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US20130217789A1 - Biodegradable liquogel and ph sensitive nanocarriers - Google Patents

Biodegradable liquogel and ph sensitive nanocarriers Download PDF

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US20130217789A1
US20130217789A1 US13/818,782 US201113818782A US2013217789A1 US 20130217789 A1 US20130217789 A1 US 20130217789A1 US 201113818782 A US201113818782 A US 201113818782A US 2013217789 A1 US2013217789 A1 US 2013217789A1
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hpg
drug
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Darlene K. Taylor
Melony A. Ochieng
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North Carolina Central University
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
    • A61K47/30—Macromolecular organic or inorganic compounds, e.g. inorganic polyphosphates
    • A61K47/34—Macromolecular compounds obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polyesters, polyamino acids, polysiloxanes, polyphosphazines, copolymers of polyalkylene glycol or poloxamers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K31/00—Medicinal preparations containing organic active ingredients
    • A61K31/33—Heterocyclic compounds
    • A61K31/395—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins
    • A61K31/435—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins having six-membered rings with one nitrogen as the only ring hetero atom
    • A61K31/47—Quinolines; Isoquinolines
    • A61K31/4738—Quinolines; Isoquinolines ortho- or peri-condensed with heterocyclic ring systems
    • A61K31/4745—Quinolines; Isoquinolines ortho- or peri-condensed with heterocyclic ring systems condensed with ring systems having nitrogen as a ring hetero atom, e.g. phenantrolines
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K31/00—Medicinal preparations containing organic active ingredients
    • A61K31/56—Compounds containing cyclopenta[a]hydrophenanthrene ring systems; Derivatives thereof, e.g. steroids
    • A61K31/565—Compounds containing cyclopenta[a]hydrophenanthrene ring systems; Derivatives thereof, e.g. steroids not substituted in position 17 beta by a carbon atom, e.g. estrane, estradiol
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
    • A61K47/50—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates
    • A61K47/51—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the non-active ingredient being a modifying agent
    • A61K47/54—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the non-active ingredient being a modifying agent the modifying agent being an organic compound
    • A61K47/55—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the non-active ingredient being a modifying agent the modifying agent being an organic compound the modifying agent being also a pharmacologically or therapeutically active agent, i.e. the entire conjugate being a codrug, i.e. a dimer, oligomer or polymer of pharmacologically or therapeutically active compounds
    • A61K47/551—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the non-active ingredient being a modifying agent the modifying agent being an organic compound the modifying agent being also a pharmacologically or therapeutically active agent, i.e. the entire conjugate being a codrug, i.e. a dimer, oligomer or polymer of pharmacologically or therapeutically active compounds one of the codrug's components being a vitamin, e.g. niacinamide, vitamin B3, cobalamin, vitamin B12, folate, vitamin A or retinoic acid
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
    • A61K47/50—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates
    • A61K47/51—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the non-active ingredient being a modifying agent
    • A61K47/56—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the non-active ingredient being a modifying agent the modifying agent being an organic macromolecular compound, e.g. an oligomeric, polymeric or dendrimeric molecule
    • A61K47/59—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the non-active ingredient being a modifying agent the modifying agent being an organic macromolecular compound, e.g. an oligomeric, polymeric or dendrimeric molecule obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polyureas or polyurethanes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/0012—Galenical forms characterised by the site of application
    • A61K9/0019—Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
    • A61K9/0024—Solid, semi-solid or solidifying implants, which are implanted or injected in body tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/06—Ointments; Bases therefor; Other semi-solid forms, e.g. creams, sticks, gels
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G83/00—Macromolecular compounds not provided for in groups C08G2/00 - C08G81/00
    • C08G83/002—Dendritic macromolecules
    • C08G83/005—Hyperbranched macromolecules
    • C08G83/006—After treatment of hyperbranched macromolecules
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L101/00—Compositions of unspecified macromolecular compounds
    • C08L101/005—Dendritic macromolecules

Definitions

  • the present invention relates to a temperature responsive liquogel and pH sensitive nanocarriers.
  • systemic therapy does not necessarily provide therapeutic tissue levels of a drug. It may also result in deleterious effects in the patient. As such there is a need for a local delivery system that can be used to deliver a drug or therapeutic agent locally to a specific site.
  • hydrogels with a lower critical solution temperature (LCST) below body temperature have been advocated as promising injectable drug delivery systems [1-7].
  • Hydrogels are often used in biological applications thus they are often biomaterials. Hydrogels swell in water and typically undergo a phase transition to gel immediately after reaching their LCST.
  • Viable representatives of these polymers are thermally smart and include polysaccharide derivatives [8], poly(N-isopropylacrylamide) (PNIPAAm) [9-11], and poly(ethylene glycol) (PEG) [6, 8].
  • PNIPAAm poly(N-isopropylacrylamide)
  • PEG poly(ethylene glycol) [6, 8].
  • all of these representative thermally smart polymers include hydrophilic materials that are biologically non-degradable on any useful timescale.
  • Biodegradable macromers such as hydrophobic lactides are often copolymerized with thermogelling polymers to facilitate bioadsorption and clearance from the body at physiological temperatures [12].
