Biodegradable polyesteramide copolymers for drug delivery

Abstract

The present invention relates to a poly (ester amide) (PEA) having a chemical formula described by structural formula (IV),

Description

FIELD

The present invention relates to new biodegradable polyesteramide copolymers. The present invention also relates to the polyesteramide copolymers for use in medical applications especially for use in drug delivery.

BACKGROUND

Biodegradable polyesteramides are known in the art, in particular α-amino acid-diol-diester based polyesteramides (PEA) are known from G. Tsitlanadze, et al. J. Biomater. Sci. Polym. Edn. (2004) 15:1-24. These polyesteramides provide a variety of physical and mechanical properties as well as biodegradable profiles which can be adjusted by varying three components in the building blocks during their synthesis: naturally occurring amino acids and, therefore, hydrophobic alpha-amino acids, non-toxic fatty diols and aliphatic dicarboxylic acids.

WO2002/18477 specifically refers to alpha-amino acid-diol-diester based polyesteramides (PEA) copolymers of formula I, further referred to as PEA-I,

wherein:

• • m varies from 0.1 to 0.9; p varies from 0.9 to 0.1; n varies from 50 to150;
  • each R1 is independently (C1-C₂₀)alkylene;
  • each R₂ is independently hydrogen or (C₆-C₁₀)aryl(C1-C₆)alkyl;
  • each R₃ is independently hydrogen, (C1-C₆) alkyl, (C₂-C₆)alkenyl, (C₂-C₆)alkynyl, or (C₆-C₁₀)aryl(C₁-C₆)alkyl; and
  • each R₄ is independently (C₂-C₂₀)alkylene.

PEA-I is a random copolymer comprising m units build upon alpha-amino acids, diols and an aliphatic dicarboxylic acids, which are copolymerized with p units build upon an aliphatic dicarboxylic acid and L-lysine. The R₂ in the amino acid L-lysine is either H (hereinafter referred to PEA-I-H) or a (C₆-C₁₀)aryl(C1-C₆)alkyl from which benzyl is the most preferred. In case that the R₂ in L-lysine of PEA-I comprises benzyl it is further referred to as (PEA-I-Bz).

It has been recognized that PEA-I-H shows high swelling profiles which results in a fast degradation and a quick burst release of bioactive agents in approximately 24-48 hours. These properties have reduced the attention of PEA-I-H polymers as materials with potential in drug delivery. It has also been recognized that PEA-I-H enzymatically degrades very fast, for example in vitro it completely degrades in 1 week. On the other hand it has been recognized that PEA-I-Bz provides a more sustained release of bioactive agents over a prolonged period of time. Moreover it shows minor if any swelling properties. PEA-I-Bz enzymatically degrades slowly and the in-vivo degradation of the polymer strongly depends of the administration site, tissue response and health status of the studied model. However, PEA-I-Bz lacks the ability to degrade hydrolytically in absence of enzymes which could result in too slow or even non complete degradation of the polymer.

The same disadvantages appear to be true for another type of prior art PEA random co-polymers according to Formula II which comprise at least two linear saturated or unsaturated aliphatic diol residues into two bis-(a amino acid)-based diol diesters. These copolymers are for example disclosed in WO2008/0299174.

In a preferred embodiment of above polyesteramide co-polymer m varies from 0.01 to 0.99; p varies from 0.2 to 3 and q varies from 0.10 to 1.00 whereby n is 5 to 100; R₁ is —(CH₂)₈; R₃ and R₄ in the backbone units m and p is leucine, —R₅ is hexane, and R₆ is a bicyclic-fragments of 1,4:3,6-dianhydrohexitols of structural formula (III);

R₇ may be chosen from H or a benzyl group and R₈ is —(CH2)4-.If R₇ is H the polymer is further indicated as PEA-III-H, if R₇ is benzyl, the polymer is further indicated as PEA-III-Bz.

SUMMARY

Because of the above described disadvantages of PEA-I-H, PEA-I-Bz PEA-III-H and PEA-III-Bz it seems that these prior art polyesteramides do not fully provide the properties of releasing bioactive agents in a consistent and reliable manner. Moreover they do not provide a satisfying degradation profile. It is either too fast or too slow degrading or only enzymatically and not hydrolytically degrading.

The object of the present invention is therefore to provide new biodegradable polyesteramide random copolymers which take away the above disadvantages.

A further object of the present invention is to provide new biodegradable polyesteramide copolymers which show a sustained release in a controllable way.

Another object of the present invention is to provide new biodegradable polyesteramide copolymers which on top of surface erosion degradation which is caused enzymatically, also shows degradation via a hydrolytic bulk erosion mechanism.

