Delivery of hydrophobic active agents from hydrophilic polyether block amide copolymer surfaces

Abstract

Embodiments of the invention include drug delivery coatings and devices including the same. In an embodiment, a drug delivery coating is included herein having a base polymeric layer, the base polymeric layer including a hydrophilic polyether block amide copolymer and having a hydrophilic surface. The drug delivery coating can further include a therapeutic agent layer forming an exterior surface the drug delivery coating, the therapeutic agent layer contacting the hydrophilic surface of the base polymeric layer and having a composition different than the base polymeric layer, the therapeutic agent layer including a particulate hydrophobic therapeutic agent and a cationic agent. Other embodiments are also included herein.

Description

FIELD OF THE INVENTION

The present invention relates to devices and coatings for medical device. More specifically, the present invention relates to devices and coatings for medical devices including hydrophilic polyether block amide copolymer and hydrophobic active agent particles disposed thereon.

BACKGROUND OF THE INVENTION

The vascular system of the human is subject to blockage due to plaque within the arteries. Partial and even complete blockage of arteries by the formation of an atherosclerotic plaque is a well-known and frequent medical problem. Frequently, such blockage occurs in the coronary arteries. Blockages may also occur secondary to past treatment of specific sites (restenosis—such as that stemming from rapidly dividing smooth muscle cells). In addition, blockages can also occur in the context of peripheral arteries.

Blockages may be treated using atherectomy devices, which mechanically remove the plaque; hot or cold lasers, which vaporize the plaque; stents, which hold the artery open; and other devices and procedures designed to increase blood flow through the artery.

One common procedure for the treatment of blocked arteries is percutaneous transluminal coronary angioplasty (PTCA), also referred to as balloon angioplasty. In this procedure, a catheter having an inflatable balloon at its distal end is introduced into the coronary artery, the deflated, folded balloon is positioned at the stenotic site, and then the balloon is inflated. Inflation of the balloon disrupts and flattens the plaque against the arterial wall, and stretches the arterial wall, resulting in enlargement of the intraluminal passageway and increased blood flow. After such expansion, the balloon is deflated, and the balloon catheter removed. A similar procedure, called percutaneous transluminal angioplasty (PTA), is used in arteries other than coronary arteries in the vascular system. In other related procedures, a small mesh tube, referred to as a stent is implanted at the stenotic site to help maintain patency of the coronary artery. In rotoblation procedures, also called percutaneous transluminal rotational atherectomy (PCRA), a small, diamond-tipped, drill-like device is inserted into the affected artery by a catheterization procedure to remove fatty deposits or plaque. In a cutting balloon procedure, a balloon catheter with small blades is inflated to position the blades, score the plaque and compress the fatty matter into the artery wall. During one or more of these procedures, it may be desirable to deliver a therapeutic agent or drug to the area where the treatment is occurring to prevent restenosis, repair vessel dissections or small aneurysms or provide other desired therapy.

Additionally, it may be desirable to transfer therapeutic agents to other locations in a mammal, such as the skin, neurovasculature, nasal, oral, the lungs, the mucosa, sinus, the GI tract or the renal peripheral vasculature.

SUMMARY OF THE INVENTION

Embodiments of the invention include drug delivery coatings and devices including the same. In an embodiment a drug delivery coating is included. The drug delivery coatings including a base polymeric layer, the base polymeric layer including a hydrophilic polyether block amide copolymer and having a hydrophilic surface. The drug delivery coating can further include a therapeutic agent layer forming an exterior surface the drug delivery coating, the therapeutic agent layer contacting the hydrophilic surface of the base polymeric layer and having a composition different than the base polymeric layer. The therapeutic agent layer can include a particulate hydrophobic therapeutic agent and a cationic agent.

In an embodiment a drug delivery device is included. The drug delivery device can include a substrate comprising a hydrophilic polyether block amide copolymer and having a hydrophilic surface. The drug delivery device can further include a therapeutic agent layer forming an exterior surface of at least a portion of the drug delivery device, the therapeutic agent layer contacting the hydrophilic surface of the substrate. The therapeutic agent layer can include a particulate hydrophobic therapeutic agent and a cationic agent.

In an embodiment, a method of making a medical device is included. The method can include depositing a therapeutic agent layer onto at least a portion of the medical device, the medical device comprising a substrate comprising a hydrophilic polyether block amide copolymer. The therapeutic agent layer can be contacting the surface of the substrate. The therapeutic agent layer can include a particulate hydrophobic therapeutic agent and a cationic agent.

This summary is an overview of some of the teachings of the present application and is not intended to be an exclusive or exhaustive treatment of the present subject matter. Further details are found in the detailed description and appended claims. Other aspects will be apparent to persons skilled in the art upon reading and understanding the following detailed description and viewing the drawings that form a part thereof, each of which is not to be taken in a limiting sense. The scope of the present invention is defined by the appended claims and their legal equivalents.

BRIEF DESCRIPTION OF THE FIGURES

The invention may be more completely understood in connection with the following drawings, in which:

FIG. 1 is a schematic cross-sectional diagram of a coating in accordance with an embodiment herein.

FIG. 2 is a schematic cross-sectional diagram of a coating in accordance with an embodiment herein.

FIG. 3 is a schematic cross-sectional diagram of a coating in accordance with an embodiment herein.

FIG. 4 is a schematic cross-sectional diagram of a coating in accordance with an embodiment herein.

FIG. 5 is a schematic diagram of a device in accordance with an embodiment herein.

FIG. 6 is a schematic cross-sectional diagram of a coating in accordance with various embodiments herein.

FIG. 7 is a schematic cross-sectional diagram of a coating in accordance with various embodiments herein.

FIG. 8 is a schematic cross-sectional diagram of a coating in accordance with various embodiments herein.

FIG. 9 is a schematic cross-sectional diagram of a coating in accordance with various embodiments herein.

While the invention is susceptible to various modifications and alternative forms, specifics thereof have been shown by way of example and drawings, and will be described in detail. It should be understood, however, that the invention is not limited to the particular embodiments described. On the contrary, the intention is to cover modifications, equivalents, and alternatives falling within the spirit and scope of the invention.

DETAILED DESCRIPTION OF THE INVENTION

The embodiments of the present invention described herein are not intended to be exhaustive or to limit the invention to the precise forms disclosed in the following detailed description. Rather, the embodiments are chosen and described so that others skilled in the art can appreciate and understand the principles and practices of the present invention.

