (14.96 g, 6.0 mmol) was reacted with LDI (2.54 g, 12.0 mmol) in anhydrous toluene (60 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. Perfluoroalcohol (5.541 g, 13.2 mmol) was dissolved in anhydrous toluene (20 mL) with slight heating, added to the reaction, and stirred at 70° C. overnight under N2. The product (Compound 10) was purified by solvent extraction and cationic SPE. GPC (THF mobile phase): retention time of 21 minutes. 1H NMR (300 MHz, CDCl3) δ (ppm) 4.29-4.45 (CH2—O, BAL), 4.02-4.11 (—CH—, LDI, —CH—O—CO, PEB), 3.92-4.02 (—CH2—O—CO, PEB), 3.75 (—CH3, LDI), 3.10-3.22 (—CH2—NH—, LDI), 2.38-2.57 (—CH2—CF2—, BAL), 0.76-1.92 (—CH2 PEB and LDI, —CH3, —CH—PEB). DSC analysis: Tg=−16° C.
PEB diol (15.10 g, 6.0 mmol) was reacted with TMX (2.94 g, 12.1 mmol) in anhydrous toluene (60 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. Perfluoroalcohol (5.55 g, 13.2 mmol) was dissolved in anhydrous toluene (20 mL) with slight heating, added to the reaction, and stirred at 70° C. overnight under N2. The product (Compound 11) was purified by solvent extraction and cationic SPE. GPC (THF mobile phase): retention time of 21.5 minutes. 1H NMR (300 MHz, CDCl3) δ (ppm) 7.20-7.48 (—CH—, TMX), 4.22-4.37 (—CH2—O, BAL), 3.90-4.03 (—CH—O—CO, PEB), 3.85-3.92 (—CH2—O—CO, PEB), 2.33-2.55 (—CH2—CF2—, BAL), 0.71-1.72 (—CH2—, CH3, —CH—, PEB and —CH3, TMX). DSC analysis: Tg=−13° C.
LBH-P hydrogenated hydroxyl terminated polybutadiene (HLB, 10.0 g, 5 mmol) was reacted with LDI (2.12 g, 10 mmol) in anhydrous toluene (65 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. Perfluoroalcohol (4.62 g, 11 mmol) was dissolved in anhydrous toluene (15 mL), brought to 45° C., added to the reaction, and stirred at room temperature overnight under N2. The product (Compound 12) was purified by solvent extraction and cationic SPE. GPC (dioxane mobile phase): retention time of 23.9 minutes. 1H NMR (400 MHz, CDCl3) δ (ppm) 4.28-4.46 (—CH2—O, BAL), 4.00-4.14 (—CH2—O, HLB), 3.72-3.80 (—CH3, LDI), 3.08-3.22 (CH2—NH, LDI), 2.37-2.54 (—CH2—CF2—, BAL), 0.57-1.75 (CH2 and CH, LDI and HLB). DSC analysis: Tg=−49° C.
Neopentyl glycol phthalic anhydride based polyester diol (BPH, 10.0 g, 10 mmol) was reacted with LDI (4.24 g, 20 mmol) in anhydrous DMAc (70 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. Perfluoroalcohol (9.24 g, 22 mmol) was dissolved in anhydrous DMAc (25 mL), added to the reaction, and stirred at room temperature overnight under N2. The product (Compound 13) was purified by solvent extraction and cationic SPE. GPC (dioxane mobile phase): retention time of 25.4 minutes. 1H NMR (400 MHz, CDCl3) δ (ppm) 7.41-7.79 (aromatic H, BPH), 4.25-4.44 (—CH2—O, BAL), 4.05-4.21 (—CH2—O, BPH), 3.67-3.79 (—CH3, LDI), 3.06-3.25 (CH2—NH, LDI), 2.32-2.56 (—CH2—CF2—, BAL), 1.26-1.90 (CH2, LDI), 0.86-1.11 (—CH3, BPH).
PTMO (5.0 g, 5 mmol) was reacted with LDI (1.59 g, 7.5 mmol) in anhydrous DMAc (35 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. Perfluoroalcohol (2.31 g, 5.5 mmol) was dissolved in anhydrous DMAc (10 mL), added to the reaction, and stirred at room temperature overnight under N2. The product (Compound 14) was purified by solvent extraction and cationic SPE. GPC (dioxane mobile phase): retention time of 24 minutes. 1H NMR (400 MHz, CDCl3) δ (ppm) 4.23-4.49 (—CH2—O, BAL), 4.00-4.18 (—CH2—O, PTMO), 3.69-3.79 (—CH3, LDI), 3.30-3.59, —CH2—O, PTMO), 3.09-3.25 (CH2—NH, LDI), 2.37-2.57 (—CH2—CF2—, BAL), 1.09-1.94 (CH2, LDI and PTMO). Elemental analysis: 13.7 wt % F.
