Patent Application
20090232762
Gene Directed Enzyme Prodrug Therapy (GDEPT) is a strategy for minimizing normal tissue toxicities associated with systemic administration of anticancer drugs. GDEPT involves expressing a gene coding for a prodrug-activating enzyme in tumorgenic cells. In typical GDEPT, delivery vectors extravasate into targeted cells, for example, by transport through leaky tumor blood vessels into a cancer tumor. A non-toxic prodrug is then injected intravenously, such that only cells expressing the enzyme convert the prodrugs into toxic agents, thereby minimizing negative side effects to healthy tissues. This therapy has great potential but has yet to be fully developed. Improved gene delivery compositions and methods would aid in the further development of GDEPT.
Viral gene delivery methods, which usually involve transfecting with lentivirus vectors containing a gene of interest are viewed with reservation because of potential problems with immunogenicity and other safety risks. There has been a considerable amount of research in the area of non-viral gene delivery methods, however, current methods still suffer from a variety of drawbacks, including inadequate delivery of vectors and unfavorable toxicity.
Accordingly, there is a need for novel compounds, compositions, and methods for mediating non-viral transfection. There is also a need for novel compositions, such as non-viral vehicles, and methods for mediating gene and prodrug delivery to cells. There is a further need for compositions that are stable, have low toxicity toward normal tissue and function, and can provide for release of therapeutic agents in target tissues or cells.
The invention provides a polyamide block polymer including a first block and a second block; wherein the first block includes amino acid units with side chains that can have neutral or negative charges; the second block includes amino acid units with side chains that can have positive charges; wherein at least one side chain of an amino acid of the first block is covalently linked to a poly(ethylene glycol) chain through a hydrazide moiety, and wherein the hydrazide moiety is linked to the poly(ethylene glycol) chain at the N′ nitrogen of the hydrazide through a hydrazone's N═C bond.
The first block can include aspartic acid or glutamic acid units. The second block can include lysine or arginine units. The aspartic acid or glutamic acid units can be covalently linked to poly(ethylene glycol) chains. The molecular weight of the poly(ethylene glycol) chains can be about 500 to about 50,000. A plurality of aspartic acid or glutamic acid units can be covalently linked to poly(ethylene glycol) chains and the poly(ethylene glycol) chains terminate in methoxy, amino, or acetamide groups. The ratio of aspartic acid or glutamic acid units to polyethylene(glycol) chains can be about 1:1 to about 20:1. The polymer can include poly(lysine) units wherein one or more of the lysine side chain amino group is protected with nitrogen protecting groups, such as trifluoroacetate groups or carbonyl-benzyloxy (CBz) groups.
In one embodiment, the first block is poly(aspartic acid) comprising about 20 to about 60 aspartic acid units. In certain embodiments, the second block is poly(lysine) comprising about 30 to about 80 lysine units. In some embodiment, the first block is poly(glutamic acid) comprising about 20 to about 60 arginine units. In certain embodiments, the second block is poly(arginine) comprising about 30 to about 80 arginine units.
Throughout this descriptions, it is important to note that the various embodiments of the invention include replacing one or more units of a ‘lysine’ block with arginine units, aspartate units, aspartate unit derivatives such as aspartate with a diethyl triamine side chain (an N-(2-aminoethyl)-2-aminoethyl group in the side chain), or an imidazole acetic acid group on a side chain. Additionally, embodiments also include replacing any aspartic acid unit with a glutamic acid unit, optionally in combination with a replacement of one or more lysine units. In some embodiments, a typical polymer of the invention will include at least about 60 repeating units. In other embodiments, the polymers of the invention may include up to about 150 repeating units.
The invention also provides a polyamide block polymer comprising at least one block of poly(aspartic acid) units and at least one block of poly(lysine) units; wherein at least one side chain of an aspartic acid unit is covalently linked to a poly(ethylene glycol) chain through a hydrazide moiety, and wherein the hydrazide moiety is linked to the poly(ethylene glycol) chain at the N′ nitrogen of the hydrazide through a hydrazone bond.
A plurality of aspartic acid units can be covalently linked to poly(ethylene glycol) chains and the molecular weight of the poly(ethylene glycol) chains can be about 500 to about 10,000. A plurality of aspartic acid units can be covalently linked to poly(ethylene glycol) chains and the poly(ethylene glycol) chains can terminate in various organic groups, such as methoxy, amino, or acetamide groups, or combinations thereof. The ratio of aspartic acid units to polyethylene(glycol) chains can be about 1:1 to about 20:1, or any ratio in between. The polymer can include poly(lysine) units wherein the side chain amino group is protected with a nitrogen protecting group, for example, a trifluoroacetate group or a carbonylbenzyloxy group. Protecting groups can optionally be removed before the polymer is used to prepare a micelle that incorporates various cargo.
