US20140005379A1 - Nanoparticle delivery system and components thereof - Google Patents

Nanoparticle delivery system and components thereof Download PDF

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Publication number
US20140005379A1
US20140005379A1 US13/923,274 US201313923274A US2014005379A1 US 20140005379 A1 US20140005379 A1 US 20140005379A1 US 201313923274 A US201313923274 A US 201313923274A US 2014005379 A1 US2014005379 A1 US 2014005379A1
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nanoparticle
nps
pla
dextran
dex
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Frank GU
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University of Waterloo
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Frank GU
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Priority to US13/923,274 priority Critical patent/US20140005379A1/en
Publication of US20140005379A1 publication Critical patent/US20140005379A1/en
Assigned to UNIVERSITY OF WATERLOO reassignment UNIVERSITY OF WATERLOO NUNC PRO TUNC ASSIGNMENT (SEE DOCUMENT FOR DETAILS). Assignors: GU, FRANK, DR., JONES, LYNDON, DR., LIU, SHENGYAN, DR., VERMA, MOHIT, DR.
Priority to US15/142,709 priority patent/US9878000B2/en
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Definitions

  • the present disclosure relates generally to a tunable nanoparticle delivery system.
  • the present disclosure also relates to components useful in the preparation of the nanoparticles, as well as to compositions, methods, processes, commercial packages, kits and uses related thereto.
  • Controlled release polymer systems can be designed to provide a drug level in the optimum range over a longer period of time than other drug delivery methods, thus increasing the efficacy of the drug and minimizing problems with patient compliance.
  • Nanomedicine the fusion of nanotechnology and medicine—is among the most promising approaches to address challenges associated with conventional drug delivery methods.
  • drug delivery systems constructed from polymeric nanoparticles (NPs) have been the cornerstone of progress in the field of nanomedicine.
  • Various types of polymeric materials have been studied for NP drug delivery applications.
  • PLGA-PEG is the most widely used polymer for making biodegradable drug delivery systems.
  • the self-assembly of PLGA-PEG block copolymers generally yields NPs of sizes greater than 150 nm (Karnik, 2008). Although smaller particles can be synthesized, they generally suffer from low drug encapsulation and rapid drug release (Karnik, 2008).
  • the present inventors reported that typical maximum drug loading in PLGA-PEG was found to be 7.1 wt/wt % (Verma, 2012, incorporated herein by reference in its entirely).
  • Other PEG based polymers showed drug loading ranging from 4.3 to 11.2 wt/wt % (Shuai, 2004; He, 2010; Missirlis, 2006).
  • Nanoparticles have been developed as sustained release vehicles used in the administration of small molecule drugs as well as protein and peptide drugs and nucleic acids.
  • the drugs are typically encapsulated in a polymer matrix which is biodegradable and biocompatible. As the polymer is degraded and/or as the drug diffuses out of the polymer, the drug is released into the body.
  • polymers used in preparing these particles are polyesters such as poly(lactide-co-glycolide) (PLGA), polyglycolic acid, poly-beta-hydroxybutyrate, polyacrylic acid ester, etc. These particles can also protect the drug from degradation by the body. Furthermore, these particles can be administered using a wide variety of administration routes.
  • Targeting controlled release polymer systems e.g., targeted to a particular tissue or cell type or targeted to a specific diseased tissue but not normal tissue
  • It can enhance the drug effect at the target site and reduce the amount of a drug present in tissues of the body that are not targeted. Therefore, with effective drug targeting, it may be possible to reduce the amount of drug administered to treat a particular disease or condition and undesirable side effects may also be reduced.
  • mucosal delivery is generally non-invasive, thereby avoiding uncomfortable aspects of intravenous, intramuscular, or subcutaneous delivery means.
  • Application of a therapeutic agent to a mucosal tissue can also reduce the effect of first-pass metabolism and clearance by circulating immune cells.
  • the administration of therapeutic agents to mucosal sites can be problematic.
  • Topical administration is the most common delivery method employed for treating diseases and conditions affecting the eye, such as corneal diseases.
  • Common topical formulations such as eye drops or ointments, suffer from low ocular bioavailability due to rapid drainage through the naso-lacrimal duct, near constant dilution by tear turnover, and low drug permeability across the corneal epithelium.
  • topical formulations are normally administered multiple times daily in order to achieve therapeutic efficacy, resulting in a higher potential for side effects and lower patient compliance.
  • NP carriers have been shown to improve drug stability in water and also prolong drug activity by releasing encapsulated compounds in a controlled manner (Ludwig, 2005; Nagarwal 2009; Liu, 2012).
  • NPs formulated using biodegradable polymers such as poly(lactic-co-glycolic acid) (PLGA)
  • PLGA poly(lactic-co-glycolic acid)
  • Poly(ethylene glycol)-based NPs have attracted significant attention due to their ability to improve the stability of drug carrier systems in physiological environments (Bazile, 1995; Dhar, 2008; Dong, 2007; Esmaeili, 2008).
  • the surfaces of polymeric NPs have been functionalized with molecular ligands that can selectively bind to the ocular mucosa to increase precorneal drug retention (du Toit, 2011; Khutoryanskiy, 2011; Shaikh, 2011).
  • molecular ligands that can selectively bind to the ocular mucosa to increase precorneal drug retention
  • the most widely used method to achieve mucoadhesion exploits electrostatic interactions between the negatively charged sialic acid moieties of the corneal mucin and cationic polymers such as chitosan (Sogias, 2008).
  • the electrostatic interactions may be hindered by various counter ions in the tear fluid, resulting in the clearance of these NPs by tear turnover.
  • Phenylboronic acid which contains a phenyl substituent and two hydroxyl groups attached to boron, has been reported to form a complex with the diol groups of sialic acid at physiological pH (Matsumoto, 2010; Matsumoto, 2010; Matsumoto, 2009).
  • PBA Phenylboronic acid
  • Another class of molecules that can covalently bind to the mucous membrane is polymeric thiomers (Ludwig, 2005). These thiomers are capable of forming covalent disulfide linkage with cysteine-rich subdomains of the mucous membrane (Khutoryanskiy, 2010).
  • polymeric thiomers include the following conjugates: poly(acrylic acid)/cysteine (Gugg, 2004), chitosan/N-acetylcysteine (Schmitz, 2008), alginate/cysteine (Bernkop-Schnurch, 2008) chitosan/thio-glycolic acid (Sakloetsakun, 2009) and chitosan/thioethylamidine (Kafedjiiski, 2006).
  • polymers with acrylate end groups are also capable of binding to the thiol moieties of mucous membrane through Michael addition (Davidovich-Pinhas and Bianco-Peled 2010).
  • the present disclosure relates generally to a nanoparticle delivery system and components thereof.
  • a block copolymer useful in the formation of a nanoparticle delivery system for encapsulating a hydrophobic therapeutic agent having a hydrophobic portion consisting of polylactide and a hydrophilic portion consisting of dextran, the dextran having a plurality of functional groups capable of conjugation to a targeting moiety.
  • nanoparticle useful for encapsulating a hydrophobic therapeutic agent comprising a plurality of amphiphilic block copolymers, each copolymer having a hydrophobic portion consisting of polylactide and a hydrophilic portion consisting of dextran, the dextran having a plurality of functional groups capable of conjugation to a targeting moiety.
  • the present disclosure provides a nanoparticle composition useful for delivery of a payload to a mucosal site, the nanoparticle comprising a plurality of amphiphilic macromolecules, the macromolecules comprising: a hydrophobic portion; a hydrophilic portion comprising comprising multiple functional moieties; and a mucosal targeting moiety, wherein at least a portion of said functional moieties on the hydrophilic portion are conjugated to the mucosal targeting moiety.
  • the present disclosure provides a a nanoparticle composition useful for delivery of a payload to a mucosal site, the nanoparticle comprising a plurality of amphiphilic macromolecules, the macromolecules comprising: a hydrophobic portion comprising a biocompatible polymer selected from a from polylactide, a polyglycolide, poly(lactide-co-glycolide), poly( ⁇ -caprolactone), or a combination thereof; a hydrophilic portion comprising a biocompatible polymer selected from polysaccharide, polynucleotide, polypeptide, or a combination thereof, the hydrophilic portion comprising multiple functional moieties; and a mucosal targeting moiety selected from a phenylboronic acid (PBA) derivative, a thiol derivative or an acrylate derivative, wherein at least a portion of said functional moieties of the hydrophilic portion are conjugated to the mucosal targeting moiety.
  • PBA phenylboronic acid
  • a nanoparticle composition useful for delivery of a payload to a mucosal site comprising a plurality of amphiphilic macromolecules, the macromolecules each comprising: a hydrophobic biocompatible polymer selected from a from polylactide, a polyglycolide, poly(lactide-co-glycolide), poly( ⁇ -caprolactone), or a combination thereof, the hydrophobic polymer forming the core of the nanoparticle; a hydrophilic biocompatible polymer selected from polysaccharide, polynucleotide, polypeptide, or a combination thereof, having multiple functional moieties, the hydrophilic portion forming the shell of the nanoparticle; at least a portion of the functional moieties being conjugated to a mucosal targeting moiety selected from a phenylboronic acid (PBA) derivative, a thiol derivative or an acrylate derivative.
  • PBA phenylboronic acid
  • a nanoparticle composition useful for delivery of a payload to a mucosal site comprising a plurality of amphiphilic macromolecules, the macromolecules comprising: a hydrophobic portion comprising a polylactide; a hydrophilic portion having multiple functional moieties, said hydrophilic portion comprising dextran; and a mucosal targeting moiety being a phenylboronic acid (PBA) derivative, wherein at least a portion of said functional moieties of the hydrophilic portion are conjugated to the mucosal targeting moiety.
  • PBA phenylboronic acid
  • a nanoparticle composition useful for delivery of a payload to a mucosal site comprising a plurality of amphiphilic macromolecules, the macromolecules each comprising a hydrophobic polylactide polymer conjugated to a hydrophilic dextran polymer having multiple functional moieties, at least a portion of said functional moieties being conjugated to a phenylboronic acid (PBA) derivative.
  • PBA phenylboronic acid
  • a Dextran-p-PLA block copolymer wherein at least a portion of the functional groups on the Dextran are conjugated to a targeting moiety capable of forming a high affinity bond with a target at a mucosal site.
  • the nanoparticle is formed by conjugating the polylactide to the dextran to form a nanoparticle and subsequently surface-functionalizing the nanoparticle by conjugating at least a portion of the functional moieties of the dextran to the PBA derivative to achieve a desired surface density of the PBA derivative.
  • the nanoparticle is formed by conjugating the polylactide to the dextran to form a nanoparticle and subsequently reacting the functional moieties of the dextran with PBA such that substantially all of the PBA is located in the shell/on the surface of the nanoparticle.
  • the core of the nanoparticle is substantially free of targeting moiety.
  • a pharmaceutical composition comprising a nanoparticle composition as defined in herein, and a pharmaceutically acceptable carrier.
  • a mucoadhesive delivery system for delivering a payload to a mucosal surface, the delivery system comprising a nanoparticle composition as defined herein; a pharmaceutically acceptable carrier; and a payload.
  • a method of treating or preventing a disease or condition comprising administering to a subject an effective amount of a nanoparticle composition or pharmaceutical composition as described herein.
  • nanoparticle composition or pharmaceutical composition as described herein for treating a disease capable of being treating by administering a therapeutic agent to a mucosal site.
  • nanoparticle composition as described herein in the manufacture of a medicament for treating a disease capable of being treating by administering a therapeutic agent to a mucosal site.
  • nanoparticle composition or pharmaceutical composition as described herein for use in treating a disease capable of being treating by administering a therapeutic agent to a mucosal site.
  • a commercial package comprising the nanoparticle composition or pharmaceutical composition as described herein, together with instructions for use in treating a disease.
  • a method of preparing a nanoparticle composition useful for delivery of a payload to a mucosal site comprising: a) preparing an ampliphilic macromolecule comprising a hydrophilic portion and a hydrophobic portion, the hydrophilic portion comprising multiple functional moieties; b) assembling a plurality of said macromolecules under suitable conditions to form a nanoparticle having a hydrophobic core and a hydrophilic shell; and c) conjugating at least a portion of said functional moieties on the hydrophobic portion to a mucosal targeting moiety to provide a surface-functionalized nanoparticle.
  • FIGS. 1A and B present NMR spectra at various steps of block copolymer synthesis.
  • FIG. 1A Proton NMR of I. Dextran 6 kDa (D2O), II. Dextran-NH-Et-NH-Boc (D2O), III. Dextran-NH-Et-NH2 (D2O), IV. PLA 20 kDa (DMSO-d6), V. Dextran-Et-PLA, or PLA20-Dex6 (DMSO-d6).
  • FIG. 1B Carbon NMR of block copolymer I. PLA 20 kDa, II. Dextran 6 kDa, III Dex-Et-PLA (PLA20-Dex6) confirming conjugation of Dextran and PLA.
  • FIGS. 2A and B show particle size and morphology of dextran-b-PLA NPs.
  • FIG. 2A Effect of MW's of PLA and Dextran on the sizes of the NPs formed from nine different polymers using PLA with MW 10 kDa (red), 20 kDa (green) and 50 kDa (blue), and Dextran with MW 1.5 kDa, 6 kDa and 10 kDa. The black bars represent the standard deviation of the particle sizes of each block copolymer.
  • FIG. 2B TEM image of PLA20-Dex6 NPs (Scale bar is 100 nm) to demonstrate spherical shape of the nanoparticles.
  • FIGS. 3A and B are graphs of drug encapsulation in NPs.
  • FIG. 3A Doxorubicin encapsulation efficiency in Dex-b-PLA and PLGA-PEG NPs using nanoprecipitation.
  • FIG. 4 is a graph of in vitro Doxorubicin cumulative release profiles from Dex-b-PLA and PLGA-PEG NPs conducted in PBS at 37° C.
  • Solid square ( ⁇ ) are for PLA20-Dex10
  • solid circles ( ⁇ ) are for PLA20-Dex6
  • FIG. 5 is a graph of hemolytic activity of Dex-b-PLA and PLGA-PEG NPs for concentrations relevant to theoretical administered dose in blood.
  • VBS was used as a negative control and deionized water was used as positive control in sheep erythrocytes.
  • FIG. 6 is a graph illustrating pharmacokinetic profiles of Dextran-b-PLA and PLGA-PEG NPs administered at 30 mg/kg i.v. to rats.
  • the NP concentration in blood was tracked using [3H]-PLA-radiolabeled nanocrystals.
  • Solid square ( ⁇ ) are for PLA20-Dex10
  • solid circles ( ⁇ ) are for PLA20-Dex6
  • FIG. 8 is a schematic illustration of mucoadhesion using particulates onto ocular mucosa to circumvent the clearance mechanisms such as tear dilution and tear turnover. Mucoadhesive agents are present throughout the surface of the nanoparticle carriers.
  • FIG. 9 is a schematic illustration of mucoadhesion of PBA modified Dextran-b-PLA NPs onto sialic acid residues present on ocular mucosa to circumvent the clearance mechanisms such as tear dilution and tear turnover.
  • FIG. 10 is a schematic illustration of the structure of the mucoadhesive nanoparticles with variations of targeting moieties on the surface of the nanoparticles.
  • the presence of multiple sites for conjugation of targeting moiety to the surface of the nanoparticle provides a high degree of tunability for targeting.
  • FIG. 11 is a schematic illustration of one embodiment showing the surface modified the NPs with PBA using two-step approach: periodate oxidation of the Dextran, and conjugation of the aldehyde groups on the oxidated Dextran with amine groups of PBA.
  • FIG. 12A demonstrates 1 H NMR verification of the presence of PBA on the Dex-b-PLA polymer chains.
  • FIG. 12B demonstrates the spherical morphology of the Dex-b-PLA_PBA NPs.
  • FIG. 13 demonstrates 1 H NMR verification of the presence of cysteamine on the Dex-b-PLA polymer chains which would expose thiol groups on the surface of the NPs.
  • FIG. 14 demonstrates the enhanced mucoadhesion property, measured using PAS staining method, of the Dex-b-PLA NPs after surface modified with PBA.
  • FIGS. 15 and 16 demonstrate the ability of the Dex-b-PLA_PBA NPs to load up to 13.7 wt/wt % of the drug Cyclosporine A, and their ability to release them in a sustained manner for up to 5 days in in vitro experiment.