PTMO (5.0 g, 5 mmol) was reacted with LDI (1.27 g, 6 mmol) in anhydrous DMAc (35 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. Perfluoroalcohol (0.92 g, 2.2 mmol) was dissolved in anhydrous DMAc (5 mL), added to the reaction, and stirred at room temperature overnight under N2. The product (Compound 15) was purified by solvent extraction and cationic SPE. GPC (dioxane mobile phase): retention time of 23 minutes. 1H NMR (400 MHz, CDCl3) δ (ppm) 4.27-4.44 (—CH2—O, BAL), 3.98-4.17 (—CH2—O, PTMO), 3.69-3.79 (—CH3, LDI), 3.27-3.52, —CH2—O, PTMO), 3.09-3.22 (CH2—NH, LDI), 2.34-2.54 (—CH2—CF2—, BAL), 1.01-1.90 (CH2, LDI and PTMO). Elemental analysis: 4.3 wt % F.
PTMO (10.0 g, 10 mmol) was reacted with LDI (2.32 g, 10.9 mmol) in anhydrous DMAc (115 mL) in the presence of DBDL catalyst, at 70° C. for two hours under N2. Perfluoroalcohol (0.84 g, 2 mmol) was dissolved in anhydrous DMAc (5 mL), added to the reaction, and stirred at room temperature overnight under N2. The product (Compound 16) was purified by solvent extraction and cationic SPE. GPC (dioxane mobile phase): retention time of 22 minutes. 1H NMR (400 MHz, CDCl3) δ (ppm) 4.27-4.44 (—CH2—O, BAL), 3.98-4.17 (—CH2—O, PTMO), 3.69-3.79 (—CH3, LDI), 3.27-3.52 (—CH2—O, PTMO), 3.09-3.22 (CH2—NH, LDI), 2.34-2.54 (—CH2—CF2—, BAL), 1.01-1.90 (CH2, LDI and PTMO). Elemental analysis: 1.3 wt % F.
Compound 1 (1.0 g) was dissolved in toluene, stirred for 24 hours at room temperature and kept at room temperature until use. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 1, and the stents were placed in a 50° C. flow oven for 20-24 hours for drying. SEM analysis (
Compound 2 (1.0 g) was dissolved in THF:toluene, stirred for 24 hours at room temperature and kept at room temperature until use. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 2, and the stents were placed in a 50° C. flow oven for 20-24 hours for drying. SEM analysis (
Compound 3 (0.2 g) was dissolved in THF:toluene, stirred for 24 hours at room temperature, and used immediately. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 3, and the stents were placed in a 50° C. flow oven for 20-24 hours for drying. Confocal/fluorescence microscopy images were taken and indicated the presence of coating on the stents (
Compound 4 (0.2 g) was dissolved in toluene and stirred for 24 hours at room temperature. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 4, and the stents were dried in a 50° C. flow oven for 20-24 hours. SEM analysis (
Compound 5 (0.2 g) was dissolved in toluene, stirred for 24 hours at room temperature, and stored at room temperature until use. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 5, and the stents were placed in a 50° C. flow oven for 20-24 hours for drying. SEM images (
Compound 6 (0.2 g) was dissolved in toluene, stirred for 24 hours at room temperature, and stored at room temperature until use. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 6, and the stents were placed in a 50° C. flow oven for 20-24 hours for drying. SEM images (
Compound 7 (0.2 g) was dissolved in toluene, and stirred for 24 hours at room temperature until used for coating. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 7. The stents were dried in a 50° C. flow oven for 20-24 hours. SEM image collection was used to validate the coating quality (
Compound 8 (0.4 g) was dissolved in THF, stirred for 24 hours at room temperature and used for coating. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 8. The stents were dried at room temperature in a fume hood for 24 hours. SEM images (
Compound 9 (0.4 g) was dissolved in THF, stirred for 24 hours at room temperature and used for coating. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 9. The stents were dried at room temperature in a fume hood for 24 hours. SEM images (
Compound 10 (0.2 g) was dissolved in toluene, stirred for 24 hours at room temperature and used for coating. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 10. The stents were dried in a 50° C. flow oven for 20-24 hours. SEM images (
Compound 11 (0.2 g) was dissolved in toluene, stirred for 24 hours at room temperature and used for coating. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 11. The stents were dried in a 50° C. flow oven for 20-24 hours. SEM images (
