Patent Application
20200268679
Sequestration of active pharmaceutical ingredients (APIs) into drug carriers has been considered for producing formulations with biological efficacy.
In an embodiment of the invention, a nanoparticle includes a modified salt including a water-soluble active pharmaceutical ingredient (API) ion paired with a hydrophobic counterion of an ion pairing (IP) reagent and a nanoparticle encapsulant material substantially surrounding the modified salt. The API can be an antibacterial and/or a biologic. The API can be an antimicrobial small molecule, a peptide, a protein, or an aminoglycoside. The API can have an aqueous solubility of greater than 10 mg/ml, a log P value less than −2 in an aqueous solution at pH of 7, and/or 1, 2, 3, 4, 5, 6, or more ionic groups. The API can be other than an oligonucleotide. The API can be gentamycin, polymyxin B, mastoparan 7, sub5, LL37, colistin, ecumicin, OZ439, ovalbumin, or lysozyme.
The counterion can have a log P value of 2 or greater at a pH of 7. The counterion can have a log P value of greater than 5, and the release profile of the API can exhibit a plateau in the release rate with time. The counterion can have 1, 2, or more ionic sites. The counterion can be an anionic counterion that has a pKa value of from −2 to 5. The counterion can have a pKb value of greater than 3. The counterion can be a quaternized cationic species. The counterion can have an ionic site selected from the group consisting of a carboxylic acid, sulfate, sulfonate, or amine. The IP reagent can be sodium hexanoate, sodium decanoate, benzenesulfonic acid monohydrate, sodium 2-naphthalenesulfonate, (1R)-(−)-10-camphorsulfonic acid, sodium 1,2-ethanesulfonate, sodium 1-heptanesulfonate, sodium 1-octanesulfonate monohydrate, sodium 1-decanesulfonate, or sodium deoxycholate. The IP reagent can be sodium dodecyl sulfate (SDS), sodium decyl sulfate (DS), sodium dodecylbenzene sulfonate (DBS), sodium myristate (MA), sodium oleate (OA), or pamoic acid disodium salt (PA). The counterion can be dodecyl hydrogen sulfate, decyl hydrogen sulfate, dodecylbenzene sulfonic acid, or myristic acid. The counterion can be oleic acid or pamoic acid.
The nanoparticle encapsulant material can be a self-assembling material. The nanoparticle encapsulant material can be hydroxypropyl methylcellulose acetate succinate (HPMCAS), polystyrene-block-polyethylene glycol (PS-b-PEG), or polycaprolactone-block-polyethylene glycol (PCL-b-PEG). For example, the nanoparticle encapsulant material can be 1.6 kDa polystyrene-block-5 kDa polyethylene glycol or 5 kDa polycaprolactone-block-5 kDa polyethylene glycol.
The nanoparticle can include a polyethylene glycol coating on the nanoparticle.
The nanoparticle can have a particle size of from 10 nm to 1000 nm, from 10 nm to 1200 nm, from 25 nm to 1000 nm, from 50 nm to 500 nm, from 75 nm to 400 nm, from 100 nm to 350 nm, from 100 nm to 250 nm, or from 100 nm to 150 nm.
The API and a supplemental hydrophobic compound can be co-encapsulated within the nanoparticle. For example, the supplemental hydrophobic compound can be a therapeutic, imaging agent, or agrochemical compound.
The API can include gentamycin, polymyxin B, mastoporan 7, sub5, LL37, colistin, ecumicin, OZ439, ovalbumin, or lysozyme. The API can include an antimicrobial small molecule, for example, an antimicrobial small molecule having a molecular weight of less than 1000 Da. The API can include an aminoglycoside, for example, a 4,6-disubstituted deoxystreptamine trisaccharide. The API can include an oligopeptide, such as a linear oligopeptide or a cyclic oligopeptide, which can have a molecular weight of from 1000 Da to 2000 Da. The API can include a protein, such as an anionic protein or a cationic protein, which can have a molecular weight of greater than 2000 Da.
The IP reagent can include sodium dodecyl sulfate (SDS), sodium decyl sulfate (DS), sodium dodecylbenzene sulfonate (DBS), sodium myristate (MA), sodium oleate (OA), pamoic acid disodium salt (PA), vitamin E succinate, or sodium dextran sulfate (DXS). The counterion can include dodecyl hydrogen sulfate, decyl hydrogen sulfate, dodecylbenzene sulfonic acid, myristic acid, oleic acid, pamoic acid, vitamin E succinic acid, or dextran hydrogen sulfate, or a salt, such as an alkali metal (e.g., lithium (Li), sodium (Na), potassium (K), rubidium (Rb), or caesium (Cs)) salt, of any of these. The counterion can include a fatty acid, an alkyl hydrogen sulfate, an alkylsulfonic acid, an alkyl quaternary ammonium cation, or a salt, such as an alkali metal salt, of any of these.
The nanoparticle encapsulant material can include hydroxypropyl methylcellulose acetate succinate (HPMCAS), polystyrene-block-polyethylene glycol (PS-b-PEG), or polycaprolactone-block-polyethylene glycol (PCL-b-PEG). The nanoparticle encapsulant material can include a block copolymer, such as an amphiphilic block copolymer, which can have a molecular weight of about 10 kDa or less.
In an embodiment the active pharmaceutical ingredient is gentamycin, the ion pairing reagent is sodium dodecyl sulfate (SDS), and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment the active pharmaceutical ingredient is polymyxin B, the ion pairing reagent is sodium dodecyl sulfate (SDS), and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment, the active pharmaceutical ingredient is polymyxin B, the ion pairing reagent is sodium dodecylbenzene sulfonate (DBS), and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment the active pharmaceutical ingredient is polymyxin B, the ion pairing reagent is sodium oleate, and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment, the active pharmaceutical ingredient is mastoporan 7, the ion pairing reagent is sodium dodecyl sulfate (SDS), and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment the active pharmaceutical ingredient is sub5, the ion pairing reagent is sodium dodecyl sulfate (SD S), and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment, the active pharmaceutical ingredient is LL37, the ion pairing reagent is sodium dodecyl sulfate (SDS), and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment, the active pharmaceutical ingredient is colistin, the ion pairing reagent is sodium oleate, and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment, the active pharmaceutical ingredient is ecumicin, the ion pairing reagent is vitamin E succinate, and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment, the active pharmaceutical ingredient is OZ439, the ion pairing reagent is sodium oleate, and the nanoparticle encapsulation material is hydroxypropyl methylcellulose acetate succinate (HPMCAS). In an embodiment, the active pharmaceutical ingredient is ovalbumin, the ion pairing reagent is a quaternary ammonium surfactant, and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment, the active pharmaceutical ingredient is ovalbumin, the ion pairing reagent is cetyl trimethylammonium bromide, and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment, the active pharmaceutical ingredient is lysozyme, the ion pairing reagent is sodium oleate, and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment, the active pharmaceutical ingredient is lysozyme, the ion pairing reagent is sodium dodecyl sulfate (SDS), and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer. In an embodiment, the active pharmaceutical ingredient is lysozyme, the ion pairing reagent is dextran sulfate (DXS) polymer, and the nanoparticle encapsulation material is polycaprolactone-block-polyethylene glycol block copolymer.
A method of the invention for encapsulating an active pharmaceutical ingredient (API) includes producing a hydrophobic salt by ion pairing charged functional groups on a water soluble API with an ion pairing (IP) reagent and forming nanoparticles that are carriers of the hydrophobic salt to encapsulate the API, with the IP reagent including a counterion for the API. Producing a hydrophobic salt can include mixing the API and the IP in water to form a water-insoluble precipitate as the hydrophobic salt, removing the water, and dissolving the water-insoluble precipitate into an organic solvent. A polymer can be dissolved into the organic solvent. The organic solvent can be water-miscible.
The dissolved water-insoluble precipitate can be used in an organic stream to form the nanoparticles by flash nanoprecipitation.
The solution of the hydrophobic salt dissolved in the organic solvent can be continuously mixed with a polar solvent to form a mixed solution from which the nanoparticles assemble and precipitate.
Producing a hydrophobic salt can include dissolving the API in a water stream, dissolving the IP in an organic stream, and forming a water-insoluble precipitate as the hydrophobic salt through micro-mixing the organic stream against the water stream in a Flash NanoPrecipitation (FNP) process. A polymer can be dissolved into the organic stream. The organic stream can be water-miscible.
The nanoparticles can be formed by dissolving the API in a polar solvent to form a polar solution stream, dissolving the IP in an organic solvent to form an organic solution stream, and continuously mixing the polar solution stream against the organic solution stream to form a mixed solution from which the nanoparticles that encapsulate the API assemble and precipitate, and the organic solvent can be less polar than the polar solvent. A polymer can be dissolved into the organic solvent. The organic solvent can be water-miscible.
The nanoparticles can be formed by an emulsion/stripping process.
The API can be an antibacterial and/or a biologic. The API can be an antimicrobial small molecule, a peptide, a cationic peptide, an anionic peptide, a protein, a cationic protein, an anionic protein, or an aminoglycoside. The API can have an aqueous solubility of greater than 10 mg/ml, can have a log P value less than −2 in an aqueous solution at pH of 7, and/or can have 1, 2, 3, 4, 5, 6, or more ionic groups. The API can be other than an oligonucleotide. The API can be gentamycin, polymyxin B, mastoparan 7, sub5, LL37, colistin, ecumicin, OZ439, ovalbumin, or lysozyme. The API can be gentamycin, polymyxin B, mastoparan 7, sub5, colistin, or ovalbumin.
The counterion can have a log P value of 2 or greater at a pH of 7. The counterion can have a log P value of greater than 5. The release profile of the API can exhibit a plateau in the release rate (or fraction released) with time. The counterion can have 1, 2, or more ionic sites. The counterion can be an anionic counterion that has a pKa value of from −2 to 5. The counterion can have a pKb value of greater than 3. The counterion can be a quaternized cationic species, for example, a quaternized cationic species that is permanently cationic. The counterion can have an ionic site selected from the group consisting of a carboxylic acid, sulfate, sulfonate, or amine. The IP reagent can be sodium hexanoate, sodium decanoate, sodium myristate (MA), sodium oleate (OA), pamoic acid disodium salt (PA), benzenesulfonic acid monohydrate, sodium 2-naphthalenesulfonate, (1R)-(−)-10-camphorsulfonic acid, sodium 1,2-ethanesulfonate, sodium 1-heptanesulfonate, sodium 1-octanesulfonate monohydrate, sodium 1-decanesulfonate, sodium dodecyl sulfate (SDS), sodium dodecylbenzene sulfonate (DBS), sodium deoxycholate, or sodium decyl sulfate (DS). The counterion can be dodecyl hydrogen sulfate, decyl hydrogen sulfate, dodecylbenzene sulfonic acid, or myristic acid. The counterion can be oleic acid or pamoic acid.
