EP0993483A1 - Konjugat aus polyäthylenglykol und chitosan - Google Patents

Konjugat aus polyäthylenglykol und chitosan

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Publication number
EP0993483A1
EP0993483A1 EP98932368A EP98932368A EP0993483A1 EP 0993483 A1 EP0993483 A1 EP 0993483A1 EP 98932368 A EP98932368 A EP 98932368A EP 98932368 A EP98932368 A EP 98932368A EP 0993483 A1 EP0993483 A1 EP 0993483A1
Authority
EP
European Patent Office
Prior art keywords
chitosan
conjugate
peg
group
polyethylene glycol
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
EP98932368A
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English (en)
French (fr)
Inventor
Stanley Stewart Davis
Wu Lin
Fabio Bignotti
Paolo Ferruti
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Kyowa Kirin Services Ltd
Original Assignee
West Pharmaceutical Services Drug Delivery and Clinical Research Center Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by West Pharmaceutical Services Drug Delivery and Clinical Research Center Ltd filed Critical West Pharmaceutical Services Drug Delivery and Clinical Research Center Ltd
Priority to EP02079756A priority Critical patent/EP1304346A3/de
Publication of EP0993483A1 publication Critical patent/EP0993483A1/de
Ceased legal-status Critical Current

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Classifications

    • 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
    • A61K9/48—Preparations in capsules, e.g. of gelatin, of chocolate
    • A61K9/50—Microcapsules having a gas, liquid or semi-solid filling; Solid microparticles or pellets surrounded by a distinct coating layer, e.g. coated microspheres, coated drug crystals
    • A61K9/51—Nanocapsules; Nanoparticles
    • A61K9/5107—Excipients; Inactive ingredients
    • A61K9/513—Organic macromolecular compounds; Dendrimers
    • A61K9/5161—Polysaccharides, e.g. alginate, chitosan, cellulose derivatives; Cyclodextrin
    • 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
    • A61K47/61—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 the organic macromolecular compound being a polysaccharide or a derivative thereof
    • 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
    • A61K9/14—Particulate form, e.g. powders, Processes for size reducing of pure drugs or the resulting products, Pure drug nanoparticles
    • A61K9/16—Agglomerates; Granulates; Microbeadlets ; Microspheres; Pellets; Solid products obtained by spray drying, spray freeze drying, spray congealing,(multiple) emulsion solvent evaporation or extraction
    • A61K9/1605—Excipients; Inactive ingredients
    • A61K9/1629—Organic macromolecular compounds
    • A61K9/1652—Polysaccharides, e.g. alginate, cellulose derivatives; Cyclodextrin
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P31/00—Antiinfectives, i.e. antibiotics, antiseptics, chemotherapeutics
    • A61P31/04—Antibacterial agents
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P31/00—Antiinfectives, i.e. antibiotics, antiseptics, chemotherapeutics
    • A61P31/10—Antimycotics
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P31/00—Antiinfectives, i.e. antibiotics, antiseptics, chemotherapeutics
    • A61P31/12—Antivirals
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08B—POLYSACCHARIDES; DERIVATIVES THEREOF
    • C08B37/00—Preparation of polysaccharides not provided for in groups C08B1/00 - C08B35/00; Derivatives thereof
    • C08B37/0006—Homoglycans, i.e. polysaccharides having a main chain consisting of one single sugar, e.g. colominic acid
    • C08B37/0024—Homoglycans, i.e. polysaccharides having a main chain consisting of one single sugar, e.g. colominic acid beta-D-Glucans; (beta-1,3)-D-Glucans, e.g. paramylon, coriolan, sclerotan, pachyman, callose, scleroglucan, schizophyllan, laminaran, lentinan or curdlan; (beta-1,6)-D-Glucans, e.g. pustulan; (beta-1,4)-D-Glucans; (beta-1,3)(beta-1,4)-D-Glucans, e.g. lichenan; Derivatives thereof
    • C08B37/0027—2-Acetamido-2-deoxy-beta-glucans; Derivatives thereof
    • C08B37/003—Chitin, i.e. 2-acetamido-2-deoxy-(beta-1,4)-D-glucan or N-acetyl-beta-1,4-D-glucosamine; Chitosan, i.e. deacetylated product of chitin or (beta-1,4)-D-glucosamine; Derivatives thereof
    • 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
    • C08G81/00—Macromolecular compounds obtained by interreacting polymers in the absence of monomers, e.g. block polymers
    • 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
    • A61K9/0034—Urogenital system, e.g. vagina, uterus, cervix, penis, scrotum, urethra, bladder; Personal lubricants
    • 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
    • A61K9/0043—Nose
    • 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
    • A61K9/0048—Eye, e.g. artificial tears

Definitions

  • the present invention concerns a novel conjugate between chitosan and polyethylene glycol (PEG-chitosan conjugate) that may be used in biomedical applications and particularly in the fields of antisense and gene therapy, drug absorption enhancement and targeting using particulate carriers.