Compound 12 (0.4 g) was dissolved in chloroform, stirred for 24 hours at room temperature and used for coating. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 12. The stents were dried at room temperature in a fume hood for 3 days. SEM images (
Compound 14 (0.4 g) was dissolved in THF, stirred for 24 hours at room temperature and used for coating. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 14. The stents were dried at room temperature in a fume hood for 3 days. SEM images (
Compound 15 (0.4 g) was dissolved in THF, stirred for 24 hours at room temperature and used for coating. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 15. The stents were dried at room temperature in a fume hood for 3 days. SEM images (
Compound 1 (0.2 g) was dissolved in THF and added to Compound 7 (0.2 g) that was dissolved in THF. The resulting solution was stirred for 24 hours at room temperature and used for coating. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 1+7. The stents were dried at room temperature in a fume hood for 3 days. SEM images (
Compound 2 (0.332 g) and PTX (0.032 g) were dissolved in THF:toluene, stirred for 24 hours at room temperature, and used immediately. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 2+PTX, and the stents were placed in a 50° C. flow oven for 20-24 hours for drying. SEM analysis (
Compound 6 (0.332 g) and PTX (0.032 g) were dissolved in THF:toluene, was stirred for 24 hours at room temperature, and used immediately. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 6+8.8 wt % PTX, and the stents were placed in a 50° C. flow oven for 20-24 hours for drying. SEM analysis (
Compounds 1, 2, 5, 6 and 7 (0.075 g) were mixed with SA (0.025 g) in MeOH under nitrogen protection, stirred, and were separated from solvent by rotary evaporation and vacuum drying. Controls were also prepared: Compounds 1, 2, 5, 6, and 7 (0.075 g) were dissolved in MeOH and were separated from solvent by rotary evaporation and vacuum drying. To each vial (Compounds with SA and controls) PBS (10 mL) was added, and SA release was measured from diluted samples using a UV/Vis spectrophotometer at 294 nm at 1, 2, 3, 4, 6 and 24 hours. A Beer-Lambert calibration plot was prepared using solutions of SA (0-0.05 mg/mL SA). Compound 1+SA: (1 hour)=1.137, (2 hour)=0.248, (3 hour)=0.120, (4 hour)=0.247, (6 hour)=0.136, (24 hour)=0.651. Compound 2+SA: (1 hour)=1.249, (2 hour)=0.316, (3 hour)=0.084, (4 hour)=0.207, (6 hour)=0.305, (24 hour)=0.373. Compound 5+SA: (1 hour)=0.518, (2 hour)=0.230, (3 hour)=0.166, (4 hour)=0.268, (6 hour)=0.583, (24 hour)=0.873. Compound 6+SA: (1 hour)=0.882, (2 hour)=0.364, (3 hour)=0.218, (4 hour)=0.282, (6 hour)=0.424, (24 hour)=0.687. Compound 7+SA: (1 hour)=0.689. The chemical composition and functional groups with in the formulation highlights the tunability of the coating matrix for a desired release profile. The amount of SA in media shows the ability of the platform to not only interact but also release the pharmaceutical component.
Compounds 1, 2, and 6 were combined with PTX at 5, 8.8 and 20 wt % in DCM, and aliquots of each solution (0.1 mL) were transferred to 4 mL glass vials in duplicate. The solvent was flashed off, and the vials were dried under vacuum at ambient temperatures. Tween PBS (1 mL) was added to each vial, and the vials were incubated at 37° C. After 1 hour, the buffer was withdrawn and PTX content was analyzed by HPLC (
Compounds 1 and 6 were combined with PTX at 5 and 8.8 wt % in DCM, and aliquots of each solution (0.1 mL) were transferred to 4 mL glass vials in duplicate. Tween PBS (1 mL) was added to each vial, and the vials were incubated at 20 and 37° C.
At selected time-points (1, 2, 3, 4, and 5 days) the buffer was withdrawn for PTX analysis by HPLC (
Compound 1 and SIBS were weighed into 4 mL glass vials as described in Table 1, and were dissolved in THF:toluene. PTX (0.04 g) was dissolved in THF:toluene, and PTX solution was added the Compound 1 and SIBS solutions (0.001 g PTX per vial) and mixed overnight. The solvent was rapidly removed from each vial under vacuum and dried overnight. Tween PBS (1 mL) was added to each vial, and the release of PTX was measured by HPLC after 24 hours (Table 1).
The data shows the enhanced differences in efficiency between conventional base polymer drug release and self eliminating drug release.