The polymer can be self-assembling. The polymer can be hydroxypropyl methylcellulose acetate succinate (HPMCAS), polystyrene-block-polyethylene glycol (PS-b-PEG), or polycaprolactone-block-polyethylene glycol (PCL-b-PEG). For example, the polymer can be 1.6 kDa polystyrene-block-5 kDa polyethylene glycol or 5 kDa polycaprolactone-block-5 kDa polyethylene glycol.
The nanoparticles can include a polyethylene glycol coating.
The nanoparticles can have a Z-average particle size of from 10 nm to 1000 nm, from 25 nm to 1200 nm, from 50 nm to 500 nm, from 75 nm to 400 nm, from 100 nm to 350 nm, from 100 nm to 250 nm, or from 100 nm to 150 nm. The nanoparticles can have a polydispersity index (PDI) of from 0.06 to 0.5, from 0.07 to 0.34, from 0.08 to 0.27, from 0.1 to 0.2, or from 0.12 to 0.18.
The API and a supplemental hydrophobic compound can be co-encapsulated in the nanoparticles. For example, the supplemental hydrophobic compound can be a therapeutic, an imaging agent, or an agrochemical compound.
The API can include gentamycin, polymyxin B, mastoporan 7, sub5, LL37, colistin, ecumicin, OZ439, ovalbumin, or lysozyme. The API can include an antimicrobial small molecule, or example, an antimicrobial small molecule having a molecular weight of less than 1000 Da. The API can include an aminoglycoside, for example, a 4,6-disubstituted deoxystreptamine trisaccharide. The API can include an oligopeptide, such as a linear oligopeptide or a cyclic oligopeptide, which can have a molecular weight of from 1000 Da to 2000 Da. The API can include a protein, such as an anionic protein or a cationic protein, which can have a molecular weight of greater than 2000 Da.
The IP reagent can include sodium dodecyl sulfate (SDS), sodium decyl sulfate (DS), sodium dodecylbenzene sulfonate (DBS), sodium myristate (MA), sodium oleate (OA), pamoic acid disodium salt (PA), vitamin E succinate, or sodium dextran sulfate (DXS). The counterion can include dodecyl hydrogen sulfate, decyl hydrogen sulfate, dodecylbenzene sulfonic acid, myristic acid, oleic acid, pamoic acid, vitamin E succinic acid, or dextran hydrogen sulfate. The counterion can include a fatty acid, an alkyl hydrogen sulfate, an alkylsulfonic acid, or an alkyl quaternary ammonium cation.
The polymer can include hydroxypropyl methylcellulose acetate succinate (HPMCAS), polystyrene-block-polyethylene glycol (PS-b-PEG), or polycaprolactone-block-polyethylene glycol (PCL-b-PEG). The polymer can include a block copolymer, for example an amphiphilic block copolymer. The block copolymer can have a molecular weight of about 10 kDa or less.
Embodiments of the invention are discussed in detail below. In describing embodiments, specific terminology is employed for the sake of clarity. However, the invention is not intended to be limited to the specific terminology so selected. A person skilled in the relevant art will recognize that other equivalent parts can be employed and other methods developed without parting from the spirit and scope of the invention. All references cited herein are hereby incorporated by reference in their entirety as if each had been individually incorporated.
Nanoprecipitation of active pharmaceutical ingredients (APIs) into drug carriers, e.g., to form nanocarriers (NCs), for example, nanoparticles (NPs), can be used to produce formulations with stable nanoparticles and biological efficacy. (In this text, unless otherwise indicated, the terms “nanocarrier” (NC) and “nanoparticle” (NP) are used interchangeably.) However, many nanoprecipitation techniques are applicable for only hydrophobic and water-insoluble APIs, and have not been demonstrated for highly soluble therapeutics. Presented here is a model and technique to encapsulate water-soluble APIs using nanoprecipitation techniques by manipulating API salt forms. APIs are ion paired with hydrophobic counterions to produce new API salts that exhibit altered solubilities suitable for nanoprecipitation processing. Nanocarrier properties, such as stability and release rates, can be tuned by varying ion-pair (IP) molecular structure and ion-pair to API molar ratios. The tools set forth herein can be used to process hydrophilic APIs into nanocarrier systems. The governing rules of ion pair identity, and processing conditions required for successful encapsulation are experimentally determined and assessed with theoretical models. Successful NC, e.g, nanoparticle, formation for the antibiotic polymyxin B can be facilitated with hydrophobicity of the ion pair acid being greater than log P=2 for strong acids and greater than log P=8 for weak acids. Oleic acid with a log P=8, and pKa=5, can be suitable as an ion pair agent, because it is biocompatible and forms ion pair complexes. NC formation from pre-formed, organic soluble ion pairs, can be compared to in situ ion pairs where NCs are made in a single precipitation step. NC properties, such as stability and release rates, can be tuned by varying ion pair molecular structure and ion pair-to-API molar ratios. For polymyxin B, NCs ˜10°-200 nm in size and with characteristic API release rates over three days were produced. The embodiments of the invention set forth herein represent new tools and demonstrate a new approach that enables the formation of nanoparticles from previously intractable compounds, for example, enabling the processing of hydrophilic APIs into nanocarrier systems.
Thus, set forth herein is encapsulation of hydrophilic actives into nanocarriers via hydrophobic ion-pairing. This approach may be employed, inter alia, in treatment of infectious diseases, such as bacterial, fungal, viral, and parasitic infections. More particularly, the controlled delivery of active therapeutic ingredients (APIs) through nanocarriers can result in improved bioavailability, reduced toxicity, sustained activity, simplified dosing regimens, improved patient adherence, and enhanced overall efficacy.
In a process that is an embodiment of the invention, charged functional groups on the API are ion-paired with a counter ion to produce an API with transiently altered solubilities. Flash NanoPrecipitation (FNP) was used to self-assemble nanoparticles (NPs) containing an encapsulated API-IP complex. Two routes of assembly were explored: (1) complexation of the API with the hydrophobic counterion during FNP (termed “in situ ion pairing”); and (2) complexation prior to FNP (termed “pre-ion pairing”). For the pre-ion paired method, particles were formed by rapid micro-mixing of a hydrophobic-hydrophilic block-copolymer and API-IP complex dissolved in an organic solvent against deionized (DI) water through a confined impingement jet (CIJ) mixer. For the in situ ion-pairing method, the organic stream containing block copolymer and anionic IP dissolved in organic solvent were rapidly micro-mixed with the water stream containing cationic hydrophilic API dissolved in water through a CIJ mixer. For both methods, the organic and water streams were mixed in a 1:1 volume ratio and the resulting mixed streams were subsequently diluted tenfold into water.
In nanoprecipitation processes, APIs may be dissolved in organic solvents and mixed with water as an antisolvent to induce precipitation and nanocarrier self-assembly. However, such direct precipitation methods may be only feasible for water insoluble compounds (c Log P>4), and may not be feasible for encapsulating hydrophilic biologics into nanocarriers. Water soluble biologics may be encapsulated through alternative water-in-oil-in-water emulsion (W/O/W) or liposomal processes that require multiple steps, suffer from poor encapsulation efficiencies, or exhibit low drug mass loadings.
Experimental verification showed the approach of the invention to be capable of encapsulating hydrophilic APIs using Flash NanoPrecipitation via hydrophobic ion pairing. For example, the following APIs were encapsulated: the antimicrobial small molecules polymyxin B and colistin; the peptides mastoparan 7 and sub5; the protein ovalbumin; and the aminoglycoside gentamycin.
The successful formulation of tobramycin, gentamycin, and polymyxin B into NPs with the FNP process can expand the applicability of these therapeutics. For example, these APIs, which are used to manage P. aeruginosa bacterial pulmonary cystic fibrosis infections, adhere to pulmonary mucus and do not effectively reach sites of infections after drug administration. Previously, for nanoparticle formulations, the ability to encapsulate soluble APIs and control release had been limited to liposomal formulations; and while some liposomes can be loaded by a mechanism of transfer across the liposome bilayer and precipitation inside the liposome, this technique is not available for highly ionic API's such as the antibiotics considered herein. Therefore, the ion pairing approach presented herein provides a powerful new tool for encapsulation of API's that was not previously available.
Pharmaceutical companies can apply the disclosed technology to enhance drug-based therapies that are already in the market. Pharmaceutical companies can also apply this technology to enable drug therapies to satisfy clinical trial objectives that would be otherwise not met.
The controlled delivery of active therapeutic ingredients from nanocarriers can result in improved bioavailability, reduced toxicity, sustained activity, simplified dosing regimens, improved patient adherence, and enhanced overall efficacy [Solaro, R., F. Chiellini, and A. Battisti, Targeted Delivery of Protein Drugs by Nanocarriers. Materials, 2010. 3(3): p. 1928-1980.]. NC formulations (e.g., nanoparticles) can be used to target delivery, and then to release cargo at the desired site. NC formation through direct precipitation methods is attractive because these methods form NCs, e.g., rapidly form active pharmaceutical ingredient (API) nanoparticles, with high mass loadings in a scalable and continuous fashion, as in the case of Flash NanoPrecipitation (FNP) [Immordino, M. L., F. Dosio, and L. Cattel, Stealth liposomes: review of the basic science, rationale, and clinical applications, existing and potential. International Journal of Nanomedicine, 2006. 1(3): p. 297-315; Steichen, S. D., M. Caldorera-Moore, and N. A. Peppas, A review of current nanoparticle and targeting moieties for the delivery of cancer therapeutics. European Journal of Pharmaceutical Sciences, 2013. 48(3): p. 416-427.; Galindo-Rodriguez, S. A., et al., Polymeric nanoparticles for oral delivery of drugs and vaccines: a critical evaluation of in vivo studies. Critical Reviews in Therapeutic Drug Carrier Systems, 2005. 22(5): p. 419-464.]. In nanoprecipitation processes, APIs, e.g., hydrophobic APIs, may be dissolved in organic solvents and mixed with water as an antisolvent to induce precipitation and NC self-assembly. However, such direct precipitation methods are only feasible for water insoluble compounds (Log P>4), and cannot be used to encapsulate hydrophilic peptides and biologics into NC form. Water soluble biologics may be encapsulated through water-in-oil-in-water emulsion (W/O/W) or liposomal processes that require multiple steps, suffer from poor encapsulation efficiencies, or exhibit low drug mass loadings [Li, S.-D. and L. Huang, Pharmacokinetics and Biodistribution of Nanoparticles. Molecular Pharmaceutics, 2008. 5(4): p. 496-504; Owens Iii, D. E. and N. A. Peppas, Opsonization, biodistribution, and pharmacokinetics of polymeric nanoparticles. International Journal of Pharmaceutics, 2006. 307(1): p. 93-102; Pattni, B. S., V. V. Chupin, and V. P. Torchilin, New Developments in Liposomal Drug Delivery. Chemical Reviews, 2015. 115(19): p. 10938-10966.]. The new methods set forth herein, which efficiently encapsulate hydrophilic APIs into nanocarriers using direct water precipitation methods, can expand the nanocarrier API pharmacokinetic (PK) and/or pharmacodynamics (PD) properties that can be achieved.