  • PEG-chitosan conjugate polyethylene glycol
  • Chitosan is a biopolymer material that is derived from chitin. Chemically, chitosan is a polyglucosamine, a linear polymer of ⁇ (1 ⁇ 4) linked 2- amino-2-deoxy-D glucopyranose. Chitosan can be derived from chitin through a process of deacetylation. While chitin is insoluble, chitosan in its salt form can demonstrate acceptable solubilities at pH's below 7.0. Chitosan is believed to be non-toxic and can be administered to mucosal surfaces.
  • chitosan Various applications for chitosan have been described in the prior art including its use in wound healing, controlled drug delivery, as a bioadhesive material and to improve the solubility of poorly soluble compounds. More recently it has been discovered that chitosan, because of its positive charge, can have an effect upon the tight junctions between cells and it has been shown to be effective in improving the paracellular transport of drugs, particularly those that are polar in character. A detailed review of the medical applications of chitosan can be found in the article by Hon in Polysaccharides in Medical Applications, Ed. Dumitni, S. , Dekker, New York, 1996, pages 631-649.
  • Chitosan can be obtained in a range of molecular weights from oligomeric materials containing a few units of glucosamine through to higher molecular weight materials of more than 200,000 Daltons. In pharmaceutical applications, the higher molecular weights from 50,000 to 500,000 Daltons are normally preferred. Chitosan can also be obtained in different degrees of deacetylation, but the materials that have a deacetylation of between 60 and 90% are normally preferred. Chitosan can be obtained from various sources, including shell fish, fungi and other materials and a pharmaceutical grade of chitosan is available from Pronova Limited of Norway.
  • chitosan carries a positive charge, it can be used to interact with negatively charged surfaces as well as with other negatively charged materials including pharmaceuticals. Chitosan can also be used to modify me surfaces of carrier particles. For example, liposomes have been described where chitosan has been bound to their surfaces (Takeuchiu et al. (1994), Chem. Pharm. Bull. 42 1954-1956).
  • Chitosan can be employed in solution, as a powder material, in microspheres or can be used as a film-forming agent.
  • N-acylchitosans N-carboxyalkyl chitosans
  • N-carboxyacyl chitosans O-carboxyalkyl chitosans.
  • chitosan/poly(ethylene oxide) polymer networks have been described by Patel and Amiji (Polymer Preprints, ACS Division of Polymer Chem. 1994, 352, 403 and ACS Symposium Series, 627, Hydrogels and biodegradable polymers for bioapplications, page 209).
  • the hydrogel was prepared by dissolving chitosan in acetic acid to produce a solution.
  • Polyethylene glycol having a molecular weight of 10 kilodaltons (kD) to 1 megadalton (mD) was dissolved in acetic acid and the resulting solution added to the chitosan solution to prepare a physical blend.
  • Chitosan/poly ether hydrogels have also been described by Peng et al. (J. Polymer Science Part A, Polymer Chemistry 32, 591-596, 1994). Here also the chitosan and a polyether (polyoxypropylene glycol) were mixed at acidic pH and then cross-linked with glutaraldehyde.
  • PCT/GB95/00686 describes microspheres for biomedical uses which contain a substantially spherical core particle of a non-water soluble polymer and an outer surface consisting substantially of a water soluble polymer.
  • the water soluble polymer is conjugated to polyethylene glycol and the non-water soluble core particle is attached to the water soluble polymer by the polyethylene glycol (PEG) moiety.
  • PEG polyethylene glycol
  • the patent application describes detailed examples using PEG-dextran conjugates. Chitosan is also mentioned as a water soluble polymer in the preparation of such microspheres, but no PEG-chitosan conjugates were actually prepared. Moreover, there was no disclosure of particles in which the PEG moieties were pendant and exposed to the external environment.
  • Ouchi et al. describes the preparation of PEG-chitosan by acylating the amino groups on the polysaccharide with the monomethyl ether of PEG as the carboxylate and then covalently bonding this compound to 5- fluorouracil (5-Fu) to produce a material for cancer chemotherapy (Ouchi et al. J. Macromol. Sci. Chem. , A28, 959, 1991).