  • FIG. 17 demonstrates the ability of Dex-b-PLA NPs to encapsulate various bioactive agents. Olopatadine and Doxorubicin were encapsulated in Dex-b-PLA NPs. Dorzolamide, Brinzolamide, and Natamycin were encapsulated in the Dex-b-PLA_PBA NPs.
  • FIG. 18 demonstrates the ability of the Dex-b-PLA_PBA NPs to release Dorzolamide (used in treatment of glaucoma) in a sustained manner for up to 18 hours in in vitro experiment.
  • the NPs were able to load up to 2.8 wt/wt % Dorzolamide.
  • FIG. 19 demonstrates the ability of the Dex-b-PLA_PBA NPs to release Brinzolamide (used in treatment of glaucoma) in a sustained manner for up to 11 days in in vitro experiment.
  • the NPs were able to load up to 6.54 wt/wt % Brinzolamide.
  • FIG. 20 demonstrates the ability of the Dex-b-PLA_PBA NPs to release Natamycin (used in treatment of ocular fungal infection) in a sustained manner for up to 24 hours in in vitro experiment.
  • the NPs were able to load up to 3.88 wt/wt % Natamycin.
  • FIG. 21 is a schematic illustration of the partition of nanoparticle carriers across tear fluid lipid layer.
  • FIG. 22 demonstrates that these various types of nanoparticle carriers are capable of achieving high percentage partition across the tear fluid lipid layer.
  • FIG. 23 demonstrates the compatibility of the exemplary NP formulation showing no short-term toxicity effect on the ocular surface in rabbits.
  • NP treated and the control eyes (contralateral eyes) after one-time administration of the NP formulation were graded using 7 different categories (discomfort, conjunctival redness and swelling, lid swelling, discharge, corneal opacification, and infiltrate) by daily slit-lamp examination.
  • the grades demonstrate that there is no significant increase in terms of severity of each category in the NP treated eye compared to the control eye.
  • FIG. 24 shows the histopathology analysis of the cornea, bulbar and tarsal conjunctiva, one week after the administration of the exemplary NP formulation on rabbits.
  • the results demonstrate that the structure and morphology of the ocular tissues are well-preserved after NP formulation and no sign of inflammation was observed.
  • FIG. 25 demonstrates the compatibility of the exemplary NP formulation showing no long-term toxicity effect on the ocular surface in rabbits after weekly administration for up to 12 weeks.
  • Chronic response of the ocular surfaces between NP treated and the control eyes (contralateral eyes) were evaluated similarly using 7 different categories (discomfort, conjunctival redness and swelling, lid swelling, discharge, corneal opacification, and infiltrate) by slit-lamp examination.
  • the grades demonstrate that there is no significant difference in terms of severity of each category in the NP treated eye compared to the control eye throughout the duration of the study.
  • FIG. 26 compares the chronic response of the ocular surfaces between NP-drug treated and the control eyes (contralateral eyes) after weekly administration of formulation containing Cyclosporine A encapsulated NPs on rabbits.
  • the grades of 7 different categories were obtained by daily slit-lamp examination for up to 4 weeks. The grades demonstrate that there is no significant difference in terms of severity of each category in the NP treated eye compared to the control eye throughout the duration of the study.
  • the present disclosure relates to a nanoparticle delivery system.
  • the nanoparticles are formed from amphiphilic macromolecules, such as block copolymers, comprising a hydrophilic portion and a hydrophobic portion.
  • the hydrophobic portion comprises multiple functional groups capable of being conjugated to a targeting moiety, such as a mucosal targeting moiety.
  • the hydrophilic portion forms the shell of the nanoparticle providing a surface that can be functionalized by coating the nanoparticle with a desired surface density of the targeting moiety.
  • the size of the nanoparticles and the surface density of the targeting moieties can be tuned without substantially compromising the stability of the particles.
  • the nanoparticles are useful for delivering a wide variety of payloads to a mucosal site in a subject and are capable of providing sustained release of the payload.
  • the nanoparticles demonstrate good loading capacity and loading efficiency.
  • the present disclosure also relates to components useful in the preparation of the mucoadhesive nanoparticles, as well as compositions, methods, processes, commercial packages, kits and uses related thereto.
  • the nanoparticles of the present disclosure are generally formed by the association or assembly of amphiphilic macromolecules.
  • the macromolecules are composed of at least a hydrophobic portion and at least one hydrophilic portion.
  • the macromolecule may comprise a hydrophobic polymer conjugated to a hydrophilic polymer.
  • Such macromolecules are capable of self-assembly to form nanoparticles according to methods well known to those skilled in the art, including nanoprecipitation methods.
  • a “polymer,” as used herein, refers to a molecular structure comprising one or more repeat units (e.g. monomers), connected by covalent bonds.
  • the repeat units may be identical, or in some cases, there may be more than one type of repeat unit present within the polymer.
  • Polymers may be obtained from natural sources or they may be chemically synthesized.
  • the polymer is a biopolymer, such as a polysaccharide, polypeptide or polynucleotide.
  • Biopolymers may comprise naturally-occurring monomers or derivatives or analogs thereof, for example, derivatives or analogs comprising modified sugars, nucleotides or amino acids. Several such modifications are known to those skilled in the art.
  • the polymer is a synthetic polymer, such as polylactide (PLA), polyglycolide (PGA), or poly(lactide-co-glycolide) (PLGA) or poly( ⁇ -caprolactone) (PCL).
  • PLA polylactide
  • PGA polyglycolide
  • PCL poly( ⁇ -caprolactone)
  • a copolymer comprises two or more distinct blocks or regions, e.g. at least a first block comprising a first polymer and a second block comprising a second polymer. It should be understood that, in this context, the terms “first” and “second” do not describe a particular order or number of elements but are merely descriptive.
  • a block copolymer may have two (a “diblock copolymer”), three (a “triblock copolymer”), or more distinct blocks.
  • Block copolymers may be chemically synthesized or may be polymeric conjugates.
  • a “polymeric conjugate” describes two or more polymers that have been associated with each other, usually by covalent bonding of two or more polymers together.
  • a polymeric conjugate may comprise a first polymer and a second polymer, which have been conjugated together to form a block copolymer where the first polymer is a first block of the block copolymer and the second polymer is a second block of the block copolymer.
  • a block copolymer may, in some cases, contain multiple blocks of polymer.
  • a block copolymer may comprise a first block comprising a first polymer, a second block comprising a second polymer, and a third block comprising a third polymer or the first polymer, etc.
  • block copolymers can also be formed, in some instances, from other block copolymers.
  • a first block copolymer may be conjugated to another polymer to form a new block copolymer containing multiple types of blocks.
  • the polymers may be conjugated by any means known in the art and may optionally be connected by an appropriate linker moiety.
  • An amphiphilic block copolymer generally has a hydrophobic portion and a hydrophilic portion, or at least a relatively hydrophilic portion and a relatively hydrophobic portion when two portions are considered relative to each other.
  • a hydrophilic polymer is one that generally attracts water and a hydrophobic polymer is one that generally repels water.
  • a hydrophilic or a hydrophobic polymer can be identified, for example, by preparing a sample of the polymer and measuring its contact angle with water (typically, the hydrophilic polymer will have a contact angle of less than 60°, while a hydrophobic polymer will have a contact angle of greater than about 60°). In some cases, the hydrophilicity of two or more polymers may be measured relative to each other, i.e., a first polymer may be more hydrophilic than a second polymer.
  • the macromolecule is a copolymer comprising a hydrophobic portion and a hydrophilic portion.
  • the macromolecule is a diblock copolymer comprising a first hydrophilic polymer and a second hydrophobic polymer.
  • Such configurations are generally useful for forming nanoparticles for encapsulating hydrophobic agents of interest in an aqueous environment, such as under physiologic conditions, since the hydrophobic portions will shelter the hydrophobic agent in the core region of the nanoparticle and the hydrophilic portion will form the shell of the nanoparticle by orienting toward the aqueous environment.
  • the macromolecule is a Dextran-b-PLA (Dex-b-PLA) diblock copolymer, which may optionally be functionalized on the dextran portion with one or more targeting moieties, such as a mucosal targeting moiety.
  • Dextran-b-PLA Dextran-b-PLA (Dex-b-PLA) diblock copolymer
  • targeting moieties such as a mucosal targeting moiety.
  • the macromolecule is a triblock copolymer comprising a first hydrophilic polymer, a second hydrophobic polymer, and third hydrophilic polymer.
  • Such configurations are generally useful for forming nanoparticles for encapsulating hydrophilic agents of interest in an aqueous environment, such as under physiologic conditions.
  • the macromolecule Since the macromolecule will be exposed to bodily tissues, it is preferable that the macromolecule comprises a biocompatible polymer, for example, the polymer does not induce a significant adverse response when administered to a living subject, for example, it can be administered without causing significant inflammation, irritation and/or acute rejection by the immune system.
  • the biocompatible polymer is biodegradable, for example, the polymer is able to degrade, chemically and/or biologically, within a physiological environment, such as when exposed to a body tissue.
  • the polymer may be one that hydrolyzes spontaneously upon exposure to water (e.g., within a subject), the polymer may degrade upon exposure to heat (e.g., at temperatures of about 37° C.). Degradation of a polymer may occur at varying rates, depending on the polymer or copolymer used.
  • the half-life of the polymer (the time at which 50% of the polymer is degraded into monomers and/or other nonpolymeric moieties) may be on the order of hours, days, weeks, months, or years, depending on the polymer.
  • the polymers may be biologically degraded, e.g., by enzymatic activity or cellular machinery, in some cases, for example, through exposure to a lysozyme (e.g., having relatively low pH).
  • the polymers may be broken down into monomers and/or other nonpolymeric moieties that cells can either reuse or dispose of without significant toxic effect on the cells (for example, polylactide may be hydrolyzed to form lactic acid, polyglycolide may be hydrolyzed to form glycolic acid, etc.).
  • biodegradable polymers include, but are not limited to, polysaccharides, polynucleotides, polypeptides, poly(lactide) (or poly(lactic acid)), poly(glycolide) (or poly(glycolic acid)), poly(orthoesters), poly(caprolactones), polylysine, poly(ethylene imine), poly(acrylic acid), poly(urethanes), poly(anhydrides), poly(esters), poly(trimethylene carbonate), poly(ethyleneimine), poly(acrylic acid), poly(urethane), poly(beta amino esters) or the like, and copolymers or derivatives of these and/or other polymers, for example, poly(lactide-co-glycolide) (PLGA).
  • PLA poly(lactide-co-glycolide)
  • copolymers may contain poly(ester-ether)s, e.g., polymers having repeat units joined by ester bonds (e.g., R—C(O)—O—R′ bonds) and ether bonds (e.g., R—O—R′ bonds).
  • the nanoparticle may further include a polymer able to reduce immunogenicity, for example, a poly(alkylene glycol) such as poly(ethylene glycol) (“PEG”).
  • PEG poly(ethylene glycol)
  • the amount of PEG in the nanoparticle should be limited however, so as not to substantiality compromise the tunability of the nanoparticles, which is enhanced by selection of a polymer with a backbone having multiple functional groups per monomer unit, such as a polysaccharide, as compared to PEG which has only reactive functional group per polymer chain.
  • the nanoparticle composition is free of PEG.
  • the hydrophobic portion of the macromolecule generally comprises a hydrophobic polymer, for example, a hydrophobic polymer selected from polyesters, polyorthoester, polycarbonates, polyimides, polybenzimidazoles, polyurethanes, polyureas, polysulfides, polyethers, polysulfones, phenolic and amino plastics, chitin and lipopolysaccharides, cholesterol, proteoglycans, and combinations thereof.
  • a hydrophobic polymer selected from polyesters, polyorthoester, polycarbonates, polyimides, polybenzimidazoles, polyurethanes, polyureas, polysulfides, polyethers, polysulfones, phenolic and amino plastics, chitin and lipopolysaccharides, cholesterol, proteoglycans, and combinations thereof.
  • the hydrophobic portion will substantially form the core of the nanoparticle.
  • the hydrophobic portion of the macromolecule comprises a biocompatible polymer, for example, selected from polylactide (PLA), polyglycolide (PGA), poly(lactide-co-glycolide) (PLGA), poly( ⁇ -caprolactone) (PCL), and combinations thereof.
  • a biocompatible polymer for example, selected from polylactide (PLA), polyglycolide (PGA), poly(lactide-co-glycolide) (PLGA), poly( ⁇ -caprolactone) (PCL), and combinations thereof.
  • PLA polylactide
  • PGA polyglycolide
  • PGA poly(lactide-co-glycolide)
  • PCL poly( ⁇ -caprolactone)
  • the hydrophobic portion is a polymer comprising 2 or more repeat units.
  • the hydrophilic portion may comprise, for example, from 2 to 200,000 repeat units depending on the size of the hydrophobic portion desired.
  • the molecular weight of the hydrophobic portion is in the range of about 100 g/mol to about 2,000,000 g/mol. In some embodiments, the molecular weight of the hydrophobic portion is in the range of about 500 g/mol to about 200,000 g/mol. In some embodiments, the molecular weight of the hydrophobic portion is in the range of about 1,000 g/mol to about 100,000 g/mol.
  • the unit “g/mol” in this case refers to the weight of the hydrophobic portion per mol of the macromolecule prior to conjugation with a targeting moiety.
  • the molecular weight of the hydrophobic portion is about 0.1 kDa to about 2000 kDa. In some embodiments, the molecular weight of the hydrophobic portion is about 0.5 kDa to about 200 kDa. In some embodiments, the molecular weight of the hydrophobic portion is about 1 kDa to 100 kDa. These values represent ranges prior to conjugation with a targeting moiety.
  • the hydrophilic portion of the macromolecule generally comprises a polymer having multiple reactive functional groups capable of being coupled to a targeting moiety.
  • the polymer may comprise a backbone made up of multiple monomer units, each monomer unit having multiple functional groups available for conjugation to a targeting moiety.
  • Each monomer unit may, for example, have 2, 3, 4 or 5 functional groups.
  • each monomer unit has 4 functional groups.
  • the functional groups may, for example, be independently selected from OH groups, thiol groups, ketone groups, amine groups, and carboxylic acid groups, among others.
  • a sugar moiety in a dextran polymer may have 40H groups available for conjugation to a targeting moiety (see Sheme 1).
  • the proportion of functional moieties conjugated to a targeting moiety can be controlled to effect targeting. In some embodiments, at least 10%, 20%, 30%, 40%, 50%, 60%, 70%, 80%, 90%, 95%, 98%, 99% or 100% of the functional moieties on the surface of the nanoparticle are conjugated to a targeting moiety.
  • hydrophilic polymers having multiple functional moieties per monomer unit allows for enhanced tunability of the nanoparticles as compared to, for example, conventional PEG-based nanoparticles having only one reactive functional group at the terminal end of each PEG chain.
  • the hydrophilic polymers of the present disclosure are more hydrophilic than a PEG polymer such that the hydrophilic portion of the macromolecule is less likely to orient toward the core of the nanoparticle during nanoparticle formation. Since the targeting moieties will typically be conjugated to the hydrophilic portion, this results in a nanoparticle wherein substantially all of the targeting moiety is on the surface of the nanoparticle) for targeting.
  • the core of the nanoparticle is substantially free of targeting moiety (i.e. substantially no targeting moiety in the core of the nanoparticle.
  • the hydrophilic portion of the macromolecule having multiple functional groups comprises a polymer selected from a polysaccharide, a polynucleotide, a polypeptide, or a combination thereof.
  • the polysaccharide, polynucleotide, or polypeptide may be based on naturally-occurring monomers, or derivatives or analogues thereof. Such derivatives and analogues are known to those skilled in the art and can be readily obtained or synthesized.
  • polysaccharides, for example, dextran are preferred since there are multiple functional groups per each monomer unit.
  • the hydrophilic portion of the macromolecule comprises a “polysaccharide”, e.g. a polymer of monosaccharide units joined together by glycosidic linkages. Any suitable polysaccharide may be used accordance with the present disclosure.
  • the polysaccharide is composed of 4- to 8-carbon ring monomers, such as 5-carbon ring monomers.
  • the monomer rings may be heterocyclic, form example, comprising one or more N, O or S atoms in the monomer ring.
  • the polysaccharide may be a “homopolysaccharide”, where all of the monosaccharides in the polysaccharide are the same type, or a “heteropolysaccharide”, where more than one type of monosaccharide is present.