The poly(aspartic acid) block can include about 20 to about 60 aspartic acid units. The poly(lysine) block can include about 30 to about 80 lysine units.
The invention further provides a micelle composition that includes a polymer as described herein and a therapeutic agent, wherein the polymer substantially encapsulates the therapeutic agent and the poly(ethylene glycol) chains of the polymer align toward the outside surface of the micelle. The therapeutic agent can include a nucleic acid, a gene, a drug, a prodrug, or a combination thereof. The nucleic acid can be plasmid DNA encoding gene products or RNAi.
Also provided is a polyamide polymer comprising amino acid units with side chains that can have positive, neutral, or negative charges; wherein at least one side chain of an amino acid of the polyamide is covalently linked to a poly(ethylene glycol) chain through a hydrazide moiety, and wherein the hydrazide moiety is linked to the poly(ethylene glycol) chain at the N′ nitrogen of the hydrazide through a hydrazone bond.
The amino acid units can include a variety of amino acids, including aspartic acid units, lysine units, or both. A plurality of aspartic acid units can be covalently linked to poly(ethylene glycol) chains. The molecular weight of the poly(ethylene glycol) chains can be about 500 to about 10,000. A plurality of aspartic acid units can be covalently linked to poly(ethylene glycol) chains and the poly(ethylene glycol) chains can terminate in PEG-capping groups, for example, amino or acetamide groups. The ratio of aspartic acid units to polyethylene(glycol) chains can be about 1:1 to about 20:1, or any ratio in between. One or more of the lysine side chain amino group can be protected with a nitrogen protecting group, such as trifluoroacetate groups or carbonylbenzyloxy groups.
The polymer can include about 5 to about 100 amino acid units in the first block. The polymer can include about 10 to about 150 amino acid units in the second block. In one embodiment, the amino acids can be aspartic acid or glutamic acid in the first block, and lysine or arginine in the second block. The polymer can also include about 5 to about 60 units, about 20 to about 100 units, about 10 to about 80 units, or about 20 to about 60 units, in the first block. The polymer can also include about 10 to about 80 units, about 20 to about 150 units, about 20 to about 120 units, about 30 to about 100 units, or about 30 to about 80 units, in the second block.
The invention further provides a polymer comprising formula I:
wherein m is about 20 to about 60; n is 0, or about 30 to about 80; p is selected such that the molecular weight of the poly(ethylene glycol) chain is about 500 to about 20,000. The group L can be a direct bond from NH to R1, or L can be a carbonyl or sulfonyl group. R1 can be H, or together with the carbonyl to which it is attached, can be a nitrogen protecting group, for example, trifluoroacetate or carbonylbenzyloxy. R2 can be hydrogen, hydroxy, (C1-C12)alkyl, alkoxy, —NHR3 wherein R3 is hydrogen, an amino protecting group, or any PEG-capping group; and X can be a direct bond, an organic linking group, or a group of about 1 to about 100 amino acids; or a salt thereof.
In certain embodiments, m can be about 30 to about 50, n can be about 40 to about 60, and p can be selected such that the molecular weight of the poly(ethylene glycol) chain is about 2,000 to about 10,000. In various embodiments, R2 can be —NHR3 wherein R3 is an acetyl group.
The invention also provides a polymer comprising formula II:
wherein m is about 20 to about 60; n is 0, or about 30 to about 80; each PG is independently hydrogen or an amino protecting group; and X is a direct bond, an organic linking group, or a group of about 1 to about 100 amino acids; or a salt thereof.
Also provided is a method of activating a therapeutic prodrug that includes contacting a micelle composition described herein and a cell, wherein the micelle composition contains a nucleic acid, gene, or vector that encodes an enzyme that converts the prodrug to an active drug. The method can further include introducing the prodrug to the vicinity of the cell after the cell has synthesized the enzyme so that the enzyme activates the prodrug to the active drug. The introduction of the prodrug to the vicinity of the cell can be via systemic delivery, such as by IV or other injection. The formulation for injection can include a pharmaceutically acceptable carrier or diluent, for example, saline that optionally includes a buffer.
Further provided is a method of delivering a nucleic acid to a cell that includes encapsulating nucleic acid in a micelle comprising a polymer described herein; and contacting a cell with the micelle. The nucleic acid can be a gene, a vector, or a specific type of RNA, such as siRNA, or a plasmid that codes for RNAi.
