AU2012247051B2 - Cyclodextrin-based polymers for therapeutics delivery - Google Patents

Abstract

Abstract The present invention relates to novel compositions of therapeutic cyclodextrin containing polymeric compounds designed as a carrier for small molecule therapeutics delivery and pharmaceutical compositions thereof. In particular, the 5 therapeutic/bioactive agents are covalently bound to the cyclodextrin-containing polymers. These cyclodextrin-containing polymers improve drug stability and solubility, and reduce toxicity of the small molecule therapeutic when used in vivo. Furthermore, by selecting from a variety of linker groups and targeting ligands the polymers present methods for controlled delivery of the therapeutic agents. The invention also relates to 10 methods of treating subjects with the therapeutic compositions described herein. The invention further relates to methods for conducting pharmaceutical business comprising manufacturing, licensing, or distribution kits containing or relating to the polymeric compounds described herein.

Description

AUSTRALIA PATENTS ACT 1990 COMPLETE SPECIFICATION FOR A STANDARD PATENT ORIGINAL Name of Applicant: Cerulean Pharma Inc. Actual Inventors: Jianjun Cheng and Mark E. Davis and Kay T. Khin Address for Service is: SHELSTON IP 60 Margaret Street Telephone No: (02) 9777 1111 SYDNEY NSW 2000 Facsimile No. (02) 9241 4666 CCN: 3710000352 Attorney Code: SW Invention Title: Cyclodextrin-based polymers for therapeutics delivery Details of Original Application No. 2009251190 dated 24 Dec 2009 The following statement is a full description of this invention, including the best method of performing it known to me/us: File: 45343AUP02 Cyclodextrin-Based Polymers for Therapeutics Delivery The present application is a divisional application of Australian Application No. 2009251190, which is incorporated in its entirety herein by reference. Background of the Invention 5 Any discussion of the prior art throughout the specification should in no way be considered as an admission that such prior art is widely known or forms part of common general knowledge in the field. Drug delivery of some small molecule therapeutic agents, such as camptothecin, has been problematic due to their poor pharmacological profiles. These therapeutic 10 agents often have low aqueous solubility, their bioactive forms exist in equilibrium with an inactive form, or high systemic concentrations of the agents lead to toxic side-effects. Some approaches to circumvent the problem of their delivery have been to conjugate the agent directly to a water-soluble polymer such as hydroxypropyl methacrylate (HPMA), polyethyleneglycol, and poly-L-glutamic acid. In some cases, such conjugates have been 15 successful in solubilizing or stabilizing the bioactive form of the therapeutic agent, or achieving a sustained release formulation which circumvents complications associated with high systemic concentrations of the agent. Another approach to the drug delivery problem has been to form host/guest inclusion complexes between the therapeutic agent and cyclodextrins or derivatives 20 thereof. Cyclodextrins (a, p, y) and their oxidized forms have unique physico-chemical properties such as good water solubility, low toxicity and low immune response. To date, most of the drug delivery studies with cyclodextrins have focused on their ability to form supra-molecular complexes, wherein cyclodextrins form host/guest inclusion complexes with therapeutic molecules and thus alter the physical, chemical, and/or 25 biological properties of these guest molecules. U.S. Patent 5,276,088 describes a method for synthesizing cyclodextrin containing polymers by either reacting polyvinyl alcohol or cellulose or derivatives thereof with cyclodextrin derivatives, or by copolymerization of a cyclodextrin derivative with vinyl acetate or methyl methacrylate. - la - U.S. Patent No. 5,855,900 describes a biodegradable cyclodextrin-containing polymer. The patent discloses a supramolecular-structured biodegradable polymeric assembly comprising a plurality of drug-modified a, p, y-cyclodextrins and a linear polymeric chain threading through the structural cavity of the cyclodextrins. 5 There is an ongoing need for new approaches to the delivery of small therapeutic agents that have poor pharmacological profiles such as camptothecin, paclitaxel, doxorubicin, and cyclosporine A. Summary of the Invention According to a first aspect, the present invention provides a modified 10 cyclodextrin ring or a salt thereof, wherein exactly two hydroxyl moieties are substituted with an alpha-amino acid selected from the group consisting of cysteine, tryptophan, glutamic acid, aspartic acid, lysine, and arginine. According to a second aspect, the present invention provides a compound of the formula: 15 AA AA, or a salt thereof, wherein ' is a cyclodextrin, wherein each AA independently comprises an alpha-amino acid selected from the group consisting of cysteine, tryptophan, glutamic acid, aspartic acid, lysine, and arginine. According to a third aspect, the present invention provides a compound of the 20 formula: AA AA -2or a salt thereof, wherein is a cyclodextrin, and wherein each AA independently comprises an alpha-amino acid selected from the group consisting of cysteine, tryptophan, glutamic acid, aspartic acid, lysine, and arginine. According to a fourth aspect, the present invention provides a compound of the 5 formula: AA AA or a salt thereof, wherein is a cyclodextrin, wherein each AA independently comprises an alpha-amino acid selected from the group consisting of cysteine, tryptophan, glutamic acid, aspartic acid, lysine, and arginine. 10 According to a fifth aspect, the present invention provides a compound of the formula: OH 0 OH 0 O O 00 OH HO OH O HO HO 0 OH HO O 0 AA OH HO AA O OH HO HO 0 OHO HO 0 OH or a salt therof, wherein each AA independently comprises an alpha-amino acid selected from the group consisting of cysteine, tryptophan, glutamic acid, aspartic acid, 15 lysine, and arginine. According to a sixth aspect, the present invention provides a composition comprising the modified cyclodextrin ring or salt thereof according to the first aspect or - 2a a compound or salt thereof according to any one of the second to fifth aspects, and a solvent. Unless the context clearly requires otherwise, throughout the description and the claims, the words "comprise", "comprising", and the like are to be construed in an 5 inclusive sense as opposed to an exclusive or exhaustive sense; that is to say, in the sense of "including, but not limited to". The present invention relates to novel compositions of polymer conjugates, defined as polymeric materials covalently coupled to therapeutic/bioactive agents, as carriers for therapeutics delivery. In one aspect, the present invention provides water 10 soluble, biocompatible polymer conjugates comprising a water-soluble, biocompatible polymer covalently attached to bioactive moieties through attachments that are cleaved under biological conditions to release the bioactive moieties. In certain such embodiments, the polymer comprises cyclic moieties alternating with linker moieties that connect the cyclic structures, e.g., into linear or branched polymers, preferably 15 linear polymers. The polymer may be a polycation, polyanion, or non-ionic polymer. The bioactive agent, which may be a therapeutic agent, a diagnostic agent, or an adjuvant, preferably makes up at least 5%, 10%, 15%, 20%, 2 5 %, 30%, or even 3 5 % by weight of the conjugate. In certain embodiments, the rate of drug release is dependent primarily upon the rate of hydrolysis. In certain other embodiments, the rate of drug 20 release is dependent primarily on enzymatic cleavage. The present invention provides cyclodextrin-containing polymeric compounds for use in drug delivery of these therapeutic agents. The invention also provides compounds for use in controlled drug delivery which are capable of releasing a therapeutic agent in a targeted, predictable, and controlled rate. 25 Accordingly, one aspect of the present invention is a polymer conjugate comprising cyclodextrin moieties, a therapeutic agent, and an optional ligand targeting agent. The polymer may be linear or branched, and may be formed via - 2b polycondensation of cyclodextrin-containing monomers, copolymerization between one or more cyclodextrin-containing monomers and one or more comonomers which do not contain cyclodextrin moieties. Furthermore, the present invention also contemplates cyclodextrin-containing polymers formed by grafting cyclodextrin 5 moieties to an already formed polymer. The cyclodextrin moieties contemplated by the present invention include, but are not limited to, a, P, and y cyclodextrins and oxidized forns thereof. Depending on the drug/polymer ratio desired, the therapeutic agent may be attached to a monomer via an optional linker prior to the polymerization step, or may be subsequently grafted onto the polymer via an 10 optional linker. Likewise, the targeting ligand may be attached to a monomer via an optional linker prior the polymerization step, or may be subsequently grafted onto the polymer via an optional linker,-or may be attached to the polymer as an inclusion complex or host-guest interactions. To illustrate further, one embodiment of the invention is a polymeric 15 compound represented by Formula I: pI (CD) M P4L2 D )a b La wherein 20 P represents a linear or branched polymer chain; CD represents a cyclic moiety such as a cyclodextrin moiety; 3 LI, L 2 and L3, independently for each occurrence, may be absent or represent a linker group; 1 D, independently for each occurrence, represents a therapeutic agent or a prodrug thereof; 5 T, independently for each occurrence, represents a targeting ligand or precursor thereof; a, n, and v, independently for each occurrence, represent integers in the range of 1 to 10 (preferably I to 8, i to 5, or even I to 3); b represents an integer in the range of 1 to about 30,000 (preferably <25,000, 10 <20,000, <15,000, <10,000, <5,000, <1,000, <500, <100, <50, <25, <10, or event <5); and n and w, independently for each occurrence, represents an integer in the range of 0 to about 30,000 (preferably <25,000, <20,000, <15,000, <10,000, <5,000, <1,000, <500, <100, <50, <25, <10, or even <5), 15 wherein either the polymer chain comprises cyclodextrin moieties or n is at least 1. Another embodiment of the present invention is a compound represented by Formula II: L7 - -p

L

6 P 20 o wherein 4 P represents a monomer unit of a polymer; T, independently for each occurrence, represents a targeting ligand or a precursor thereof; L6, L 7 , Ls, L9, and L 1 o, independently for each occurrence, may be absent or 5 represent a linker group; CD, independently for each occurrence, represents a cyclic moiety such as a cyclodextrin moiety or a derivative thereof; D, independently for each occurrence, represents a therapeutic agent or a prodrug form thereof; 10 m, independently for each occurrence, represents an integer in the range of I to 10 (preferably I to 8, 1 to 5, or even I to 3); o represents an integer in the range of 1 to about 30,000 (preferably <25,000, <20,000, <15,000, <10,000, <5,000, <1,000, <500, <100, <50, <25, <10, or even <5); and 15 p, n, and q, independently for each occurrence, represent an integer in the range of 0 to 10 (preferably 0 to 8, 0 to 5, 0 to 3, or even 0 to about 2), wherein CD and D are preferably each present at at least I location (preferably at least 5, 10, 25, 50 or even >100 locations) in the compound. 20 Another embodiment of the present invention is a compound represented by Formula III: Ty zz CD f 5 wherein CD represents a cyclic moiety such as a cyclodextrin moiety, or derivative thereof;

L

4 , L 5 , LG, and L7, independently for each occurrence, may be absent or 5 represent a linker group; D and D', independently for each occurrence, represent the same or different therapeutic agent or prodrugs thereof; T and T', independently for each occurrence, represent the same or different targeting ligand or precursor thereof; 10 f and y, independently for each occurrence, represent an integer in the range of I and 10 (preferably I to 8, I to 5, or even I to 3); g and z, independently for each occurrence, represent an integer in the range of 0 and 10 (preferably 0 to 8, 0 to 5, 0 to 3, or even 0 to about 2); and h represents an integer in the range of. 1 and 30,000 (preferably <25,000, 15 <20,000, <15,000, <10,000, <5,000, <1,000, <500, <100, <50, <25, <10, or even <5), wherein at least one occurrence (and preferably at least 5, 10, or even at least 20, 50, or >100 occurrences) of g represents an integer greater than 0. 20 Another aspect of the present invention is a method for preparing the therapeutic cyclodextrin-containing polymeric conjugates described herein, Another aspect of the present invention is a pharmaceutical composition comprising a compound or polymer as discussed above. Another aspect of the present invention is a pharmaceutical dosage form 25 comprising a polymeric conjugate as described herein. Another aspect of the present invention is a method for treating a subject comprising administering a therapeutically effective amount of any of the polymeric conjugates described herein. 6 Another aspect of the present invention is a method of conducting a pharmaceutical business comprising manufacturing, licensing, or distributing kits containing or relating to any of the polymeric conjugates described herein. In certain embodiments, these therapeutic polymer conjugates improve drug 5 stability and/or solubility of the therapeutic agent when used in vivo. Furthermore, by selecting from a variety of liner groups, the polymer conjugates present methods for controlled release of the therapeutic and/or bioactive agents, or improve the in vivo safety and/or therapeutic efficacy of the therapeutic/bioactive agent. In certain embodiments, the polymer conjugates are bioerodable or biodegradable. 10 Brief Description of the Figures Figure 1 shows strategies for varying polymer conjugates to tune their characteristics. Figure 2 demonstrates the effect of peptide tether length on drug release rate for drug-loade'd CD polymer. 15 Figure 3 presents the effect that tethering camptothecin has on enhancing camptothecin stability, e.g., inhibiting lactone ring-opening. Figure 4 shows lactone ring opening studies in pH 7.4 KH2PO4 buffer. Figure 5a and 5b show polymerization control by adjusting polymerization time. 20 Figures 6 illustrates CPT release from HG6 and HGGG6 at 37 "C after 24 h in buffer solutions with pHs ranging from 1.1 to 13.1. Figure 7 Displays HlPLC analysis of degradation of CD-BisCys-SS-Peg3400 Polymer Figure 8 Shows the tumor growth curve as a function of time for the D5W, 25 CPT, irinotecan, LGGGIO at its highest non-toxic dose tested (18 ing CPT/kg), and the other three conjugates with high MW polymer (HGGG6, HG6, HGGGJ0) at their MTDs in xenograft mice. Figure 9 presents the median tumor growth curves for HGGG6, HG6 and HGGGIO in xenograft mice. 30 FigurelO presents the medium tumor growth curves for LGGG1O and HGGG1O each dosed at 9 mg CPT/kg in xenograft mice. 7 Figure 11 presents the mean body weight (MBW) losses as a function of time plotted for D5W, CPT, irinotecan and the three conjugates containing high MW polymer at their MTDs in xenograft mice. Figure 12 shows the correlation of CPT concentration (ng/mng tissue) to 5 tumor size (in mg) in xenograft mice. Detailed Description of the Invention I. Overview The present invention relates to novel compositions of therapeutic 10 cyclodextrin-containing polymeric compounds designed for drug delivery of therapeutic agents. In certain embodiments, these cyclodextrin-containing polymers improve drug stability and/or solubility, and/or reduce toxicity, and/or improve efficacy of the small molecule therapeutic when used in vivo. In certain embodiments, the polymers can be used for delivery of therapeutics such as 15 camptothecin, taxol, doxorubicin, and amphotericin. Furthermore, by selecting from a variety of linker groups, and/or targeting ligands, the rate of drug release from the polymers can be attenuated for controlled delivery. The invention also relates to methods of treating subjects with the therapeutic compositions described herein. The invention further relates to methods for conducting a pharmaceutical business 20 comprising manufacturing, licensing, or distributing kits containing or relating to the polymeric compounds described herein. More generally, the present invention provides water-soluble, biocompatible polymer conjugates comprising a water-soLuble, biocompatible polymer covalently attached to bioactive moieties through attachments that are cleaved under biological 25 conditions to release the bioactive moieties. In certain such embodiments, the polymer comprises cyclic moieties alternating with liner moieties that connect the cyclic structures, e.g., into linear or branched polymers, preferably linear polymers. The cyclic moieties may be any suitable cyclic structures, such as cyclodextrins, crown ethers (e.g., 18-crown-6, 15-crown-5, 12-crown-4, etc.), cyclic oligopeptides 30 (e.g., comprising from 5 to 10 amino acid residues), cryptands or cryptates (e.g., cryptand [2.2.2], cryptand-2,1,1, and complexes thereof), calixarenes, or cavitands, 8 or any combination thereof. Preferably, the cyclic structure is (or is modified to be) water-soluble. In certain embodiments, e.g., where a linear polymer is desired, the cyclic structure is selected such that under polymerization conditions, exactly two moieties of each cyclic structure are reactive with the linker moieties, such that the 5 resulting polymer comprises (or consists essentially of) an alternating series of cyclic moieties and linker moieties, such as at least four of each type of moiety. Suitable difunctionalized cyclic moieties include many that are commercially available and/or amenable to preparation using published protocols. In certain embodiments, conjugates are soluble in water to a concentration of at least 0.1 g/mL, 10 preferably at least 0.25 g/mL. The polymer may be a polycation, polyanion, or non-ionic polymer. A polycationic or polyanionic polymer has at least one site that bears a positive or negative charge, respectively. In certain such embodiments, at least one of the linker moiety and the cyclic moiety comprises such a charged site, so that every occurrence 15 of that moiety includes a charged site. The bioactive agent, which may be a therapeutic agent, a diagnostic agent, or an adjuvant (such as a radiosensitizer, or a compound that lacks significant activity administered alone but that potentiates the activity of another therapeutic agent), preferably makes up at least 5%, 10%, 15%, 20%, 25%, 30%, or even 35% by 20 weight of the conjugate. In preferred embodiments, administration of the polymer to a patient results in release of the bloactive agent over a period of at least 6 hours, preferably at least 12 or 18 hours. For example, the agent may be released over a period of time ranging from 6 hours to a month, 6 hours to two weeks, 6 hours to 3 days, etc. In certain embodiments, the rate of drug release is dependent primarily 25 upon the rate of hydrolysis (as opposed to enzymatic cleavage), e.g., the rate of release changes by less than a factor of 5, preferably less than a factor of 2, in the presence of hydrolytic enzymes. In other embodiments, the rate of drug release may be dependent primarily on the rate of enzymatic cleavage. Polymeric conjugates of the present invention may be useful to improve 30 solubility and/or stability of a bioactive/therapeutic agent, reduce drug-drug interactions, reduce interactions with blood elements including plasma proteins, 9 reduce or eliminate immunogenicity, protect the agent from metabolism, modulate drug-release kinetics, improve circulation time, improve drug half-life (e.g., in the serum, or in selected tissues, such as tumors), attenuate toxicity, improve efficacy, normalize drug metabolism across subjects of different species, ethnicities, and/or 5 races, and/or provide for targeted delivery into specific cells or tissues. Poorly soluble and/or toxic compounds may benefit particularly from incorporation into polymeric compounds of the invention. II. Definitions (a) General Terms 10 An 'adjuvant', as the term is used herein, is a compound that has little or no therapeutic value on its own, but increases the effectiveness of a therapeutic agent. Exemplary adjuvants include radiosensitizers, transfection-enhancing agents (such as chloroquine and analogs thereof), chemotactic agents and chemoattractants, peptides that modulate cell adhesion and/or cell mobility, cell permeabilizing agents, 15 inhibitors of multidrug resistance and/or efflux pumps, etc. The term "agonist", as used herein, is meant to refer to an agent that mimics or up-regulates (e.g., potentiates or supplements) the bioactivity of a protein of interest, or an agent that facilitates or promotes (e.g., potentiates or supplements) an interaction among polypeptides or between a polypeptide and another molecule 20 (e.g., a steroid, hormone, nucleic acids, small molecules etc.). An agonist can be a wild-type protein or derivative thereof having at least one bioactivity of the wild type protein. An agonist can also be a small molecule that up-regulates the expression of a gene or which increases at least one bioactivity of a protein. An agonist can also be a protein or small molecule which increases the interaction of a 25 polypeptide of interest with another molecule, e.g., a target peptide or nucleic acid. "Antagonist" as used herein is meant to refer to an agent that down-regulates (e.g., suppresses or inhibits) the bioactivity of a protein of interest, or an agent that inhibits/suppresses or reduces (e.g., destabilizes or decreases) interaction among polypeptides or other molecules (e.g., steroids, hormones, nucleic acids, etc.). An 30 antagonist can also be a compound that down-regulates the expression of a gene of 10 interest or which reduces the amount of the wild-type protein present. An antagonist can also be a protein or small molecule which decreases or inhibits the interaction of a polypeptide of interest with another molecule, e.g., a target peptide or nucleic acid. The terms biocompatiblee polymer" and "biocornpatibility" when used in 5 relation to polymers are art-recognized, For example, bioconpatible polymers include polymers that are neither themselves toxic to the host (e.g., an animal or human), nor degrade (if the polymer degrades) at a rate that produces monomeric or oligomeric subunits or other byproducts at toxic concentrations in the host. In certain embodiments of the present invention, biodegradation generally involves 10 degradation of the polymer in an organism, e.g., into its monomeric subunits, which may be known to be effectively non-toxic. Intermediate oligomeric products resulting from such degradation may have different toxicological properties, however, or biodegradation may involve oxidation or other biochemical reactions that generate molecules other than monomeric subunits of the polymer. 15 Consequently, in certain embodiments, toxicology of a biodegradable polymer intended for in vivo use, such as implantation or injection into a patient, may be determined after one or more toxicity analyses. It is not necessary that any subject composition have a purity of 100% to be deemed biocompatible. Hence, a subject composition may comprise 99%, 98%, 97%, 96%, 95%, 90% 85%, 80%, 75% or 20 even less of biocompatible polymers, e.g., including polymers and other materials and excipients described herein, and still be biocompatible. To determine whether a polymer or other material is biocompatible, it may be necessary to conduct a toxicity analysis. Such assays are well latown in the art. One example of such an assay may be performed with live carcinoma cells, such as 25 GT3TKB tumor cells, in the following manner: the sample is degraded in I M NaOH at 37 *C until complete degradation is observed. The solution is then neutralized with I M HCL. About 200 gL of various concentrations of the degraded sample products are placed in 96-well tissue culture plates and seeded with human gastric carcinoma cells (GT3TKB) at 104/well density. The degraded sample 30 products are incubated with the GT3TKB cells for 48 hours. The results of the assay may be plotted as % relative growth vs. concentration of degraded sample in the 11 tissue-culture well. In addition, polymers and formulations of the present invention may also be evaluated by well-known in vivo tests, such as subcutaneous implantations in rats to confirm that they do not cause significant levels of irritation or inflammation at the subcutaneous implantation sites. 5 The term "biodegradable" is art-recognized, and includes polymers, compositions and formulations, such as those described herein, that are intended to degrade during use. Biodegradable polymers typically differ from non biodegradable polymers in that the former may be degraded during use. In certain embodiments, such use involves in vivo use, such as in vivo therapy, and in other 10 certain embodiments, such use involves in vitro use. In general, degradation attributable to biodegradability involves the degradation of a biodegradable polymer into its component subunits, or digestion, e.g., by a biochemical process, of the polymer into smaller, non-polymeric subunits. In certain embodiments, two different types of biodegradation may generally be identified. For example, one type of 15 biodegradation may involve cleavage of bonds (whether covalent or otherwise) in the polymer backbone. In such biodegradation, monomers and oligomers typically result, and even more typically, such biodegradation occurs by cleavage of a bond connecting one or more of subunits of a polymer. In contrast, another type of biodegradation may involve cleavage of a bond (whether covalent or otherwise) 20 internal to sidechain or that connects a side chiin to the polymer backbone. For example, a therapeutic agent or other chemical moiety attached as a side chain to the polymer backbone may be released by biodegradation. In certain embodiments, one or the other or both general types of biodegradation may occur during use of a polymer. 25 As used herein, the term "biodegradation" encompasses both general types of biodegradation. The degradation rate of a biodegradable polymer often depends in part on a variety of factors, including the chemical identity of the linkage responsible for any degradation, the molecular weight, crystallinity, biostability, and degree of cross-linldng of such polymer, the physical characteristics (e.g., shape and 30 size) of an implant, and the mode and location of administration. For example, the greater the molecular weight, the higher the degree of crystallinity, and/or the 12 greater the biostability, the biodegradation of any biodegradable polymer is usually slower. The term "biodegradable" is intended to cover materials and processes also temied "bioerodible". In certain embodiments wherein the biodegradable polymer also has a 5 therapeutic agent or other material associated with it, the biodegradation rate of such polymer may be characterized by a release rate of such materials. In such circumstances, the biodegradation rate may depend on not only the chemical identity and physical characteristics of the polymer, but also on the identity of material(s) incorporated therein. Degradation of the subject compositions includes not only the 10 cleavage of intramolecular bonds, e.g., by oxidation and/or hydrolysis, but also the disruption of intermolecular bonds, such as dissociation of host/guest complexes by competitive complex formation with foreign inclusion hosts. In certain embodiments, polymeric formulations of the present invention biodegrade within a period that is acceptable in the desired application. In certain 15 embodiments, such as in vivo therapy, such degradation occurs in a period usually less than about five years, one year, six months, three months, one month, fifteen days, five days, three days, or even one day on exposure to a physiological solution with a pH between 6 and 8 having a temperature of between 25 and 37 *C. In other embodiments, the polymer degrades in a period of between about one hour and 20 several weeks, depending on the desired application. As used herein the term "bioerodable" refers to polymers which deliver sustained effective amounts of therapeutic agent to target tissue over desired extended periods of time. Thus, a polymer according to the invention in the biological environment of host tissue and the like, in one aspect, is subjected to 25 hydrolytic enzymes and oxidative species under, and in proportion to, the host's inflammatory response. This results in release of the therapeutic agent via the breaking of the covalent linked bonds. Thus, in certain embodiments, the materials of the invention utilize the mammal's own wound-healing repair process in being degraded thereby, as hereinbefore described. 13 The biodegradable polymers polylactic acid, polyglycolic acid, and polylactic-glycolic acid copolymer (PLGA), have been investigated extensively for nanoparticle formulation. These polymers are polyesters that, upon implantation in the body, undergo simple hydrolysis. The products of such hydrolysis are 5 biologically compatible and metabolizable moieties (e.g., lactic acid and glycolic acid), which are eventually removed from the body by the citric acid cycle. Polymer biodegradation products are formed at a very slow rate, and hence do not affect normal cell function. Several implant studies with these polymers have proven safe in drug delivery applications, used in the form of matrices, microspheres, bone 10 implant materials, surgical sutures, and also in contraceptive applications for long term effects. These polymers are also used as graft materials for artificial organs, and recently as basement membranes in tissue engineering investigations. Nature Med. 824-826 (1996). Thus, these polymers have been time-tested in various applications and proven safe for human use. Most importantly, these polymers are 15 FDA-approved for human use. When polymers are used for delivery of pharmacologically active agents in vivo, it is essential that the polymers themselves be nontoxic and that they degrade into non-toxic degradation products as the polymer is eroded by the body fluids. Many synthetic biodegradable polymers, however, yield oligomers and monomers 20 upon erosion in vivo that adversely interact with the surrounding tissue. D. F. Williams, J. Mater. Sci. 1233 (1982). To minimize the toxicity of the intact polymer carrier and its degradation products, polymers have been designed based on naturally occurring metabolites. Probably the most extensively studied examples of such polymers are the polyesters derived from lactic or glycolic acid and polyamides 25 derived from amino acids. A number of bioerodable of biodegradable polymers are known and used for controlled release of pharmaceuticals. Such polymers are described in, for example, U.S. Pat. No. 4,291,013; U.S. Pat. No. 4,347,234; U.S. Pat. No. 4,525,495; U.S. Pat. No. 4,570,629; U.S. Pat. No. 4,572,832; U.S. Pat. No. 4,587,268; 30 U.S. Pat. No. 4,638,045; U.S. Pat. No. 4,675,381; U.S. Pat. No. 4,745,160; and U.S. Pat. No. 5,219,980. 14 A biohydrolyzable bond (e.g., ester, amide, carbonate, carbamates, or imide) refers to a bond that is cleaved (e.g., an ester is cleaved to forn a hydroxyl and a carboxylic acid) under physiological conditions. Physiological conditions include the acidic and basic environments of the digestive tract (e.g., stomach, intestines, 5 etc.), acidic environment of a tumor, enzymatic cleavage, metabolism, and other biological processes, and preferably refer to physiological conditions in a vertebrate, such as a mammal. As used herein the terms "comonomer A precursor', "lincer", "linker group", and linerr moiety" refer to any straight chain or branched, symmetric or 10 asymmetric compound which upon reaction with a cyclodextrin monomer precursor or other suitable cyclic moiety links two such moieties together. In certain embodiments, a comonomer A precursor is a compound containing at least two functional groups through which reaction and thus linkage of the cyclodextrin monomers can be achieved. Examples of functional groups, which may be the same 15 or different, terminal or internal, of each comonomer A precursor include, but are not limited, to amino, acid, imidazole, hydroxyl, thio, acyl halide, -C=C-, or -C-C groups and derivatives thereof. In preferred embodiments, the two functional groups are the same and are located at termini of the comonomer. In certain embodiments, a comonomer A precursor contains one or more pendant groups with at least one 20 functional group through which reaction and thus linkage of therapeutic agent or targeting ligand can be achieved, or branched polymerization can be achieved. Examples of functional groups, which may be the same or different, terminal or internal, of each comonoiner A precursor pendant group include, but are not limited, to amino, acid, imidazole, hydroxyl, thiol, acyl halide, ethylene, and ethyne groups 25 and derivatives thereof. In certain embodiments, the pendant group is a (un)substituted branched, cyclic or straight chain Cl-C 10 (preferably Cl-C6) alkyl, or arylalkyl optionally containing one or more heteroatoms, e.g., N, 0, S, within the chain or ring. Upon copolymerization of a comonomer A precursor with a cyclodextrin 30 monomer precursor, two cyclodextrin monomers may be linked together by joining the primary hydroxyl side of one cyclodextrin monomer with tie primary hydroxyl 15 side of another cyclodextrin monomer, by joining the secondary hydroxyl side of one cyclodextrin monomer with the secondary hydroxyl side of another cyclodextrin monomer, or by joining the primary hydroxyl side of one cyclodextrin monomer with the secondary hydroxyl side of another cyclodextrin monomer. Accordingly, 5 combinations of such linkages may exist in the final copolymer. Both the comonomer A precursor and the comonomer A of the final copolymer may be neutral, cationic (e.g., by containing protonated groups such as, for example, quaternary ammonium groups), or anionic (e.g., by containing deprotonated groups, such as, for example, sulfate, phosphate, borinate or carboxylate). The charge of 10 comonomer A of the copolymer may be adjusted by adjusting pH conditions. Examples of suitable comonomer A precursors include, but are not limited to succinimide (e.g., dithiobis(succinimidyl propionate) DSP, and dissucinimidyl suberate (DSS)), glutanates, and aspartates). The cyclodextrin-containing polymers of the present invention may be linear, 15 branched or grafted. As used herein, the term "linear cyclodextrin-containing polymer" refers to a polymer comprising (a, P, or y) cyclodextrin molecules, or derivatives thereof which are inserted within a polymer chain. As used herein, the term "grafted cyclodextrin-containing polymer" refers to a polymer comprising (a., 0, or y) cyclodextrin molecules, or derivatives thereof which are pendant off of 20 the polymer chain. The term "graft polymer" as used herein refers to a polymer molecule which has additional moieties attached as pendent groups along a polymer backbone. The term "graft polymerization" denotes a polymerization in which a side chain is grafted onto a polymer chain, which side chain consists of one or several other monomers. The properties of the graft copolymer obtained such as, for 25 example, solubility, melting point, water absorption, wettability, mechanical properties, adsorption behavior, etc., deviate more or less sharply from those of the initial polymer as a function of the type and amount of the grafted monomers. The term "grafting ratio", as used herein, means the weight percent of the amount of the monomers grafted based on the weight of the polymer. As used herein, a branched 30 cyclodextrin-containing polymer refers to a polymer backbone with a plurality of branch points, wherein each branch point is a starting point of yet another strand of the polymer backbone, and each section of polymer backbone may have a plurality 16 of (a, P, or y) cyclodextrin molecules, or derivatives thereof, inserted into or grafted onto the chain. The term "cyclodextrin moiety" refers to (a, P, or y) cyclodextrin molecules or derivatives thereof, which may be in their oxidized or reduced forms. 5 Cyclodextrin moieties may comprise optional linkers. Optional therapeutic agents and/or targeting ligands may be further linked to these moieties via an optional linker. The linkage may be covalent (optionally via biohydrolyzable bonds, e.g., esters, amides, carbamates, and carbonates) or may be a host-guest complex between the cyclodextrin derivative and the-therapeutic agent and/or targeting ligand or the 10 optional linkers of each. Cyclodextrin moieties may further include one or more carbohydrate moieties, preferably simple carbohydrate moieties such as galactose, attached to the cyclic core, either directly (i.e., via a carbohydrate linkage) or through a linker group. The term "EDso" means the dose of a drug that produces 50% of its 15 maximum response or effect. An 'effective amount' of a subject compound, with respect to the subject method of treatment, refers to an amount of the therapeutic in a preparation which, when applied as part of a desired dosage regimen provides a benefit according to clinically acceptable standards for the treatment or prophylaxis of a particular 20 disorder. The term "healthcare providers" refers to individuals or organizations that provide healthcare services to a person, community, etc. Examples of Healthcaree providers" include doctors, hospitals, continuing care retirement communities, skilled nursing facilities, subacute care facilities, clinics, multispecialty clinics, 25 freestanding ambulatory centers, home health agencies, and HMO's, "Instruction(s)" as used herein means documents describing relevant materials or methodologies pertaining to a kit. These materials may include any combination of the following: background information, list of components and their availability information (purchase information, etc.), brief or detailed protocols for 17 using the kit, trouble-shooting, references, technical support, and any other related documents. Instructions can be supplied with the kit or as a separate member component, either as a paper form or an electronic form which may be supplied on computer readable memory device or downloaded from an internet website, or as 5 recorded presentation. Instructions can comprise one or multiple documents, and are meant to include future updates. "Kit" as used herein means a collection of at leasttwo components constituting the kit. Together, the components constitute a functional unit for a given purpose. Individual member components may be physically packaged 10 together or separately. For example, a kit comprising an instruction for using the kit may or may not physically include the instruction with other individual member components. Instead, the instruction can be supplied as a separate member component, either in a paper form or an electronic form which may be supplied on computer readable memory device or downloaded from an internet website, or as 15 recorded presentation. The term "LD 50 " means the dose of a drug that is lethal in 50% of test subjects. A "patient" or "subject" to be treated by the subject method can mean either a human or non-human subject. 20 The "polymerizations" of the present invention include radical, anionic, and cationic mechanisms, as well as reactions of bifunctional molecules (analogous to the formation of nylon, e.g., reacting molecules each of which bears two or more different reactive moieties that react with each other (but, preferably, are disfavored from reacting intramolecularly by steric, conformational, or other constraints), or 25 reacting two or more different compounds, each compound bearing two or more reactive moieties that react only with reactive moieties of different compounds (i.e., intermolecularly)), as well as metal-catalyzed polymerizations such as olefin metathesis, and other polymerization reactions known to those of skill in the art. 18 The term "prophylactic or therapeutic" treatment is art-recognized and includes administration to the host of one or more of the subject compositions. If it is administered prior to clinical manifestation of the unwanted condition (e.g., disease or other unwanted state of the host animal) then the treatment is 5 prophylactic, i.e., it protects the host against developing the unwanted condition, whereas if it is administered after manifestation of the unwanted condition, the treatment is therapeutic, (i.e., it is intended to diminish, ameliorate, or stabilize the existing unwanted condition or side effects thereof). The term "preventing" is art-recognized, and when used in relation to a 10 condition, such as a local recurrence (e.g., pain), a disease such as cancer, a syndrome complex such as heart failure or any other medical condition, is well understood in the art, and includes administration of a composition which reduces the frequency of, or delays the onset of, symptoms of a medical condition in a subject relative to a subject which does not receive the composition. Thus, 15 prevention of cancer includes, for example, reducing the number of detectable cancerous growths in a population of patients receiving a prophylactic treatment relative to an untreated control population, and/or delaying the appearance of detectable cancerous growths in a treated population versus an untreated control population, e.g., by a statistically and/or clinically significant amount. Prevention of 20 an infection includes, for example, reducing the number of diagnoses of the infection in a treated population versus an untreated control population, and/or delaying the onset of symptoms of the infection in a treated population versus an untreated control population. Prevention of pain includes, for example, reducing the frequency of, or alternatively delaying, pain sensations experienced by subjects in a 25 treated population versus an untreated control population. As used herein, the terms "therapeutic agent" include any synthetic or naturally occurring biologically active compound or composition of matter which, when administered to an organism (human or nonhuman animal), induces a desired pharmacologic, immunogenic, and/or physiologic effect by local and/or systemic 30 action. The term therefore encompasses those compounds or chemicals traditionally regarded as drugs, vaccines, and biopharmaceuticals inchiding molecules such as 19 proteins, peptides, hormones, nucleic acids, gene constructs and the like. More particularly, the term "therapeutic agent" includes compounds or compositions for use in all of the major therapeutic areas including, but not limited to, adjuvants; anti infectives such as antibiotics and antiviral agents; analgesics and analgesic 5 combinations, anorexics, anti-inflammatory agents, anti-epileptics, local and general anesthetics, hypnotics, sedatives, antipsychotic agents, neuroleptic agents, antidepressants, anxiolytics, antagonists, neuron blocking agents, anticholinergic and cholinomimetic agents, antimuscarinic and muscarinic agents, antiadrenergics, antiarrhythmics, antihypertensive agents, hormones, and nutrients, antiarthritics, 10 antiasthmatic agents, anticonvulsants, antihistamines, antinauseants, antineoplastics, antipruritics, antipyretics; antispasmodics, cardiovascular preparations (including calcium channel blockers, beta-blockers, beta-agonists and antiarrythmics), antihypertensives, diuretics, vasodilators; central nervous system stimulants; cough and cold preparations; decongestants; diagnostics; hormones; bone growth 15 stimulants and bone resorption inhibitors; inmunosuppressives; muscle relaxants; psychostimulants; sedatives; tranquilizers; proteins, peptides, and fragments thereof (whether naturally occurring, chemically synthesized or recombinantly produced); and qucleic acid molecules (polymeric forms of two or more nucleotides, either ribonucleotides (RNA) or deoxyribonucleotides (DNA) including both double- and 20 single-stranded molecules, gene constructs, expression vectors, antisense molecules and the like), small molecules (e.g., doxorubicin) and other biologically active macromolecules such as, for example, proteins and enzymes. The agent may be a biologically active agent used in medical, including veterinary, applications and in agriculture, such as with plants, as well as other areas. The term therapeutic agent 25 also includes without limitation, medicaments; vitamins; mineral supplements; substances used for the treatment, prevention, diagnosis, cure or mitigation of disease or illness; or substances which affect the structure or function of the body; or pro-drugs, which become biologically active or more active after they have been placed in a predetermined physiological environment. 30 As used herein the term "low aqueous solubility" refers to water insoluble compounds having poor solubility in water, that is <5 mg/mi at physiological pH (6.5-7.4). Preferably, their water solubility is <1 mg/ml, more preferably <0.1 20 mg/mI. It is desirable that the drug is stable in water as a dispersion; otherwise a lyophilized or spray-dried solid form may be desirable. Examples of some preferred water-insoluble drugs include immunosuppressive agents such as cyclosporins including cyclosporine (cyclosporin 5 A), imnunoactive agents, antiviral and antifungal agents, antineoplastic agents, analgesic and anti-inflammatory agents, antibiotics, anti-epileptics, anesthetics, hypnotics, sedatives, antipsychotic agents, neuroleptic agents, antidepressants, anxiolytics, anticonvulsant agents, antagonists, neuron blocking agents, anticholinergic and cholinomimetic agents, antimuscarinic and muscarinic agents, 10 antiadrenergic and antiarThythmics, antihypertensive agents, hormones, and nutrients. A detailed description of these and other suitable drugs may be found in Remington's Pharmaceutical Sciences, 18th edition, 1990, Mack Publishing Co. Philadelphia, Pa The term "therapeutic index" refers to the therapeutic index of a drug defined 15 as LD 5 0