All publications and patents mentioned herein are hereby incorporated by reference. The publications and patents disclosed herein are provided solely for their disclosure. Nothing herein is to be construed as an admission that the inventors are not entitled to antedate any publication and/or patent, including any publication and/or patent cited herein.

As described above, in association with procedures such as percutaneous transluminal coronary angioplasty (PTCA), percutaneous transluminal angioplasty (PTA), and the like, it can be desirable to deliver a therapeutic agent or drug to the area where the treatment is occurring to prevent restenosis, repair vessel dissections or small aneurysms or provide other desired therapy. One approach for accomplishing this is to deliver a therapeutic agent (or active agent) to the desired tissue site using a drug delivery device such as a drug eluting balloon catheter or a drug-containing balloon catheter.

Drug delivery coatings for certain medical applications desirably exhibit various properties. By way of example, in the context of a drug eluting balloon catheter or a drug-containing balloon catheter, the coating should maintain structural integrity during steps associated with preparation of the balloon catheter device include pleating, folding, and curing (such as heat treatment). In addition, it is desirable for the coating to maintain structural integrity during the process of passing through the vasculature through a catheter and/or over the guide wire, with limited loss of the active agent. Yet, it is also desirable upon inflation of the balloon at the desired site to transfer a substantial amount of the active agent from the balloon and onto the vessel wall. In addition, it is desirable to maximize uptake of the active agent into the tissue of the of the vessel wall and reduce the amount of active agent that is washed away into the blood flowing through the treatment site in the vasculature.

Embodiments herein can be useful to enhance one or more desirable properties of drug delivery coatings, such as those properties desirable in the context of drug eluting balloon catheters, drug-containing balloon catheters and similar devices. In various embodiments, a drug delivery device is provided that includes a substrate and coated therapeutic agent particles disposed on the substrate. The coated therapeutic agent particles can include a particulate hydrophobic therapeutic agent and a cationic agent disposed over the particulate hydrophobic therapeutic agent.

Referring now to FIG. 1, a schematic cross-sectional diagram (not to scale) is provided of a coating in accordance with an embodiment herein. In this embodiment, coated therapeutic agent particles 104 are disposed on a substrate 102. Exemplary substrates are described in greater detail below. The coated therapeutic agent particles 104 can include a plurality of cationic agents 108 disposed over a particulate hydrophobic therapeutic agent 106. The coated therapeutic agent particles 104 can be contiguously coated with cationic agents 108. In other embodiments, the cationic agent 108 coating on the therapeutic agent particles 104 can be discontinuous. Additionally, the particulate hydrophobic agents 106 can coexist in a matrix with cationic agents 108 wherein the cationic agent 108 does not coat the particulate hydrophobic agent 106. Various mixtures of the embodiments described above can be found on a specific substrate 102. For example, but not limiting, a coating on a substrate can include coated therapeutic agent particles 104 contiguously coated with cationic agents 108 and particulate hydrophobic agents 106 in a matrix with cationic agents 108 wherein the cationic agent 108 does not coat the particulate hydrophobic agent 106. It will be appreciated that as actually applied there will be many hydrophobic therapeutic agent particulates within a given coating and that a single particulate is shown in FIG. 1 just for purposes of ease of illustration. Exemplary cationic agents and hydrophobic therapeutic agents are described in greater detail below. The charge provided by the cationic agents 108 can be electrostatically attracted to negative charges and/or polar groups associated with the lipid bilayer 110 of a cell membrane and cellular components within the lipid bilayer 110.

In some embodiments, nucleic acids may also be included in coatings herein. By way of example, nucleic acids, including but not limited to siRNA, may be associated with the cationic agent. Exemplary nucleic acids are described in greater detail below. Referring now to FIG. 2, a schematic cross-sectional diagram (not to scale) is provided of another embodiment herein. In this embodiment, coated therapeutic agent particles 204 are disposed on a substrate 202. The coated therapeutic agent particles 204 can include a plurality of cationic agents 208 disposed over a particulate hydrophobic therapeutic agent 206. Nucleic acids 212 can be associated with the cationic agent. The charge provided by the cationic agents 208 can be electrostatically attracted to negative charges and/or polar groups associated with the lipid bilayer 210 of a cell membrane and cellular components within the lipid bilayer 210.

In some embodiments, an additive may be included along with the coated therapeutic agent particles 304 in coatings herein. Referring now to FIG. 3, a schematic cross-sectional diagram (not to scale) is provided of another embodiment. In this embodiment, coated therapeutic agent particles 304 are disposed on a substrate 302. An additive 314 can be disposed along with the coated therapeutic agent particles 304. The amount of the additive 314 can be more than, less than, or equal to the amount of the coated therapeutic agent particles 304. In some embodiments, the additive 314 can form a matrix or layer in which the coated therapeutic agent particles 304 are disposed. In various embodiments, the additive can be hydrophilic. Exemplary additive components are described in greater detail below. The coated therapeutic agent particles 304 can include a plurality of cationic agents 308 disposed over a particulate hydrophobic therapeutic agent 306. The charge provided by the cationic agents 308 can be electrostatically attracted to negative charges and/or polar groups associated with the lipid bilayer 310 of a cell membrane and cellular components within the lipid bilayer 310.

In some embodiments, a hydrophilic polymer layer can be disposed on the surface of the substrate, between the coated therapeutic agent particles and the surface of the substrate. Exemplary polymers for the hydrophilic polymer layer are described in greater detail below. Referring now to FIG. 4, a schematic cross-sectional diagram (not to scale) is provided of another embodiment herein. In this embodiment, coated therapeutic agent particles 404 are disposed on a hydrophilic polymer layer 416, which is in turn disposed on a substrate 402. The coated therapeutic agent particles 404 can include a plurality of cationic agents 408 disposed over a particulate hydrophobic therapeutic agent 406. The charge provided by the cationic agents 408 can be electrostatically attracted to negative charges and/or polar groups associated with the lipid bilayer 410 of a cell membrane and cellular components within the lipid bilayer 410.

Referring now to FIG. 5, a schematic view of an exemplary device is shown in accordance with an embodiment. The device 500 can be, for example, an angioplasty balloon catheter or a drug eluting balloon catheter or a drug-containing balloon catheter. However, further examples of exemplary devices are described in greater detail below. The device 500 includes a catheter shaft 502 and a manifold end 505. The device 500 also includes an inflatable balloon 504 disposed around the catheter shaft 502. In FIG. 5, the balloon 504 is shown in an inflated configuration. The catheter shaft 502 can include a channel to convey fluid through the catheter shaft 502 and to or from the balloon 504, so that the balloon 504 can selectively go from a deflated configuration to the inflated configuration and back again.

