The present invention relates to particles comprising polyesteramide co-polymers. The present invention also relates to the particles for use in medical applications especially for use in the delivery of bioactive agents.

Biodegradable polyesteramides are known in the art, in particular a- 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,

Formula I wherein:

m varies from 0.1 to 0.9; p varies from 0.9 to 0.1 ; n varies from 50 to about 150;

each R1 is independently (Ci -C ₂ o)alkylene;

each R ₂ is independently hydrogen or (C ₆ -Ci ₀ )aryl(C1 -C ₆ )alkyl;

each R ₃ is independently hydrogen, (C1 -C ₆ ) alkyl, (C ₂ -C ₆ )alkenyl, (C ₂ -

C ₆ )alkynyl, or (C6-Cio)aryl(Ci-C ₆ )alkyl; and

each R ₄ is independently (C ₂ -C ₂ o)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.

WO2008/0299174 discloses particles based on random PEA copolymers according to Formula II comprising at least two linear saturated or

unsaturated aliphatic diol residues into two bis-(a amino acid)-based diol-diesters.

Formula II wherein

-m is 0.01 to 0.99; p is 0.99 to 0.01 ; and q is 0.99 to 0.01 ; and wherein n is 5 to 100; wherein

-Ri can be independently selected from the group consisting of (C ₂ - C ₂₀ )alkylene, (C ₂ -C ₂ o)alkenylene, -(R9-CO-O- 10-O-CO- 9)-, -CHR _i O-CO-Ri ₂ - COOCR11- and combinations thereof;

-R ₃ and R ₄ in a single co-monomer m or p, respectively, can be independently selected from the group consisting of hydrogen, (CrC ₆ )alkyl, (C ₂ - C ₆ )alkenyl, (C ₂ -C ₆ )alkynyl, (C ₆ -Ci ₀ )aryl, (C C ₆ )alkyl, -(CH ₂ )SH, -(CH ₂ ) ₂ S(CH ₃ ), -CH ₂ OH, -CH(OH)CH ₃ , -(CH ₂ ) ₄ NH ₃ +, -(CH ₂ ) ₃ NHC(=NH ₂ +)NH ₂ , -CH ₂ COOH,

-(CH ₂ )COOH, -CH ₂ -CO-NH ₂ , -CH ₂ CH ₂ -CO-NH ₂ , - -CH ₂ CH ₂ COOH,

CH ₃ -CH ₂ -CH(CH ₃ )-, (CH ₃ ) ₂ -CH-CH ₂ -, H ₂ N-(CH ₂ ) ₄ -, Ph-CH ₂ -, CH=C-CH ₂ -,

HO-p-Ph-CH ₂ -, (CH ₃ ) ₂ -CH-, Ph-NH-, NH-(CH ₂ ) ₃ -C-, NH-CH=N-CH=C-CH ₂ -.

-R ₅ is can be selected from the group consisting of (C ₂ -C ₂₀ )alkylene, (C ₂ -C ₂₀ )alkenylene, alkyloxy or oligoethyleneglycol;

-R ₆ can be selected from bicyclic-fragments of 1 ,4:3,6- dianhydrohexitols of structural formula (III);

Formula III

-R ₇ can be hydrogen, (C ₆ -Ci ₀ ) aryl, (Ci-C ₆ ) alkyl or a protecting group such as benzyl- or a bioactive agent;

-R ₈ can be independently (C1-C20) alkyl or (C ₂ -C ₂ o)alkenyl;

-R ₉ or R-io can be independently selected from C2-C12 alkylene or C ₂ -

Ci ₂ alkenylene.

-R11 or R ₁₂ can be independently selected from H, methyl, C ₂ -Ci ₂ alkylene or C ₂ -Ci ₂ alkenylene.

If in the random polyesteramide co-polymer of Formula (II) m+p+q=1 , q=0.25, p=0.45 whereby Ri is -(CH ₂ ) ₈ ; R3 and R ₄ in the backbone units m and p is leucine, -R ₅ is hexane, and R ₆ is a bicyclic-fragments of 1 ,4:3,6-dianhydrohexitols of structural formula (III); R ₇ is benzyl group and R ₈ is -(CH2)4- this polyesteramide is further referred to as PEA-lll-Bz. In case that R ₇ is H, the polyesteramide is further referred to as PEA-III-H.

In case that m+p+q=1 , q=0.25, p=0.75 and m=0, whereby Ri is-(CH ₂ ) ₄ ; R ₃ is (CH ₃ ) ₂ - CH-CH ₂ -, R ₇ is benzyl, R ₈ is -(CH ₂ ) ₄ ; and R ₆ is selected from bicyclic-fragments of 1 ,4:3,6-dianhydrohexitols of structural formula (III), the polyesteramide is further referred to as PEA-IV-Bz, in case that R ₇ is H the polyesteramide is further referred to as PEA-IV-H.