Engineering of API water solubilities can enable new processing methods for nanocarrier encapsulation. This can be performed by reversible covalent conjugation of APIs with hydrophobic molecules, which results in the production of a hydrophobic prodrug. After encapsulation and delivery, covalent linkages are cleaved, thereby producing the original API for therapeutic activity. However, covalent modification of APIs results in the creation of a new molecular entity, which requires additional comprehensive, costly, and time-consuming testing for Food & Drug Administration (FDA) approval. API salt form engineering is an alternative route to tune API water solubility. In this process, charged functional groups on the API are ion-paired with a counter ion to produce a API with transiently altered solubilities. An advantage of salt form engineering is that resultant products are not considered new molecular entities, and do not require full FDA reapproval. However, in most instances, API salt forms are screened and engineered for enhanced water solubility. The alternative use of hydrophobic ion-pairs to create hydrophobic salt forms is a non-conventional method to increase API hydrophobicity. This technique has been used for the precipitation of weakly hydrophobic small molecules (c Log P=2-5) into nanocarriers, but not for highly water soluble (c Log P>0) and positively charged biologics. In this text, hydrophobic ion pairing is demonstrated to encapsulate highly soluble, positively charged antibiotic biologics, such as gentamycin (c Log P=−4.21) and polymyxin B (c Log P=−5.6). The ion pairs (IPs) are processed into stable nanocarriers through Flash NanoPrecipitation, a continuous and scalable water precipitation process. A priori, it might have been expected that such biologics could not be precipitated in water with hydrophobic ion-pairs, because of their high API water solubilities. The chemical identities of ion pairs, rules governing precipitation, and processing methods that can give rise to API salts with the desired solubilities for encapsulation were previously unknown.
Previously, ion pairing has been used to formulate nanoparticles from hydrophobic compounds. These are defined by having log P values greater than 1, 2, 3, 4, or 5 at neutral pH [Pinkerton, N. M., et al., Formation of stable nanocarriers by in situ ion pairing during block-copolymer directed rapid precipitation. Molecular pharmaceutics, 2013. 10(1): p. 319-328]. For example, Song et. al [Song, Y. H., et al., A novel in situ hydrophobic ion pairing (HIP) formulation strategy for clinical product selection of a nanoparticle drug delivery system. Journal of Controlled Release, 2016. 229: p. 106-119.] used ion pairing for AZD281, which had a log P of 2 at a neutral pH of 7. Another group of researchers has complexed proteins and polymeric charged species with oppositely charged polymeric compounds with high solubility. High solubility could mean log P values less than −2 and/or solubilities in aqueous media of over 10 mg/ml at pH=7. Patel and Guadana [Gaudana, R., et al., Design and evaluation of a novel nanoparticulate-based formulation encapsulating a HIP complex of lysozyme. Pharmaceutical development and technology, 2013. 18(3): p. 752-759; Patel, A., R. Gaudana, and A. K. Mitra, A novel approach for antibody Nanocarriers development through hydrophobic ion-pairing complexation. Journal of Microencapsulation, 2014. 31(6): p. 542-550] showed that soluble antibody or lysozyme proteins could be complexed with oppositely-charged dextran sulfate. Dextran sulfate is a water-soluble polymer. The resulting precipitate is not a hydrophobic complex, but rather a “coacervate” as commonly defined in the polymer community [Antonov, M., M. Mazzawi, and P. L. Dubin, Entering and exiting the protein—polyelectrolyte coacervate phase via nonmonotonic salt dependence of critical conditions. Biomacromolecules, 2009. 11(1): p. 51-59; Overbeek, J. T. G. and M. Voorn, Phase separation in polyelectrolyte solutions. Theory of complex coacervation. Journal of Cellular Physiology, 1957. 49(S1): p. 7-26]. A coacervate is a precipitate resulting from ionic interactions between two soluble polymer species with opposite charges.
Soluble, or relatively soluble, compounds have been encapsulated by covalent conjugation to create hydrophobic pro-drugs [Bruno, B. J., G. D. Miller, and C. S. Lim, Basics and recent advances in peptide and protein drug delivery. Therapeutic delivery, 2013. 4(11): p. 1443-1467.; Jain, A., et al., Peptide and Protein Delivery Using New Drug Delivery Systems. Crit Rev Ther Drug Carrier Syst. 2013. 30(4): p. 293-329.]. After encapsulation and delivery, covalent linkages are cleaved, thereby producing the original API for therapeutic activity. However, covalent modification of APIs results in the creation of a new molecular entity, which requires additional FDA approval. An alternative route to reduce API water solubility is to ion pair the active with a hydrophobic counterion [Muheem, A., et al., A review on the strategies for oral delivery of proteins and peptides and their clinical perspectives. Saudi Pharmaceutical Journal, 2016. 24(4): p. 413-428.; Sohn, J. S., et al., Polymer prodrug approaches applied to paclitaxel. Polymer Chemistry, 2010. 1(6): p. 778-792.; Ansell, S. M., et al., Modulating the Therapeutic Activity of Nanoparticle Delivered Paclitaxel by Manipulating the Hydrophobicity of Prodrug Conjugates. Journal of Medicinal Chemistry, 2008. 51(11): p. 3288-3296.; Marcus, Y. and G. Hefter, Ion Pairing. Chemical Reviews, 2006. 106(11): p. 4585-4621.; Matschiner, S., R. Neubert, and W. Wohlrab, Optimization of topical erythromycin formulations by ion pairing. Skin Pharmacology: The Official Journal of the Skin Pharmacology Society, 1995. 8(6): p. 319-325.]. With this approach the resultant products are not considered new molecular entities and do not require full FDA reapproval. In most instances, API salt forms have been engineered for enhanced water solubility or crystal stability; that is, the technique has been conventionally used for the precipitation of hydrophobic small molecules (Log P=2-5) into NCs. [Serajuddin, A. T. M., Salt formation to improve drug solubility. Advanced Drug Delivery Reviews, 2007. 59(7): p. 603-616.; Meyer, J. D. and M. C. Manning, Hydrophobic Ion Pairing: Altering the Solubility Properties of Biomolecules. Pharmaceutical Research, 1998. 15(2): p. 188-193.]. By contrast, the use of hydrophobic ion pairs to create less soluble drug forms is non-conventional.
In this text is demonstrated hydrophobic ion pairing to encapsulate highly soluble, positively charged antibiotic biologics: using model gentamycin (c Log P=−4.21) and polymyxin B (c Log P=−5.6). The ion pairs are processed into stable nanocarriers through Flash NanoPrecipitation, a continuous and scalable water precipitation process. A priori, it might have been expected that such biologics cannot be precipitated in water with hydrophobic ion pairs, because of their high water solubilities. The chemical identities of ion pairs, rules governing precipitation, and processing methods that can give rise to API salts with the desired solubilities for encapsulation were previously unknown.
This text describes the use of Flash NanoPrecipitation, a continuous and scalable method of forming NCs with high API mass loads (>50 to 90%) to encapsulate the APIs. The FNP process relies upon rapid micromixing (O(ms)) of a solvent and an antisolvent stream to create high supersaturations, which drive high nucleation rates. The hydrophobic APIs precipitate into NCs, while the hydrophobic block of the stabilizing polymer absorbs onto the NC surface to arrest particle growth. This results in highly loaded NCs with a narrow size distribution. We have described the process in detail elsewhere [Johnson, B. K. and R. K. Prud'homme, Flash NanoPrecipitation of Organic Actives and Block Copolymers using a Confined Impinging Jets Mixer. Australian Journal of Chemistry, 2003. 56(10): p. 1021-1024.; D'Addio, S. M. and R. K. Prud'homme, Controlling drug nanoparticle formation by rapid precipitation. Advanced Drug Delivery Reviews, 2011. 63(6): p. 417-426.; Saad, W. S. and R. K. Prud'homme, Principles of nanoparticle formation by flash nanoprecipitation. Nano Today, 2016. 11(2): p. 212-227.].
Certain research has considered the precipitation of oligonucleotides (DNA, RNA, siRNA, mRNA) with oppositely-charged hydrophobic lipids [Gindy, M. E., et al., Mechanism of macromolecular structure evolution in self-assembled lipid nanoparticles for siRNA delivery. Langmuir, 2014. 30(16): p. 4613-4622.; Luo, D. and W. M. Saltzman, Synthetic DNA delivery systems. Nature biotechnology, 2000. 18(1): p. 33-37.; Mueller, R. H., K. Maeder, and S. Gohla, Solid lipid nanoparticles (SLN) for controlled drug delivery—a review of the state of the art. European journal of pharmaceutics and biopharmaceutics, 2000. 50(1): p. 161-177.; Radler, J. O., et al., Structure of DNA-cationic liposome complexes: DNA intercalation in multilamellar membranes in distinct interhelical packing regimes. Science, 1997. 275(5301): p. 810-814.]. These examples are only demonstrated for complexation with the highly negatively charged oligonucleotides which have charge spacings of 3.4 Å, which is for 6 bonds between ionized phosphorous units. Prior to the invention in this patent application there was no indication that materials with lower charge densities than oligonucleotides could be precipitated with hydrophobic compounds to produce nanoparticles.