Compound 1 (0.33 g) was dissolved in THF:toluene, mixed with a PTX solution (0.032 g/mL), stirred for 24 hours at room temperature, and used immediately. The solution was sprayed onto stents using an EFD spray system with settings specific to Compound 1+8.8 wt % PTX, and the stents were dried in a 50° C. flow oven for 20-24 hours. SEM analysis (
Compounds 1, 6, 7, 1+7, 8, 9, and 12 (0.4 g) were dissolved in THF, mixed with a PTX solution (0.032 g/mL), stirred for 24 hours at room temperature, and used immediately. The solutions were sprayed onto stents using an EFD spray system with settings specific to each Compound+1 wt % PTX. The stents were dried at room temperature in a fume hood for 4 days. SEM analyses (
Compound 1 (0.40 g) and PTX (0.0386 g) were dissolved in toluene:THF and stirred overnight. Stainless steel coupons (1.5 g) with dimensions of approximately 3.5 cm×1 cm were immersed in acetone, sonicated for 45 minutes, and were dried in a 50° C. flow oven overnight. One side of each coupon was coated with the solution, and the average mass of Compound 1+PTX on individual coupons was measured (0.005-0.008 g). The coated sides of the stainless steel coupons were placed in contact with cardiac muscle (7.0-13.0 g), and were secured with umbilical tape (
Compound 1 (0.405 g) and PTX (0.004 g) were dissolved in toluene:THF and stirred overnight. Stainless steel coupons (1.5 g) with dimensions of approximately 3.5 cm×1 cm were immersed in acetone, sonicated for 45 minutes, and dried in 50° C. flow oven overnight. One side of each coupon was coated with the solution, and the average mass of Compound 1+PTX on individual coupons was measured (0.005-0.008 g). The coated sides of the stainless steel coupons were placed in contact with cardiac muscle (7.0-13.0 g), and were secured with umbilical tape. At selected time-points (1 and 24 hours), triplicate test articles and duplicate control articles were removed, rinsed with water, and dried in 50° C. flow oven overnight. The coating was then stripped off with THF (15 mL) for 3 days and an aliquot (1 mL) of stripping solution was submitted for HPLC analysis (acetonitrile: water mobile phase) to determine the average PTX remaining on the coupons (
Stainless steel coupons prepared as in Example 40 were incubated in porcine blood (4 mL). After 1 hour, triplicate test articles and duplicate control articles were rinsed with water, dried at 50° C. overnight, and weighed. The coatings were then stripped off with THF (15 mL) for 3 days and an aliquot
(1 mL) of stripping solution was submitted for HPLC analysis (acetonitrile:water mobile phase) to determine the average PTX remaining on the coupons. Control (ng/mL): (by weight)=32888, (HPLC)=38405. 1 hour sample (ng/mL): (by weight)=34667, (HPLC)=40962.
All vials were pre-dried in the oven overnight and tared. Compounds 1, 2, 3, 6, 7, 1+7, 8, 9, 10, 11, 12, 14, 15 and 16 (0.2 g) were weighed into the vials, PBS was added (4 mL), and each vial was then incubated at 37° C. At selected time-points (1, 3, 7, 14 and 21 days) vials were isolated and rinsed with copious amounts of water to remove residual salt, dried in a 50° C. flow oven overnight, and weighed. The residency time was calculated by measuring the percentage of mass loss at each time point (
Compound 1 (0.20 g), Compound 10 (0.22 g), and Compound 12 (0.20 g) were dissolved in toluene. Compound 1+7 (0.20 and 0.30 g) was dissolved in THF, and Compound 2 (0.20 g) was dissolved in THF: toluene. Stainless steel coupons (1.5 g) with dimensions of approximately 3.5 cm×1 cm were immersed in acetone, sonicated for 45 minutes, and dried in a 50° C. flow oven overnight. Both sides of the coupons were coated with each Compound solution and the average weight of Compound was measured (0.020-0.040 g). Every coupon was placed in a vial and incubated with PBS (15 mL) at 37° C. At selected time-points (1 and 14 days), the coupons were isolated and rinsed with copious amounts of water and dried in a 50° C. flow oven. The residency time was calculated by measuring the percentage of mass loss at each time point (
All vials were pre-dried in the oven overnight and tared. Compounds 1, 2, 6, 1+7, and 12 (0.2 g) were weighed into the vials, porcine blood (4 mL) was added to each vial, and incubated at 4° C. At selected time-points (1, 3, 7 and 14 days), vials were isolated and rinsed with copious amounts of water and dried in a 50° C. flow oven overnight. The residency time was calculated by measuring the percentage of mass loss after incubation at each time point (
Compound 1 (0.20 g), Compound 10 (0.22 g), and Compound 12 (0.20 g) were dissolved in toluene. Compound 2 (0.20 g) was dissolved in THF: toluene. Stainless steel coupons (1.5 g) with dimensions of approximately 3.5 cm×1 cm were immersed in acetone, sonicated for 45 minutes, and dried in a 50° C. flow oven overnight. Both sides of the coupons were coated with each Compound solution, the average weight of Compound was measured (0.020-0.040 g), and incubated with porcine blood (15 mL) at 4° C. At selected time-points (1 and 14 days) coupons were isolated and rinsed with copious amounts of water and dried in a 50° C. flow oven. The residency time was measured by the percentage of mass loss at the end of each time point (
All vials were pre-dried in the oven overnight and tared. Compounds 1, 2, 6, 7, 1+7, 10, and 12 (0.2 g) were weighed in the vials and incubated in artificial urine (4 mL) at 37° C. At selected time-points (1, 3, 7, 14, and 21 days), vials were isolated, rinsed with copious amounts of water, dried in a 50° C. flow oven overnight, and weighed. The residency time was calculated by measuring the percentage of mass loss after incubation (