WO2008/0299174 further discloses that the polyesteramides and particles made thereof, facilitate the in vivo release of bioactive agents dispersed in the polymer at a controlled release rate, which is specific and constant over a prolonged period. It is furthermore disclosed that the PEA break down in vivo via enzymes to produce biological a-amino acids upon break down products which are substantially non-inflammatory.

However in some medical areas there is a need for polymers and drug delivery forms such as particles comprising polymers which degrade hydrolytically instead of enzymatically. This need exists for example in ophthalmology where the delivery of drugs intraocularly is a particular problem. The eye is divided into two chambers; the anterior segment which is the front of the eye, and the posterior segment which is the back of the eye. In the back of the eye, in the vitreous, less or no enzymes are present such that for example particles based on enzymatically degradable polyesteramides will not degrade or will degrade too slow. If the particles degrade too slowly, the release of the bioactive agents will also be influenced negatively.

Beside the issue of enzymatic degradation it has further been observed that particles, such as micro-and nanoparticles comprising the above mentioned polyesteramides such as PEA-lll-Bz tend to aggregate when exposed to aqueous medium. These properties could have a negative effect on re-dispersibility and injectability of the particles and respectively on the administration of such particles for drug delivery purposes. Furthermore, the aggregation and agglomeration of the particles would result in a change of the effective surface area of the particles directly impacting the drug release rate in an unpredictable and hardly reproducible way.

There is thus still a need in the art for new and better particle delivery system comprising biodegradable polyesteramides which provide for continuous delivery of bioactive agents over a sustained period of time and which moreover takes away the above mentioned disadvantages of particle aggregation.

The object of the present invention is therefore to provide micro-and nanoparticles comprising biodegradable polyesteramide copolymers which take away the above mentioned disadvantages.

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

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 could be 0

n is about 5 to about 300;

-F is independently selected from the group consisting of (C ₂ -C ₂ o) alkylene, (C ₂ -C ₂ o) alkenylene, -(R9-CO-O- 10-O-CO- 9)-, -CH Rn-0-CO-Ri ₂ -COOCRn- and combinations thereof;

-R ₃ and R ₄ in a single backbone unit m or p, respectively, are independently selected from the group consisting of hydrogen, (CrC ₆ )alkyl, (C ₂ -C ₆ )alkenyl, (C ₂ -C ₆ )alkynyl, (C ₆ - Cio)aryl, (C C ₆ )alkyl, -(CH ₂ )SH, -(CH ₂ ) ₂ S(CH ₃ ), -CH ₂ OH, -CH(OH)CH ₃ , -(CH ₂ ) ₄ NH ₃ +, -(CH ₂ ) ₃ NHC(=NH ₂ +)NH ₂ , -CH ₂ COOH, -(CH ₂ )COOH, -CH ₂ -CO-NH ₂ , -CH ₂ CH ₂ -CO-NH ₂ , -CH ₂ CH ₂ COOH, CH ₃ -CH ₂ -CH(CH ₃ )-, (CH ₃ ) ₂ -CH-CH ₂ -, H ₂ N-(CH ₂ ) ₄ -, Ph-CH ₂ -,

CH=C-CH ₂ -, HO-p-Ph-CH ₂ -, (CH ₃ ) ₂ -CH-, Ph-NH-, NH-(CH ₂ ) ₃ -C-, NH-CH=N-CH=C- CH ₂ -;

-R ₅ is selected from the group consisting of (C ₂ -C ₂₀ )alkylene, (C ₂ -C ₂₀ )alkenylene, alkyloxy or oligoethyleneglycol

-R ₆ is selected from bicyclic-fragments of 1 ,4:3,6-dianhydrohexitols of structural formula

(in);

Formula III

-R ₇ is selected from the group consisting of (C ₆ -Ci ₀ ) aryl (Ci-C ₆ ) alkyl

-R ₈ is -(CH ₂ ) ₄ -;

-R ₉ or R ₁₀ are independently selected from C ₂ -C ₁₂ alkylene or C ₂ -C ₁₂ alkenylene.

-R-i-i or R ₁₂ are independently selected from H, methyl, C ₂ -Ci ₂ alkylene or

C ₂ -Ci ₂ alkenylene whereby a is at least 0.05, b is at least 0.05 and a+b=1 .

Surprisingly it has been found that micro-or nanoparticles comprising the biodegradable polyesteramides of formula IV in which both L-Lysine-H as well L- lysine-benzyl are present, (hereinafter referred to as PEA-H/Bz) provide unexpected properties in terms of release, degradation and aggregation properties. It has been found that micro-or nanoparticles comprising PEA-H/Bz co-polymers provide a sustained release of bioactive agents and degrade hydrolytically at physiological conditions via bulk erosion mechanism in contrast with the PEA polymers known in the prior art that degrade only in presence of certain classes of enzymes by surface erosion.

It is even more unexpected that micro-or nanoparticles of the biodegradable polyesteramides of Formula IV do not aggregate in aqueous

environment even exposed at temperature above their wet Tg for a long time. The ('wet') glass transition temperature (T _g ) is the glass transition temperature when the polymesteramide is exposed to an aqueous environment.