The ion pairing between the highly soluble active species (API) and the counterion species can form nanoparticles using either the Flash NanoPrecipitation technique or an emulsification and stripping technique [Song, Y. H., et al., A novel in situ hydrophobic ion pairing (HIP) formulation strategy for clinical product selection of a nanoparticle drug delivery system. Journal of Controlled Release, 2016. 229: p. 106-119]. The nanoparticles formed can, for example, have sizes between 25 nm and 100 nm, or 25 nm and 400 nm, or 25 nm and 1000 nm, or 25 nm and 1200 nm, or 25 nm and 6000 nm. Sizes can be measured using a Malvern Nanosizer dynamic light scattering instrument using normal mode analysis software. The Z-average, also known as intensity average, diameter is reported.
The ion pairing process described herein can be useful for the preparation of antibacterial actives. Antibacterial agents based on peptide units can be suitable for this ion pairing technique.
Embodiments according to the present invention can include the complexation of highly soluble actives, that is, the species of interest to be encapsulated, with oppositely charged hydrophobic species.
An embodiment of the invention involves the complexation of highly soluble actives, that is, the species of interest to be encapsulated, with oppositely-charged hydrophobic species. For example, the actives can have solubilities of greater than 10 mg/ml or log P values of −2 or less or −3 or less in pH 7 aqueous solutions. The actives (APIs) can have 2, 3, 4, 5, 6, or more ionic groups that make them water soluble. In an embodiment, the actives can be other than oligonucleotides.
In an embodiment of the invention, an active of intermediate solubility, e.g., −2<log P<5, can be ion paired with a hydrophobic counterion, so that the formed complex precipitates in a mixing step in FNP and is encapsulated in a NP.
The use of ion pairing agents with log P values greater than 5 can be useful in making encapsulated actives with release profiles that include a plateau in release rates (release over time).
In an embodiment, the counterions that cause precipitation can have log P values of 2 or greater at pH=7. In an embodiment, the counterions can have 1, 2, or more ionic sites. In an embodiment, anionic counterions can have pKa values of −2 to 5. In an embodiment, the counterions can have pKb values above 3, or may be quaternized cationic species that are permanently cationic. In an embodiment, the ionic sites may be carboxylic acids, sulfates, sulfonates, sulfates, or amines.
Oleic and palmitic acids can be useful ion-pairing agents or counterions for an embodiment of the invention.
The ion paired hydrophilic active may be co-encapsulated along with a hydrophobic compound, such as a therapeutic, imaging agent, or agrochemical.
The successful formulation of therapeutics such as tobramycin and polymyxin B into NPs with the FNP process can expand their applicability. These APIs, which are used to manage P. aeruginosa bacterial pulmonary cystic fibrosis infections, adhere to pulmonary mucus and do not effectively reach sites of infections after drug administration [Davies, J. C., A.-M. Ebdon, and C. Orchard, Recent advances in the management of cystic fibrosis. Archives of Disease in Childhood, 2014. 99(11): p. 1033-1036.; Lai, S. K., et al., Rapid transport of large polymeric nanoparticles in fresh undiluted human mucus. Proceedings of the National Academy of Sciences, 2007. 104(5): p. 1482-1487.]. To mitigate this effect, APIs can be encapsulated into mucus-penetrating vehicles for delivery [Muheem, A., et al., A review on the strategies for oral delivery of proteins and peptides and their clinical perspectives. Saudi Pharmaceutical Journal, 2016. 24(4): p. 413-428.; Sohn, J. S., et al., Polymer prodrug approaches applied to paclitaxel. Polymer Chemistry, 2010. 1(6): p. 778-792.; Ensign, L. M., R. Cone, and J. Hanes, Oral drug delivery with polymeric nanoparticles: The gastrointestinal mucus barriers. Advanced Drug Delivery Reviews, 2012. 64(6): p. 557-570.; Lai, S. K., Y.-Y. Wang, and J. Hanes, Mucus-penetrating nanoparticles for drug and gene delivery to mucosal tissues. Advanced drug delivery reviews, 2009. 61(2): p. 158-171.; Khanvilkar, K., M. D. Donovan, and D. R. Flanagan, Drug transfer through mucus. Advanced Drug Delivery Reviews, 2001. 48(2-3): p. 173-193.; Cu, Y. and W. M. Saltzman, Drug delivery: Stealth particles give mucus the slip. Nature Materials, 2009. 8(1): p. 11-13.; Livraghi, A. and S. H. Randell, Cystic Fibrosis and Other Respiratory Diseases of Impaired Mucus Clearance. Toxicologic Pathology, 2007. 35(1): p. 116-129.]. However, liposomal formulations suffer from poor drug loading, as the drugs are limited to within the water interior of the construct. Poor drug loadings and the high costs of liposomal antibiotic formulation processes pose a significant barrier for widespread adoption, since antibiotic therapies are priced low relative to cancer therapies that utilize liposomal formulations. In contrast, FNP is a continuous and scalable method of forming NPs with high API mass loads (>50-90%) using kinetic controlled self-assembly [Høiby, N., Recent advances in the treatment of Pseudomonas aeruginosa infections in cystic fibrosis. BMC Medicine, 2011. 9: p. 32-32.; Davies, J. C., A.-M. Ebdon, and C. Orchard, Recent advances in the management of cystic fibrosis. Archives of Disease in Childhood, 2014. 99(11): p. 1033-1036.; Lai, S. K., et al., Rapid transport of large polymeric nanoparticles in fresh undiluted human mucus. Proceedings of the National Academy of Sciences, 2007. 104(5): p. 1482-1487.]. Hydrophobic APIs and amphiphilic block copolymers can be dissolved in a water miscible organic stream, and rapidly mixed with water within a confined impingement jet (CIJ) mixer. Hydrophobic APIs precipitate into nanoparticles, while the hydrophobic block of the polymer absorbs onto API NPs to arrest particle growth into a defined diameter and narrow size distribution. The hydrophilic component of the block copolymer provides a steric stabilizing layer and affords water dispersity. If a polyethylene glycol (PEG) hydrophilic functionalized block copolymer is used during FNP, particles can exhibit mucus-penetrating properties. [Crater, J. S. and R. L. Carrier, Barrier Properties of Gastrointestinal Mucus to Nanoparticle Transport. Macromolecular Bioscience, 2010. 10(12): p. 1473-1483.] The development of a new FNP-based process to encapsulate hydrophilic APIs, including biologics such as antibiotics, would expand the types of applications for which such hydrophilic biologics can be used.
The ion pairs (IPs) can be processed into stable NCs through Flash NanoPrecipitation (FNP). The ion pairing technique is quite general, but as examples, we show gentamicin (Log P=−4.21) and polymyxin B (Log P=−5.6). These cationic APIs, which are used to manage P. aeruginosa bacterial pulmonary cystic fibrosis infections, adhere to pulmonary mucus and do not effectively reach sites of infections after drug administration [Langer, R., Drug delivery and targeting. Nature, 1998. 392(6679): p. 5-10.; Zhang, L., et al., Development of Nanoparticles for Antimicrobial Drug Delivery. Current Medicinal Chemistry, 2010. 17(6): p. 585-594.]. Encapsulation, especially in a muco-diffusive PEG NC would increase efficacy.
Sodium hexanoate, sodium decanoate, sodium myristate, sodium oleate (OA), pamoic acid disodium salt (PA), benzenesulfonic acid monohydrate, sodium 2-naphthalenesulfonate, (1R)-(−)-10-camphorsulfonic acid, sodium 1,2-ethanesulfonate, sodium 1-heptanesulfonate, sodium 1-octanesulfonate monohydrate, sodium 1-decanesulfonate, sodium dodecyl sulfate (SDS), sodium dodecylbenzenesulfonate (DBS), and sodium deoxycholate were obtained from Sigma-Aldrich (St. Louis, Mo., USA) and used as ion pairing reagents. Gentamicin sulfate (MP Biochemicals, Santa Ana, Calif., USA) and polymyxin B sulfate (Calbiochem, San Diego, Calif., USA) were used as hydrophilic and cationic antibiotic APIs for encapsulation. The block copolymers 1.6 kDa polystyrene-block-5 kDa polyethylene glycol (abbreviated herein as PS-PEG, PS-b-PEG, or PS1.6k-b-PEG5k) and 5 kDa polycaprolactone-block-5 kDa polyethylene glycol (abbreviated herein as PCL-PEG, PCL-b-PEG, or PCL5k-b-PEG5k) were obtained from Polymersource (Montreal, Quebec, Canada) and used as NC formation, encapsulation, and stabilizing agents. Bicinchoninic acid (BCA) assay reagents were obtained from Thermo Scientific (Waltham, Mass., USA) and used to quantify protein concentrations. Corning 96 well, clear, circular flat bottom, half area microplates were used for the BCA assays. Amicon 50 kDa centrifugal ultrafilters (EMD Millipore, Billerica, Mass., USA) were used to separate encapsulated drug from unencapsulated drugs.
The fifteen ion pairing (IP) reagents listed above were screened to assess if hydrophobic API salt forms would be formed and would precipitate from solution. Ion pair and API drug properties were calculated with Molinspiration software (Molinspiration Cheminformatics, Slovakia). APIs were dissolved in water at 5 mg mL−1 concentration and mixed with IPs dissolved in water at varying concentrations to yield different API to IP ratios. Ratios are defined based on positive charges of APIs with negative charges on the IP, and exact compositions given in Table 1. The screening process determines whether a particular IP may be used with a given API for NC formation.
The IP process may be performed either prior to or during Flash NanoPrecipitation. In the case of the latter, referred to as “in situ ion pairing” or “pre-ion pairing”. These two ion pairing methods are described in
In the case of pre-ion pairing, API and IP are mixed in water to form a water-insoluble precipitate (referred to as an API:IP complex). The water is then removed, and the API:IP complex is dissolved into an organic solvent (along with a block copolymer) for use in the organic stream in FNP. In this case, the API:IP complex is treated as a component in the organic stream of normal FNP. The screening process for the pre-ion paired method FNP involves four sequential tests.
1. The first test examines the solubility of the IP agent. IP is added to DI water at a concentration that would be required for a 1:1 API:IP charge ratio if the API were dissolved at 5 mg mL−1. (In this text the ratios are presented as charge ratios of API:IP.) Substantial insolubility in water is required for successful ion pairing.