The object of the present invention is achieved by providing a biodegradable poly(esteramide) random copolymer (PEA) according to structural formula (IV),

wherein

• • m+p varies from 0.9-0.1 and q varies from 0.1 to 0.9
  • m+p+q=1 whereby m or p can be 0
  • n varies from 5 to 300;
  • R₁ is independently selected from the group consisting of (C₂-C₂₀) alkylene, (C₂-C₂₀) alkenylene, —(R₉—CO—O—R₁₀—O—CO—R₉)—, —CHR₁₁—O—CO—R₁₂—COOCR₁₁— and combinations thereof;
  • R₃ and R₄ in a single backbone unit m or p, respectively, are independently selected from the group consisting of hydrogen, (C₁-C₆)alkyl, (C₂-C₆)alkenyl, (C₂-C₆)alkynyl, (C₆-C₁₀)aryl, (C₁-C₆)alkyl, —(CH₂)SH, —(CH₂)₂S(CH₃), —CH₂OH, —CH(OH)CH₃, —(CH₂)₄NH₃+, —(CH₂)₃NHC(═NH₂+)NH₂, —CH₂COOH, —(CH₂)COOH, —CH₂—CO—NH₂, —CH₂CH₂—CO—NH₂, —CH₂CH₂COOH, CH₃—CH₂—CH(CH₃)—, (CH₃)₂—CH—CH₂—, H₂N—(CH₂)₄—, Ph-CH₂—, CH═C—CH₂—, HO-p-Ph-CH₂—, (CH₃)₂—CH—, Ph-NH—, NH—(CH₂)₃—C—, NH—CH═N—CH═C—CH₂—.
  • R₅ is selected from the group consisting of (C₂-C₂₀)alkylene, (C₂-C₂₀)alkenylene, alkyloxy or oligoethyleneglycol
  • R₆ is selected from bicyclic-fragments of 1,4:3,6-dianhydrohexitols of structural formula (III);

• • R₇ is selected from the group consisting of (C₆-C₁₀)aryl (C₁-C₆)alkyl
  • R₈ is —(CH₂)₄—;
  • R₉ or R₁₀ are independently selected from C₂-C₁₂ alkylene or C₂-C₁₂ alkenylene.
  • R₁₁ or R₁₂ are independently selected from H, methyl, C₂-C₁₂ alkylene or C₂-C₁₂ alkenylene and whereby a is at least 0.05, b is at least 0.05 and a+b=1.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1: The PEA weight loss after immersion in a buffer with 8.5 U/mL α-chymotrypsin is illustrated up to 36 days. The degradation of both PEA-I-H/Bz polymers follows closely the degradation of PEA-I-Bz., contrary to pure PEA-I-100% H which degraded much faster.

FIG. 2: The relative molecular weight of samples immersed in a solution which contained 8.5 U/mL α-chymotrypsin is illustrated up to 36 days. The relative molecular weight of PEA-I-Bz showed a marginal change while polymers with an increasing H % showed a clear molecular weight drop. Illustrating that also random chain scission (hydrolytic degradation) occurs for polymers which contain an increasing H %.

FIG. 3: The relative molecular weight evaluation of samples which were immersed in a buffer at pH 7.4 is illustrated up to 22 days. The relative molecular weight of PEA-I-Bz changed marginal while the molecular weights of polymers with an increasing H % showed a clear drop. Illustrating that random chain scission (hydrolytic degradation) occurs for polymers which contain an increasing H %.

FIG. 4: Average mass gain in % in time of PEA-I-H/Bz polymers comprising (5-, 25-, 50-, 100% (H)).

FIG. 5: Swelling behavior of different PEA's in PBS buffer.

FIG. 6: In vitro release of chloramphenicol (10% loading) from PEA I-H/Bz polymers comprising (0% H, 25% H and 50% H)).

FIG. 7: Swelling properties of PEA-I-H/Bz (25% H and 35% H) compared to blends of PEA-H and PEA-Bz. Blend 1 comprising 25 wt % PEA-I-H and 75 wt % PEA-I-Bz; blend 2 comprising 35 wt % PEA-I-H and 65 wt % PEA-I-Bz; blend 3 comprising 50 wt % PEA-I-H and 50 wt % PEA-I-Bz.

FIG. 8: Hydrolytic degradation of PEA-I-Bz compared to PEA-I-H/Bz (comprising 15% H, 35% H and 5% H).

FIG. 9: Release of Fluoresceine in PBS from PEA-I-H, PEA-I-Bz and PEA-III-H/PEA-III-Bz.

DETAILED DESCRIPTION

Surprisingly it has been found that polyesteramides of formula IV in which both L-Lysine-H as well as L-lysine-benzyl are present, (hereinafter referred to as PEA-H/Bz) provide unexpected properties in terms of swelling, release and degradation properties. It has been found that PEA-H/Bz co-polymers provide a sustained release of bioactive agents and provide a hydrolytic degradation profile in contrast to the prior art polyesteramides.

It is unexpected that the swelling of PEA-I-H is very high and the swelling of PEA-I-Bz is very low whereas the swelling of the PEA-I-H/Bz copolymers according to the present invention shows a profile comparable to the swelling profile of PEA-I-Bz. This is shown in FIG. 4.