/ED

50 . A "therapeutically effective amount" of a compound, with respect to a method of treatment, refers to an amount of the compound(s) in a preparation which, when administered as part of a desired dosage regimen (to a mammal, preferably a human) alleviates a symptom, ameliorates a condition, or slows the onset of disease 20 conditions according to clinically acceptable standards for the disorder or condition to be treated or the cosmetic purpose, e.g., at a reasonable benefit/risk ratio applicable to any medical treatment. A "therapeutically effective daily dosage" of a compound, with respect to a method of treatment, refers to an amount of the compound(s) in a preparation which, 25 when administered as part of a desired daily dosage regimen (to a mammal, preferably a human) alleviates a symptom, ameliorates a condition, or slows the onset of disease conditions according to clinically acceptable standards for the disorder or condition to be treated or the cosmetic purpose, e.g., at a reasonable benefit/risk ratio applicable to any medical treatment. 30 (b) Chemical Terms 21 An aliphatic chain comprises the classes of alkyl, allkenyl and alkynyl defined below. A straight aliphatic chain is limited to unbranched carbon chain radicals. As used herein, the tenn "aliphatic group" refers to a straight chain, branched-chain, or cyclic aliphatic hydrocarbon group and includes saturated and 5 unsaturated aliphatic groups, such as an alkyl group, an alkenyl group, and an alkynyl group. Alkyl refers to a fully saturated branched or unbranched carbon chain radical having the number of carbon atoms specified, or up to 30 carbon atoms if no specification is made. For example, alkyl of 1 to 8 carbon atoms refers to radicals 10 such as methyl, ethyl, propyl, butyl, pentyl, hexyl, heptyl, and octyl, and those radicals which are positional isomers of these radicals. Alkyl of 10 to 30 carbon atoms includes decyl, undecyl, dodecyl, tridecyl, tetradecyl, pentadecyl, hexadecyl, heptadecyl, octadecyl, nonadecyl, eicosyl, heneicosyl, docosyl, tricosyl and tetracosyl. In preferred embodiments, a straight chain or branched chain alkyl has 15 30 or fewer carbon atoms in its backbone (e.g., Cl-C30 for straight chains, C3-C30 for branched chains), and more preferably 20 or fewer. Likewise, preferred cycloalkyls have from 3-10 carbon atoms in their ring structure, and more preferably have 5, 6 or 7 carbons in the ring structure. Moreover, the term "alkyl" (or "lower alkyl") as used throughout the 20 specification, examples, and claims is intended to include both "unsubstituted alkyls" and "substituted alkyls", the latter of which refers to alkyl moieties having substituents replacing a hydrogen on one or more carbons of the hydrocarbon backbone. Such substituents can include, for example, a halogen, a hydroxyl, a carbonyl (such as a carboxyl, an alkoxycarbonyl, a formyl, or an acyl), a 25 thiocarbonyl, (such as a thioester, a thioacetate, or a thioformate), an alkoxyl, a phosphoryl, a phosphate, a phosphonate, a phosphinate, an amino, an amido, an amidine, a cyano, a nitro, a sulfhydryl, an alkylthio, a sulfate, a sulfonate, a sulfamoyl, a sulfonainido, a sulfonyl, a heterocyclyl, an aralkyl, or an aromatic or heteroaromatic moiety. It will be understood by those skilled in the art that the 30 moieties substituted on the hydrocarbon chain can themselves be substituted, if appropriate. For instance, the substituents of a substituted alkyl may include substituted and unsubstituted forms of amino, azido, imino, amido, phosphoryl 22 (including phosphonate and phosphinate), sulfonyl (including sulfate, sulfonamido, sulfamoyl and sulfonate), and silyl groups, as well as ethers, alkylthios, carbonyls (including ketones, aldehydes, carboxylates, and esters), -CF3, -CN and the like. Bxemplary substituted alkyls are described below. Cycloalkyls can be further 5 substituted with alkyls, ailcenyls, alkoxyls, alkylthios, aminoalkyls, carbonyl substituted alkyls, -CF3, -CN, and the like. Unless the number of carbons is otherwise specified, "lower alkyl", as used herein, means an alkyl group, as defined above, but having from one to ten carbons, more preferably from one to six carbon atoms in its backbone structure such as 10 methyl, ethyl, n-propyl, isopropyl, n-butyl, isobutyl, sec-butyl, and tert-butyl. Likewise, "lower alkenyl" and "lower alkynyt" have similar chain lengths. Throughout the application, preferred alkyl groups are lower alkyls. In preferred embodiments, a substituent designated herein as alkyl is a lower alkyl. The term "alkylthio" refers to an alkyl group, as defined above, having a sulfur 15 radical attached thereto. In preferred embodiments, the "alkylthio" moiety is represented by one of -(S)-alkyl, -(S)-alkenyl, -(S)-alkynyl, and -(S)-(CH2)m-Rl, wherein m and RI are defined below. Representative alkylthio groups include methylthio, ethylthio, and the like. Alkenyl refers to any branched or unbranched unsaturated carbon chain 20 radical having the number of carbon atoms specified, or up to 26 carbon atoms if no limitation on the number of carbon atoms is specified; and having I or more double bonds in the radical. Alkenyl of 6 to 26 carbon atoms is exemplified by hexenyl, heptenyl, octenyl, nonenyl, decenyl, undecenyl, dodenyl, tridecenyl, tetradecenyl, pentadecenyl, hexadecenyl, heptadecenyl, octadecenyl, nonadecenyl, eicosenyl, 25 heneicosoenyl, docosenyl, tricosenyl and tetracosenyl, in their various isomeric forms, where the unsaturated bond(s) can be located anywhere in the radical and can have either the (Z) or the (E) configuration about the double bond(s). Alkynyl refers to hydrocarbyl radicals of the scope of alkenyl, but having I or more triple bonds in the radical. 30 The terms "alkoxyl" or "alkoxy" as used herein refers to an alkyl group, as defined below, having an oxygen radical attached thereto. Representative alkoxyl 23 groups include methoxy, ethoxy, propoxy, tert-butoxy and the like. An "ether" is two hydrocarbons covalently linked by an oxygen. Accordingly, the substituent of an alkyl that renders that alkyl an ether is or resembles an alkoxyl, such as can be represented by one of -0-alkyl, -0-alkenyl, -0-alkynyl, -O-(CH2)m-R1, where in 5 and RI are described below. The terms "amine" and "amino" are art-recognized and refer to both unsubstituted and substituted amines, e.g., a moiety that can be represented by the general formulae: RR6

R

5 I N' 5 or -N-R.

R

3 I 10 wherein R3, R5 and R6 each independently represent a hydrogen, an alkyl, an alkenyl, -(CH2)m-RI, or R3 and R5 taken together with the N atom to which they are attached complete a heterocycle having from 4 to 8 atoms in the ring structure; RI represents an alkenyl, aryl, cycloalkyl, a cycloalkenyl, a heterocyclyl or a polycyclyl; and n is zero or an integer in the range of I to 8. In preferred 15 embodiments, only one of R3 or R5 can be a carbonyl, e.g., R3, R5 and the nitrogen together do not form an imide. In even more preferred embodiments, R3 and R5 (and optionally R6) each independently represent a hydrogen, an alkyl, an alkenyl, or -(CH2)m-R I. Thus, the term "alkylamine" as used herein means an amine group, as defined above, having a substituted or unsubstituted alkyl attached thereto, i.e., at 20 least one of R3 and R5 is an alkyl group. In certain embodiments, an amino group or an alkylamine is basic, meaning it has a pKa > 7.00. The protonated forms of these functional groups have pKas relative to water above 7.00. The term "carbonyl" is art-recognized and includes such moieties as can be 25 represented by the general formula: 0 0 \ y, R7 or X R 8 24 wherein X is a bond or represents an oxygen or a sulfur, and R7 represents a hydrogen, an alkyl, an alkenyl, -(CH2)m-RI or a pharmaceutically acceptable salt, R8 represents a hydrogen, an alkyl, an alkenyl or -(CH2)m-R 1, where m and R1 are as defined above. Where X is an oxygen and R7 or R8 is not hydrogen, the formula 5 represents an "ester". Where X is an oxygen, and R7 is as defined above, the moiety is referred to herein as a carboxyl group, and particularly when R7 is a hydrogen, the formula represents a "carboxylic acid". Where X is an oxygen, and R8 is hydrogen, the formula represents a "formate". In general, where the oxygen atom of the above formula is replaced by sulfur, the formula represents a "thiocarbonyl" group. Where 10 X is a sulfur and R7 or R8 is not hydrogen, the formula represents a "thioester" group. Where X is a sulfur and R7. is hydrogen, the formula represents a "thiocarboxylic acid" group. Where X is a sulfur and R8 is hydrogen, the formula represents a "thioformate" group. On the other hand, where X is a bond, and R7 is not hydrogen, the above formula represents a "ketone" group. Where X is a bond, 15 and R7 is hydrogen, the above formula represents an "aldelyde" group. The term "derivatized" refers to chemically modifying molecules. The chemical modifications may be artificial such as formation of drugs, natural such as formation of metabolites. The skilled artisan would readily recognize the variety of ways molecules may be modified, such as oxidations, reductions, 20 electrophilic/nucleophilic substitutions, alkylations, ester/amide formations and the like. For example, cyclodextrins of the present invention may be chemically modified by amination, tosylation, or iodination prior to covalently attaching them to the polymeric matrix. Likewise, therapeutic agents may be chemically modified by preparing prodrugs (e.g., glycine-camptothecin). 25 The terms "heterocyclyl" or "heterocyclic group" refer to 3- to 10-membered ring structures, more preferably 3- to 7-membered rings, whose ring structures include one to four heteroatoms. Heterocycles can also be polycycles. Heterocyclyl groups include, for example, thiophene, thianthrene, furan, pyran, isobenzofuran, chromene, xanthene, phenoxathiin, pyrrole, imidazole, pyrazole, isothiazole, 30 isoxazole, pyridine, pyrazine, pyrimidine, pyridazine, indolizine, isoindole, indole, indazole, purine, quinolizine, isoquinoline, quinoline, phthalazine, naphthyridine, 25 quinoxaline, quinazoline, cinnoline, pteridine, carbazole, carboline, phenanthridine, acridine, pyrimidine, phenanthroline, phenazine, phenarsazine, phenothiazine, furazan, phenoxazine, pyrrolidine, oxolane, thiolane, oxazole, piperidine, piperazine, morpholine, lactones, lactams such as azetidinones and pyrrolidinones, sultams, 5 sultones, and the like. The heterocyclic ring can be substituted at one or more positions with such substituents as described above, as for example, halogen, alkyl, aralkyl, alkenyl, alkynyl, cycloalkyl, hydroxyl, amino, nitro, sulfhydryl, inino, amido, phosphate, phosphonate, phosphinate, carbonyl, carboxyl, silyl, sulfamoyl, sulfinyl, ether, alkylthio, sulfonyl, ketone, aldehyde, ester, a heterocyclyl, an 10 aromatic or heteroaromatic moiety, -CF3, -CN, or the like. As used herein, the term "substituted" is contemplated to include all permissible substituents of organic compounds. In a broad aspect, the permissible substituents include acyclic and cyclic, branched and unbranched, carbocyclic and heterocyclic, aromatic and nonarornatic substituents of organic compounds. 15 Illustrative substituents include, for example, those described herein above. The permissible substituents can be one or more and the same or different for appropriate organic compounds. For purposes of this invention, the heteroatoms such as nitrogen may have hydrogen substituents and/or any permissible substituents of organic compounds described herein which satisfy the valences of the heteroatoms. 20 This invention is not intended to be limited in any manner by the permissible substituents of organic compounds. The term "hydrocarbyl" refers to a monovalent hydrocarbon radical comprised of carbon chains or rings of up to 26 carbon atoms to which hydrogen atoms are attached. The term includes alkyl, cycloalkyl, alkenyl, ailcynyl and aryl 25 groups, groups which have a mixture of saturated and unsaturated bonds, carbocyclic rings and includes combinations of such groups. It may refer to straight chain, branched-chain, cyclic structures or combinations thereof. The term "hydrocarbylene" refers to a divalent hydrocarbyl radical. Representative examples include alkylene, phenylene, or cyclohexylene. Preferably, 30 the hydrocarbylene chain is fully saturated and/or has'a chain of I-10 carbon atoms. 26 As used herein, the term "nitro" means -N02; the term "halogen" designates -F, -Cl, -Br or -I; the term "sulfhydryl" means -SH; the term "hydroxyl" means -OH; and the term "sulfonyl" means -S02-. It will be understood that "substitution" or "substituted with" includes the 5 implicit proviso that such substitution is in accordance with permitted valence of the substituted atom and the substituent, and that the substitution results in a stable compound, e.g., which does not spontaneously undergo transformation such as by rearrangement, cyclization, elimination, etc. Analogous substitutions can be made to alkenyl and alkynyl groups to 10 produce, for example, arninoalkenyls, aminoalkynyls, armidoalkenyls, amidoalkynyls, iminoalkenyls, ininoalkynyls, thioalkenyls, thioalkynyls, carbonyl substituted alkenyls or alkynyls. As used herein, the definition of each expression, e.g., alkyl, m, n, etc., when it occurs more than once in any structure, is intended to be independent of its 15 definition elsewhere in the same structure. The terms triflyl, tosyl, mesyl, and nonaflyl are art-recognized and refer to trifluoromethanesulfonyl, p-toluenesulfonyl, methanesulfonyl, and nonafluorobutanesulfonyl groups, respectively. The terms triflate, tosylate, mesylate, and nonaflate are art-recognized and refer to trifluoronethanesulfonate 20 ester, p-toluenesulfonate ester, methanesulfonate ester, and nonafluorobutanesulfonate ester functional groups and molecules that contain said groups, respectively. The abbreviations Me, Et, Ph, Ms represent methyl, ethyl, phenyl, and methanesulfonyl, respectively. A more comprehensive list of the abbreviations 25 utilized by organic chemists of ordinary skill in the art appears in the first issue of each volume of the Journal of Organic Chemistry; this list is typically presented in a table entitled Standard List of Abbreviations. The abbreviations contained in said list, and all abbreviations utilized by organic chemists of ordinary skill in the art are hereby incorporated by reference. 27 Certain compounds of the present invention may exist in particular geometric or stereoisomeric forms. The present invention contemplates all such compounds, including cis- and trans-isomers, (R)- and (S)-enantiomers, diastereomers, (d) isomers, ()-isomers, the racemic mixtures thereof, and other mixtures thereof, as 5 falling within the scope of the invention. Additional asymmetric carbon atoms may be present in a substituent such as an ailcyl group. All such isomers, as well as mixtures thereof, are intended to be included in this invention. If, for instance, a particular enantiomer of a compound of the present invention is desired, it may be prepared by asymmetric synthesis, or by 10 derivatization with a chiral auxiliary, where the resulting diastereomeric mixture is separated and the auxiliary group cleaved to provide the pure desired enantiomers. Alternatively, where the molecule contains a basic functional group, such as amino, or an acidic functional group, such as carboxyl, diastereomeric salts may be formed with an appropriate optically active acid or base, followed by resolution of the 15 diastereomers thus formed by fractional crystallization or chromatographic means well known in the art, and subsequent recovery of the pure enantiomers. Contemplated equivalents of the compounds described above include compounds which otherwise correspond thereto, and which have the same general properties thereof, wherein one or more simple variations of substituents are made 20 which do not adversely affect the efficacy of the compound. In general, the compounds of the present invention may be prepared by the methods illustrated in the general reaction schemes as, for example, described below, or by modifications thereof, using readily available starting materials, reagents and conventional synthesis procedures. In these reactions, it is also possible to make use of variants 25 which are in themselves known, but are not mentioned here. For purposes of this invention, the chemical elements are identified in accordance with the Periodic Table of the Elements, CAS version, Handbook of Chemistry and Physics, 67th Ed., 1986-87, inside cover. Also for purposes of this invention, the term "hydrocarbon" is contemplated to include all permissible 30 compounds having at least one hydrogen and one carbon atom. In a broad aspect, the permissible hydrocarbons include acyclic and cyclic, branched and unbranched, 28 carbocyclic and heterocyclic, aromatic and nonaromatic organic compounds which can be substituted or unsubstituted. II. Exemplary Applications of Method and Compositions 5 (a) Exemplary Compositions The present invention includes polymer conjugates, such as cyclodextrin containing polymer conjugates, wherein one or more therapeutic/bioactive agents are covalently attached. In certain embodiments, the therapeutic agent is a small molecule, a macromolecule, an antibody, a peptide, a protein, an enzyme, a nicleic 10 acid, or a polymer that has therapeutic function. The polymers include linear or branched cyclodextrin-containing polymers and polymers grafted with cyclodextrin. Exemplary cyclodextrin-containing polymers that may be modified as described herein are taught in U.S. Patent No. 6,509,323, published U.S. application No. 20020151523, and U.S. patent application serial No.s 60/417373, and 10/372723. 15 These polymers are useful as carriers for small molecule therapeutic delivery, and may improve drug stability and solubility when used in vivo, Accordingly, one embodiment of present invention is a polymeric compound represented by Formula I: CD 3 L1 P L+D al b 20 [. w 29 wherein P represents a linear or branched polymer chain; CD represents a cyclic moiety such as a cyclodextrin moiety; 5 LI, L 2 and L3, independently for each occurrence, may be absent or represent a linker group; D, independently for each occurrence, represents a therapeutic agent or a prodrug thereof; T, independently for each occurrence, represents a targeting ligand or 10 precursor thereof; a, m, and v, independently for each occurrence, represent integers in the range of I to 10 (preferably 1 to 8, 1 to 5, or even I to 3); n and w, independently for each occurrence, represent an integer in the range of 0 to about 30,000 (preferably <25,000, <20,000, <15,000, <10,000, <5,000, 15 <1,000, <500, <100, <50, <25, <10, or even <5); and b represents an integer in the range of 1 to about 30,000 (preferably <25,000, <20,000, <15,000, <10,000, <5,000, <1,000, <500, <100, <50, <25, <10, or even <5), wherein either P comprises cyclodextrin moieties or n is at least 1. 20 In certain embodiments, P contains a plurality of cyclodextrin moieties within the polymer chain as opposed to the cyclodextrin moieties being grafted on to pendant groups off of the polymeric chain. Thus in certain embodiments, the polymer chain of formula I further comprises n' units of U, 25 wherein n' represents an integer in the range of 1 to about 30,000 (preferably <25,000, <20,000, <15,000, <10,000, <5,000, <1,000, <500, <100, <50, <25, <10, or even <5); and U is represented by the general formula: 30 y - - -- 4 . CD 7 1y - ~ g - -Sr - z Mf . g wherein CD represents a cyclic moiety, such as a cyclodextrin moiety, or derivative 5 thereof; L4, Ls, L6, and L7, independently for each occurrence, may be absent or represent a linker group; D and D', independently for each occurrence, represent the same or different therapeutic agent or prodrug forms thereof; 10 T and T', independently for each occurrence, represent the same or different targeting ligand or precursor thereof; f and y, independently for each occurrence, represent an integer in the range of I and 10; and g and z, independently for each occurrence, represent an integer in the range 15 of 0 and 10. In preferred embodiments, L4 and L 7 represent liner groups. In certain embodiments, the polymer may be selected from polysaccharides, and other non-protein biocompatible polymers, and combinations thereof, that 20 contain at least one terminal hydroxyl group, such as polyvinylpyrrollidone, poly(oxyethylene)glycol (PEG), polysuccinic anhydride, polysebacic acid, PEG phosphate, polyglutamate, polyethylenimine, maleic anhydride divinylether (DIVMA), cellulose, pullulans, inutin, polyvinyl alcohol (PVA), N-(2 31 hydroxypropyl)methacrylamide (H1PMA), dextran and hydroxyethyl starch (HES), and have optional pendant groups for grafting therapeutic agents, targeting ligands and/or cyclodextrin moieties. In certain embodiments, the polymer may be biodegradable such as poly(lactic acid), poly(glycolic acid), poly(alkyl 2 5 cyanoacrylates), polyanhydrides, and polyorthoesters, or bioerodible such as polylactide-glycolide copolymers, and derivatives thereof, non-peptide polyaminoacids, polyiminocarbonates, poly alpha-amino acids, polyalcyl-cyano acrylate, polyphosphazenes or acyloxymethyl poly aspartate and polyglutanate copolymers and mixtures thereof. 10 Another embodiment of the invention is a polymeric compound represented by Formula II: L7 L6 P Le (CD) (D q 15 wherein P represents a monomer unit of a polymer; T, independently for each occurrence, represents a targeting ligand or a precursor thereof; L6, L7, L 8 , L9, and Lio, independently for each occurrence, may be absent or 20 represent a liner group; 32 CD, independently for each occurrence, represents a cyclodextrin moiety or a derivative thereof, D, independently for each occurrence, represents a therapeutic agent or a prodrug form thereof; 5 m, independently for each occurrence, represents an integer in the range of 1 to 10 (preferably I to 8, 1 to 5, or even I to 3); o represents an integer in the range of 1 to about 30,000 (preferably <25,000, <20,000, <15,000, <10,000, <5,000, <1,000, <500, <100, <50, <25, <10, or even <5); and 10 p, n, and q, independently for each occurrence, represent an integer in the range of 0 to 10 (preferably 0 to 8, 0 to 5, 0 to 3, or even 0 to about 2), wherein CD and D are preferably each present at at least 1 location (preferably at least 5, 10, 25, or even 50 or 100 locations) in the compound. 15 Another embodiment of the invention is a compound represented by Formula Ty LS CD (D)f ') g Le z III: -I) g wherein CD represents a cyclic moiety, such as a cyclodextrin moiety, or derivative 20 thereof;