Compounds 1, 2, 4 and 6 (1.05 g) were dissolved in toluene. Stainless steel coupons (1.5 g) with dimensions of approximately 3.5 cm×1 cm were immersed in acetone, sonicated for 45 minutes, and dried in a 50° C. flow oven overnight. Both sides of the coupons were coated with the Compound solutions and the average weight of Compound was measured (0.008-0.012 g). Silicone tubing and PVC tubing were cut 5 cm and 3 cm in length, respectively. Each of the coated coupons were inserted into a silicone tubing segment and labeled. All silicone tubing segments were then connected together by PVC tubing. Clean silicone tubing (100 cm) was wrapped around the head of a peristaltic pump. The outlet was connected to the silicone tubing segments containing coated coupons. PBS was pumped aggressively through the loop system from a PBS reservoir (1000 mL). At selected time-points (2 and 6 hours for Compounds 1, 2, and 6, and 0.5, 1, and 2 hours for Compound 4) triplicate coupons were isolated and rinsed with water several times, dried, and weighed. The residency times were calculated by measuring the percentage of mass loss after each time-point (
Compounds 1, 2, and 6 (0.50 g) were dissolved in toluene. Stainless steel coupons (1.5 g) with dimensions of approximately 3.5 cm×1 cm were immersed in acetone, sonicated for 45 minutes, and dried in a 50° C. flow oven overnight. Both sides of the coupons were coated with Compound solutions and the average mass of Compound was measured (0.008 to 0.012 g). Silicone tubing and PVC tubing were cut 5 cm and 3 cm in length, respectively. Each of the coated coupons were inserted into a silicone tubing segment and labeled. All silicone tubing segments were then connected together by PVC tubing. Clean silicone tubing (100 cm) was wrapped around the head of a peristaltic pump. The outlet was connected to the silicone tubing segments containing coated coupons. Porcine blood was pumped aggressively through the loop system from a porcine blood reservoir (1000 mL). At selected time-points (2 and 6 hours) triplicate coated coupons and duplicate control coupons were isolated, rinsed with water several times, dried, and weighed. The residency time was calculated by measuring the percentage of mass loss after incubation at each time point (
Compounds 1, 2 and 6 (0.50 g) were dissolved in toluene. Stainless steel coupons (1.5 g) with dimensions of approximately 3.5 cm×1 cm were immersed in acetone, sonicated for 45 minutes, and dried in 50° C. flow oven overnight. Both sides of the coupons were coated with Compound solutions and the average mass of Compound was measured (0.008 to 0.012 g). Silicone tubing and PVC tubing were cut 5 cm and 3 cm in length, respectively. Each of the coated coupons were inserted into a silicone tubing segment and labeled. All silicone tubing segments were then connected together by PVC tubing. Clean silicone tubing (100 cm) was wrapped around the head of a peristaltic pump. The outlet was connected to the silicone tubing segments containing coated coupons. Artificial urine was pumped aggressively through the loop system from an artificial urine reservoir (1000 mL). At selected time-points (2 and 6 hours) triplicate coated coupons and duplicate control (uncoated) coupons were isolated, rinsed with water several times, dried, and weighed. The residency time was calculated by measuring the percentage of mass loss after incubation at each time point (
Compounds 1, 2, and 6 (0.5 g) were dissolved in toluene. Stainless steel coupons (1.5 g) with dimensions of approximately 3.5 cm×1 cm were immersed in acetone, sonicated for 45 minutes, and dried in a 50° C. oven overnight. Both sides of the coupons were coated with Compound 1, 2 and 6 solutions and the average mass of Compound was measured (0.008 to 0.012 g). Porcine hearts were thawed and washed with water. A pocket incision 5.5 cm wide was made in the left ventricle of the porcine hearts using a scalpel. The incisions penetrated into the ventricle cavity (
Compounds 1, 2, 3, 6, 7, 1+7, 8, 9, 10, 11, 12, 14, 15, and 16 (0.16-0.20 g) were weighed into pre-dried vials and incubated in PBS (4 mL) at 37° C. At selected time-points (1, 3, 7, 14, 21, 30, 45, 60, 75, 90, 105, 120, 135, 150 days) the PBS was withdrawn, and the Compounds were rinsed with water and dried in a 50° C. flow oven overnight. Compounds were weighed the following day and re-incubated with PBS at 37° C. The cycle of PBS removal-water rinsing-drying-re-incubation was repeated until day 150. The residency time was measured by the percentage of mass loss of each Compound at each time point (
The partitioning of Compounds synthesized in Examples 1-13 was measured in a 1-octanol/PBS system. The partitioning correlates with the lipophilicity of the Compounds, and is used to predict the adsorption and distribution of Compounds under investigation. 1-octanol and PBS were thoroughly mixed to provide PBS-saturated 1-octanol in the top phase and 1-octanol-saturated PBS in the bottom phase. Solutions of Compounds 1, 2, 3, 6, 7, 8, 9, 10, 11, 12, 16, PTX, and SIBS (0.05 mL) were added to each vial of 1-octanol/PBS. The vials were rocked for 4 hours, ensuring good contact between the phases. An aliquot of the organic phase from each sample was then analyzed by GPC (THF mobile phase, R1), which had been calibrated using known concentrations of each compound. The area under the R1 peak was used to estimate the concentration of each compound in the organic phase. The mass of each Compound was then used to calculate the weight percentage in organic phase by the following formula: (mass of Compound in 1-octanol phase/total mass)×100%. The partition coefficient was calculated according to the following formula: log([Compound in 1-octanol]/[Compound in PBS]). Results (wt % in 1-octanol, partition coefficient): Compound 1 (86%, 0.80), Compound 2 (78%, 0.54), Compound 3 (96%, 1.42), Compound 6 (86%, 0.80), Compound 7 (85%, 1.50), Compound 8 (94%, 1.20), Compound 9 (91%, 1.00), Compound 10 (93%, 1.14), Compound 11 (99%, 2.37), Compound 12 (98%, 1.64), SIBS (93%, 1.54), PTX (94%, 1.00).