Swelling properties are directly related to release properties. FIG. 6 shows the release of Chloramphenicol (10% loading) from PEA-I-Bz (0% L-lysine-H) compared to PEA-I-H/Bz co-polymers comprising 25% L-Lysine-H and 50% L-lysine-H The figure clearly shows that PEA-III-H/Bz 50% H films do release chloramphenicol over period of a month, just slightly faster than PEA-III-Bz. This observation emphasized that the drug elution properties of PEA-III-H/Bz 50% H are comparable to the art would expect that both swelling and drug elution properties of PEA-III-H/Bz-(50% H) are somewhere in between of these of the two extremes PEA-III-Bz (0% H) and PEA-III-H(100% H). Even more surprising PEA-III-H/Bz 25% H does provide a more sustained release of chloramphenicol than PEA-III-Bz.

Furthermore, it has surprisingly been found that the properties of the newly synthesized PEA-H/Bz co-polymers cannot be achieved via mechanical blending of the corresponding PEA-H and PEA-Bz polymers. This is further evidenced in FIG. 7 which shows that PEA-I-H/Bz 25% H shows a different swelling behavior than the mechanical blend containing 25 wt % PEA-I-H and 75 wt % PEA-I-Bz. The same findings are valid for PEA-I-H/Bz comprising 35% H. This implies that drug elution properties and degradation of the PEA-H/Bz polymers also cannot be matched by mechanical blending of PEA-Bz and PEA-H polymers.

Despite the newly synthesized PEA-H/Bz co-polymers show a little swelling, their degradation properties are markedly different than for the prior art polymers PEA-I-Bz and PEA-III-Bz. It has been found that PEA-I-H/Bz co-polymers seem to degrade hydrolytically and via bulk erosion mechanism whereas it is known that prior art PEA's (PEA-I-Bz, PEA-III-Bz) degrade only via an enzymatic degradation process and via a surface erosion mechanism.

In summary the PEA H/Bz polymers provide a good solution for sustained drug delivery and degrade hydrolytically in contrast to the prior art PEA Bz polymers. Also other prior art polymers such as PLGA or PLLA seem to degrade mainly via bulk erosion mechanism. This is confirmed in FIG. 8.

It is moreover known that the degradation of PLGA and PLLA will result in a pH drop which is undesired because it may influence the stability of the bioactive agent to be released from the polymers. From experiments it has surprisingly been found that the newly designed polymers PEA H/Bz do not show a significant pH drop.

The above findings confirm that the polyesteramides of formula IV in which both L-Lysine-H as well L-lysine-benzyl are present in a certain ratio is a new class of polymers with surprising properties addressing better the needs of polymers for drug delivery.

In the following embodiments of the present invention n preferably varies from 50-200 whereby a may be at least 0.15, more preferably at least 0.5, most preferably at least 0.8, even more preferably at least 0.85.

In one embodiment in biodegradable polyesteramide copolymer according to Formula (IV) comprises p=0 and m+q=1 whereby m=0.75, a=0.5 and a+b=1, R₁ is (CH₂)₈, R₃ is —(CH₃)₂—CH—CH₂—, R₅ is hexyl, R₇ is benzyl and R₈ is —(CH₂)₄— This polyesteramide is referred to as PEA-I-H/Bz 50% H.

In another preferred embodiment of the present invention the biodegradable polyesteramide copolymer according to Formula (IV) comprises m+p+q=1, q=0.25, p=0.45 and m=0.3 whereby a is 0.5 and a+b=1 and whereby R₁ is —(CH₂)₈; R₃ and R₄ respectively are —(CH₃)₂—CH—CH₂—, R₅ is selected from the group consisting of (C₂-C₂₀)alkylene, R₆ is selected from bicyclic-fragments of 1,4:3,6-dianhydrohexitols of structural formula (III), R₇ is benzyl and R₈ is —(CH₂)₄—. This polyesteramide is referred to as PEA-III-H/Bz 50% H.

In a still further preferred embodiment of the present invention the biodegradable polyesteramide copolymer according to Formula (IV) comprises m+p+q=1, q=0.25, p=0.45 and m=0.3 whereby a is 0.75 and a+b=1, R₁ is —(CH₂)₈; R₄ is (CH₃)₂—CH—CH₂—, R₇ is benzyl, R₈ is —(CH₂)₄— and R₆ is selected from bicyclic fragments of 1,4:3,6-dianhydrohexitols of structural formula (III). This polyesteramide is referred to as PEA-III-H/Bz 25% H.

In a yet further preferred embodiment of the present invention the biodegradable polyesteramide copolymer according to Formula (IV) comprises m+p+q=1, q=0.1, p=0.30 and m=0.6 whereby a=0.5 and a+b=1, R₁ is —(CH₂)₄; R₃ and R₄ respectively, are (CH₃)₂—CH—CH₂—; R₅ is selected from the group consisting of (C₂-C₂₀)alkylene, R₇ is benzyl, R₈ is —(CH₂)₄— and R₆ is selected from bicyclic-fragments of 1,4:3,6-dianhydrohexitols of structural formula (III). This polyesteramide is referred to as PEA-II-H/Bz50% H.

As used herein, the term “alkyl” refers to a straight or branched chain hydrocarbon group including methyl, ethyl, n-propyl, isopropyl, n-butyl, isobutyl, tert-butyl, n-hexyl, and the like.