2. The second test examines whether an in situ API:IP complex can be formed in a single step. For example, The second test examines whether solids precipitate upon mixing of the aqueous IP solution with an aqueous API solution. Alternatively, IP in an organic, but water miscible, solution is mixed against the aqueous API solution. The final solution is checked visually to see if precipitation has occurred. In this test, the IP solution is at a concentration such that mixing equal volumes of IP solution and API solution will form a 1:1 API to IP charge ratio. Four API:IP ratios are investigated: 200 μL API solution is mixed with 100 μL IP solution for a 1:0.5 charge ratio; 200 μL API solution is mixed with 200 IP solution for a 1:1 charge ratio; 200 μL API solution is mixed with 400 μL IP solution for a 1:2 charge ratio; and 200 μL API solution is mixed with 800 μL IP solution for a 1:4 charge ratio.
3. The third test examines whether the API:IP complex can be solubilized in the organic phase for subsequent FNP NC formation. Pellets of the precipitate formed in the second test are tested to see if they are soluble in a water-miscible organic solvent such as tetrahydrofuran (THF) or more polar solvents such as dimethyl sulfoxide (DMSO) or methanol (MeOH). For example, if precipitates were formed in the second test, the mixture can be centrifuged at 20800 rcf for 20 minutes, and the aqueous supernatant can be removed in order to recover pelleted precipitate. 200 μL of organic solvent can be added to the pellet; the solution can then be mixed to determine whether the pellet dissolves.
4. The final (fourth) test assesses if the hydrophobic APLIP complex will re-precipitates when mixed with water, e.g., upon FNP mixing with water as the antisolvent. The organic solvent containing APLIP from the third test is diluted ten-fold in water, and precipitate formation is examined. If a precipitate forms, then the construct is suitable for use in FNP.
In this route, the ion pairing complexation occurs in situ, during FNP. The hydrophilic API enters in the aqueous stream, and the stabilizing block copolymer and hydrophobic IP enter in via the water-miscible organic stream. The results of the solubility screening show three different solvent compositions for six IPs. Pamoic acid (PA), sodium dodecyl sulfate (SDS), and sodium decyl sulfate (DS) dissolve in 50% dimethylsulfoxide (DMSO)/tetrahydrofuran (THF); oleic acid (OA) and myristic acid (MA) dissolve in 50% methanol (MeOH)/THF; and sodium dodecylbenzene sulfonate (DBS) dissolves in 20% water/THF.
Nanocarrier Formation by Flash NanoPrecipitation (Ion Pairing of API:IP into PEG-Coated NPs)
Flash NanoPrecipitation was used to self-assemble PEG-coated NCs containing an encapsulated API:IP complex. For the pre-ion paired method, particles were formed by rapid micro-mixing of hydrophobic-hydrophilic block-copolymer PCL-PEG and API:IP complex dissolved in organic solvent against deionized (DI) water through a confined impingement jet (CIJ) mixer. For the in situ ion pairing method, the organic stream containing PCL-PEG and anionic IP dissolved in organic solvent were rapidly micro-mixed in the CIJ mixer against the water stream containing cationic hydrophilic API dissolved in water. For both methods, the organic and water streams were mixed in a 1:1 volume ratio and the resulting mixed streams were subsequently diluted tenfold into water. Concentrations of PCL-PEG stabilizer and hydrophilic API (gentamicin and polymyxin B) were kept constant, while IP concentrations were varied to form NCs, e.g., nanoparticles, with a range of drug (API):IP ratios. This ratio is the ratio of the molar concentration of cationic functional groups in the API, to the molar concentration of anionic functional groups in the IP. Exact compositions of the stabilizer block co-polymers, APIs, and IPs used are given in Table 1 (above).
Particle sizes and polydispersities were characterized by dynamic light scattering (Malvern Zetasizer Nano, Malvern Instruments). Sizes were determined with backscattering measurements and reported as Z-average and intensity-weighted distributions. The polydispersity index (PDI) reported herein is obtained from the Taylor series expansion of the autocorrelation function and is implemented into the Malvern Nanosizer data analysis software. A ratio of the second to the first moment is defined as the PDI, where values of 0.1 are generally obtained for monodisperse particles.
Particles were diluted tenfold into two different collection buffers, deionized (DI) water and 1× phosphate-buffered saline (PBS) for sizing measurements and NC, e.g., nanoparticle, stability assessments. PBS contains significant salt concentration, has an ionic strength of 163 mM, and mimics the ionic strength of serum. Incubation in PBS assesses the stability of the NC under conditions where ion exchange, e.g. with physiological charged species, might destabilize the NC ion-paired complex. NC stability was assessed by taking DLS measurements of the particles at 4 time points: t=0, 3 hr, 24 hr, and 72 hr. Stability measurements were conducted at room temperature.
NC drug encapsulation efficiencies were determined by separating encapsulated API from dissolved/unencapsulated drugs in the NC sample through ultrafiltration across a 50 kDa membrane (Amicon Ultra, EMD Millipore) and determining the concentration of dissolved/unencapsulated API in ultrafiltration flow-through. Encapsulation efficiency is calculated as the concentration of API within the flow-through fraction divided by the concentration of API within the unseparated NC sample, and then subtracting this ratio from 1 (Eq. 1).
Drug concentrations were determined with the bicinchoninic acid (BCA) assay (Spectramax i3x, Molecular Devices) with absorbance measurements at 562 nm, using a standard curve of the same drug (unencapsulated) as the reference. API fractional release was determined by dialyzing NC sample in 100-fold 1×PBS. Aliquots were taken from within the dialysis bag at different time points: t=0, 1 day, 2 days, 3 days, 5 days, and 7 days. The drug concentration in each aliquot was determined by the BCA assay at 562 nm. The released fraction is the API concentration at each time point divided by the initial API concentration before dialysis (Eq. 2).
For successful encapsulation through nanoprecipitation methods, API:IP complexes must rapidly precipitate when mixed with an antisolvent stream (in this case an aqueous solution). However, as shown in
We first investigated preformed API:IP complexes by the following sequence of studies: (1) determination of which ion-pairs (IPs) can be used to convert the highly water soluble APIs gentamycin and polymyxin B into water-insoluble salt forms; and (2) production of salt forms that can be dissolved in highly nonpolar solvents containing THF and yield complexes that re-precipitate from THF when mixed with excess water.
Several water-soluble counter ion salts IPs were chosen for this investigation to determine the physical properties of the counter ions required for successful complex formation (
Out of the fifteen IPs tested with gentamycin, nine IPs resulted in the formation of precipitates; six IPs did not produce an observable precipitate (Tables 1 and 3).
After successfully identifying water-insoluble API:IP complexes, it was determined whether these new salt forms could be dissolved in THF for NC processing. Pellets formed from the previous step were incubated with THF at a 1× volume equal to the starting volume of API in water. Of the eleven API:IP complexes tested, all complexes, except sodium decanoate and sodium deoxycholate, dissolved in THF. The IP sodium octanesulfonate, which has a hydrophobic eight carbon chain pendant group, was sufficient for API:IP dissolution into THF, whereas sodium decanoate, which has a hydrophobic nine carbon chain pendant group, was not. The pKa of the acid form of sodium octanesulfonate is −0.40, while that of sodium decanoate is 4.0; this effect of pKa highlights differences in the ability of these two IPs to charge interact with the APIs. Thus, although sodium decanoate is a more hydrophobic IP with a Log P of 2.01, sodium octanesulfonate with a Log P of 0.85 is a better IP agent due to its greater ability to ionically complex with APIs. As a control, APIs prepared without IP complexation were not soluble in THF, highlighting that association with hydrophobic IPs is necessary for solubility in organic solvents. These results demonstrated that IP reagents that are more hydrophobic are not necessarily better for API:IP complex formation, and IPs with lower acid form pKa can be better at forming hydrophobic salts.
In the FNP process, API:IP complexes dissolved in organic solvents must rapidly precipitate when mixed against the water antisolvent. To assess whether the nine remaining API:IP salt complexes would behave accordingly, complexes dissolved from the previous step were rapidly mixed and diluted tenfold into water.
The results of the tests are shown in
Ion pairs that are the least hydrophobic and least acidic failed the first screening test, while ion pairs with intermediate hydrophobicity and acidity failed during the first and third screening tests (
Increasing difficulty in deprotonation, represented by increased pKa, requires greater hydrophobicity for successful NC formation. The first ionization of polymyxin occurs at pH=10.23. Therefore, the ΔpKa gap between oleic acid and polymyxin is over 5 units. In a previous study of hydrophobic APIs, ΔpKa>2 values were required for stable NC formation. For the very strongly basic polymyxin B and gentamicin, that criteria ΔpKa>2 is satisfied by all of the IP counterions. These results provided general experimental insight on candidate IP selection for hydrophobic ion pairing.
Without being bound by theory, in order to gain additional insight on IP selection and complexation formation procedures, a quantitative model of complexation and precipitation for basic and acidic APIs and IPs was developed and compared with experimental results. The goal was to have rules that can predict the properties of successful IP agents, and determine concentration ratios for successful FNP NC formation. For the complexation of an ionized basic API and acidic IP:
Concentrations in square brackets are given in equivalents of anionic or cationic charge, so [API+] indicates API in the units of molarity, with the compound having a single cationic charge. At or above saturation of ion paired complex, the concentration of aqueous API:IP is equal to the aqueous saturation concentration of API:IP.
[API:IP]=[API:IP]sat (5)
Correspondingly, at or above saturation, the concentrations of aqueous API, IP, and API:IP complex are described by the equilibrium relationship of Ks and that of [API:IP]sat. While this equation is commonly reduced by combining the saturation concentrations and Ks terms to provide a solubility product, it is useful to separate these terms when assessing precipitation yields.
For strongly disassociating and fully ionized API and IP, the starting concentrations of ionized compounds would be equal to the initial concentrations of the salt forms added.