  • the active ester method was used to prepare the PEG-chitosan products in Ouchi et al and the chitosan was a low molecular weight material having a degree of polymerization of 30 which had been produced by acid treatment of chitosan.
  • the 5-Fu attached to the end of the PEG chain in the PEG- chitosan conjugate and the resulting soluble complex was administered by injection.
  • Ouchi et al did not consider that an unmodified PEG-chitosan conjugate could be used for the delivery of anionic macromolecular drugs, such as antisense oligonucleotides and DNA (nucleic acids), nor did they consider that the unmodified conjugate could be used as a coating agent in the field of colloidal drug delivery through the interaction of the positively charged chitosan with negatively charged surfaces and negatively charged colloidal particles. Furthermore, there was no suggestion in Ouchi et al that such positively charged PEG-chitosan conjugates might be used to provide increased absorption of drugs across mucosal surfaces through their interaction with negatively charged mucus or negatively charged surfaces of epithelial cells.
  • PEG-chitosan conjugate may be interacted with anionic materials, such as antisense oligonucleotides and DNA (nucleic acid), and may be used to enhance drug absorption or for targeting using particulate carriers.
  • a polymer conjugate comprising a chitosan moiety or a derivative thereof and a polyethylene glycol (PEG) moiety or a derivative thereof which are bonded together via the amino function on the chitosan by the use of an activated chitosan species.
  • PEG polyethylene glycol
  • a polymer conjugate comprising a chitosan moiety or a derivative thereof and a polyethylene glycol (PEG) moiety or a derivative thereof which are bonded together, the chitosan portion of the conjugate having a molecular weight in the range of from 10 kilodalton to 1000 kilodalton.
  • PEG polyethylene glycol
  • a composition comprising a complex formed between a PEG-chitosan conjugate and a therapeutic agent selected from the group consisting of oligonucleotides and nucleic acids.
  • the PEG-chitosan conjugate comprises a chitosan moiety or a derivative thereof and a polyethylene glycol moiety or a derivative thereof which are bonded together.
  • compositions comprising a polymer conjugate in the form of chitosan covalently attached to polyethylene glycol that can be used in drug delivery.
  • Chitosan is a polymeric material comprising repeating monomeric units having the formula:
  • p is an integer and represents the number of monomeric units in the chitosan chain, i.e. the degree of polymerisation.
  • chitosan will generally contain a proportion of the monomeric units found in chitin. This proportion will depend on the degree of deacetylation. Typically, the degree of deacetylation is in the range of from 99% to 10% , and is preferably in the range of from 90% to 20% , more preferably in the range of from 85% to 40% .
  • the polyethylene glycol moiety may well increase the solubility of the PEG-chitosan conjugate or, more importantly, the solubility of a PEG-chitosan conjugate that has been complexed with a therapeutic agent such as a drug or a nucleic acid.
  • the conversion of the amino (NH 2 ) functions within chitosan to the PEGylated form can be within the range of 1 to 99% . However, it is preferred that the conversion is in the range 10 to 90% and more preferably in the range 10 to 50% .
  • the PEG-chitosan conjugate should have a residual positive charge.
  • the PEG-chitosan conjugate should retain sufficient positive charge to allow it to interact with negatively charged (anionic) materials such as oligonucleotides or nucleic acids (DNA) and provide for compaction of the anionic species.
  • anionic materials such as oligonucleotides or nucleic acids (DNA)
  • compaction we mean reduction in particle size as measured by a techmque such as atomic force microscopy or photon correlation spectroscopy.
  • the PEG-chitosan conjugate should have sufficient positive charge to allow it to interact with negatively charged colloidal carriers intended for drug delivery, such as emulsions, liposomes, microspheres and microcapsules as well as negatively charged drug particles of a size less than 100 microns.
  • negatively charged colloidal carriers intended for drug delivery such as emulsions, liposomes, microspheres and microcapsules as well as negatively charged drug particles of a size less than 100 microns.
  • the PEG-chitosan conjugate should have a sufficient positive charge to interact with mucin or epithelial cells.
  • a positive charge on the PEG-chitosan conjugate can be evaluated by studying the interaction of the conjugate with a negatively charged polymer so that a polyelectrolyte complex is formed as described by Terayama in J. Polymer Science, 8 243 (1952).
  • the PEG- chitosan conjugate can be absorbed onto a polymer particle such as a polystyrene microsphere of about 1 micron in size and the charge on the system evaluated by particle microelectrophoresis using an apparatus such as the Malvern Zeta Sizer.