As used herein, the term “alkylene” refers to a divalent branched or unbranched hydrocarbon chain containing at least one unsaturated bond in the main chain or in a side chain.

As used herein, the term “alkenyl” refers to a straight or branched chain hydrocarbon group containing at least one unsaturated bond in the main chain or in a side chain.

As used herein, “alkenylene”, refers to structural formulas herein to mean a divalent branched or unbranched hydrocarbon chain containing at least one

As used herein, “alkynyl”, refers to straight or branched chain hydrocarbon groups having at least one carbon-carbon triple bond.

The term “aryl” is used with reference to structural formulas herein to denote a phenyl radical or an ortho-fused bicyclic carbocyclic radical having about nine to ten ring atoms in which at least one ring is aromatic. Examples of aryl include, but are not limited to, phenyl, naphthyl, and nitrophenyl.

The term biodegradable” refers to material which is capable of being completely or substantially degraded or eroded when exposed to an in vivo environment or a representative in vitro. A polymer is capable of being degraded or eroded when it can be gradually broken-down, resorbed, absorbed and/or eliminated by, for example, hydrolysis, enzymolysis, oxidation, metabolic processes, bulk or surface erosion, and the like within a subject. The terms “bioabsorbable” and “biodegradable” are used interchangeably in this application.

The term “random” as used herein refers to the distribution of the m, p and q units of the polyesteramide of formula (IV) in a random distribution.

At least one of the alpha-amino acids used in the polyesteramide co-polymers is a natural alpha-amino acid. For example, when the R₃s or R₄s are CH₂Ph, the natural alpha-amino acid used in synthesis is L-phenylalanine. In alternatives wherein the R₃s or R₄s are —CH₂—CH(CH₃)₂, the co-polymer contains the natural amino acid, leucine. By independently varying the R₃s and R₄s within variations of the two co-monomers as described herein, other natural alpha-amino acids can also be used, e.g., glycine (when the R₃s or R₄s are H), alanine (when the R₃s or R₄s are CH₃), valine (when the R₃s or R₄s are CH(CH₃)₂), isoleucine (when the R₃s or R₄s are CH(CH₃)—CH₂—CH₃), phenylalanine (when the R₃s or R₄s are CH₂—C₆H₅), lysine (when the R₃s or R₄s (CH₂)₄—NH₂); or methionine (when the R₃s or R₄s are —(CH₂)₂S(CH₃), and mixtures thereof.

The polyesteramide co-polymers preferably have an average number molecular weight (Mn) ranging from 15,000 to 200,000 Daltons. The polyesteramide co-polymers described herein can be fabricated in a variety of molecular weights and a variety of relative proportions of the m, p, and q units in the backbone. The appropriate molecular weight for a particular use is readily determined by one skilled in the art. A suitable Mn will be in the order of about 15,000 to about 100,000 Daltons, for example from about 30,000 to about 80,000 or from about 35,000 to about 75,000. Mn is measured via GPC in THF with polystyrene as standard.

The basic polymerization process of polyesteram ides is based on the process described by G. Tsitlanadze, et al. J. Biomater. Sci. Polym. Edn. (2004) 15:1-24, however different building blocks and activating groups were used.

The polyesteramides of the present invention are for example synthesized as shown in scheme 1; via solution polycondensation of para-toluene sulfonate di-amines salts (X1, X2, X3) with activated di-acids (Y1). Typically dimethylsulfoxide or dimethylformamide are used as solvent. Typically as a base triethylamide is added, the reaction is carried out under an inert atmosphere at 60° C. for 24-72 hours under constant stirring. Subsequently the obtained reaction mixture is purified via a water precipitation followed by an organic precipitation and filtration. Drying under reduced pressure yields the polyesteramide.

The polyesteramide copolymers of the present invention may further comprise at least a bioactive agent. The bioactive agent can be any agent which is a therapeutic, prophylactic, or diagnostic agent. Such bioactive agent may include without any limitation small molecule drugs, peptides, proteins, DNA, cDNA, RNA, sugars, lipids and whole cells. The bioactive agents can have antiproliferative or anti-inflammatory properties or can have other properties such as antineoplastic, antiplatelet, anti-coagulant, anti-fibrin, antithrombotic, antimitotic, antibiotic, antiallergic, or antioxidant properties. Examples of antiproliferative agents include rapamycin and its functional or structural derivatives, 40-O-(2-hydroxy)ethyl-rapamycin (everolimus), and its functional or structural derivatives, paclitaxel and its functional and structural derivatives. Examples of rapamycin derivatives include ABT-578, 40-0-(3-hydroxy)propyl-rapamycin, 40-O-[2-(2-hydroxy)ethoxy]ethyl-rapamycin, and 40-0-tetrazole-rapamycin. Examples of paclitaxel derivatives include docetaxel. Examples of antineoplastics and/or antimitotics include methotrexate, azathioprine, vincristine, vinblastine, fluorouracil, doxorubicin hydrochloride (e.g. Adriamycin® from Pharmacia AND 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 Hb/nia platelet membrane receptor antagonist antibody, recombinant hirudin, thrombin inhibitors such as Angiomax (Biogen, Inc., Cambridge, Mass.), 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 AND 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), super oxide dismutases, super oxide dismutase mimetic, 4-amino-2,2,6,6-tetramethylpiperidine-1-oxyl (4-amino-TEMPO), estradiol, anticancer agents, dietary supplements such as various vitamins, and a combination thereof. Examples of anti-inflammatory agents including steroidal and nonsteroidal anti-inflammatory agents include biolimus, tacrolimus, dexamethasone, clobetasol, corticosteroids or 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 AND Co., Inc., Whitehouse Station, N.J.). An example of an antiallergic agent is permirolast potassium. Other therapeutic substances or agents which may be appropriate include alpha-interferon, pimecrolimus, imatinib mesylate, midostaurin, and genetically engineered epithelial cells. The foregoing substances can also be used in the form of prodrugs or co-drugs thereof. The foregoing substances also include metabolites thereof and/or prodrugs of the metabolites. The foregoing substances are listed by way of example and are not meant to be limiting.