The manufacture of expandable balloons is well known in the art, and any suitable process can be carried out to provide the expandable substrate portion of the insertable medical device as described herein. Catheter balloon construction is described in various references, for example, U.S. Pat. Nos. 4,490,421, 5,556,383, 6,210,364, 6,168,748, 6,328,710, and 6,482,348. Molding processes are typically performed for balloon construction. In an exemplary molding process, an extruded polymeric tube is radially and axially expanded at elevated temperatures within a mold having the desired shape of the balloon. The balloon can be subjected to additional treatments following the molding process. For example, the formed balloon can be subjected to additional heating steps to reduce shrinkage of the balloon.

Referring back to FIG. 5, the insertable medical device 500 can also have one or more non-expandable (or inelastic) portions. For example, in a balloon catheter, the catheter shaft 502 portion can be the non-expandable portion. The non-expandable portion can be partially or entirely fabricated from a polymer. Polymers include those formed of synthetic polymers, including oligomers, homopolymers, and copolymers resulting from either addition or condensation polymerizations.

Examples of suitable addition polymers include, but are not limited to, acrylics such as those polymerized from methyl acrylate, methyl methacrylate, hydroxyethyl methacrylate, hydroxyethyl acrylate, acrylic acid, methacrylic acid, glyceryl acrylate, glyceryl methacrylate, methacrylamide, and acrylamide; vinyls such as ethylene, propylene, vinyl chloride, vinyl acetate, vinyl pyrrolidone, vinylidene difluoride, and styrene. Examples of condensation polymers include, but are not limited to, polyamides such as polycaprolactam, polylauryl lactam, polyhexamethylene adipamide, and polyhexamethylene dodecanediamide, and also polyurethanes, polycarbonates, polyamides, polysulfones, poly(ethylene terephthalate), polydimethylsiloxanes, and polyetherketone. The non-expandable portion can also be partially or entirely fabricated from a metal.

Referring now to FIG. 6, a schematic cross-sectional diagram (not to scale) is provided of a drug delivery coating in accordance with various embodiments herein. In this embodiment, particulate hydrophobic therapeutic agents 606 are disposed on a substrate 602. Exemplary substrates are described in greater detail below. A plurality of cationic agents 608 are also disposed on the substrate. The particulate hydrophobic therapeutic agents 606 and the cationic agents 608 can form a matrix. It will be appreciated that as actually applied there can be many more hydrophobic therapeutic agent particulates within a given matrix. Exemplary cationic agents and hydrophobic therapeutic agents are described in greater detail below. The charge provided by the cationic agents 608 can be electrostatically attracted to negative charges and/or polar groups associated with the lipid bilayer 610 of a cell membrane and cellular components within the lipid bilayer 610.

Referring now to FIG. 7, a schematic cross-sectional diagram (not to scale) is provided of a drug delivery coating in accordance with various embodiments herein. In this embodiment, particulate hydrophobic therapeutic agents 706 are disposed on a substrate 702. A plurality of cationic agents 708 are also disposed on the substrate. The particulate hydrophobic therapeutic agents 706 and the cationic agents 708 can form a matrix. The particulate hydrophobic therapeutic agents 706 and the cationic agents 708 can be associated with one another and in some cases can form coated therapeutic agent particles 704 disposed on the substrate 702. The coated therapeutic agent particles 704 can include a plurality of cationic agents 708 disposed over a particulate hydrophobic therapeutic agent 706. It will be appreciated that as actually applied there can be many hydrophobic therapeutic agent particulates within a given coating and that particulates shown in FIG. 7 are just for purposes of ease of illustration. The charge provided by the cationic agents 708 can be electrostatically attracted to negative charges and/or polar groups associated with the lipid bilayer 710 of a cell membrane and cellular components within the lipid bilayer 710.

In some embodiments, a hydrophilic polymer layer can be disposed on the surface of the substrate, between the therapeutic agent, cationic agent, and/or coated therapeutic agent particles and the surface of the substrate. Exemplary polymers for the hydrophilic polymer layer are described in greater detail below. Referring now to FIG. 8, a schematic cross-sectional diagram (not to scale) is provided of a drug delivery coating in accordance with various embodiments herein. A hydrophilic polymer layer 816 is disposed on a substrate 802. Particulate hydrophobic therapeutic agents 806 are disposed on the hydrophilic polymer layer 816. A plurality of cationic agents 808 can also be disposed on the hydrophilic polymer layer 816. The particulate hydrophobic therapeutic agents 806 and the cationic agents 808 can be associated with one another. The particulate hydrophobic therapeutic agents 806 and the cationic agents 808 can form a matrix. The charge provided by the cationic agents 808 can be electrostatically attracted to negative charges and/or polar groups associated with the lipid bilayer 810 of a cell membrane and cellular components within the lipid bilayer 810.

Referring now to FIG. 9, a schematic cross-sectional diagram (not to scale) is provided of a drug delivery coating in accordance with various embodiments herein. A hydrophilic polymer layer 916 is disposed on a substrate 902. Particulate hydrophobic therapeutic agents 906 can be disposed on the hydrophilic polymer layer 916. A plurality of cationic agents 908 can also disposed on the hydrophilic polymer layer 916. The particulate hydrophobic therapeutic agents 906 and the cationic agents 908 can form a matrix. The particulate hydrophobic therapeutic agents 906 and the cationic agents 908 can be associated with one another and in some cases can form coated therapeutic agent particles 904 disposed on the hydrophilic polymer layer 916. The coated therapeutic agent particles 904 can include a plurality of cationic agents 908 disposed over a particulate hydrophobic therapeutic agent 906. The charge provided by the cationic agents 908 can be electrostatically attracted to negative charges and/or polar groups associated with the lipid bilayer 910 of a cell membrane and cellular components within the lipid bilayer 910.

Cationic Agents

Cationic agents used in embodiments herein can include compounds containing a portion having a positive charge in aqueous solution at neutral pH along with a portion that can exhibit affinity for hydrophobic surfaces (such as hydrophobic or amphiphilic properties) and can therefore interface with hydrophobic active agents. In some embodiments, cationic agents used in embodiments herein can include those having the general formula X-Y, wherein X is a radical including a positively charged group in aqueous solution at neutral pH and Y is a radical exhibiting hydrophobic properties. In some embodiments, the cationic agent can include a hydrophilic head and a hydrophobic tail, along with one or more positively charged groups, typically in the area of the hydrophilic head.