  • the polysaccharide is a “homopolysaccharide”.
  • the polysaccharide is a “heteropolysaccharide”.
  • the polysaccharide is a linear polysaccharide.
  • the polysaccharide is a branched polysaccharide.
  • the polysaccharide has a reducing end that can be modified for conjugation purposes.
  • the polysaccharide is a homopolysaccharide with a reducing end.
  • the polysaccharide is composed of monomers of glucose, fructose, lactose or a combination thereof.
  • the polysaccharide is selected from dextran, chitosan, alginate, hyaluronic acid, heparin, chondroitin sulphate, pectin, pullulan, amylose, cyclodextrin, carboxymethylcellulose or a polysaccharide with thiol functional groups conjugated to the polymer backbone.
  • the polysaccharide is dextran, alginate, hyaluronic acid, chitosan, cyclodextrin, or carboxymethylcellulose. In some embodiments, the polysaccharide is dextran.
  • the hydrophilic portion comprises a polynucleotide, e.g. a polymer of nucleotides.
  • a “nucleotide” refers to a molecule comprising a sugar moiety, a phosphate group, and a base (usually nitrogenous).
  • the nucleotide comprises one or more bases connected to a sugar-phosphate backbone (a base connected only to a sugar moiety, without the phosphate group, is a “nucleoside”).
  • the sugars within the nucleotide may be, for example, ribose sugars (a “ribonucleic acid,” or “RNA”), or deoxyribose sugars (a “deoxyribonucleic acid,” or “DNA”).
  • the polymer may comprise both ribose and deoxyribose sugars.
  • bases include, but not limited to, the naturally-occurring bases (e.g., adenosine or “A,” thymidine or “T,” guanosine or “G,” cytidine or “C,” or uridine or “U”).
  • the nucleotide may be a naturally-occurring nucleotide or a derivative or analog thereof. Several derivatives and analogs are known to those skilled in the art.
  • the hydrophilic portion comprises a polypeptide, e.g. a polymer of amino acids.
  • the amino acid may be a naturally-occurring amino acid or a derivative or analog thereof.
  • at least a portion (e.g. greater than 50%, 60%, 70%, 80%, 90%, 95%, 98%, 99%, 100%) of the nucleotides in the polynucleotide have side chains with reactive functional groups capable of being conjugated to the targeting moiety.
  • the hydrophilic portion is a polymer comprising 2 or more repeat units.
  • the hydrophilic portion may comprise, for example, 2 to 100,000 repeat units depending on desired size of the nanoparticle.
  • the molecular weight of the hydrophilic portion ranges from about 100 g/mol to about 1,000,000 g/mol. In some embodiments, the molecular weight of the hydrophilic portion ranges from about 500 g/mol to 100,000 g/mol. In some embodiments, the molecular weight of the hydrophilic portion ranges from about 1,000 g/mol to about 50,000 g/mol.
  • the unit “g/mol” in this case refers to the weight of the hydrophilic portion per mol of the macromolecule prior to conjugation with a targeting moiety.
  • the molecular weight of the hydrophilic portion ranges from about 0.1 kDa to about 1,000 kDa. In some embodiments, the molecular weight of the hydrophilic portion ranges from about 0.5 kDa to 100 kDa. In some embodiments, the molecular weight of the hydrophilic portion ranges from about 1 kDa to 50 kDa. These values represent ranges prior to conjugation with a targeting moiety.
  • the relative amount of hydrophobic polymer to hydrophilic polymer in the macromolecule may be any suitable ratio that provides the desired characteristics of the resulting nanoparticle.
  • the molecular weight of the hydrophobic portion is larger than the molecular weight of the hydrophilic portion. In some embodiments, the molecular weight of the hydrophilic portion is larger than the molecular weight of the hydrophobic portion.
  • the ratio of the molecular weight of the hydrophobic portion to the hydrophilic portion is a about 0.1:1 to 100:1. In some embodiments, the molecular weight ratio is about 0.5:1 to about 50:1. In some embodiments, the molecular weight ratio is about 1:1 to about 10:1. In some embodiments, the molecular weight ratio is about 1:1 to about 5:1, about 1:1 to about 4:1, about 1:1 to about 3:1, or about 1:1 to about 2:1. In some embodiments, the molecular weight ratio is about 5:1, 4:1, 3:1, 2:1, 1:1, 1:2, 1:3, 1:4 or 1:5. These values prepresent ratios before conjugation of the targeting moiety. A skilled person will be albe to determine a suitable ratio based on the particular polymers selected and the agent of interest to be encapsulated.
  • the macromolecules described herein are conjugated to a targeting moiety, such that the targeting moiety located on the surface of the nanoparticle when the nanoparticle is formed to thereby surface-functionalize nanoparticle.
  • the interaction between the targeting moiety and a target at the mucosal site directs the nanoparticle to a particular site and/or increases the retention time of the nanoparticle at a particular site compared to a nanoparticle with no targeting moiety.
  • Any suitable targeting moiety may be selected.
  • targeting moieties include, but are not limited to, small molecules, polynucleotides, polypeptides, polysaccharides, fatty acids, lipids, and antibodies.
  • the targeting moiety may be a mucosal targeting moiety.
  • a “mucosal targeting moiety” is a targeting moiety capable of binding to a target expressed at the mucosal site.
  • the nanoparticles may comprise more than one type of mucosal targeting moiety.
  • an individual macromolecule may be functionalized with two or more different targeting moieties, or the nanoparticle may be formed from two or more macromolecules, each being functionalized with a different targeting moiety.
  • binding refers to the interaction between a corresponding pair of molecules or portions thereof that exhibit mutual affinity or binding capacity, typically due to specific or non-specific binding or interaction, including, but not limited to, biochemical, physiological, electrostatic and/or chemical interactions.
  • the targeting moiety is able to selectively bind to a target expressed at the mucosal site, for example, a molecule, receptor or residue expressed at the mucosal site.
  • Selective binding refers to a targeting moiety, which may be a small molecule or a large molecule, that is able to preferentially bind to or recognize a particular target or subset of targets, to a substantially higher degree than to others.
  • the target may, for example, be a biological substrate that is preferentially expressed at the musosal site, such as mucin or a receptor or a glycoprotein or a polysaccharide or residue expressed on the surface of an epithelial cell.
  • the binding is a high affinity binding the binding, such as covalent bonding, van der Waal force or hydrogen bonding.
  • the binding is covalent binding.
  • the target may possess functional groups reactive with the targeting moiety and in a particular configuration that permits covalent binding of the targeting moiety.
  • the targeting moiety is capable of binding to carbohydrate residues that contain cis-diol groups, for example, galactose, N-acetylgalactosamine, N-acetyl-glucosamine, fucose, and sialic acids. Such carbohydrate residues may, for example, be present on mucin. In some embodiments, the carbohydrate residue is a sialic acid residue. In some embodiments, the targeting moiety is a boronic acid derivative capable of binding a cis-diol group on a sialic acid residue. In some embodiments, the targeting moiety is a phenylboronic acid (PBA) derivative.
  • PBA phenylboronic acid
  • the targeting moiety is a thiol derivative or an acrylate derivative capable of binding to thiol groups of cysteine moieties. Cysteine moieties may, for example, be present on mucin. In some embodiments, the targeting moiety is a thiol derivative, such as cysteamine. In some embodiments, the targeting molecule may be cysteamine derivative capable of forming a disulfide linkage with a cysteine moiety on the mucous membrane. In some embodiments, the targeting moiety is an acrylate derivative capable of binding to hydroxyl groups of the glycoproteins on the mucous membrane. Acrylate derivatives include, but are not limited to methacrylate, ethyl acrylate, and diacrylate. In some embodiments, the targeting moiety is an acrylate derivative selected from methacrylate, ethyl acrylate, and diacrylate.
  • the targeting moiety is a phenylboronic acid (PBA) derivative, a thol derivative or an acrylate derivative.
  • PBA phenylboronic acid
  • the targeting moiety is the hydrophobic portion of the macromolecule comprises PLA; the hydrophilic portion comprises dextran; and the targeting moiety comprises PBA.
  • the targeting moiety is the hydrophobic portion is PLA; the hydrophilic portion is dextran, and the targeting moiety is PBA.
  • the targeting moiety is a biological moiety.
  • biological moieties include a peptide, a protein, an enzyme, a nucleic acid, a fatty acid, a hormone, an antibody, a carbohydrate, a peptidoglycan, a glycopeptide, or the like.
  • the biological moiety may be relatively large, for example, for peptides, nucleic acids, or the like.
  • the biological moiety may have a molecular weight of at least about 1,000 Da, at least about 2,500 Da, at least about 3000 Da, at least about 4000 Da, or at least about 5,000 Da, etc. Relatively large targeting moieties may be useful, in some cases, for differentiating between cells.
  • targeting moieties may not have adequate specificity for certain targeting applications, such as mucosal targeting applications.
  • larger molecular weight targeting moieties can offer a much higher targeting affinity and/or specificity.
  • a targeting moiety may offer smaller dissociation constants, e.g., tighter binding.
  • the targeting moiety may be relatively small, for example, having a molecular weight of less than about 1,000 Da or less than about 500 Da.
  • Another aspect of the disclosure is directed to nanoparticles formed generally from the association of macromolecules, such as the macromolecules described above.
  • the nanoparticles demonstrated effective targeting and adhesion, as well as sustained release of payload at the mucosal site.
  • the macromolecules are capable of assembling to form a nanoparticle of the core-shell type, where the core of the nanoparticle is relatively hydrophobic in comparison to the shell.
  • the core of the nanoparticle may be relatively hydrophilic in comparison to the shell.
  • the shell provides a surface of the nanoparticles, which may comprise a targeting moiety at a desired surface density, such that the nanoparticles are coated with the targeting moiety.
  • the nanoparticles may have a substantially spherical shape (i.e., the particles generally appear to be spherical). Such nanoparticles may also be referred to as “nanospheres” or “nanovesicles” due to their generally spherical shape and the formation of a cavity within the nanoparticle. It will be understood that the particles, for example, upon swelling or shrinkage, may adopt a non-spherical configuration.
  • the nanoparticles formed have an average particle size of less than about 1000 nm (1 micrometer).
  • the average particle size is less than about 500 nm, less than about 300 nm, less than about 200 nm, less than about 150 nm, less than about 100 nm, less than about 75 nm, less than about 60 nm, less than about 50 nm, less than about 30 nm, less than about 10 nm, less than about 3 nm, or less than about 1 nm in some cases.
  • particles less than 150 nm are preferred, for example, such particles are better able to penetrate the tear layer of the eye compared to larger particles.
  • the average particle size is between about 0.1 nm and about 1000 nm, about 1 nm and about 500 nm, about 1 nm and about 300 nm, about 1 nm and about 200 nm, about 1 nm and about 150 nm, about 1 nm and about 100 nm, about 1 nm and about 50 nm, about 10 nm and about 150 nm, about 10 nm and about 100 nm, about 10 nm and about 75 nm, about 10 nm and about 60 nm, and about 10 nm and about 50 nm, or about 20 and about 40 nm.
  • particle size refers to the average characteristic dimension of a population of nanoparticles formed, where the characteristic dimension of a particle is the diameter of a perfect sphere having the same volume as the particle.
  • a population of nanoparticles may, for example, include at least 20 particles, at least 50 particles, at least 100 particles, at least 300 particles, at least 1,000 particles, at least 3,000 particles, at least 5,000 particles, at least 10,000 particles, or at least 50,000 particles.
  • Various embodiments of the present invention are directed to such populations of particles.
  • the particles may each be substantially the same shape and/or size, in which case the population is “monodisperse”.
  • the particles may have a distribution of particle sizes such that no more than about 5% or about 10% of the particles have a particle size greater than about 10% greater than the average particle size of the particles, and in some cases, such that no more than about 8%, about 5%, about 3%, about 1%, about 0.3%, about 0.1%, about 0.03%, or about 0.01% have a particle size greater than about 10% greater than the average particle size of the particles.
  • no more than about 5% of the particles have a particle size greater than about 5%, about 3%, about 1%, about 0.3%, about 0.1%, about 0.03%, or about 0.01% greater than the average particle size of the particles.
  • the particles have an interior core and an exterior shell which forms the surface of the nanoparticle, where the shell has a composition different from the core i.e., there may be at least one polymer or moiety present in shell but not in the core (or vice versa), and/or at least one polymer or moiety present in the core and/or the shell at differing concentrations.
  • the core of the particle is more hydrophobic than the shell of the particle.
  • a drug or other payload may be hydrophobic, and therefore readily associates with the relatively hydrophobic interior of the particle.
  • the drug or other payload may thus be contained within the interior of the particle, which may thus shelter it from the external environment surrounding the particle (or vice versa).
  • a targeting moiety present on the surface of the particle may allow the particle to become localized at a particular targeting site, for instance, a mucosal site.
  • the drug or other payload may then, in some cases, be released from the particle and allowed to interact with the particular targeting site.
  • particles may contain more than one distinguishable macromolecule, and the ratios of the two (or more) macromolecules may be independently controlled, which allows for the control of properties of the particle.
  • a first macromolecule may be a biocompatible polymeric conjugate, such as a block copolymer, comprising a targeting moiety
  • a second macromolecule may comprise a biocompatible polymer but no targeting moiety, or the second macromolecule may contain a distinguishable biocompatible polymer from the first macromolecule.
  • Control of the amounts of these macromolecules within the polymeric particle may thus be used to control various physical, biological, or chemical properties of the particle, for instance, the size of the particle (e.g., by varying the molecular weights of one or both polymers), the surface charge (e.g., by controlling the ratios of the polymers if the polymers have different charges or terminal groups), the surface hydrophilicity (e.g., if the polymers have different molecular weights and/or hydrophilicities), the surface density of the targeting moiety (e.g., by controlling the ratios of the two or more polymers), etc.
  • the size of the particle e.g., by varying the molecular weights of one or both polymers
  • the surface charge e.g., by controlling the ratios of the polymers if the polymers have different charges or terminal groups
  • the surface hydrophilicity e.g., if the polymers have different molecular weights and/or hydrophilicities
  • nanoparticles described herein are highly tunable.
  • the size of the nanoparticles can be tuned by adjusting the molecular weight and/or composition of the hydrophobic portion and/or the hydrophilic portion.
  • the particular targeting moiety selected, as well as the surface density of the targeting moiety on the surface of the nanoparticles, will also impact the particle size.
  • hydrophilic and/or hydrophobic polymer components does not always result in a larger particle size.
  • longer polymer chains may be more flexible and capable of folding to produce a more compact particle whereas a shorter polymer chain may be confined to a more linear configuration.
  • Selection of a branched verus a linear polymer can also impact particle size.
  • a skilled person will be able to select suitable polymers for a particular application.
  • the hydrophilic portion of the macromolecules will form the shell of the nanoparticles in an aqueous environment.
  • the hydrophilic portion is selected such that it has multiple functional moieties for conjugation to a targeting moiety.
  • the proportion of functional moieties conjugated to a targeting moiety can be controlled, at least in part, by the amount of targeting moiety added to the conjugation reaction.
  • the more functional moieties present on the hydrophilic portion the higher the degree of tunability of the nanoparticles.
  • the nanoparticles disclosed herein are thus more tunable than PEG-based nanoparticles having only one functional moiety per PEG chain, or other similar polymers.
  • the extent of targeting can be controlled.
  • a high surface density of the targeting moiety can be achieved with the nanoparticles disclosed herein due to the presence of multiple functional moieties on the hydrophilic portion.
  • a skilled person will be able to control the extent of targeting without substantially compromising the stability of the nanoparticle delivery system.
  • an optimal density can be determined in which maximum targeting is achieved without substantially compromising the stability of the nanoparticle.
  • a majority e.g. at least 50%, 60%, 70%, 80%, 90%, 95%, 98%, 99%, or 100%
  • a portion of the mucosal targeting moieties may be located within the core of the nanoparticle when the nanoparticle forms, depending on the components of the nanoparticle and the method utilized. For instance, where a one-step method is used, it is possible that some of the targeting moieties may orient toward the core of the particles.