  • a sufficient positive charge for interacting with the above described anionic species we typically mean a charge, measured as the Zeta potential, of at least lmV and preferably in the range of from 1 to 200 mV at pH 7.4 in ImM HEPES buffer.
  • a charge measured as the Zeta potential, of at least lmV and preferably in the range of from 1 to 200 mV at pH 7.4 in ImM HEPES buffer.
  • the PEG-chitosan conjugate has sufficient positive charge, not more than 90% of the amine groups in chitosan should be PEGylated.
  • the chitosans used for the preparation of the PEG-chitosan conjugates can have a molecular weight in the range of from 10 kD to 1000 kD, but more preferably will have a molecular weight in the range of from 10 kD to 500 kD, e.g. 20 kD to 500 kD, particularly from 30 kD to 300 kD, e.g. between 100 kD and 300 kD.
  • the degree of polymerisation of the chitosans used in d e preparation of the PEG-chitosan conjugates is typically in the range of from 50 to 6000, preferably in the range of from 100 to 3000 and particularly in the range of from 150 to 2000.
  • the polyethylene glycol content of the PEG-chitosan conjugate is typically from 1 to 50% on a weight basis, preferably from 5 to 20% .
  • Chitosans that have been derivatised by modification of the hydroxyl function could also be used.
  • Such derivatives include O-acylated and alkylated materials such as O-benzoyl chitosan and O-sulphated chitosans as detailed in Chitin Chemistry, A F Roberts, Macmillan, 1992, p. 166.
  • the chitosan moiety in the PEG-chitosan conjugate may be a chitosan derivative and by the term chitosan we are also intending to include derivatives thereof.
  • the chitosan is unmodified.
  • the PEG-chitosan conjugate can be used to modify surfaces that are negatively charged or to interact with or form complexes with negatively charged molecules such as DNA, DNA plasmids or nucleic acids.
  • the positively charged chitosan can bind strongly to such a negative surface and in doing so will expose the PEG group to the external environment.
  • Such an exposed polyethylene glycol group will tend to provide for steric stabilization. This can lead to an improved stability, e.g. for a colloidal dispersion, but can also have important biological implications in minimising the uptake of proteins to the surface of a particle, e.g. when the particle is injected into the bloodstream or administered to a body compartment.
  • the PEG-chitosan conjugate or adduct may be prepared using techniques known in the art for bonding PEG moieties to polymeric materials.
  • the PEG-chitosan conjugate is prepared by a process comprising the steps of:
  • a PEG derivative we mean a modified polyethylene glycol, for example polyethylene glycol in which one or both of the terminal hydroxyl groups has been previously modified.
  • Suitable PEG derivatives include alkoxy PEGs in which a terminal hydroxyl group(s) has been converted into an alkoxy group, i.e. a group having the formula RO- in which R is alkyl.
  • Preferred PEG derivatives are those comprising a single alkoxy terminal group.
  • Preferred alkoxy groups are C 1-4 alkoxy, such as methoxy.
  • the preparation of a PEG or PEG derivative carrying an acrylic ester group can be carried out by reacting a PEG or PEG derivative containing a hydroxyl function with acryloyl chloride.
  • the preparation of a PEG or PEG derivative carrying an acrylic thioester group can be carried out by reacting a PEG or PEG derivative containing a sulfhydryl group with acryloyl chloride.
  • the preparation of a PEG or PEG derivative carrying an acrylamido group can be performed by reacting PEG or a PEG derivative containing one primary or secondary amine function with acryloyl chloride.
  • the activated PEG or PEG derivative can be characterized by Gel Permeation Chromatography (GPC), FT-IR and UV spectroscopy.
  • the degree of activation can be determined by end-group titration which involves adding an excess of 2- mercaptoethanol and titrating excess thiol with a calibrated KI/I 2 solution, or by UV spectroscopy, after calibration with a standard acrylamide or acrylic ester such as N-acryloylmorpholine or tetraethyleneglycol diacrylate, conducted at 233 nm.
  • Activated PEGs or activated PEG derivatives can be stored for several months at T ⁇ 4°C in the presence of a desiccant.
  • a radical inhibitor such as 4-methoxyphenol may also be added to prevent radical polymerization.
  • the reaction of the activated PEG or activated PEG derivative with chitosan is preferably performed in an aqueous media. Alcohols or alcohol/ water mixtures can also be used.
  • the pH of the reaction medium is preferably at least 8 and typically in the range 8 to 9.