Cationic agents of the present disclosure can include salts of cationic agents at various pH ranges, such as, but not limited to, halide salts, sulfate salts, carbonate salts, nitrate salts, phosphate salts, acetate salts and mixtures thereof.

Cationic agents can specifically include cationic lipids and net neutral lipids that have a cationic group (neutral lipids with cationic groups). Exemplary lipids can include, but are not limited to, 3β[N—(N′,N′-dimethylaminoethane)-carbamoyl]cholesterol hydrochloride (DC-cholesterol); 1,2-dioleoyl-3-trimethylammonium-propane (DOTAP); dimethyldioctadecylammonium (DDAB); 1,2-dioleoyl-sn-glycero-3-ethylphosphocholine (EPC); 1,2-di-O-octadecenyl-3-trimethylammonium propane (DOTMA); 1,2-di-(9Z-octadecenoyl)-3-dimethylammonium-propane (DODAP); 1,2-dilinoleyloxy-3-dimethylaminopropane (DLinDMA) and derivatives thereof. Additional lipids can include, but are not limited to, 1,2-dioleoyl-sn-glycero-3-phosphoethanolamine (DOPE); cholesterol; 1,2-dioctadecanoyl-sn-glycero-3-phosphocholine (DSPC); 1,2-distearoyl-sn-glycero-3-phosphoethanolamine (DSPE). Other cationic agents can include mono- or polyaminoalkanes such as spermine and spermidine.

Cationic agents can specifically include cationic polymers. Cationic agents can also include polycation-containing cyclodextrin (for example, but not limited to, amino cyclodextrin and derivatives thereof), amino dextran, histones, protamines, cationized human serum albumin, aminopolysaccharides such as chitosan, peptides such as poly-L-lysine, poly-L-ornithine, and poly(4-hydroxy-L-proline ester, and polyamines such as polyethylenimine (PEI; available from Sigma Aldrich), polyallylamine, polypropylenimine, polyamidoamine dendrimers (PAMAM; available from Sigma Aldrich), cationic polyoxazoline and poly(beta-aminoesters). Cationic agents can also specifically include cationic lipidoids (as described by K. T. Love in the publication PNAS 107, 1864-1869 (2010)). Other exemplary cationic polymers include, but are not limited to, block copolymers such as PEG-PEI and PLGA-PEI copolymers. Other exemplary cationic agents include positively charged gelatin (for example, base-treated gelatin), and the family of aminated cucurbit[n]urils (wherein n=5, 6, 7, 8, 10).

In other embodiments of the present disclosure, cationic agents containing a portion having a positive charge in aqueous solutions at neutral pH include the following Compounds (A-I):

Additionally, other cationic agents include structures of the general Formula I:

TABLE 1
Values for Variables x + z, y and R for Compounds J-R of
Formula I.
	Compound	x + z	y	R
	Compound J	6	12.5	C12H25
	Compound K	1.2	2	C12H25
	Compound L	6	39	C12H25
	Compound M	6	12.5	C14H29
	Compound N	1.2	2	C14H29
	Compound O	6	39	C14H29
	Compound P	6	12.5	C16H33
	Compound Q	1.2	2	C16H33
	Compound R	6	39	C16H33

Cationic agents, such as those listed above, can generally be prepared by the reaction of an appropriate hydrophobic epoxide (e.g. oleyl epoxide) with a multi-functional amine (e.g. propylene diamine). Details of the synthesis of related cationic agents are described by K. T. Love in the publication PNAS 107, 1864-1869 (2010) and Ghonaim et al., Pharma Res 27, 17-29 (2010).

It will be appreciated that polyamide derivatives of PEI (PEI-amides) can also be applied as cationic agents. PEI-amides can generally be prepared by reacting PEI with an acid or acid derivative such as an acid chloride or an ester to form various PEI-amides. For example, PEI can be reacted with methyl oleate to form PEI-amides.

In yet other embodiments cationic agents can include moieties used to condense nucleic acids (for example lipids, peptides and other cationic polymers). In some instances these cationic agents can be used to form lipoplexes and polyplexes.

Exemplary embodiments of cationic agents can also include, but are not limited to, cationic agent derivatives that are photo reactive. Photo reactive groups are described below. Such cationic agent derivatives include PEI polymer derivatives of benzophenone and PAMAM polymer derivatives of benzophenone.

In some embodiments, the molecular weight of the cationic agent can be about 1.2 kDa, 2.5 kDa, 10 kDa, 25 kDa, 250 kDa or even, in some cases, 750 kDa. In yet other embodiments the molecular weight of the cationic agent can be in the range of 50-100 kDa, 70-100 kDa, 50-250 kDa, 25-100 kDa, 2.5-750 kDa or even, in some cases, 2.5-2,000 kDa. Other embodiments include molecular weights greater than 1.2 kDa, 2.5 kDa, 10 kDa, 25 kDa, 250 kDa or even, in some cases, greater than 750 kDa. Other embodiments can include cationic agents up to 2,000 kDa.

Low molecular weight cationic agent monomers or low molecular weight cationic oligomers can be combined with hydrophobic active agent to produce a reactive coating. These reactive coatings can then be coated onto a substrate and thermally polymerized or polymerized with UV-radiation. Exemplary monomers include, but are not limited to, aziridine, vinylamine, allylamine and oligomers from 80 g/mol to 1200 g/mol. Crosslinkers (e.g., 1,2-dichloroethane, epichlorohydrin, 1,6-diisocyanatohexane) could be used to crosslink oligomers.

Additive Components

In some embodiments of the present disclosure the additive components can be hydrophilic in nature. Exemplary hydrophilic polymers include, but are not limited to, PEG, PVP and PVA.

Exemplary additive components can include saccharides. Saccharides can include monosaccharides, disaccharides, trisaccharides, oligosaccharides, and polysaccharides. Polysaccharides can be linear or branched polysaccharides. Exemplary saccharides can include but are not limited to dextrose, sucrose, maltose, mannose, trehalose, and the like. Exemplary saccharides can further include, but are not limited to, polysaccharides including pentose, and/or hexose subunits, specifically including glucans such as glycogen and amylopectin, and dextrins including maltodextrins, fructose, mannose, galactose, and the like. Polysaccharides can also include gums such as pullulan, arabinose, galactan, etc.

Saccharides can also include derivatives of polysaccharides. It will be appreciated that polysaccharides include a variety of functional groups that can serve as attachment points or can otherwise be chemically modified in order to alter characteristics of the saccharide. As just one example, it will be appreciated that saccharide backbones generally include substantial numbers of hydroxyl groups that can be utilized to derivatize the saccharide.