  • hydrophilic polymer having multiple functional moieties along the polymer backbone renders the hydrophilic portion of the molecule more hydrophilic than other polymers, such as PEG, thus the hydrophilic portion is more likely to orient toward an aqueous environment. Since the targeting moiety is conjugated to the hydrophilic portion, typically after formation of a nanoparticle, substantially all of the targeting moieties are located on the surface of the nanoparticle as opposed to the core.
  • substantially all (e.g. at least 95%, 96%, 97% , 98% , 99%, or 100%) of the mucosal targeting moieties are located on the surface of the nanoparticle. Localizing substantially all of the targeting moieties to the surface of the nanoparticles enhances targeting efficiency.
  • the selection of a hydrophilic polymer having multiple functional moieties along the polymer backbone renders the hydrophilic portion of the molecule more hydrophilic than other polymers, such as PEG having only one functional moiety, thus the hydrophilic portion is more likely to orient toward an aqueous environment. Since the targeting moiety is conjugated to the hydrophilic portion, typically after formation of a nanoparticle, substantially all of the targeting moieties are located on the surface of the nanoparticle as opposed to the core.
  • the nanoparticles can be tuned by controlling the surface density of the targeting moieties on the nanoparticle.
  • a skilled person will be able to precisely tune the nanoparticle for a particular application without substantially compromising the stability of the nanoparticles.
  • the surface density of the targeting moiety is about 1 per nm 2 to 15 per nm 2 , about 1 per nm 2 to 10 per nm 2 , about 1 per nm 2 to 5 per nm 2 , about 1 per nm 2 to about 15 per nm 2 , about 3 per nm 2 to about 12 per nm 2 , or from about 5 per nm 2 to about 10 per nm 2 .
  • the surface density of the targeting moiety is about 1, 2, 3, 4, 5, 6, 7, 8, 8, 9, 11, 12, 13, 14 or 15 per nm 2 .
  • the nanoparticle is approximately 10 nm in size and the density of targeting moieties on the surface of the nanoparticle (i.e. surface density) ranges from about 50 to about 3,500, from about 500 to about 3500, or from about 1000 to about 3500 per nanoparticle.
  • the nanoparticle is approximately 30 nm in size and the density of targeting moieties on the surface of the nanoparticle (i.e. surface density) ranges from about 50 to about 30000, from about 1000 to about 30000, or from about 10000 to about 30000 per nanoparticle.
  • the nanoparticle is approximately 50 nm in size and the density of targeting moieties on the surface of the nanoparticle (i.e. surface density) ranges from about 50 to about 90000, from about 3000 to about 90000, or from about 30000 to about 90000 per nanoparticle.
  • the nanoparticle is approximately 100 nm in size and the density of targeting moieties on the surface of the nanoparticle (i.e. surface density) ranges from about 50 to about 350000, from about 10000 to about 350000, or from about 100000 to about 350000 per nanoparticle.
  • the nanoparticle is approximately 150 nm in size and the density of targeting moieties on the surface of the nanoparticle (i.e. surface density) ranges from about 50 to about 800000, from about 30000 to about 800000, or from about 300000 to about 800000 per nanoparticle.
  • the nanoparticle is approximately 200 nm in size and the density of targeting moieties on the surface of the nanoparticle (i.e. surface density) ranges from about 50 to about 1,500,000, from about 60000 to about 1,500,000, or from about 600000 to about 1,500,000 per nanoparticle.
  • the nanoparticle is approximately 250 nm in size and the density of targeting moieties on the surface of the nanoparticle (i.e. surface density) ranges from about 50 to about 2,500,000, from about 100,000 to about 2,500,000, or from about 1,000,000 to about 2,500,000 per nanoparticle.
  • the nanoparticle is approximately 300 nm in size and the density of targeting moieties on the surface of the nanoparticle (i.e. surface density) ranges from about 50 to about 3,500,000, from about 150,000 to about 3,500,000, or from about 1,500,000 to about 3,500,000 per nanoparticle.
  • the surface density of the targeting moiety tunable by the amount of targeting moiety added in the reaction during the functionalization step(s).
  • the density of a phenylboronic acid derivative on the nanoparticle surface is tuneable by the amount of phenylboronic acid added in the reaction to control the extent of mucoadhesion properties of the nanoparticles.
  • the density of a cysteamine derivative on the nanoparticle surface is tuneable by the amount of cysteamine derivative added in the reaction to control the extent of mucoadhesion properties of the nanoparticles.
  • the density of an acrylate derivative on the nanoparticle surface is tuneable by the amount of acrylate derivative added in the reaction to control the extent of mucoadhesion properties of the nanoparticles.
  • the optimal density of surface functional groups may be determined by those skilled in the art in order to achieve balance between the extent of mucoadhesion and the colloidal stability of the nanoparticles.
  • the nanoparticles are dispersed in aqueous medium.
  • the aqueous medium may, for example, be a physiologically compatible aqueous medium.
  • a controlled release system refers to a nanoparticle delivery system capable of delivering a payload, such as a therapeutic agent, a diagnostic agent, a prognostic, a prophylactic agent, to a body tissue, such as a mucous membrane, where the payload is released in a predesigned or controlled manner.
  • a payload such as a therapeutic agent, a diagnostic agent, a prognostic, a prophylactic agent
  • the active agent may be released in a constant manner over a predetermined period of time
  • the active agent may be released in a cyclic manner over a predetermined period of time, or an environmental condition or external event may trigger the release of the active agent.
  • the controlled release polymer system may include a polymer that is biocompatible, and in some cases, the polymer is biodegradable.
  • the nanoparticles disclosed herein are part of a controlled release delivery system. The nanoparticles disclosed herein demonstrated sustained release of payload.
  • the mucosal targeting moiety assists in retaining the nanoparticles at the mucosal site, i.e. for a longer time that the same nanoparticle without the targeting moiety, such that controlled delivery of a payload at the mucosal site can be achieved.
  • the controlled delivery may include sustained delivery.
  • in the payload is released from the nanoparticle for a sustained period of at least 24, 36, 48, 60, 72, 84, of 96 hours. In some embodiments, the payload is released from the nanoparticle for a sustained period of at least 1, 2, 3, 4, 5, 6, 7 or 8 days. In some embodiments, the payload is released is released from the nanoparticle for a sustained period of at least 1 week. In some embodiments, the payload is released is released from the nanoparticle for a sustained period of at least 1 month.
  • At least 50% of the payload is released within the first 24 hours. In other embodiments, at least 10% the payload is released within the first 6 hours.
  • the “payload” may be any agent of interest to be delivered to a mucosal site, for example, a therapeutic agent (e.g. drug), a diagnostic agent, a prophylactic agent, an imaging agent, or a combination thereof.
  • the payload is a single agent of interest.
  • the payload comprises more than one agent of interest, for example, a combination of two or more agents of interest.
  • the payload comprises 2, 3 or 4 agents of interest.
  • the payload may comprise two or more agents of interest selected from a therapeutic agent, a diagnostic agent, a prophylactic agent, an imaging agent and combinations thereof.
  • the nanoparticles described herein are useful as a mucoadhesive nanoparticle delivery system for delivering the payload to a mucosal site.
  • the payload is predominantly encapsulated within the core of the nanoparticle.
  • “predominantly” it is meant that more than 60%, 70%, 80%, 90%, 95% or 99% of the payload is encapsulated within the core of the nanoparticle. It will be understood that, depending on the composition of the nanoparticle and the payload, a portion of the payload could also be distributed within the shell of the nanoparticle and/or on the surface of the nanoparticle.
  • the payload comprises a hydrophobic agent.
  • the payload may be a hydrophobic therapeutic agent, a hydrophobic diagnostic agent, a hydrophobic prophylactic agent or a hydrophobic imaging agent.
  • the payload is a hydrophobic therapeutic agent.
  • the payload is a hydrophobic diagnostic agent.
  • the payload is a hydrophobic prophylactic agent.
  • the payload is a hydrophobic imaging agent. The encapsulation of hydrophobic compounds in the nanoparticles is due to the hydrophobic interaction between the hydrophobic agent and the hydrophobic portions of the copolymers that form the core of the nanoparticles.
  • the payload comprises a hydrophilic agent.
  • the payload may be a hydrophilic therapeutic agent, a hydrophilic diagnostic agent, a hydrophilic prophylactic agent or a hydrophilic imaging agent.
  • the payload is a hydrophilic therapeutic agent.
  • the payload is a hydrophilic diagnostic agent.
  • the payload is a hydrophilic prophylactic agent.
  • the payload is a hydrophilic imaging agent. It will be understood that the composition of the nanoparticle would be modified to encapsulate a hydrophilic payload, for example, a triblock copolymer comprising a first hydrophilic block, and second hydrophobic block and a third hydrophilic block could be used. Such modifications are well known to those skilled in the art.
  • nanoparticles described herein were found to have good loading capacity and efficiency.
  • the loading capacity of various drugs using exemplary Dex-b-PLA (optionally surface functionalized with PBA) nanoparticles is demonstrated in the Examples.
  • the nanoparticles disclosed herein have higher loading capacity than reported for conventional PEG-based polymers. Naturally, loading capacity will be affected by the composition of the nanoparticles and the choice of payload.
  • the loading capacity is in the range of about 1 to about 40% wt/wt, about 1 to about 30% wt/wt., about 1 to about 20%, 1 to about 10%, about 1% to about 8%, about 1% to about 6%, about 1% to about 5%, about 1% to about 3%, or about 1% to about 2%.
  • the loading capacity (%) is calculated here as the molecular weight of encapsulated drug over the entire weight of the nanoparticle multiplied by 100.
  • the total weight of the nanoparticle refers to the weight of the nanoparticle including the targeting moiety and the encapsulated drug.
  • the loading capacity is up to about 40%, up to about 30% wt/wt., up to about 20%, up to about 10%, up to about 8%, up to about 6%, up to about 5%, up to about 3%, up to about 2%, or up to about 1%.
  • the payload has a molecular weight of about 0.001 kDa to 100 kDa, about 0.01 kDa to 50 kDa, about 0.1 kDa to 10 kDa.
  • the payload has a diameter of about 0.01 nm to about 300 nm, about 0.01 nm to about 100 nm, about 0.01 nm to about 50 nm.
  • Non-limiting examples of potentially suitable therapeutic agents include antimicrobial agents, analgesics, antinflammatory agents, IOP lowering agents, counterirritants, coagulation modifying agents, diuretics, sympathomimetics, anorexics, antacids and other gastrointestinal agents; antiparasitics, antidepressants, antihypertensives, anticholinergics, stimulants, antihormones, central and respiratory stimulants, drug antagonists, lipid-regulating agents, uricosurics, cardiac glycosides, electrolytes, ergot and derivatives thereof, expectorants, hypnotics and sedatives, antidiabetic agents, dopaminergic agents, antiemetics, muscle relaxants, para-sympathomimetics, anticonvulsants, antihistamines, beta-blockers, purgatives, antiarrhythmics, contrast materials, radiopharmaceuticals, antiallergic agents, tranquilizers, vasodilators, antiviral agents, and antineoplastic or
  • antiinfectives such as antibiotics and antiviral agents; analgesics and analgesic combinations; anorexics; antiheimintics; antiarthritics; antiasthmatic agents; anticonvulsants; antidepressants; antidiuretic agents; antidiarrleals; antihistamines; antiinflammatory agents; antimigraine preparations; antinauseants; antineoplastics; antiparkinsonism drugs; antipruritics; antipsychotics; antipyretics, antispasmodics; anticholinergics; sympathomimetics; xanthine derivatives; cardiovascular preparations including calcium channel blockers and beta-blockers such as pindolol and antiarrhythmics; antihypertensives; diuretics; vasodilators including general coronary, peripheral and cerebral; central nervous system stimulants; cough and cold preparations, including decongestants
  • drugs include timolol, betaxolol, metipranolol, dorzolamide, brinzolamide, neptazane, acetazolamide, alphagan, xalatan, bimatoprost, travaprost, olopatadine, ketotifen, acyclovir, gancyclovir, valcyclovir, doxorubicin, mitomycin, cisplatin, daunorubicin, bleomycin, actinomycin D, neocarzinostatin, carboplatin, stratoplatin, Ara-C.
  • Capoten Monopril, Pravachol, Avapro, Plavix, Cefzil, Duricef/Ultracef, Azactam, Videx, Zerit, Maxipime, VePesid, Paraplatin, Platinol, Taxol, UFT, Buspar, Serzone, Stadol NS, Estrace, Glucophage (Bristol-Myers Squibb); Ceclor, Lorabid, Dynabac, Prozac, Darvon, Permax, Zyprexa, Humalog, Axid, Gemzar, Evista (Eli Lily); Vasotec/Vaseretic, Mevacor, Zocor, Prinivil/Prinizide, Plendil, Cozaar/Hyzaar, Pepcid, Prilosec, Primaxin, Noroxin, Recombivax HB, Varivax, Timoptic/XE, Trusopt, Proscar, Fosamax, Sinemet, Crixivan, Propecia,
  • the payload may be an anti-cancer drug such as 20-epi-1,25 dihydroxyvitamin D3,4-ipomeanol, 5-ethynyluracil, 9-dihydrotaxol, abiraterone, acivicin, aclarubicin, acodazole hydrochloride, acronine, acylfulvene, adecypenol, adozelesin, aldesleukin, all-tk antagonists, altretamine, ambamustine, ambomycin, ametantrone acetate, amidox, amifostine, aminoglutethimide, aminolevulinic acid, amrubicin, amsacrine, anagrelide, anastrozole, andrographolide, angiogenesis inhibitors, antagonist D, antagonist G, antarelix, anthramycin, anti-dorsalizing morphogenetic
  • an anti-cancer drug such as 20-epi-1
  • the therapeutic agent is an agent used for treating or preventing a disease or condition that affects the eye (e.g. an ophthalmic agent).
  • ophthalmic agents include lubricants, demulcents, antibiotics, antivirals (e.g. acyclovir, gancyclovir, valcyclovir), antiallergic agents (e.g. antihistamine, e.g.
  • olopatadine IOP lowering agents
  • counterirritants acetazolamide, alphagan, antazoline, aspirin, atropine, azelastine, bacitracin, betaxolol, bimatoprost, botanical drugs including zeaxanthine lutein, lycopene brimonodine, brinzolamide, carbachol, carteolol, ciprofloxacin, ofloxacin, cromalyn, cyclosporine (including cyclosporine pro-drugs and cyclosporine derivatives), other immunomodulators, dapiprazole, dexamethasone, diclofenac, dipivifren, dorzolamide, epinephrine, erythromycin, fluoromethalone, flurbiprofen, gentamycin, glaucoma medications (e.g.
  • prostaglandins carbonic anhydrase inhibitors, epinephrine or alpha-agonists, beta-blockers), gramicidin, homatropine, hydrocortisone, hyoscine, keterolac, ibuprofen, ketotifen, latanaprost, levobunolol, levocabastine, levofloxin, lotepprednol, medrysone, methazolamide, metipranolol, naphazoline, natamycin, nedocromil, neomycin, neptazane, neuroprotective agents, nonsteroidal anti-inflammatory agents, nepafanec, norfloxacin, ofloxacin, olopatadine, oxymetazoline, pemirolast, pheniramine, phenylephrine, pilocarpine, povidone, prednisolone, proparacaine, scopolamine
  • the therapeutic agent is an ophthalmic agent selected from cycloprorin A, timolol, betaxolol, metipranolol, dorzolamide, brinzolamide, natamycin, neptazane, acetazolamide, alphagan, xalatan, bimatoprost, travaprost, olopatadine, ketotifen, acyclovir, gancyclovir, valcyclovir.
  • the therapeutic agent is cyclosporine A, natamycin, olopatadine, brinzolamide or dorzolamine.
  • the therapeutic agent is an ophthalmic agent used to treat glaucoma, such as an agent used to reduce a sign and/or symptom of glaucoma, for example, and agent used to reduce intraocular pressure associated with ocular hypertension.
  • the therapeutic agent is a glaucoma medication, such as a prostaglandin, carbonic anhydrase inhibitor, epinephrine or alpha-agonist, or a beta-blocker.
  • the therapeutic agent is Dorzolamide, Brinzolamide, Brimonidine, timolol, or latanoprost.
  • the therapeutic agent is an ophthalmic agent used to treat allergic conjunctivitis, such as an agent used to reduce a sign and/or symptom of allergic conjunctivitis.
  • the therapeutic agent is olopatadine.
  • the therapeutic agent is an ophthalmic agent used to treat keratoconjunctivitis sicca (KCS) or “dry eye”, such as an agent used to reduce a sign and/or symptom of KCS.