  • PNIPAAm-based hydrogels incorporating poly(lactic acid) (PLA) macromers are routinely investigated as injectable bulking biomaterials since the ester linkages of PLA are hydrolytically degraded in the presence of water and the LCST can be tuned by the monomer feed ratio. Further improvements to the hydrogel delivery system are realized by copolymerizing small amounts of hydrophilic molecules, such as acrylic acid, to enhance the bioadsorption of the hydrolytically degraded copolymer [13].
  • a delivery system that includes degradable biomaterials that not only respond to temperature but also easily accommodate chemical linkage of active molecules.
  • Such a platform could utilize orthogonally triggered mechanisms (such as temperature stimulated entrapment and pH programmed linkage) to provide targeted and controlled delivery of therapeutic agents.
  • the present invention relates to multi-functional and programmable delivery systems for targeted therapy. Local delivery of drugs embedded in a hyperbranched polyglycerol (HPG) based nanocarrier has the potential to reduce the need for surgical and other procedures that are time consuming for the patient and can result in complications to the patient.
  • HPG hyperbranched polyglycerol
  • thermoresponsive, biocompatible nanocarriers have been designed and synthesized to contain various amounts of HPG.
  • the present invention relates to a delivery system using materials that form a liquogel comprising hyperbranched polyglycerols (HPG).
  • HPG hyperbranched polyglycerols
  • Another aspect of the invention is a pH sensitive nanocarrier prepared using hyperbranched glycerols and a pH responsive linker.
  • the delivery system comprises a drug or therapeutic agent that is entrapped in a liquogel or nanocarriers.
  • Another aspect of the invention is a method of using the delivery system to administer a subject a drug or therapeutic agent locally.
  • FIG. 1 shows a schematic for obtaining thermogelling biomaterials from acrylic macromers methacryalated- hyperbranched polyglycerol (HPG-MA) and 2-hydroxyethyl methacrylate-poly(lactic acid) (HEMAPLA) copolymerized with monomers n-isopropylacrylamide (NIPAAm) and Acrylic Acid (AAc) by Radical Polymerization.
  • HPG-MA methacryalated- hyperbranched polyglycerol
  • HEMAPLA 2-hydroxyethyl methacrylate-poly(lactic acid) copolymerized with monomers n-isopropylacrylamide (NIPAAm) and Acrylic Acid (AAc) by Radical Polymerization.
  • NIPAAm 2-hydroxyethyl methacrylate-poly(lactic acid)
  • AAc Acrylic Acid
  • FIG. 2 shows a method according to U.S. Patent Publication 2008/0096975 and is a schematic drawing for the synthesis of the polylactide hydroxyethyl methacrylate-lactide (HEMAPLA) macromer from hydroxyethyl methacrylate (HEMA) and lactide (LA).
  • HEMAPLA polylactide hydroxyethyl methacrylate-lactide
  • HEMA hydroxyethyl methacrylate
  • LA lactide
  • FIG. 3 shows 1 H NMR spectra (CD 3 OD) of hyperbranched polyglycerol (HPG) obtained from anionic polymerization initiated with 1, 1, 1-tris (hydroxymethyl)propane.
  • HPG hyperbranched polyglycerol
  • FIG. 4 shows ESI-TOF of (A) HPG-MA and (B) HPG macromer precursor.
  • FIG. 5 shows 1 H NMR spectra (DMSO-d 6 ) of HEMAPLA.
  • FIG. 6 shows 1 H NMR spectra (DMSO-d 6 ) of copolymers of poly(NIPAAm-co- HEMAPLA-co-AAc-co-HPG-MA), where the spectra represent (A) Control (B) HPG Low (C) HPG Med and (D) HPG High.
  • FIG. 7 shows a 13 C NMR spectra (DMSO-d 6 ) of copolymers of poly(NIPAAm-co-HEMAPLA-co-AAc-co-HPG-MA), where the spectrum represents polymer sample HPG High.
  • FIG. 8 shows MALDI of copolymers (A) HPG-High and (B) Control.
  • FIG. 9 shows LCST determination by DSC analysis for all solutions of poly(NIPAAm-co- HEMAPLA-co-AAc-co-HPG-MA): control, HPG low, HPG medium, and HPG high.
  • FIG. 10 shows LCST determination by measurement of copolymer solution optical absorption as a function of temperature.
  • FIG. 11 shows results of MTS assay to measure the cytotoxicity of HPG or copolymer HPG High at various concentrations.
  • FIG. 12 shows degradation studies of 16.7% copolymer gel HPG High at 37° C. showing GPC curves (A) and change in molecular weight with time (B).
  • FIG. 13 shows 1 H NMR data showing spectral changes during the hydrolytic degradation of a representative poly(NIPAAm-co-HEMAPLA-co-AAc-co-HPG-MA) sample.
  • FIG. 14 shows a delivery system with a pH responsive component.
  • FIG. 15 schematic of synthesis to prepare HPG based drug delivery system with pH sensitive linkers.
  • FIG. 16 shows the effects on cell viability.
  • FIG. 17 shows the cytotoxic effect on MCF-7 cells.
  • FIG. 18 illustrates the transition from a clear solution to a gel.
  • FIG. 19 shows optical absorption of the liquogel as a function of the temperature observation of the liquogel transition temperature.
  • FIG. 20 shows a differential scanning calorimetry (DSC) curve showing transition in liquogel at 35.7° C., heating rate, 10° C./min.