[API+]0=[API]0 (7)
[IP−]0=[IP]0 (8)
After exceeding the solubility of the API:IP complex, precipitates form. The amount of precipitate formed is denoted as V×[API:IP]sld, where V is the volume of the system and [API:IP]sld is the concentration of API:IP complex above its saturation concentration prior to precipitation. This relationship would hold, if the volume of the precipitated solid phase is much lower than that of the initial volume of reaction such that the volume of the solution phase is essentially constant. By mass balance and combining equations (7-8), the concentration of aqueous soluble ionized API and IP are as follows:
[API+]=[API+]0−[API:IP]sat−[API:IP]sld (9)
[IP−]=[IP−]0−[API:IP]sat−[API:IP]sld (10)
Substitution of (9-10) into (6), yields a general expression that relates the starting concentrations of aqueous API and IP with the moles of solid precipitated API:IP complex.
Solving for the precipitated API:IP complex, the expression for the solid precipitate is obtained.
This expression holds for concentrations above the API:IP saturation concentrations. For the complexation of the strongly basic polymyxin B and gentamicin at neutral pH ˜7, and at concentrations where precipitates had formed, these conditions are satisfied. Thus, under these assumptions and conditions, the bulk concentration of precipitated API:IP is a function of the starting concentrations of API and IP, the equilibrium constant Ks, and aqueous saturation solubility [API:IP]sat—all of which are readily determined. Whereas the Ks [API:IP]sat term is typically simplified to a Ksp solubility product, separation of these two terms provides mechanistic insight on precipitation yields. Ksp is a function of complexation strength and molecular actions between the API and IP (the charged groups between the API and IP), while the [API:IP]sat is a function of the hydrophobicity of the IP complex, e.g., a function of the complex hydrophobicity and interactions with water due to the hydrophobic tail group on the IP.
Inspection of Eq. 12 provides insight on how to design precipitation reactions for NC processing, as shown in
For a system with a specific [API:IP]sat and Ks, the fraction of initial API that precipitates increases as the initial concentrations of API and IP increase, as shown in
The four IP candidates (OA, SDS, DBS, PA) that passed the screening process were used to form NCs with the FNP process. Gentamicin and polymyxin B were precipitated with IPs and dissolved into THF as described above, and mixed with PCL-PEG dissolved in THF to yield an organic THF stream containing both polymeric stabilizer and API:IP complex. This stream was rapidly mixed against water within a confined impingement jet to precipitate API:IP complex in the presence of the amphiphilic PCL-PEG to form NCs. DLS analysis of the resultant samples demonstrated that NCs 50-200 nm with narrow polydispersity were formed (
No particles, only PCL-PEG micelles, were formed when only stabilizer and API, or when only stabilizer and IP, was used in the FNC process, with the exception of OA (Table 1). Large aggregates were formed when only API and IP was included during the FNC process, demonstrating that the inclusion of all three stabilizer, API, and IP components are simultaneously needed for NC formation. These results demonstrate that while water-soluble APIs cannot be formulated into NCs, hydrophobic API:IP complexes can be formed into NCs with the water-precipitation process.
NC formation using pre-formed API:IP complex is, therefore, demonstrated. However, there are advantages to in situ API:IP NC complex formation, since NC formation could be accomplished in a single step. This single step would simplify processing. That is, although APIs can be pre-formed into hydrophobic API:IP complexes using batch processes prior to FNP, a single continuous processing step that can result in both API complexation and NP formation can simplify production procedures and reduce production costs. To test in situ complexation and NC formation and assess if APIs can be encapsulated in a single continuous step by in situ complexation, polymyxin B dissolved in water was impinged against organic solvent containing IP and PCL-PEG in the FNP process. The IPs previously identified as capable of forming NCs using pre-formed complexes were studied using this method. Out of the IPs assessed, all converted polymyxin B into hydrophobic forms in situ during mixing to yield stable NCs with narrow size distributions (
To measure the encapsulation efficiency of polymyxin B, free un-encapsulated drug was separated from that which was encapsulated in NCs through ultrafiltration across a 100 kDa membrane, and characterized with BCA analysis. The encapsulation efficiency is based on the relative ratio of free drug compared to the total amount of drug included in the FNC system.
At a 1:1 IP to API charge ratio, polymyxin B was encapsulated with efficiency greater than 95% efficiency for all IPs tested. At excess IP, high encapsulation efficiency was retained, but at a 0.5:1 IP to API charge ratio, encapsulation efficiency dropped significantly, to ˜70% in the case of sodium oleate. These results demonstrate that decreasing the amounts of IP relative to API that is present can cause decreased encapsulation efficiencies, by increasing the relative amount of solubilized API that is not retained in the core by ion pairing.
NC stability was assessed by measuring the size distributions of the NCs when diluted into a closed volume of water or PBS, all at room temperature. Although characterization of NPs in a closed volume does not capture the sink conditions that would be present in vivo, behavior in closed systems can shed insight on NP properties. When paired with at least one charge equivalent of counterion for the four counterions tested, nanoparticle size remained mostly constant in water, despite minor ripening or swelling. When diluted tenfold into PBS, however, particles exhibited size changes over time, which are driven by ion exchange between the anionic IP and the Cl− and PO4−3 ions in PBS. The ion exchange releases the bound API, which is soluble in the external phase. In the case of pamoic acid IPs, particles shrank in size, which suggests simple dissolution of encapsulated API from the NC core (Table 4A). (Polydispersity index at the several times is shown in Table 4B.) In the case of sodium dodecylbenzenesulfonate (DBS), sodium dodecyl sulfate (SDS), and sodium oleate (OA), particles increased in size over time. These results are consistent with Ostwald ripening of particles, where complexes and API are released into solution but subsequently redeposit onto particles of larger size, resulting in particle size growth over time [Liu Y, Kathan K, Saad W, Prud'homme R K. Ostwald ripening of beta-carotene nanoparticles. Phys Rev Lett. 2007 Jan. 19; 98(3):0361021. The least hydrophobic of these IPs, sodium dodecyl sulfate (SDS), demonstrated the greatest size change rates over time, while those IPs with greater hydrophobicity and lower pKa exhibited size changes at a slower and smaller (lesser) extent. Increasing the IP ratio above 1:1 increased stability. For IP ratios above 1:4 resulted in NCs that did not change size, even in PBS, over 72 hours. This is consistent with the model, which would show that increasing IP, would drive higher complexation. These results demonstrate that while NP are stable over time in solution and for storage in deionized water, transfer into high ionic strength PBS can initiate changes in NP structure, to an extent that is dependent on the structure of the IP that is initially used.
Because encapsulation efficiency was a function of the amount of IP that was included during NP processing, we sought to also investigate how particle size stability was affected by the amount of IP included in NP processing. NPs were made with IP to API charge ratios between 0.5 to 4, using sodium dodecyl sulfate (SDS) and sodium oleate (OA) as IPs. These NPs exhibited a wide range of stability profiles when diluted into a closed volume of PBS, ranging from rapid ripening under three hours, to small size changes over days, or no size changes over days. As an important note, size changes are exhibited as a shift of mean-peak diameters, as would occur in the case of Ostwald ripening, and are not the formation of aggregates, which would occur if there were API release and precipitation/recrystallization. Aggregation would be seen as a significant increase in the polydispersity, PDI. NP stability increased as the amount of IP included in the system increased; this result is consistent with the phenomenon that by increasing the concentration of IP during NP processing, at a constant API concentration, the formation of the API:IP complex is further favored. This is especially relevant in the case of polymyxin B, as there are multiple sites for ion-pairing on the API. While outside the scope of this current proof of concept experiment, interesting future work includes determining the exact solid-state compositions of the materials formed to provide insight on the behavior of these NPs. Together, these results highlight that the ratio of IP to API during NP processing is an additional handle to tune NP properties and stability.
API Release from NCs
API release rates from NCs are a critical determinant of dosing frequency, in vivo active concentrations, and overall therapeutic effectiveness. The release rates of polymyxin B were assessed by enclosing NCs in an 8 kDa MWCO dialysis bag and diluting into a thousand-fold excess volume of PBS to simulate an “open sink” condition at room temperature. Encapsulated polymyxin within dialysis bags was measured over time, using the BCA assay, to determine the amount of API that had been released (
At a constant 1:1 IP to API charge ratio, the release rate profiles of NPs (NCs) varied depending on the identifies of the IP used. The IPs with a more hydrophobic pendant side chain, and charge group with a lower acid form pKa resulted in the formation of particles with slower release rates. NPs made with sodium decanesulfonate and sodium oleate release rapidly, with near complete dissolution within one day. This result is consistent with visual observations of the NP constructs, which were initially opalescent but which appeared clear after one day of dialysis. In the case of sodium dodecyl sulfate and sodium dodecylbenzenesulfonate, NPs remained visually opalescent over time even to up to five days of dialysis. This corresponded with slower release rates and higher concentrations of retained polymyxin B over time as determined by BCA analysis. NPs made with sodium dodecylbenzenesulfonate IP exhibited characteristic release rates as slow as three days. Notably, the NP constructs that exhibit the slowest release rates also exhibited the greatest size stability profiles in closed systems. The increased hydrophobicity and stronger interactions between the IP and API lead to decreased IP:API decomplexation rates, that both improve NP stability and prolong release.
The release profiles for SDS and OA have different characteristics. The SDS has high water solubility, the “soft” sulfate anion couples well with the polymyxin B amines. The release is tunable with an almost linear (i.e. first order release) over 3-9 days depending on the SDS-polymyxin ratio. This indicates a strong, but mobile ionic interaction between the SDS and API. At the high concentration in the NC core, the SDS hydrophobic groups contribute to the stability of the complex. The hydrophobic surfactant chain tails prevent water and counterion entry that would weaken the ion pairing. This is equivalent to “salt-bridges” in the hydrophobic cores of proteins. The salt bridges are merely ion pairs, that would rapidly ion exchange if exposed to the external aqueous phase, but when in the hydrophobic core of the protein, they substantially contribute to the stability of protein. The release process for the micellizing IP involves: (i) ion exchange to destabilize the ion pair, (ii) release of the hydrophilic API, (iii) dissolution of the micellizing IP agent, (iv) exposure of remaining IP:API to exchange.
The oleic acid release follows a different pattern. Rather than continuous release, there is initial release but then containment with no further release. Again, the NC is created by the ionic interactions between polymyxin B and the carboxylic acid head group of the oleic acid molecule. The data in
The solubility of oleic acid in water at ambient temperature is ˜0.3×10−6 g/g. The water:oleate remaining at the surface of the NC forms a liquid crystal phase. The lamellar structure of the liquid crystal phase, that is, the stacked C18 bilayers, provide a barrier for the release of the hydrophilic polymyxin B. This is similar to the barrier properties of a lipid bilayer in a liposome, which would encapsulate and prevent release of a hydrophilic, high molecular weight species.