L

4 , Ls, L 6 , and L 7 , independently for each occurrence, may be absent or represent a linker group; 33 D and D', independently for each occurrence, represent the same or different therapeutic agent or prodrugs thereof; T and T', independently for each occurrence, represent the same or different targeting ligand or precursor thereof; 5 f and y, independently for each occurrence, represent an integer in the range of 1 and 10 (preferably I to 8, I to 5, or even I to 3); g and z, independently for each occurrence, represent an integer in the range of 0 and 10 (preferably 0 to 8, 0 to 5, 0 to 3, or even 0 to about 2); and h represents an integer in the range of I and 30,000 (preferably <25,000, 10 <20,000, <15,000, <10,000, <5,000, <1,000, <500, <100, <50, <25, <10, or even <5), wherein at least one occurrence (and preferably at least 5, 10, or even at least 20, 50, or 100 occurrences) of g represents an integer greater than 0. 15 In preferred embodiments, L4 and L7 represent linker groups. In certain embodiments, the underlying polymers are linear cyclodextrin containing polymers, e.g., the polymer backbone includes cyclodextrin moieties. For example, the polymer may be a water-soluble, linear cyclodextrin polymer produced by providing at least one cyclodextrin derivative modified to bear one reactive site at 20 each of exactly two positions, and reacting the cyclodextrin derivative with a linker having exactly two reactive moieties capable of forming a covalent bond with the reactive sites under polymerization conditions that promote reaction of the reactive sites with the reactive moieties to form covalent bonds between the linker and the cyclodextrin derivative, whereby a linear polymer comprising alternating units of 25 cyclodextrin derivatives and linkers is produced. Alternatively the polymer may be a water-soluble, linear cyclodextrin polymer having a linear polymer backbone, which polymer comprises a plurality of substituted or unsubstituted cyclodextrin moieties and linker moieties in the linear polymer backbone, wherein each of the cyclodextrin moieties, other than a cyclodextrin moiety at the terminus of a polymer chain, is 30 attached to two of said linker moieties, each linker moiety covalently linking two cyclodextrin moieties. In yet another embodiment, the polymer is a water-soluble, linear cyclodextrin polymer comprising a plurality of cyclodextrin moieties 34 covalently linked together by a plurality of linker moieties, wherein each cyclodextrin moiety, other than a cyclodextrin moiety at the terminus of a polymer chain, is attached to two linker moieties to form a linear cyclodextrin polymer. The linker group(s) may be an alkylene chain, a polyethylene glycol (PEG) 5 chain, polysuccinic anhydride, poly-L-glutamic acid, poly(ethyleneimine), an oligosaccharide, an amino acid chain, or any other suitable linkage. in certain embodiments, the linker group itself can be stable under physiological conditions, such as an alkylene chain, or it can be cleavable under physiological conditions, such as by an enzyme (e.g., the linkage contains a peptide sequence that is a 10 substrate for a peptidase), or by hydrolysis (e.g., the linkage contains a hydrolyzable group, such as an ester or thioester). The linker groups can be biologically inactive, such as a PEG, polyglycolic acid, or polylactic acid chain, or can be biologically active, such as an oligo- or polypeptide that, when cleaved from the moieties, binds a receptor, deactivates an enzyme, etc. Various oligomeric linker groups that are 15 biologically compatible and/or bioeredible are known in the art, and the selection of the linkage may influence the ultimate properties of the material, such as whether it is durable when implanted, whether it gradually deforms or shrinks after implantation, or whether it gradually degrades and is absorbed by the body. The linker group may be attached to the moieties by any suitable bond or functional 20 group, including carbon-carbon bonds, esters, ethers, amides, amines, carbonates, carbamates, sulfonamides, etc. In certain embodiments, the linker group(s) of the present invention represent a hydrocarbylene group wherein one or more methylene groups is optionally replaced by a group Y (provided that none of the Y groups are adjacent to each 25 other), wherein each Y, independently for each occurrence, is selected from, substituted or unsubstituted aryl, heteroaryl, cycloalkyl, heterocycloalkyl, or -0-, C(=X) (wherein X is NRI, 0 or S), -OC(0)-, -C(=0)O, -NR.-, -NRICO-, -C(O)NR-, -S(O),- (wherein n is 0, 1, or 2), -OC(0)-NR, -NR-C(0)-NRI-, -NR-C(NRI)-NRI-, and -B(OR,)-; and R,, independently for each occurrence, 30 represents H or a lower alkyl. 35 In certain embodiments, the linker group represents a derivatized or non derivatized amino acid. In certain embodiments, linker groups with one or more terminal carboxyl groups may be conjugated to the polymer. In certain embodiments, one or more of these terminal carboxyl groups may be capped by 5 covalently attaching them to a therapeutic agent, a targeting moiety, or a cyclodextrin moiety via an (thio)ester or amide bond. In still other embodiments, linker groups with one or more terminal hydroxyl, thiol, or amino groups may be incorporated into the polymer. In preferred embodiments, one or more of these terminal hydroxyl groups may be capped by covalently attaching them to a 10 therapeutic agent, a targeting moiety, or a cyclodextrin moiety via an (thio)ester, amide, carbonate, carbamate, thiocarbonate, or thiocarbamate bond. In certain embodiments, these (thio)ester, amide, (thio)carbonate or (thio)carbamates bonds may be biohydrolyzable, i.e., capable of being hydrolyzed under biological conditions. 15 In certain embodiments, the polymers as described above have polydispersities less than about 3, or even less than about 2. In certain embodiments, the therapeutic agent is a small molecule, a peptide, a protein, or a polymer that has therapeutic function. In certain embodiments, the agent is an anti-cancer (such as camptothecin or related derivatives), anti-fungal, 20 anti-bacterial, anti-mycotic, or anti-viral therapeutic. In certain embodiments, the agent is a receptor agonist. In certain embodiments, the agent is a receptor antagonist, In certain embodiments, the therapeutic agent is a protease inhibitor. Furthermore, a polymer of the present invention may contain one kind of therapeutic agent, or may contain more than one kind of therapeutic agent. For instance, two or 25 more different cancer drugs, or a cancer drug and an immunosuppressant, or an antibiotic and an anti-inflammatory agent may be grafted on to the polymer via optional linkers. By selecting different linkers for different drugs, the release of each drug may be attenuated to achieve maximal dosage and efficacy. One embodiment of the present invention provides an improved delivery of 30 certain hydrophobic small molecule therapeutics by covalently conjugating them to cyclodextrin containing polymers. Such conjugation improves the aqueous 36 solubility and hence the bioavailability of the therapeutic agents. Accordingly, in one embodiment of the invention, the therapeutic agent is a hydrophobic compound with a log P >0.4, >0.6, >0.8, >1, >2, >3, >4, or even >5, In other embodiments, a hydrophobic therapeutic agent, such as camptothecin, may be conjugated to another 5 compound, such as an amino acid, prior to covalently attaching the conjugate on to the polymer. Examples of amino acid derivatized camptothecin molecules are illustrated in Scheme V. The polymer conjugates of the present invention preferably have molecular weights in the range of 10,000 to 500,000; 30,000 to 200,000; or even 70,000 to 10 150,000 amu. In certain embodiments, the cyclodextrin moieties make up at least about 2%, 5% or 10% by weight, up to 20%, 30%, 50% or even 80% of the cyclodextrin modified polymer by weight. In certain embodiments, the therapeutic agents, or targeting ligands make up at least about 1%, 5%, 10% or 15%, 20%, 25%, 30% or 15 even 35% of the cyclodextrin-modified polymer by weight. Number-average molecular weight (Mn) may also vary widely, but generally fall in the range of about 1,000 to about 500,000 daltons, preferably from about 5000 to about 200,000 daltons and, even more preferably, from about 10,000 to about 100,000. Most preferably, Mn varies between about 12,000 and 65,000 daltons. In certain other 20 embodiments, Mn vaies between about 3000 and 150,000 daltons. Within a given sample of a subject polymer, a wide range of molecular weights may be present. For example, molecules within the sample may have molecular weights that differ by a factor of 2, 5, 10, 20, 50, 100, or more, or that differ from the average molecular weight by a factor of 2, 5, 10, 20, 50, 100, or more. Exemplary cyclodextrin 25 moieties include cyclic structures consisting essentially of from 7 to 9 saccharide moieties, such as cyclodextrin and.oxidized cyclodextrin. A cyclodextrin moiety optionally comprises a linker moiety that forms a covalent linkage between the cyclic structure and the polymer backbone, preferably having from I to 20 atoms in the chain, such as alkyl chains, including dicarboxylic acid derivatives (such as 30 glutaric acid derivatives, succinic acid derivatives, and the like), and heteroalkyl chains, such as oligoethylene glycol chains. 37 Cyclodextrins are cyclic polysaccharides containing naturally occurring D-(+) glucopyranose units in an a-(1,4) linkage. The most common cyclodextrins are alpha ((a)-cyclodextrins, beta (p)-cyclodextrins and gamma (y)-cyclodextrins which contain, respectively six, seven, or eight glucopyranose units. Structurally, the cyclic nature of a 5 cyclodextrin forms a torus or donut-like shape having an inner apolar or hydrophobic cavity, the secondary hydroxyl groups situated on one side of the cyclodextrin torus and the primary hydroxyl groups situated on the other. Thus, using (p)-cyclodextrin as an example, a cyclodextrin is often represented schematically as follows. OH 0 0 0 HO OHO HO O secondary hydroxyl HO0 HO OH HO0 OH H primary hydroxyl OH HO O_ HO OH OOH 0 HO 0 HOHO 0 OH 0 OH HO X OHO 0- HO 10 The side on which the secondary hydroxyl groups are located has a wider diameter than the side on which the primary hydroxyl groups are located. The present invention contemplates covalent linkages to cyclodextrin moieties on the primary and/or secondary hydroxyl groups. The hydrophobic nature of the cyclodextrin inner cavity 15 allows for host-guest inclusion complexes of a variety of compounds, e.g., adamantane. (Comprehensive Supramolecular Chemistry, Volume - 38 - 3, J.L. Atwood et al., eds., Pergamon Press (1996); T. Cserhati, Analytical Biochemistry, 225:328-332(1995); Husain et al., Applied Spectroscopy, 46:652-658 (1992); FR 2 665 169). Additional methods for modifying polymers are disclosed in Suh, J. and Noh, Y., Bioorg. Med Chem. Lett. 1998, 8, 1327-1330. 5 In certain embodiments, the present invention contemplates linear, water soluble, cyclodextrin-containing polymer, wherein a plurality of bioactive moieties are covalently attached to the polymer through attachments that are cleaved under biological conditions to release the bioactive moieties, wherein administration of the polymer to a patient results in release of the bioactive agent over a period of at least 10 2, 3, 5, 6, 8, 10, 15, 20, 24, 36, 48 or even 72 hours. In certain embodiments, the present invention contemplates attenuating the rate of release of the therapeutic agent by introducing various linking groups between the therapeutic agent and/or targeting ligand and the polymer. Thus, in certain embodiments, the polymeric therapeutics of the present invention are 15 compositions for controlled delivery of therapeutic agents. One skilled in the art would also recognize that by labeling the therapeutic agent and/or targeting ligand with radionuclei, or by forming complexes of NMR active nuclei, e.g., technetium, gadolinium, or dysprosium, the polymers of the present invention can achieve a dual diagnostic/therapeutic utility. 20 In other embodiments, the polymeric compounds stabilize the bioactive form of a therapeutic agent which exists in equilibrium between an active and inactive form. For instance, conjugating the therapeutic agent to the polymers of the present invention may shift the equilibrium between two tautomeric forms of the agent to the bioactive tautomer. In other embodiment, the polymeric compounds may 25 attenuate the equilibrium between lactonic and acid forms of a therapeutic agent. One method to determine molecular weight is by gel permeation chromatography ("GPC"), e.g., mixed bed columns, CH2C1 2 solvent, light scattering detector, and off-line dn/dc. Other methods are known in the art. 39 In other embodiments, the polymer conjugate of the invention may be a flexible or flowable material. When the polymer used is itself flowable, the polymer composition of the invention, even when viscous, need not include a biocompatible solvent to be flowable, although trace or residual amounts of biocompatible solvents 5 may still be present. While it is possible that the biodegradable polymer or the biologically active agent may be dissolved in a small quantity of a solvent that is non-toxic to more efficiently produce an amorphous, monolithic distribution or a fine dispersion of the biologically active agent in the flexible or flowable composition, it is an advantage 10 of the invention that, in a preferred embodiment, no solvent is needed to form a flowable composition. Moreover, the use of solvents is preferably avoided because, once a polymer composition containing solvent is placed totally or partially within the body, the solvent dissipates or diffuses away from the polymer and must be processed and eliminated by the body, placing an extra burden on the body's 15 clearance ability at a time when the illness (and/or other treatments for the illness) may have already deleteriously affected it. However, when a solvent is used to facilitate mixing or to maintain the flowability of the polymer conjugate of the invention, it should be non-toxic, otherwise biocompatible, and should be used in relatively small amounts. Solvents 20 that are toxic should not be used in any material to be placed even partially within a living body. Such a solvent also must not cause substantial tissue irritation or necrosis at the site of administration. Examples of suitable biocompatible solvents, when used, include N-methyl 2-pyrrolidone, 2-pyrrolidone, ethanol, propylene glycol, acetone, methyl acetate, 25 ethyl acetate, methyl ethyl ketone, dimethylformamide, dimethylsulfoxide, tetraliydrofuran, caprolactam, oleic acid, or 1-dodecylazacylcoheptanone. Preferred solvents include N-methylpyrrolidone, 2-pyrrolidone, dimethylsulfoxide, and acetone because of their solvating ability and their biocompatibility. In certain embodiments, the subject polymer conjugates are soluble in one or 30 more common organic solvents for ease of fabrication and processing. Common 40 organic solvents include such solvcnts as chloroform, dichloromethane, dichloroethane, 2-butanone, butyl acetate, ethyl butyrate, acetone, ethyl acetate, dimethylacetam ide, N-methylpyrrolidone, d imethylformam ide, and dimethylsulfoxide. 5 One aspect of the present invention contemplates attaching a hydrophobic therapeutic agent such as (S)-20-camptothecin to linear or branched cyclodextrin containing polymers for better delivery of the drug. (S)-20--camptothecin (CPT), an alcaloid isolated from Camptitheca accuminata in the late 1950's, was found to exhibit anticancer activity by inhibiting the action of topoisonierase I during the S 10 phase of the cell cycle. Its application in human cancer treatment, however, is limited due to several factors, especially its undesirable interactions with human serum albumin, instability of the bioactive lactone form, and poor aqueous solubility. In order to circumvent this problem, many CPT analogs have been developed to improve lactone stability and aqueous solubility. Topotecan and 15 irinotecan are analogs of CPT that have already been approved by FDA for human cancer treatment. The present invention discloses various types of linear, branched, or grafted cyclodextrin-containirng polymers wherein (S)-20-camptothecin is covalently bound to the polymer. In certain embodiments, the drug is covalently liUked via a biohydrolyzable bond selected from an ester, amide, carbamates, or 20 carbonate. An exemplary synthetic scheme for covalently bonding a derivatized CD to 20(S)-camptothecin is shown in Scheme . Scheme 1 0 0 0 NN N 0 00 HO .0 0 0=I. 0 CMTCDO X<\ 0 25 41 Without intending to limit the scope of the invention, a general strategy for synthesizing linear, branched or grafted cyclodextrin-containing polymers (CD Polymer) for loading a therapeutic agent such as camptothecin, and an optional targeting ligand is shown in Scheme I. 5 Scheme II Exemplary cyclodextrin monomers for linear, branch or aft cyclodextin polymers Thcrnpcujlic ageni (D) Rl5HM with Optiouni liner(W CD Polymer ------ 1 CD Polymer Multifunctional polymerizabc monomers o T fio lrelig ligand (), wVith opliousi iikecri(L') To illustrate further, without intending to be limiting, comonomer A precursors, cyclodextrin moieties, therapeutic agents, and/or targeting ligands may 10 be assembled as shown in Schemes lla-HIb. Note that in schemes Ila-b, in any given reaction there may be more than one comonomer A precursor, cyclodextrin moiety, therapeutic agent or targeting ligand that is of the same type or different. Furthermore, prior to polymerization, one or more comonomer A precursor, cyclodextrin moiety, therapeutic agent or targeting ligand may be covalently linked 15 with each other in one or more separate step. Scheme Ila: General scheme for graft polymers. The comonomer A precursor, cyclodextrin moiety, therapeutic agent and targeting ligand are as defined above. Furthermore, one skilled in the art may choose from a variety of reactive groups, e.g., hydroxyls, carboxyls, halides, amines, and activated ethenes, ethynes, 20 or aromatic groups in order achieve polymerization. For further examples of 42 reactive groups are disclosed in Advanced Organic Chemistry: Reactions, Mechanisms, and Structure, 5th Edition, 2000. Reactive .__Comronomner A Reactive Group precursor Group + OPTONALLY Group linGrou A ent AND/OR Reactive- optional _._ T-ge-Tin Group Linker Ligand PolymerizAtion Comonom er A T Oting Opiuna Pendant Optiooal sTargingc n e p ur a | Linker Group(s) Linker Lig an i Optional Linker Cyclodextrin Moiety 5 Scheme Ilb: General scheme of preparing linear cyclodextrin-containing polymers. One skilled in the art would recognize that by choosing a comonomer A precursor that has multiple reactive groups polymer branching can be achieved. 43 Reactive Comonorner A Group precursor Reactive - Cyclodextrin - Reactive Group Moiety Group + OPTIONALLY Reactive Optional Group Linker AND/OR Reactive_ Optional Targeting Group Linker Ligand Polymerization R R Lptional Cyclodextrin ..... _Comonomer A:]

.

R -n Wherein R is a therapeutic agent and/or targeting ligand which may be absent or present. Examples for different ways of synthesizing linear cyclodextrin-CPT S polymers are shown in Schemes HI-VIII. Scheme III 44 COOKO)S 0 0 COOH 0 (W)-CPT wherein R 0 W represents an opfianni inking group; and Scheme IV 5 OBz B COX OBz HO-111 O NH20 ' HO OHZ 0,OH H0H0 OH 0 0 W-CPT CPT 011k werein W represents an opdonal linking group 0 0 Scheme V 10 45 0 oO H 0 0 0 OCPT CPT or G-OcT s NN Op XCPT 0 0N 0 Om N H O 0 yH 0 CPTA 0 Sr"- N A 0 tW wherein Tac W represents an optilaim linking group, e.g.. glycyl residue Scheme VI 5 46 0 CPTr T7 HN 0 HIN s ,N-"__NH, HO Fl EDC o 0 NHS CPT MN 0 00 Scheme VII 00 xc ~ NH 0O~ G ' ON 0 100 HC HOk"-Y'Y-M I 47 CPT 0 OH + 0 0 Lys-oly-CPT 0 0 HN "O cPT Examples for grafting cyclodextrins on to side-chains of CPT-containing 5 polymers subunits are shown in Schemes IX-XUl. Each subunit may repeat any number of times, and one subunit may occur with substantially the same frequency, more often, or less often than another subunit, such that both subunits may be present in approximately the same amount, or in differing amounts, which may differ slightly or be highly disparate, e.g., one subunit is present nearly to the 10 exclusion of the other. In certain instances, the polymers are random copolymers, in which the different subunits and/or other monomeric units are distributed randomly throughout the polymer chain. Thus, where the formula Xm-Y-Z appears, wherein X, Y and Z are polymer subunits, these subunits may be randomly interspersed throughout the 15 polymer backbone. In part, the term "random" is intended to refer to the situation in which the particular distribution or incorporation of monomeric units in a polymer that has more than one type of monomeric units is not directed or controlled directly by the synthetic protocol, but instead results from features inherent to the polymer 48 system, such as the reactivity, amounts of subunits and other characteristics of the synthetic reaction or other methods of manufacture, processing, or treatment. Scheme IX 0-1 .e P--O-CH-CH2-+. C 0--CH-CH2-+ CPT H NaOH C+ CC1 0-CH-CH2-0 O-CH-CH-0 0-CH-CH2 NH OCPT Cl 5L1 Scheme X n m0 0 0 0 00 qM 0 0 H N cPT CPT 0 0 10 Scheme XI 49 Scheme XII 5 NH 0 o 00 H2N 0 -N- -n 0 N 0 a HO 0 H050 N The present invention further contemplates CD-polymers synthesized using 10 CD--biscysteine monomer and a di-NHS ester such as PEG-DiSPA or PEG-BTC as shown in Schemes XII[-XIV. 50 Scheme XIlI 0 0 + 0 34 EDCN