  • FIG. 21 shows 1 H NMR spectra (CD3OD) of hyperbranched polyglycerol (HPG) obtained from anionic polymerization initiated with 1,1,1-tris (hydroxymethyl)propane.
  • FIG. 22 shows 1 H NMR (S H , 500 MHz, CDCL3): of TEGDVE linker.
  • FIG. 23 shows 1 H NMR of HPG-linker conjugate.
  • FIG. 24 shows 1 H NMR of four component copolymer HPG-co-TREDVE-co-folic acid-co-fulvestrant.
  • FIG. 25 shows (S H , 500 MHz, CDCL3): fulvestrant.
  • drug or therapeutic agent means a diagnostic or therapeutic molecule that can be used for prevention or treatment of a disease, condition or disorder.
  • drug or therapeutic agent can be used interchangeably and the liquogels and nanocarriers of this invention may contain one or more drugs, or therapeutic agents.
  • quogel is a material that transitions from liquid to gel due to a change in temperature.
  • orthogonal trigger means external stimuli (i.e. temperature trigger, pressure trigger, magnetic trigger, electrochemical trigger etc.) that illicit independent responses from the material.
  • physiologically acceptable is meant that the carrier, diluent, and/or excipients, must be compatible with the other ingredients of the formulation, and not deleterious to the recipient thereof. “Physiologically acceptable” also means that the compositions, or dosage forms are within the scope of sound medical judgment, suitable for use for an animal or human without excessive toxicity, irritation, allergic response, or other problem or complication, commensurate with a reasonable benefit/risk ratio.
  • prevention refers to delaying, slowing, inhibiting, reducing or ameliorating the onset of disease or condition.
  • treatment and “therapy” and the like refer to alleviating, slowing the progression, prophylaxis, attenuation or cure of existing disease or condition.
  • Treatment of a subject includes the application or administration of a composition to a subject, or application or administration of a composition to a cell or tissue from a subject who has such a disease or condition, or is at risk of or susceptible to such a disease or condition, with the purpose of curing, healing, alleviating, relieving, altering, remedying, ameliorating, improving, or affecting the disease or condition, the symptom of the disease or condition, or the risk of or susceptibility to the disease or condition.
  • subject means mammals. Examples of mammals include humans, monkeys, cows, sheep, goats, dogs, cats, mice, rats, and transgenic species thereof.
  • the biodegradable liquogel of this invention responds to temperature and can easily accommodate chemical linkage of active molecules such as drugs and therapeutic agents.
  • This system can utilize orthogonally triggered mechanisms to provide targeted and controlled delivery of a drug or therapeutic agent.
  • thermoresponsive, crosslinking, and biodegradable macromers are copolymerized with hyperbranched polyglycerols (HPG) to form a composition that can be used to incorporate or entrap a drug, other therapeutic agent or one or more of both.
  • HPG hyperbranched polyglycerols
  • the biodegradable and thermoresponsive copolymers are covalently linked with HPG macromers that can be further manipulated by an orthogonal trigger.
  • compositions of this invention are soluble in aqueous media and form liquogels.
  • the nanocarrier will gel at body temperature. Gelation properties have been optimized by systematically varying the ratios of the components of the nanocarrier. The in vitro degradation kinetics have been evaluated, and the cytotoxicity of gradation products have been evaluated on cultured cells.
  • the copolymers presented herein represent a tunable thermoresponsive platform with potentially versatile functionality for drug delivery.
  • the incorporation of HPG macromers permits chemically modifiable functional sites. HPG macromers impart functionality to the copolymers because of the internal cavities that form that are suitable for small molecule interaction, large number of modifiable surface hydroxyl groups, and excellent biocompatibility [14-20].
  • a trigger other than temperature has been developed.
  • Other triggers include pH triggers, pressure triggers, magnetic triggers, and electrochemical triggers.
  • the liquogel provides a sufficient barrier against metabolic degradation and allows solubility of the drug therapeutic agent.
  • the liquogel gels in vivo before degrading in a controlled way to release the entrapped drug or therapeutic agent.
  • the drug may be entrapped non-covalently or by hydrogen bonding. The release can be controlled by one or more orthogonal external triggers.
  • the liquogel is in solution at temperatures ranging from 5° C. to 27° C. and gels at body temperature before degrading to release an entrapped drug or therapeutic agent.
  • a method to yield a series of copolymers with different ratios of NIPAAm, HEMAPLA, AAc, and HPG-MA is described herein.
  • the liquogels typically have an LCST between room temperature and 37° C.
  • HPGs may now be obtained in a single step with properties that rival the dendritic materials platform [24].
  • the liquogel nanocarrier comprises HPG macromers, a crosslinker, a biodegradable component, and a thermoresponsive component.
  • Systematically varied ratios of HPG macromers, crosslinker, biodegradable component and thermoresponsive component can be used to prepare liquogels. This can result in liquogels having different properties.
  • the liquogel nanocarrier will gel at body temperature.
  • Thermoresponsive, biocompatible liquogels with various amounts of HPG (—up to 17 wt %) have been generated. Gelation properties have been optimized by systematically varying the ratios of the components of the liquogel.
  • the composition of each component in the liquogel determines the lower critical solution temperature (LCST) of the liquogel.
  • LCST critical solution temperature
  • the liquogel is a liquid and can be physically mixed with a drug or therapeutic agent to form a suspension.