For example PEA-lll-Bz of formula II where m+p+q=1 , q=0.25, p=0.45 and m=0.3, whereby Ri is-(CH ₂ ) ₈ ; R ₄ and R ₃ are (CH ₃ ) ₂ -CH-CH ₂ -, R ₇ is benzyl, R ₈ is - (CH ₂ ) ₄ ; and R ₆ is selected from bicyclic-fragments of 1 ,4:3,6-dianhydrohexitols of structural formula (III), is a polymer with "a wet glass transition temperature" of about 24 °C as determined after exposure to 0.1 M PBS buffer at 37 °C. Particles of this polymer were prepared via standard water/oil/water (w/o/w) emulsion technique, dispersed in 0.1 M PBS buffer and kept at 37 °C. Already in 24 hours the particles started to form aggregates, they fused together at later stage and became an unshaped mass. These properties are also representative for the prior art

polyesteramide as described in for example in WO2008/0299174.

Alternatively, when analogous micro-or nanoparticles were prepared from random co-polymers of PEA-lll-H/Bz 50%H of formula IV wherein m+p+q=1 , q=0.25, p=0.45 and m=0.3, a is 0.5, a+b=1 and whereby Ri is-(CH ₂ )8; R ₄ and R ₃ are - (CH ₃ )2-CH-CH2-, R7 is benzyl, R ₈ is -(CH2)4; and R ₆ is selected from bicyclic-fragments of 1 ,4:3,6-dianhydrohexitols of structural formula (III) with "a wet" glass transition temperature of 21 °C, the obtained particles did not aggregate in the solution during the entire experimental time of 21 days.

The above mentioned 'wet' T _g 's were determined by performing temperature ramp tests from 45 to 0 °C (cooling @ 5°C/min) at an angular frequency of 1 Hz (6.28 rad/s) and a variable strain (autostrain control enabled) with an initial value of 0.1 %. The gap was controlled manually to ensure a constant axial force

(compression) on the sample (F _N ~30 grams). This constant compressive force is necessary to prevent a loss of contact between the sample and the parallel plates. Figure 5 gives a schematic representation of the geometry as it was used for 'wet' Tg measurement.

Also the degradation properties of the micro-or nanoparticles comprising the PEA-H/Bz co-polymers according to the present invention are markedly different than the degradation properties of prior art polymers such as PEA-I, PEA-III, PEA-IV or PLGA. It has been found that the micro-or nanoparticles comprising the PEA-H/Bz co-polymers seem to degrade hydrolytically and mainly via surface erosion mechanism whereas the known PEA particles degrade mainly via an enzymatic degradation process and via a bulk erosion mechanism. Also other prior art polymers such as PLGA or PLLA seem to degrade mainly via bulk erosion mechanism. This is confirmed in Figure 1 .

A further disadvantage in the degradation of for example PLGA and PLLA particles is the fact that they often result in a pH drop which is undesired because it may influence the stability of the bioactive agent to be released from the micro-or nanoparticles. After four weeks of degradation PLGA particles start to release highly acidic degradation products resulting in pH drop. In contrast the pH of the PEA-I-H/Bz micro-or nanoparticles did not change along the entire 13 weeks. It seems that lysine free carboxylic groups and acidic species generated during the degradation are in a right balance to catalyze bonds cleavage along the polyesteramide chain but not compromising the optimal physiological conditions. From experiments it has surprisingly been found that micro-or nanoparticles of PEA-H/Bz do not show a significant pH drop.

The above findings confirm that micro-or nanoparticles comprising the polyesteramides of formula IV in which both L-Lysine-H as well L-lysine-benzyl are present in a certain ratio provides surprising properties addressing better the needs of micro-and nanoparticles in drug delivery.

In the following embodiments of the present invention n in Formula IV preferably varies from 50-200 and a may be at least 0.15, more preferably at least 0.5, most preferably 0.75, even more preferably at least 0.8.

In one embodiment the micro-or nanoparticles comprising the biodegradable polyesteramide copolymer according to Formula (IV) comprise p=0 and m+q=1 whereby m=0.75, a=0.5 and a+b=1 , Ri is (CH ₂ ) ₈ , R ₃ is -(CH ₃ )2-CH-CH ₂ -, R ₅ is hexyl, R ₇ is benzyl and R ₈ is -(CH ₂ )4-. This polyesteramide is referred to as PEA-I-H/Bz 50% H.

In another preferred embodiment of the present invention the micro-or nanoparticles comprising the biodegradable polyesteramide copolymer according to Formula (IV) comprise 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 Ri is -(CH ₂ )8; R3 and R ₄ respectively are -(CH ₃ )2-CH-CI-l2-, R5 is selected from the group consisting of (C ₂ -C ₂ o)alkylene, R ₆ is selected from bicyclic- fragments of 1 ,4:3,6-dianhydrohexitols of structural formula (III); R ₇ is benzyl and R ₈ is -(CH ₂ ) ₄ .This polyesteramide is referred to as PEA-lll-H/Bz 50%H.