The invention additionally provides a method of treatment for a disease or a condition in a human or an animal by administering a micelle composition that includes a polymer disclosed herein and a therapeutic agent, such as a nucleic acid or a drug. The nucleic acid can encode for a therapeutic protein, such as an enzyme. A prodrug can then be administered to a patient, whereby cells that produce the enzyme then activate the prodrug to a drug, and then the drug takes its effect on the cell.
One aspect of the invention involves the preparation of a pH-sensitive polyamide copolymer, such as a poly(Aspartate-Hydrazide-PEG)-b-poly(L-Lysine) block-copolymer. The poly(L-Lysine) segment of the polyamide can be used to condense an agent within an association of polyamide molecules, such as in a micelle core or polyamide particle core. The agent can be a therapeutic agent, such as a drug or a gene therapy agent, for example, a pDNA, or the agent can be a diagnostic agent or an imaging agent. Aldehyde-PEG groups can be attached, for example, through the formation of hydrazone bonds to hydrazide groups, forming a variable brush layer in the particle shell, composed of acid labile PEG moieties. At a pH of less than approximately 7.0, these acid labile PEG moieties can be released from the polymer, leaving behind hydrazide groups that can enhance the escape of pDNA from endolysosomes via membrane disruptions. The rapid release of the PEG brush layer can further enhance agent unpacking, for example, pDNA unpackaging.
The compositions and methods thus provide non-viral transfection vehicles with reduced toxicity compared to standard poly(lysine) delivery vehicles. The compositions and methods also improved in vivo stability, wherein the rate of release of encapsulated agents can be tuned by varying the amount of PEG groups on the cationic polymers.
The invention thus provides novel polymers, polymer compositions, including micelles, and methods of making and using the polymers and polymer compositions. The polymers and compositions can be used to treat diseases or disorders of mammals, for example, using GDEPT. The polymers and compositions can also be used to prepare a medicament to treat diseases in mammals, for example, cancer in a human. Also provided are useful intermediates for the preparation of the polymers disclosed herein.
The following drawings form part of the specification and are included to further demonstrate certain embodiments or various aspects of the invention. In some instances, embodiments of the invention can be best understood by referring to the accompanying drawings in combination with the detailed description presented herein. The description and accompanying drawings may highlight a certain specific example, or a certain aspect of the invention, however, one skilled in the art will understand that portions of the example or aspect may be used in combination with other examples or aspects of the invention.
a) illustrates a GPC (10 mM LiCl in DMF) of p(Asp-Hyd)36-PLL(TFA)53 reaction with aldehyde-PEG7k at a 1:1 molar ratio after 2 and 5 days incubation at RT. Peak a is un-reacted PEG7k, peak b is un-reacted p(Asp-Hyd)36-PLL(TFA)53 block-copolymer and peak c is the multimodal distribution of pre-PEGylated block-copolymers.
b) illustrates a GPC (10 mM LiCl in DMF) of p(Asp-Hyd)36-PLL(TFA)50 reaction with aldehyde-PEG7k at a 1:0.5 molar ratio after 2 and 5 days incubation at RT. Peak a is un-reacted PEG7k, peak b is un-reacted p(Asp-Hyd)36-PLL(TFA)53 block-copolymer and peak c is the unimodal distribution of pre-PEGylated block-copolymers.
c) illustrates a GPC (10 mM LiCl in DMF) of p(Asp-Hyd)36-PLL(TFA)50 reaction with aldehyde-PEG7k at a 1:0.1 molar ratio after 2 and 5 days incubation at RT. Peak a is un-reacted PEG7k, peak b is un-reacted p(Asp-Hyd)36-PLL(TFA)53 block-copolymer and peak c is perhaps pre-PEGylated block-copolymers.
a) poly(aspartate-hydrazide)-block-poly(L-lysine) (BC); and b) pH-sensitive poly(aspartate-hydrazide-PEG)-block-poly(L-lysine) (pH-PBC), and covalent poly(aspartate-hydrazide-PEG)-block-poly(L-lysine) (cov-PBC).
The invention provides polymers, particularly block co-polymers, that can have refined properties that make them “tunable” in response to various environmental conditions, addition of ligands, excipients, etc. Block co-polymers that include PEG groups are of interest because PEG is unique in its ability to facilitate transfer of appended agents across cell membranes. PEG is both water soluble and membrane permeable.