While this permanent encapsulation with oleic acid may seem problematic, it may enable novel delivery routes. Salentinig et al. note that at physiological pH the oleic acid has a limited degree of ionization that supports multilamellar layer formation [S. Salentinig, L. Sagalowicz and O Glatter, Self-Assembled Structures and pKa Value of Oleic Acid in Systems of Biological Relevance, Langmuir, 2010, 26 (14), pp 11670-11679 DOI: 10.1021/1a101012a]. Using small-angle X-ray scattering (SAXS) they show that at pH below 6.8 the liquid crystal structure is eliminated and an unstructured fluid phase is present. This pH dependence indicates that in an endosome or locally inflamed tissue, at a lower pH the liquid crystal phase may be disrupted and the encapsulated polymyxin B may be released. This may enable targeted release into sites of inflammation or into endosomes that may afford significant advantages for some drug applications.
Together, the results for SDS and oleic acid ion pairing show that changing the phase behavior of the ion pairing agent can change the release characteristics of the soluble compound. It is possible to tune release profiles from continuous release from minutes to a week. The liquid crystal behavior of oleic acid provides a mechanism to encapsulate at high efficiency and high loading and to have release provided by pH shifts or possibly enzymatic action.
The biological activity of released polymyxin B—after complexation, exposure to organic solvents during FNP, and de-complexation—is an important consideration. Here, it should be noted that polymyxin B is a locked macrocycle and does not undergo large structural changes, so we expect biological efficacy to be maintained. Reversible hydrophobic ion-pairing (HIP) complexation may protect macromolecules such as peptides or proteins, with complex structures, from degradation and loss of function.
The release profiles depend on the IP agent. For the micellizing SDS or dodecylbenzene sulfonate IPs, release can be tuned over a 7-day period with uniform release. Without being bound by theory, for the more hydrophobic oleic acid, a process of sealing the NC surface occurs, which leads to containment of the soluble API in the core. That is, this is a mechanism of secondary containment, which may be used for triggered release.
To assess if the ratio of IP:API during NP formation affected release profiles, NPs were made using 1:0.5, 1:1, and 1:4 IP to API ratios (see
The stability with SDS is interesting, given the high solubility of SDS in solution: SDS is soluble in aqueous solution up to 8 mM prior to micellization. In a study with small molecule APIs with single ionic sites, the ion pairing was shown to be 1:1. Polymyxin B has four secondary amines and 11 amide nitrogens. Without being bound by theory, the interactions with SDS may involve non-stoichiometric association. This SDS interaction may be similar to the SDS:protein interactions which are the basis for SDS electrophoresis. The denatured protein backbone would be similar to the peptide backbone in polymyxin B. The SDS binding to proteins is cooperative and results from both ionic interactions and cooperative alkyl chain interactions among the SDS molecules associated with the backbone, as has been elucidated in the paper by Turro et al. [Turro, N. J., et al., Spectroscopic probe analysis of protein-surfactant interactions: the BSA/SDS system. Langmuir, 1995. 11(7): p. 2525-2533.]. The combination of ionic interactions and surfactant tail association can lead to intricate structures which have been demonstrated for ionic polymers and DNA by x-ray diffraction [Antonietti, M., J. Conrad, and A. Thuenemann, Polyelectrolyte-Surfactant Complexes: A New Type of Solid, Mesomorphous Material. Macromolecules, 1994. 27(21): p. 6007-6011.]. These more complex structures are not strictly stoichiometric, but are determined by geometrical arrangement. The peptide ion paired complexes discussed herein may display similar structural features.
Very hydrophobic lipids and alkyl acids and unsaturated acids are those with log P values greater than 3 at pH=7. Also, very hydrophobic cationic counterions can be used, which have the same values of Log P. Log P values can be calculated using Mol Inspiration software. With very hydrophobic counterions the release of soluble actives from the surface layer can lead to an encapsulation of interior actives. This encapsulation is demonstrated in
Mastoparan 7 (MP7) is a cationic antibiotic peptide having a molecular weight of 1422 Da with sequence INLKALAALAKALL-NH2 (conventional single-letter amino acid abbreviation used). 11 (79%) of its 14 amino acids are hydrophobic (nonpolar), and 2 (14%) of its 14 amino acids are basic. It has a +3 charge. Mastoparan 17 is a non-active derivative of MP7 that is used as a control for activity tests.
MP7 was ion paired and encapsulated using the ion pairing and Flash NanoPrecipitation approach. Its release from nanoparticles was measured, and was found to depend on the counterion used. This finding is consistent with the results from the polymyxin B experiments. Nanoparticles containing encapsulated MP7 were then tested in vivo to demonstrate that the drug retained its activity throughout the steps of ion pairing, encapsulation, and release.
MP7 was encapsulated into nanoparticles using ion pairing and Flash NanoPrecipitation. First, MP7 (5 mg/ml) was ion paired with sodium dodecyl sulfate (SDS) at a 1:1 charge ratio in water. A precipitate was observed, indicating the formation of an insoluble ion paired complex. The complex was frozen and dried by lyophilization, then resuspended in a mixture of tetrahydrofuran (THF) and dimethylsulfoxide (DMSO) as a solution, and that solution then loaded into an organic (THF) feed stream containing a polycaprolactone (5 kDa)-block-polyethylene glycol (5 kDa) (PCL5k-b-PEG5k) block copolymer. That organic feed stream was impinged against water in a confined impinging jet (CIJ) mixer. NPs ˜120 nm in diameter and with PDI<0.2 were formed through this Flash NanoPrecipitation (FNP) technique.
Encapsulation efficiency and MP7 release were measured as described above. Encapsulation efficiency was measured to be over 95%. Release from free MP7 and MP7 in NPs was measured. The characteristic release time (time for 50% release) of encapsulated MP7 from NPs was 30 hours, which was significantly longer than the 2.9 hour characteristic release time from unencapsulated MP7. Thus, encapsulation within NPs resulted in extended release. This NP formulation released all its MP7 by 7 days.
This ‘one-week release’ formulation was tested in vivo in a dermonecrotic S. aureus wound model. In brief, a wound was made on a mouse's back, then infected with S. aureus. A one-time injection of NPs with or without MP7 was injected into the wound, and lesion size was measured over time. The results shown in
Release was further extended by the addition of sodium oleate (OA) into the formulation. When sodium oleate was added in addition to SDS, complete release was slowed to two weeks. This finding is consistent with the polymyxin B result that oleate-containing ion paired formulations release more slowly than SDS-containing formulations.
MP17 is an inactive version of MP7 that will be used as a control in a repeat of the experiment above. MP17 was successfully ion paired with the same counterion (SDS) as MP7 and encapsulated into NPs. A hydrophobic dye, ETTP5, was co-encapsulated with MP17, demonstrating the compatibility of the ion pairing approach with traditional FNP. By pairing ion pairing FNP with regular FNP, co-encapsulation of hydrophilic and hydrophobic materials is possible.
Sub5 is a cationic antibiotic peptide with the sequence RRWKIVVIRWRR-NH2. It contains 12 amino acid residues and has a molecular weight of 1723 Da (Daltons, g/mol). 6 (50%) of its 12 amino acids are hydrophobic (nonpolar), and 6 (50%) of its 12 amino acids are basic. It has a +7 charge. Sub5 was ion paired and encapsulated using the ion pairing and Flash NanoPrecipitation approach. Its release from nanoparticles was measured, and was found to be different from MP7's even under the same ion pairing conditions. This demonstrated that the release of an ion paired hydrophilic active depends on (1) the counterion used, (2) the charge ratio of active to counterion, and (3) the active itself.
Sub5 was encapsulated into nanoparticles using ion pairing and Flash NanoPrecipitation. First, Sub5 (5 mg/ml) was ion paired with sodium dodecyl sulfate (SDS) at a 1:1 charge ratio in water. A precipitate was observed, indicating the formation of an insoluble ion paired complex. The complex was frozen and dried by lyophilization and then resuspended in a mixture of THF and DMSO as a solution, and that solution was then loaded into an organic (THF) feed stream containing PCL5k-b-PEG5k block copolymer. That organic feed stream was impinged against water in a confined impinging jet (CIJ) mixer. NPs ˜120 nm in diameter and with PDI<0.2 were formed through this FNP technique.
Encapsulation efficiency and Sub5 release were measured as described above. Encapsulation efficiency was measured to be over 95%. Release from free Sub5 and Sub5 in NPs was measured. The characteristic release time (time for 50% release) of Sub5 from NPs was 6.9 days, which was significantly longer than the 2.1 hour characteristic release time from unencapsulated Sub5. Thus, encapsulation within NPs resulted in extended release.
LL37 is a cationic antibiotic peptide with sequence FKRIVQRIKDFLR. It contains 13 amino acid residues and has a molecular weight of 1719 Da. 6 (46%) of its 13 amino acids are hydrophobic. It has a +4 charge. LL37 was ion paired and encapsulated using the ion pairing and Flash NanoPrecipitation approach.
LL37 was ion paired with sodium dodecyl sulfate (SDS) at a 1:1 charge ratio in water; the resulting complex was dried by lyophilization and then resuspended in a mixture of THF and DMSO. This organic solution was mixed with a THF solution containing PCL5k-b-PEG5k block copolymer to create the organic feed stream for FNP. That stream was impinged against water to form NPs ˜120 nm in diameter. Encapsulation efficiency was measured as described above to be over 95%.
Colistin (“polymyxin E”) is a cyclic peptide having a molecular weight of 1155 Da. A structural comparison of colistin with polymyxin B sulfate is shown in
Colistin was ion paired in situ with sodium oleate (OA) and encapsulated. Colistin was dissolved at 5 mg/mL in water. This stream was impinged against an organic stream of 50/50 v/v % tetrahydrofuran (THF) and methanol (MeOH). This organic solution contained PCL5k-b-PEG5k block copolymer and sodium oleate. NPs ˜100 nm in diameter were formed. Colistin release from these NPs was measured and compared to polymyxin B release. The release of colistin was similar to that of polymyxin B (see
Ecumicin is a cationic cyclic peptide having a molecular weight of 1599 Da with 1 secondary amine and 1 tertiary amine. It has a +2 charge. It is active against M. tuberculosis in vivo. Ecumicin was ion paired and encapsulated using the ion pairing and Flash NanoPrecipitation approach. Vitamin E succinate was used as the counterion (ion pair agent).