The present invention further relates to compositions comprising the polyesteramides according to the present. The polyesteramides may for example be blended with another polymer for example with a biocompatible polymer. The biocompatible polymer can be biodegradable or non-degradable. Examples of biocompatible polymers are ethylene vinyl alcohol copolymer, poly(hydroxyvalerate), polycaprolactone, poly(lactide-co-glycolide), poly(hydroxybutyrate), poly(hydroxybutyrate-co-valerate), polydioxanone, poly(glycolic acid-co-trimethylene carbonate), polyphosphoester urethane, poly(amino acids), polycyanoacrylates, poly(trimethylene carbonate), poly(iminocarbonate), 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, 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, and ethylene-vinyl acetate copolymers, polyamides, such as Nylon 66 and polycaprolactam, alkyd resins, polycarbonates, polyoxymethylenes, polyimides, polyethers, poly(glyceryl sebacate), poly(propylene fumarate), epoxy resins, cellulose acetate, cellulose butyrate, cellulose acetate butyrate, cellophane, cellulose nitrate, cellulose propionate, cellulose ethers, and carboxymethyl cellulose, copolymers of these polymers with poly(ethylene glycol) (PEG), or combinations thereof.

In a preferred embodiments, the biocompatible polymer can be poly(ortho esters), poly(anhydrides), poly(D,L-lactic acid), poly (L-lactic acid), poly(glycolic acid), copolymers of poly(lactic) and glycolic acid, poly(L-lactide), glycolide), poly(phospho esters), poly(trimethylene carbonate), poly(oxa-esters), poly(oxa-amides), poly(ethylene carbonate), poly(propylene carbonate), poly(phosphoesters), poly(phosphazenes), poly(tyrosine derived carbonates), poly(tyrosine derived arylates), poly(tyrosine derived iminocarbonates), copolymers of these polymers with poly(ethylene glycol) (PEG), or combinations thereof. It is of course also possible that more than one polyesteramides of formula (IV) is mixed together or that the polyesteramides of the present invention are blended with other polyesteramides such as for example the disclosed prior art polyesteramides of Formula I or Formula II.

The polyesteramides may also comprise further excipients such as for example fillers, anti-oxidants, stabilizers, anti-caking agents, emulsifiers, foaming agents, sequestrants or dyes.

The polyesteramide copolymers of the present invention can be used in the medical field especially in drug delivery in the field of management of pain, musculoskeletal applications (MSK), ophthalmology, oncology, vaccine delivery compositions, dermatology, cardiovascular field, orthopedics, spinal, intestinal, pulmonary, nasal, or auricular.

The present invention further relates to articles comprising the polyesteramide copolymers of the present invention. In another aspect, the invention provides for a device comprising the polyesteramide copolymers of the present invention. In the context of the present invention an article is an individual object or item or element of a class designed to serve a purpose or perform a special function and can stand alone. Examples of articles include but are not limited to micro- and nanoparticles, coatings, films or micelles.

In yet another preferred embodiment, the invention provides for a device comprising the article of the present invention. A device is a piece of equipment or a mechanism designed to serve a special purpose or perform a special function and can consist of more than one article (multi-article assembly).

Examples of devices include, but are not limited to catheters, stents, rods, implants.

In another preferred embodiment, the invention provides for a polyesteramide copolymer of the present invention for use as a medicament.

The present invention will now be described in detail with reference to the following non limiting examples which are by way of illustration only.

Example 1: (FIG. 1) (Degradation)

PEA-I-Bz, PEA-I-H/Bz 25% H, PEA-I-H/Bz 50% H and PEA-I-100% H were coated on stainless steel films and immersed in a buffer which contained 8.5 U/mL α-chymotrypsin (bovine) and 0.05% NaN₃, the buffers were refreshed twice a week. Weight loss over time was determined on dried samples using a micro balance. Results are given in FIG. 1.

It was observed that PEA-I-Bz, PEA-I-H/Bz 25% H and PEA-I-H/Bz 50% H degraded with a comparable degradation rate and lost 40-60% of the initial mass over the test period of 35 days. In contrast hereto PEA-I-100% H degraded much faster and degraded completely within 10 days.