  • the temperature is increased above the LCST, the liquogel gels and retains a shape that will entrap or incorporate the drug or therapeutic agent within its matrix. In most cases, the drug or therapeutic agent are non-covalently or hydrogen bonded in the liquogel.
  • the crosslinker is an acrylate group.
  • a nonlimiting example of an acrylate group is hydroxyethyl methacrylate (HEMA).
  • Non limiting examples of compounds that can be used as the biodegradable component are poly(lactic acid) (PLA), lactide, poly(trimethylene carbonate), and poly(e-caprolactone).
  • Other examples of compounds that can be used as the biodegradable component are hyaluronic acid, gelatin, peptides, and collagen.
  • Poly(lactic acid) (PLA) provides biodegradability through hydrolytic bond cleavage.
  • Non limiting examples of compounds that can be used as a thermoresponsive component are N-alkyl acrylamide or polyethylene glycol.
  • the alkyl is a straight, branched or cyclic C1-C6 alkyl.
  • Non-limiting examples of such alkyl groups are methyl, ethyl, n-propyl, isopropyl or cyclopropyl.
  • N-alkyl acrylamide N-isopropylacrylamide (NIPAAm).
  • Poly N-isopropylacrylamide is represented by PNIPAAm.
  • a non limiting example of a hydrophilic compound that can be used to re-solubilize the degraded polymer products is acrylic acid (AAc).
  • AAc provides a hydrophilic component to increase the transition temperature of the copolymer after hydrolysis.
  • the liquogel is prepared from at least: N-isopropylacrylamide or an N-alkyl acrylamide in which the alkyl is methyl, ethyl, propyl, isopropyl or cyclopropyl acrylic acid and/or methacrylic acid, an acrylic monomer having an amine-reactive group (such as acrylic N-hydroxysuccinimide ester) and a polyester macromer.
  • the polyester macromer is a polylactide macromer, comprising hydroxyethyl methacrylate residues and varying numbers of lactide units/residues.
  • FIG. 1 shows a HPG based liquogel with a HPG multifunctional platform, functional acrylate groups that comprise the crosslinker, biodegradable group and thermoresponsive and acrylic acid groups).
  • HPG-MA methacrylated hyperbranched polyglycerol
  • NIPAAm N-isopropylacrylamide
  • HEMA-PLA hydroxyethyl methacrylate-polylactide
  • AAc acrylic acid
  • Poly(NIP AAm-co-HEMAPLA-co-AAc-co-HPG-MA) displayed increasing lower critical solution temperatures (LCST) as the HPG content increased over a range of macromer ratios.
  • LCST critical solution temperatures
  • this nanocarrier showed no toxicity when human uterine fibroid cells were co-cultured with the copolymer for up to 72 h. This copolymer lost approximately 92% of its mass after 17 hours at 37° C. ( FIG. 12 ).
  • components that can be used with HPGs are the components disclosed in US Patent application publication 2008/0096975 (Guan et al.) and include compositions comprising an N-isopropylacrylamide residue (an N-isopropylacrylamide monomer incorporated into a polymer), one or both of an acrylic acid residue and a methacrylic acid residue and an acrylic residue. (See FIG. 2 ).
  • HPG polymers may be functionalized with an optimized combination of lactides, methacrylates, and isopropylacrylamides to afford a degradable, vitrifing and thermoresponsive delivery system.
  • N-isopropylacrylamide provides thermogelling with a LCST below physiological conditions
  • poly(lactic acid) PLA
  • acrylic acid AAc
  • HPG provides a number of hydroxyl groups available for attachment of drug or therapeutic agent or chemical modification to covalently attach fluorescent tags for biomarkers or pH triggered linkers terminated with bioactive molecules.
  • HEMA-PLA was chosen over PLA alone to facilitate chemical synthesis.
  • HPG in like manner, was functionalized with methacrylate groups, HPG-MA, in order to realize its incorporation in the copolymer.
  • the PLA macromer is incorporated as side components linked to 2-hydroxyethyl methacrylate (HEMA), yielding HEMA-PLA.
  • HEMA is easily coupled to PLA and renders an olefin group that can be copolymerized with the other acrylic macromers.
  • the liquogel nanocarriers and compositions of the invention can be prepared by co-polymerizing the components by any useful polymerization method, for example, and without limitation by free-radical polymerization or ring-open polymerization. In addition to these methods and the method shown in FIG. 1 can be prepared by other methods known to those of skill in the art.
  • Methacrylated HPGs have been incorporated into thermoresponsive hydrogels creating materials with added functional groups that can be easily manipulated in the design of drug delivery systems.
  • the copolymers were loaded with HPG up to 17% molar equivalents and displayed LCST as high as 30° C. for the highest HPG containing copolymer. All of the transition temperatures observed for the copolymers of the examples were below physiological temperature of 37° C., and increasing the feed ratio of HPG beyond 17% molar equivalents or % by weight would presumably further increase the sol-gel temperature.
  • the selected poly(NIPAAm-co-HEMAPLA-co-AAc-co-HPG-MA) at a molar ratio of 70:1:3.3:17 has attractive properties and was not toxic to cultured uterine fibroid cells.