In a still further preferred embodiment of the present invention micro- or nanoparticles comprising the biodegradable polyesteramide copolymer according to Formula (IV) comprise m+p+q=1 , q=0.25, p=0.45 and m=0.3 whereby a is 0.75 and a+b=1 , Ri is-(CH ₂ ) ₈ ; R ₄ is (CH ₃ ) ₂ -CH-CH ₂ -, R ₇ is benzyl, R ₈ is -(CH ₂ ) ₄ - and R ₆ is selected from bicyclic fragments of 1 ,4:3,6-dianhydrohexitols of structural formula (III). This polyesteramide is referred to as PEA-lll-H/Bz 25%H.

In a yet further preferred embodiment of the present invention the micro-or nanoparticles comprising the biodegradable poly(esteramide) copolymer according to Formula (IV) comprise m+p+q=1 , q=0.1 , p=0.30 and m=0.6 whereby a=0.5 and a+b=1 . Ri is -(CH ₂ ) ₄ ; R ₃ and R ₄ respectively, are (CH ₃ ) ₂ -CH-CH ₂ -; R ₅ is selected from the group consisting of (C ₂ -C ₂₀ )alkylene, R ₇ is benzyl, R ₈ is -(CH ₂ ) ₄ - and R ₆ is selected from bicyclic-fragments of 1 ,4:3,6-dianhydrohexitols of structural formula (III). This polyesteramide is referred to as PEA-ll-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 unsaturated bond in the main chain or in a side chain.

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 copolymer" as used herein refers to the distribution of the m, p and q units of the polyesteramide of formula (IV) in a random distribution.

As used herein, particles include micro- or nano-particles.

At least one of the alpha -amino acids used in the polyesteramide copolymers according to formula (IV) is a natural alpha -amino acid. For example, when the R3s or R4s are benzyl the natural alpha-amino acid used in synthesis is L- phenylalanine. In alternatives wherein the R ₃ s or R ₄ s are -CH ₂ -CH(CH ₃ )2, the copolymer contains the natural amino acid, leucine. By independently varying the R ₃ s and R ₄ s within variations of the two co-monomers as described herein, other natural alpha - amino acids can also be used, e.g., glycine (when the R ₃ or R ₄ are H), alanine (when the R ₃ or R ₄ are CH ₃ ), valine (when the R ₃ or R ₄ are -CH(CH ₃ ) ₂ , isoleucine (when the R ₃ or R ₄ are -CH(CH ₃ )-CH ₂ -CH ₃ ), phenylalanine (when the R ₃ or R ₄ are CH ₂ -C ₆ H ₅ ), lysine (when the R ₃ or R ₄ (CH ₂ ) ₄ -NH ₂ ); or methionine (when the R ₃ s or R ₄ s are - (CH ₂ ) ₂ S(CH ₃ ), and mixtures thereof.

The polyesteramide co-polymers of Formula (IV) 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 polyesteramides 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 Formula (IV) 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 24-72hours 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.

Typically, the average diameter of the microparticles given by the Fraunhofer theory in volume percent ranges from 10 nm to 1000 μηη. The preferred average diameter depends on the intended use. For instance, in case the

microparticles are intended for use as an injectable drug delivery system, in particular as an intravascular drug delivery system, an average diameter of 1 -40 μηη may be desired, more preferably an average diameter of 20-40 μηη may be desired.

It is envisaged that particles with an average diameter of less than 1000 nm are nanoparticles. Typically nanoparticles with a size of less than 800 nm, in particular less than 500 nm are useful for intracellular purposes. For such purposes, the average diameter preferably ranges from 50-500 nm, more preferably it ranges from 100-300 nm.

In other applications, larger dimensions may be desirable, for instance an average diameter in the range of 1 -100 μηη or even 1 -1000 μηη. Preferably the average diameter of the microparticles ranges from 10-100 μηη. More preferably the average diameter of the microparticles range from 20-60 μηη. Even more preferably the average diameter of the microparticles range from 20-40 μηη. In particular, the particle diameter as used herein is the diameter as determinable by a Malven Mastersizer 2000. Particles can be defined and classified in various different ways depending on their specific structure, size, or composition, see e.g. Encyclopaedia of Controlled drug delivery Vol2 M-Z Index, Chapter: Microencapsulation Wiley Interscience, page 493- 496.

If particles are too small or non-analyzable by light scattering which may be the case with nanoparticles because of their optical properties, then scanning electron microscopy (SEM) or transmission electron microscopy (TEM) can be used.

The micro- and nanoparticles of the present invention may be used as a delivery system for bioactive agents but also for the delivery of diagnostic aids or imaging agents.

The micro- or nanoparticles according to the present invention may comprise one or more bioactive agents. The bioactive agent(s) may be more or less homogeneously dispersed within the micro-or nanoparticles. The bioactive agent may also be located within the micro-or nanoparticle core or shell.