  • the preferred reaction temperature is between 20 and 30°C and typical reaction times are 12-48 hours.
  • the occurrence of vinyl radical polymerization is inhibited by conducting the reaction under inert atmosphere, in the dark and in the presence of a radical inhibitor such as 4-methoxyphenol.
  • the molecular weight of the PEG or the PEG portion in the case of a PEG derivative is typically between 1 and 30 kD, preferably between 2 and 20 kD and more preferably between 2 and 10 kD.
  • Recovery of the PEG-chitosan conjugate or adduct is generally carried out by ultrafiltration in water or by evaporating the reaction solvent and extracting the crude material with a new solvent.
  • the purity of the adduct can be assessed by GPC, FT-IR, NMR and UV spectroscopy. Checking for residual activated PEG or activated PEG derivative is usually performed spectrophotometrically at 233 nm.
  • the method can have advantages over other PEGylation processes known in the art because: (a) free base is the species reacting with the double bond so that the reaction rate tends to increase with increase in pH, i.e. with increasing the concentration of free base; (b) no by-product is produced during the reaction; and
  • the PEG-chitosan conjugate is prepared by a process which involves activating the chitosan rather than the PEG or PEG derivative.
  • Activation of the chitosan is preferably achieved by adding a large excess of a bis(acrylamide) to the chitosan.
  • the excess bis(acrylamide) is preferably removed and the activated chitosan reacted with a PEG or PEG derivative, preferably a monofunctional PEG carrying a hydroxyl, sulfhydryl or primary or secondary amino group.
  • Grafting bis(acrylamide) to chitosan may make the chitosan more soluble or at least more swellable at pH > 8 and, moreover, may provide for reactive functions which are more accessible than the original NH 2 groups which are close to the main polymer chain. Furthermore, activating the chitosan with bis(acrylamide) may allow higher amounts of PEG to be grafted or bonded to the chitosan.
  • the PEG-chitosan conjugates prepared by the above described methods comprise a chitosan moiety and a PEG moiety which are joined together through a linking group or coupling moiety having the formula -CH 2 CH 2 C(O)-R 2 -X-.
  • the linking group is bonded to the amino nitrogen on the chitosan moiety via the -CH 2 CH 2 - group and to the PEG moiety via the X group.
  • R 2 is a bond or a divalent organic group
  • X is oxygen, sulphur or -NR 3 -
  • R 3 is H or an organic group such as alkyl, e.g. C 1-10 alkyl.
  • Cm is the remainder of the monomeric unit making up the chitosan moiety or a derivative of such a monomeric unit;
  • p is an integer and represents the number of monomeric units of formula -Cm-NR' 2 - in the chitosan moiety, each R is independently H or a group -A-PEG providing that at least a proportion of the R groups are -A-PEG;
  • each PEG is independently a polyethylene glycol moiety or a derivative thereof;
  • each A is independently a linking group having the formula -CH 2 CH 2 -C(O)-R -X- which is bonded to the amino nitrogen on the chitosan moiety via the -CH 2 CH 2 - group and to the PEG moiety via the X group;
  • R is a bond or a divalent organic group
  • X is oxygen, sulphur or -NR 3 -;
  • R 3 is H or an organic group, or a physiologically acceptable derivative thereof.
  • Cm as the remainder of the monomeric unit making up the chitosan moiety we are referring to a group which together with the -NH 2 group makes up the full monomeric unit found in chitosan.
  • the complete monomeric unit itself has the formula Cm-NH 2 .
  • a derivative of such a monomeric unit we are referring to physiologically acceptable derivatives in which a hydroxyl group has been modified. Suitable derivatives include O-acylated and alkylated materials such as O-benzoyl chitosan and O-sulphated chitosans as detailed in Chitin Chemistry, A F Roberts, Macmillan, 1992, p. 166.
  • Cm is preferably the remainder of the monomeric unit making up chitosan.
  • p is preferably an integer in the range of from 50 to 6000, more preferably in the range of from 100 to 3000 and particularly in the range of from 150 to 2000.
  • PEG is preferably a modified polyethylene glycol moiety having the formula R - - OCH 2 CH 2 -) endeavour— where R 4 is an aliphatic, alicyclic or aromatic hydrocarbon group, such as an alkyl, cycloalkyl, aryl or aralkyl group, and n is an integer.
  • R 4 is alkyl, more preferably C 1-10 alkyl, e.g. C 1-4 alkyl, and especially methyl, n is suitably in the range of from 10 to 1000 and is preferably in the range of from 10 to 100.