N

0 0 Mn55.700 Mw 9 50 MwI/l~n=1.74 Gy-CPT 00 00 Mg 0 0 5Scheme XIV 000 MIS 140 0 0 0 5 -- Gl-P 0 0 MP0 0 0 0 0- i o 0 0 0 C P T-G ly .p y 0 G ybCPT0 51 In certain embodiments, the present invention discloses several strategies to increase drug loading as shown in Figure 1. (b) Targeting Ligand 5 As mentioned above, one aspect of the present invention contemplates attaching a therapeutic agent to the polymer conjugates described herein. In certain embodiments, the polymer conjugate further comprises a targeting ligand. Thus in certain embodiments, a receptor, cell, and/or tissue-targeting ligand, 10 or a precursor thereof is coupled to a polymer conjugate. As used herein the term "targeting ligand" refers to any material or substance which may promote targeting of receptors, cells, and/or tissues in vivo or in vitro with the compositions of the present invention. The targeting ligand may be synthetic, semi-synthetic, or naturally-occurring. Materials or substances which may serve as targeting ligands 15 include, for example, proteins, including antibodies, antibody fragments, hormones, hormone analogues, glycoproteins and lectius, peptides, polypeptides, amino acids, sugars, saccharides, including monosaccharides and polysaccharides, carbohydrates, small molecules, vitamins, steroids, steroid analogs, hormones, cofactors, bioactive agents, and genetic material, including nucleosides, nucleotides, nucleotide acid 20 constructs and polynucleotides. As used herein, the term "precursor" to a targeting ligand refers to any material or substance which may be converted to a targeting ligand. Such conversion may involve, for example, anchoring a precursor to a targeting ligand. Exemplary targeting precursor moieties include maleimide groups, disulfide groups, such as ortho-pyridyl disulfide, vinylsulfone groups, azide groups, 25 and a-iodo acetyl groups. The attachment of the targeting ligand or precursor thereof to the polymer may be accomplished in various ways including but not limited to chelation, covalent attachment, or formation of host-guest complexes. In certain embodiments, an optional linker group may be present between the targeting ligand or precursor thereof and the polymer, wherein the linker group is attached to the 30 polymer via chelation, covalent attaclunent or form host guest complexes. For example, the one terminal end of a linker group may be attached to the targeting 52 ligand while the other may be attached to an adamantane group, or other such hydrophobic moiety, which forms a host guest complex with a cyclodextrin moiety. Thus the targeting ligand may be attached to a grafted cyclodextrin moiety, to a cyclodextrin moiety within the polymeric chain, or to the polymeric chain itself. 5 The number of targeting ligands per polymeric chain may vary according to various factors including but not limited to the identity of the therapeutic agent, nature of the disease, type of polymer chain. Structures of possible linker groups are the same as linker groups defined elsewhere in this application. 10 (c) Pharmaceutical Compositions. Formulations and Dosages In part, a biocompatible polymer composition of the present invention includes a biocompatible and optionally biodegradable polymer, such as one having the recurring monomeric units shown in one of the foregoing formulas, optionally including any other biocompatible and optionally biodegradable polymer mentioned 15 above or known in the art. In certain embodiments, the compositions are non pyrogenic, e.g., do not trigger elevation of a patient's body temperature by more than a clinically acceptable amount. The subject compositions may contain a "drug", "therapeutic agent," medicamentt," or "bioactive substance," which are biologically, physiologically, or 20 pharmacologically active substances that act locally or systemically in the human or animal body. For example, a subject composition may include any of the other compounds discussed above. Various forms of the medicaments or biologically active materials may be used which are capable of being released from the polymer matrix into adjacent 25 tissues or fluids. They may be hydrophobic molecules, neutral molecules, polar molecules, or molecular complexes capable of hydrogen bonding. They may be in the form of ethers, esters, aides and the like, including prodrugs which are biologically activated when injected into the human or animal body, e.g., by cleavage of an ester or amide. A therapeutic agent in a subject composition may 30 vary widely with the purpose for the composition. 53 Plasticizers and stabilizing agents known in the art may be incorporated in polymers of the present invention. In certain embodiments, additives such as plasticizers and stabilizing agents are selected for their biocompatibility. In certain embodiments, the additives are lung surfactants, such as 1,2 5 dipalmitoylphosphatidycholine (DPPC) and L-a-phosphatidylcholine (PC). A composition of this invention may further contain one or more adjuvant substances, such as fillers, thickening agents or the like. In other embodiments, materials that serve as adjuvants may be associated with the polymer matrix. Such additional materials may affect the characteristics of the polymer matrix that results. 10 For example, fillers, such as bovine serum albumin (BSA) or mouse serum albumin (MSA), may be associated with the polymer matrix. In certain embodiments, the amount of filler may range from about 0.1 to about 50% or more by weight of the polymer matrix, or about 2.5, 5, 10, 25, or 40 percent. Incorporation of such fillers may affect the biodegradation of the polymeric material 15 and/or the sustained release rate of any encapsulated substance. Other fillers known to those of skill in the art, such as carbohydrates, sugars, starches, saccharides, celluloses and polysaccharides, including mannitose and sucrose, may be used in certain embodiments of the present invention. In other embodiments, spheronization enhancers facilitate the production of 20 subject polymeric matrices that are generally spherical in shape. Substances such as zein, microcrystalline cellulose or microcrystalline cellulose co-processed with sodium carboxymethyl cellulose may confer plasticity to the subject compositions as well as implant strength and integrity. In particular embodiments, during spheronization, extrudates that are rigid, but not plastic, result in the formation of 25 dumbbell shaped implants and/or a high proportion of fines, and extrudates that are plastic, but not rigid, tend to agglomerate and fonn excessively large implants. In such embodiments, a balance between rigidity and plasticity is desirable. The percent of spheronization enhancer in a formulation typically range from 10 to 90% (w/w). 54 In certain embodiments, a subject composition includes an excipient. A particular excipient may be selected based on its melting point, solubility in a selected solvent (e.g., a solvent that dissolves the polymer and/or the therapeutic agent), and the resulting characteristics of the microparticles. S Excipients may comprise a few percent, about 5%, 10%, 15%, 20%, 25%, 30%, 40%, 50%, or higher percentage of the subject compositions. Buffers, acids and bases may be incorporated in the subject compositions to adjust their pH. Agents to increase the diffusion distance of agents released from the polymer matrix may also be included. 10 Disintegrants are substances that, in the presence of liquid, promote the disruption of the subject compositions. Disintegrants are most often used in implants, in which the function of the disintegrant is to counteract or neutralize the effect of any binding materials used in the subject formulation. In general, the mechanism of disintegration involves moisture absorption and swelling by an 15 insoluble material. Examples of disintegrants include croscarmellose sodium and crospovidone which, in certain embodiments, may be incorporated into the polymeric matrices in the range of about 1-20% of total matrix weight. In other cases, soluble fillers such as sugars (mannitol and lactose) may also be added to facilitate disintegration of 20 implants. Other materials may be used to advantage or to control the desired release rate of a therapeutic agent for a particular treatment protocol. For example, if the sustained release is too slow for a particular application, a pore-forning agent may be added to generate additional pores in the matrix. Any biocompatible water 25 soluble material may be used as the pore-forming agent. They may be capable of dissolving, diffusing or dispersing out of the fonned polymer system whereupon pores and microporous channels are generated in the system. The amount of pore forming agent (and size of dispersed particles of such pore-forming agent, if 55 appropriate) within the composition should affect the size and number of the pores in the polymer system. Pore-forming agents include any pharmaceutically acceptable organic or inorganic substance that is substantially miscible in water and body fluids and will 5 dissipate from the forming and formed matrix into aqueous medium or body fluids or water-immiscible substances that rapidly degrade to water-soluble substances. Suitable pore-forming agents include, for example, sugars such as sucrose and dextrose, salts such as sodium chloride and sodium carbonate, and polymers such as hydroxylpropylcellulose, carboxymethylcellulose, polyethylene glycol, and 10 PVP. The size and extent of the pores may be varied over a wide range by changing the molecular weight and percentage of pore-forming agent incorporated into the polymer system. The charge, lipophilicity or hydrophilicity of any subject polymeric matrix may be modified by attaching in some fashion an appropriate compound to the 15 surface of the matrix. For example, surfactants may be used to enhance wettability of poorly soluble or hydrophobic compositions. Examples of suitable surfactants include dextran, polysorbates and sodium lauryl sulfate. In general, surfactants are used in low concentrations, generally less than about 5%. Binders are adhesive materials that may be incorporated in polymeric 20 formulations to bind and maintain matrix integrity. Binders may be added as dry powder or as solution. Sugars and natural and synthetic polymers may. act as binders. Materials added specifically as binders are generally included in the range of about 0.5%-15% w/w of the matrix formulation. Certain materials, such as 25 microcrystalline cellulose, also used as a spheronization enhancer, also have additional binding properties. Various coatings may be applied to modify the properties of the matrices. 56 Three exemplary types of coatings are seal, gloss and enteric coatings. Other types of coatings having various dissolution or erosion properties may be used to further modify subject matrices behavior, and such coatings are readily known to one of ordinary skill in the art. 5 The seal coat may prevent excess moisture uptake by the matrices during the application of aqueous based enteric coatings. The gloss coat generally improves the handling of the finished matrices. Water-soluble materials such as hydroxypropylcellulose may be used to seal coat and gloss coat implants. The seal coat and gloss coat are generally sprayed onto the matrices until an increase in 10 weight between about 0.5% and about 5%, often about 1% for a seal coat and about 3% for a gloss coat, has been obtained. Enteric coatings consist of polymers which are insoluble in the low pH (less than 3.0) of the stomach, but are soluble in the elevated pH (greater than 4.0) of the small intestine. Polymers such as EUDRAGITm, RohmTech, Inc., Malden, Mass., 15 and AQUATERICTm, FMC Corp., Philadelphia, Penn., may be used and are layered as thin membranes onto the implants from aqueous solution or suspension or by a spray drying method. The enteric coat is generally sprayed to a weight increase of about 1% to about 30%, preferably about 10 to about 15% and may contain coating adjuvants such as plasticizers, surfactants, separating agents that reduce the 20 tackiness of the implants during coating, and coating permeability adjusters. The present compositions may additionally contain one or more optional additives such as fibrous reinforcement, colorants, perfumes, rubber modifiers, modifying agents, etc. In practice, each of these optional additives should be compatible with the resulting polymer and its intended use. Examples of suitable 25 fibrous reinforcement include PGA microfibrils, collagen nicrofibrils, cellulosic microfibrils, and olefinic microfibrils. The amount of each of these optional additives employed in the composition is an amount necessary to achieve the desired effect. The therapeutic polymer conjugates as described herein can be administered 30 in various pharmaceutical formulations, depending on the disorder to be treated and 57 the age, condition and body weight of the patient, as is well known in the art. For example, where the compounds are to be administered oraUy, they may be formulated as tablets, capsules, granules, powders or syrups; or for parenteral administration, they may be formulated as injections (intravenous, intramuscular or 5 subcutaneous), drop infusion preparations or suppositories. For application by the ophthalmic mucous membrane route, they may be formulated as eyedrops or eye ointments. These formulations can be prepared by conventional means, and, if desired, the active ingredient may be mixed with any conventional additive, such as an excipient, a binder, a disintegrating agent, a lubricant, a corrigent, a solubilizing 10 agent, a suspension aid, an emulsifying agent or a coating agent. Although the dosage will vary depending on the symptoms, age and body weight of the patient, the nature and severity of the disorder to be treated or prevented, the route of administration and the form of the drug, in general, a daily dosage of from 0.01 to 2000 mg of the therapeutic agent is recommended for an adult human patient, and 15 this may be administered in a single dose or in divided doses. The precise time of administration and/or amount of therapeutic polymer conjugate that will yield the most effective results in terms of efficacy of treatment in a given patient will depend upon the activity, pharmacokinetics, and bioavailability of a particular compound, physiological condition of the patient 20 (including age, sex, disease type and stage, general physical condition, responsiveness to a given dosage and type of medication), route of administration, etc. However, the above guidelines can be used as the basis for fine-timing the treatment, e.g., determining the optimum time and/or amount of administration, which will require no more than routine experimentation consisting of monitoring 25 the subject and adjusting the dosage and/or timing. The phrase "pharmaceutically acceptable" is employed herein to refer to those therapeutic polymer conjugates, materials, compositions, and/or dosage forms which are, within the scope of sound medical judgment, suitable for use in contact with the tissues of human beings and animals without excessive toxicity, irritation, 30 allergic response, or other problem or complication, commensurate with a reasonable benefit/risk ratio. 58 The phrase pharmaceuticallyy acceptable carrier" as used herein means a pharmaceutically acceptable material, composition or vehicle, such as a liquid or solid filler, diluent, excipient, solvent or encapsulating material, involved in carrying or transporting the subject chemical from one organ, or portion of the body, to 5 another organ, or portion of the body. Each carrier must be "acceptable" in the sense of being compatible with the.other ingredients of the formulation and not injurious to the patient. Some examples of materials which can serve as pharmaceutically acceptable carriers include: (1) sugars, such as lactose, glucose and sucrose; (2) starches, such as corn starch and potato starch; (3) cellulose, and its 10 derivatives, such as sodium carboxymethyl cellulose, ethyl cellulose and cellulose acetate; (4) powdered tragacanth; (5) malt; (6) gelatin; (7) talc; (8) excipients, such as cocoa butter and suppository waxes; (9) oils, such as peanut oil, cottonseed oil, safflower oil, sesame oil, olive oilcom oil and soybean oil; (10) glycols, such as propylene glycol; (11) polyols, such as glycerin, sorbitol, mannitol and polyethylene 15 glycol; (12) esters, such as ethyl oleate and ethyl laurate; (13) agar; (14) buffering agents, such as magnesium hydroxide and aluminum hydroxide; (15) alginic acid; (16) pyrogen-free water; (17) isotonic saline; (18) Ringer's solution; (19) ethyl alcohol; (20) phosphate buffer solutions; and (21) other non-toxic compatible substances employed in pharmaceutical formulations. 20 The term "pharmaceutically acceptable salts" refers to the relatively non toxic, inorganic and organic acid addition salts of the therapeutic polymer conjugates. These salts can be prepared in situ during the final isolation and purification of the therapeutic polymer conjugates, or by separately reacting a purified polymer in its free base form with a suitable organic or inorganic acid, and 25 isolating the salt thus formed. Representative salts include the hydrobrornide, hydrochloride, sulfate, bisulfate, phosphate, nitrate, acetate, valerate, oleate, palmitate, stearate, laurate, benzoate, lactate, phosphate, tosylate, citrate, maleate, fumarate, succinate, tartrate, naphthylate, mesylate, glucoheptonate, lactobionate, and laurylsulphonate salts and the like. (See, for example, Berge et al. (1977) 30 "Pharmaceutical Salts", J. Pharm. Sci. 66:1-19) 59 In other cases, the therapeutic polymer conjugates useful in the methods of the present invention may contain one or more acidic functional groups and, thus, are capable of forming pharmaceutically acceptable salts with pharmaceutically acceptable bases. The term "pharmaceutically acceptable salts" in these instances 5 refers to the relatively non-toxic, inorganic and organic base addition salts of the polymer(s). These salts can likewise be prepared in situ during the final isolation and purification of the polymer(s), or by separately reacting the purified polymer(s) in its free acid form with a suitable base, such as the hydroxide, carbonate or bicarbonate of a pharmaceutically acceptable metal cation, with ammonia, or with a 10 pharmaceutically acceptable organic primary, secondary or tertiary amine. Representative alkali or alkaline earth salts include the lithium, sodium, potassium, calcium, magnesium, and aluminum salts and the like. Representative organic amines useful for the formation of base addition salts include ethylamine, diethylamine, ethylenediamine, ethanolamine, diethanolamine, piperazine and the 15 like (see, for example, Berge et aL., supra). Wetting agents, emulsifiers and lubricants, such as sodium lauryl sulfate and magnesium stearate, as well as coloring agents, release agents, coating agents, sweetening, flavoring and perfuming agents, preservatives and antioxidants can also be present in the compositions. 20 Examples of pharmaceutically acceptable antioxidants include: (1) water soluble antioxidants, such as ascorbic acid, cysteine hydrochloride, sodium bisulfate, sodium metabisulfite, sodium sulfite and the like; (2) oil-soluble antioxidants, such as ascorbyl palmitate, butylated hydroxyanisole (BHA), butylated hydroxytoluene (BHT), lecithin, propyl gallate, alpha-tocopherol, and the like; and (3) metal 25 chelating agents, such as citric acid, ethylenediaimine tetraacetic acid (EDTA), sorbitol, tartaric acid, phosphoric acid, and the like. Formulations useful in the methods of the present invention include those suitable for oral, nasal, topical (including ophthalmic, otic, buccal and sublingual), rectal, vaginal, aerosol and/or parenteral administration. The formulations may 30 conveniently be presented in unit dosage form and may be prepared by any methods well known in the art of pharmacy. The amount of active ingredient which can be 60 combined with a carrier material to produce a single dosage form will vary depending upon the host being treated, the particular mode of administration, The amount of active ingredient which can be combined with a carrier material to produce a single dosage form will generally be that amount of the compound which 5 produces a therapeutic effect. Generally, out of one hundred per cent, this amount will range from about I per cent to about ninety-nine percent of active ingredient, preferably from about 5 per cent to about 70 per cent, most preferably from about 10 per cent to about 30 per cent. Methods of preparing these formulations or compositions include the step of 10 bringing into association a therapeutic polymer conjugate(s) with the carrier and, optionally, one or more accessory ingredients. In general, the formulations are prepared by uniformly and intimately bringing into association a therapeutic polymer conjugate with liquid carriers, or finely divided solid carriers, or both, and then, if necessary, shaping the product. 15 Formulations suitable for oral administration may be in the form of capsules, cachets, pills, tablets, gums, lozenges (using a flavored basis, usually sucrose and acacia or tragacanth), powders, granules, or as a solution or a suspension in an aqueous or non-aqueous liquid, or as an oil-in-water or water-in-oil liquid emulsion, or as an elixir or syrup, or as pastilles (using an inert base, such as gelatin and 20 glycerin, or sucrose and acacia) and/or as mouthwashes and the like, each containing a predetermined amount of a therapeutic polymer conjugate(s) as an active ingredient. A compound may also be administered as a bolis, electuary or paste. A tablet may be made by compression or molding, optionally with one or more accessory ingredients. Compressed tablets may be prepared using binder (for 25 example, gelatin or hydroxypropylmethyl cellulose), lubricant, inert diluent, preservative, disintegrant (for example, sodium starch glycolate or cross-linked sodium carboxymethyl cellulose), surface-active or dispersing agent. Molded tablets may be made by molding in a suitable machine a mixture of the powdered peptide or peptidomimetic moistened with an inert liquid diluent. 61 Tablets, and other solid dosage forms, such as dragees, capsules, pills and granules, may optionally be scored or prepared with coatings and shells, such as enteric coatings and other coatings well known in the pbarmaceutical-formulating art. They may also be formulated so as to provide slow or controlled release of the 5 active ingredient therein using, for example, hydroxypropylmethyl cellulose in varying proportions to provide the desired release profile, other polymer matrices, liposomes and/or microspheres. They may be sterilized by, for example, filtration through a bacteria-retaining filter, or by incorporating sterilizing agents in the form of sterile solid compositions which can be dissolved in sterile water, or some other 10 sterile injectable medium immediately before use. These compositions may also optionally contain pacifying agents and may be of a composition that they release the active ingredient(s) only, or preferentially, in a certain portion of the gastrointestinal tract, optionally, in a delayed manner. Examples of embedding compositions which can be used include polymeric substances and waxes. The 15 active ingredient can also be in micro-encapsulated form, if appropriate, with one or more of the above-described excipients. Liquid dosage forms for oral administration include pharmaceutically acceptable emulsions, microemulsions, solutions, suspensions, syrups and elixirs. In addition to the active ingredient, the liquid dosage forms may contain inert diluents 20 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, oils (in particular, cottonseed, groundnut, corn, germ, olive, castor and sesame oils), glycerol, tetrahydrofuryl alcohol, polyethylene glycols and fatty acid 25 esters of sorbitan, and mixtures thereof. Besides inert diluents, the oral compositions can also include adjuvants such as wetting agents, emulsifying and suspending agents, sweetening, flavoring, coloring, perfuming and preservative agents. Suspensions, in addition to the active therapeutic polymer conjugates may 30 contain suspending agents as, for example, ethoxylated isostearyl alcohols, 62 polyoxyethylene sorbitol and sorbitan esters, microcrystalline cellulose, aluminum inetahydroxide, bentonite, agar-agar and tragacanth, and mixtures thereof. Formulations for rectal or vaginal administration may be presented as a suppository, which may be prepared by mixing one or more therapeutic polymer 5 conjugates with one or more suitable nonirritating excipients or carriers comprising for example, cocoa butter, polyethylene glycol, a suppository wax or a salicylate, and which is solid at room temperature, but liquid at body temperature and, therefore, will melt in the rectum or vaginal cavity and release the active agent. Formulations which are suitable for vaginal administration also include 10 pessaries, tampons, creams, gels, pastes, foams or spray formulations containing such carriers as are known in the art to be appropriate. Dosage forms for the topical or transdermal administration of a therapeutic polymer conjugate(s) include powders, sprays, ointments, pastes, creams, lotions, gels, solutions, patches and inhalants. The active component may be mixed under 15 sterile conditions with a pharmaceutically acceptable carrier, and with any preservatives, buffers, or propellants which may be required. The ointments, pastes, creams and gels may contain, in addition to ligand(s), excipients, such as animal and vegetable fats, oils, waxes, paraffins, starch, tragacanth, cellulose derivatives, polyethylene glycols, silicones, bentonites, silicic 20 acid, talc and zinc oxide, or mixtures thereof. Powders and sprays can contain, in addition to a therapeutic polymer conjugate(s), excipients such as lactose, talc, silicic acid, aluminum hydroxide, calcium silicates and polyamide powder, or mixtures of these substances. Sprays can additionally contain customary propellants, such as chlorofluorohydrocarbons 25 and volatile unsubstituted hydrocarbons, such as butane and propane. The therapeutic polymer conjugate(s) can be alternatively administered by aerosol. This is accomplished by preparing an aqueous aerosol, liposomal preparation or solid particles containing the compound. A noiaqueous (e.g., fluorocarbon propellant) suspension could be used. Sonic nebulizers are preferred 63 because they minimize exposing the agent to shear, which can result in degradation of the compound. Ordinarily, an aqueous aerosol is made by fonnulating an aqueous solution or suspension of the agent together with conventional pharmaceutically acceptable 5 carriers and stabilizers. The carriers and stabilizers vary with the requirements of the particular compound, but typically include nonionic surfactants (Tweens, Pluronics, or polyethylene glycol), innocuous proteins like serum albumin, sorbitan esters, oleic acid, lecithin, amino acids such as glycine, buffers, salts, sugars or sugar alcohols. Aerosols generally are prepared from isotonic solutions. 10 Transdermal patches have the added advantage of providing controlled delivery of a therapeutic polymer conjugate(s) to the body. Such dosage forms can be made by dissolving or dispersing the agent in the proper medium. Absorption enhancers can also be used to increase the flux of the ligand across the skin. The rate of such flux can be controlled by either providing a rate controlling membrane 15 or dispersing the peptidomimetic in a polymer matrix or gel. Ophthalmic formulations, eye ointments, powders, solutions and the like, are also contemplated as being within the scope of this invention. Pharmaceutical compositions of this invention suitable for parenteral administration comprise one or more therapeutic polymer conjugate(s) in 20 combination with one or more pharmaceutically acceptable sterile isotonic aqueous or nonaqueous solutions, dispersions, suspensions or emulsions, or sterile powders which may be reconstituted into sterile injectable solutions or dispersions just prior to use, which may contain antioxidants, buffers, bacteriostats, solutes which render the formulation isotonic with the blood of the intended recipient or suspending or 25 thickening agents. Examples of suitable aqueous and nonaqueous carriers which may be employed in the pharmaceutical compositions of the invention include water, ethanol, polyols (such as glycerol, propylene glycol, polyethylene glycol, and the like), and suitable mixtures thereof, vegetable oils, such as olive oil, and injectable 64 organic esters, such as ethyl oleate. Proper fluidity can be maintained, for example, by the use of coating materials, such as lecithin, by the maintenance of the required particle size in the case of dispersions, and by the use of surfactants. These compositions may also contain adjuvants such as preservatives, 5 wetting agents, emulsifying agents and dispersing agents. Prevention of the action of microorganisms may be ensured by the inclusion of various antibacterial and antifungal agents, for example, paraben, chlorobutanol, phenol sorbic acid, and the like. It may also be desirable to include isotonic agents, such as sugars, sodium chloride, and the like Into the compositions. In addition, prolonged absorption of the 10 injectable pharmaceutical form may be brought about by the inclusion of agents which delay absorption such as aluminum monostearate and gelatin. In some cases, in order to prolong the effect of a drug, it is desirable to slow the absorption of the drug from subcutaneous or intramuscular injection. This may be accomplished by the use of a liquid suspension of crystalline or amorphous 15 material having poor water solubility. The rate of absorption of the drug then depends upon its rate of dissolution which, in turn, may depend upon crystal size and crystalline form. Alternatively, delayed absorption of a parenterally administered drug form is accomplished by dissolving or suspending the drug in an oil vehicle. 20 Injectable depot forms are made by forming microencapsule matrices of therapeutic polymer conjugate(s) in biodegradable polymers such as polylactide polyglycolide. Depending on the ratio of drug to polymer, and the nature of the particular polymer employed, the rate of drug release can be controlled. Examples of other biodegradable polymers include poly(orthoesters) and poly(anhydrides). 25 Depot injectable formulations are also prepared by entrapping the drug in liposomes or microemulsions which are compatible with body tissue. When the therapeutic polymer conjugate(s) of the present invention are administered as pharmaceuticals, to humans and animals, they can be given per se or as a pharmaceutical composition containing, for example, 0.1 to 99.5% (more 65 preferably, 0.5 to 90%) of active ingredient in combination with a pharmaceutically acceptable carrier. The preparations of agents may be given orally, parenterally, topically, or rectally. They are of course given by forms suitable for each administration route. 5 For example, they are administered in tablets or capsule fbrm, by injection, inhalation, eye lotion, ointment, suppository, infusion; topically by lotion or ointment; and rectally by suppositories. Oral administration is preferred. The phrases "parenteral administration" and "administered parenterally" as used herein means modes of administration other than enteral and topical 10 administration, usually by injection, and includes, without limitation, intravenous, intramuscular, intraarterial, intrathecal, intracapsular, intraorbital, intracardiac, intradermal, intraperitoneal, transtracheal, subcutaneous, subcuticular, intraarticular, subcapsular, subarachnoid, intraspinal and intrasternal injection and infusion. The phrases "systemic administration," "administered systemically," 15 "peripheral administration" and "administered peripherally" as used herein mean the administration of a therapeutic polymer conjugate, drug or other material other than directly into the central nervous system, such that it enters the patient's system and, thus, is subject to metabolism and other like processes, for example, subcutaneous administration. 20 These therapeutic polymer conjugate(s) may be administered to humans and other animals for therapy by any suitable route of administration, including orally, nasally, as by, for example, a spray, rectally, intravaginally, parenterally, intracisternally and topically, as by powders, ointments or drops, including buccally and sublingually. 25 Regardless of the route of administration selected, the therapeutic polymer conjugate(s), which may be used in a suitable hydrated form, and/or the pharmaceutical compositions of the present invention, are fonnulated into pharmaceutically acceptable dosage forms by conventional methods known to those of skill in the art. 66 Actual dosage levels of the active ingredients in the pharmaceutical compositions of this invention may be varied so as to obtain an amount of the active ingredient which is effective to achieve the desired therapeutic response for a particular patient, composition, and mode of administration, without being toxic to 5 the patient. (c) Physical Structures Of The Subject Compositions The subject polymers may be formed in a variety of shapes. For example, in certain embodiments, subject polymer matrices may be presented in the form of microparticles or nanoparticles. Microspheres typically comprise a biodegradable 10 polymer matrix incorporating a drug. Microspheres can be formed by a wide variety of techniques known to those of skill in the art. Examples of microsphere forming techniques include, but are not limited to, (a) phase separation by emulsification and subsequent organic solvent evaporation (including complex emulsion methods such as oil in water emulsions, water in oil emulsions and water-oil-water emulsions); (b) 15 coacervation-phase separation; (c). melt dispersion; (d) interfacial deposition; (e) in situ polymerization; (f) spray drying and spray congealing; (g) air suspension coating; and (h) pan and spray coating. These methods, as well as properties and characteristics of microspheres are disclosed in, for example, U.S. Pat. No. 4,652,441; U.S. Pat. No. 5,100,669; U.S. Pat. No. 4,526,938; WO 93/24150; 20 EPA 0258780 A2; U.S. Pat. No. 4,438,253; and U.S. Pat. 5,330,768, the entire disclosures of which are incorporated by reference herein. To prepare microspheres of the present invention, several methods can be employed depending upon the desired application of the delivery vehicles. Suitable methods include, but are not limited to, spray drying, freeze drying, air drying, 25 vacuum drying, fluidized-bed drying, milling, co-precipitation and critical fluid extraction. In the case of spray drying, freeze drying, air drying, vacuum drying, fluidized-bed drying and critical fluid extraction; the components (stabilizing polyol, bioactive material, buffers, etc.) are first dissolved or suspended in aqueous conditions. In the case of milling, the components are mixed in the dried form and 30 milled by any method known in the art. In the case of co-precipitation, the components are mixed in organic conditions and processed as described below. 67 Spray drying can be used to load the stabilizing polyol with the bioactive material. The components are mixed under aqueous conditions and dried using precision nozzles to produce extremely uniform droplets in a drying chamber. Suitable spray drying machines include, but are not limited to, Buchi, NIRO, APV and Lab-plant 5 spray driers used according to the manufacturer's instructions. The shape of microparticles and nanoparticles may be determined by scanning electron microscopy. Spherically shaped nanoparticles are used in certain embodiments, for circulation through the bloodstream. If desired, the particles may be fabricated using known techniques into other shapes that are more useful for a 10 specific application. In addition to intracellular delivery of a therapeutic agent, it also possible that particles of the subject compositions, such as microparticles or nanoparticles, may undergo endocytosis, thereby obtaining access to the cell. The frequency of such an endocytosis process will likely depend on the size of any particle. 15 In certain embodiments, solid articles useful in defining shape and providing rigidity and structural strength to the polymeric matrices may be used. For example, a polymer may be formed on a mesh or other weave for implantation. A polymer may also be fabricated as a stent or as a shunt, adapted for holding open areas within body tissues or for draining fluid from one body cavity or body lumen into another. 20 Further, a polymer may be fabricated as a drain or a tube suitable for removing fluid from a post-operative site, and in some embodiments adaptable for use with closed section drainage systems such as Jackson-Pratt drains and the like as are familiar in the art. The mechanical properties of the polymer may be important for the 25 processability of making molded or pressed articles for implantation. For example, the glass transition temperature may vary widely but must be sufficiently lower than the temperature of decomposition to accommodate conventional fabrication techniques, such, as compression molding, extrusion, or injection molding. (d) Biodevgadability And Release Characteristics 68 In certain embodiments, the polymers and blends of the present invention, upon contact with body fluids, undergo gradual degradation. The life of a biodegradable polymer in vivo depends upon, among other things, its molecular weight, crystallinity, biostability, and the degree of crosslinking. In general, the 5 greater the molecular weight, the higher the degree of crystallinity, and the greater the biostability, the slower biodegradation will be. If a subject composition is formulated with a therapeutic agent or other material, release of such an agent or other material for a sustained or extended period as compared to the release from an isotonic saline solution generally results. 10 Such release profile may result in prolonged delivery (over, say I to about 2,000 hours, or alternatively about 2 to about 800 hours) of effective amounts (e.g., about 0.0001 mg/kg/hour to about 1 0 mg/kg/hour) of the agent or any other material associated with the polymer. A variety of factors may affect the desired rate of hydrolysis of polymers of 15 the subject invention, the desired sofhiess and flexibility of the resulting solid matrix, rate and extent of bioactive material release. Some of such factors include the selection/identity of the various subunits, the enantiomeric or diastereomeric purity of the monomeric subunits, homogeneity of subunits found in the polymer, and the length of the polymer. For instance, the present invention contemplates 20 heteropolymers with varying linkages, and/or the inclusion of other monomeric elements in the polymer, in order to control, for example, the rate of biodegradation of the matrix. To illustrate further, a wide range of degradation rates may be obtained by adjusting the hydrophobicities of the backbones or side chains of the polymers while 25 still maintaining sufficient biodegradability for the use intended for any such polymer. Such a result may be achieved by varying the various functional groups of the polymer. For example, the combination of a hydrophobic backbone and a hydrophilic linkage produces heterogeneous degradation because cleavage is encouraged whereas water penetration is resisted. 69 One protocol generally accepted in the field that may be used to determine the release rate of any therapeutic agent or other material loaded in the polymer matrices of the present invention involves degradation of any such matrix in a 0.1 M PBS solution (pH 7.4) at 37 "C, an assay known in the art. For purposes of the 5 present invention, the term "PBS protocol" is used herein to refer to such protocol. In certain instances, the release rates of different polymer systems of the present invention may be compared by subjecting them to such -a protocol. In certain instances, it may be necessary to process polymeric systems in the same fashion to allow direct and relatively accurate comparisons of different systems to be 10 made. For example, the present invention teaches several different means of formulating the polymeric, matrices of the present invention. Such comparisons may indicate that any one polymeric system releases incorporated material at a rate from about 2 or less to about 1000 or more times faster than another polymeric system. 15 Alternatively, a comparison may reveal a rate difference of about 3, 5, 7, 10, 25, 50, 100, 250, 500 or 750 times. Even higher rate differences are contemplated by the present invention and release rate protocols. In certain embodiments, when formulated in a certain manner, the release rate for polymer systems of the present invention may present as mono- or bi-phasic. 20 Release of any material incorporated into the polymer matrix, which is often provided as a microsphere, may be characterized in certain instances by an initial increased release rate, which may release from about 5 to about 50% or more of any incorporated material, or alternatively about 10, 15, 20, 25, 30 or 40%, followed by a release rate of lesser magnitude. 25 The release rate of any incorporated material may also be characterized by the amount of such material released per day per mg of polymer matrix. For example, in certain embodiments, the release rate may vary from about I ng or less of any incorporated material per day per mg of polymeric system to about 500 or more ng/day/mg. Alternatively, the release rate may be about 0.05, 0.5, 5, 10, 25, 70 50, 75, 100, 125, 150, 175, 200, 250, 300, 350, 400, 450, or 500 ng/day/mg. In still other embodiments, the release rate of any incorporated material may be 10,000 ng/day/mg, or even higher. In certain instances, materials incorporated and characterized by such release rate.protocols may include therapeutic agents, fillers, 5 and other substances. In another aspect, the rate of release of any material from any polymer matrix of the present invention may be presented as the half-life of such material in the matrix. In addition to the embodiment involving protocols for in vitro detennination 10 of release rates, in vivo protocols, whereby in certain instances release rates for polymeric systems may be determined in vivo, are also contemplated by the present invention. Other assays useful for determining the release of any material from the polymers of the present system are known in the art. (e) Impiants and Delivery Svstems 15 In its simplest form, a biodegradable delivery system for a therapeutic agent consists of a dispersion of such a therapeutic agent in a polymer matrix. In other embodiments, an article is used for implantation, injection, or otherwise placed totally or partially within the body, the article comprising the subject compositions. It is particularly important that such an article result in minimal tissue irritation 20 when implanted or injected into vasculated tissue. Biodegradable delivery systems, and articles thereof, may be prepared in a variety of ways known in the art. The subject polymer may be melt-processed using conventional extrusion or injection molding techniques, or these products may be prepared by dissolving in an appropriate solvent, followed by formation of the 25 device, and subsequent removal of the solvent by evaporation or extraction. Once a system or implant article is in placc, it should remain in at least partial contact with a biological fluid, such as blood, internal organ secretions, mucus membranes, cerebrospinal fluid, and the like to allow for sustained release of any encapsulated therapeutic agent. 71 () Methods of MaMfacturing Generally, compounds of the present invention can be prepared in one of two ways: monomers bearing therapeutic agents, targeting ligands, and/or cyclodextrin moieties can be polymerized, or polymer backbones can be derivatized with 5 therapeutic agents, targeting ligands, and/or cyclodextrin moieties. Thus, in one embodiment, the present invention contemplates the synthesis of compounds of the invention by reacting monomers M-L-CD and M-L-D (and, optionally, M-L-T), wherein CD represents a cyclic moiety, such as a cyclodextrin molecule, or derivative 10 thereof; L, independently for each occurrence, may be absent or represents a linker group; D, independently for each occurrence, represents the same or different therapeutic agent or prodrugs thereof; 15 T, independently for each occurrence, represents the same or different targeting ligand or precursor thereof; and M represents a monomer subunit bearing one or more reactive moieties capable of undergoing a polymerization reaction with one or more other M in the monomers in the reaction mixture, under conditions that cause polymerization of the 20 monomers to take place. In certain embodiments, the reaction mixture may further comprise monomers that do not bear CD, T, or D moieties, e.g., to space the derivatized monomer units throughout the polymer. In an alternative embodiment, the invention contemplates synthesizing a 25 compound of the present invention by reacting a polymer P (the polymer bearing a plurality of reactive groups, such as carboxylic acids, alcohols, thiols, amines, epoxides, etc.) with grafting agents X-L-CD and Y-L-D (and, optionally, Z-L-T), wherein CD represents a cyclic moiety, such as a cyclodextrin molecule, or derivative 30 thereof; 72 L, independently for each occurrence, may be absent or represents a linker group; D, independently for each occurrence, represents the same or different therapeutic agent or prodrugs thereof; 5 T, independently for each occurrence, represents the same or different targeting ligand or precursor thereof; X, independently for each occurrence, represents a reactive group, such as carboxylic acids, alcohols, thiols, amines, epoxides, etc., capable of forming a covalent bond with a reactive group of the polymer; and 10 Y and Z, independently for each occurrence, represent inclusion hosts or reactive groups, such as carboxylic acids, alcohols, thiols, amines, epoxides, etc., capable of forming a covalent bond with a reactive group of the polymer or inclusion complexes with CD moieties grafted to the polymer, under conditions that cause the grafting agents to form covalent bonds and/or inclusion complexes, as 15 appropriate, with the polymer or moieties grafted to the polymer. For example, if the polymer includes alcohols, thiols, or amines as reactive groups, the grafting agents may include reactive groups that react with them, such as isocyanates, isothiocyanates, acid chlorides, acid anhydrides, epoxides, ketenes, sulfonyl chlorides, activated carboxylic acids (e.g., carboxylic acids treated with an 20 activating agent such as PyBrOP, carbonyldiimidazole, or another reagent that reacts with a carboxylic acid to form a moiety susceptible to nucleophilic attack), or other electrophilic moieties known to those of skill in the art. In certain embodiments, a catalyst may be needed to cause the reaction to take place (e.g., a Lewis acid, a transition metal catalyst, an amine base, etc.) as will be understood by those of skill 25 in the art. In certain embodiments, the different grafting agents are reacted with the polymer simultaneously or substantially simultaneously (e.g., in a one-pot reaction), or are reacted sequentially with the polymer (optionally with a purification and/or wash step between reactions). 30 Another aspect of the present invention is a method for manufacturing the linear or branched cyclodextrin-containing polymers represented by formulae I-Kl. 73 While the discussion below focuses on the preparation of linear cyclodextrin molecules, one skilled in the art would readily recognize that the methods described can be adapted for producing branched polymers by choosing an appropriate comonomer A precursor. 5 Accordingly, one embodiment of the invention is a method of preparing a linear cyclodextrin copolymer. According to the invention, a linear cyclodextrin copolymer of the invention may be prepared by copolymerizing a cyclodextrin monomer precursor disubstituted with an appropriate leaving group with a comonomer A precursor capable of displacing the leaving groups. The leaving 10 group, which may be the same or different, may be any leaving group known in the art which may be displaced upon copolymerization with a comonomer A precursor. In a preferred embodiment, a linear cyclodextrin copolymer may be prepared by iodinating a cyclodextrin monomer precursor to form a diiodinated cyclodextrin monomer precursor and copolymerizing the diiodinated cyclodextrin monomer 15 precursor with a comonomer A prdcursor to form a linear cyclodextrin copolymer having a repeating unit of formula II or III, or a combination thereof, each as described above. While examples presented below discuss iodinated cyclodextrin moieties, one skilled in the art would readily recognize that the present invention contemplates and encompasses cyclodextrin moieties wherein other leaving groups 20 such as alkyl and aiyl sulfonate may be present instead of iodo groups. In a preferred embodiment, a method of preparing a linear cyclodextrin copolymer of the Invention by iodinating a cyclodextrin monomer precursor as described above to form a diiodinated cyclodextrin monomer precursor of formula IVa, IVb, IVc or a mixture thereof: 74 Iva IVb IVc The diiodinated cyclodextrin may be prepared by any means known in the art. (Tabushi et aL. J. Am. Chem. 106, 5267-5270 (1984); Tabushi et al. J. Am. Chem. 106, 4580-4584 (1984)). For example, 0--cyclodextrin may be reacted with 5 biphenyl-4,4'-disulfonyl chloride in the presence of anhydrous pyridine to form a biphenyl-4,4'-disulfonyl chloride capped 0--cyclodextrin which may then be reacted with potassium iodide to produce diiodo-p-cyclodextrin. The cyclodextrin monomer precursor is iodinated at only two positions. By copolymerizing the diiodinated cyclodextrin monomer precursor with a comonomer A precursor, as described 10 above, a linear cyclodextrin polymer having a repeating unit of Formula la, Ib, or a combination thereof, also as described abovc, may be prepared. If appropriate, the iodine or iodo groups may be replaced with other known leaving groups. Also according to the invention, the iodo groups or other appropriate leaving group may be displaced with a group that permits reaction with a comonomer A 15 precursor, as described above. For example, a diiodinated cyclodextrin monomer precursor of formula IVa, IVb, IVc or a mixture thereof may be aminated to form a dianinated cyclodextrin monomer precursor of formula Va, Vb, Vc or a mixture thereof: 75