Compounds 1, 2, 6, 7, 8, 9, 12, 14, 15, and 16 (0.05 g) were incubated in Tween PBS or water for 24 hours at room temperature. Tween PBS solutions and water were withdrawn and filtered through 0.45 μm filter discs and dried in a flow oven at 50° C. for 2 days. Dried samples were analyzed by 1H NMR, and the soft segment assignments were used to quantitatively measure Compound solubility in each environment. 1H NMR (Reference: 20353.52, Compound 1 (Tween PBS): 251.68, Compound 1 (water): 41.82, Compound 2 (Tween PBS): 818.37, Compound 6 (Tween PBS): 52.32, Compound 6 (water): 24.57, Compound 14 (Tween PBS): 76.84, Compound 15 (Tween PBS): 83.27, Compound 16 (Tween PBS): 90.04). 1H NMR (Reference: 15434.13, Compound 7 (Tween PBS): 88.32, Compound 7 (water): 17.63). 1H NMR (Reference: 53909, Compound 8 (water): 23.43). 1H NMR (Ref: 35697.31, Compound 9 (Tween PBS): 106.42). 1H NMR (Reference: 19736.11, Compound 12 (Tween PBS): 1001.88, Compound 12 (water): 1804.78).
Compounds 1, 5 and 7 (0.06 g×4 each) were weighed into glass vials and incubated at 37° C. for 3 days in PBS, 10 mM NaOCl, 1N NaOH, and 1N HCl (10 mL). DL-PLGA (0.3 g) was dissolved in DCM (1.5 mL), and 0.3 mL of this solution was transferred into glass vials. The solvent was driven off in a 60° C. flow oven followed by overnight vacuum drying. The films were then incubated at 37° C. for 3 days in PBS, 10 mM NaOCl, 1N NaOH, and 1N HCl (10 mL). The weight change (
Compounds 1, 2, and 6 (0.115 g) were weighed into a glass vial and melted at 50° C. for 30 minutes to form an even layer on the vial bottom. After chilling, the vials were capped with a lint-free tissue, placed in a sterilization pouch, and sterilized by EtO. No changes to the analytical profile were observed. Compounds 1-D, 3,6-D, 7-D, 8-D, 9-D, 10, 11, 12, 14, 15, and 16 (0.15 g) were weighed into polypropylene conical tubes capped with lint-free tissue, placed in sterilization pouches, and were sterilized by EtO. The sterilized compounds were analyzed, and these results were compared to the pre-sterilization profile. No changes were observed for pre and post sterilization samples. Residual EtO content: ethylene oxide=2 ppm, ethylene chlorohydrin=13 ppm, ethylene glycol<100 ppm. LAL testing: <0.020 EU/mL in the sample extract.
SPINCOATED FILMS: Compound 1 (0.5 g) was dissolved in toluene. A clean 4×4 cm stainless steel coupon was placed on the chuck of a Specialty Coating Systems spin-coater, spun at 2000 rpm, and Compound 1 solution (0.15 mL) was applied. The resulting smooth coatings were analyzed by SEM to confirm continuous coverage, and scratched to confirm the presence of coating. XPS analysis (90°) was performed to obtain surface elemental analysis, and to examine for evidence of incomplete coating. Stainless steel: C: 27.84%, Ca: 0.40%, F: 1.18%, Mo: 0.48%, N: 1.18%, Na: 0.46%, O: 52.39% Si: 5.89%, Cr: 3.03%, Fe: 7.15%. Compound 1 coating: C: 51.55%, Ca: 0.36%, F: 31.32%, Mo: 0.02%, N: 3.85%, Na: 0%, Si: 0.06%, Cr: 0%, Fe: 0.01%.