The inclusion of multiple PEG residues in the polymers disclosed herein allows for the covalent yet labile attachment of targeting ligands and tenability or modulation of the release of agents, such as DNA packages, into the polycationic core. In particular, the contents of the particle can be released upon hydrolytic removal of PEG residues in response to slightly lower than physiological pH, such as the pH found in cancerous cells.
One embodiment of the invention comprises a poly(PEG)-poly(lysine) copolymer that encapsulates a vector encoding the non-mammalian enzyme yeast cytosine deaminase (yCD), which has shown potential in activating the prodrug 5-fluorocytosine (5FC) into cytotoxic 5-fluorouracil (5FU) in several tumor models. Cytosine deaminase can be obtained both from S. Cerevisiae (yeast) and E. Coli (bacteria). Both the prodrug and the gene encoding the enzyme can be preferentially delivered to tumor cells because the slightly more acidic extracellular environment, combined with the leaky vasculature of tumor cells, favors delivery of the DNA vector and prodrug to tumor cells.
Variations of this embodiment can be considered a platform for the creation of a library of tunable poly(PEG)-polycation copolymers with modulatable gene and therapeutic agent delivery properties. Thus, the invention adds to the compendium of non-viral vehicles for tunable, specific gene and prodrug delivery into cells.
The invention also provides nonviral gene vectors from synthetic catiomers (polyplexes) as alternatives to viral vectors. One embodiment employs the use of poly(ethylene glycol) (“PEG”)-linked block catiomers, which form a nanoscaled core-shell polyplex with biocompatible PEG palisades. A schematic diagram of this approach is illustrated in
A series of PEG-linked block catiomers with various amine functionalities have been prepared by a simple and affordable synthetic procedure based on aminolysis reactions. These PEG-linked block catiomers can be used as gene carriers. The catiomers with various side chains are capable of efficient and low toxicity transfection even toward primary cells, highlighting important structural factors of the cationic units in the construction of polyplex-type gene vectors. Moreover, the polyplex micelle for transfection with cells, for example, primary osteoblasts, allows for therapeutic methods, including bone regeneration in vivo, mediated by nonviral gene transfection.
References in the specification to “one embodiment”, “an embodiment”, “an example embodiment”, etc., indicate that the embodiment described may include a particular feature, structure, or characteristic, but every embodiment may not necessarily include that particular feature, structure, or characteristic. Moreover, such phrases are not necessarily referring to the same embodiment. Further, when a particular feature, structure, or characteristic is described in connection with an embodiment, it is submitted that it is within the knowledge of one skilled in the art to affect such feature, structure, or characteristic in connection with other embodiments whether or not explicitly described.
A “block copolymer” refers to a polymer with repeating units of one type adjacent to each other in a linear manner to form a block, which is linked, for example, through a covalent bond to a second block made up of repeating units of a second type, which are adjacent to one another in a linear manner to form a second block of the block copolymer.
The first block of the polyamide block polymer includes amino acid units derived from amino acid units with side chains that can have neutral or negative charges and the second block of the polyamide block polymer includes amino acid units derived from amino acid units with side chains that can have positive charges.
The phrase “amino acid units derived from amino acid units with side chains that can have negative charges” refers to amino acid units (repeat segments of a polyamide) whose side chains possess a group that can form an anion, for example, at a slightly basic pH, such as under mammalian physiological conditions. In some embodiments, the group can form an anion at intracellular pH. The group can also be uncharged at a neutral pH. Examples of suitable amino acids include aspartic acid, glutamic acid, and derivatives thereof.
The amino acid units of the first block can undergo a variety of reactions to provide multifunctional polyamides. Some side chain groups may remain as the initial unreacted side chains. Others can be converted to hydrazide groups. In some embodiments, more than 90% of the first block side chains will be converted to hydrazide groups. Many of these groups can be further reacted to provide hydrazone groups that link the amino acid unit to PEG groups, for example, by a condensation reaction between the N′ nitrogen and an aldehyde group of a PEG chain.
The phrase “amino acid units derived from amino acid units with side chains that can have positive charges” refers to amino acid units (repeat segments of a polyamide) whose side chains possess a group that can form a cation, for example, at a slightly acidic pH, such as under certain mammalian physiological conditions. In some embodiments, the group can form a cation at certain intracellular pH ranges, such as at a pH less than 7. The group can also be uncharged at a neutral pH. Examples of suitable amino acids include lysine, arginine, glutamine, histadine, and derivatives thereof. One suitable derivative includes an imidazole-acetic acid-lysine group such as described by Langer and coworkers (PNAS 2001, 98(3), 1200-1205).