NH

2 NH 2 Va Vb

NH

2

NH

2

NH

2 Vc

NH

2 The diaminated cyclodextrin monomer precursor may be prepared by any means known in the art. (Tabushi et al. Tetrahedron Lett. 18:11527-1530 (1977); Mungall et al., J. Org. Chem. 16591662 (1975)). For example, a diiodo-0 5 cyclodextrin may be reacted with sodium azide and then reduced to form a diamino p-cyclodextrin). The cyclodextrin monomer precursor is aminated at only two positions. The diaminated cyclodextrin monomer precursor may then be copolymerized with a comonomer A precursor, as described above, to produce a linear cyclodextrin copolymer having a repeating unit of formula II-III or a 10 combination thereof, also as described above. However, the amino functionality of a diaininated cyclodextrin monomer.precursor need not be directly attached to the cyclodextrin moiety. Alternatively, the amino functionality or another nucleophilic functionality may be introduced by displacement of the iodo or other appropriate leaving groups of a cyclodextrin monomer precursor with amino group containing 15 moieties such as, for example, HSCH 2

CH

2

NH

2 (or a di-nucleophilic molecule more generally represented by HW-(CRIl),-WH wherein W, independently for each occurrence, represents 0, S, or NRi; Ri and R 2 , independently for each occurrence, represent H, (un)substituted alkyl, (un)substituted aryl, (un)substituted heteroalkyl, (un)substituted heteroaryl) with an appropriate base such as a metal hydride, alkali 20 or alkaline carbonate, or tertiary amine to form a diaminated cyclodextrin monomer precursor of formula Vd, Ve, Vf or a mixture thereof: 76 Vd ye v( CN1z HNN NH 2 S S SS Ps A linear oxidized cyclodextrin-containing copolymer of the invention may also be prepared by oxidizing a reduced linear cyclodextrin-containing copolymer of the invention as described below. This method may be performed as long as the 5 comonomer A does not contain an .oxidation sensitive moiety or group such as, for example, a thiol. According to the invention, a linear cyclodextrin copolymer of the invention may be oxidized so as to introduce at least one oxidized cyclodextrin monomer into the copolymer such that the oxidized cyclodextrin monomer is an integral part of the 10 polymer backbone. A linear cyclodextrin copolymer which contains at least one oxidized cyclodextrin monomer is defined as a linear oxidized cyclodextrin copolymer or a linear oxidized cyclodextrin-containing polymer. The cyclodextrin monomer may be oxidized on either the secondary or primary hydroxyl side of the cyclodextrin moiety. If more than one oxidized cyclodextrin monomer is present in 15 a linear oxidized cyclodextrin copolymer of the invention, the same or different cyclodextrin monomers oxidized on either the primary hydroxyl side, the secondary hydroxyl side, or both may be present. For illustration purposes, a linear oxidized cyclodextrin copolymer with oxidized secondary hydroxyl groups has, for example, at least one unit of formula VIa or Vib: 77 C

A

Via

A

C VIb / \ In formulae Via and VIb, C is a substituted or unsubstituted oxidized cyclodextrin monomer and A is a comononer bound, i.e., covalently bound, to the 5 oxidized cyclodextrin C. Also in formulae VIa and VIb, oxidation of the secondary hydroxyl groups leads to ring opening of the cyclodextrin moiety and the formation of aldehyde groups. A linear oxidized cyclodextrin copolymer may be prepared by oxidation of a linear cyclodextrin copolymer as discussed above. Oxidation of a linear 10 cyclodextrin copolymer of the invention may be accomplished by oxidation techniques known in the art. (H4isamatsu et al., Starch 44:188-191 (1992)). Preferably, an oxidant such as, for example, sodium periodate is used. It would be understood by one of ordinary skill in the art that under standard oxidation conditions that the degree of oxidation may vary or be varied per copolymer. Thus 15 in one embodiment of the invention, a linear oxidized copolymer of the invention may contain one oxidized cyclodextrin monomer. In another embodiment, substantially all cyclodextrin monomers of the copolymer would be oxidized. Another method of preparing a linear oxidized cyclodextrin copolymer of the invention involves the oxidation of a diiodinated or diarninated cyclodextrin 78 monomer precursor, as described above, to form an oxidized diiodinated or diaminated cyclodextrin monomer precursor and copolymerization of the oxidized diiodinated or diaminated cyclodextrin monomer precursor with a comonomer A precursor. In a preferred embodiment, an oxidized diiodinated cyclodextrin 5 monomer precursor of formula VIla, VUb, VIlc, or a mixture thereof: V 0 VIT: VII / \ may be prepared by oxidation of a diiodinated cyclodextrin monomer precursor of formulae IVa, IVb, IVe, or a mixture thercof as described above. In another preferred embodiment, an oxidized diaminated cyclodextrin monomer precursor of 10 formula VUila, VIb, VIlIc or a mixture thereof: 79 0 O VH~a 0 O NH2

NH

2 NH 2 VfIc VIlIb

NH

2

H

2 N

NH

2 0 0 may be prepared by amination of an oxidized diiodinated cyclodextrin monomer precursor of formulae VIla, VlIb, VI1c, or a mixture thereof, as described above. In still another preferred embodiment, an oxidized diaminated cyclodextrin monomer 5 precursor of formula IXa, IXb, IMc or a mixture thereof: o o H2N IXa o 0 S S S IXc

NH

2

H

2 N s

NH-

2

H

2 N may be prepared by displacement of the iodo or other appropriate leaving groups of an oxidized cyclodextrin monomer precursor disubstituted with an iodo or other 80 appropriate leaving group with the amino or other nucleophilic group containing moiety such as, e.g. HSCH2CH 2

NH

2 (or a di-nucleophilic inolecule more generally represented by HW-(CRIR 2 )n-WH wherein W, independently for each occurrence, represents 0, S, or NRI; R, and R 2 , independently for each occurrence, represent H, 5 (un)substituted alkyl, (un)substituted aryl, (un)substituted heteroalkyl, (un)substituted heteroaryl) with an appropriate base such as a metal hydride, alkali or alkaline carbonate, or tertiary amine. Alternatively, an oxidized dilodinated or diaminated cyclodextrin monomer precursor, as described above, may be prepared by oxidizing a cyclodextrin 10 monomer precursor to form an oxidized cyclodextrin monomer precursor and then diiodinating and/or diaminating the oxidized cyclodextrin monomer, as described above. As discussed above, the cyclodextrin moiety may be modified with other leaving groups other than iodo groups and other amino group containing functionalities. The oxidized diiodinated or diaminated cyclodextrin monomer 15 precursor may then be copolymerized with a comonomer A precursor, as described above, to form a linear oxidized cyclodextrin copolymer of the invention, A linear oxidized cyclodextrin copolymer may also be further modified by attachment of at least one ligand to the copolymer, The ligand is as described above. According to the invention, a linear cyclodextrin copolymer or linear 20 oxidized cyclodextrin copolymer may be attached to or grafted onto a substrate. The substrate may be any substrate as recognized by those of ordinary skill in the art. In another preferred embodiment of the invention, a linear cyclodextrin copolymer or linear oxidized cyclodextrin copolymer may be crosslinked to a polymer to forni, respectively, a crosslinked cyclodextrin copolymer or a crosslinked oxidized 25 cyclodextrin copolymer. The polymer may be any polymer capable of crosslinking with a linear or linear oxidized cyclodextrin copolymer of the invention (e.g., polyethylene glycol (PEG) polymer, polyethylene polymer). The polymer may also be the same or different linear cyclodextrin copolymer or linear oxidized cyclodextrin copolymer. Thus; for example, a linear cyclodextrin copolymer may be 30 crosslinked to any polymer including, but not limited to, itself, another linear cyclodextrin copolymer, and a linear oxidized cyclodextrin copolymer. A 81 crosslinked linear cyclodextrin copolymer of the invention may be prepared by reacting a linear cyclodextrin copolymer with a polymer in the presence of a crosslinking agent. A crosslinked linear oxidized cyclodextrin copolymer of the invention may be prepared by reacting a linear oxidized cyclodextrin copolymer 5 with a polymer in the presence of an appropriate crosslinking agent. The crosslinking agent may be any crosslinking agent known in the art. Examples of crosslinking agents include dihydrazides and disulfides. In a preferred embodiment, the crosslinking agent is a labile group such that a crosslinked copolymer may be uncrosslinked if desired, 10 A linear cyclodextrin copolymer and a linear oxidized cyclodextrin copolymer of the invention may be characterized by any means known in the art. Such characterization methods or techniques include, but are not limited to, gel permeation chromatography (GPC), matrix assisted laser desorption ionization-time of flight mass spectrometry (MALDI-TOF Mass spec), 'H and "C NMR, light 15 scattering and titration. The invention also provides a cyclodextrin composition containing at least one linear cyclodextrin copolymer and at least one linear oxidized cyclodextrin copolymer of the invention as described above. Accordingly, either or both of the linear cyclodextrin copolymer and linear oxidized cyclodextrin copolymer may be 20 crosslinked to another polymer and/or bound to a ligand as described above. Therapeutic compositions according to the invention contain a therapeutic agent and a linear cyclodextrin copolymer or a linear oxidized cyclodextrin copolymer, including crosslinked copolymers, of the invention. A linear cyclodextrin copolymer, a linear oxidized cyclodextrin copolymer and their crosslinked 25 derivatives are as described above. The therapeutic agent may be any synthetic or naturally occurring biologically active therapeutic agent including those known in the art. Examples of suitable therapeutic agents include, but are not limited to, antibiotics, steroids, polynucleotides (e.g., genomic DNA, cDNA, rmRNA, double stranded RNA, and antisense oligonucleotides), plasmids, peptides, peptide 30 fragments, small molecules (e.g., doxorubicin) and other biologically active macromolecules such as, for example, proteins and enzymes. 82 (g) Business Methods Other aspects of the invention provides for certain methods of doing business. In particular, practicing the methods of the invention may enable novel therapeutic compositions and improved formulations thereof. This technical step, 5 when combined with one or more additional steps, provides for novel approaches to conduct a pharmaceutical, or preferably a life-science business. For example, such therapeutic prepared by the method of the invention may be tested for efficacy as therapeutics in a variety of disease models, the potential therapeutic compositions then tested for toxicity and other safety-profiling before formulating, packaging and 10 subsequently marketing the resulting formulation for the treatment of disease. Alternatively, the rights to develop and market such formulations or to conduct such steps may be licensed to a third party for consideration. Accordingly, in certain embodiments, the present invention provides a method for conducting a pharmaceutical business, comprising: 15 a. manufacturing a formulation or kit including a pharmaceutical composition of any of the compounds of claims 1-4; and b. marketing to healthcare providers the benefits of using the formulation or kit in the treatment of a disease or disorder. In other embodiments, the present invention discloses a method for 20 conducting a pharmaceutical business, comprising: a. providing a distribution network for selling a pharmaceutical composition of any of the compounds of claims 1-4; and b. providing instruction material to patients or physicians for using the preparation in the treatment of a disease or disorder. 25 In certain embodiments, the present invention provides a method for conducting a pharmaceutical business, comprising: a. determining an appropriate formulation and dosage of a pharmaceutical composition of any of the compounds of claims 1-4; 83 b. conducting therapeutic profiling of formulations identified in step (a), for efficacy and toxicity in animals; and c. providing a distribution network for selling a preparation or preparations identified in step (b) as having an acceptable therapeutic profile. 5 An additional step of the embodiment comprises providing a sales group for marketing the preparation to healthcare providers. In still other embodiments, the present invention provides a method for conducting a pharmaceutical business, comprising: a. determining an appropriate formulation and dosage of a 10 pharmaceutical composition of any of the compounds of claims 1-4; and b. licensing, to a third party, the rights for further development and sale of the formulation. Exemplification 15 Materials. p-Cyclodextrin, "p-CD", (Cerestar USA, Inc. of Hammond, IN) was dried in vacuo (<0.1 mTorr) at 120 'C for 12 h before use. ON H ~ 4 O OH HD H 0HO OH O OH OH O HO OH HO 0 OH HO p-CD P-CD 20 All the anhydrous solvents, HPLC grade solvents and other common organic solvents were purchased from commercial suppliers and used without further purification. Biphenyl-4,4'-disulfonyl chloride (Aldrich Chemical Company, Inc. of 84 Milwaukee, WI) was recrystallized from chloroform/hexanes. Potassium iodide was powdered with a mortar and pestle and dried in an oven at 200 'C. Polyethylene glycol dipropanoicsuccinimide (PEG-DiSPA, MW 3400), polyethylene glycol dibutanoicsuccinimide (PEG-DiSBA, MW 3400), and polyethylene glycol 5 dibenzotrizolecarbonate (PEG-DiBTC, MW 3400) were purchased from Nektar (Huntsville, AL). Polyethylene glycol di-p-nitrophenolcarbonate (PEG-DiNPC, MW 3400) was acquired from Sigma (St. Louis, MO). CPT was purchased from Boehringer Ingelheim (Ingelheim, Germany). Human plasma was purchased from Sigma and reconstituted with DI water. Mouse plasma was prepared by centrifuge 10 removal of blood cells of fiesh blood samples collected from BALB/C female mice (Charles River). 6^,6'-diiodo-6^,61-dideoxy-f-cyclodextrin (CDDI, Scheme 2) was synthesized according to previous reported procedure by Hwang et. al (Bioconjugate Chem. 12, 280-290). Deionized water (18-Mn-cm) was obtained by passing in house deionized water through a Barnstead E-pure purification system. NMR spectra 15 were recorded on a Bruker AMX 500 MHz or a Varian 300 MHz spectrometer. Mass spectral (MS) analysis was performed using either an electrospray mass spectrometer equipped with LCQ ion trap (Thermo Finnigan) and fitted with an electrospray ionization source or a MALDT-TOF mass spectrometer (Voyager DE PRO, Applied Biosystems). MWs.of the polymer samples were analyzed on a GPC 20 system equipped with a Hitachi L-6200 Intelligent Pump, an Anspec RI detector (ERC-7512, Erma, Inc.), a Precision Detectors DLS detector (PD 2020), and double gel permeation columns (PL-aquagel-OH-40 8 pm 300 mm x 7.5 mm, Polymer Laboratory) calibrated using polyethylene glycol standard and eluded using PBS (Ix) at a concentration of 20-50 mg/mL and at a 0.7 minmin flow rate at ambient 25 temperature. CD derivatives were analyzed with a C-1 8 reverse phase column on a HPLC system equipped with an UV detector (System Gold 168 Detector, Beckman Coulter) and an evaporative light scattering (ELS) detector (Sedex 75, Sedere, France). CPT, CPT derivatives, and polymer-CPT conjugates were analyzed on HPLC systems with a C-18 reverse phase column (HIRPB-4438, 4.6 x 150 mm, 30 Richard Scientific) equipped with a fluorescence detector (FD-500, GTI/Spectro Vision, Groton Technology, Inc.) using a gradient of potassium phosphate buffer 85 (pH 4.1) and acetonitile. Excitation and emission wavelengths of the fluorescence detector were set at 370 nm and 440 nm, respectively. 5 Example 1: Biphenyl-4,4'-disuilfonyl-A,D-Capped P-Cyclodextrin, 1 (Tabushi et al. J. Am. Chem. Soc. 106, 5267-5270 (1984)) Scheme XV 91 C1 1 10 A 500 mL round bottom flask equipped with a magnetic stirbar, a Schienk adapter and a septum was charged with 7.92 g (6.98 mmol) of dry 0-cyclodextrin and 250 mL of anhydrous pyridine (Aldrich Chemical Company, Inc.). The resulting solution was stirred at 50 'C under nitrogen while 2.204 g (6.28 mmtol) of biphenyl-4,4'-disulfonyl chloride was added in four equal portions at 15 min 15 intervals. After stirring at 50 'C for an additional 3 h, the solvent was removed in vacuo and the residue was subjected to reversed-phase column chromatography using a gradient elution of 0-40% acetonitrile in water. Fractions were analyzed by high performance liquid chromatography (HPLC) and the appropriate fractions were combined. After removing the bulk of the acetonitrile on a rotary evaporator, the 20 resulting aqueous suspension was lyophilized to dryness. This afforded 3.39 g (38%) of 1 as a colorless solid. Example 2: 6^,6D Diiodo6 A 6D-Dideoxy--cyclodextrin, 2 (Tabushi et al. J. Am. Chem. 106, 4580-4584 (1984)) Scheme XVI 25 60 o 2 86 A 40 mL centrifuge tube equipped with a magnetic stirbar, a Schienk adapter and a septum was charged with 1.02 g (7.2 mmol) of 1, 3.54 g (21.3 mmol) of dry, powdered potassium iodide (Aldrich) and 15 mL of anhydrous 5 NN-dimethylformamide (DMF) (Aldrich). The resulting suspension was stirred at 80 'C under nitrogen for 2 h. After cooling to room temperature, the solids were separated by filtration and the supernatant was collected. The solid precipitate was washed with a second portion of anhydrous DMF and the supernatants were combined and concentrated in vacuo. The residue was then dissolved in 14 mL of 10 water and cooled in an ice bath before 0.75 mL (7.3 mmol) of tetrachloroethylene (Aldrich) was added with rapid stirring. The precipitated product was filtered on a medium glass frit and washed with a small portion of acetone before it was dried under vacuum over P205 for 14 h. This afforded 0.90 g (92%) of 2 as a white solid. 15 Example 3: 6^,6D-Bis-(2-aminoethylthio)-6^'6D-dideoXy-p-cyclodeXtrin, 3 (Tabushi, I: Shimokawa, K; Fugita, K. Tetrahedron Lett. 1977, 1527-1530) Scheme XVII 3 20 A 25 mL Schlenk flask equipped with a magnetic stirbar and a septum was charged with 0.91 mL (7.37 nmol) of a 0.81 M solution of sodium 2-aminoethylthiolate in ethanol. (Fieser, L.F.; Fieser, M. Reagentsfor Organic Synthesis; Wiley: New York, 1967; Vol. 3, pp.265-266). The solution was evaporated to dryness and the solid was redissolved in 5mL of anhydrous DMF 25 (Aldrich). 6^ 6D-Diiodo-6^,6D-dideoXy---cyclodeXtrin (2) (100mg, 7.38 x 10- mol) was added and the resulting suspension was stirred at 60 *C under nitrogen for 2 h. After cooling to room temperature, the solution was concentrated in vacuo and the residue was redissolved in water. After acidifying with 0.1 N HCI, the solution was applied to a Toyopearl SP-650M ion-exchange column (NH 4 +form) and the product 30 was eluted with a 0 to 0.4 M ammonium bicarbonate gradient. Appropriate fractions 87 were combined and lyophilized to dryness. This afforded 80mg (79%) of 3 as a white powder. Alternative Synthesis of dicysteamine p-CD 3. 5 To a solution of 4.69g (3.17 inmol) of 2 in 100 mL of degassed water was added 0.489 g (6.34 mmol) of freshly sublimed cysteamine. The solution was stirred under reflux for 2 h. After cooling to room temperature and acidifying with I N HCI, the solution was applied to a Toyopearl SP-650M ion-exchange column

(NH

4 form) and the product was eluted with a 0 to 0.2 M ammonium bicarbonate 10 gradient. Appropriate fractions were combined and lyophilized to dryness. This procedure gave 1.87 g (39% yield) of a white solid. The solid was characterized by TLC (silica gel, n-PrOH-AcOEt-H 2 0-NH 3 aq 5/3/3/1, detection by ninhydrin) and exhibited a major spot corresponding to 3. Matrix-assisted laser dcsorption/ionization (MALDI) time-of flight (TOF) mass spectrum was recorded 15 on 2 meter ELITE instrument supplied by PerSeptive Biosystems, Inc. MALDI-TOF m/z calcd for 3: 1252, found: 1253.5 [M+H)*, 1275.5 [M+Na]*, 1291.4 (M+K]. 1 3 C NMR (Bruker 500 MHz, D 2 0) S ppm; 32.1 (S-CH 2 ) and 38.8 (CH 2