  • the LCST can be determined by measuring the change in transmittance with a UV-V is spectrometer as a function of temperature (Advanced Drug Delivery Reviews (1998), 31: 197-221 and Annals N.Y. of Science, 1999, 875(1):24-35). LCST also can be determined by any other method known in the art-for example and without limitation by Differential Scanning calorimetry (DSC).
  • DSC Differential Scanning calorimetry
  • the copolymers can be characterized by nuclear magnetic resonance (NMR) spectroscopy and gel permeation chromatography (GPC). Solutions of the macromers were characterized for their phase-transition properties by differential scanning calorimetry (DSC) and optical absorption. Copolymers were analyzed by mass spectrometry and cytocompatibility and degradation properties were also assessed.
  • NMR nuclear magnetic resonance
  • GPC gel permeation chromatography
  • FIG. 1 shows the preparation of thermogelling biomaterials from the acrylic macromers methacryalated-hyperbranched polyglycerol (HPG-MA) and 2-Hydroxyethyl Methacrylate-poly(lactic acid) (HEMAPLA) copolymerized with monomers N-Isopropylacrylamide (NIPAAm) and acrylic Acid (AAc) by radical polymerization.
  • HPG-MA methacryalated-hyperbranched polyglycerol
  • HEMAPLA 2-Hydroxyethyl Methacrylate-poly(lactic acid) copolymerized with monomers N-Isopropylacrylamide (NIPAAm) and acrylic Acid (AAc) by radical polymerization.
  • NIPAAm N-Isopropylacrylamide
  • AAc acrylic Acid
  • the schematic illustration of this reaction is simplified, recognizing that on average one out of 29 pendant HPG hydroxyl groups reacted in the methylation step.
  • the HEMAPLA macromer is prepared as a stand alone reaction.
  • the resulting four component copolymer is a branched statistical copolymer.
  • the first reaction depicted in FIG. 1 is a method used to prepare methacrylated HPG macromer.
  • the methacryloyl group was directly linked to the starting HPG by transesterification.
  • 1 H NMR analysis of the product was consistent with results reported by Oudshoorn et al. [26].
  • new peaks were detected.
  • 1 H NMR spectra shown in FIG. 1 In addition to the four methylene and one methine (broad multiplet at 3.4 ppm) and one hydroxyl proton (4.8 ppm) originating from the monomer repeat units of HPG, new peaks were detected. 1 H NMR spectra shown in FIG.
  • FIG. 3A shows the 1 H NMR spectra (CD 3 OD) of hyper branched polyglycerol (HPG) obtained from anionic polymerization initiated with 1,1,1-tris (hydroxymethyl)propane.
  • FIG. 3C shows the magnified region where the acylate peaks of HPG-MA appear and confirmed the incorporation of the methacryloyl group with the observation of methyl (1.8 ppm) and acrylate protons (5.67 and 6.08 ppm, shown more clearly with the enlarged insert).
  • the MALDI MS of HPG-MA was consistent with the ion fragmentation pattern obtained by ESI MS which is shown in FIG. 4A .
  • the top mass number in the figure corresponds to the peak m/z value, with a charge (z) of +1 evident in all labeled peaks (data not shown).
  • 4A and 4B may correspond to incorporation of a cyclic derivative of glycidol as previously reported [21]. No peaks are observed in HPG with a mass delta of 142. Together, this data confirms that glycidyl methacrylate was incorporated into the hyperbranched structure. No evidence of multiple methacryloyl incorporation was observed. This supports 1 H-NMR data discussed above, which implied that on average ⁇ 1 out of 29 hydroxyl groups of HPG are substituted with a methacryloyl group.
  • the macromer HEMAPLA was prepared and its synthesis confirmed by 1 H NMR shown in FIG. 5 which is 1 H NMR spectra (DMSO-d 6 ) of HEMAPLA.
  • the proton peaks are in agreement with the molecular structure of HEMAPLA.
  • the number average length of PLA units per macromer was determined from the 1 H NMR spectrum by calculation from the ratio of the integrals of hydrogen peaks from PLA (peaks c, f, j, and h) relative to the double bond hydrogen peaks (peaks a and b at 5.6 and 6.1 ppm).
  • a PLA repeat unit of 3 was determined and found to be in agreement with the molar feed ratio of HEMA to L-lactide (1:1) utilized in the synthesis of HEMAPLA
  • FIG. 6 shows the stacked 1 H NMR spectra for all the copolymers synthesized.
  • the molecular weights of the poly(NIPAAm-co-HEMAPLA-co-AAc-co-HPG-MA) copolymers were determined by GPC.
  • the molecular weights obtained for the synthesized copolymers were low due to the monomer to initiator feed ratio.
  • the molecular weight decreases as the HPG-MA feed ratio content increases. This result may be a result of steric hindrance as it is more difficult to easily incorporate the bulky HPG group into the polymer backbone via the approximately one acrylate group per HPG molecule.
  • All of the copolymers have molecular weights between 1,200 and 3,700 g/mol and a polydispersity index of 1.5-1.7.
  • the measured M n values for HPG High, HPG Med and HPG Low are expected to be problematic as the hyperbranched structure of the HPG component does not accurately correspond to the linear polystyrene calibrant.
  • the GPC-determined molecular weight distribution of the copolymers can be used as a reference.
  • FIG. 8 shows the MALDI of copolymers (A) CONTROL and (B) HPG HIGH.