SPRAYED FILMS: Compounds 1 (0.4 g), Compound 6 (0.4 g), Compound 10 (0.2 g), Compound 11 (0.2 g), Compound 12 (0.4 g), Compound 14 (0.2 g), and Compound 15 (0.2 g) were dissolved in toluene. Similarly, Compounds 7, 1+7, 8, and 9 (all 0.4 g) were dissolved in THF. The solutions were stirred for 24 hours at room temperature and were sprayed onto 316 stainless steel coupons ranging in total surface area from 6.25 cm2 to 16 cm2, using an EFD spray system with settings specific to each Compound. The coupons were dried in a 50° C. flow oven for 20-24 hours. SEM images (
Compounds 1, 2, 6, 7, 1+7, 8, 9, 15, and 16 were dissolved in THF or toluene, and were cast into 96 well polypropylene plates. The solvent was evaporated off at room temperature for 24 hours, the plates were then placed in a 60° C. flow oven for 24 hours, and finally dried under vacuum overnight. For comparison purposes, films of SIBS and 316 stainless steel inserts were added to the plates. The plates were sterilized under a UV lamp for 1 hour, after which each sample well was hydrated with PBS. U937 monocyte-like cells (2.5×105 cells) were seeded into each well in the presence of PMA, and the plates were incubated at 37° C. in a humid incubator for three days. Non-adherent cells were removed, and adherent U937 macrophages were enumerated using a CyQuant assay (
Compound 1 (0.1 g) was dissolved in MeOH (0.5, 1, 2 and 4 mL), and these solutions (0.05 mL) were pipetted onto and wicked through a BD 8 μm PET membrane insert. Compound 1 was also blended with PTX to form 1 and 10 wt % solutions, and these were coated onto membranes. As a control, a solution of SIBS polymer of suitable concentration was coated onto membranes. The resulting coated membranes were examined by SEM and porosity was confirmed by the passage of water through the membranes. Further, Compound 6 (fluorescently labeled form of Compound 1) was coated using the same method, and fluorescence (Ex 320, Em 540 nm) was measured to confirm the presence of coating: (uncoated membrane)=3.5, (Compound 1)=0.6, (Compound 6)=28.2. HCAEC were cultured to third passage using media and supplements supplied by Lonzo, and were starved in serum-free media overnight. Cells were lifted and re-suspended in 0.5% FBS media, and HCAEC were seeded (80 000 per membrane insert). The lower wells were filled with 20% FBS media. The negative control consisted of an uncoated membrane with 0.5% FBS media in the lower well. The positive control consisted of an uncoated membrane with 20% FBS media in the lower well. After four hours of incubation, the wells were lifted out, the inner membranes were scrubbed free of cells, and the lower membrane surface was fixed and stained with DiffQuik. Images of the membranes were collected by microscopy, and cell morphology characteristics and population were recorded (
The migration assay as described for the HCAEC was repeated with cell lines from other species on all Compounds described in Examples 1-16.
Compounds 1, 7, 1+7, and 12 were dissolved in toluene or THF. All Compound solutions were stirred for 24 hours at room temperature and used for coating. The solutions were sprayed onto 4 cm×4 cm 316L stainless steel coupons using an EFD spray system with settings specific to each Compound. The coupons were dried in a 50° C. flow oven for 20-24 hours. Human whole blood was obtained from healthy drug-free volunteers and collected in centrifuge tubes with either acid citrate dextrose anti-coagulant (6 parts ACD to 1 part blood) or low molecular weight heparin to a final concentration of 0.2 U/mL. Platelets from blood collected with ACD were isolated by centrifugation and tagged with 0.5 mCi/mL Na51Cr. Red blood cells were also isolated from the ACD whole blood and washed. The Na51Cr tagged platelets and washed red blood cells were combined with platelet poor plasma to give a final platelet concentration of 250,000 platelets/μL and a 40% hematocrit. Finally, 125I-fibrinogen was added to the whole blood suspension such that it represented approximately 2% of the total amount of fibrinogen. Platelet adhesion was measured from flowing whole blood in a cone-and-plate device which produces laminar flow and a uniform rate of shear. Coated coupons were placed in the wells of the cone-and-plate device with 1.2 mL of the whole blood suspension containing Na51Cr platelets and the assay was conducted for 15 minutes. The coupons were then rinsed with fresh buffer and the radioactivity was measured with a γ counter and correlated to the number of adherent platelets (Na51Cr platelets) and adsorbed fibrinogen (125I-fibrinogen) based on the radioactivity of the original whole blood suspension. Compared to the uncoated stainless steel coupon, all coated coupons significantly reduced platelet adhesion and fibrinogen adsorption (
Compounds 1-D, 6-D, 8-D, 9-D, 15, and 16 were weighed and incubated in MEM media at a 4 g:20 mL ratio for 24 hours at 37° C. L-929 mouse fibroblast cells were seeded and incubated at 37° C. in 5% CO2 to obtain sub-confluent monolayers of cells. The growth medium in triplicate cultures was replaced with MEM extract (2 mL). Triplicate cultures were also prepared as positive and negative controls. Cell cultures were examined under microscope after 24 hours to evaluate cellular characteristics and percent lysis. Under the conditions of this test, the MEM extracts showed no evidence of causing cell lysis or toxicity. The same experimental procedure was applied to all Compounds described in Examples 1 to 16.