-NH

2 ), 32.9 (C6 adjacent to S), 60.2 (C6 adjacent to OH), 70.8, 71.4, 72.5 (C2, C3, CS), 81.8 (C4), 101.7 (Cl). 20 Example 4: 6^,6D-Bis-(2-amino-2-carboxylethylthio)-6^'6D cyclodextrin, 4 (CD-BisCys) Scheme XVIII HS OH NHH NH, NH, 4 25 167 mL of 0.1 M sodium carbonate buffer were degassed for 45 minutes in a 500 mL 2-neck round bottom flask equipped with a magnetic stir bar, a condenser and septum. To this solution were added 1.96 g (16.2 mmol) of L-cysteine and 10.0 88 g (73.8 mmol) of diiodo, deoxy-P-cyclodextrin 2. The resulting suspension was heated at a reflux temperature for 4.5 h until the solution turned clear (colorless). The solution was then cooled to room temperature and acidified to pH 3 using IN HCL. The product was precipitated by slow addition of acetone (3 times weight ratio 5 of the solution). This afforded 9.0 g crude material containing CD-biscysteine (90.0%), unreacted cyclodextrin, CD-mono-eysteine and cystine. The resulting solid was subjected to anionic exchange column chromatography (SuperQ650M, Tosoh Bioscience) using a gradient elution of 0-0.4M ammonium bicarbonate. All fractions were analyzed by HPLC. The desired fractions were combined and the 10 solvent was reduced to 100 mL under vacuum. The final product was either precipitated by adding acetone or by adding methanol (3 times weight ratio of the solution). 4 was obtained in 60-90% yield. 'H NMR (D 2 0) 8 5.08 (m, 7H, CD-2 CH), 3.79-3.94 (m, 30H, CD-3,4-CH, CD-CH 2 , Cys-CH, 3.49-3.62 (in, 14H, CD-5, 6-CH), 2 .92-3.30(m, 4H, Cys-CH 2 ). 3 C NMR (D 2 0) 8 172.3, 101.9, 83.9, 81.6, 15 81.5, 73.3, 72.2, 72.0, 60.7, 54.0, 34.0, 30.6. ESI/MS (m/z): 1342 (MJ+, 1364 [M+ Na)]. Purity of 4 was confirmed by HPLC. Example 5: 6 A,6-Bis-(carboxylmethyithio)-6A-6D-dideoxy-f--cyclodextrin, 5 (CDDM) 20 Scheme XIX HS OH Y01 3 HO 5-s:: Z " OH 0 0 A 50 mL of 0.1 M sodium carbonate solution was degassed for 2 h in a 100 mL 3-neck round bottom flask equipped with a magnetic stir bar, a condenser and septa. Mercaptoacetic acid (0.46 mL, 6.64 mmol) was syringed into the flask and 25 pH of the solution was adjusted to 9.3 with 1N sodium hydroxide. To this resulting solution was added 3.00 g (2.21 mmol) of di-iodo-p--cyclodextrin 2 and heated at 80 "C for an hour. The solution temperature was increased 10 "C every hour until it reached 100 "C. After 3 h. at the reflux temperature, the clear colorless solution was cooled to room temperature and acidified to pH 3.5 using 1 N HCL. The crude 89 product was crashed out by slow addition of acetone (3 times weight ratio of the solution). The resulting solid was subjected to anionic exchange column chromatography using a gradient elution of 0-0.4 M ammonium bicarbonate solution. This afforded 1.8 g (63.4%) of 5 as a colorless solid. ESI/MS (r/z): 1281 5 [M-. Purity of this compound was confirmed with HPLC. Example 6: CD-Bis(Glutamic acid-y-Benzyl ester) 6 Scheme XX CH O"H 7 0 0 6 10 A 50 mL round bottom flask equipped with a magnetic stirbar and a condenser and a septum was charged with 0.101 g (0.425 mrnol) of H-Glu(Obzl) 0H and 0.15 g (0.106 m-mol) of dio-iodo p cyclodextrin 2 in 5 mL of degassed 0.1 M sodium carbonate solution. The solution mixture was heated at 100'C for 2 h. 15 The solution was then cooled to room temperature and acidified to pH 4 before dialyzing in MWCO 500 membranes for 24 h. The yield of 6 was 0.142 g (83.6 %). Example 7 CD-BisLys(Z) 7 Scheme XXI BCBZ . CBZ,NH FIN".B

H

2 N OH > <OO\ OH 20 7 90 A 50 mL round bottom flask equipped with a magnetic stirbar and a condenser and a septum was charged with 0.124 g (0.443 mmol) of H-Lysine(Z)-OH and 0.5 g (0.111 mmol) of di-iodo..--cyclodextrin 2 in 5anL of degassed 0.IM sodium carbonate solution. The solution mixture was heated at 100 'C for 4 h. The 5 solution was then filtered and the pH of the filtrate is adjusted to 8.5 before dialyzing in MWCO 500 membranes for 24 h. The yield of 7 was 0.124 g (68.9%). Example 8: Synthesis of p-cyclodextrin-Tosylate, 8 (Melton, L.D., and Slessor, K.N., Carbohydrate Research, 18, p. 29 (1971)) Scheme XXII 10 Tosyl-Cl 8 A 500 mL round-bottom flask equipped with a magnetic stirbar, a vacuum adapter and a septum was charged with a solution of dry p-cyclodextrin (8.530 g, 7.51 mmol) and 200 mL of dry pyridine. The solution was cooled to 0 *C before 15 1.29 g (6.76 mmol) of tosyl chloride was added. The resulting solution was allowed to warm to room temperature overnight. The pyridine was removed as much as possible in vacuo. The resulting residue was then recrystallized twice from 40 mL of hot water to yield 7.54 (88%) of a white crystalline solid 8. 20 Example 9: Synthesis of Iodo-5-cyclodextrin, 9 Scheme XXII KI ~ Ii 9 A round bottom flask with a magnetic stirbar and a Schienk adapter is 25 charged with 8, 15 equivalents of potassium iodide, and DMF. The resulting mixture is heated at 80 'C for 3 h, after which the reaction is allowed to cool to room temperature. The mixture is then filtered to remove the precipitate and the filtrate evaporated to dryness and redissolved in water at 0 *C. Tetrachloroethylene 91 is added and the resulting slurry stirred vigorously at 0 *C for 20 minutes. The solid 9 is collected on a medium glass frit, triturated with acetone and stored over P 2 05. Example 10: Synthesis of Cysteamine-p.-Cyclodextrin, 10 5 Scheme XXIV HS N 10 To a solution of 9 in 100 mL of degassed water is added 1 eq. of freshly sublimed cysteamine. The solution is stirred under reflux for 2 h. After 10 cooled to room temperature and acidified with 1 N HC), the solution is applied to a Toyopearl SP-650M ion-exchange column (NH 4 form) and the product is eluted with an ammonium bicarbonate gradient. Appropriate fractions are combined and lyophilized to dryness to yield 10. 15 Example 11: Synthesis of Gly-CPT 11 (Greenwald et al., Bioorg. Med Chem., 1998, 6, 551-562) Scheme XXV Bo-c-ly N ->. _ N_ HO ~0 .

OTFA 0 TFN 0 F 11 20 t-Boc-glycine (0.9 g, 4.7 nmol) was dissolved in 350 mL of anhydrous methylene chloride at room temperature, and to this solution were added DIPC (0.75 mL, 4.7 mmol), DMAP (382 mg, 3.13 nunol) and camptothecin (0.55g, 1.57 mmol) at 0 *C. The reaction mixture was allowed to warm to room temperature 25 and left for 16 h. The solution was washed with 0.1 N HCI, dried and evaporated under reduced pressure to yield a white solid, which was recrystallized from 92 methanol to give camptothecin-20-ester of t-Boc-glycine: 'H NMR(DMSO-d 6 ) 7.5-8.8 (m), 7.3 (s),5.5 (s), 5.3 (s), 4 (in), 2.1 (m), 1.6 (s), 1.3 (d), 0.9 (t). Camptothecin-20-ester of t-Boc-glycine (0.595 g, 1.06 mmol) was dissolved in a mixture of methylene chloride (7.5 mL) and TFA (7.5 mL) and stirred at room 5 temperature for 1 h. Solvent was removed and the residue was recrystallized from methylene chloride and ether to give 0.45 g of 11. 'H NMR (DMSO-d 6 ) 87.7-8.5 (m); 7.2 (s), 5.6 (s), 5.4 (s), 4.4 (m), 2.2 (m), 1.6 (d), 1.0 (t), "C NMR (DMSO-d 6 ) 5168.6, 166.6, 156.5, 152.2, 147.9, 146.2, 144.3, 131.9, 130.6, 129.7, 128.8, 128.6, 128.0, 127.8, 119.0, 95.0, 77.6, 66.6, 50.5, 47.9, 30.2, 15.9, 7.9. BSI/MS (m/Z) 10 expected 405; Found 406 (M+H). Example 12 Synthesis of GlyGlyGly-CPT 12 Scheme XXVI 15 t-Boc-GlyGlyGly (1.359 g, 4.7 mmol) was dissolved in 350 mL of anhydrous methylene chloride at room temperature and to this solution were added DIPC (0.75 mL, 4.7 mmol), DMAP (382 mg,.3.13 mrnol) and camptothecin (0.55g, 20 1.57 mmol) at 0 *C. The reaction mixture was allowed to warm to room temperature and left for 16 i. The solution was washed with 0.1 N HCI, dried and evaporated under reduced pressure to yield a white solid, which was recrystallized from methanol to give camptothecin-20-ester of t-Boc-GlyGlyGly: 'H NMR(DMSO-ds) 5 8.40 (s), 8.25 (d), 7.91 (d), 7.78 (m), 7.65 (t), 7.26 (s), 7.05 (br, s), 5.65 (d), 5.40 (d), 25 5.25 (s), 5.10 (br, s), 3.75-4.42 (m), 2.15-2.35 (im), 1.45 (s), 0.95 (t) Camptothecin 20-ester of t-Boc-GlyGlyGly (1.5 g, 1.06 nmol) was dissolved in a mixture of inethylene chloride (10 mL) and TFA (10 mL) and stirred at room temperature for 1 i. Solvent was removed tinder vacuum and the residue was re-dissolved in inethylene chloride. The solution was poured into ether to give instant precipitate 93 (yellow). The precipitate was filtered and washed with cold ether to give 1.31 g of 12. 'H NMR (DMSO-d 6 ) 8 8.79 (s), 7.75-8.61 (m), 7.10 (s), 5.55 (s), 3.90-4.37 (m), 3.86 (s), 3.54 (s), 2.11-2.23 (m), 0.95 (t). ESI/MS (m/z) expected 519; Found 520 (M+H). 5 Stability of CPT-Peptide ester bond 11 and 12 were dissolved in PBS buffer (pH 7.4) at room temperature to prepare a solution about 500 pg/mL. This solution was further diluted in 8.5%

H

3 P0 4 to 10 pg/nL. Hydrolysis rate was analyzed using HPLC equipped with a Cis 10 RP (reverse phase) column and a fluorescence detector using a 50/50 (v/v) of acetonitrile/potassium phosphate buffer (pH 4.1). The peaks of 11 (or 12) and the released CPT (lactone form) were integrated. The stability of the ester bond in aqueous solution is peptide-length dependant. Thus the drug release rate hydrolysiss rate) can be tuned by adjusting the peptide length. See Figure 2. 15 Lactone Stability of CPT, 11 and 12 in Phosphate Buffered Saline (PBS) CPT, 11 or 12 was dissolved in DMSO at I mg/mL and then diluted to 1 pg/mL with PBS (lx, pH 7.4). 30 pL of solution were injected into the HPLC at room temperature at selected time intervals. The peak area from the CPT lactone form of CPT, 11 or 12) were integrated. 20 The rate of lactone ring opening for 11, 12 and CPT were studied in PBS buffer (pH 7.4). Both 11 and 12 were very stable against ring-opening and no carboxylate forms of 11 and 12 were detected throughout the study (7 hours). On the other hand, more than 60% of the CPT lactone form was transformed to its carboxylate form in the same period of time. (See Fig. 3) 25 Example 13: Synthesis of Lys(BisCBZ)-CPT 13 Scheme XXVII 94 N 0 H N N \CBZ N'C N O Y H O OHO 0 0 0 CBZ-N N-CBZ H H 13 N, N-BisCBZ-Lysine (311 mg, 0.75 mmol) was dissolved in 56 mL of 5 anhydrous methylene chloride at room temperature. To this solution were added DIPC (0.12 mL, 0.75 nmol), DMAP (0.61 mg, 0.5 mmnol) and camptothecin (0.087 g, 0.25 mmol) at 0 *C. The reaction mixture was allowed to warm to room temperature and left for 16 h. The solution was washed with 0.1 N HC, dried and evaporated under reduced pressure to yield a light yellow solid, which was 10 recrystallized from methanol to give camptothecin-20-ester of N,N-BisCBZ-Lys 13. Purification of 13 was satisfactory based on TLC and HPLC analysis. Hydrolysis of 13 in aqueous solution is very slow and cannot be detected using HPLC equipped with a UV detector. Hydrolysis rate of the ester bond of CPT-peptide linker can be tuned not only by adjusting the length of peptide, as 15 shown in Example 12, but also by using different amino acid linked directly with CPT's 20-OH. The transformation of lactone form to carboxylate form of CPT and 13 were also tested in PBS buffer. It was found that the transformation of lactone form to carboxylate form of compound 13 was much slower than that of free CPT, 20 indicating that lactone form (drug active form) can be stabilized by fonning an ester with the -OH of CPT at its 20 position. (See Fig. 4) Example 14 Synthesis Lys-Gly-CPT 14 11 is dissolved in chloroform. N, N-DiBoc-Lys-NHS (1.0 eq) is added 25 followed by triethylamine (1.0 eq). The mixture is stirred at rt for 16 hours and extracted twice with water and then dried with MgSO4. Solvent is removed under 95 high vacuum to yield N, N-DiBoc-Lys-Gly-CPT. To this compound is added a mixture of equal volume CH 2 C1 2 and TFA and stirred at rt for i h. The solvent is then removed under vacuum. The residue is redissolved in CHC1 3 . Ether is added to the solution to crash out the product 14. The precipitate is washed several times 5 with ether and then dried under vacuum. It is purified using a silica gel column chromatography to yield 14 in pure TFA salt form. Example 15 Synthesis of Suc-Gly-CPT 15 A solution of succinic anhydride is mixed with 11 (1 eq) in dry CHCl 3 in the presence of a catalytic amount of DMAP and DIBA (1 eq). The mixture is stirred at 10 rt for 24 hours to yield 15. 15 is purified by crystallization. Example 16 Synthesis of Glu-Suc-Gly-CPT 16 15 is converted to its NHS ester using traditional DCC/NHS method. The NHS ester of 15 is then reacted with glutamic acid (1.0 eq) in DMSO in the presence of triethylamine. The solution is added to ether to precipitate 16. 16 is purified by 15 crystallization. Example 17 Synthesis of Glu-Bis(GlyCPT) 17 11 and Boc-Glu(NHS)-NHS (0.4 eq) are mixed in CHCi 3 under argon before triethylamine (I eq) is added to the mixture. The solution is stirred at rt for 16 h and 20 then washed with acidic water. The organic layer is dried and then solvent is removed under vacuum. The resulting compound is purified using a silica gel column chromatography. The purified compound is then dissolved in an equal volume mixture of TFA and CH 2

CI

2 . The mixture is stirred at rt for I h and then poured into ether. The precipitate 17 is washed with ether and dried under vacuum. 25 Example 18 Synthesis of Cyclodextrin-Camptothecin 18 Scheme XXVIII 96 ~'N ' 00 N .0 N N N cocN CD-NH 2 N 00 0 HO~ 0 0 0HO o CPT-CD O-< 0 18 CPT (197 ag, 0.566 mmol) was vacuumed for 30 minutes. Dry chloroform 5 (100 mL) was added under argon. Phosgene (1.34 mL, 20% in toluene solution) was added at 0 'C. Ice bath was removed and the solution was warmed up to room temperature. Two hours later solvent was removed under high vacuum. Dry DMSO (50 mL) was added to the residue, followed by 200 mg CD-NH 2 (Cyclodextrin Technology, Inc.) and triethylanine (4 mL, excess). 16 hours later, the solution was 10 poured into 200 mL ether. Precipitate was washed with ether extensively and then dried. 167 mig yellow powder (18) was obtained (62% yield). TLC analysis (silica gel) of 18: Rf= 0 (developed with CHCls/MeOH v/v -5/1). TLC analysis of CPT: Rr= 0.65 (developed with CHC13/MeOH v/v =5/1). Solubility: >10 mg/mL in water. This indicates that solubility of CPT in water can be substantially increased 15 when it is covalently attached to cyclodextrin molecule (free CPT solubility in water <0.004 mg/mL). Example 19. Synthesis of CDDC-Dianhydride Copolymer 19,21 and its CPT conjugate 20, 22 Scheme )XIX 97 0OMX H oH H 0 0 19 a octcpT TFA-CJyCPT S O oolCPT 20 d-0 21 0 0 A: Ethylenediamine tetraacetic dianhydride (25.6 mg, 0.1 mmol) and CDDC 5 (3, 125.3 mg, 0.1 mmol) were dissolved in 2 niL of dry DMSO. The solution was heated at 50 *C for 72 h. Water was added to the mixture, followed by addition of 1 N NaOH to pH around 12. The polymer was dialyzed in 10,000 MWCO membrane for 24 h. Precipitation was observed in the dialysis membrane. The solid was removed and the remaining solution was dialyzed again in 10,000 MWCO 10 membrane for 24 h. A white powder 19 (75 mg) was obtained after lyophilization. 11 is added to the polymer (19)/DMSO solution in the presence of EDC (2 eq), Ni-S (1 eq), and DIBA (1.0 eq). The solution is stirred for 16 h and then poured into ether. The precipitate is washed with CH 2 Cl 2 extensively until no free drug is observed in the washing solution. Compound 20 is obtained after drying under high 15 vacuum. B: Diethylenetriamine pentaacetic dianhydride (8.5 mg, 0.024 mmol) and CDDC, 3 (30 mg, 0.024 mmol) were dissolved in 1-nethyl-2pyridinone (2 mL). 98 The mixture was stirred at 64 C for 4 days and then dialyzed in 10,000 MWCO membrane for 2 days. A white powder 21 (3 mg) was obtained after lyophilization. 11 is added to the polymer (21)/DMSO solution in the presence of EDC (2 eq), NHS (1 eq), and DIEA (1.0 eq). The solution is stirred for 16 h and then 5 precipitated in ether. The precipitate is washed with CH 2 C1 2 extensively until no free drug is observed in the washing solution. Compound 22 is obtained after drying under high vacuum. Example 20 Synthesis of CCD-Cys Copolymer 23 and its CPT conjugatc 24 Scheme XXX HNS 23 COOH 1-CPT TFAilyCPT 24 10 CCD 1 (141.3 mg, 0.1 mmol) and cystine (24 mg, 0.1 mmol) were dissolved in dry DMSO (0.3 mL) and pyridine (0.1 mL). The mixture was stirred under argon 15 for overnight at 72 C. Water (10 mnL) was added. Precipitate was filtered and the filtrate was dialyzed in 10,000 MWCO membrane (Spectra/Por 7) for 48 h. A white powder 23 (8 mg) was obtained. 11 is mixed with 23 in DMSO. EDC (2 eq), NHS (1 eq), and DIEA (1.0 eq) are added to the solution. The solution is stirred for 16 h and then precipitated with 20 ether. The precipitate is washed with CH 2

C

2 extensively until no free drug is observed in the washing solution. Compound 24 is obtained after drying under high vacuum. 99 Example 21 Synthesis of CD-BisGlu-Diamine Copolymer 25 and its CPT conjugate 26 5 Scheme XXXI Tt'A.GK~PT 0YP 25 26 CD-Bis(Glutamic acid-y-Benzyl ester) 6 and ethyleneglycolbisethylamine 10 are dissolved in dry DMSO. EDC (3 eq) and Sulfo-NHS (2 eq) are added to the mixture. The solution is stirred under argon for 2 days at rt. The solution is then transferred to a 10,000 MWCO dialysis membrane and dialyzed for 48 hours. After lyophilization a white powder is obtained. The solid is then dissolved in DMSO and methanol solvent mixture and treated with H 2 in the presence of 10% Pd/C catalyst 15 for 24 hours. The solution is poured into ether to crash out the product. 25 is obtained after drying under vacuum. 11 is mixed with 25 in DMSO solution. EDC (2 eq), NHS (I eq), and DIEA (1.0 eq) are added to the solution. The solution is stirred for 16 hrs and then precipitated with ether. The precipitate is washed with CH 2 C1 2 extensively until no 20 free drug is observed in the washing solution. Compound 26 is obtained after drying under high vacuum. Example 22 Synthesis of CDDM-Lys(GlyCPT) Polymer 27 25 Scheme XXXII 100 oepr 0 AN 27 OLCP CDDM, 5, and Lys-Gly-CPT, 14, are dissolved in dry DMSO. EDC (3 eq) 5 and Sulfo-NHS (2 eq) are added to the mixture. The solution was stirred under argon for 2 days at rt. The solution is then poured into ether. The precipitate 27 is dried under vacuum. Example 23 Synthesis of CDDC-Cys(Boc) Copolymer 28, CDDC-CysCopolymer 29 and its CPT Conjugate 30 10 Scheme XXXIU HN, 0 OWNH s 28 * ar H 0 ircPTP MC Hk-Y G 1 CPT HN 0 30 101 CDDC (3) and NN-DiBoc-Cystine are dissolved in dry DMSO. EDC (3 eq) and Sulfo-NHS (2 eq) were added to the mixture. The solution was stirred under argon for 2 days at rt. The solution is then transferred to a 10,000 MWCO dialysis membrane and dialyzed for 48 hours. After lyophilization a white powder, CDDC 5 Cys(Boc) polymer 28, is obtained. To the white powder 28 is added a mixture of HCI and DMSO solution. The solution is stirred at it for 1 h and then dialyzed against water for 24 i using 10,000 MWCO membrane. 29 is obtained as a white solid. Suc-Gly-CPT 15 is mixed with 29 in DMSO solution. EDC (2 eq), NHS (1 10 eq), and DIEA (1.0 eq) are added to the solution. The solution is stirred for 16 h under argon and then precipitated with ether. The precipitate is washed with ether until no free drug is observed in the washing solution. Compound 30 is obtained after drying under high vacuum. 15 Example 24 Synthesis of biodegradable CD-Polyphosphoester Polymer 31 and its CPT conjugates 32 Scheme XXXIV o ^ -o- -0-o-a+ o o H Hc - II -o- -o--.--o -oL- H 2 NH OCPT 0 1VA-0IyCPr 32 20 Synthesis of the biodegradable polyphosphoester can be found in Wang J et al, JACS, 2001, 123,9480-9481. 102 Polyphosphoester is mixed with 10 (0.5 eq of repeat unit) in DMSO. EDC (2 eg), NHS (1 eq), and DIEA (1.0 eq) are added to the solution. The solution is stirred for 16 hrs and then precipitated with ether. The obtained CD-polyphosphoester 31 is dissolved in DMSO. To the solution is added 11 (0.5 eq of repeat unit), EDC (2 eq), 5 NHS (1 eq), and DIEA (1.0 eq). The solution is stirred for 16 h and then precipitated with ether. The precipitate is washed with ether extensively until no free drug is observed in the washing solution. Compound 32 is obtained after drying under high vacuum. 10 Example 25 Synthesis of CD Copolymer-CPT conjugate 33 with polyethylene backbone via radical polymerization Scheme XXXV n M o 0 0 0 0 0 0 AIBN orATRP \ 0 HN 0 0 33 15 Acrylate monomers of CPT, triethyleneglycol monoiethylether, and CD monocystamine can be synthesized from N-Acryloxysuccinimide (Polysciences, Inc.). These monomers are mixed in 1:1:1. ratio in dry DMSO. AIBN is added to the mixture under argon. The solution is stirred at rt for 24-48 hrs until the solution becomes viscous. Polymer-CPT conjugate 33 is precipitated with ether and dried 20 under vacuum. Example 26 Synthesis of CD-grafi-poly(ethylene-alt-maleic anhydride) GlyGlyGlyCPT 34 Scheme XXXVI 103 T 0 a 0 0 0 0 0 00 340 Poly(ethylene-alt-maleic anhydride) (Aldrich) is dissolved in DMSO. 10 (0,4 5 eq of repeat unit) and 12 (0.4 eq of repeat) are added. The solution is heated at 70 'C for 16 hrs and then precipitated with ether. The obtained CD-graft poly~ethylene-alt-maleic anihydride)-GlyGlyGlyCPT 34 is dried under high vacuum. 10 Example 27 Synthesis of Polyglutamate-CD-CPT Conjugate 35 Scheme XXXVII 104 Polyglutamate (from Sigma-Aldrich) is mixed with 10 (0.5 eq of repeat unit) and 11 (0.5 eq of repeat unit) in DMSO. EDC (3 eq), NHS (2 eq), and DIEA (1.0 eq) are added to the solution. The solution is stirred for 16 hr and then precipitated with ether. After drying under high vacuum, polyglutamate-CD-CPT conjugate 35 is obtained. 5 Example 28: Synthesis and Characterization of CD-BisCys-Peg3400 Copolymers 36 and their CPT Conjugates 37. A. Synthesis and Characterization of CD-BisCys-Peg3400 Copolymers 36 10 Scheme XXXVIIIa o oro0 o V~~~O 0 oo HO noH 0 oHn OH HO<H PEG-DiSPA (MW = 3400 kDa) H " on o on DMSO/DIEA, TEA or DMAP O on -a 4 36a-f Poly(CDDCys-PA-PEG) Abbr: PA = propanoicamide bond between PEG and CD Scheme XXXVIIIb H HH o OH HQH0 O H OH OH HOHOA HO HOHo Comonomer BB OH0 H O H O H DM SO/DIEA S OH O H O OHV 36g-i N 36g R = PEG-DiSBA (MW = 3400 kDa) Poly(CDDCys-BA-PEG) 36h R = PEG-DiBTC (MW = 3400 kDa) Poly(CDDCys-CB-PEG) O O NO 36i R- = r 0 PEG-DiNPC (MW = 3400 kDa) Poly(CDDCys-CB-PEG) Abbr: BA = butanoicarnide bond; CB = carbanate bond - 105 - Synthesis of Poly(CDDCys-PA-PEG), 36n 4 (after precipitation with acetone, 63 mg, 0.047 mmol) and PEG-DiSPA (MW 3400, 160 mg, 0.047 mmol) were dried under vacuum for 8 hours. Anhydrous DMSO (1.26 mL) was added to 5 the mixture under argon. After 10 minutes of stirring, anhydrous diisopropylethylamine (DMA, 19 jL, 2.3 eq.) was added under argon. The reaction mixture was stirred under argon for 120 h. The polymer containing solution was dialyzed using a 10,000 MWCO membrane (Spectra/Por 7) against water for 48 h and lyophilized to yield 196 mg 36a (90%, Table 1). M, = 57.4 kDa, M= 41.7 10 kDa, MWM,, = 1.38. 1 H NMR (D 2 0) 8 5.08 (m, CD-2-H), 4.27 (m, Cys-CH), 2.72 3.76 (m, CD-3,4,5,6-CH, CD-CH 2 , PEG-CH 2 ), 2.44 (m, Cys-CH 2 ). Synthesis of other poly(CDDCys-PA-PEG) (36b-f), Poly(CDDCys-BA-PEG) (36g) Poly(CDDCys-CB-PEG) (36h1-i) were achieved under polymerization condition similar to that of 36a. Details for the polymerization conditions, monomer 15 selection, polymer molecular weight, polydispersity and yields are listed in Table 1. 36g: 'H NMR (D 2 O) 8 5.10 (m, CD-2-H), 4.25-4.37 (m, Cys-CH), 2.72-3.86 (m, CD-3,4,5,6--CH, CD-CH 2 , PEG-CH 2 ), 2.21 (M, Cys-CH 2 ). 36h-i: '1H NMR (D 2 0) 8 5.05 (m, CD-2-H), 4.56 (m, Cys-CH), 2.70-3.93 (in, CD-3,4,5,6-CH, CD-CH 2 , PEG