Example 2: (FIG. 2) (Mass Gain)

PEA-I-Bz, PEA-I-H/Bz 25% H and PEA-I-H/Bz 50% H were coated on stainless steel films and immersed in a buffer which contained 8.5 U/mL α-chymotrypsin (bovine) and 0.05% NaN₃, the buffers were refreshed twice a week. Relative molecular weights were evaluated with a GPC system using THF as the mobile phase on dried samples. Molecular weights are relative to polystyrene standards. Results are given in FIG. 2.

It was observed that PEA-I-Bz maintained a constant molecular weight. In contrast hereto PEA-I-H/Bz 25% H and PEA-I-H/Bz 50% H showed a significant drop in the molecular weight which indicates hydrolytic degradation of the bulk polymers.

Since the polymers also lost mass as illustrated in example 1 it was concluded that PEA-I-Bz degraded via surface erosion mediated by α-chymotrypsin. However since the molecular weight of PEA-I-H/Bz 25% H and PEA-I-H/Bz 50% H also dropped significantly it was concluded that these materials degrade via a combined degradation mechanism, both hydrolytic bulk degradation as well as enzymatic surface erosion.

Example 3 (FIG. 3) (Mass Gain)

PEA-I-Bz, PEA-I-H/Bz 25% H and PEA-I-H/Bz 50% H were coated on stainless steel films and immersed in a PBS buffer which contained 0.05% NaN₃; the buffers were refreshed twice a week. Relative molecular weights were evaluated with a GPC system using THF as the solvent on dried samples. Molecular weights are relative to polystyrene standards. Results are given in FIG. 3.

The graph illustrates that the molecular weight of PEA-I-Bz remained constant over the test period of 35 days indicating good hydrolytic stability of the material. In contrast the molecular weight of PEA-I-H/Bz 25% H and PEA-I-H/Bz 50% H films dropped significantly over the same period of time, indicating hydrolytic degradation of the materials. This example confirms that that the PEA-I-H/Bz polymers are indeed hydrolytically unstable and show hydrolytic bulk degradation.

Example 4 (FIGS. 4 and 5) Swelling/Mass Gain

From each PEA-I-H/Bz copolymer (5-, 25-, 50-, 100% H) five disks with a diameter of 10 mm were punched out of the film, weighed and placed in a 5.0 ml phosphate buffered saline (PBS) at 37° C. At several time intervals the disks were weighed to determine mass increase by water absorption. After each 2 days the PBS solution was refreshed. Results are given in FIGS. 4 and 5.

In FIG. 4, it was surprisingly found that PEA-I-H/Bz 5% H, PEA-I-H/Bz 25% H, PEA-I-H/Bz 35% H and PEA-I-H/Bz 50% H behaves very similar to PEA-I-Bz as shown in FIG. 4.

In FIG. 5 it was observed that PEA-III-H exhibited a very fast swelling/water uptake, the material doubled in mass within the first hours after immersion in PBS buffer.

This was not the case for the remaining PEA-I-Bz and PEA-III-Bz polymers.

Example 5 (FIG. 6) Chloramphenicol Release

Drug loaded disks of PEA-I-Bz, PEA-I-H/Bz 25% H, PEA-I-H/Bz 50% H with a loading percentage of 10% chloroamphenicol were prepared. Three individual disks with a diameter of 7 mm were placed in 5.0 ml PBS buffer solution at 37° C. At varying time points the complete PBS solution was refreshed to assure sink conditions and the drug concentration was subsequently measured. Typically, samples were measured every day in the first week and weekly at later time points. Results are given in FIG. 6. Chloramphenicol release was measured by RP-HPLC on a C18 column with detection at 278 nm. The release of chloroamphenicol from 10% loaded disks of PEA-I-H/Bz 25% H was faster compared to PEA-I-Bz.

FIG. 6 clearly shows that PEA-I-H/Bz 50% H disks do release chloramphenicol over period of 30 days, just slightly faster than PEA-I-Bz. Even more surprising PEA-I-H/Bz 25% H disks do provide even more sustained release of chloramphenicol than PEA-I-Bz.

Example 6 (FIG. 7 Blends Compared to PEA-I H/Bz)

The swelling behavior of polymers PEA-I-H/Bz 25% H, PEA-I-H 35% H and mechanical blends of PEA-I-H and PEA-I-Bz were compared; blend 1 comprises 25 wt % PEA-I-H and 75 wt % PEA I Bz, blend 2 comprises 35 wt % PEA-I-H and 65 wt % PEA I Bz and blend 3 comprises 50 wt % PEA-I-H and 50 wt % PEA I Bz. The polymers were dissolved in absolute ethanol to have approximately 20 g of solution at 10% (w/w) polymer. The dissolution took few hours. After that, the solution was poured in a Teflon dish (disk of 8 cm diameter). These disks were covered by a glass beaker or placed in a desiccator under nitrogen flow. When the surface was not sticky anymore, the disks were further dried under full vacuum at 65° C. The maximum vacuum was reached slowly to prevent from air bubbles formation. The temperature started to increase once the maximum vacuum was reached.