In particular, the bioactive agent may be selected from the group of nutrients, pharmaceuticals, small molecule drugs, proteins and peptides, vaccines, genetic materials, (such as polynucleotides, oligonucleotides, plasmids, DNA and RNA), diagnostic agents, and imaging agents. The bioactive agent, such as an bioactive pharmacologic ingredient (API), may demonstrate any kind of activity, depending on the intended use.

The bioactive agent may be capable of stimulating or suppressing a biological response. The bioactive agent may for example be chosen from growth factors (VEGF, FGF, MCP-1 , PIGF, antibiotics (for instance penicillin's such as B- lactams, chloramphenicol), anti-inflammatory compounds, antithrombogenic compounds, anti-claudication drugs, anti-arrhythmic drugs, anti-atherosclerotic drugs, antihistamines, cancer drugs, vascular drugs, ophthalmic drugs, amino acids, vitamins, hormones, neurotransmitters, neurohormones, enzymes, signalling molecules and psychoactive medicaments.

The bioactive agents can have antiproliferative or anti-inflammatory properties or can have other properties such as antineoplastic, antiplatelet, anticoagulant, 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(R) from Pharmacia AND Upjohn, Peapack NJ.), and mitomycin (e.g. Mutamycin(R) 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(R) from Merck AND Co., Inc., Whitehouse Station, NJ), 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-l- 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 combinations thereof.

Examples of such cytostatic substances include angiopeptin, angiotensin converting enzyme inhibitors such as captopril (e.g. Capoten(R) and Capozide(R) from Bristol- Myers Squibb Co., Stamford, Conn.), cilazapril or lisinopril (e.g. Prinivil(R) and

Prinzide(R) from Merck AND Co., Inc., Whitehouse Station, NJ). 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.

Further examples of specific bioactive agents are neurological drugs (amphetamine, methylphenidate), alphal adrenoceptor antagonist (prazosin, terazosin, doxazosin, ketenserin, urapidil), alpha2 blockers (arginine, nitroglycerin), hypotensive (clonidine, methyldopa, moxonidine, hydralazine minoxidil), bradykinin, angiotensin receptor blockers (benazepril, captopril, cilazepril, enalapril, fosinopril, lisinopril, perindopril, quinapril, ramipril, trandolapril, zofenopril), angiotensin-1 blockers

(candesartan, eprosartan, irbesartan, losartan, telmisartan, valsartan), endopeptidase (omapatrilate), beta2 agonists (acebutolol, atenolol, bisoprolol, celiprolol, esmodol, metoprolol, nebivolol, betaxolol), beta2 blockers (carvedilol, labetalol, oxprenolol, pindolol, propanolol) diuretic actives (chlortalidon, chlorothiazide, epitizide,

hydrochlorthiazide, indapamide, amiloride, triamterene), calcium channel blockers (amlodipin, barnidipin, diltiazem, felodipin, isradipin, lacidipin, lercanidipin, nicardipin, nifedipin, nimodipin, nitrendipin, verapamil), anti arthymic active (amiodarone, solatol, diclofenac, flecainide) or ciprofloxacin, latanoprost, flucloxacillin, rapamycin and analogues and limus derivatives, paclitaxel, taxol, cyclosporine, heparin, corticosteroids (triamcinolone acetonide, dexamethasone, fluocinolone acetonide), anti-angiogenic (iRNA, VEGF antagonists: bevacizumab, ranibizumab, pegaptanib), growth factor, zinc finger transcription factor, triclosan, insulin, salbutamol, oestrogen, norcantharidin, microlidil analogues, prostaglandins, statins, chondroitinase, diketopiperazines, macrocycli compounds, neuregulins, osteopontin, alkaloids, immuno suppressants, antibodies, avidin, biotin, clonazepam. 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.

In accordance with the present invention, if a bioactive agent is present, the concentration of one or more bioactive agent(s) in the micro-or

nanoparticles, is preferably at least 1 wt%, based on the total weight of the micro-or nanoparticles, in particular at least 5 wt. %, more in particular at least 10 wt %. The concentration may be up to 90 wt%, up to 70 wt.%, up to 50 wt.% or up to 30 wt.%, as desired.

It is also possible to functionalise at least the surface of the microparticles since the polymer naturally contains free carboxyl groups along the polymer chain, in particular with a signalling molecule, an enzyme or a receptor molecule, such as an antibody. The receptor molecule may for instance be a receptor molecule for a component of interest, which is to be purified or detected, e.g. as part of a diagnostic test, making use of the particles of the present invention. Suitable functionalisation methods may be based on a method known in the art. In particular, the receptor molecule may be bound to the biodegradable polyesteramide of which the particles are prepared via an available or post introduced reactive group

Since the micro-or nanoparticles comprise -COOH groups, it is possible to functionalize these -COOH groups with carbodiimide which may further react with a hydroxyl group or amino group of a target functional moiety to be coupled to the particles.

In addition to the biodegradable polyesteramides as represented by formula IV, the micro-or nanoparticles of the present invention may further comprise one or more other polymers selected from the group of biocompatible polymers.