  • HPG High was determined to have a number average molecular weight of 1,412 g/mole and a polydispersity index of 1.16. This value is 3 times lower than the value obtained by GPC.
  • Others have observed hyperbranched polymers with up to 5 times lower molecular weights obtained by MALDI MS as compared to GPC [21].
  • the number average molecular weight M n calculated from the MALDI-TOF spectrum for Control is 1,164 g/mole which is in good agreement with the value of 1,253 obtained from GPC.
  • the mass difference exactly corresponds to 72.
  • the LCST of the different copolymers was determined based on abrupt changes in optical and thermal properties of the materials. DSC measurements of thermogelling solutions is a common method used to describe the phase transition temperature [9, 13]. An endothermic peak occurs when a temperature is reached that induces hydrogen bond breaking in the water clusters around the hydrophobic domains and between the water molecules and amide bonds in the copolymers [30]. Typical DSC curves of copolymer solutions (16.7 wt % in PBS) showed broad but obvious endothermic peaks in the range of 20-28 ° C. as shown in FIG. 9 . The gray box focuses on the temperature range where all transitions were observed as indicated by the minimum in the endotherm trace. The transition temperature shifts to lower values as the HPG content is reduced.
  • FIG. 10 shows LCST determination by measurement of copolymer solution optical absorption as a function of temperature.
  • FIG. 12 shows Degradation studies of 16.7 wt % copolymer gel HPG High at 37° C. showing GPC curves FIG. 12A and change in the molecular weight with time FIG. 12B .
  • the GPC chromatogram did show a decrease in polydispersity index (PDI) from 1.7 to 1.3 after complete hydrolysis.
  • PDI polydispersity index
  • the polydispersity is affected by both the composition and degree of polymerization. After hydrolysis, the affect of the composition on the polydispersity is reduced and the degree of polymerization becomes the main determinate of the polydispersity.
  • FIG. 12B presents the GPC-generated findings that show a relatively fast decrease in molecular weight over a six day period. Hydrolysis of the PLA containing chains leads to mass loss. Within the first 16.5 hours, the copolymer has lost 95% of its PLA molecular weight.
  • FIG. 13 shows 1 H-NMR (D 2 O) spectral change during hydrolytic degradation of a representative poly(NIPAAm-co-HEMAPLA-co-AAc-co-HPG-MA) sample: (A) after 0 hours (B) 15 hours (C) 21 hours; and (D) 56 hours of degradation.
  • the HEMA-lactate peak (methane proton, 1 H) at 5.2 ppm disappeared as the ester linkages of the polylactic acid spacers hydrolyzed during incubation. After 15 hours, there is a sharp decrease in the peak and after 21 hours in the peak is no longer amendable to integration.
  • the system allows a wide variety of diagnostic and therapeutic molecules for local delivery to target tissues without the need for modification of the drug, or therapeutic agent.
  • the liquogel including a drug or active agent is mixed with an aqueous solvent before being used.
  • solvents are water, saline and phosphate buffered saline.
  • the HPG nanocarrier may be injected into the treatment site. Local injection under imaging guidance would allow for exact tissue placement of the drug or therapeutic agent. Drugs or therapeutic agents that can be used to treat a disease or disorder can be used. For example, local delivery of hormones or other antiproliferative and antifibrotic drugs directly to a fibroid has the potential to decrease fibroid growth and size without systemic side effects.
  • the HPG nanocarrier may be injected into the fibroid through the abdomen or intravaginally. The HPG nanocarrier can be injected into a tumor in the breast or other location.
  • the type of drug or therapeutic agent that can be used in the delivery system is one that suitable for treatment of the particular disease or condition.
  • the therapeutic agent that can be used to prevent or treat uterine fibroids is selected from anti-fibrotic agents such as a Transforming Growth Factor beta (TGF ⁇ ) inhibitors.
  • TGF ⁇ inhibitors that can be used include P144, a fourteen amino acid long peptide that inactivates TGF ⁇ and has been shown to reduce soluble collagen content in skin fibrosis 2) SB-525334, a small molecule TGF ⁇ inhibitor with a polyaromatic-ring-structure shown to reduce fibroids in a rat model and CDB-4124, a selective progesterone receptor modulator (SPRM) thought to inhibit cell proliferation and fibrosis can also be used as the active agent.
  • SPRM selective progesterone receptor modulator
  • drugs that can be used are Tamoxifen, letrozole, anastrozole, exemestane, trastuzumab, doxorubicin, cyclophosphamide, paclitaxel, docetaxel, fulvestrant and camptothecin.
  • FIG. 14 illustrates a drug delivery system triggered to release drug in response to pH changes.
  • the system consists of: (1) HPG (core circle); (2) a pH responsive polymer link (black wavey line); and (3) a covalently attached drug.
  • HPG core circle
  • pH responsive polymer linkers derived from hydrazones, (37) orthoesters, (38) and acetals, (39-43) that are pH-sensitive (44). These linkers are protonated within the endosome (pH ⁇ 5.5-6) as protons are pumped over the endosome's plasma membrane but not out of the endosome (pH 7.4). Repulsions between charges contribute to endosomal swelling. The accumulation of positive charge in the endosome causes the influx of chlorine ions and water until the endosome ruptures, releasing the drug or therapeutic agent into the cytosol.
  • a non-limiting aspect of this invention is a polymeric carrier involving hyper branched polyglycerol (HPG)/ tri(ethylene glycol) divinyl ether/drug.