CH

2 ), 2.38 (ma, -OCHCH 2

CH

2 C(O)-NH-), 2.34 (m, Cys-CH 2 ), 1.90 (m, 20 OCH 2 CH2CH 2 C(O)-NH-). Addition of a non-nucleophilic organic base (such as DIEA) was essential for this polymerization as no viscosity changes of the polymerization solutions were observed after 48 hours if no base was added. When 2.3 eq. of DIEA were added, 25 the viscosity of the polymerization solution increased dramatically after 4-6 hours of reaction. DIEA deprotonates the amino groups of 4 to render them more nucleophilic for coupling with PEG-DiSPA. There were essentially no differences in the polymerizations if other bases, -such as TEA or DMAP, were used (36b-c, Table 1). Polymerization using 4 recovered by the two different precipitation methods 30 (acetone and methanol) produced polymers with different MWs. 4 that was purified by the methanol-precipitation method (contains no free cystine) gave higher MW polymer (36d-e) as compared to the less pure 4 that was obtained from the acetone 106 precipitation method (36a). Polymerization of 4 with PEG-DiSPA typically produced polymer yields greater than 90%. 4 was polymerized with other activated monomers such as PEG-DiSBA, PEG 5 DiBTC, and PEG-DiNPC. Reaction of 4 with PEG-DiSBA gave polymer 36g with similar linkages as 36n-f (amide bond, but one more -CH 2 group than 36a-f at the linker) with M, over 100 kDa, while reaction of 4 with PEG-DiBTC and PEG DiNPC generated polymers 36h and 36i, respectively, with connecting carbamate moiety and M,'s over 50 kDa (Table L). 10 Table 1. Polymerization of 4 with difluctionalized PEG PEG Polymerization MI M,, M,/ Yield CDP Base Comonomer time (h) (kDa) (kDa) M, (%) 36n" PEG-DiSPA DIEA 120 57.4 41.7 1.38 90 36b" PEG-DiSPA DMAP 120 54.2 38.1 1.42 91 36c' PEG-DiSPA TEA 120 57.4 42.6 1.35 91 36d PEG-DISPA DIEA 120 93.6 58.0 1.48 96 36eb PEG-DiSPA DIEA 144 97.3 58.0 1.67 94 3 6 0b PEG-DiSPA DIEA 2 35.3 25.6 1.38 95 36g PEG-DiSBA DIEA 120 114.7 77.9 1.47 96 36h PEG-DiBTC DIEA 120 67.6 39.4 1.47 95 36i PEG-DiNPC DIEA 120 86.5 57.2 1.51 96 " 4 was washed with acetone before polymerization. 15 b 4 was washed with methanol before polymerization. Polymers 36a-i are highly soluble in aqueous solution, They can be easily dissolved in water or phosphate buffered saline (PBS) solution at concentrations of at least 200 mg/mL. Solubility of these polymers in aqueous solution at 20 concentrations higher than 200 mg/InL was not attempted due to the high viscosity. These polymers were also soluble in DMF, DMSO and methanol, slightly soluble in CH3CN and CHC 3 , but insoluble in THF and ethyl ether. 107 Molecular Weight Control of CD Polymers 4 (after precipitation with methanol) (56.2 mg, 0.0419 mmol) and PEG-DiSPA (147 mg, 0.0419 mmol) were dried under vacuum for 4-8 hours. To the mixture was added dry DMSO (1.1 mL) under argon. After 10 minutes stirring, DIEA (16 uL, 2.2 eq) was added under argon. A 5 portion of polymerization solution (150 uL) was removed and precipitated with ether at selected times (2 h, 18 h, 43 h, 70 h, 168 h and 288 h). MWs of the precipitated polymers were determined as described above. As shown in Figures 5a and 5b, molecular weights of 36 can be controlled by adjusting polymerization time. 10 B. Synthesis of Poly(CDDCys-PA-PEG)-CPTConjugates (HGGG6, LGGG1O, HG6, HGGG1O). Scheme XXXIX 0 0 N O OH N ~H OH ON kC O H H N EDSmNHS H O mN DHHO O O TFA-NH2 O OO &~000 11 0 N OH orNorf OH OY N O EDC/NHS S HO O O O0 H OHO0 TFA NNH O H HO O 12 0 04 N ~NA J 15 - 108 - Synthesis of Poly(CDDCys-PA-PEG)-GlyGlyGly-CPT (HGGG6) 36e (1.37 g, 0.30 mmol of repeat unit) was dissolved in dry DMSO (136 mL). The mixture was stirred for 10 minutes. 12 (419 mg, 0.712 nunol, 2.36 eq), DIBA (0.092 mL, 0.712 mmol, 2.36 eq), EDC (172 mg, 0.903 mmol, 3 eq), and NHS (76 mg, 0.662 5 mmol, 2.2 eq) were added to the polymer solution and stirred for ca. 15 hours. The polymer was precipitated with ethyl ether (1 L). The ether was poured out and the precipitate was washed with CH 3 CN (3 x 100 mL). The precipitate was dissolved in water 600 mL. Some insoluble solid was filtered through 0.2 pm filters. The solution was dialyzed using 25,000 MWCO membrane (Spectra/Por 7) for 10 h at 10 10-15 *C in DI water. Dialysis water was changed every 60 minutes. The polymer drug conjugate solution was sterilized by passing it through 0.2 yM filters. The solution was lyophilized to yield a -yellow solid HGGG6 (1.42 g, 85% yield). Synthesis of Poly(CDDCys-PA-PEG)-GlyGlyGly-CPT (LGGG10) Conjugation of 12 to 36f was performed in a manner similar to that used to produce 15 HGGG6 except that this conjugate was dialyzed with 10,000 MWCO membrane (Spectra/Por 7) instead of with 25,000 MWCO membrane. The yield of LGGGIO was 83%. Synthesis of Poly(CDDCys-PA-PEG)-Gly-CPT (HG6) Conjugation of 11 to 36e was performed in a manner similar to that used to produce HGGG6. The 20 yield of HG6 was 83%. Synthesis of Poly(CDDCys-PA-PEG)-GlyGlyGly-CPT (HGGG10) 36c (1.5 g, 0.33 mmol of repeat unit) was dissolved in dry DMSO (150 mL). The mixture was stirred for 10 minutes. 12 (941 mg, 1.49 mmol, 4.5 eq), DIBA (0.258 mL, 1.49 mmol, 4.5 eq), EDC (283 mg, 1.49 mmol, 4.5 eq), and NHS (113 ng, 0.99 mmol, 3 25 eq) was added to the polymer solution and stirred for ca. 24 hours. Another portion of EDC (142 mg, 0.75 mmol, 2.3 eq) and NHS (56 mg, 0.5 mmol, 1.5 eq) were added to the conjugation solution. The polymer was stirred for an additional 22 hours. The workup procedure was the same as that for the synthesis of HGGG6. The yield of HGGG1O was 77%. 30 Determination of wt% CPT on the Conjugates Stock solutions of HGGG6, LGGG1O, HG6 and HGGG1O were prepared at a concentration of 10 mg/mL in DMSO. An aliquot of corresponding stock solution was diluted to 100 109 pg/mL using 1 N Na.OH. CPT was completely hydrolyzed in this basic solution and transformed to its carboxylate form within 2 h at room temperature. An aliquot of this solution was diluted to 10 pg/mL using 8.5% H 3 P0 4 , and the CPT carboxylate form was transformed to its lactone form. 30 puL of this solution was injected into 5 the HPLC. The peak area from the CPT lactone form was integrated and compared to a standard curve. 11 and 12 were conjugated to 36e or 36f (Table 2) using conventional coupling methods. Due to the instability of the ester linker of 11 and 12 in aqueous solution, the conjugation was conducted in anhydrous DMSO under argon. An 10 organic base was required to deprotonate the TFA salts of 11 and 12 to facilitate the coupling. For polymer conjugation with 12, the weight percent (wt%) drug loading was around 6-10%. The theoretical maximum drug loading is around 13% using PEG with MW of 3400 Da; maximum values can be increased by decreasing the MW of the PEG segments. Solubilities of all conjugates in water or PBS were more 15 than 200 ing/mL (equivalent to a 12-20 mg CPT/mL for 6-10 wt% drug loading, respectively). Details for the HGGG6, LGGG10, HG6, and HGGG1O are summarized in Table 2. Table 2. Properties of polymer-CPT conjugates. M, of parent polymer ik t Conjugate' .X M0/14 Linker CPT (wt%) (x 10 ) HGGG6 97 1.7 triglycine 6.1 LGGG1O 35 1.6 triglycine 10.2 HG6 97 1.7 glycine 6.8 HGGG1O 97 1.7 triglycine 9.6 20 "Abbreviations: H = High M, polymer (97 kDa), L = Low M, polymer (35 kDa), GGG = triglycine linker, G = glycine linker, 6= drug loading around 6 wt%, 10= drug loading around 10 wt%. b Polymer polydispersity as measured by light scattering techniques(26) 110 C. Release of CPT from HGGG6 and HG6 Release of CPT in PBS HGGG6 and HG6 were prepared at 1 mg/mL in PBS (1x, pH 7.4). A 100 pL aliquot of the solution was transferred to a 1.5 nL Eppendorf 5 tube and incubated at 37 *C. The incubated samples were quenched at selected time intervals and stored at -80 "C until the analysis. Each solution was diluted with 8.5% H3PO4 to a 5 mL total volume in a volumetric flask. 30 pL of such solution was injected into the HPLC. The peak area from the CPT lactone form was integrated and compared to a standard curve. 10 Analysis for the release of CPT from HGGG6 and HG6 in PBS containing acetyl cholinesterase (an esterase, 100 units/mL), in KH2PO 4 buffer (pH 6.1, 0.1 M) and in the KH 2

PO

4 buffer (pH 6.1, 0.1 M) containing cathepsin B (a cysteine proteinase, 200 pM, preactivated on ice for 30 minutes in this buffer containing 2 mM DTT and 1 mM EDTA) were performed in a manner similar to that described 15 above for PBS alone. Release ofCPT in Human Plasma An aliquot of HGGG6 and HG6 stock solution were diluted to give final concentration of 0.5 mg/mL in PBS (1x, pH 7.4). This solution was added to a lyophilized powder of human plasma to reconstitute 100% human plasma by the recommended amount. The solution was divided into 20 equal volume (250 uL) to 1.5 mL Eppendorf tubes, incubated at 37 *C, and stopped at selected time point. Samples were stored at -80 *C until the analysis. Samples were separated from plasma by solid phase extraction columns. The solid phase extraction cartridge (Oasis HLB Ico cartridge from Waters) was pre-conditioned with I mL of acetonitrile and then with I mL of 8.5% H 3

PO

4 before loading. 25 Samples were acidified with equal volume of 8.5% H3PO4 prior to loading. After the acidified solution was loaded on the cartridge, the bed was washed with 3 x 1 mL of water. Released CPT and polymer conjugate were eluted with 3 x I mL of a solution mixture of acetonitrile and potassium phosphate buffer (pH 4.1) (60/40 v/v). The eluted solution was diluted to 5 mL total volume in a 5 mL volumetric flask. 30 30 pL of such solution was injected into the HPLC. The peak area from the CPT lactone form was integrated and compared to a standard curve. 111l Release of CPT from HGGG6 and HG6 in PBS containing 4% human plasma (PBS/reconstituted human plasma solution = 96/4 (v/v)), in mouse plasma and in reconstituted human albumin (PBS solution) were performed in a manner similar to that described above for pure human plasma. 5 In PBS (lx, pH 7.4), the half-lives (t, 1 2 ) for releasing CPT from HG6 and HGGG6 were 59h and 32h, respectively. The half-lives decreased to 25h and 22h, respectively, in the presence of 4% human plasma, and to 1.7h and 1.6h, respectively, in 100% human plasma ("HP") and 2.6h and 2.2h, respectively, in 100% mouse plasma ("MP"). CPT release rates for both HG6 and HGGG6 in the 10 presence of albumin ("Alb") or acetyl cholinesterase ("Ac Clio") were on the same order of magnitude as in PBS. In a buffer solution at a pH lower than PBS (pH 6.1) with or without the enzyme cathepsin B (active at pH 6.1), less than 50% of total conjugated CPT was released from both HG6 and HGGG6 for times up to 144 h (Table 3). 15 Table 3. Half-life (t, in hour) of the release of CPT from HG6 and HGGG6a 20 4%pH61 CtB Conjugate PBSb HP W Alb' Ac Chog pH 6.1 Oath B HP . buffer (pH 6.1)' HG6 59 25 1.7 2.6 62 33 >144 > 144 HGGG6 32 22 1.6 2.2 73 43 >144 >144 a tin is defined as time (hours) for the release of half of the total conjugated CPT. Abbreviations: HP means human plasma, MP means mouse plasma. b pH 7.4 PBS lx buffer. 25 C Reconstituted human plasma mixed with PBS (v/v = 4/96). d Reconstituted human plasma *Fresh mouse plasma 112 rIn reconstituted human albumin PBS buffer 9 In the presence of acetyl cholinesterase PBS solution (100 units/mL). h pH 6.1 phosphate buffer (0.1M) pH 6.1 phosphate buffer in the presence of Cathepsin B 5 Release of CPT in Solution at DifferentpH. HGGG6 and HG6 were prepared at 1 mg/nmL in buffer solution with pHs ranging from acidic (pH = 1.2) to basic (pH = 13.1) and incubated at 37 "C for 24h. An aliquot of each solution was diluted with 8.5% H 3 P0 4 to about 100 pg/mL. 30 pL of such solution was injected into HPLC. The peak area from the CPT lactone form was integrated and compared 10 to a standard curve. The pH of aqueous solution has a significant effect on the CPT release rates from both HG6 and HGGG6. The amounts of CPT released from HG6 and HGGG6 at 37 *C after 24 h in buffer solutions with pHs ranging from 1.1 to 13.1 15 are illustrated in Figure 6. The glycinyl-CPT ester bonds of both HG6 and HGGG6 were very stable in acidic pH (1.1 to 6.4) as less than 7% of CPT were released in 24 h. ICso via MTT Assay The human ovarian carcinoma A2780 cell line was 20 obtained from the European Collection of Cell Cultures (Salisbury, Wiltshire, UK). The human colorectal adenocarcinoma -T29, human prostate carcinoma PC-3, and human colonic adeoncarcinoma LS174T cell lines were obtained from the American Type Culture Collection (Rockville, MD). Cells were seeded in 96-well plates at 5000 cells/well and grown in medium containing 10% fetal bovine serum at 37 *C 25 for 24 h in a humidified 5% CO 2 atmosphere. The medium was replaced with fresh medium containing CPT, 36e, HGGG6 or HG6 in concentrations ranging from I nM to 10 pM of CPT and 36e (CPT equivalent for HGGG6 and HG6). At each concentration three wells per plate were treated. The effect of the compounds on cell growth was measured by the MITT assay after 72 h. The medium was removed, 30 the cells were rinsed with PBS, MTT solution was added at a concentration of 0.5 mg/nL, and the plates were incubated for 4 h at 37 *C. The medium was removed and the formazan crystals were solubilized in DMSO. Absorbance was measured at 113 560 nm using a SPECTRAFluor Plus plate reader (Tecan, Durham, NC). The percentage of cell survival was calculated relative to untreated cells, and IC 50 's were determined from plots of dose versus cell survival. ICSO data of CPT, 36e, HGGG6 or HG6 are listed in Table 4. 5 Table 4. ICo of CPT, unconjugated polymer 36e and CPT conjugates HG6 and HGGG6 in various cell lines Cell Line 36e (pM) CPT (pM) HG6 (pM) HGGG6 (pM) LS174T >300 0.005 0.050 0.010 HT29 300 0.020 0.050 0.030 A2780 100 0.007 0.025 0.020 PC3 >300 0.075 0.25 0.15 10 Example 29: Poly-CD-BisCys-Peg3400-Ala-CPT 37 36e (54 mg, 0.012 mmol of repeat unit) was dissolved in dry DMSO (226 nL) and stirred for 10 minutes. TFA-Ala-CPT which is prepared similar to 11 (15 mg, 15 0.028 mmol, 2.36 eq), DIBA (4.88 mL, 0.028 mmol, 2.36 eq), DCC (24.52 mg, 0.12 mmol, 10 eq), and NHS (13.6 mg, 0.12 mmol, 10 eq) were added to the polymer solution. The mixture was stirred for about 16 hours. The polymer was precipitated with ether (40 mL) and washed with ether (2 x 30 mL) and with CH3CN (2 x 10 mLr). It was then redissolved in pH 4 aqueous solution (10 mL) and dialyzed at room 20 temperature for 48h using 25,000 MWCO membrane. The solution was then passed through a sterilized 0.2 pum filter and then lyophilized to yield 37(46 mg, 85%). Weight percent of drug loading was calculated to be 5.5% using HPLC equipped with a fluorescence detector after releasing CPT from 37 using base. Free CPT in 37 is <1%. 25 Example 30: Poly-CD-BisCys-Peg3400-Leu-CPT 38 114 36e (54 mg, 0.012 mmol of repeat unit) was dissolved in dry DMSO (226 mL) and stirred for 10 minutes. TFA-Leu-CPT which is prepared similar to 11 (16 mg, 0.028 mmol, 2.36 eq), DIBA (4.88 mL, 0.028 mmol, 2.36 eq), DCC (24.52 ing, 0.12 immol, 10 eg), and NHS (13.6 mg, 0.12 mmol, 10 eq) were added to the polymer 5 solution. The mixture was stirred for about 16 hours. The polymer was precipitated with ether (40 mL) and washed with ether (2 x 30 mL) and with CH 3 CN (2 x 10 mL). It was then redissolved in pH 4 aqueous solution (10 mL) and dialyzed at room temperature for 48 h using 25,000 MWCO membrane. The solution was then passed through a sterilized 0.2 pm filter and then lyophilized to yield 38 (42 mg, 78%). 10 Weight percent of drug loading was calculated to be 5.0% using HPLC equipped with a fluorescence detector after releasing CPT from 38 using base. Free CPT in 38 is < 1%. Example 31: Synthesis of CD-BisCys-BisPeg-FITC 39 15 Scheme XXXX 39 4 (25 mg, 0.0186 mmol) and FITC-Peg5000-NHS (Shearwater, 186 mg, 20 0.0373 mmol) were dissolved in dry DMSO (2 mL). DIEA (0.0094 mL, 0.056 mmol, 3 eq) was added to the mixture. The mixture was kept in dark and stirred for 24 hours. Water (10 mL) was then added and the solution was dialyzed in dark using 10,000 MWCO for about 48 hours. After lyophilization a yellow polymer 39 was obtained. Polymer was characterized by MS and 'H NMR. 25 Example 32: Synthesis of Bis-succinimidyl succinatePeg3400 (Bis-SS-PEG) (40a) and biodegradable CD-BisCys-SS-Peg3400 (40b) and its CPT conjugate 41 Scheme XXXXI 115 HOoAH ).o Ho 0 o;i Hx~sx NHS o 00 40a 0 0 S 0 OGly-CPT HO O o O H 40b 0 0 0 CPT-Gy 0 o Gly.CPT 41 A 100 mL round bottom flask equipped with a magnetic stirbar and a septum 5 was charged with 10 g (2.99 mmol) of polyethylene glycol Mw 3350, 2.0 g (20 mmol) of succinic anhydride and 50 mL of anhydrous pyridine. After stirring the solution at 50 'C for 16 h, the solvent was removed by rotary evaporator. The residue was redissolved in 30 mL of water and extracted with 10 mL of chloroform three times. The organic layer was dried over MgSO 4 and filtered. The solvent was 10 then concentrated and precipitated out in diethyl ether. This resulted in 9.6 g of bis succinimidyl Peg3400 at a yield of 90.6%. The product was analyzed by reverse phase columned High Performance Liquid Chromatography. A 100 mL round bottom flask equipped with a magnetic stirbar and a septum was charged with 2 g (0.56 mmol) of bis-succinimidyl Peg3400 and 10 mL of 15 anhydrous dichloromethane. To this solution was added 0.324 g (2.82 mmol) of N hydroxyl succinirnide. The solution mixture was then cooled in an ice bath and added 0.58 g (2.82 mmol) of 1,3-dicyclohexylcarbodiimide. After leaving at room temperature for 24 h, the solution was filtered and precipitated out in 150 mL of diethyl ether. Dissolution in 10 mL dichloromethane and precipitation in diethyl 20 ether was repeated two times. This afforded 1.74 g (82.9 %) of Bis-SS-PEG 40a. It 116 was analyzed by reverse-phase columned High Performance Liquid Chromatography. CD-BisCys-SS-Peg3400 Polymer 40b 5 A 50-mL pearl shaped flask was charged with 100 mg (0.0746 mmol) of 4 and 254 mg (0.0746 innol) of 40a. The combined solids were dried under vacuum for 24 hours before the addition of 1mL of anhydrous DMSO and 2.2 equivalents (0.164 mmol) of DIEA. The solution mixture was stirred at room temperature for 3 days and then precipitated out in diethyl ether. This yielded 100% of 40b. Molecular 10 weight was analyzed on a Hitachi HAPLC system equipped with an Anspec RI detector, a Precision Detectors DLS detector, and a Progel-TSK G3000pwxL column using 0.1 M PBS as eluant at a 0.7 mL-min~' flow rate. M,= 93,000, Mn = 61,000 and M,/M, = 1.5. 15 CD-BisCys-SS-Peg3400-GlyGlyGly-CPT conjugate 41 40b (201.8 mg, 0.044 mmol of repeat unit), TFA-GlyGlyGly-CPT 12 (66 mg, 0.105 mmol, 2.36 eq), EDC (25.5 mg, 0.133 mnol, 3 eq), and NHS (11 mjg, 0.0977 mmol, 2.2 eq) were dissolved in dry DMSO (6 mL) and stirred for 30 minutes. 20 DIEA (19 pL, 0.105 mmol, 2.36 eq), added to the polymer solution. The mixture was stirred for about 41 hours. The polymer was crashed out with diethyl ether (250 imL) and washed with acetonitrile (3x 25 mL). It was then re-dissolved in pH 4 water (10mg/mL) and dialyzed at room temperature for 24 hours using 10,000 MWCO membrane. The solution was then passed through a sterilized 0.2 p~m filter 25 and then lyophilized to yield 41 (128 mg, 52%). Weight percent of drug loading was calculated to be 6.95% using HPLC equipped with a fluorescence detector after releasing CPT from 41 using base. Hydrolysis of 41 was set up in human plasma (100% solution) at I mg/mL. Aliquot solutions (100 pL) were placed in 1.5mL eppendorf tubes and incubated in 30 37 "C water bath. Then, the samples were acidified with 100 jiL of 8.5% H 3 P0 4 and loaded on pre-conditioned solid phase extraction cartridge. It was eluted with 60:40 117 (v/v) acetonitrile: KH 2

PO

4 buffer. Free CPT (lactone form) was analyzed on HPLC/Fluorescence detector using acetonitrile/ KH 2

PO

4 buffer. Half-life was determined to be 3 h. Degradation of CD-BisCys-SS-Peg3400 Polymer 40b 5 50mg/mL of 40b solution was prepared in human plasma reconstituted in PBS (pH 7.4) solution. 100 pL aliquots were incubated at 37 'C. Each sample tube was taken out at a specific time point and crashed out in 900tL cold methanol. The solution was centrifuged and the supernatant was analyzed on a HPLC/ELS detector. The resulting spectrum is shown in Figure 7. 10 Methods for increasing drug weight percent loading Method L Synthesis of CD-BisCys-Peg Copolymer with a short Peg linkage and its GlyCPT conjugate 15 Example 33: Synthesis of CD-BisCys-Peg (short PEG, e.g., Peg200-Peg2000) and its CPT Conjugate 42 Scheme XXXXII N: S SH, O: 0O O N O N HN 0N 20 HN 0 HN 0 o 0 0 0N0 -N -N 20 Synthesis of polymer and drug conjugate 42 are same as 36, 37, and 38 in Example 28. -118- Method . Synthesis of CD-BisCys-Peg Copolymer with iniltiple drug molecides on each loading site. Example 34: Synthesis of CD-BisCys-Peg and its GluBis(GlyCPT) Conjugate 43. 5 Scheme XXXXIII H 0 0 PEG Mw = 3400 2 CPT per CD Maximum drug lending 13.4 % 0 S, S M 1 s s 0o % oPG Mwv = 3400 4 CPT per CD 0 Maximum drug londing 25 % NN N 43 36 and Glu-Bis(Gly-CPT) 17 are dissolved in DMSO. BDC (3 eq), NHS (2.2 10 eq), and DIEA (2.2 eq) are added to the solution. CD-BisCys-Peg-GluBis(GlyCPT) 43 is precipitated with CH3CN and washed with the same solvent until no free drug is detected using UV or TLC. 43 is dried under high vacuum. Example 35: Synthesis of PEI-CD-CPT conjugate 44 (Branched CD-Polymer with 15 CPT conjugates) 119 A: Synthesis of branched PEI-cyclodextrin polymer Scheme XXXXIV NH HN NH, NH 5 PEI (29 mg, Aldrich Mw 25,000) was dissolved in dry DMSO (2 mL). Cyclodextrin monotosylate (448 mg, Cyclodextrin Technologies Development, Inc.) was added to the solution under N 2 . The cloudy solution turned clear after the mixture was stirred at 70 "C for about I hour. The solution turned slightly yellow 10 after 48 hours at such temperature under N 2 . The solution was transferred to a Spectra/Por MWCO 10,000 membrane and dialyzed against water for 4 days. Water was then removed by lyophilization. A white powder was obtained (120-140 mg) after the solution was lyophilized. Cyclodextrin/PEI ratio was calculated based on the proton integration of 'H NMR. 15 B: Synthesis of branched PEI-CD-CPT conjugate Scheme XXXXV 120 H Hi HN -~k\~44 PEI-CD and Suc-Gly-CPT 15 (1.0 eq) are dissolved in DMSO. EDC (3 eq), NHS (2.2 eq), and DIEA (1 eq) are added to the solution. PEI-CD-Gly-CPT 44 is 5 precipitated with ether, washed extensively with this solvent, and dried under high vacuum. Example 36: Synthesis of Ad-PEG 34 o--Ad 45 Scheme XXXXVI 10 0 0 NH2 + N-----CHr-CH2-0-PEGIIO--O-CHr-CH2- 0--N l- -CH r-CH2- 0-PE-G34 - -O- CH r-CH 45 240 mg of 1 -aninoadamantane (1.60 mmol, Aldrich) and 272 mg of 15 PEG 34 oo(SPA) 2 (0.080 mmol, Shearwater Polymers) was added to a glass vial equipped with a stirbar. To this was added 5 mL of dichloromethane, and the solution was stirred overnight. The next day, the solution was filtered to remove the n-hydroxysuccinimide byproduct and the dichloromethane was removed in vacuo. The residue was dissolved in water and centrifuged to remove excess 1.