  • R 2 is preferably a bond or a divalent organic group having the formula:
  • R 5 is a divalent organic group which is bonded to the carbonyl (C(O)) group of linking group A.
  • R 5 is bonded to the carbonyl group in Formula II above and the carbonyl group of linking group A via nitrogen atoms. More preferably, R 5 is a group having the formula:
  • R is independently a linear or branched C alkyl chain
  • R is a divalent organic group, particularly a linear or branched C alkylene chain
  • R , R , R and R 11 are each independently H or a linear or branched C 1-3 alkyl chain.
  • X is preferably oxygen or -NR 3 -.
  • Suitable organic groups for R 3 include hydrocarbon groups such as alkyl, e.g. C 1-10 alkyl.
  • R 3 is H.
  • the conjugate prepared by activating the aminated monomethoxy-PEG with an acrylamido group and reacting the activated compound with chitosan has the structure:
  • R 5 is a group having the formula:
  • R is hydrogen or a second PEG chain bound to chitosan in the same way, that is through an acrylamide (method 1) or a bis(acrylamide) (method 2) coupling moiety;
  • R 6 is a linear or branched C 1-4 alkyl chain;
  • R is a linear or branched C alkylene chain
  • R R 8 ,, RR 9 ,, RR 10 aanndd R are each mdependently H or a linear or branched C 1-3 alkyl chain
  • particulate materials in the form of emulsions, liposomes, microparticles, microcapsules and nanoparticles are employed.
  • Such particles often carry a net negative charge. It is often important to be able to modify this negative charge through the process of surface modification.
  • the properties of liposomes can be modified by the adsorption of chitosan. It is now possible through the present invention to modify such particles with the PEG-chitosan system so that the particle carries not only a positive charge but a polyethylene glycol group that will provide for steric stabilisation and beneficial biological and physical properties.
  • a PEG-chitosan conjugate can be used to compact plasmid DNA.
  • the compacts produced should have enhanced solubility and beneficial properties for the interaction with cells and the subsequent expression of the gene product.
  • the PEG-chitosan material described herein could be further modified by the attachment of targeting ligands to the hydroxyl and unmodified amino functions in order to achieve site specific targeting.
  • targeting ligands can take the form of sugars and proteins. The latter can include monoclonal antibodies and fragments thereof.
  • the sugars include mannose, fucose and galactose.
  • sugar will be dictated by the nature of the tissue or cell that is identified as the target site.
  • a complex of PEG-chitosan with DNA could be targeted to the liver by the covalent attachment of a triantennary galactose moiety.
  • Figure 1 is a graph showing the effect of added Na 2 SO 4 on the properties of polystyrene particles (190 nm) coated with chitosan or PEG-chitosan.
  • Figure 2 is a graph showing the effect of increasing chitosan and PEG- chitosan concentrations on the size of the complexes formed between these materials and DNA.
  • Figure 3 is a graph showing the effect of adding chitosan and PEG- chitosan on the fluorescence of a DNA/ethidium bromide complex.
  • Monomethoxy-PEG 1900 (12.26 g, 6.45 mmol) was dissolved in "alcohol- free" CHC1 3 (60 ml). The solution was dried overnight over calcium hydride, which was then removed by filtration. l, l '-carbonyldiimidazole of 97 % purity (2.16 g, 12.9 mmol) was then added and the resulting solution allowed to stand at 30°C for 30 min after which cold water was added (10 ml) and the mixture stirred for 10 min. After separation of the phases, anhydrous piperazine (0.56 g, 12.9 mmol) was added to the organic phase and allowed to react for 20 hours at 25 °C.
  • the solution was then diluted with CHC1 3 (100 ml), extracted with water (5 x 30 ml), dried with Na 2 S0 4 , filtered, concentrated in vacuo to 60 ml and finally poured into diethyl ether at about 10°C.
  • the powder which precipitated out was collected by filtration and dried to constant weight at 0.1 torr. The yield was 10.64 g.
  • the GPC chromatogram exhibited one peak with retention time 1030 sec.
  • the FT-IR spectrum showed a band in the urethane region at 1703 cm- 1 .
  • the molecular weight, determined by potentiometric titration with 0.1 M HC1, was 2190.
  • the reaction mixture was then diluted with CHC1 3 to 150 ml and washed in a separatory funnel with 5 % KNO 3 (2 x 30 ml) and water (1 x 30 ml). After drying with Na 2 SO 4 and filtering, the volume was reduced to about 50 ml by evaporating most of the CHC1 3 in vacuo.