  • HPG hyper branched polyglycerol
  • FIG. 15 shows a synthesis to prepare HPG based drug delivery systems with pH sensitive linkers.
  • HPG is combined with tri(ethylene glycol) divinyl ether and Fmoc-ethanolamine.
  • Fmoc is cleaved to produce the unprotected terminal acid groups of the nanocarrier and of folic acid (squares) and fulvestrant drug (ovals) are covalently linked to nanocarrier.
  • HPG and tri(ethylene glycol) divinyl ether were copolymerized with Fmoc-serinol in anhydrous tetrahydrofuran (THF) (70% yield).
  • THF tetrahydrofuran
  • the protecting group was removed in piperidine (55% yield) prior to forming a covalent conjugate between the HPG-linker macromer, folic acid, and fulvestrant.
  • the latter reaction was followed by TLC over the course of three days to monitor extent of coupling.
  • 1 H NMR was performed on a 400 MHz in deuterated chloroform.
  • Another preparation could involve the following: a solution of the drug in anhydrous tetrahydrofuran (THF) added to a rigorously dried mixture of HPG and p-toluenesulfonic acid monohydrate (p-TSA) followed by a solution of tri(ethylene glycol) divinyl ether in anhydrous THF. Triethylamine will be added to complex the p-TSA catalyst and the mixture will be precipitated from hexane.
  • THF tetrahydrofuran
  • p-TSA p-toluenesulfonic acid monohydrate
  • This bifunctional pH-sensitive polymeric drug delivery system can also be used for local delivery of a drug or therapeutic agent.
  • this delivery system can be used to treat breast cancer.
  • the covalently attached folic acid will enhance the tumor targeting properties of the delivery system while increasing the solubility of fulvestrant and the feasibility of delivering this anti-cancer drug with a high payload.
  • the nanocarrier can target estrogen receptors with high affinity, by covalently linking folic acid, while releasing the native form of fulvestrant with full activity in response pH.
  • the one or more drugs or therapeutic agents are entrapped or attached into the liquogel or polymeric delivery system by a method known to those of skill in the art. In most cases, the drug or active agent(s) are non-covalently or hydrogen bonded to the liquogel.
  • the preparations normally contain about 1 to 99%, for example, about 5 to 70%, or from about 5 to about 30% by weight of an active ingredient.
  • the liquogels with the active compounds are administered at a therapeutically effective dosage sufficient to prevent or treat the disease or condition.
  • the liquogels may be administered in single or multiple doses.
  • Physiologically acceptable carriers can be used with liquogels, nanocarriers and pH polymeric delivery systems.
  • the dose of drug or therapeutic agent to be administered is selected to suit the desired effect.
  • Actual dosage levels of the drug or therapeutic agent in the compositions of this invention may be varied so as to obtain an amount of the drug or agent, which is effective to achieve the desired therapeutic response for a particular patient, without causing undue side effects or being toxic to the patient.
  • the dose may be determined by the time of administration, the rate of excretion of the particular compound being employed, the duration of the treatment, other drugs, compounds and/or materials used in combination with the particular compounds employed, the age, weight, condition, general health and prior medical history of the patient being treated, and like factors well known in the medical arts.
  • Glycidyl methacrylate (GMA), Acrylic acid (AAc), and N-isopropylacrylamide (NIPAAm) were purchased from Sigma-Aldrich (St. Louis, Mo.). AAc was purified immediately prior to use by passage through a basic alumina column. NIPAAm was recrystallized from hexane and vacuum dried.
  • BPO Benzoyl peroxide
  • stannous 2-ethylhexanoate [(Sn(Oct) 2 ],(3S)-cis-3,6 Dimethyl-1,4-dioxane,-2,5 dione (98%) (L-lactide)
  • DMAP 4-(N,N-diethylamino)pyridine
  • DMSO dimethyl sulfoxide
  • 1,4-dioxane methyl sulfoxide-d6 (99.9% atom D
  • anhydrous methanol, tetrahydrofuran (THF), and phosphate-buffered saline (PBS) were purchased from Fisher Scientific (Pittsburgh, Pa.). All polymerizations were carried out under a dry nitrogen atmosphere.
  • HPG-MA Methacrylated HPG was synthesized essentially as described by Oudshoorn et al. [26]. As shown in FIG. 1 , HPG-MA structures were prepared by functionalization of the HPG hydroxyl groups with glycidyl methacrylate.
  • HEMAPLA was synthesized by ring-opening polymerization of L-lactide initiated by HEMA with Sn(Oct) 2 as a catalyst ( FIG. 1 ). Equivalent molar ratios of HEMA and lactide were reacted at 110° C. in a nitrogen atmosphere for 1 h in the presence of catalyst Sn(Oct) 2 (121.5 mg, 1 mol % with respect to HEMA). The cooled reaction mixture was dissolved in THF and precipitated in ice cold water. The precipitate was dissolved in ethyl acetate and filtered to remove the remaining solids. The filtrate was dried over MgSO 4 and concentrated under reduced pressure to obtain purified HEMAPLA.