121 aminoadamantane. The supernatant was then dialyzed overnight in Pierce's Slide A-Lyzer with MWCO=3500. The solution was then lyophilized to afford 248 mg of a white fluffy solid of Ad-PEG4oo-Ad 45. 5 Example 37: Synthesis of DiCyclodextrin PEG 46 362 mg of CD-NH 2 (0.32 mmol, Cyclodextrin Technology, Inc.) and 436 mg of PEG 34 oo(SPA) 2 (0.128 mmol, Shearwater Polymers) were added to a glass vial equipped with a stirbar. To this vial was added 4.36 mL of DMSO, and the solution was stirred for 72 hrs. The solution was dialyzed using 2000 MWCO membrane for 10 4 days in water. 46 (603 mg, 86%) was obtained as a white powder after lyophilization. Example 38: Synthesis of Inclusion polymer 47 using DiAD-Peg 45 and DiCD PEG 46 15 46 (54.6 mg, 0.01 mmol) and 45 (34 mg, 0.01 mmol) were mixed in water (0.27 mL) and stirred for overnight. The solution is very viscous. Polymer 47 was crashed out with ether and dried under vacuum Example 39: Synthesis of Inclusion Polymer CPT-Conjugate 48 between DiCD 20 PEG 46 and a CPT-Di-AD compound Synthesis of diadamantane crosslinker: Bis-(2(1-adamantyl)ethyl)phosphate (Zhang et al., J. Am. Chem. Soc. 1997, 119, 1676-1681) Scheme XXXXVII 2 Pyridine 25 OCF1, OH Anhydrous pyridine (10 mL, Aldrich, Milwaukee, WI) was cooled in an ice bath and methyl dichlorophosphate (1.488 g, 10 mmol, Aldrich, Milwaukee, WI) 30 was added dropwise. The mixture was kept cold for a further 15 min. During this 122 period a precipitate of N-methylpyridinium dichlorophosphate formed. 1 Adamantane ethanol (4.758 g, 26.4 mmol, Aldrich, Milwaukee, WI) was added, and the sealed mixture was stirred overnight at room temperature. It was then poured into 10% NaHCO 3 solution (50 mL) and the pyridine was evaporated under vacuum. 5 The slightly yellow solid was dissolved in I L of water and extracted with ether (three 150 mL portions). The aqueous phase was acidified with 2 N HCl to pH 1, and then extracted with three 150 mL portions of CHCl 3 :n-BuOH (7:3). The combined organic layer (ether and.CHCl 3 :n-BuOH) was washed with water and a slightly yellow precipitate was formed in the mixed solvents, at which point the 10 solvents were evaporated under vacuum. A slightly yellow solid was formed and was recrystallized from acetone/hexane. The solid was dried under vacuum, yield 60 Scheme XXXXVIII 15 OH Bis-(2(1-adainantyl)ethyl)phosphate and 11 are mixed in DMSO. EDC (3 eq), NIHS (2.2 eq), and DIEA (1 eq) are added to the solution. Solution is stirred 20 under argon for 16 hours. Bis-(2(l-adamantyl)ethyl)phosphate-Gly-CPT is precipitated with ether, washed extensively with this solvent, and dried under high vacuum. This compound and Di-CD-PEG 46 are mixed in DMSO to form inclusion polymer-CPT conjugate 48. 25 Example 40: Synthesis of AD-Peg-Folate 49 123 The following procedure is the synthesis of AD-Pegooo-Folate. This method can be adapted for the synthesis of any Guest molecule-Linker-Ligand tri component molecules. 5 1. Synthesis ofAD-Peg-NH 2 266 mg of FMOC-PEG 5 ooo-NHS (78.2 unol, Shearwater Polymers, Huntsville AL) were added to a glass vial equipped with a magnetic stirbar. 10 eq. of I -adamantane-methylamine (1.5 nmol, Aldrich) dissolved in 3 niL of dichloromethane were then added and the solution stirred overnight at room 10 temperature. The solvent was removed in vacuo and water was added to the remaining solution to dissolve the PEG product. The solution was centrifuged at 20K rcf for 10 minutes, whereupon the adamantane-methylamine phase-separated as a denser liquid. The aqueous portion was collected and water removed in vacuo. The remaining viscous liquid was redissolved in 20% piperidine in DMF for FMOC 15 deprotection and stirred for 30 minutes at room temperature. The solvent was removed in vacuo, washed several times with DMF, redissolved in water, and run on an anionic exchange column to remove unreacted PEG. The first fractions were collected and lyophilized to yield 222 mg of a white, fluffy powder (76% yield) of the desired product which was confined by MALDI-TOF analysis. 20 2. Synthesis of N-Hydroxysuccinimide-folate (NHS-folate) Scheme XXXXTX '00 2 5 0 %0 NHS-folate is synthesized according to the method of Lee and Low (Lee, R. J; Low, P. S. J Biol. Chem. 1994, 269,3198-3204). Folic acid (5 g, 11.3 mmol; 124 Sigma) is dissolved in DMSO (100 ml) and triethylamine (2.5 ml) and reacted with N-hydroxysuccinimide (2.6 g, 22.6 mmol) and dicyclohexylcarbodiimide (4.7 g, 22.7 mmol) over-night at room temperature. The solution is filtered and concentrated under reduced pressure. NHS-folate is precipitated using diethyl ether 5 (yellow-orange precipitate), and washed 2-3 times in anhydrous ether, dried under vacuum, and stored at -20 *C. 3. AD-Pegsooo-Folate Scheme L 10 49 AD-Peg5000-NH 2 and NHS-Folate are mixed at 1:1 eq. in DMSO solution. 15 DIEA (2 eq) is added. The mixture is allowed to stir at room temperature for overnight. The DMSO solution is then dialyzed against 3500 MWCO (Spectra/Por 7) membrane for 48 hours. AD-Peg5OOO-Folate 49 is obtained after lyophilization. Example 41: Formulation of the AD-Peg-Folate and a CD-Polymer-CPT conjugate 20 A typical procedure: A CD-polymer CPT conjugate is dissolved in a D5W buffer. A D5W solution containing 0.1-1 eq (mols of repeat unit) of AD-Peg-Folate solution is added to po lymer solution. Particle sizes of polymer are measured before and after adding of AD-Peg-Folate using light scattering. This solution is used for either in vitro or in vivo test for the analysis of folate targeting effects. 25 Example 42: Covalent linking a targeting ligand (e.g., folate) to a CD-CPT polymer conjugate (eg PEI-CD-GlyCPT) 50 Scheme LI 125 550 so PEI-CD-GlyCPT 44 and Folate-NHS (0.1-0.5 eq) are mixed in DMSO and stirred 5 for 24 hours. The polymer is crashed out with ether and washed extensively with this solvent until no free folate molecule can be detected. The resulting CD polymer-CPT-Folate conjugate 50 is dried under vacuum. Example 43: Crosslinking of CD-CPT polymer using Ad-Peg-Ad. 51 10 A typical procedure: AD-Peg-AD 45 (0.01-0.1 eq of CD-polymer repeat unit) and CD-polymer CPT conjugate are mixed in a minimum amount of DMSO. The resulting viscous solution is precipitated with ether and dried under vacuum to yield lightly crosslinked polymer 51. 51 should still maintain small particle size in solution, have good water solubility, and have higher molecular weight than parent 15 CD-polymer CPT conjugate. Example 44: In vivo tests of camptothecin polymer conjugates HGGG6, LGGG1O, HG6, and HGGGIO (Synthesized according to Example 28). 20 A. In Vivo Toxicity aud Blood Chemistry Analysis from Dosing With Parent Polymer 36e The toxicity of 36e and its effects on blood chemistry were evaluated in female Charles River nude mice (13-14 weeks old). Four treatment groups of six mice each were treated with a D5W solution of 36e at a dose of 240 mg/kg, 160. 126 mg/kg, 80 mg/kg or D5W alone by i.v. tail vein injection on Days 1, 5, and 9, respectively. Dosing volume was determined based upon a ratio of 200 ,l for a 20 g mouse, and was scaled appropriately according to the actual BW of the mice. The BWs of the mice were followed daily for the first 5 days and then twice a week, 5 thereafter. Blood samples (150-200 pl) were collected from each mouse by retro orbital bleeding under isoflourane on Day 12. Samples from three mice in each group were used for complete blood count (CBC) analyses, while blood samples from the remaining three mice in each group were processed for blood chemistry analyses. The study was stopped at Day 23. All mice were euthanized by cardiac LO puncture under CO 2 , and blood from each mouse was collected for CBC and blood chemistry analysis in the same manner as on Day 12. There was no significant difference in BW loss, CBC or blood chemistry data between any of the 36e treated groups and D5W control group throughout the study, and no time dependent effects were observed over 23 days for all the treated groups. 15 36e was well tolerated by mice at the maximum dose treated (240 mg/kg). B. Determination of Maximum Tolerable Dose (MTD) for CDP-CPT Conjugates. The MTD was determined using female Charles River nude mice (15-16 weeks old) 20 for HG6, LGGG10, HGGG1O. A 5% (w/v) of dextrose solution (D5W) of the polymer-CPT conjugates was freshly prepared before each injection. Doses for the treatment groups ranged from 2.25 mg CPT/kg to 54 mg CPT/kg. Dosing was administered intravenously (i.v.) by tail vein injection on Days 1, 5, and 9. The dosing volume was determined based upon a ratio of 200 d for a 20 g mouse, and 25 was scaled appropriately according to actual body weight (BW) of the mice. Three to five mice were used in each treatment group. The BWs of the mice were followed daily for the first 5 days and then twice a week, thereafter. The MTD was defined as the highest administered dose that resulted in a decrease of mean group BW of less than 20% or the highest administered dose that did not result in death of any animal 30 in that group. The maximum mean body weight loss and treatment related deaths for all treated groups are listed in Table 5. 127 Table 5. Treatment response for the MTD study. Nude mice (n= 3-6) were treated i.v. by tail vein injection. Agent mg/kg Max %BW loss; Dayb N-r/N* DSW - -2.5%; Day 3 0/6 36e 240 -2.0%; Day 3 0/6 36e 160 -3.5%; Day 13 0/6 36e 80 -2.3%; Day 3 0/6 LGGG1O 54 -20.6%; Day 3 3/3 LGGG1O 36 -9.3%; Day 13 0/3 LGGG1O 18 0 0/3 LGGG1O 9 0 0/5 LGGG1O 4.5 -0.8%; Day 13 0/5 HG6 54 -28.5%; Day 3 1 3/3 HG6 36 -23.9%; Day 3 3/3 HG6 18 -22.1%; Day 3 3/3 HG6 9 -6.1%; Day 9 0/5 HG6 4.5 -4.4%; Day 5 0/5 HG6 2.25 -2.9%; Day 9 0/5 HGGG1O 54 --- 3/3 HGGG10 36 -34%; Day 5 3/3 HGGG1O 18 -16%; Day 3 1/3 HGGG10 9 -3.3%; Day 9 0/5 HGGG1O 4.5 -2.5%; Day 9 0/5 * Mg CDP /kg for the CDP polymer and mg CPT/kg for the three 5 conjugates tested. b Maximum body weight (BW) loss observed post injection "Number of treatment-related deaths (N-r) to the number of mice treated (N) The MTD of LGGG10, HG6, and HGGGIO were determined to be 36 mg 10 CPT/kg, 9 mg CPT/kg, and 9 mug CPT/kg, respectively. Based on the structural 128 similarities between HGGG6 and HGGG1O, it is expected that the MTD for these two groups are similar. Therefore, the MTD of HGGG6 (not tested) was assumed to be 9 mg CPT/kg. 5 C. Antitumor Efficacy Study. The antitumor efficacy study was performed using female Charles River nude mice (15-16 weeks old). A fragment (1 mm 3 ) of human LS174T colon carcinoma tissue was implanted subcutaneously (s.c.) into the right flank of each test mouse 10 approximately 14-18 days before dosing. The tumor volume was determined by measuring the tumor in two dimensions with calipers and calculated using the formula: tumor volume = (length x width 2 )/2. Tumor volume was converted to tumor weight assuming 1 mm 3 is equal to I mg tumor in weight. Treatment was initialized when mean tumor size reached approximately 60-100 mg (Day 1). The 15 animals were sorted into twelve groups. Each group consisted of seven mice with tumor sizes ranging from 62.5-144.0 mg with group mean tumor sizes of 88.6-90.7 mg. Mice in each group were treated according to the protocol listed in Table 6. All conjugate treatments were administered intravenously by tail vein injection. Tumor sizes were measured twice a week for the duration of the experiment. At the end of 20 study, tumors from each euthanized mouse were harvested and frozen at -80 *C. Table 6. Dosing protocol for efficacy study.a Group Agent Dose (mg Route' Scheduled CPT/kg)b I D5W - i.v. Q4D x 3 2 CPT 9 i.p. Q4Dx2' 3 Irinotecan 100' i.p. Qwk x 3 4 HGGG6 9 i.v. Q4D x 3 5 HGGG6 4.5 i.v. Q4D x 3 129 6 LGGG1O 36 i.v. Q4D x 3 7 LGGG1O 18 i.v. Q4D x 3 8 LGGG10 9 i.v. Q4D x 3 9 HG6 9 i.v. Q4D x 3 10 HG6 4.5 i.v. Q4D x 3 11 HGGG1O 9 i.v. Q4D x 3 12 HGGGIO 4.5 i.v. Q4D x 3 a Seven mice were used in each group b Doses are equivalent of CPT except for group 3 * i.p. = intraperitoneal, i.v. = intravenous d Administration schedules were abbreviated as: Q4D x 3= three injection with 5 four-day intervals, Qwk x 3 = three injection with one-week interval, first dose was initialized on day 1 for all groups. * The scheduled third dose was not given due to the emerging toxicity r 100 mg irinotecan/kg 10 Each animal was euthanized when tumor weight reached the predetermined endpoint size (1,500 mg). The time-to-endpoint (TIE) for each mouse was calculated from the equation: TTE = (log(endpoint-b))/m, where b and m are the intercept and the slope, respectively, of the line obtained by linear regression of a 15 log-transformed tumor growth data set comprised of the first observation that exceeded the study endpoint volume and the three consecutive observations that immediately preceded the attainment of the endpoint volume. Animals that do not reach the endpoint were assigned a TTE value equal to the last day of the study (114 days), Animals classified as treatment-related deaths (TR) were assigned a TTE 20 value equal to the day of death. Animals classified as non-treatment-related death (NTR) are excluded from TTE calculations. Tumor growth delay (TGD), defined as the increase in the median time to endpoint (TTE) in a treatment group compared to the control group, was one parameter investigated to evaluate treatment efficacy. 130 TGD is calculated as the difference between the median T'E for a treatment group and the median TTE of the control group (TGD = T - C) and is expressed in days, and as a percentage of the median TTE of the control group; %TGD = (T-C)/C where T is equal to median TTE for a treatment groups and C is equal to median 5 TTE for the control, Group 1. Toxicity. Animals were weighed daily on Days 1-5, then twice weekly thereafter. Mice were examined frequently for overt signs of any adverse, drug related side effects. Acceptable toxicity for cancer drugs in mice is defined by the NCI as a group mean body-weight loss of less than 20% during the study, and not 10 more than one toxic death among seven treated animals. Results for this efficacy study that include median TTE values, median tumor burden on day 114, treatment response and deaths are summarized in Table 7. Table 7. Median Median Tumor P vs P vs Group T-Cb %TGDC Nma/ TTEa Burden in D5W" CPT' mg (N d) 1 34.9 - - -(0) 0/1/6 - 2 51.4 [6.5 47% -(0) 2/0/5 0.2128 3 68.7 33.8 97% 1152 (3) 0/0/4 0.0002 0.0253 4 114.0 79.1 227% 256(5) 1/0/1 0.0040 0.0115 5 65.6 30.7 88% 566 (2) 0/1/4 0.0046 0.1369 6 100.0 65.1 187% 666 (3) 4/0/0 0.0272 0.0289 7 75.6 40.7 117% 221 (3) 0/0/4 0.0018 0.0601 8 63.2 28.3 81% 700 (1) 1/0/5 0.0006 0.1064 9 114.0 79.1 , 227% 394(4) 0/0/3 0.0002 0.0028 10 74.2 39.3 113% 668(2) 1/1/3 0.0016 0.0673 11 114.0 79.1 227% 500 (5) 1/0/1 0.0040 0.0050 12 78.0 43.1 123% 1010 (2) 0/0/6 0.0006 0.0392 15 'TTE = Time (Days) to endpoint (1500 mg) 131 b T-C = Difference between T'E (Days) of treated versus control group '%TGD = [(T-C)/C] d Mice surviving "N-r = Number of treatment-related death 5 'NNTR = Number of non-treatment-related death 8 NEU =Number of mice euthanized after reaching endpoint P value versus the D5W treatment group (Group 1) P value versus the CPT treatment group (Group 2) 10 One NTR death on day 72 was observed in the control animals treated with D5W. Tumors in the other six control mice grew to the 1500 mg endpoint size, yielding a median TTE of 34.9 days (Table 7). Two treatment-related deaths were reported on Day 9 for CPT at 9 mg/kg. Thus, CPT must be considered to be toxic at this dose in this experiment. The median TTE 15 for this group was 51.4 days, corresponding to a 16.5 day T-C and a 47% TGD, relative to untreated control mice (not signficant). No animal in Group 2 survived to Day 114. Group 3 received irinotecan i.p. at 100 mug/kg (Qwk x 3). The median TTE for Group 3 was 68.7 days, corresponding to a significant 33.8 day T-C and a 97% 20 TGD, relative to control mice (P < 0.01). Three animals survived to Day 114 with a median tumor burden of 1,152 mg. No regressions were recorded. Groups 4 and 5 received HGGG6 i.v. Q4D x 3 at 9 and 4.5 mg CPT/kg, respectively. One treatment-related death was observed on Day 16 in Group 4, and one NTR death was recorded on Day 37 in Group 5. The median TTE for Group 4 25 was 114 days, the maximum possible value in this study. This TTE value corresponds to a significant 79.1 day T-C and a 227% TGD, relative to control (P < 0.01). Tumors in five mice of Group 4 did not reach the 1,500 mng endpoint. These five mice had a median tumor burden of 256 mg on Day 114. The median TTE for Group 5 was 65.6 days, and corresponds to a significant 30.7 day T-C and an 88% 30 TGD, relative to control (P < 0.01). Groups 6-8 were treated with LGGG10 i.v. Q4D x 3 at 36, 18, and 9 mg CPT/kg, respectively. Although no death was observed in MTD study using this 132 conjugate in non-tumor bearing mice at 36 mg CPT/kg (Table 5), four treatment related deaths were recorded in Group 6 when tumor-bearing mice were given at this dose, two on Day 16 and one each on Days 75 and 100. These results indicate that 36 mg CPT/kg is probably over the MTD of LGGG1O. As shown in Table 5, no 5 significant body weight loss was recorded in the MTD study when the mice were dosed at 18 mg CPT/kg, indicating that this dose is below the MTD. Therefore, the MTD of LGGG1O lies somewhere between 18 to 36 mg CPT/kg. The median TTE for Group 7 (18 mg CPT/kg) was 75.6 days. This TTE value corresponds to a significant 40.7 day T-C and a 117% TOD, relative to control mice (P < 0.01). 10 Three mice in this group had a median tumor burden of 221 mg on Day 114. One late TR death was recorded on Day 103 in Group 8 (9 mg CPT/kg). The median TTE for Group 8 was 63.2 days. This TTE value corresponds to a significant 28.3 day T-C and an 81% TGD, relative to untreated control mice (P < 0.01). The remaining mouse in this group had a tumor burden of 700 mg on Day 114. 15 Groups 9 and 10 were dosed with HG6 i.v. Q4D x 3 at 9 and 4.5 mg CPT/kg, respectively. One TR and one NTR death were recorded in Group 10 on Days 47 and 84, respectively. The median TTE for Group 9 was the maximum, 114 days. This TTE value corresponds to a significant 79.1 day T-C and a 227% TGD, relative to untreated control mice (P < 0.01). Four mice in Group 9 had a median 20 tumor burden of 394 mg on Day 114. The median TTE for Group 10 was 74.2 days. This TTE value corresponds to a significant 39.3 day T-C and a 113% TGD, relative to control mice (P < 0.01). The remaining two mice in Group 10 had a median tumor burden of 668 mg on Day 114. Groups 11 and 12 were dosed with HGGG10 i.v. Q4D x 3 at 9 and 4.5 mg 25 CPT/kg, respectively. One treatment-related death was recorded on Day 16 in Group 11. The median TTE for Groups 11 and 12 were 114 days and 78 days, respectively. The TTE value for Group I I corresponds to a significant 79.1 day T-C and a 2 2 7 % TGD, relative to control mice (P < 0.01). Tumors in five mice in Group 11 did not reach the endpoint; these five mice had a median tumor burden of 500 mg on Day 30 114. The TTE value of Group 12 corresponds to a significant 43.1 day T-C and a 123% TOD, relative to control mice (P < 0.01). The remaining two mice in this group had a median tumor burden of 1,010 mg on Day 114. 133 The tumor growth curve as a function of time for the D5W, CPT, irinotecan, LGGG10 at its highest non-toxic dose tested (18 mg CPT/kg), and the other three conjugates with high MW polymer (HGGG6, HG6, HGGG1O) at their MTDs are shown in Figure 8. The three high MW conjugates administered at their MTDs 5 displayed moe prolonged tumor growth inhibition compared to D5W, CPT and irinotecan. The median tumor growth curves for HGGG6, HG6 and HGGG10 that are illustrated in Figure 9 show that there is a distinct dose response for all three of these polymers when dosed as their MTD and at half of their MTD. The medium tumor growth curves for LGGG10 and HGGG1O each dosed at 9 mg CPT/kg as 10 illustrated in Figure 10 demonstrate that high MW polymer-drug conjugate has greater antitumor effect when compared to the low MW conjugates presumably due to the enhanced accumulation (EPR effect) and reduced renal clearance. Mean Body Weight Loss of Mice. Mean body weight (MBW) losses as a function of time are plotted for D5W, CPT, irinotecan and the three conjugates 15 containing high MW polymer at their MTDs (Fig. 11). Maximum MBW losses observed in Group 2 (CPT) and the two conjugates with the triglycine linker dosed at their MTDs (Groups 4 and 11) were 13.1%, 18.3%, and 12.6%, respectively. Maximum MBW loss of HG6 (3.4%), the only conjugate with a glycine linker, was similar to the maximum MBW loss recorded for irinotecan (5.0%). Negligible 20 (<5%) maximum group mean body-weight losses were recorded in all the other treatment groups and in the D5W group. Mean body weight returned to baseline levels for all treatment groups following cessation oftherapy. D Correlation of Tumor size of eutlinnizedi mouse and the CPT concentration in 25 corresponding tumor. Each tumor harvested from mice at the completion of the LS174t xenograft mouse study was thawed and placed in a 2 ml lysis tube (Lysing Matrix D, Qbiogen). 300 IiL of lysis reagent (Cellytic -MT Mommalian Tissue 30 Lysis/Extraction reagent) was added to each tube. The tissue was homogenized on a FastPrep FP12 homogenizer (Qbiogen) at 5 m/s for 40 sec. Homogenization was repeated six times with a 10 mini interval between successive homogenization. The 134 homogenized solution was centrifuged at 14000g for]5 min at 100C. 90 4L of the solution was syringed out to which 10 .L IN NaOH was added. An aliquot of 400 pL MeOH was added to this solution after allowing the homogenized solution to stand for 2h at room temperature. The solution was centrifuged for 15 min at 14000 5 g. The supernatant (270 gL) was mixed with 30 iL IN HCI and injected into an HPLC for analysis. The correlation of CPT concentration (ng/ng tissue) to tumor size (in mg) is illustrated in Figure 12. CPT concentration was inversely correlated to tumor size. Example 45; Synthesis of Poly(CDDC-PEG)-Amphotericin B 52 via amide tinker 10 Scheme LII Zrn ArnS k 0 52 Poly(CDDC-PEG) (788 mg) and 1,1'-carbonyl diimidazole (CDI, 1.45 g, 50 15 eq.) were stirred in anhydrous DMSO (10 mL) in the presence of DMAP (429 mg, 20 eq) for 16 h. Ether (200 mL) was added to the mixture to precipitate poly(CDDC-PEG)-carbonyl-imidazole. The resulting yellow solid was washed with ether 2 x 200 nL and dried under vacuum. The solid was dissolved in anhydrous DMSO (15 mL), followed by adding AmB (332 mg, 2 eq) and DMAP (43.0 ing, 20 2eq). The solution was stirred in dark for 48 h and dialyzed in water using 25000 MWCO membrane for 3 days. The solution was then filtered using 0.2 ptm filter and lyophilized. A yellow solid (920 mg) 52 was obtained. The wt% of AnB is around 13%. Example 46: Synthesis of Poly(CDDC-PEG)-Amphotericin B 53 via imine linker 25 135 DI 53 3 and PEG-DiSPA (1:1 ratio) were dried under vacuum at room temperature. DMSO (10 mg of 3/mL DMSO) was added to the solid and followed by adding of 5 DIEA (2 eq) to the mixture. Polymer was crashed out with excess ether 5 days later and dialyzed using 25000 MWCO membrane for 48 h. The yield of poly(CDDC PEG) is 80-95%. The Mw of polymer was determined using GPC to be 70-100 kDa. Poly(CDDC-PEG) (1.124g, 0.25 mmol) was dissolved in water (55 mL). 10 NaIO 4 (0.264g, 5 eq.) was added. The solution was stirred in dark at room temperature for 20 min and stored 'at 4 *C for 24h in dark. BaCl 2 solution was added (5.05 eq) to the solution to give immediate precipitation of Ba(10 4

)

2 . The precipitate was filtered. Saturated Na 2

CO

3 solution was added to adjust pH to 11. Amphotericin B (343mg, 1.5 eq) was then added to solution and stirred at rt in dark 15 for 48h. The pH of solution was maintained to be 11 by adding NaOH (0.IN) throughout the reaction. The solution was dialyzed at 4 *C for 48 h using 25000 MWCO and lyophilized to give 1.03 g polymer-AmB conjugate 53 as a yellow powder. The wt% of AmB is determined to be 18 using UV spectrometer at 405 n1m. 20 D. References Additional cyclodextrin-containing polymers that can be modified according to the teachings of the present invention, as well as methods of preparing such polymers, are disclosed in U.S. Patent applications 09/203,556, 09/339,818, 25 09/453,707, 10/021,294, and 10/021,312, al of which are hereby incorporated herein by reference in their entireties. All of the references, patents, and publications cited herein are hereby incorporated by reference. 136 Equivalents Those skilled in the art will recognize, or be able to ascertain using no more than routine experimentation, numerous equivalents to the compounds and methods 5 of use thereof described herein. Such equivalents are considered to be within the scope of this invention and are covered by the following claims. 137

Claims (32)

1. A modified cyclodextrin ring or a salt thereof, wherein exactly two hydroxyl moieties are substituted with an alpha-amino acid selected from the group consisting of cysteine, tryptophan, glutamic acid, aspartic acid, lysine, and arginine. 5

2. The modified cyclodextrin ring or salt according to claim 1, wherein the two hydroxyl moieties are substituted with a nitrogen or sulfur atom of the amino acid.

3. The modified cyclodextrin ring or salt according to claim 1 or claim 2, wherein the amino acid is glutamic acid.

4. The modified cyclodextrin ring or salt according to any one of claims I to 3, 10 wherein the amino acid is a boc protected glutamic acid.

5. The modified cyclodextrin ring or salt according to claim 1 or claim 2, wherein the amino acid is cysteine.

6. The modified cyclodextrin ring or salt according to any one of claims 1 to 5, wherein the cyclodextrin is a p-cyclodextrin. 15

7. The modified cyclodextrin ring or salt according to claim 5 or claim 6, wherein the two hydroxyl moieties are substituted with the sulfur atom of the cysteine.

8. The modified cyclodextrin ring or salt according to any one of claims 5 to 7, wherein the cysteine is attached at the A and D positions of the cyclodextrin and wherein the two hydroxyl moieties are substituted with the sulfur atom of the cysteine. 20

9. The modified cyclodextrin ring or salt according to any one of claims I to 8, wherein the amino acid is included in an oligopeptide comprising 2 to 50 amino acid residues.

10. The modified cyclodextrin ring or salt according to claim 9, wherein the oligopeptide comprises 2 to 30 amino acid residues. 25

11. The modified cyclodextrin ring or salt according to claim 10, wherein the oligopeptide comprises 2 to 15 amino acid residues. - 138 -

12. A compound of the formula: AA AA or a salt thereof, wherein is a cyclodextrin, wherein each AA independently comprises an alpha-amino acid selected from the group consisting of cysteine, 5 tryptophan, glutamic acid, aspartic acid, lysine, and arginine.

13. The compound or salt according to claim 12, wherein ' 'is a cyclodextrin.

14. The compound or salt according to claim 13, wherein ' is linked in an A, D configuration. 10 15. A compound of the formula: AA AA or a salt thereof, wherein is a cyclodextrin, and wherein each AA independently comprises an alpha-amino acid selected from the group consisting of cysteine, tryptophan, glutamic acid, aspartic acid, lysine, and arginine.

15

16. The compound or salt according to claim 15, wherein is a cyclodextrin.

17. A compound of the formula: - 139 - AA AA or a salt thereof, wherein is a cyclodextrin, wherein each AA independently comprises an alpha-amino acid selected from the group consisting of cysteine, tryptophan, glutamic acid, aspartic acid, lysine, and arginine. 5

18. The compound or salt according to claim 17, wherein is a cyclodextrin.

19. A compound of the formula: OH 0 OH 0 00 OH HO OH O HO HO 0 OH HO O 0 AA OH HO AA O OH HO HO 0 OHO HO 0 0 OH or a salt therof, wherein each AA independently comprises an alpha-amino acid selected 10 from the group consisting of cysteine, tryptophan, glutamic acid, aspartic acid, lysine, and arginine.

20. The compound or salt according to claim 19, wherein the compound is: - 140 - OH 0 HO Oi H2Nl s 0II HO sa NH2 O OH HO HO O O H H '0 OH HO 0 0 HO O O OH

21. The compound or salt according to any one of claims 12 to 20, wherein the amino acid is linked to the cyclodextrin via a nitrogen or a sulfur atom of the amino acid.

22. The compound or salt according to any one of claims 12 to 21, wherein the 5 amino acid is cysteine.

23. The compound or salt according to any one of claims 12 to 21, wherein the amino acid is glutamic acid.

24. The compound or salt according to any one of claims 12 to 21, wherein the amino acid is a boc protected glutamic acid. 10

25. The compound or salt according to any one of claims 12 to 24, wherein the amino acid is included in an oligopeptide comprising 2 to 50 amino acid residues.

26. The compound of claim 25, wherein the oligopeptide comprises 2 to 30 amino acid residues.

27. The compound or salt according to claim 25 or claim 26, wherein the 15 oligopeptide comprises 2 to 15 amino acid residues.

28. The compound or salt according to claim 12, wherein the compound is: H 2 N NH 2 HO O HO 0 - 141 -

29. A composition comprising the modified cyclodextrin ring or salt thereof according to any one of claims 1 to 11 or a compound or salt thereof according to any one of claims 12 to 28, and a solvent.

30. The composition according to claim 29, further comprising an activated 5 monomer.

31. The composition according to claim 30, wherein the activated monomer comprises an activated ester.

32. The modified cyclodextrin ring or salt thereof according to any one of claims 1 to 11; or a compound or salt thereof according to any one of claims 12 to 28; or a 10 composition according to any one of claims 29 to 31, substantially as hereinbefore described with reference to the figures and/or examples, but excluding comparative examples. - 142 -