  • the solution was then diluted with diethyl ether (200 ml).
  • the product which precipitated out was collected by filtration and dried to constant weight at 0.1 torr. The yield was 6.05 g.
  • the GPC chromatogram exhibited one peak with retention time 1020 sec.
  • the FT- IR spectrum was very similar to that of starting MPEG-PF, but showed an amidic band at 1649 cm "1 .
  • Monomethoxy-PEG piperazinyl formate (MPEG-PF) was prepared using exactly the same techmque as described in Example 1 (part A) above, but using monomethoxy-PEG 550 (3.55 g, 6.45 mmol) instead of monomethoxy-PEG 1900. The yield was 5.18 g.
  • MPEG-PF was then added (3.25 g, 5.0 meq) to the aqueous phase and allowed to react for 10 days at 25°C in the dark and under a nitrogen atmosphere, the pH being adjusted to 7 by the addition of isobutyric acid.
  • the solution was freeze dried, extracted in a Soxhlet apparatus with a 3: 1 diethyl ether/CH 2 Cl 2 mixmre and dried in vacuo to constant weight. The yield was 0.38 g.
  • Example 3 The physical adsorption of PEG-chitosan to colloidal particles
  • polystyrene nanoparticles were used as a model system.
  • the polystyrene particles were purchased from IDC Spheres, Interfacial Dynamics Corp. USA. The particles were stabilised with negative sulphate groups.
  • Samples of the polystyrene particles were coated with either chitosan (SeaCure CL 113) or with a PEG-chitosan conjugate.
  • the PEG-chitosan conjugate was prepared as in Example 1 from chitosan SeaCure CL 113 obtained from Pronova Ltd. , Norway.
  • the chitosan had an average molecular weight of about 50 kD and an intrinsic viscosity of 153 ml/g. About 12% of the amino functions were acetylated (88 % deacetylated).
  • the average molecular weight of the attached PEG was 2100 and the degree of PEGylation 15 % .
  • chitosan and PEG-chitosan conjugate were added to 10 ml glass test tubes (0-100 ⁇ g) together with 1.5 ml of purified water. 0.5 ml of a 0.1 % suspension of polystyrene particles was then added (representing 500 ⁇ g of particles) drop wise with vigorous stirring for 2 hours. The effect of the adsorbed chitosan and PEG-chitosan on the zeta potential of the particles was measured using a Malvern Zeta Sizer (Mark IV), Malvern Instruments, UK, at pH 7.4 in 1 mM HEPES buffer.
  • the uncoated polystyrene particles carried a net negative charge of -50 mV.
  • the addition of chitosan or PEG-chitosan gave rise to a rapid charge reversal as measured using a Zeta Sizer so that the polystyrene particles carried a net positive charge of +20 mV upon the addition of 100 ⁇ g of chitosan or PEG-chitosan to 500 ⁇ g of the polystyrene particles suspended in 2 ml of an aqueous buffer solution.
  • both chitosan and PEG- chitosan have the ability to strongly adsorb to a negatively charged colloidal particle and reverse the charge.
  • the ability of coated particles to withstand flocculation was measured by studying the effect of added sodium sulphate (Na 2 SO 4 ).
  • Na 2 SO 4 induced flocculation of coated polystyrene particles (190 nm) was measured using a weight ratio of chitosan or PEG-chitosan to particles of 1 :5.
  • the optical density (OD) at 600 nm was used to assess the properties of the coated particles.
  • Figure 1 shows the effect of added Na 2 SO 4 on the properties of polystyrene particles (190 nm) coated with chitosan and PEG-chitosan, respectively. (0.2 ml of polymer coated particles (10 ⁇ g chitosan or PEG- chitosan/50 ⁇ g polystyrene)) in 0-1.6 M Na 2 SO 4 solution). Both the chitosan and PEG-chitosan coated particles were affected by low concentrations of Na 2 S0 4 (the uncoated particles required at least 0.25 M Na 2 SO 4 to commence a change in OD).
  • chitosan and PEG-chitosan can be measured by the Na 2 SO 4 induced flocculation of solutions of the two cationic polymers.
  • Example 3 were suspended in 0.4 ml of water, 0.1 mg and 1 mg. Then Na 2 SO 4 was added to induce flocculation. The degree of flocculation was measured as previously as the OD at 600 nm. At an Na 2 SO 4 concentration of 0.2 M the following OD figures were obtained.
  • a model plasmid material was employed. This is in the form of the plasmid CMV-CAT that encodes for chloramphemcol acetyl transferase (CAT), a so-called reporter gene system.