The viability of HeLa epithelial cells in direct contact with test materials was used to assess the potential cytotoxicity of Compounds 1-D, 6-D, 8-D, 9-D, 15, and 16.
Samples of Compounds were solvent cast on agar-supported Supor filters. Subsequently, a monolayer of HeLa cells were cultured directly on the filter, in the presence of MEM culture media. After 24 hours of incubation, the Supor filter was rinsed and stained with succinic dehydrogenase. Viable cells were identified by a positive purple stain and cytotoxicity was determined by examining the stained filter for cell exclusion zones around the cast material, or a low cell density. Each cytotoxicity assay included a positive and negative control. The same experimental method was applied to all Compounds described in Examples 1-16.
Compound 1-D was weighed and exposed to citrated human plasma at a ratio of 0.2 g test sample to 1 mL of plasma for 15 minutes at 37° C. At the end of incubation period, a PTT reagent of Rabbit Brain Cephalin (RBC) and an activator reagent (calcium chloride) were added to the plasma samples. The plasma samples were then analyzed on the Cascade M-4 manual coagulation analyzer for the time required to form a clot. By this assay, Compound 1-D was considered to be a non-activator of the intrinsic pathway. The same experimental method was applied to all Compounds described in Examples 1-16.
Stents of different types (bare metal, test Compound, and test Compound+1% PTX) were implanted in porcine coronary arteries (castrated male farm porcines, Sus scrofa domestica; weight 40-50 kg at time of stent implantation). Each animal received ASA (0.081 g) and Clopidogrel (0.075 g) by mouth daily for three days prior to stent implant, and were fasted overnight before the procedure. For surgical procedures, after sedation a marginal ear vein was cannulated for infusion of intravenous fluids and medications. The animal was intubated for administration of anesthetic gases and placed on the catheterization table. Under sterile conditions, a vascular introducer sheath was placed in the right femoral artery by surgical cut down. Continuous hemodynamic monitoring and electrocardiographic monitoring was maintained throughout the procedure. Using the guide catheter as a calibration reference, the diameter of the vessel at reference sites proximal and distal to the intended site of implant, as well as the target site diameter, was measured. Stents were implanted in LAD, RCA and LCX arteries in each animal and were sized ˜15% larger than the target site diameter by balloon catheter expansion. At termination seven days after stent implantation, the animals were euthanized, the heart was excised and examined for any abnormalities, and the vasculature was perfused with saline solution to clear the blood. Hearts were kept immersed in fresh formalin until excision of stents for microscopic analysis (
COATING QUALITY: Compound 3 (0.2 g) was dissolved in THF: toluene, was stirred for 24 hours at room temperature, and the solution was sprayed onto stents using an EFD spray system using settings specific to Compound 3. The stents were dried in a 50° C. flow oven for 20-24 hours. The stent coating was assessed for uniform strut coverage by SEM. Stents were then either crimped and deployed or kept as cut. After processing, the coatings on both stents and balloons were assessed by microplate analysis (Ex 320 nm, Em 540 nm). Coating quantity was measured directly on both the stent (as cut: 97.88, deployed: 54.39) and balloon (36.69), as well as after stripping with MeOH for 24 hours (stent as cut: 47.03, deployed: 29.79, balloon: 10.55). Transfer of Compound 3 to the balloon during deployment was examined by UV light.
COATING STABILITY: Stents were coated with Compound 3 as above and stored in the dark at room temperature for 42 days. Stent coatings were stripped in MeOH and the coating was quantified using a microplate reader (Ex 320 nm, Em 540 nm) after 1 and 42 days in storage. The microplate readings were similar regardless of storage time ((1 day)=40.85, (42 days)=39.80). SEM confirmed that the coating on the stent did not change after 42 days in storage (
COATING INTEGRITY: Stents were coated with Compound 3 as above and crimped on balloons. A female pig (20 lb) was implanted with a Compound 3 coated stent in each of the following arteries: left anterior descending artery (LAD), left circumflex artery (LCX), and right coronary artery (RCA). Stents were explanted 45-90 minutes after implantation (
All publications, patents, and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each independent publication or patent application was specifically and individually indicated to be incorporated by reference.
While the invention has been described in connection with specific embodiments thereof, it will be understood that it is capable of further modifications and this application is intended to cover any variations, uses, or adaptations of the invention following, in general, the principles of the invention and including such departures from the present disclosure that come within known or customary practice within the art to which the invention pertains and may be applied to the essential features hereinbefore set forth, and follows in the scope of the claims.
Other embodiments are within the claims.
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/CA2008/001848 | 10/17/2008 | WO | 00 | 1/14/2011 |
| Number | Date | Country | |
|---|---|---|---|
| 60999634 | Oct 2007 | US |