Five disks of 5 mm diameter were punched out of the 8 mm disks. They were weighted and placed in a 10 mL glass vial. Each disk was immersed in 5.0 mL of PBS buffer which was refreshed every 2 days. All the samples were kept at 37° C. For each data point, the disks were dried with a tissue and weighted. A data point was taken twice a day for the first three weeks, then once a day, then twice a week. The mass gain at time t was calculated with below Formula V;

$\begin{array}{cc}\%\mathrm{mass}\mathrm{gain}=\frac{\mathrm{Dry}\mathrm{disk}\mathrm{mass}-\mathrm{Disk}\mathrm{mass}\mathrm{at}\mathrm{time}t}{\mathrm{Dry}\mathrm{disk}\mathrm{mass}}& \mathrm{Formula}V\end{array}$ Results are given in FIG. 7.

Example 8 (FIG. 8 Hydrolytic Degradation)

10 wt % solutions of PEA-I-Bz, PEA-I-H/Bz 5% H, PEA-I-H/Bz 15% H and PEA-I-35% H were prepared in ethanol. The polymer solutions were solvent casted on stainless steel foil with a thickness of 75 μm and dried under reduced pressure at 65° C. The obtained coated metal films were cut into pieces with a surface area of approximately 1 cm2. The polymer coated metal pieces were used to assess the polymer degradation over time. The polymer coated stainless steel pieces were individually immersed in 5 ml PBS buffer that contained 0.05% NaN3. In triplicate samples were taken and dried under reduced pressure at 65° C. The dried coatings were assessed via mass loss and molecular weight analysis using a GPC system with THF as the eluent. PEA-I-Bz illustrated a good hydrolytic stability based on the stable molecular weight, the introduction of very limited number of carboxyl groups (as in PEA-I-H/Bz 5% H) already results in minor drop of the molecular weight over time but apparently too slow to result in feasible polymer degradation. Surprisingly PEA-I-H/Bz 15% H and PEA-I-H/Bz 35% H showed a pronounced drop in the molecular weight associated with hydrolytic degradation of the polymers. Results are given in FIG. 8.

Example 9 (FIG. 9 Release Fluoresceine)

a. Preparation of the Solution of Polymers & Drugs and Film Preparation

A drug polymer formulation of 5 w % drug in polymer was prepared as followed. Approximately 100 mg of fluorescine were dissolved in 10 ml THF. After complete dissolution, the solution was used to dissolve ˜2.0 g of polymer. Once a clear solution was obtained it was degassed by means of ultrasound the samples at least for 90 min. Afterwards, the solution was casted into a Teflon mould (Diameter=0.40 mm Depth=4 mm) up to full level. The solvent was allowed to evaporate at room temperature on air overnight. Then the whole Teflon mould was transferred into a vacuum oven for continuous evaporation at room temperature under gradually reduced pressure until the entire solvent was removed.

b. Disc Preparation

After evaporation of solvent, coated films were punched to obtain circled discs (Ø7 mm). The weight and thickness of each punched disc was determined. The weight of a used disc was approximately 15 to 30 mg.

c. Release Experiment

The punched discs from the dye-polymer coatings were prepared in duplo for the release experiment. The discs were immersed in 9 ml of PBS in a glass vial, being gently shaken at constant 37° C. during the release period. PBS solution was refreshed twice every day at the beginning of the experiment. Then the time was reduced to once per day and afterwards to once every two days at the later stage. The content of fluorescine released into the buffer solution was determined by either HPLC or UV spectroscopy.

Results are shown in FIG. 9.

FIG. 9 shows that in contrast of the PEA I Bz and PEA III Bz which provide sustained release on fluorescine, PEA-I-H an d PEA-III-H polymers do release the entire drug load in 24-48 hours. This is a consequence of the quick and significant swelling of the polymers.

Claims

1. An article or device comprising a bioactive agent and a biodegradable polyesteramide copolymer (PEA) according to the following formula:

2. The article or device according to claim 1, wherein a is at least 0.15.

3. The article or device according to claim 1, wherein a is at least 0.5.

4. The article or device according to claim 1, wherein a is at least 0.8.

5. The article or device according to claim 1, wherein p=0, m=0.75, and a=0.5;wherein the m, qa, and qb units are randomly distributed;R1 is —(CH2)8—, R3 is (CH3)2—CH—CH2—, R5 is hexyl, and R7 is benzyl.

6. The article or device according to claim 1, wherein q=0.25, p=0.45, m=0.3, and a=0.5;wherein the m, p, qa, and qb units are randomly distributed;R1 is —(CH2)8—; R3 and R4 respectively, are (CH3)2—CH—CH2—; R5 is (C2-C20)alkylene; and R7 is benzyl.

7. The article or device according to claim 1, wherein q=0.25, p=0.45, m=0.3, and a=0.75;wherein the m, p, qa, and qb units are randomly distributed;R1 is —(CH2)8—; R4 is (CH3)2—CH—CH2—; and R7 is benzyl.