  • CAT chloramphemcol acetyl transferase
  • the p-CAT material was obtained from Gene Medicine Inc., Houston, USA.
  • a plasmid and a cationic polymer can be followed by a variety of techniques including the following:
  • Example 6 a number of the above techniques were used to illustrate the differences between compaction using chitosan and compaction with the PEG-chitosan system.
  • the PEG- chitosan was prepared from a sample of SeaCure CL 113, where about 12% of the amino functions were acetylated. The method described in Example 1 was employed. The average molecular weight of the PEG bound to the chitosan was 2100. Unmodified chitosan SeaCure CL 113 was used as a control. Photon Correlation Spectroscopy and Zeta Potential Measurements:
  • the pCAT-DNA/chitosan or the pCAT-DNA/PEG-chitosan complexes were prepared in the following way to give different pCAT-DNA/polymer ratios.
  • chitosan and PEG-chitosan complexes and their zeta potentials in water and 1 mM HEPES buffer at pH 7.4 were determined using a Malvern S4700 PCS and a Malvern Zeta Sizer (Mark IV), respectively. It can be seen from Table 1 that the surface properties of the chitosan-DNA complex are different from the properties of the DNA complex made with the conjugate that is the subject of the present invention. It is believed that the improved solubility of this complex and the difference in particle charge is beneficial for a biological response. Interestingly, the complexes formed by chitosan and PEG-chitosan with DNA produced small sized nanoparticles of about 140 nm as measured by PCS.
  • a more detailed smdy of die interaction between a selected plasmid DNA material (CMV-CAT) and PEG-chitosan was carried out.
  • the plasmid was at a concentration of 1 mg/ml and the PEG- chitosan at 500 microgram/ml.
  • the PEG-chitosan was centrifuged at 10,000 rpm for 10 mins to remove any particulate from the solution.
  • results show the importance of the amount of PEG-chitosan added for complexing DNA with the polymer.
  • the results also show that the presence of the PEG function does not greatly affect the condensing properties of chitosan.
  • the greater size of the PEG chitosan complexes as compared to the chitosan complexes is considered to be due to the PEG group providing a steric barrier.
  • the decrease in fluorescence was measured as follows.
  • the example shows that the PEGylation of chitosan does not substantially affect the ability of chitosan to intereact strongly with plasmid DNA.
  • the method involved injecting a solution of chitosan or PEG-chitosan from a precision syringe into two DNA solutions at specified time intervals. 2.0 ml of a DNA solution containing 81.1 ⁇ g pDNA was used for each experiment and 0.35 ml of the chitosan and PEG-chitosan solutions were added as 35 separate 10 ⁇ l injections. The time interval between two injections was about 10 minutes.
  • the mean MW of plasmid DNA per a phosphate group was calculated as 308.8 Daltons.
  • the mean MW of chitosan (87% of deacetylation) per an amino group was calculated as 227.9 Daltons.
  • the mean MW of PEG-chitosan (15% of PEG 2100 w/w. , 87% deacetylation) per an amino group was calculated as being 273.9 Daltons.
  • the invention provides for the use of a PEG-chitosan material in drug delivery.
  • the PEG moiety may confer advantageous properties, particularly in relation to the physicochemical properties of the chitosan material and the interaction of chitosan with surfaces, particles and DNA where it will be possible to provide a combination of positive charge (from those NH 2 groups of the chitosan that have not been PEGylated) and die PEG-modified amino groups.
  • PEG-chitosan may also improve the paracellular transport of drugs as already described for chitosan itself.
  • the PEG-chitosan conjugate may be used to form controlled release materials in the form of microspheres, microparticles and matrices for administration to the gastrointestinal tract, to the vaginal cavity, to the nose and to die buccal cavity.
  • the conjugate could also be used for the administration of drugs to the eye wherein the chitosan would bind preferably to the mucus.
  • Such an agent may also be used for the treatment of dry eye syndrome, where the PEG moiety provides a steric stabilisation and lubricating effect.
  • These products could be delivered to the eye using eye-drop systems known in the art.
  • PEG-chitosan complexes with carbohydrates such as alginates, xanthans, dextran sulphate and gellan could be beneficial as gels for drug delivery applications.
  • PEG-chitosan can also be interacted with heparin and other negatively charge macromolecular drugs to form complexes.
  • Nasal and vaginal products as liquids or powders based on PEG-chitosan can be delivered by conventional devices such as spray pumps, powder insufflators or syringes.

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