Saccharides can also include copolymers and/or terpolymers, and the like, that include saccharide and/or saccharide subunits and/or blocks.

Polysaccharides used with embodiments herein can have various molecular weights. By way of example, glycogen used with embodiments herein can have a molecular weight of greater than about 250,000. In some embodiments glycogen used with embodiments herein can have a molecular weight of between about 100,000 and 10,000,000 Daltons.

Refinement of the molecular weight of polysaccharides can be carried out using diafiltration. Diafiltration of polysaccharides such as maltodextrin can be carried out using ultrafiltration membranes with different pore sizes. As an example, use of one or more cassettes with molecular weight cut-off membranes in the range of about 1K to about 500 K can be used in a diafiltration process to provide polysaccharide preparations with average molecular weights in the range of less than 500 kDa, in the range of about 100 kDa to about 500 kDa, in the range of about 5 kDa to about 30 kDa, in the range of about 30 kDa to about 100 kDa, in the range of about 10 kDa to about 30 kDa, or in the range of about 1 kDa to about 10 kDa.

It will be appreciated that polysaccharides such as maltodextrin and amylose of various molecular weights are commercially available from a number of different sources. For example, Glucidex™ 6 (avg. molecular weight ˜95,000 Da) and Glucidex™ 2 (avg. molecular weight ˜300,000 Da) are available from Roquette (France); and MALTRIN™ maltodextrins of various molecular weights, including molecular weights from about 12,000 Da to 15,000 Da are available from GPC (Muscatine, Iowa). Examples of other hydrophobic polysaccharide derivatives are disclosed in US Patent Publication 2007/0260054 (Chudzik), which is incorporated herein by reference.

Exemplary additive components can include amphiphilic compounds. Amphiphilic compounds include those having a relatively hydrophobic portion and a relatively hydrophilic portion. Exemplary amphiphilic compounds can include, but are not limited to, polymers including, at least blocks of, polyvinylpyrrolidone, polyvinyl alcohol, polyethylene glycol, polyoxazolines (such as poly(2-alkyloxazoline) and derivatives) and the like. Exemplary amphiphilic compounds can specifically include poloxamers. Poloxamers are nonionic triblock copolymers composed of a central hydrophobic chain of polyoxypropylene flanked by two hydrophilic chains of polyoxyethylene. Poloxamers are frequently referred to by the trade name PLURONIC®. It will be appreciated that many aspects of the copolymer can be varied such the characteristics can be customized. One exemplary poloxamer is PLURONIC® F68 (nonionic, co-polymer of ethylene and propylene oxide commercially available from BASF Corporation; also designated as F68 and poloxamer F68), which refers to a poloxamer having a solid form at room temperature, a polyoxypropylene molecular mass of approximately 1,800 g/mol and roughly 80% polyoxyethylene content, with a total molecular weight of approximately 8,400 g/mol, the copolymer terminating in primary hydroxyl groups.

Exemplary additive components can further include compounds that stabilize poorly water soluble pharmaceutical agents. Exemplary additive components providing such stabilization include biocompatible polymers, for example albumins. Additional additive components are described in U.S. Pat. No. 7,034,765 (De et al.), the disclosure of which is incorporated herein by reference. Stabilization of suspensions and emulsions can also be provided by compounds, for example, such as surfactants (e.g. F68).

Various additive components can be added as an optional topcoat over the layer containing the hydrophobic active agent. In some embodiments, the topcoat can be applied to modify the release characteristic of the hydrophobic active agent. Other topcoats can be added as a protection layer to reduce inadvertent loss of the hydrophobic active agent through friction or general wear. For example, the topcoat can act as a protection layer for handling purposes during packaging or to protect the hydrophobic active agent until the hydrophobic active can be delivered to the target site in the body, or both. For example, the optional topcoat can include polyvinylpyrrolidone (PVP), polyacrylic acid (PAA), and polyurethane.

Hydrophobic Active Agents

It will be appreciated that hydrophobic active agents of embodiments herein (e.g., particulate hydrophobic therapeutic agents), can include agents having many different types of activities. The terms “active agent” and “therapeutic agent” as used herein shall be coterminous unless the context dictates otherwise. Hydrophobic active agents can specifically include those having solubility in water of less than about 100 μg/mL at 25 degrees Celsius and neutral pH. In various embodiments, hydrophobic active agents can specifically include those having solubility in water of less than about 10 μg/mL at 25 degrees Celsius and neutral pH. In some embodiments, hydrophobic active agents can specifically include those having solubility in water of less than about 5 μg/ml at 25 degrees Celsius and neutral pH.

In some exemplary embodiments, active agents can include, but are not limited to, antiproliferatives such as paclitaxel, sirolimus (rapamycin), zotarolimus, everolimus, temsirolimus, pimecrolimus, tacrolimus, and ridaforolimus; analgesics and anti-inflammatory agents such as aloxiprin, auranofin, azapropazone, benorylate, diflunisal, etodolac, fenbufen, fenoprofen calcim, flurbiprofen, ibuprofen, indomethacin, ketoprofen, meclofenamic acid, mefenamic acid, nabumetone, naproxen, oxyphenbutazone, phenylbutazone, piroxicam, sulindac; anti-arrhythmic agents such as amiodarone HCl, disopyramide, flecainide acetate, quinidine sulphate; anti-bacterial agents such as benethamine penicillin, cinoxacin, ciprofloxacin HCl, clarithromycin, clofazimine, cloxacillin, demeclocycline, doxycycline, erythromycin, ethionamide, imipenem, nalidixic acid, nitrofurantoin, rifampicin, spiramycin, sulphabenzamide, sulphadoxine, sulphamerazine, sulphacetamide, sulphadiazine, sulphafurazole, sulphamethoxazole, sulphapyridine, tetracycline, trimethoprim; anti-coagulants such as dicoumarol, dipyridamole, nicoumalone, phenindione; anti-hypertensive agents such as amlodipine, benidipine, darodipine, dilitazem HCl, diazoxide, felodipine, guanabenz acetate, isradipine, minoxidil, nicardipine HCl, nifedipine, nimodipine, phenoxybenzamine HCl, prazosin HCL, reserpine, terazosin HCL; anti-muscarinic agents: atropine, benzhexol HCl, biperiden, ethopropazine HCl, hyoscyamine, mepenzolate bromide, oxyphencylcimine HCl, tropicamide; anti-neoplastic agents and immunosuppressants such as aminoglutethimide, amsacrine, azathioprine, busulphan, chlorambucil, cyclosporin, dacarbazine, estramustine, etoposide, lomustine, melphalan, mercaptopurine, methotrexate, mitomycin, mitotane, mitozantrone, procarbazine HCl, tamoxifen citrate, testolactone; beta-blockers such as acebutolol, alprenolol, atenolol, labetalol, metoprolol, nadolol, oxprenolol, pindolol, propranolol; cardiac inotropic agents such as amrinone, digitoxin, digoxin, enoximone, lanatoside C, medigoxin; corticosteroids such as beclomethasone, betamethasone, budesonide, cortisone acetate, desoxymethasone, dexamethasone, fludrocortisone acetate, flunisolide, flucortolone, fluticasone propionate, hydrocortisone, methylprednisolone, prednisolone, prednisone, triamcinolone; lipid regulating agents such as bezafibrate, clofibrate, fenofibrate, gemfibrozil, probucol; nitrates and other anti-anginal agents such as amyl nitrate, glyceryl trinitrate, isosorbide dinitrate, isosorbide mononitrate, pentaerythritol tetranitrate.