8. The article or device according to claim 1, wherein q=0.1, p=0.30, m=0.6, and a=0.5;wherein the m, p, qa, and qb units are randomly distributed;R1 —(CH2)4—; R3 and R4 respectively, are (CH3)2—CH—CH2—; R7 benzyl;and R5 is (C2-C20)alkylene.

9. The article or device according to claim 1, wherein R1 is independently selected from (C2-C20)alkylene.

10. The article or device according to claim 1, wherein R5 is (C2-C20)alkylene.

11. The article or device according to claim 10, wherein R5 is (C2-C20)alkylene.

12. The article or device according to claim 1, wherein the biodegradable polyesteramide copolymer has an Mn of about 15,000 to about 100,000 Daltons, as measured via GPC in THF with polystyrene as standard.

13. The article or device according to claim 1, wherein the biodegradable polyesteramide copolymer has an Mn of about 30,000 to about 80,000 Daltons, as measured via GPC in THF with polystyrene as standard.

14. The article or device according to claim 11, wherein the biodegradable polyesteramide copolymer has an Mn of about 15,000 to about 100,000 Daltons, as measured via GPC in THF with polystyrene as standard.

15. The article or device according to claim 11, wherein the biodegradable polyesteramide copolymer has an Mn of about 30,000 to about 80,000 Daltons, as measured via GPC in THF with polystyrene as standard.

16. The article or device according to claim 7, wherein R5 is (C2-C20)alkylene.

17. The article or device according to claim 16, wherein the biodegradable polyesteramide copolymer has an Mn of about 15,000 to about 100,000 Daltons, as measured via GPC in THF with polystyrene as standard.

18. The article or device according to claim 16, wherein the biodegradable polyesteramide copolymer has an Mn of about 30,000 to about 80,000 Daltons, as measured via GPC in THF with polystyrene as standard.

19. The article or device according to claim 1, wherein the article or the device is a film, a coating, a micelle, a catheter, a stent, a rod, a microparticle, a nanoparticle, or an implant.

20. The article or device according to claim 2, wherein the article or the device is a film, a coating, a micelle, a catheter, a stent, a rod, a microparticle, a nanoparticle, or an implant.

21. The article or device according to claim 3, wherein the article or the device is a film, a coating, a micelle, a catheter, a stent, a rod, a microparticle, a nanoparticle, or an implant.

22. The article or device according to claim 11, wherein the article or the device is a film, a coating, a micelle, a catheter, a stent, a rod, a microparticle, a nanoparticle, or an implant.

23. The article or device according to claim 14, wherein the article or the device is a film, a coating, a micelle, a catheter, a stent, a rod, a microparticle, a nanoparticle, or an implant.

24. The article or device according to claim 15, wherein the article or the device is a film, a coating, a micelle, a catheter, a stent, a rod, a microparticle, a nanoparticle, or an implant.

25. The article or device according to claim 16, wherein the article or the device is a film, a coating, a micelle, a catheter, a stent, a rod, a microparticle, a nanoparticle, or an implant.

26. The article or device according to claim 17, wherein the article or the device is a film, a coating, a micelle, a catheter, a stent, a rod, a microparticle, a nanoparticle, or an implant.

27. The article or device according to claim 18, wherein the article or the device is a film, a coating, a micelle, a catheter, a stent, a rod, a microparticle, a nanoparticle, or an implant.

28. The article or device according to claim 1, wherein the article or device is a drug delivery device for ophthalmology applications and the bioactive agent is a small molecule ophthalmic drug, or prodrug or metabolite thereof.

29. The article or device according to claim 2, wherein the article or device is a drug delivery device for ophthalmology applications and the bioactive agent is a small molecule ophthalmic drug, or prodrug or metabolite thereof.

30. The article or device according to claim 3, wherein the article or device is a drug delivery device for ophthalmology applications and the bioactive agent is a small molecule ophthalmic drug, or prodrug or metabolite thereof.

31. The article or device according to claim 11, wherein the article or device is a drug delivery device for ophthalmology applications and the bioactive agent is a small molecule ophthalmic drug, or prodrug or metabolite thereof.

32. The article or device according to claim 14, wherein the article or device is a drug delivery device for ophthalmology applications and the bioactive agent is a small molecule ophthalmic drug, or prodrug or metabolite thereof.

33. The article or device according to claim 15, wherein the article or device is a drug delivery device for ophthalmology applications and the bioactive agent is a small molecule ophthalmic drug, or prodrug or metabolite thereof.

34. The article or device according to claim 16, wherein the article or device is a drug delivery device for ophthalmology applications and the bioactive agent is a small molecule ophthalmic drug, or prodrug or metabolite thereof.

35. The article or device according to claim 17, wherein the article or device is a drug delivery device for ophthalmology applications and the bioactive agent is a small molecule ophthalmic drug, or prodrug or metabolite thereof.

36. The article or device according to claim 18, wherein the article or device is a drug delivery device for ophthalmology applications and the bioactive agent is a small molecule ophthalmic drug, or prodrug or metabolite thereof.