The term “hydrazone bond” refers to the imine (N═C) bond of a hydrazone. In other words, the hydrazone bond refers to the bond formed between the N′ nitrogen of a hydrazine or hydrazide, and a carbonyl group of an aldehyde or ketone, which results in the formation of an N═C bond. The term hydrazone refers to an N-alkylidene derivative of a hydrocarbyl derivative of a hydrazine. The term hydrazide refers to a hydrazine that has an acyl substituent.
The term “therapeutic agent” refers to biologically active agents, prodrugs, or drugs, including, for example, any organic or inorganic small molecule compound (e.g., a molecule with a molecular weight of less than about 700, or less and about 500), polymeric species (including nucleic acids (DNA, such as pDNA, and RNA), proteins, peptides, hormones, carbohydrates, and derivatives thereof), lipids and mixtures thereof, wherein said drug or agent can be administered in vivo (in humans or animals) for the treatment of a disease, condition, or disorder. In one embodiment, the micelle cargo can be lactate dehydrogenase (LKD). In other embodiments, the micelle cargo can be a plasmid that encodes for an enzyme that can activate a prodrug to a drug.
When the therapeutic agent is pDNA, it can either be used for expression of a prodrug activating protein, or the pDNA can include sequences that allow for transposition of a gene into a host genome. Such a method can be used for long term protein expression of, for example, a deficient gene, for treating a genetic disorder. One significant advantage of non-viral vehicles over viral vehicles is that the micelle polyplexes described herein can encapsulate very large sized agents, such as a plasmid with about 5K or about 6K base pairs. For example, pGL3 plasmid (5280 bp) (Promega Corp.) was used as a reporter assay in various experiments. One can increase the amount of polymer in proportion to size of pDNA, using the suitable N/P ratio, for example, a N/P ratio of about 20, for many of the polymers disclosed herein. The N/P 1 for pGL3 was determined by running agarose gels, defining a suitable ratio as the lowest amount of polymer it takes to retard 1 μg of pGL3 (pDNA). This ratio will of course change as other forms of DNA are selected for use in the micelles.
Other therapeutic agents include siRNAs, which are now known to be tolerated and effective in several different tissues. Plasmids encoding RNAi can be used as the therapeutic agent of the micelles of the invention. Certain of these plasmids are available from InvivoGen, San Diego, Calif. RNAi-based drugs currently in pre-clinical development include those targeting respiratory syncytial virus, hepatitis C, HIV, Huntington's disease and several other neurodegenerative disorders (Check (2005) Nat Med 11(3):243-244; Schmidt Knockout Punch. The Promise of RNAi. bio.com, New & Features 2005 Jun. 28). Phase I clinical trials are underway for several siRNA-based drugs targeting age-related macular degeneration (AMD), and Phase II trials have recently started for one siRNA candidate for AMD (www.sirna.com/sirnaproduct/sirna-027.html; www.acuitypharma.com/press.asp). Cellular delivery and stabilization are critical hurdles to overcome in development of viable siRNA-based drugs, therefore the drug delivery vehicles described herein should provide needed help in this important area of therapy. See Soutschek et al. (2004) Therapeutic silencing of an endogenous gene by systemic administration of modified siRNAs. Nature 432(7014):173-178.
A “prodrug” is a pharmacological substance that can be administered in an inactive (or significantly less active) form that the active compound that the substance is metabolized in vivo. Some specific examples of prodrugs include, but are not limited to, enalapril, valaciclovir, levodopa, chloramphenicol, codeine, and gamma-butyrolactone (GBL).
The term “micelle” refers to a supermolecular structure having a core-shell form. Micelle formation is entropy driven and water molecules are typically excluded into the bulk phase. When above critical micelle concentration (CMC), amphiphilic portions of the polymer employed aggregate into structured micelles. Polymeric micelles are typically spherical and can have nanoscopic dimensions in the range of about 1 to about 250 nm, typically in the 20-100 nm range. This is advantageous because circulating particles less than about 200 nm can avoid filtering by interendothelial cell slits at the spleen. Additionally, delivery vehicles of less than about 150 nm are much more efficiently taken up by cells. Polymeric micelles have been shown to circulate in the blood for prolonged periods and capable of targeted delivery of therapeutic agents, for example, nucleic acids or poorly water-soluble compounds. Upon disassociation, micelle unimers are typically <50,000 g/mol, permitting elimination by the kidneys. These properties allow for prolonged circulation with little or no buildup of micelle components in the liver that could lead to storage diseases. A “micelle composition” as used herein is any composition that includes a micelle, for example, a novel micelle as described herein.