Ecumicin was encapsulated within PCL-b-PEG nanoparticles by the ion pairing Flash NanoPrecipitation approach. Ecumicin was loaded in an organic stream of 50/50 v/v % THF and MeOH along with PCL-b-PEG and vitamin E succinate (vitE succinate) and impinged against a water stream in a CU mixer. Charge ratios of 1:1 and 1:2 ecumicin:vitE succinate were tested, and both resulted in NPs ˜70 nm in diameter and with a PDI<0.2. Encapsulation efficiency was measured as described above and was over 95%.
Ecumicin:vitE succinate was also encapsulated into NPs stabilized by specialized versions of PCL-PEG. These include PCL-PEG with an alexafluor fluorescent tag conjugated onto the end of the PEG chain, and PCL-PEG with hexamannose conjugated onto the end of the PEG chain. These formulations can be used for in vitro tracking, macrophage uptake, and targeting, e.g., organ targeting, tests, in addition to other uses of controlled delivery.
Ecumicin NPs have also been flash frozen and lyophilized. Dry powders produced this way were then redispersed back to nano-size upon water addition.
OZ439 (artefenomel) is a synthetic trioxolane small molecule antimalarial having a molecular weight of 470 Da. It is promising as a single-dose oral cure for malaria. OZ439 has intermediate solubility and is not sufficiently hydrophobic to precipitate into nanoparticles. It was successfully encapsulated in NPs after being ion paired with sodium oleate. The stabilizer used was hydroxypropyl methylcellulose acetate succinate (HPMCAS). Particles formed were 150 nm and had a PDI<0.2. OZ439 is an example of a charged small molecule of intermediate solubility (log P˜4.6) that can be encapsulated by the ion pairing FNP approach. Furthermore, this experiment demonstrated that a stabilizer other than a block copolymer may be used to stabilize nanoparticles produced through the ion pairing FNP strategy.
OZ439 was encapsulated within HPMCAS nanoparticles by the ion pairing Flash NanoPrecipitation approach. OZ439 was loaded in an organic stream of 67/33 v/v % THF and MeOH along with HPMCAS and sodium oleate and impinged against a water stream in a CIJ mixer. Charge ratios of 1:1 and 1:2 OZ439:oleate were tested, and both resulted in NPs ˜150 nm in diameter and with a PDI<0.2. Encapsulation efficiency was measured to be over 95%.
Ovalbumin (OVA) is an anionic protein that was encapsulated in PCL-b-PEG NPs by the ion pairing Flash NanoPrecipitation strategy. Ovalbumin has 385 amino acid residues, its molecular weight is 43,000 Da, and its charge at physiological pH is −48. Because ovalbumin is anionic, quaternary ammonium surfactants were used as ion pairing agents. Ovalbumin encapsulation demonstrates that the ion pairing Flash NanoPrecipitation approach is not limited to peptides and small molecules, but is effective for larger proteins as well.
OVA was encapsulated in nanoparticles by the ion pairing Flash NanoPrecipitation approach. In brief, OVA was dissolved in water at 5 mg/mL. This stream was impinged against an organic stream of 50/50 v/v % THF and MeOH containing PCL5k-b-PEG5k and a quaternary ammonium surfactant. When at least one charge equivalent of surfactant was included, OVA was successfully encapsulated into stable NPs ˜150 nm in diameter and with a PDI<0.2. Nanoparticles were successfully formed with each of the following quaternary ammonium surfactants: cetyl trimethylammonium bromide, tetraoctylammonium bromide, tetrakis(decyl)ammonium bromide, tetradodecylammonium bromide, tetrahexadecylammonium bromide, didodecyldimethylammonium bromide, dimethylditetradecylammonium bromide, dimethyldioctadecylammonium bromide, and dimethyldihexadecylammonium bromide. Other cationic surfactants may be used. OVA nanoparticles are potentially useful as vaccines and for other immunology studies.
Lysozyme (LYZ) is a cationic protein that was encapsulated in PCL-b-PEG NPs by the ion pairing Flash NanoPrecipitation strategy. Lysozyme has 129 amino acid residues, its molecular weight is 14,300 Da, and its charge at physiological pH is +8. Taken together, LYZ and OVA encapsulation demonstrate that the ion pairing Flash NanoPrecipitation approach is a robust approach that may be applied to both cationic and anionic proteins. LYZ was shown to still be an active protein after it is released from NPs.
LYZ was encapsulated in nanoparticles by the in situ ion-pairing Flash NanoPrecipitation (FNP) approach. LYZ was dissolved in water at 5 mg/mL. This stream was impinged against an organic stream of 50/50 v/v % THF and MeOH containing PCL5k-b-PEG5k and a counterion such as sodium oleate.
The pre-forming approach was also used, with the counterions sodium dodecyl sulfate (SDS) and dextran sulfate (DXS). IP and LYZ were mixed in water; the resulting complex was dried by lyophilization and then resuspended in a mixture of THF and DMSO. This organic solution was mixed with a THF solution containing PCL5k-b-PEG5k block copolymer to create the organic feed stream for FNP. LYZ was successfully encapsulated into stable NPs ˜150 nm in diameter and with a PDI<0.2.
In a modified pre-forming method, IP and LYZ were mixed in water. The resulting complex was centrifuged to pelletize the insoluble complex; the supernatant was removed; the pellet was then dried by lyophilization; and the pellet was then resuspended in a mixture of THF and dimethylsulfoxide (DMSO). This organic solution was then mixed with a THF solution containing PCL5k-b-PEG5k block copolymer to create the organic feed stream for Flash NanoPrecipitation (FNP).
Results for forming lysozyme-encapsulated NPs by HIP-FNP using each of the in situ, pre-formed, and modified pre-formed methods are shown in Table 5.
LYZ encapsulation efficiency was measured to be >90%. LYZ release from NPs was measured and found to depend on counterion and charge ratio in a manner consistent with the original findings for polymyxin, above.
NPs assembled using SDS as an ion pairing agent for LYZ released 50% of LYZ by 14 days at a 1:1 charge ratio. Release was slower for higher LYZ: SDS charge ratios. NPs assembled using OA as an ion pairing agent for LYZ released 30% of LYZ by 14 days at a 1:1 charge ratio. At a 1:2 charge ratio, 20% was released by 14 days, and at a 1:4 charge ratio, 10% was released by 14 days. Thus, (1) for a given counterion, LYZ release was slower at higher charge ratios; and (2) at the same charge ratio, LYZ paired with OA released more slowly than LYZ paired with SDS.
The activity of lysozyme, measured by its ability to lyse cells, was measured after release. Following release, up to 100% of released LYZ demonstrated activity equal to LYZ that was never encapsulated.
When paired 1:1 or 1:2 with OA, and when paired 1:1 with DXS, 100% of released LYZ was bioactive. When paired 1:4 with OA, and when paired 1:2 or 1:4 with DXS, and when paired 1:1 with SDS, approximately 60% of released LYZ was bioactive. When paired 1:2 or 1:4 with SDS, little (<10%) of released LYZ was bioactive.
These results show that the ion pairing Flash NanoPrecipitation approach may be used to encapsulate proteins without causing them to denature.
Embodiments according to the present invention may be useful in the treatment of infectious diseases, such as bacterial, fungal, viral, and parasitic infections, and the delivery of nucleic acids for gene therapy, gene delivery, or gene editing. For example, the controlled delivery of active therapeutic ingredients (APIs) through nanocarriers can result in improved bioavailability, reduced toxicity, sustained activity, simplified dosing regimens, improved patient adherence, and enhanced overall efficacy. For example, embodiments according to the present invention may be useful in controlled release, targeting to tumors, tissues, organs, regions of the GI tract, endosomes, or other areas of the body or of cells. Embodiments according to the present invention may be useful in encapsulating charged hydrophilic small molecules, peptides, proteins, and nucleic acids.
The invention includes methods for transiently changing API water solubility to enable API processing with nanoprecipitation methods. Without being bound by theory, a theoretical framework for optimizing processing conditions is presented herein. The rules for ion pair selection for nanoparticle stability are based on the hydrophobicity and the pKa of the IP. There are two processing routes. As a first route, the IP:API complex can be pre-formed and isolated as a single component and then assembled into NCs via Flash NanoPrecipitation. As a second route, the IP:API complex can be formed in a precipitation where the hydrophobic IP agent, the stabilizing polymer, and the hydrophilic API can be assembled into the final NC during a single precipitation step. The former (first) route has the advantage of knowing the stoichiometry of the IP:API a priori; the latter (second) route has the advantage of being a simple, single precipitation.
Hydrophilic APIs using Flash NanoPrecipitation can be encapsulated via hydrophobic ion pairing. For example, the following APIs can be encapsulated: antimicrobial small molecules OZ439, cinnarizine, clozapine, α-lipoic acid; peptides polymyxin B, colistin, mastoparan 7, mastoparan 17, sub5, LL37, ecumicin, streptomycin; proteins ovalbumin and lysozyme; aminoglycoside gentamycin; and nucleic acids such as linear salmon testes DNA or coiled plasmid DNA.
Nanoprecipitation-based methods can formulate active pharmaceutical ingredients (APIs) in a scalable and continuous manner with high API loading.
The ion pairing approach presented herein provides a powerful new tool for the encapsulation of API's.
The embodiments illustrated and discussed in this specification are intended only to teach those skilled in the art the best way known to the inventors to make and use the invention. Nothing in this specification should be considered as limiting the scope of the present invention. All examples presented are representative and non-limiting. The above-described embodiments of the invention may be modified or varied, without departing from the invention, as appreciated by those skilled in the art in light of the above teachings. It is therefore to be understood that, within the scope of the claims and their equivalents, the invention may be practiced otherwise than as specifically described.
This International Application claims the benefit of the filing date of U.S. Provisional Application 62/581,394, filed Nov. 3, 2017, which is incorporated by reference in its entirety herein.
This invention was made with government support under Grant No. GM-066134 awarded by the National Institutes of Health and Grant No. CNS-0612345 awarded by the National Science Foundation. The government has certain rights in the invention.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US2018/058869 | 11/2/2018 | WO | 00 |
| Number | Date | Country | |
|---|---|---|---|
| 62581394 | Nov 2017 | US |