Examples of biocompatible polymers are 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), poly(D,L-lactide), poly(glycolide), poly(D,L-lactide-co-glycolide), poly(L-lactide-co-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.

In principle the micro-or nanoparticles may be prepared in a manner known in the art, provided that the polymers used in the prior art are replaced by the biodegradable polyesteramides of Formula (IV). In general particles can for example be prepared via aggregation with heat or pH adjustment, via co-acervation (phase separation), via spray drying or via solvent extraction. An overview of preparation methods has been disclosed in J. Control Release, 102:313-332, in 2005 by Freitas S et al. The micro or nanoparticles of the present invention are preferably prepared via oil in water emulsion method. This method is disclosed in detail in Example I.

If desired the micro- or nanoparticles may be loaded with one or more bioactive agents. Loading may be achieved by forming the micro-or nanoparticles in the presence of the bioactive agent or thereafter. To achieve micro- or nanoparticles with a high amount of bioactive agent, it is generally preferred to prepare the micro- or nanoparticles in the presence of the bioactive agent. In particular in the case that the bioactive agent is sensitive it is preferred to load the micro or nanoparticles after they have been formed. This can be achieved by contacting the micro- or nanoparticles with the bioactive agent and allowing the bioactive agent to diffuse into the micro-or nanoparticles and/or adhere/ adsorb to the surface thereof.

In accordance with the invention it is possible to provide micro-or nanoparticles with one or more bioactive agents with satisfactory encapsulation efficiency, (i.e. the amount of bioactive agent in the particles, divided by the amount of active agent used). Depending upon the loading conditions, an efficiency of at least 20%, an efficiency of at least 50%, at least 75% or at least 90% or more is feasible.

Several types of micro-and nanoparticle structures can be prepared, these include substantially homogenous structures. However in case that more than one bioactive agent has to be released or in case that one or more functionality is needed it is preferred that the micro or nanoparticles are provided with a structure comprising an inner core and an outer shell. A core/shell structure enables more multiple mode of action for example in drug delivery of incompatible compounds or in imaging. The shell can be applied after formation of the core using a spray drier. The core and the shell may comprise the same or different polymers with different active agents. In this case it is possible to release the bioactive agents at different rates. It is also possible that the bioactive agent is only present in the core and that the shell is composed of a polymer.

The micro-or nanoparticles can also be used to fill a capsule or tube by using high pressure or may be compressed as a pellet, without substantially damaging the particles. It can also be used in injectable or spray-able form as a suspension in a free form or in an in-situ forming gel formulation. Furthermore, the micro- and nanoparticles can be incorporated in for example (rapid prototyped) scaffolds, coatings, patches, composite materials, gels, plasters or hydrogels.

The micro- or nanoparticles according to the present invention can be injected, sprayed, implanted or absorbed.

In a preferred embodiment, the particles according to the present invention are even essentially free of cryoprotectants. A cryoprotectant is a substance that protects a material, i.e. particles, from freezing damage (damage due to ice formation). Examples of cryoprotectants include a glycol, such as ethylene glycol, propylene glycol and glycerol or dimethyl sulfoxide (DMSO).

In still a further embodiment, the micro- or nanoparticles may comprise a magnetic or magnetisable core and a shell comprising the biodegradable polyesteramides. Suitable magnetic or magnetisable materials are known in the art. Such microparticles may be useful for the capability to be attracted by objects comprising metal, in particular steel, for instance an implanted object such as a graft or a stent. Such micro- or nanoparticles may further be useful for purification or for analytical purposes.

In a still further embodiment, the micro-or nanoparticles are imageable by a specific technique. Suitable imaging techniques are MRI, CT, X-ray. The imaging agent can be incorporated inside the micro- and nanoparticles or coupled onto their surface. Such micro- or nanoparticles may be useful to visualize how the particles migrate, for instance in the blood or in cells. A suitable imaging agent is for example gadolinium.

The micro-or nanoparticles comprising the polyesteramide copolymers according to the present invention can be used in the medical field especially in drug delivery in the field of management of pain, MSK, ophthalmology, cancer treatment, vaccine delivery compositions, dermatology, cardiovascular field, orthopedics, spinal, intestinal, pulmonary, nasal, or auricular field.

In a preferred embodiment, the invention provides for micro-or nanoparticles of the present invention for use as a medicament.

Besides in medical field the micro-or nanoparticles according to the invention may inter alia be used in an agricultural application. In that case the micro-or nanoparticles particles may comprise a pesticide or a plant-nutrient.

The present invention further relates to articles comprising the micro- or nanoparticles of the present invention. In another aspect, the invention provides for a device comprising micro-or nanoparticles. 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.

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.

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

FIG. 1 : Hydrolytic degradation of PEA-I, PEA-MI, PEA H/Bz and PLGA FIG. 2: Aggregation behavior of PEA-lll-H/Bz compared to PEA-I II-

Bz.