  • the therapeutic agent is cyclosporine A.
  • the therapeutic agent is cyclosporine A. In one embodiment, the therapeutic agent is dorzolamide. In one embodiment, the therapeutic agent is natamycin. In one embodiment, the therapeutic agent is olopatadine.
  • the therapeutic agent is an antibiotic, for example, a fluoroquinolone, vancomycin, cephalosporin, gentamycin, erythromycin, azithromycin, a sulfa drug, bacitracin, gatifloxacin, levofloxin, moxifloxacin, or ofoxacin.
  • an antibiotic for example, a fluoroquinolone, vancomycin, cephalosporin, gentamycin, erythromycin, azithromycin, a sulfa drug, bacitracin, gatifloxacin, levofloxin, moxifloxacin, or ofoxacin.
  • the therapeutic agent is an antiviral, for example, acyclovir, gancyclovir, valcyclovir.
  • the therapeutic agent is an antiallergy agent, for example, an antihistamine. In one embodiment, the therapeutic agent is olopatadine.
  • the nanoparticle composition comprising the therapeutic agent is administered to the anterior surface of the eye.
  • the ophthalmic agent is formulated in a dosage form for administration to the eye surface, such as a drop, ointment or gel. In some embodiments, the ophthalmic agent is formulated in a dosage form for administration to the eye via a contact lens.
  • the payload is a diagnostic agent.
  • the payload may be a fluorescent molecule; a gas; a metal; a commercially available imaging agent used in positron emissions tomography (PET), computer assisted tomography (CAT), single photon emission computerized tomography, x-ray, fluoroscopy, and magnetic resonance imaging (MRI); or a contrast agents.
  • PET positron emissions tomography
  • CAT computer assisted tomography
  • MRI magnetic resonance imaging
  • suitable materials for use as contrast agents in MRI include gadolinium chelates, as well as iron, magnesium, manganese, copper, and chromium.
  • materials useful for CAT and x-ray imaging include, but are not limited to, iodine-based materials.
  • the payload may include a radionuclide, e.g., for use as a therapeutic, diagnostic, or prognostic agent.
  • a radionuclide e.g., for use as a therapeutic, diagnostic, or prognostic agent.
  • gamma-emitters, positron-emitters, and X-ray emitters are suitable for diagnostic and/or therapy, while beta emitters and alpha-emitters may also be used for therapy.
  • Suitable radionuclides for use with various embodiments of the present invention include, but are not limited to, 123 I, 125 I, 130 I, 131 I, 133 I, 135 I, 47 Sc, 72 As, 72 Sc, 90 Y, 88 Y, 97 Ru, 100 Pd, 101 mRh, 119 Sb, 128 Ba, 197 Hg, 211 At, 212 Bi, 212 Pb, 109 Pd, 111 In, 67 Ga, 68 Ga, 67 Cu, 75 Br, 77 Br, 99 mTc, 14 C, 13 N, 15 O, 32 P, 33 P, or 18 F.
  • the radionucleotide may be contained within the nanoparticle (e.g., as a separate species), and/or form part of a macromolecule or polymer that forms the nanoparticle.
  • compositions comprising a nanoparticle composition as defined herein, and a pharmaceutically acceptable carrier.
  • Pharmaceutical compositions can be prepared in a manner well known in the pharmaceutical art, and can be administered by a variety of routes of administration, depending upon whether local or systemic effect is desired and upon the area to be treated.
  • the pharmaceutical composition is administered to a desired mucosal site in a subject.
  • the pharmaceutical composition can be administered to a desired mucosal site by any suitable route of administration.
  • the route of administration is non-parenteral, such as topical.
  • topical administration may include, for example, administration to a mucous membrane via the mouth, eye, ear, nose, esophagus, stomach, small intestine, large intestine, rectum, vagina, urethra, penis, uterus, etc. It is understood that administration of a therapeutic agent to a mucosal site may provide local and/or systemic effect, for example, depending on the ability of the agent to be absorbed into the circulation via the mucous membrane.
  • compositions and formulations for topical administration generally include ointments, lotions, creams, gels, drops, suppositories, sprays, liquids and powders.
  • an oral dosage form such as a liquid, emusion, tablet, caplet or capsule may be used.
  • Conventional pharmaceutical carriers, excipients and dulients may be employed.
  • the compositions are administered in a dosage form suitable for topical or transdermal administration.
  • dosage forms suitable for topical or transdermal administration of a pharmaceutical composition as disclosed herein include ointments, pastes, creams, lotions, gels, powders, solutions, suspensions, emulsions, sprays, inhalants, or patches.
  • the composition is typically admixed under sterile conditions with a pharmaceutically acceptable carrier and any needed preservatives or buffers as may be required.
  • the composition is in a dosage form suitable for oral administration.
  • a dosage form may, for example, be useful for administration to an oral, esophageal, gastric or intestinal mucosal site.
  • the composition may or may not be swallowed depending on the target mucosal site.
  • the dosage form could be a mouth wash.
  • the oral dosage form is a liquid dosage form, such as a suspension, solution or emulsion.
  • the dosage form is a solid dosage from, such as a powder, tablet, capsule or caplet.
  • the composition is in a dosage form suitable for rectal or vaginal administration.
  • the composition for rectal or vaginal administration is in the form of a suppository.
  • the composition for rectal or vaginal administration is in the form of a liquid, such as a douche or enema.
  • the composition for rectal or vaginal administration is in the form of a cream, ointment or gel, which may optionally be applied using an applicator.
  • the composition is in a dosage form suitable for nasal or pulmonary administration.
  • the dosage form for nasal or pulmonary administration is a spray or inhalant.
  • the dosage form is a spray.
  • the dosage form in an inhalant which may be administered with an inhaler.
  • the composition is in a dosage form suitable for ocular or otic administration, i.e. administration to the eye or ear.
  • the dosage form for ocular or otic administration is a drop.
  • the composition is in a dosage form suitable for ocular administration, such as a drop, gel or ointment. Such drop, gel or ointment may, for example, be applied to the anterior surface of the eye.
  • Parenteral routes of administration includes intravenous, intraarterial, subcutaneous, intraperitoneal intramuscular or injection or infusion; or intracranial, e.g., intrathecal or intraventricular, administration.
  • Parenteral administration can be in the form of a single bolus dose, or may be, for example, by a continuous perfusion pump.
  • the nanoparticle compositions may be administered by injection (e.g., intravenous, subcutaneous or intramuscular, intraperitoneal injection), rectally, vaginally, topically (as by powders, creams, ointments, or drops), or by inhalation (as by sprays).
  • sterile injectable preparations for example, sterile injectable aqueous or oleaginous suspensions may be formulated according to the known art using suitable dispersing or wetting agents and suspending agents.
  • the sterile injectable preparation may also be a sterile injectable solution, suspension, or emulsion in a nontoxic parenterally acceptable diluent or solvent, for example, as a solution in 1,3-butanediol.
  • acceptable vehicles and solvents that may be employed are water, Ringer's solution, U.S.P., and isotonic sodium chloride solution.
  • sterile, fixed oils are conventionally employed as a solvent or suspending medium.
  • any bland fixed oil can be employed including synthetic mono- or diglycerides.
  • fatty acids such as oleic acid are used in the preparation of injectables.
  • the inventive conjugate is suspended in a carrier fluid comprising 1% (w/v) sodium carboxymethyl cellulose and 0.1% (v/v) TWEENTM 80.
  • the injectable formulations can be sterilized, for example, by filtration through a bacteria-retaining filter, or by incorporating sterilizing agents in the form of sterile solid compositions which can be dissolved or dispersed in sterile water or other sterile injectable medium prior to use.
  • Ointments, pastes, creams, and gels may contain, in addition to the nanoparticle delivery system of the present disclosure, excipients such as animal and vegetable fats, oils, waxes, paraffins, starch, tragacanth, cellulose derivatives, polyethylene glycols, silicones, bentonites, silicic acid, talc, and zinc oxide, or mixtures thereof.
  • excipients such as animal and vegetable fats, oils, waxes, paraffins, starch, tragacanth, cellulose derivatives, polyethylene glycols, silicones, bentonites, silicic acid, talc, and zinc oxide, or mixtures thereof.
  • Powders and sprays can contain, in addition to the inventive conjugates of this invention, excipients such as lactose, talc, silicic acid, aluminum hydroxide, calcium silicates, and polyamide powder, or mixtures thereof.
  • Sprays can additionally contain customary propellants such as chlorofluorohydrocarbons.
  • compositions for oral administration can be liquid or solid.
  • Liquid dosage forms suitable for oral administration of inventive compositions include pharmaceutically acceptable emulsions, microemulsions, solutions, suspensions, syrups, and elixirs.
  • the liquid dosage forms may contain inert diluents commonly used in the art such as, for example, water or other solvents, solubilizing agents and emulsifiers such as ethyl alcohol, isopropyl alcohol, ethyl carbonate, ethyl acetate, benzyl alcohol, benzyl benzoate, propylene glycol, 1,3-butylene glycol, dimethylformamide, oils (in particular, cottonseed, groundnut, corn, germ, olive, castor, and sesame oils), glycerol, tetrahydrofurfuryl alcohol, polyethylene glycols and fatty acid esters of sorbitan, and mixtures thereof.
  • inert diluents commonly used in the art
  • the oral compositions can also include adjuvants, wetting agents, emulsifying and suspending agents, sweetening, flavoring, and perfuming agents.
  • adjuvant refers to any compound which is a nonspecific modulator of the immune response.
  • the adjuvant stimulates the immune response. Any adjuvant may be used in accordance with the present invention.
  • a large number of adjuvant compounds is known in the art (Allison Dev. Biol. Stand. 92:3-11, 1998; Unkeless et al. Annu. Rev. Immunol. 6:251-281, 1998; and Phillips et al. Vaccine 10:151-158, 1992).
  • Solid dosage forms for oral administration include capsules, tablets, caplets, pills, powders, and granules.
  • the encapsulated or unencapsulated conjugate is mixed with at least one inert, pharmaceutically acceptable excipient or carrier such as sodium citrate or dicalcium phosphate and/or (a) fillers or extenders such as starches, lactose, sucrose, glucose, mannitol, and silicic acid, (b) binders such as, for example, carboxymethylcellulose, alginates, gelatin, polyvinylpyrrolidinone, sucrose, and acacia, (c) humectants such as glycerol, (d) disintegrating agents such as agar-agar, calcium carbonate, potato or tapioca starch, alginic acid, certain silicates, and sodium carbonate, (e) solution retarding agents such as paraffin, (f) absorption accelerators such as quaternary ammonium compounds, (g) wetting agents such as
  • Solid compositions of a similar type may also be employed as fillers in soft and hard-filled gelatin capsules using such excipients as lactose or milk sugar as well as high molecular weight polyethylene glycols and the like.
  • the solid dosage forms of tablets, dragees, capsules, pills, and granules can be prepared with coatings and shells such as enteric coatings and other coatings well known in the pharmaceutical formulating art.
  • the exact dosage of the nanoparticle or components thereof, such as a therapeutic agent may be determined by a physician in view of the patient to be treated. In general, dosage and administration are adjusted to provide an effective amount of the inventive conjugate to the patient being treated.
  • the “effective amount” refers to the amount necessary to elicit the desired biological response. As will be appreciated by those of ordinary skill in this art, the effective amount may vary depending on such factors as the desired biological endpoint, the drug to be delivered, the target tissue, the route of administration, etc. Additional factors which may be taken into account include the severity of the disease state; age, weight and gender of the patient being treated; diet, time and frequency of administration; drug combinations; reaction sensitivities; and tolerance/response to therapy.
  • compositions described herein may be formulated in unit dosage form for ease of administration and uniformity of dosage.
  • unit dosage form refers to a physically discrete unit appropriate for the patient to be treated. It will be understood, however, that the total daily dosage of the composition of the present invention may be decided by a physician.
  • the therapeutically effective dose can be estimated initially either in cell culture assays or in animal models, usually mice, rabbits, dogs, or pigs. The animal model is also used to achieve a desirable concentration range and route of administration. Such information can then be used to determine useful doses and routes for administration in humans.
  • Therapeutic efficacy and toxicity of conjugates can be determined by standard pharmaceutical procedures in cell cultures or experimental animals, e.g., ED50 (the dose is therapeutically effective in 50% of the population) and LD50 (the dose is lethal to 50% of the population).
  • the dose ratio of toxic to therapeutic effects is the therapeutic index, and it can be expressed as the ratio, LD50/ED50.
  • Pharmaceutical compositions which exhibit large therapeutic indices may be useful in some embodiments.
  • the data obtained from cell culture assays and animal studies can be used in formulating a range of dosage for human use.
  • compositions in kits or commercial packages, optionally with instructions for use or administration of any of the compositions described herein by any suitable technique as previously described.
  • Instructions can define a component of promotion, and typically involve written instructions on or associated with packaging of compositions of the invention. Instructions also can include any oral or electronic instructions provided in any manner.
  • kit typically defines a package including any one or a combination of the compositions of the invention and the instructions, but can also include the composition of the invention and instructions of any form that are provided in connection with the composition in a manner such that a clinical professional will clearly recognize that the instructions are to be associated with the specific composition.
  • kits described herein may also contain one or more containers, which may contain the inventive composition and other ingredients as previously described.
  • the kits also may contain instructions for mixing, diluting, and/or administrating the compositions of the invention in some cases.
  • the kits also can include other containers with one or more solvents, surfactants, preservative and/or diluents (e.g., normal saline (0.9% NaCl), or 5% dextrose) as well as containers for mixing, diluting or administering the components in a sample or to a subject in need of such treatment.
  • compositions of the kit may be provided as any suitable form, for example, as liquid solutions or as dried powders.
  • the composition may be reconstituted by the addition of a suitable diluent, which may also be provided.
  • a suitable diluent which may also be provided.
  • the liquid form may be concentrated or ready to use.
  • the diluent will depend on the components of the composition and the mode of use or administration. Suitable diluents for drug compositions are well known, for example as previously described, and are available in the literature. The diluent will depend on the conjugate and the mode of use or administration.
  • the present disclosure also encompasses, in another aspect, promotion of the administration of the nanoparticle delivery system described herein.
  • one or more compositions of the invention are promoted for the prevention or treatment of various diseases such as those described herein via administration of any one of the compositions of the present invention.
  • “promoted” includes all methods of doing business including methods of education, hospital and other clinical instruction, pharmaceutical industry activity including pharmaceutical sales, and any advertising or other promotional activity including written, oral and electronic communication of any form, associated with compositions of the invention.
  • the nanoparticle compositions disclosed herein may be useful in the treatment or prevention of any disease or condition capable of being treated via controlled delivery of a therapeutic agent to a mucosal site.
  • “treating” includes preventing, reducing or alleviating one or more signs and/or symptoms of the disease or condition.
  • the nanoparticle compositions provide controlled release of the therapeutic agent and are surface-functionalized for targeting and retention of the nanoparticles at the mucosal site such that sustained release at the mucosal site can be achieved.
  • compositions or components thereof as defined herein for treating and/or preventing a disease or condition.
  • uses of the compositions or components thereof as defined herein for the manufacture of a medicament to treating and/or preventing a disease or condition there are provided compositions or components thereof disclosed herein for the manufacture of a medicament to treating and/or preventing a disease or condition.
  • compositions or components thereof as defined herein for the treatment of a disease or condition there are provided.
  • the disease or condition to be treated is a disease or condition capable of being treated via delivery of a therapeutic agent to a mucosal site, such as a mucosal site of the mouth, eye, ear, nose, esophagus, stomach, small intestine, large intestine, rectum, vagina, urethra, penis or uterus.
  • a mucosal site such as a mucosal site of the mouth, eye, ear, nose, esophagus, stomach, small intestine, large intestine, rectum, vagina, urethra, penis or uterus.
  • the disease or condition to be treated is a disease or condition affecting the mouth, eye, ear or nose. In some embodiments, the disease or condition to be treated is a disease or condition affecting the rectum, vagina, urethra, penis, or uterus. In some embodiments, the disease or condition to be treated is a disease or condition affecting the esophagus, stomach, small intestine or large intestine.
  • the disease or condition to be treated is a disease or condition affecting the eye.