Other exemplary embodiments of active agents include, but are not limited to, active agents for treatment of hypertension (HTN), such as guanethidine.

In a particular embodiment, the hydrophobic active agents are selected from the group consisting of paclitaxel, sirolimus (rapamycin) and mixtures thereof.

In some embodiments, a hydrophobic active agents can be conjugated to a cationic agent. The conjugation can include a hydrophobic active agent covalently bonded to the cationic agent. In some embodiments wherein the hydrophobic agent is conjugated to the cationic agent a linking agent can be used to attach the hydrophobic agent to the cationic agent. Suitable linking agents include, but are not limited to, polyethylene glycol, polyethylene oxide and polypeptides of naturally-occurring and non-naturally occurring amino acids. In some embodiments, linking agents can be biodegradable or cleavable in vivo to assist in release of the hydrophobic active agents. Exemplary linking agents can further include alkane or aromatic compounds with heteroatom-substitutions such as N, S, Si, Se or O.

Particle size and size distribution of a particulate preparation can be determined using any one of various techniques known in the art. In one mode of practice, laser diffraction can be used to measure particle size and distribution. In laser diffraction a laser beam passes through a dispersed particulate sample and angular variation in intensity of light scattered is measured. The angle of light scattering is greater for large particles and less for smaller particles, and the angular scattering intensity data can be collected and analyzed to generate a particle size profile.

Analysis of particulate size and distribution can be performed using laser light scattering equipment such as Malvern System 4700, (for particles from 1 nm to 3 μm) or Horiba LA-930 (e.g., for particles from 100 nm to 2 mm). The output from such analyzers can provide information on the sizes of individual particulates, and the overall amount of particulates of these sizes reflecting the distribution of particulates in terms of size. Analysis providing data on the size distribution can be provided in the form of a histogram, graphically representing the size and size distribution of all the particulates in a preparation.

Exemplary particulate hydrophobic therapeutic agents can have different morphological characteristics. In some embodiments the particulate hydrophobic therapeutic agent can be crystalline. In yet other embodiments of the present disclosure the particulate hydrophobic therapeutic agent can be amorphous. Additionally, combinations of crystalline and amorphous particulate hydrophobic therapeutic agents can be desirable in order to achieve, for example, desired solubilities of the particulate hydrophobic therapeutic agents.

In some embodiments, the particulate hydrophobic therapeutic agent can have an average diameter (“dn”, number average) that is less than about 30 μm or less than about 10 μm. Also, in some embodiments, the particulate hydrophobic therapeutic agent can have an average diameter of about 100 nm or larger. For example, the microparticulates associated with the expandable elastic portion can have an average diameter in the range of about 100 nm to about 10 μm, about 150 nm to about 2 μm, about 200 nm to about 5 μm, or even about 0.3 μm to about 1 μm.

Nucleic Acids

Nucleic acids used with embodiments of the invention can include various types of nucleic acids that can function to provide a therapeutic effect. Exemplary types of nucleic acids can include, but are not limited to, ribonucleic acids (RNA), deoxyribonucleic acids (DNA), small interfering RNA (siRNA), micro RNA (miRNA), piwi-interacting RNA (piRNA), short hairpin RNA (shRNA), antisense nucleic acids, aptamers, ribozymes, locked nucleic acids and catalytic DNA. In a particular embodiment, the nucleic acid used is siRNA and/or derivatives thereof.

In some exemplary embodiments of the present disclosure, the range of the percent ratio of hydrophobic active agent to cationic agent (e.g. % PTX/% PEI or % PTX/% DOTAP; wt/wt) is from about 99.9/0.1 to about 70/30. In yet other embodiments it can be appreciated that the range of the percent ratio of hydrophobic active agents is from about 99/1 to about 73/27; from about 98/2 to about 75/25; from about 98/2 to about 86/14; from about 97/3 to about 88/12; from about 95/5 to about 90/10; and even in some exemplary embodiments from about 93/7 to about 91/9.

Hydrophilic Base Coatings

In various embodiments herein, a hydrophilic base coat and/or the substrate of the device or a portion of the device can be formed from a hydrophilic material such as a hydrophilic polyether block amide copolymer. The polyether block amide copolymer can include blocks with hydrophilic properties. In some embodiments the polyether block amide copolymer can include blocks of polyethylene glycol (PEG).

In various embodiments, the hydrophilic polyether block amide copolymer can have a water contact angle less than or equal to 80 degrees. In various embodiments, the hydrophilic polyether block amide copolymer can have a water contact angle less than or equal to 70 degrees. In various embodiments, the hydrophilic polyether block amide copolymer can have a water contact angle less than or equal to 60 degrees. In some embodiments, the hydrophilic polyether block amide copolymer can have a water contact angle greater than or equal to 20 degrees.

In some embodiments the hydrophilic polyether block amide copolymer can have a water absorption at equilibrium at 20 degrees Celsius and 50% relative humidity of greater than or equal to 1.0, 1.1, 1.2, 1.3, 1.4, 1.5, or 1.6% (as measured by ISO 62). In some embodiments the hydrophilic polyether block amide copolymer can have a water absorption at equilibrium at 20 degrees Celsius and 50% relative humidity of less than 5.0, 4.5, 4.0, 3.5, 3.0, 2.5, 2.0 or 1.6% (as measured by ISO 62).