FIG 3: Release of Dexamethasone from microparticles comprising either PEA-lll-Bz; PEA-MI- H/Bz 25%H; PEA-lll-H/Bz 50%H or PLGA 50:50.

FIG 4: pH of the buffer during the degradation study of PEA-I-H/Bz 25%H, PEA-I-H/Bz 50%H and PLGA.

FIG 5: ARES2-rheometer with disposable geometries.

FIG 6: Experimental set up of degradation study

Example I

Protocol used PEA-I-Bz, copolymers of PEA-I-H/Bz 25%H, 50%H, PEA-IV-Bz, and PLGA 50/50, PLGA 75/25.

20g oil phase comprised 5wt% polymer, 0.5wt% fluorescein, 9.45wt% dimethyl sulfoxide (DMSO) and 85.05wt% dichloromethane (DCM). Usually, 1 g of polymer was dissolved in 9g DCM.

The water phase comprised 2.5wt% NaCI, 1wt% Polyvinyl Acetate (PVA) (9-10kDa, 80% hydrolyzed) and 96.5wt% demi water. The PVA was dissolved in warm water (80°C) and let under stirring overnight at 75°C. The concentration used was 5% PVA in water. 200mL of cold water phase was used per 20g of oil phase.

For the particle formation, the water phase was poured into a 300mL VWR beaker, 12cm high, 6.7cm diameter. The emulsification was done with an Ultraturrax IKA T25 coupled with a S25NK-19G stirrer. The stirring speed used was 4000rpm. The polymer was injected via a 20mL syringe with a bent 12cm, 0.80mm diameter needle. The stirring was let on 3min after the injection end. Then the mixture was let under magnetic stirring overnight with an aluminum sheet with small holes on top of the beaker to let the solvent evaporate.

The solution used contains 0.4mg/ml_ Tween 20 in water solution. Around 400ml_ of washing solution was used per 20g oil phase.

The mixture previously obtained was divided into four 50ml_ falcon tubes and kept in ice. The beaker was rinsed with washing solution which was added to the tubes. They were centrifuged at l OOOrpm for 5min. The supernatant was removed and replaced by 40ml_ of washing solution. The particles were re-dispersed by gentle shaking. The tubes were centrifuged at l OOOrpm for 2min. Once again, the supernatant was removed and replaced by 40ml_ of washing solution. This washing was repeated twice and the supernatant was removed and replaced by 5ml_ of washing solution. The fractions were blended into one tarred 50ml_ falcon tube. The tubes were rinsed with washing solution which was added to the tarred tube.

The particles were re-dispersed (sonication bath can be used) and frozen in liquid nitrogen. At this step, the tube can be stored in a freezer. Holes were pierced in a cap which fit to the falcon tube. Then the tarred falcon tube with the pierced cap was placed in a freeze dryer (0.04mbar, -40°C) for at least four days.

Example II

This study was carried out with microparticles prepared according to example I, the microparticles were loaded with fluorescein. Samples of about 25mg of dry particles were introduced in a 15ml_ flacon tube. Eighteen tubes were used per polymer studied (six data points in triple). 12ml_ of 0.1 M PBS buffer, pH 7.4 with 0.05% NaN ₃ was added to each tube. Then the tubes were placed in a tube rack under shaking in a climate chamber as represented on Figure 6.

Then, for each data point, the pH of the buffer was measured and 2ml_ of the buffer was filtered and stored in HPLC vial in a freezer.

After that, the buffer was removed and particles washed with demineralized water. The particles were then monitored by microscope and dried under vacuum at 37°C overnight. The next step was to dissolve 5mg of particles in 2ml_ of THF to measure their molecular weight distribution.

The fluorescein loaded micro particles were challenged in the degradation study while monitoring the changes of the polymer molecular weight and particles capability to retain the loaded fluorescien. It was shown that PEA-H particles do swell quickly releasing the dye molecule. More hydrophobic PEA-Bz particles do not swell and retain the loaded fluorescien much better however the polymers do not show any sign of degradation during the experiment (13 weeks).

Results of the degradation study are shown in Figure 1 .

Example III

W/O/W emulsion technique for preparation of PEA microparticles. The polymers used in this study were PEA-lll-Bz, PEA-lll-H/Bz and

PLGA.

Water 1 (W1 ) solution: 10mg/ml Fitc-BSA containing 100mg/ml_ trehalose .2H20 Oil composition: 5% Wt of the corresponding polymer was dissolved in chloroform. Water 2 (W2) solution: 80 gram 5% PVA and 320 gram Demiwater and 20 gram NaCI. For the fabrication of the microparticles Falcon tube (50ml_) and syringe (10ml_) were used. After adding the W1 solution to the oil, the mixture was vortexed for 30 seconds. After removing the plunger a needle was attached to the syringe the mixture was poored in the syring (10ml_). Plunger was added when the needle of the syring was in the W2 layer. O/W mixture was added in circa 60 seconds at 4000RPM. Mixture was stirred for additional 3 minutes at 4000RPM. Particles were stirred overnight with magnetic stirrer and nitrogen flow.