The term “PEG” refers to poly(ethylene glycol) and derivatives thereof. The molecular weight of the PEG chain can be about 500 to about 20,000. In certain embodiments, the PEG group can have a molecular weight of about 1,000 to about 20,000, about 2,000 to about 15,000, about 3,500 to about 12,000, or about 3,000 to about 9,000. In other embodiments, the PEG groups can have a molecular weight of about 4,000 or about 7,000. PEG groups can terminate in any variety of groups including hydroxy, alkyl, alkoxy, aryl, arylalkyl, amino, and the like, referred to herein as PEG-capping groups.
The term “PEG-capping group” refers to a group at the end of a PEG chain. The PEG chain can terminate in any variety of groups including hydroxy, alkyl, alkoxy, aryl, arylalkyl, amino, and the like. Other PEG-capping groups that can be used include acyl groups such as acetyl, acryloyl, and benzoyl, various silane protecting groups, benzyl groups, or heterocyclic groups, or the terminal hydroxy group of the PEG can be oxidize to an aldehyde or a carboxylic acid (i.e., the CH2CH2—R2 group of formula I is oxidized to CH2CO2H).
PEG groups can also have an amino acid capping group, such as a group of 1 to about 30 amino acids. In one embodiment, the PEG capping group is melittin, a 26 amino acid membrane disrupting agent. In another embodiment, the melittin can be attached directly to a amino acid unit of the polymer backbone, allowing it to be exposed when the PEG groups of the polymer are hydrolyzed from side chain to which they are linked. Also, the amount of PEG groups relative to the number of amino acid units in a particular block can be effectively adjusted by linking branched PEG groups to the appropriate linking functional groups of the amino acid side chains. It should also be noted that the skilled artisan can control the substitution rate of hydrazide groups on the PEG conjugating block so that carboxyl groups or other functional groups can be introduced to capture small molecules as well as ions. This may induce more effective endosomal escape by affecting ion channels and material transport in the cell.
The term “organic linking group” refers to a group that includes at least one carbon atom that links two other groups together, for example, two polymer blocks. In some embodiments, the organic linking group can be a group of the formula -X1-X2—C(═Y*)-Z1-Z2- wherein X1, X2, Y*, Z1, and Z2 are each independently O, S, NH, CH2, or absent.
The term “protecting group” refers to any group which, when bound to a hydroxyl, nitrogen, or other heteroatom prevents undesired reactions from occurring at this group and which can be removed by conventional chemical or enzymatic steps to reestablish the ‘unprotected’ hydroxyl, nitrogen, or other heteroatom group. The particular removable group employed is often interchangeable with other groups in various synthetic routes. Certain removable protecting groups include conventional substituents such as, for example, allyl, benzyl, acetyl, chloroacetyl, thiobenzyl, benzylidine, phenacyl, methyl methoxy, silyl ethers (e.g., trimethylsilyl (TMS), t-butyl-diphenylsilyl (TBDPS), or t-butyldimethylsilyl (TBS)) and any other group that can be introduced chemically onto a hydroxyl functionality and later selectively removed either by chemical or enzymatic methods in mild conditions compatible with the nature of the product. These protecting groups can likewise be used to protect a nitrogen atom.
A large number of protecting groups and corresponding chemical cleavage reactions are described in Protective Groups in Organic Synthesis, Theodora W. Greene (John Wiley & Sons, Inc., New York, 1991, ISBN 0-471-62301-6) (“Greene”, which is incorporated herein by reference in its entirety). Included therein are nitrogen protecting groups, for example, amide-forming groups. In particular, see Chapter 1, Protecting Groups: An Overview, pages 1-20, Chapter 2, Hydroxyl Protecting Groups, pages 21-94, Chapter 4, Carboxyl Protecting Groups, pages 118-154, and Chapter 5, Carbonyl Protecting Groups, pages 155-184. See also Kocienski, Philip J.; Protecting Groups (Georg Thieme Verlag Stuttgart, New York, 1994), which is incorporated herein by reference in its entirety. Some specific protecting groups that can be employed in conjunction with the methods of the invention are discussed below.