Exemplary hydrophilic polyether block amide copolymers include PEBAX® MV1074 and MI-11657, commercially available from Arkema. Some examples of hydrophilic polyether block amide copolymers are described in U.S. Pat. No. 8,952,103 and U.S. Publ, Pat. Appl. No. US2009/0221767 the content of which relating to hydrophilic polyether block amide copolymers is herein incorporated by reference.

Substrates

In embodiments the device substrate can be formed from a hydrophilic polyether block amide copolymer such as those described above. However, in some embodiments the hydrophilic polyether block amide copolymer does not form the substrate, but exists as a layer disposed over the substrate. In such embodiments it will be appreciated that the substrate can be formed from any desirable material, or combination of materials, suitable for use within the body. In some embodiments the substrate is formed from compliant and flexible materials, such as elastomers (polymers with elastic properties). Exemplary elastomers can be formed from various polymers including polyurethanes and polyurethane copolymers, polyethylene, styrene-butadiene copolymers, polyisoprene, isobutylene-isoprene copolymers (butyl rubber), including halogenated butyl rubber, butadiene-styrene-acrylonitrile copolymers, silicone polymers, fluorosilicone polymers, polycarbonates, polyamides, polyesters, polyvinyl chloride, polyether-polyester copolymers, polyether-polyamide copolymers, and the like. The substrate can be made of a single elastomeric material, or a combination of materials.

Other materials for the substrate can include those formed of polymers, including oligomers, homopolymers, and copolymers resulting from either addition or condensation polymerizations. Examples of suitable addition polymers include, but are not limited to, acrylics such as those polymerized from methyl acrylate, methyl methacrylate, hydroxyethyl methacrylate, hydroxyethyl acrylate, acrylic acid, methacrylic acid, glyceryl acrylate, glyceryl methacrylate, methacrylamide, and acrylamide; vinyls such as ethylene, propylene, vinyl chloride, vinyl acetate, vinyl pyrrolidone, vinylidene difluoride, and styrene. Examples of condensation polymers include, but are not limited to, nylons such as polycaprolactam, polylauryl lactam, polyhexamethylene adipamide, and polyhexamethylene dodecanediamide, and also polyurethanes, polycarbonates, polyamides, polysulfones, poly(ethylene terephthalate), polydimethylsiloxanes, and polyetherketone.

Beyond polymers, and depending on the type of device, the substrate can also be formed of other inorganic materials such as metals (including metal foils and metal alloys), glass and ceramics.

Processes to modify substrates described above can include chemical modifications to improve performance characteristics of the substrate. Specific chemical processes that can be used include ozone treatment, chemical oxidation, acid chemical etching, base chemical etching, plasma treatment and corona treatment, surface grafting, thermally activated coating processes (both covalent and non-covalent) and surface modifications including coatings containing dopamine, tannic acid, plant polyphenols and other catechols or catechol containing derivatives of hydrophilic moieties. Additionally, processes to form substrates described above can include physical modifications for example, but not limited to, sand blasting and surface texturing (for example either during or after the molding process of polymers).

In some embodiments, the modification of substrates as described herein can allow for omission of a base coating layer (such as a hydrophilic layer) as substrate surfaces that have been modified will allow for improved adhesion of a hydrophobic therapeutic agent and cationic agent compared with that of a hydrophilic layer.

Devices

It will be appreciated that embodiments herein include, and can be used in conjunction with, various types of devices including, but not limited to, drug delivery devices such as drug eluting balloon catheters, drug-containing balloon catheters, stents, grafts, and the like.

Some embodiments described herein can be used in conjunction with balloon expandable flow diverters, and self-expanding flow diverters. Other embodiments can include uses in contact with angioplasty balloons (for example, but not limited to, percutaneous transluminal coronary angioplasty and percutaneous transluminal angioplasty). Yet other embodiments can include uses in conjunction with sinoplasty balloons for ENT treatments, urethral balloons and urethral stents for urological treatments and gastro-intestinal treatments (for example, devices used for colonoscopy). Hydrophobic active agent can be transferred to tissue from a balloon-like inflatable device or from a patch-like device. Other embodiments of the present disclosure can further be used in conjunction with micro-infusion catheter devices. In some embodiments, micro-infusion catheter devices can be used to target active agents to the renal sympathetic nerves to treat, for example, hypertension.

Embodiments included herein can also be used in conjunction with the application of various active agents to the skin (for example, but not limited to transdermal drug delivery).

Other exemplary medical applications wherein embodiments of the present disclosure can be used further encompass treatments for bladder neck stenosis (e.g. subsequent to transurethral resection of the prostrate), laryngotrachial stenosis (e.g. in conjunction with serial endoscopic dilatation to treat subglottic stenosis, treatment of oral cancers and cold sores and bile duct stenosis (e.g. subsequent to pancreatic, hepatocellular of bile duct cancer). By way of further example, embodiments herein can be used in conjunction with drug applicators. Drug applicators can include those for use with various procedures, including surgical procedures, wherein active agents need to be applied to specific tissue locations. Examples can include, but are not limited to, drug applicators that can be used in orthopedic surgery in order to apply active agents to specific surfaces of bone, cartilage, ligaments, or other tissue through physical contact of the drug applicator with those tissues. Drug applicators can include, without limitation, hand-held drug applicators, drug patches, drug stamps, drug application disks, and the like.

In some embodiments, drug applicators can include a surface having a hydrophilic polymer layer disposed thereon and coated therapeutic agent particles disposed on the hydrophilic polymer layer, the coated therapeutic agent particles comprising a particulate hydrophobic therapeutic agent; and a cationic agent disposed over the particulate hydrophobic therapeutic agent.

In use, various embodiments included herein can enable rapid transfer of therapeutic agents to specific targeted tissues. For example, in some embodiments, a care provider can create physical contact between a portion of a drug delivery device including a therapeutic agent and the tissue being targeted and the therapeutic agent will be rapidly transferred from the drug delivery device to that tissue. As such, precise control over which tissues the therapeutic agent is provided to can be achieved.

One beneficial aspect of various embodiments described herein is that the therapeutic agent can be transferred from the drug delivery device or coating to the targeted tissue very rapidly. In some embodiments substantial transfer of the therapeutic agent from the drug delivery device or coating to the tissue occurs in 30 minutes or less. In some embodiments substantial transfer of the therapeutic agent from the drug delivery device or coating to the tissue occurs in 15 minutes or less. In some embodiments substantial transfer of the therapeutic agent from the drug delivery device or coating to the tissue occurs in 10 minutes or less. In some embodiments substantial transfer of the therapeutic agent from the drug delivery device or coating to the tissue occurs in 5 minutes or less. In some embodiments substantial transfer of the therapeutic agent from the drug delivery device or coating to the tissue occurs in 2 minutes or less. In some embodiments substantial transfer of the therapeutic agent from the drug delivery device or coating to the tissue occurs in 1 minute or less.