In a stock solution of Tween 20 in H20 at 0.4 mg/mL which was prepared and stored in fridge the microparticles were suspended. Next the particle suspension was added to 4 falcon tubes. The tubes were centrifuged at 1000 rpm for 5 min and placed directly in ice. The supernatant was replaced it with 5 ml. of the cold Tween 20 solution and 4 fractions were collected in a falcon tube.

The samples were re-dispersed immediately by gentle shaking and short sonication when need. Then the samples were centrifuged again and supernatant replaced. The washing procedure was repeated twice.

After a re-dispersion step the particles were immediately frozen into liquid nitrogen. Next the caps of the tubes were pierced and samples were attached to the freeze- dryer.

Approximately 20-40 mg of the freeze-dried micro particles were accurately weighted and transferred to 5 ml sample vials. Next was added two ml. of stock solution to each vial containing 0.1 M PBS buffer containing 0.05 wt% NaN3 and 0.05 wt% Tween 20. The vials were placed in a climate chamber at 37°C under gentle agitation. Samples were assessed and pictures were taken after 7 and 24 hours, 3, 4, 8, 21 days. Particles of PEA-lll-H/Bz 50 % H were floating freely in solution in contrast with PEA-III- Bz particles which formed agglomerates already in the first in 24 hours.

Results are shown in Figure 2.

It can be observed that micro particles consisting of PLGA 50:50 formed aggregates which could be re-dispersed after vigorous stirring. Micro particles consisting of PEA- lll-Bz formed a minor amount of aggregates however the

aggregates were not easy re-dispersable. Surprisingly micro particles of PEA-lll-H/Bz 25%H and PEA-III- H/Bz 50% did not show agglomeration at all.

Example IV

Micro particles were prepared via solid in oil in water (S/O/W) emulsion technique. Briefly, 100mg dexamethasone was dispersed in 20g CHCI ₃ polymer solution that contained 5% polymer (oil phase). The polymers used were respectively PEA III Ac Bz, PEA III H/Bz 25%H, PEA III H/Bz 50%H and PLGA 50:50. The obtained oil phase dispersions were injected into the water phase that contained 1 %PVA 9-10kDa 88%hydrolyzed and 2.5% NaCI under ultra turrax mixing. The obtained microparticle suspension was stirred for 18 hours under ambient conditions prior to centrifugation at 1000RPM for 5 minutes. After which the supernatant was decanted off. The microparticle residue was resuspended in 10ml distilled water that contained 0.4mg/ml Tween 20. The suspension was again centrifuged at 1000RPM for 5 minutes and the supernatant was decanted off. The microparticle residue was resuspended in 10ml distilled water that contained 0.4mg/ml Tween 20. The obtained microparticle suspension was freeze-dried and stored at -20°C.

Dexamethasone loading was determined with 1 H-NMR.

Drug loading 5-7%, particle size range 10-35μη-ι.

Particle size was determined using SLS (Static Light Scattering).

Results are given in Figure 3.

In duplicate approximately 20mg freeze-dried micro particles were accurately weighted and transferred to 10ml sample vials. To the vials 4ml PBS buffer containing 0.05%NaN ₃ and 0.05% Tween 20 was added. The vials were placed at 37°C under gentle agitation. Sampling took place on a bi-weekly basis followed by a weekly sampling. During the sampling the microparticles were allowed to sediment for at least 1 hour after which 2ml of the buffer was replaced with fresh buffer. The dexamethasone concentration was determined in the release buffer using a RP-HPLC method with DAD detection at 238nm. The graph illustrates sustained release of dexamethasone up to 62 days from the polyesteramide matrices.

The release from PLGA followed a bimodal release curve associated with the bulk degradation property of the material. Dexamethasone release from PEA micro particles did not illustrate this behavior and showed a sustained release over the test period of 62 days. Polymers with an increasing H% exhibited increased polarity and swelling properties associated with water uptake. However surprisingly the release kinetics did not correlate with the increased H% it was anticipated that PEA-lll-H/Bz 50%H would release fastest and PEA-lll-Bz would release slowest.

Example V

This study was carried out with microparticles made with the oil in water method as described in example I. 20-25mg of microparticles was introduced in a 15ml_ flacon tube. Each data point was in triple. 12ml_ of PBS buffer with 0.05% NaN ₃ was introduced to each tube. The_pH was measured with a Metrohm 848 Titrino plus. The calibration was checked before each use with pH buffers of pH=7 and pH=2 or 4 and was performed with pH=2 and pH=9.

For each data point, the pH of the buffer was measured and 2ml_ of the buffer was filtered and stored in HPLC vial in a freezer.

After that, the buffer was removed and particles washed with demineralized water. The particles were then monitored by microscope and dried under vacuum at 37°C overnight. The next step was to dissolve 5mg of particles in 2ml_ of THF to measure their molecular weight distribution. Some of the polymers studied didn't dissolve in THF after being in PBS buffer lists the issues and the solutions found. Results are shown in Figure 4.