Typical nitrogen protecting groups described in Greene (pages 14-118) include benzyl ethers, silyl ethers, esters including sulfonic acid esters, carbonates, sulfates, and sulfonates. For example, suitable nitrogen protecting groups include substituted methyl ethers; substituted ethyl ethers; p-chlorophenyl, p-methoxyphenyl, 2,4-dinitrophenyl, benzyl; substituted benzyl ethers (p-methoxybenzyl, 3,4-dimethoxybenzyl, o-nitrobenzyl, p-nitrobenzyl, p-halobenzyl, 2,6-dichlorobenzyl, p-cyanobenzyl, p-phenylbenzyl, 2- and 4-picolyl, diphenylmethyl, 5-dibenzosuberyl, triphenylmethyl, p-methoxy-phenyldiphenylmethyl, di(p-methoxyphenyl)phenylmethyl, tri(p-methoxy-phenyl)methyl, 1,3-benzodithiolan-2-yl, benzisothiazolyl S,S-dioxido); silyl ethers (silyloxy groups) (trimethylsilyl, triethylsilyl, triisopropylsilyl, dimethylisopropylsilyl, diethylisopropylsilyl, dimethylthexylsilyl, t-butyldimethylsilyl, t-butyldiphenylsilyl, tribenzylsilyl, tri-p-xylylsilyl, triphenylsilyl, diphenylmethylsilyl, t-butylmethoxy-phenylsilyl); esters (formate, benzoylformate, acetate, choroacetate, dichloroacetate, trichloroacetate, trifluoroacetate, methoxyacetate, triphenylmethoxyacetate, phenoxyacetate, p-chlorophenoxyacetate, 3-phenylpropionate, 4-oxopentanoate (levulinate), pivaloate, adamantoate, crotonate, 4-methoxycrotonate, benzoate, p-phenylbenzoate, 2,4,6-trimethylbenzoate (mesitoate)); carbonates (methyl, 9-fluorenylmethyl, ethyl, 2,2,2-trichloroethyl, 2-(trimethylsilyl)ethyl, 2-(phenylsulfonyl)ethyl, 2-(triphenylphosphonio)ethyl, isobutyl, vinyl, allyl, p-nitrophenyl, benzyl, p-methoxybenzyl, 3,4-dimethoxybenzyl, o-nitrobenzyl, p-nitrobenzyl, S-benzyl thiocarbonate, 4-ethoxy-1-naphthyl, methyl dithiocarbonate); groups with assisted cleavage (2-iodobenzoate, 4-azidobutyrate, 4-nitro-4-methylpentanoate, o-(dibromomethyl)benzoate, 2-formylbenzenesulfonate, 2-(methylthiomethoxy)ethyl carbonate, 4-(methylthiomethoxy)butyrate, miscellaneous esters (2,6-dichloro-4-methyl-phenoxyacetate, 2,6-dichloro-4-(1,1,3,3 tetramethylbutyl)phenoxyacetate, 2,4-bis(1,1-dimethylpropyl)phenoxyacetate, chlorodiphenylacetate, isobutyrate, monosuccinate, (E)-2-methyl-2-butenoate (tigloate), o-(methoxycarbonyl)-benzoate, p-poly-benzoate, α-naphthoate, nitrate, alkyl N,N,N′N′-tetramethyl-phosphorodiamidate, n-phenylcarbamate, borate, 2,4-dinitrophenylsulfenate); and sulfonates (sulfate, methanesulfonate (mesylate), benzenelsulfonate, benzylsulfonate, tosylate, triflate).
Specific ranges, values, and embodiments provided herein are for illustrative purposes and do not otherwise limit the scope of the invention, as defined by the claims. The term “about” is intended to encompass variations in physical values, and in amounts of ingredients and the like, owing to variations in weighing and other measurement techniques, purity of ingredients, and other factors, as would be known to the art worker. Such variations are often no more than about ±0.5%. The term “about” can thus indicate a variation of +5 percent, or ±10 percent of the value specified; for example about 50 percent carries a variation from 45 to 55 percent; or the term can indicate ±1, 2, or 3 integers from the value specified.
Gene Directed Enzyme Prodrug Therapy (GDEPT) is a strategy for minimizing normal tissue toxicities associated with systemic administration of anticancer drugs.
The long circulating nanoparticles extravasate across leaky tumor blood vessels into the cancer. New proteins are synthesized by the nucleus that express the incorporated gene coding, e.g., the encoded enzymes. A non-toxic prodrug such as 5-fluorocytosine is injected intravenously. Only cells expressing the enzyme can convert prodrugs into toxic drug molecules (e.g. 5-fluorouracil), thereby minimizing negative side effects to healthy tissues.