  • Non-limiting examples include abrasion, acanthamoeba keratitis, actinic keratosis, acute allergic blepharoconjunctivitis, allergic conjunctivitis, adenoviral keratoconjunctivitis, aniridia, atopic keratoconjunctivitis, bacterial conjunctivitis, bacterial keratitis, band keratopathy, basal cell carcinoma, Bell's palsy, blepharitis, bullous keratopathy, canaliculitis, caruncular cyst, cataract, chalazion, chlamydial conjunctivitis, climatic droplet keratopathy, concretions, conjunctival intraepithelial neoplasia, conjunctival lymphoma, conjunctival papilloma, conjunctival pigmented lesions,
  • the disease or condition is a disease or condition of the eye is glaucoma, keratoconjunctivitis sicca or allergic conjunctivitis, fungal infection, viral infection or bacterial infection. In some embodiments, the disease or condition of the eye is glaucoma, keratoconjunctivitis sicca or allergic conjunctivitis. In some embodiments, the disease or condition of the eye is a fungal infection, viral infection or bacterial infection.
  • Cyclosporine A is administered for the treatment of keratoconjunctivitis sicca.
  • Olopatadine is administered for the treatment of allergic conjunctivitis.
  • Brinzolamide, Brimonidine, or Dorzolamide are administered for the treatment of glaucoma.
  • the composition is administered topically on the surface of the eye for treatment of diseases associated with the anterior segments of the eye.
  • the composition is administered topically on the surface of the eye for treatment of diseases associated with the posterior segments of the eye.
  • the composition is administered intranasally to target the nasal mucosa.
  • the composition is administered orally to target the oral mucosa.
  • the composition is administered intravenously to target the gastrointestinal mucin for treatment of diseases associated with the intestine.
  • the composition is administered vaginally to target the vaginal mucosa.
  • the disease or condition to be treated is selected from one or more of acquired angioedema, acrodermatitis enteropathica, acute serous conjunctivitis, adenomatous polyposis of the colon, adenoviridae infections, adenovirus-related cold, allergic asthma, allergic contact cheilitis, allergic rhinitis, allergies, amyloidosis of gingiva and conjunctiva mental retardation, analgesic asthma syndrome, Anderson's triad, angina bullosa haemorrhagica, angular conjunctivitis, asthma, asthmatic Bronchitis, atrophic glossitis, atrophic rhinitis, attenuated familial polyposis, Behcet's disease, benign migratory glossitis, benign mucosal penphigoid, black hairy tongue, Brodie pile, bronchitis, bullous penphigoid, candidiasis, canker sores, carbon baby syndrome,
  • the subject may be a human or non-human animal.
  • the subject is a mammal.
  • mammals include human, dog, cat, horse, donkey, rabbit, cow, pig, sheep, goat, rat, mouse, guinea pig, hamster, and primate.
  • the subject is a human.
  • the present disclosure provides a process for the preparation of macromolecules useful in the formation of a mucoadhesive nanoparticle delivery system.
  • the macromolecule is typically an amphiphilic copolymer, in particular, a block copolymer, which is conjugated to a plurality of mucosal targeting moieties.
  • the macromolecules are capable of assembly under suitable conditions to form a nanoparticle, i.e. of the core-shell type.
  • the nanoparticle has a hydrophobic core and a hydrophilic shell, the shell providing a surface of the nanoparticle, the surface of the nanoparticle being coated in a desired amount (i.e. surface density) of the mucosal targeting moiety for controlled targeting and adhesion of the nanoparticle.
  • the macromolecules disclosed herein may be made by any suitable process known to those skilled in the art, for example, using suitable conjugation techniques.
  • Starting materials including hydrophobic polymer and hydrophilic polymer, may be purchased from various commercial suppliers. Where desired, the starting materials can be prepared by those of skill in the art. For example, where polymers comprising modified backbone residues are desired. Exemplary methods for making macromolecules useful in the formation of a mucoadhesive delivery system are described below.
  • the method is carried out in a series of steps, such as, preparation of an amphiphilic macromolecule, nanoparticle formation, and conjugation to a targeting moiety (i.e. coating of the surface of the nanoparticle with a desired surface density of the targeting moiety).
  • a targeting moiety i.e. coating of the surface of the nanoparticle with a desired surface density of the targeting moiety.
  • the hydrophilic portion comprising multiple functional groups may first be coupled to a desired amount of the targeting moiety, followed by conjugation of the functionalized hydrophilic portion to a hydrophobic polymer, which may be in the form of a hydrophobic nanoparticle (i.e. coating the surface of a hydrophobic nanoparticle with a functionalized hydrophilic polymer).
  • hydrophobic polymer When the hydrophobic polymer is modified for conjugation, one end of the polymer will typically become more hydrophilic (e.g. presence of a carboxyl group). Such polymers can assemble to form hydrophobic nanoparticles in aqueous medium. Preparation of the nanoparticles in a controlled sequence results in surface-functionalized nanoparticles wherein substantially all (e.g. greater than 90%, 95%, 96%, 97%, 98%, 99%) of the targeting moieties are located on the surface of the nanoparticle formed by the hydrophilic portion of the macromolecules.
  • substantially all (e.g. greater than 90%, 95%, 96%, 97%, 98%, 99%) of the targeting moieties are located on the surface of the nanoparticle formed by the hydrophilic portion of the macromolecules.
  • the method of preparing a nanoparticle composition useful for delivery of a payload to a mucosal site comprises preparing an ampliphilic macromolecule comprising a hydrophilic portion and a hydrophobic portion, the hydrophilic portion comprising multiple functional moieties; b) assembling a plurality of said macromolecules under suitable conditions to form a nanoparticle having a hydrophobic core and a hydrophilic shell; and c) conjugating at least a portion of said functional moieties on the hydrophobic portion to a mucosal targeting moiety, to thereby provide a surface-functionalized nanoparticle.
  • a) comprises conjugation of a hydrophilic polymer to a hydrophobic polymer to form a diblock copolymer.
  • the hydrophilic polymer is dextran and the hydrophobic polymer is PLA.
  • the targeting moiety is a phenylboronic acid derivative, a thiol derivative or an acrylate derivative. In some embodiments, the targeting moiety is a phenylboronic acid (PBA) derivative.
  • step b) is performed before step c). However, in other embodiments, step c) is performed before step b).
  • the surface density of the mucosal targeting moiety on the nanoparticle is controlled by the amount of mucosal targeting moiety introduced into the reaction.
  • the process comprises reductive animation between the multimer and a suitable linker.
  • the reaction takes place between the amine end of N-protected-ethylenediamine and the reducing end of a multimer having multiple functional groups per monomer unit, such as a polysaccharide, a polynucleotide or a polypeptide.
  • Any suitable N-protecting group can be used.
  • the N-protecting group is tert-butoxycarbonyl (BOC).
  • the choice of a hydrophilic polymer having multiple functional groups per monomer unit enables tuning of the resulting nanoparticle to control particle size, targeting and/or adhesion at a mucosal site, as described further below.
  • the hydrophilic polymer is a polysaccharide.
  • the hydrophilic polymer is dextran. Therefore, in some embodiments, the reaction takes place between N—BOC-ethylenediamine and an aldehyde of the reducing end of a dextran polymer.
  • the reaction may be carried out in a suitable solvent, such as a borate buffer solution, in the presence of a reducing agent, such as NaCNBH 3 .
  • the mixture is stirred for a sufficient amount of time to complete the reaction, for example, about 24 to 120 hours hours. In one embodiment the mixture is stirred for about 24, 48, 72, 96, or 120 hours. In some embodiments, this step is carried out at room temperature. In some embodiments, this step is carried out in the dark.
  • the mixture may then be washed to remove any unreacted molecules or catalysts.
  • methanol is used in the washing step.
  • the end-modified dextran can optionally be dried before continuing the process.
  • the protecting group is then removed followed by conjugation of the amine-terminated multimer to a hydrophobic polymer in a suitable solvent to provide an amphiphilic macromolecule.
  • a suitable solvent to provide an amphiphilic macromolecule.
  • hydrochloric acid and triethyl amien are used for the removal of the protecting group.
  • the macromolecule may be washed, for example, using methanol, to remove unreacted polymer.
  • the conjugation of the amine-terminated multimer with a hydrophobic polymer takes place in a suitable solvent.
  • the solvent is DMSO, acetone, or acetonitrile.
  • Catalysts may be employed to drive the reaction.
  • the catalysts are EDC and Sulfo-NHS.
  • the mixture may then be washed to remove any unreacted molecules or catalysts.
  • methanol is used in the washing step. Additional washing step may be used to remove unreacted polymer.
  • the unreacted polymer is dextran.
  • the final mixture is dissolved in a suitable solvent, centrifuged and the resulting supernatant is collected.
  • the suitable solvent is acetone or acetonitrile.
  • the final product is dried.
  • vacuum dessicator is used to dry the product.
  • the present disclosure provides a process for the preparation of nanoparticles useful in the formation of a mucoadhesive nanoparticle delivery system.
  • the polymers or macromolecules described herein may be formed into a nanoparticle using techniques known to those skilled in the art.
  • the geometry formed by the particle from the macromolecule may depend on factors such as the size and composition of the polymers that form the macromolecule.
  • the particle may include an agent of interest, such as a therapeutic, diagnostic or imaging agent.
  • the nanoparticle may contain a therapeutic agent, such as a drug.
  • the agent of interest may be incorporated into the particle during formation of the particle, e.g., by including the agent in a solution containing the polymers that are used to form the particle, and/or the agent may be incorporated in the particle after its formation.
  • first and second (or more) macromolecules may be combined together at different ratios to produce particles comprising the first and second (or more) macromolecules, keeping in mind that, in some embodiments, it is desirable to have hydrophilic portions with multiple functional groups present in the shell of the nanoparticle for tunable targeting of the nanoparticles via coupling of the functional groups to a mucosal targeting moiety, such as a targeting moiety capable of forming high affinity binding to a target at the mucosal site.
  • the targeting moieties are conjugated to the macromolecules following nanoparticle formation.
  • the present disclosure also provides a process for conjugating targeting moieties on the surface of the nanoparticles formed using the amphiphilic macromolecules described herein.
  • the conjugation is between the functional groups of the hydrophilic portion (e.g. the backbone of a hydrophilic polymer) and the functional groups of the targeting moieties.
  • catalysts for example, EDC
  • the functional groups of the polymer backbone are modified into other types of functional groups prior to the conjugation reaction.
  • NaIO 14 is used to oxidize hydroxyl groups into aldehyde groups.
  • the mixture may be washed, for example, using methanol, to remove nonconjugated targeting moieties.
  • dialysis is used to remove the unreacted molecules.
  • the method may include conjugation with more than one type of targeting moiety.
  • the surface density of targeting moiety on the resulting nanoparticles may be controlled by adjusting the amount of material in the reaction mixture.
  • conjugation and nanoparticle formation may occur as a single-step reaction, for example, according to a single-step reaction as described in U.S. Pat. No. 8,323,698.
  • a single-step reaction such as this will result in a nanoparticle having a detectable amount of targeting moieties located within the core of the nanoparticle, thereby decreasing the targeting efficiency of the particles compared to a more controlled sequence as described above.
  • Example 1 An exemplary method of preparing a Dextran-b-PLA (Dex-b-PLA) block copolymer is described below in Example 1 (Verma, 2012). Briefly, an exemplary procedure for the synthesis of Dex-b-PLA may be divided into three stages: reductive amination between Dextran and N-Boc-ethylenediamine, deprotection of the Boc group, and conjugation of the amine-modified Dextran end group with carboxyl-terminated PLA. Reductive amination may be carried out by dissolving Dex in a borate buffer and mixing it with N-Boc-ethylenediamine and NaCNBH 3 in dark condition for about 72 hrs.
  • a method of preparing a Dex-b-PLA macromolecule comprising: 1) reductive amination between Dextran and N-Boc-ethylenediamine, 2) deprotection of the Boc group, and 3) conjugation of the end modified Dextran with PLA (Scheme 1).
  • the first step of the synthesis involves reductive amination between the aldehyde on the reducing end of Dextran and the amine group of N-Boc-ethylenediamine cross-linker.
  • the reducing agent, NaCNBH 3 was added to the borate buffer solution and the mixture was stirred for 72 hours in dark conditions at room temperature. The mixture was then washed in methanol to remove any unreacted molecules or catalysts.
  • the end-modified Dextran was dried overnight in vacuo.
  • the dried Dextran was re-dissolved in de-ionized water (DI-H 2 O).
  • DI-H 2 O de-ionized water
  • the deprotection of Boc group was performed first by adding HCl for 1 hour to cleave the amide bond between the Boc group and the protected amine moiety. Subsequently, TEA was added to increase the pH of the solution up to 9 to deprotonate the NH 3 + end groups which were deprotected. The mixture was then washed twice using methanol and dried in vacuo. An NMR sample of the dried product was prepared in D 2 O ( ).
  • the amine terminated Dextran and carboxyl terminated PLA20 (Mw ⁇ 20 kDa, 6 g, 0.3 mmol) were dissolved in DMSO.
  • the conjugation between the two polymers was facilitated by adding catalysts EDC (120 mg, 0.773 mmol) and Sulfo-NHS (300 mg, 1.38 mmol) and allowing reaction to proceed for 4 hours at room temperature.
  • the resulting Dex-b-PLA was twice precipitated and purified using excess methanol.
  • the mixture was dissolved in acetone (30 mL) to form a cloudy suspension. This was centrifuged at 4000 rpm for 10 minutes and the supernatant was extracted carefully. The supernatant was purged with air to remove the solvent and then dried overnight in vacuo to obtain the final copolymers.
  • Dex-b-PLA may be dissolved in DMSO (30 mg/ml), and added slowly into water under mild stirring. Periodate oxidation of the Dextran surface was carried out by adding 60 mg of NaIO 4 and stirring for an hour. Subsequently, glycerol was added to quench the unreacted NaIO 4 .
  • Various amounts of PBA i.e. 40 mg for Dex-b-PLA — 40PBA) were added to the mixture, along with NaCNBH 3 , for 24 hours. All reactions were carried out in the dark. The mixture was then dialyzed in water for 24 hrs to remove any unreacted solutes, through changing the wash medium 4 times.
  • the polymers or macromolecules described herein may be formed into a nanoparticle using techniques know to those skilled in the art, including those discussed in detail below.
  • the geometry formed by the particle from the polymer or macromolecule may depend on factors such as the polymers that form the particle.
  • the particle may include a hydrophilic agent or a hydrophobic agent of interest, depending on the structure of the particle.
  • the particle may contain a drug or other therapeutic agent.
  • the hydrophilic or hydrophobic agent may be incorporated in the particle during formation of the particle, e.g., by including the agent in a solution containing the polymers that are used to form the particle, and/or the agent may be incorporated in the particle after its formation.
  • MSD volume averaged multimode size distribution
  • the method may employ additional polymers or macromolecules, which may be distinguishable from the polymers or macromolecules discussed above.
  • the first and second macromolecules may be combined together at different ratios to produce particles comprising the first and second macromolecules.
  • the method may include conjugation with more than one type of targeting moiety.
  • the surface density of targeting moiety on the resulting nanoparticles may be controlled by adjusting the amount of material in the reaction mixture.
  • the reaction may occur as a single-step reaction, i.e., the conjugation is performed without using intermediates such as N-hydroxysuccinimide or a maleimide, such as that described in U.S. Pat. No. 8,323,698.
  • the conjugation is performed without using intermediates such as N-hydroxysuccinimide or a maleimide, such as that described in U.S. Pat. No. 8,323,698.
  • such method results in a nanoparticle having a portion of the targeting moiety located in the core of the particle.
  • a multi-step approach will be used to achieve higher targeting efficiently.
  • a nanoparticle composition useful for delivery of a payload to a mucosal site comprising a plurality of amphiphilic macromolecules, the macromolecules comprising: a hydrophobic portion comprising a biocompatible polymer selected from a from polylactide, a polyglycolide, poly(lactide-co-glycolide), poly( ⁇ -caprolactone), or a combination thereof; a hydrophilic portion comprising a biocompatible polymer selected from polysaccharide, polynucleotide, polypeptide, or a combination thereof, the hydrophilic portion comprising multiple functional moieties; and a mucosal targeting moiety selected from a phenylboronic acid (PBA) derivative, a thiol derivative or an acrylate derivative, wherein at least a portion of said functional moieties of the hydrophilic portion are conjugated to the mucosal targeting moiety.