It should be noted that, as used in this specification and the appended claims, the singular forms “a,” “an,” and “the” include plural referents unless the content clearly dictates otherwise. Thus, for example, reference to a composition containing “a compound” includes a mixture of two or more compounds. It should also be noted that the term “or” is generally employed in its sense including “and/or” unless the content clearly dictates otherwise.

It should also be noted that, as used in this specification and the appended claims, the phrase “configured” describes a system, apparatus, or other structure that is constructed or configured to perform a particular task or adopt a particular configuration to. The phrase “configured” can be used interchangeably with other similar phrases such as arranged and configured, constructed and arranged, constructed, manufactured and arranged, and the like.

All publications and patent applications in this specification are indicative of the level of ordinary skill in the art to which this invention pertains. All publications and patent applications are herein incorporated by reference to the same extent as if each individual publication or patent application was specifically and individually indicated by reference. To the extent inconsistencies arise between publications and patent applications incorporated by reference and the present disclosure, information in the present disclosure will govern.

The invention has been described with reference to various specific and preferred embodiments and techniques. However, it should be understood that many variations and modifications may be made while remaining within the spirit and scope of the invention.

Claims

1. A drug delivery coating for an inflatable balloon comprising a base polymeric layer, the base polymeric layer comprising a hydrophilic polyether block amide copolymer and having a hydrophilic surface, the base polymeric layer configured to be disposed on the inflatable balloon;a therapeutic agent layer forming an exterior surface of the drug delivery coating, the therapeutic agent layer disposed on the hydrophilic surface of the base polymeric layer and having a composition different than the base polymeric layer, the therapeutic agent layer comprising a particulate hydrophobic therapeutic agent; anda cationic agent;wherein the therapeutic agent layer is configured on the exterior surface to be transferred from the hydrophilic surface to a target tissue in 15 minutes or less.

2. The drug delivery coating of claim 1, the hydrophilic polyether block amide copolymer having a water contact angle less than or equal to 80 degrees.

3. The drug delivery coating of claim 1, the hydrophilic polyether block amide copolymer having a water contact angle less than or equal to 70 degrees.

4. The drug delivery coating of claim 1, the hydrophilic polyether block amide copolymer having a water contact angle less than or equal to 60 degrees.

5. The drug delivery coating of claim 1, the hydrophilic polyether block amide copolymer comprising a water absorption at equilibrium at 20 degrees Celsius and 50% relative humidity of greater than 1.0% (ISO 62).

6. The drug delivery coating of claim 1, the hydrophilic polyether block amide copolymer comprising a water absorption at equilibrium at 20 degrees Celsius and 50% relative humidity of 1.4% or greater (ISO 62).

7. The drug delivery coating of claim 1, the particulate hydrophobic therapeutic agent and the cationic agent forming coated therapeutic agent particles.

8. The drug delivery coating of claim 1, the cationic agent selected from the group consisting of cationic lipids, neutral lipids with cationic groups, and cationic polymers.

9. The drug delivery coating of claim 1, the cationic agent selected from the group consisting of polyethyleneimine and 1,2-dioleoyl-3-trimethylammonium-propane (DOTAP).

10. A drug delivery device comprising a drug delivery coating for an inflatable balloon, the drug delivery device comprising a substrate comprising the inflatable balloon; a base polymeric layer, the base polymeric layer comprising a hydrophilic polyether block amide copolymer and having a hydrophilic surface, the base polymeric layer configured to be disposed on the inflatable balloon;a therapeutic agent layer forming an exterior surface of at least a portion of the drug delivery device, the therapeutic agent layer contacting the hydrophilic surface of the substrate, the therapeutic agent layer comprisinga particulate hydrophobic therapeutic agent; anda cationic agent; andwherein the therapeutic agent layer is configured on the exterior surface to be transferred from the hydrophilic surface to a target tissue in 15 minutes or less.

11. The drug delivery device of claim 10, the hydrophilic polyether block amide copolymer having a water contact angle less than or equal to 80 degrees.

12. The drug delivery device of claim 10, the hydrophilic polyether block amide copolymer comprising a water absorption at equilibrium at 20 degrees Celsius and 50% relative humidity of greater than 1.0% (ISO 62).

13. A method of making a medical device comprising a drug delivery coating for an inflatable balloon, the method comprising: depositing a base polymeric layer onto at least a portion of the inflatable balloon,the base polymeric layer comprising a hydrophilic polyether block amide copolymer and having a hydrophilic surface, the base polymeric layer configured to be disposed on the inflatable balloon;depositing a therapeutic agent layer onto at least a portion of the base polymeric layer, the therapeutic agent layer contacting the surface of the base polymeric layer, the therapeutic agent layer comprisinga particulate hydrophobic therapeutic agent; anda cationic agent; andwherein the therapeutic agent layer is configured on the exterior surface to be transferred from the hydrophilic surface to a target tissue in 15 minutes or less.

14. The method of claim 13, the hydrophilic polyether block amide copolymer having a water contact angle less than or equal to 80 degrees.

15. The method of claim 13, the hydrophilic polyether block amide copolymer comprising a water absorption at equilibrium at 20 degrees Celsius and 50% relative humidity of greater than 1.0% (ISO 62).

16. The method of claim 13, wherein the therapeutic agent layer is deposited using a solvent that does not absorb into the hydrophilic polyether block amide copolymer.

17. A drug delivery coating for an inflatable balloon comprising a base polymeric layer, the base polymeric layer comprising a hydrophilic polyether block amide copolymer and having a hydrophilic surface, the base polymeric layer configured to be disposed on the inflatable balloon;a therapeutic agent layer forming an exterior surface of the drug delivery coating, the therapeutic agent layer disposed on the hydrophilic surface of the base polymeric layer and having a composition different than the base polymeric layer, the therapeutic agent layer comprising a particulate hydrophobic therapeutic agent; anda cationic agent;wherein the therapeutic agent layer is configured on the exterior surface for delivery to a cell membrane and cellular components within a lipid bilayer in 5 minutes or less.

18. The drug delivery coating of claim 1, the hydrophilic polyether block amide copolymer having a water contact angle less than or equal to 20 degrees.