  • Poly(NIPAAm-co-HEMAPLA-co-AAc-co-HPG-MA) copolymers were synthesized by free radical polymerization ( FIG. 1 ). All glassware was dried at 120° C. for 12 h and flamed in a vacuum to eliminate moisture before use. A 5 wt % solution of monomers (NIPAAm and AAc) and macromers (HEMAPLA and HPG-MA) in 1,4-dioxane was introduced in a dry, preweighted round-bottom flask equipped with rubber septum and a magnetic stir bar.
  • MALDI-TOF-MS Matrix-Assisted Laser Desorption and Ionization Time-of-Flight Mass Spectrometry
  • An Applied Biosystems Voyager-DE PROmass spectrometer equipped with a nitrogen laser (337 nm) was used to collect mass spectra data. A 32 ns delay was applied before ions were accelerated to 25 kV and positive ions detected. Additionally, the grid and guide wire voltages were set at 90% and 0.15% of the applied acceleration voltage, respectively, to focus the beam of ions. Typically, 40 laser shots were averaged for each spectrum. 4′-hydroxyazobenzene-2-carboxylicacid (HABA) was used as the matrix.
  • HABA 4′-hydroxyazobenzene-2-carboxylicacid
  • the 1-100 mM matrix and analyte stock solutions were prepared as methanol solutions and were mixed in microcentrifuge tubes at matrix/analyte ratios varying from 1:1 to 1000:I, 1-2 ⁇ l of this solution was applied to the sample plate and air-dried.
  • Electrospray Ionization Time-of-Flight Mass Spectrometry (ESI-TOF MS).
  • ESI-TOF mass spectrometry was performed using a Micromass Q-tof micro (Waters Corp., Milford, Mass.). Samples were dissolved in methanol (0.1 or 1 mg mL ⁇ 1 , HPG or HPG-MA, respectively) and passed (0.5-1) ⁇ L min ⁇ 1 ) through a nano-ESI source operated in positive ion mode with a capillary voltage of 2-3 kV, sample cone voltage of 33 V, source temperature of 90° C. and desolvation temperature set at 180° C. Nitrogen was used as the nebulizing gas.
  • GPC Gel Permeation Chromatography
  • DSC′ Differential Scanning calorimetry
  • DMEM-FI2 Sterile phenol red free Dulbecco's modified Eagle's medium
  • FBS fetal bovine serum
  • antibiotics were obtained from Sigma.
  • Human uterine fibroid tissue was obtained from the existing IRB approved infrastructure of the Uterine Fibroid Tissue Repository which is part of Duke University School of Medicine Research Foundation's tissue banking operation.
  • the fibroid cells were isolated by enzymatic digestion of fibroid tissue obtained at hysterectomy and cultured in DMEM-F 12 medium supplemented with antibiotics, antimycotic and 10% FBS. In general, third passage cells were used in the cytotoxicity studies. Polymer solutions (16.5 wt % in PBS) were filtered through 0.22 ⁇ m filters (VWR 28145-501 polyethersulfone sterile filters). Cells were plated in 24-well plates and incubated for 24-48 h until 80% confluent. Then, cells were washed with prewarmed PBS and incubated with fresh media and HPG containing copolymer hydrogel or HPG macromer (0.09-90 ⁇ g/mL) for 72 h. Each concentration was measured four times.
  • Cytotoxicity was assessed with a methyl tetrazolium salt (MTS) assay kit (Promega, CellTiter96® AQueous Non-Radioactive Cell Proliferation Assay) following the protocol provided by the manufacturer and a 3 h incubation time. Results are expressed as percent viability relative to control cells grown in media alone (100% viability). The assay was repeated with fibroid cells from a different patient. Microscopy was used to help verify assay results.
  • MTS methyl tetrazolium salt
  • thermoresponsive nature of a liquogel according to the invention in 16.5 wt % phosphate buffered saline (PBS) solution was investigated to determine the lower critical solubility temperature (LCST) at which gelling begins to occur.
  • LCST lower critical solubility temperature
  • the LCST was also investigated by measurement of the liquogel solution optical absorption as a function of temperature using UV/Vis spectroscopy and differential scanning calorimetry differential scanning calorimetry (DSC). Scanning the liquogel solution at 500 nm over the temperature range of 0° C. to 43.3° C. (see FIG. 19 ), the temperature at which the optical absorption rapidly transitions (the LCST) occurs around 35° C. This was also confirmed by a transition at 35.7° C. (see FIG. 20 ). The heating rate for DSC was 10° C./min.
  • the cytotoxicity of the delivery system (0.09-90 ⁇ g/mL) was assessed using fibroid cells.
  • the cells were isolated by enzymatic digestion of fibroid tissue obtained at hysterectomy and cultured in the presence of 10% serum until 80% confluent.
  • the HPGs are less than 3,000 g/mole. Glass transition temperatures are in the sub-ambient range. Viscosity of the polymers were linearly related to concentration in the range between 0.61 and 71.4 g/L.
  • the HPG polymers were derivatized with a linker that was 3:1 methacrylate to lactide and subsequently treated with 60% isopropylacrylamide to afford the final delivery system. After 60 h incubation of the delivery system with primary fibroid cells at 37° C., there was no significant cell death.
  • FIGS. 16 and 17 The cytotoxic effects of a pH triggered delivery system of fulvestrant, camptothecin or nanocarrier on MCF-7 cells is shown in FIGS. 16 and 17 . Comparison of cytotoxic effects by Fulvestrant, Camptothecin and Nanocarrier.

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