  • PBA phenylboronic acid
  • a nanoparticle composition useful for delivery of a payload to a mucosal site comprising a plurality of amphiphilic macromolecules, the macromolecules each comprising: a hydrophobic biocompatible polymer selected from a from polylactide, a polyglycolide, poly(lactide-co-glycolide), poly( ⁇ -caprolactone), or a combination thereof, the hydrophobic polymer forming the core of the nanoparticle; a hydrophilic biocompatible polymer selected from polysaccharide, polynucleotide, polypeptide, or a combination thereof, having multiple functional moieties, the hydrophilic portion forming the shell of the nanoparticle; at least a portion of the functional moieties being conjugated to a mucosal targeting moiety selected from a phenylboronic acid (PBA) derivative, a thiol derivative or an acrylate derivative.
  • PBA phenylboronic acid
  • a nanoparticle composition useful for delivery of a payload to a mucosal site comprising a plurality of amphiphilic macromolecules, the macromolecules comprising: a hydrophobic portion comprising a polylactide; a hydrophilic portion having multiple functional moieties, said hydrophilic portion comprising dextran; and a mucosal targeting moiety being a phenylboronic acid (PBA) derivative, wherein at least a portion of said functional moieties of the hydrophilic portion are conjugated to the mucosal targeting moiety.
  • PBA phenylboronic acid
  • a nanoparticle composition useful for delivery of a payload to a mucosal site comprising a plurality of amphiphilic macromolecules, the macromolecules each comprising a hydrophobic polylactide polymer conjugated to a hydrophilic dextran polymer having multiple functional moieties, at least a portion of said functional moieties being conjugated to a phenylboronic acid (PBA) derivative.
  • PBA phenylboronic acid
  • the macromolecule is Dextan-p-PLA. In some embodiment, the functionalized macromolecule is Dextran-p-PLA_PBA.
  • the nanoparticle is formed by conjugating the polylactide to the dextran to form macromolecule, then forming a nanoparticle, and subsequently surface-functionalizing the nanoparticle by conjugating at least a portion of the functional moieties of the dextran to the PBA derivative to achieve a desired surface density of the PBA derivative.
  • Acid-terminated poly(D, L-lactide) (PLA, M w ⁇ 10, 20 and 50 kDa) and PLGA-PEG (PLGA M w ⁇ 40 kDa, PEG M w ⁇ 6 kDa) were purchased from Lakeshore Biomaterials (Birmingham, Ala., USA). PLA was purified by dissolving in dimethyl sulfoxide (DMSO) and precipitating in methanol to remove residual monomers.
  • DMSO dimethyl sulfoxide
  • Dextran (Dex, M r ⁇ 1.5, 6, and 10 kDa), hydrochloric acid (HCl), triethylamine (TEA), N-(3-dimethylaminopropyl)-N-ethylcarbodiimide (EDC), and sodium cyanoborohydride (NaCNBH 3 ) were purchased from Sigma Aldrich (Oakville, ON, Canada), and used without further purification.
  • N-Hydroxysulfosuccinimide (Sulfo-NHS) and N-Boc-ethylenediamine were purchased from CNH Technologies (Massachusetts, USA).
  • DCM Dichloromethane
  • Borate buffer was prepared at a concentration of 0.05M with pH of 8.2 by mixing boric acid and sodium hydroxide.
  • Whole sheep blood (in Alsever's) was purchased from Cedarlane (Burlington, ON, Canada).
  • Veronal Buffer solution (VBS, 5 ⁇ ) was purchased from Lonza Walkersville Inc (Walkersville, Md., USA).
  • Tritium [ 3 H]-PLA-radiolabeled nanocrystals were purchased from PerkinElmer (Boston, Mass., USA).
  • the synthesis of the linear block copolymer is divided into three stages: 1) reductive amination between Dextran and N-Boc-ethylenediamine, 2) deprotection of the Boc group, and 3) conjugation of the end modified Dextran with PLA (Scheme 1).
  • the first step of the synthesis involves reductive amination between the aldehyde on the reducing end of Dextran and the amine group of N-Boc-ethylenediamine cross-linker.
  • Dex6 M r ⁇ 6 kDa, 6 g, 1 mmol
  • borate buffer 0.05 M, pH 8.2
  • the reducing agent NaCNBH 3 (1 g, 15 mmol) was added to the borate buffer solution and the mixture was stirred for 72 hours in dark conditions at room temperature. The mixture was then washed in methanol to remove any unreacted molecules or catalysts. The end-modified Dextran was dried overnight in vacuo. H NMR samples were prepared by dissolving the end-modified Dextran in D 2 O (30 mg/mL). The dried Dextran was re-dissolved in de-ionized water (DI-H 2 O). The deprotection of Boc group was performed first by adding HCl ( ⁇ 4 M) for 1 hour to cleave the amide bond between the Boc group and the protected amine moiety.
  • TEA was added to increase the pH of the solution up to 9 to deprotonate the NH 3 + end groups which were deprotected.
  • the mixture was then washed twice using methanol and dried in vacuo.
  • An NMR sample of the dried product was prepared in D 2 O (30 mg/mL).
  • the amine terminated Dextran and carboxyl terminated PLA20 (Mw ⁇ 20 kDa, 6 g, 0.3 mmol) were dissolved in DMSO.
  • the conjugation between the two polymers was facilitated by adding catalysts EDC (120 mg, 0.773 mmol) and Sulfo-NHS (300 mg, 1.38 mmol) and allowing reaction to proceed for 4 hours at room temperature.
  • the resulting Dex-b-PLA was twice precipitated and purified using excess methanol.
  • the mixture was dissolved in acetone (30 mL) to form a cloudy suspension. This was centrifuged at 4000 rpm for 10 minutes and the supernatant was extracted carefully. The supernatant was purged with air to remove the solvent and then dried overnight in vacuo to obtain the final copolymers.
  • NMR samples were prepared at a concentration of 30 mg/mL in DMSO-d6 for proton NMR and 150 mg/mL in DMSO-d6 for carbon NMR.
  • MSD volume averaged multimode size distribution
  • the particle size and the morphology of the Dex-b-PLA NPs were further verified using Transmission Electron Microscopy (TEM, Philips CM10) with the accelerating voltage of 60 kV and the Lanthanum Hexaboride filament (LaB6). 300 Mesh Formvar coated copper grids (Canemco & Marivac) were used for this experiment.
  • the NP suspension in water was prepared using the nanoprecipitation method as mentioned above. A drop of the NP suspension was placed onto the grid, and the grid was briefly stained with aqueous phosphotungstic acid solution. The copper grid with the NP suspension was dried under ambient environment overnight before imaging under TEM.
  • the size and morphology of NPs using nine formulations of Dex-b-PLA block copolymers are shown in FIG. 2 . Varying the MW of PLA and Dextran resulted in creating NPs with different sizes ranging from 15 to 70 nm. As shown in FIG. 2 a , increasing the MW of PLA increased the particle size whereas increasing the MW of Dextran decreased the particle size.
  • the NP core, formed by PLA was predicted to increase in size with increasing MW's of the PLA chains as demonstrated previously (Riley 1999; Riley 2001) and it was confirmed here by the NPs composed of PLA MW of 10 kDa, 20 kDa and 50 kDa.
  • Dex-b-PLA NPs with sizes under 50 nm have been synthesized using the simple process of bulk nanoprecipitation.
  • PLGA-PEG block copolymer was used as a commercial benchmark, which formed NPs with size 133.9 ⁇ 6.1 nm following the same procedure.
  • the particle size for PLGA-PEG is in agreement to previous literature values (Dhar 2009).
  • PLGA-PEG NPs have been able to achieve smaller particle sizes but it required the assistance of microfluidic devices for enhanced control (Karnik 2008).
  • the particle size of Dex-b-PLA NPs on the other hand, can be controlled simply by changing the MW of the compositional polymers as exemplified in FIG. 2 a.
  • the encapsulation of Doxorubicin in the Dex-b-PLA NPs was accomplished using nanoprecipitation method.
  • Dex-b-PLA and Doxorubicin were both dissolved in DMSO (Dex-b-PLA concentration of 7 mg/mL, with varying drug concentrations). 1 mL of the DMSO solution is added drop-wise into 10 mL of water under stirring and continued to stir for additional 30 minutes.
  • Encapsulation ⁇ ⁇ efficiency ⁇ ⁇ ( % ) mass ⁇ ⁇ of ⁇ ⁇ drug ⁇ ⁇ encapsulated mass ⁇ ⁇ of ⁇ ⁇ initial ⁇ ⁇ drug ⁇ ⁇ feed ⁇ 100 ⁇ % ( 1 )
  • Drug ⁇ ⁇ loading ⁇ ⁇ ( wt ⁇ ⁇ % ) mass ⁇ ⁇ of ⁇ ⁇ drug ⁇ ⁇ encapsulated mass ⁇ ⁇ of ⁇ ⁇ the ⁇ ⁇ nanoparticle ⁇ 100 ⁇ % ( 2 )
  • PLA20-Dex10 (MWPLA ⁇ 20 kDa, MWDextran ⁇ 10 kDa) and PLA20-Dex6 were selected for analyzing the encapsulation efficiencies and the drug loading using Doxorubicin as a model hydrophobic drug ( FIG. 3 ).
  • the increased drug loading is most likely due to the greater hydrophilicity of Dextran compared to PEG (Alpert 1990), which in turn reduces the probability of Dextran chains from the block copolymers associating in the hydrophobic core of the NPs.
  • the encapsulation efficiency and the total drug payload using the Dex-b-PLA system is comparable to commercially available liposomal systems such as the FDA approved Doxil®, which has a drug loading of 12.5% and DaunoXome®, which has Daunorubicin loading of 7.9% (Drummond 1999).
  • the concentration of Doxorubicin in the Doxil® formulation translates into 6.25 mg/m 2 when Doxil® is administered at 50 mg/m 2 (Drummond 1999; Safra 2000).
  • the same physiological concentration of Doxorubicin can theoretically be achieved using only 30 mg/m 2 of PLA20-Dex10 NP-Doxorubicin formulation.
  • NPs-drug suspension was prepared and filtered to remove non-encapsulated drug aggregates.
  • a purified sample of NPs-drug suspension was collected to measure the maximum absorbance and this was used as the 100% release point.
  • MWCO phosphate buffered saline
  • the release medium was replaced several times to maintain the concentration of Doxorubicin in the medium below 3 ⁇ g/mL and to stay below the solubility limit of the Doxorubicin in PBS. Replacing the medium was also expected to prevent the adhesion of released Doxorubicin to the glass walls of the beaker or the magnetic stir bar.
  • the release of Doxorubicin from PLGA-PEG was also obtained with identical procedure for comparative analysis.
  • Free Doxorubicin, without any polymers, release was also observed using the same procedure and all three release profiles from the NPs were normalized using the free Doxorubicin release data along with encapsulation efficiency data. This normalization resulted in a release curve for only encapsulated Doxorubicin. All experiments were performed in dark environment, and the beakers were sealed with Parafilm to prevent evaporation of PBS.
  • the in vitro release of Doxorubicin from the NPs was carried out in pH 7.4 PBS buffer at 37° C.
  • the release profile of Doxorubicin from NPs was characterized with an initial burst followed by a sustained-release phase. It is possible that the burst-release region corresponds to drugs non-specifically bound on the surface of the NPs, or drugs encapsulated near the surface of the NPs during the nanoprecipitation procedure (Magenheim 1993).
  • PLA20-Dex6 and PLA20-Dex10 NPs exhibited burst-release region within the initial 24 hours, releasing up to 48% and 74% respectively.
  • the subsequent sustained-release phase of Doxorubicin from PLA20-Dex6 and PLA20-Dex10 NPs continued for 192 hours with similar rate of release from both NPs.
  • the sustained-release phase may correspond to the diffusional release of the drugs from the core of the NPs.
  • the burst-release phase of Doxorubicin was within the first 6 hours while steady-release phase continued up to 96 hours, similar to what has been reported previously (Esmaeili 2008).
  • NPs were not significantly hemolytic ( ⁇ 5%) up to a concentration of 10 mg/mL in the blood ( FIG. 5 ).
  • the hemolysis by both PLA20-Dex6 and PLA20-Dex 10 were similar since they have the same component polymers.
  • Doxil® a liposomal formulation of doxorubicin
  • This dose translates to a concentration of 0.018 mg/mL in blood for an average human being (body surface area 1.79 m 2 (Sacco 2010), and blood volume 5 L) (Kusnierz-Glaz 1997).
  • the tested hemocompatible concentration (10 mg/mL) for PLA-b-Dex NPs is considerably higher than the administered dose of Doxil®. This suggests that PLA-b-Dex NPs are a safe system for intravenous administration.
  • tritium [ 3 H]-PLA-radiolabeled nanocrystals were washed and purified in methanol prior to NP formation.
  • Albino Wistar rats body weight between 200 and 250 g, were fasted overnight but had free access to water.
  • 200 ⁇ L of the NP formulations were prepared in NaCl 0.9% and injected intravenously into the tail vein at a dose of approximately 30 mg/kg.
  • Blood (approximately 200 ⁇ L) was collected in heparinized microcentrifuge tubes by controlled bleeding of hind leg saphenous veins at the indicated time intervals.
  • NPs neuropeptides
  • Rats were euthanized at 24 h after NP injections. Approximately 200 ⁇ L of blood was drawn by cardiac puncture from each mouse. Organs including heart, lungs, liver, spleen and kidneys were harvested from each animal as described previously (Gu 2008). The 3 H content in the tissue and blood were assayed in a Wallac 1414 Liquid Scintillation Counter.
  • the NP circulation half-life in vivo was characterized by measuring the amount of tritium [ 3 H]-PLA-radiolabeled nanocrystals that were incorporated in the NP formulations.
  • FIG. 6 shows NP concentration in blood circulation at predetermined time intervals after intravenous administration. It is noted that the time-dependent NP concentration in the blood were characterized by two regions of distinct slopes. The first region (first ⁇ 18 hrs) corresponds to the initial clearance of the NPs from the blood circulation, whereas the second region indicates the terminal clearance of the NPs. The former region profiles the NP volume of distribution among vascular and extravascular tissues, while the terminal half-life relates to the systemic clearance of the NPs from the body (Yang 2009).
  • the initial half-life (t 1/2 ), terminal half-life t z1/2 ), the blood retention time for 90% of the NPs (t 0.9 ), and AUC (Gaucher 2009) of the three NPs are summarized in Table 1.
  • rats were euthanized, and the major organs were harvested from the animals to evaluate the biodistribution of the NPs ( FIG. 7 ). It was observed that all three NPs had maximum accumulation in the liver and the percent distribution was similar for each NP. Higher accumulations in the spleen were observed with PLGA-PEG NPs compared to both of Dex-b-PLA NPs (p ⁇ 0.01). Accumulation of NPs in all other organs was below 5% with similar amount of accumulation among the NPs in each organ.
  • NPs Although all three types of NPs showed similar t z1/2 values, both PLA20-Dex10 and PLA20-Dex6 NPs showed significantly higher values of t 1/2 , t 0.9 , and AUC compared to that of the model NPs composed of PLGA-PEG.
  • Dex-b-PLA NPs outperform these NPs with a t 0.9 of 38.3 hrs, they are also comparable to 60 nm PEG-b-PCL system (Lee 2010) and Stealth® liposomes (Allen 1991), both of which have t 0.9 values over 48 hours.
  • a recent study by Rehor et al. showed that NPs with diameter of 40 nm had longer circulation half-life compared to larger NPs with diameter of 100 nm (Rehor 2008).
  • Dex-b-PLA NPs having smaller sizes than PLGA-PEG NPs, have increased curvature that reduce protein adsorption, which may in turn result in slower clearance rate by the RES. This is further supported by the longer blood circulation time of PLA20-Dex10 compared PLA20-Dex6 since the former has smaller particle size.
  • the abundant hydroxyl groups on the Dextran surface may induce sufficient hydration layer around the NPs to limit protein adsorption (Portet 2001). It has been reported that accumulation rate in tissues such as spleen increases with increase in the particle sizes (Li 2008) which is consistent with the current findings.
  • Dex-b-PLA NPs are expected to have low complement activation as observed for dextran-poly(methyl methacrylate) NPs, whose behaviour was similar to soluble dextran (Passirani 1998).
  • the lower accumulation of the Dex-b-PLA NPs in spleen along with lower complement activation may have attributed to their longer blood circulation (Meerasa 2011).
  • NP drug carriers The long circulation half-life of NP drug carriers is a crucial parameter in cancer therapy since it increases the probability of accumulating at cancerous tissues due to EPR effect: particle size below 100 nm directly promotes accumulation of NPs in the tumor sites since the vascular pores around tumor are at least 100 nm in size (Cho 2008).
  • the size-tuneable Dex-b-PLA system developed here presents a polymeric platform for systematically studying the effect of NP size on various in vivo characteristics such as biocompatibility, blood clearance, tumor accumulation and biodistribution and screening candidates for further clinical evaluation.
  • Dex-b-PLA The synthesis of Dex-b-PLA was carried out as described in Example 1 (see also, Verma, 2012). Briefly the procedure for the synthesis of Dex-b-PLA divides into three stages: reductive amination between Dextran and N-Boc-ethylenediamine, deprotection of the Boc group, and conjugation of the amine-modified Dextran end group with carboxyl-terminated PLA. Reductive amination was carried out by dissolving Dex in borate buffer and mixing it with N-Boc-ethylenediamine and NaCNBH 3 in dark condition for 72 hrs. After the reaction the mixture is washed with methanol and dried in vacuum desiccator.
  • the sample is then dissolved in DI-H 2 O and treated with hydrochloric acid and triethyl amine for the deprotection of the Boc group.
  • the conjugation of amine-terminated Dextran and PLA was carried out in DMSO with EDC and Sulfo-NHS as catalysts for 4 hrs.
  • the final product was washed several times with methanol.
  • the wash sample was further dissolved in acetone and centrifuged. The supernatant was extracted carefully in order to separate from free unreacted Dextran that have been precipitated. Finally the supernatant containing Dex-b-PLA was dried in vacuum desiccator.
  • Dex-b-PLA was dissolved in DMSO (30 mg/ml), and added slowly into water under mild stirring. Periodate oxidation of the Dextran surface was carried out by adding 60 mg of NaIO 4 and stirring for an hour. Subsequently, glycerol was added to quench the unreacted NaIO 4 .
  • Various amounts of PBA i.e. 40 mg for Dex-b-PLA — 40PBA) were added to the mixture, along with NaCNBH 3 , for 24 hours. All reactions were carried out in the dark. The mixture was then dialyzed in water for 24 hrs to remove any unreacted solutes, through changing the wash medium 4 times.
  • the surface modification with PBA was verified using 1 H NMR spectroscopy (Bruker 300 MHz).
  • Dex-b-PLA_PBA polymers were dissolved in DMSO-d6 (25 mg/ml) for the 1 H NMR characterization.
  • UV-Vis absorption measurement at 291 nm was performed with Epoch Multi-Volume Spectrophotometer System (Biotek, USA) on the Dex-b-PLA_PBA in order to quantify the amount of PBA attached to the Dextran chains.
  • Dex-b-PLA solution with same concentration was used as the baseline for UV-vis absorption study.
  • MSD volume-averaged multimode size distribution
  • the particle size and morphology of Dex-b-PLA_PBA NPs were further confirmed verified using TEM (Philips CM10) with the accelerating voltage of 60 kV and the Lanthanum Hexaboride filament (LaB6). 300 Mesh Formvar coated copper grids (Canemco & Marivac) were used for this experiment.
  • the NP suspension in water was prepared using the nanoprecipitation method as mentioned above. A drop of the NP suspension was placed onto the grid, and the grid was briefly stained with aqueous phosphotungstic acid solution (2 w/v % in water). The copper grid with the NP suspension was dried under ambient environment overnight before imaging under TEM.
  • the NMR spectrum of Dex-b-PLA_PBA shows peaks corresponding to both PLA (multiplets at 5.2 ppm) and Dextran (multiplets at 4.86 ppm), while also showing multiplet peaks at 6.6 ppm and 6.9 ppm, which correspond to the protons from carbon 2 to 6 in the phenyl group of the PBA ( FIG. 12 a ).
  • UV absorption at 291 nm was measured to quantify the amount of PBA on the NPs with respect to the Dextran monomers.
  • the sizes and morphology of the nanoparticles were analyzed using the procedure illustrated in Example 1.
  • the sizes of the NPs were in the range of 25 to 28 nm, which are smaller than the unmodified NPs of 47.9 nm.
  • the particle size reduction is attributed by the PBA molecules causing the Dextran chains to be less hydrophilic, leading them to form more compact shells around the PLA particle core.
  • TEM images confirmed a spherical morphology, due to the formation of a core-shell structure of the amphiphilic block copolymers ( FIG. 12 b ).
  • Dex-b-PLA_PBA NPs obtained are smaller than that normally achieved with PEG-based block copolymers such as PLGA-PEG (Karnik, 2008). We postulate that smaller NPs may be more desirable for mucoadhesion, since they provide greater surface area for interaction with the mucous membrane.
  • Cyclosporine A (CycA) encapsulation in the Dex-b-PLA and Dex-b-PLA_PBA NPs were measured using the procedure described in 0. Maximum encapsulation of CycA was achieved at an initial feed of 40 wt/wt %: Dex-b-PLA NPs encapsulated up to 10.8 wt/wt %, whereas Dex-b-PLA — 40PBA and Dex-b-PLA — 320PBA encapsulated up to 11.2 and 13.7 wt/wt %, respectively ( FIG. 15 ).
  • the 13.7 wt/wt % encapsulation is equivalent to 2.38 ⁇ g of CycA in 28 ⁇ L formulation (which is the same as the administration volume of commercially available RESTASIS®), whereas the commercial product contains 14 ⁇ g. Therefore, a therapeutically relevant dosage can be achieved by simply adjusting the polymer and drug concentration in the formulation.
  • the bioactive agent is Dorzolamide, which is commonly used to treat glaucoma.
  • the bioactive agent is Brinzolamide, which is also used to treat glaucoma.
  • Natamycin which is an antifungal agent, is also used as a bioactive agent in the encapsulation in the Dex-b-PLA_NPs.
  • Doxorubicn, an anti-cancer agent, and Olopatadine, antihistamine were also explored in the encapsulation in the PLA-Dex NPs.
  • Cyclosporine A (CycA) in the Dex-b-PLA NPs was accomplished using nanoprecipitation method.
  • Dex-b-PLA and CycA were both dissolved in DMSO (Dex-b-PLA concentration of 7 mg/mL, with varying drug concentrations). 1 mL of the DMSO solution is added drop-wise into 10 mL of DI-H 2 O under mild stirring and continued to stir for additional 30 minutes.
  • Dex-b-PLA_PBA NPs demonstrated a sustained release rate for up to 120 hours
  • Dex-b-PLA_PBA NPs showed two regions of slightly different release rate.
  • the Dex-b-PLA_PBA NPs released CycA at a faster rate compared to Dex-b-PLA NPs, which may be due to the release of CycA that were encapsulated near the slightly more hydrophobic surface Dex-b-PLA_PBA NPs.
  • the subsequent slower release rate, compared to Dex-b-PLA NPs may be due to the release of drugs from the core of the Dex-b-PLA_PBA NPs, which need to diffuse through the more compact Dextran surface.
  • STF simulated tear fluid
  • 1 mL of the release medium was extracted and the same volume of fresh new STF was added to the release medium.
  • the release medium was replaced several times to maintain the concentration of CycA in the medium in order to stay below its solubility limit in water. Replacing the medium was also expected to prevent the adhesion of released CycA to the glass walls of the beaker or the magnetic stir bar.
  • the beakers were sealed with Parafilm to prevent evaporation of water.
  • the Dex-b-PLA_PBA NPs may shield the negative charges from the surface of the mucin particles and also cause aggregation of the mucin particles, thus increasing the overall surface charge.
  • Dex-b-PLA — 160PBA (22.9 mol % PBA)
  • Dex-b-PLA — 320PBA NPs (34.6 mol %) showed significant interaction with mucin particles compared to the control study (Table 2).
  • Low PBA surface functionalization densities do not appear to show a difference compared to unmodified NPs in terms of mucin-NP interaction.
  • NPs with abundant surface functional groups such as Dextran-based NPs
  • Dextran-based NPs Dextran-based NPs
  • the maximum PBA modification can be achieved is only 0.44 mol % (assuming the same MW of PEG, i.e. 10 kDa).
  • An increased amount of PBA functionalization also increased the extent of NP-mucin interaction, which allows potential increase of mucin-NP interaction by saturating PBA on the surface.
  • the functionalization of PBA causes the Dextran surface to be more hydrophobic, increasing the potential for aggregation of the NPs. It is therefore ideal to tune the amount of PBA functionalization to achieve optimal mucin-NP interaction without compromising the NP colloidal stability.
  • zeta potential was measured for quantitative analysis of interaction between mucin particles and Dex-b-PLA_PBA NP suspension.
  • 1 w/v % mucin solution was prepared in pH 7.4 PBS by stirring overnight and the solution was subsequently sonicated for 10 minutes (Branson Digital Sonifier 450, USA).
  • To 700 ⁇ L of mucin particle solution were added 200 ⁇ L of 0.7 mg/ml Dex-b-PLA_PBA NP suspension in PBS.
  • a control study was also performed by adding 200 ⁇ L of PBS to the mucin particle solution.
  • the zeta potential of mucin particles with the NP suspension and the control study were determined using a Malvern ZetaSizer Nano ZS90 (Malvern Instruments, Worcestershire, U.K.).
  • Dex-b-PLA — 320PBA decreased the amount of mucin adsorbed.
  • excess functionalization of the NP surfaces with PBA causes the Dextran to become more hydrophobic. This would increase the potential for self-aggregation of the NPs, reducing the total available surface area for mucin adsorption. It is therefore ideal to tune the amount of PBA functionalization to achieve optimal mucin-NP interaction without compromising the NP colloidal stability. It is also possible that smaller NPs render higher mucin adsorption due to their larger total surface area, as shown by comparing PLGA-PEG, Dex-b-PLA, and Dex-b-PLA_PBA NPs.
  • Mucoadhesion was calculated as the amount of mucin adsorbed per mg of NPs.
  • NP suspension (1 ml) was mixed with 1 ml of mucin solution (1 mg/ml in STF) and incubated at 37° C. for 1 hr. The mixture was then centrifuged at 15,000 rpm for 1 hr and free mucin in the supernatant was quantified using the periodic acid/Schiff (PAS) staining method (Lee, 2006).
  • Mucin adsorption was calculated by subtracting the free mucin concentration from the initial mucin concentration.
  • Mucin standards (0.1, 0.25 and 0.5 mg/ml) were determined using the same procedure to obtain a calibration curve.
  • the formulations were administered to rabbit eyes, while having contralateral eyes as control, and daily slit-lamp examination for up to 7 days was performed to analyze the ocular surface.
  • the control eyes showed overall higher values compared to the corresponding NP treated eyes ( FIG. 23 ).
  • conjunctival swelling, corneal opacification, and infiltrate were not observed in any of the rabbits.
  • the nanoparticles are prepared using the nanoprecipitation method described in Example 4 but without the drug.
  • the nanoparticles were filtered using 200 nm syringe filter, and further sterilized using UV irradiation inside a BioSafety Cabinet (BSC) for 1 hour.
  • BSC BioSafety Cabinet
  • One eye was administered with NPs (28 ⁇ l; 19 ⁇ g of Dex-b-PLA_PBA NPs) while the contra-lateral eye is used as control.
  • the rabbits were euthanized and the ocular tissues (the entire ocular globe, and upper and lower eyelids) were collected for histopathology analysis (0).
  • the ocular tissues the entire ocular globe, and upper and lower eyelids
  • normal ocular tissues surfaces were observed in both the NP treated and the control eyes ( FIG. 24 ).
  • All eyes showed anterior segment with preserved architecture and morphology. No sign of inflammation, altered layer integrity, or presence of residual particles were detected in any of the eyes. Adequate number of goblet cells with preserved morphology was also shown. Presence of occasional intraepithelial and subepithelial eosinophils in tarsal conjunctiva were found in both NP treated and control eyes, suggesting that the phenomenon is not directly caused by the administration of the NP formulation.
  • the eyes were enucleated and collected immediately after euthanasia for histpathological evaluation.
  • the entire upper and lower eyelids were also dissected and collected for evaluation of the tarsal conjunctiva and underlying soft tissues.
  • Consecutive sections of the entire ocular globe and eyelids were processed for microscopic analysis: after initial fixation in 10% neutral buffered formalin, the tissue was embedded in paraffin, serially sectioned in 5 ⁇ m thick sections, and stained with hematoxylin and eosin (H&E).
  • the histological slides were evaluated using bright field microscopy (Leica DM1000, ICC50 HD, Leica Microsystems Inc, Concord, ON).
  • the formulations were administered to rabbit eyes once a week for up to 12 weeks, while having contralateral eyes as control, and daily slit-lamp examination was performed similar to above. Similar to acute response study, no sign of conjunctival swelling, corneal opacification, or infiltrate were observed in any of the rabbits at any point of the time during the study. Overall, the difference in values between the NP treated and control eyes were insignificant across all of the 7 categories throughout the duration of the study (12 weeks) ( FIG. 25 ).
  • the nanoparticles are prepared using the nanoprecipitation method described in Example 4 but without the drug.
  • the nanoparticles were filtered using 200 nm syringe filter, and further sterilized using UV irradiation inside a BioSafety Cabinet (BSC) for 1 hour.
  • BSC BioSafety Cabinet
  • One eye was administered with NPs (28 ⁇ l; 19 ⁇ g of Dex-b-PLA_PBA NPs) once a week for 12 weeks while the contra-lateral eye is used as control. Slit lamp examination at 0, 1, 24, 48 hr after administration each week was used to evaluate 7 different categories (Note that 0 hr means before administration).
  • the long-term biocompatibility of the NP formulation with encapsulation of Cyclosporine A was also examined using slit-lamp.
  • the formulation containing both the Dex-b-PLA_PBA NPs and Cyclosporine A were administered to rabbit eyes, while having contralateral eyes as control.
  • the slit-lamp examination for up to 4 weeks has shown no significant difference between the NP treated and the control eyes in any of the 7 categories ( FIG. 26 ).
  • the nanoparticles are prepared using the nanoprecipitation method described in Example 4 with Cyclosporine A.
  • the nanoparticles were filtered using 200 nm syringe filter, and further sterilized using UV irradiation inside a BioSafety Cabinet (BSC) for 1 hour.
  • BSC BioSafety Cabinet
  • One eye was administered with NPs (28 ⁇ l; 19 ⁇ g of Dex-b-PLA_PBA NPs and 8 ⁇ g of Cyclosporine A) once a week for 12 weeks, while the contra-lateral eye is used as control.
  • the present inventors synthesized a model linear block copolymer using PLA and Dextran (Dex-b-PLA), and demonstrated that NPs composed of Dex-b-PLA can self-assemble into core-shell structured NPs of small particle size, e.g. sizes less than 40 nm, without using any flow-focusing devices. They further showed that the size of Dex-b-PLA NPs can be precisely fine-tuned, e.g. between 15-70 nm by altering the molecular weight of the component blocks (Verma, 2012).
  • Dextran a natural polysaccharide composed of 1 ⁇ 6 linked ⁇ -D-glucopyranosyl units, was selected as a model hydrophilic block because of its high hydrophilicity and biocompatibility. Dextran has an abundance of functional hydroxyl groups on its back bone. The higher density of surface functional groups (as opposed to PEG, which has one functional group per chain) can improve the efficiency of surface functionalization, and thus, desirable surface properties are more easily achieved with Dextran based NPs. Dextran coated NPs showed excellent colloidal stability in physiological media in vitro and long retention in the systemic circulation in vivo (Verma, 2012; Albert, 1990).
  • NPs composed of Dextran-PLA particles and PEG-PLA particles, which is due to the greater hydrophilicity of the Dextrans compared to that of PEG.
  • the more hydrophilic Dextran is less likely randomly associated in the hydrophobic core of the NPs compared to PEG, which could also explain the increased drug encapsulated in the Dextran-PLA NPs compared to PLGA-PEG NPs (Verma, 2012).

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CA2877051A1 (en) 2013-12-27
KR102177557B1 (ko) 2020-11-11
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WO2013188979A1 (en) 2013-12-27
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US9993439B2 (en) 2018-06-12

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