A pH-sensitive poly(Aspartate-Hydrazide-PEG)-b-poly(L-Lysine) block-copolymer particle and its release of PEG groups, according to an embodiment of the invention, is illustrated in
The non-viral delivery vehicles described herein can furthermore deliver pDNA to cancer cells. Upon deliver of the pDNA to the cell interior, the cancer cells can then code for antigens and cytokines to illicit or enhance the body's immune response toward cancer cells. Today nearly 40% of all gene therapy clinical trials have used genes coding for antigens and cytokines (using mostly viral vehicles) with about 70% of trials targeting cancer diseases. Gene therapy agents that can be used in conjunction with the micelles described herein include those being studied in worldwide clinical trials. See for example, http://www.wiley.co.uk/genetherapy/clinical/countries.html. One can also deliver tumor suppressor genes to arrest cancer cell development. Useful information on RNA interference can be obtained from Ambion, Austin, Tex., and from their technical resources and technical notes found at www.ambion.com.
Polyplex micelle (or “poly-ion complexes”) can be prepared by various methods, including cosolvent evaporation methods. Micelles can be prepared by mixing solutions of the cationic polymers disclosed herein and pDNA in various ratios of N/P, for which N is the total number of amine groups in the block catiomer and P represents the number of phosphate units in the pDNA. For example, a polymer and an agent can be dissolved in a water miscible solvent system. The solution can be slowly added to a vigorously stirred aqueous solution, followed by solvent evaporation. The resulting composition can be nanofiltered and/or centrifuged to remove unincorporated agent. Other useful techniques for preparing micelles have been reported by Kwon and coworkers, Pharm. Res. 2004, 21, 1184-1191.
The ratio of the solvent phase to the aqueous phase can be adjusted to adjust the size of the resulting micelles. For example, in one embodiment, using a lower proportion of the solvent phase results in smaller micelles. Suitably the ratio of solvent phase to aqueous phase can be in the range of about 1:1 to about 1:10, or about 1:2 to about 1:6.
One useful aspect of micelle carriers is that they can be employed for the delivery of therapeutic agents without chemically modifying the agent. The structure of the polymers described herein can be tailored in order to enhance the properties of the micelles for therapeutic agent delivery. Such tailoring includes varying the amount and nature of amino acid side chain modifications, such as those described in the Examples below.
Micelles formed from the polymers disclosed herein allow for the PEG side-groups of the polymers to concentrated at outer portions of the micelles, referred to as the micelle corona. The micelle corona is therefore hydrophilic and allows for its incorporation into cells.
One advantage of micelle compositions includes their ease of storage and delivery. Micelle compositions can be lyophilized and reconstituted before intravenous administration. This allows for a lower risk of agent precipitation, which can in some cases lead to embolism formation. Micelle compositions are capable of long blood circulation, low mononuclear phagocyte uptake, and low levels of renal excretion. Also, micelle compositions have enhanced permeability and retention (EPR) to increase the likelihood of their encapsulated therapeutics reaching their targets, for example, tumors.
Tumors typically have high vascular density, as well as defective vasculature. Accordingly, high extravasation occurs and there may be impaired lymphatic clearance. The endocytosis and subsequent micelle disaggregation allows for the release of the encapsulated agent its delivery into the cell.
Polyplex micelles of various diameters can be prepared. In various embodiments, the unloaded or empty micelles can be prepared. In other embodiments, the resultant micelles can have average diameters of less than about 200 nm, or less than about 100 nm. In another embodiment, the micelles can have an average diameter of between about 55 nm and about 90 nm. In one embodiment, cumulant diameters of polyplex micelles can be about 70 nm to about 90 nm for polymer/pDNA complexes with N/P ratios of 1 to about 20.
The small size of polymeric micelles that have PEG coronas can help the micelle carrier to stay unrecognized, as self, in a biological system. Other advantages associated with nanoscopic dimensions of polymeric micelles include the ease of sterilization via filtration and safety of administration. The core of the micelles can take up, protect and retain biologically active agents, leading to improved solubility and stability of the agents in vivo, their controlled release, and overall reduced toxicity and attenuated pharmacokinetic interaction with other treatment agents.
Related polyplex micelles and their uses are described by Kanayama, Kataoka, and coworkers, ChemMedChem 2006, 1, 439-444, which is incorporated herein by reference. Other related technology is disclosed by Fukushima, Kataoka, and coworkers, J. Am. Chem. Soc. 2005, 127, 2810-2811, which is incorporated herein by reference. Additionally, photochemical transfection technology is disclosed by Kataoka and coworkers, J. Controlled Release 2006, 115, 208-215, which is also incorporated herein by reference. Other useful information on polyamides and micelle technology can be found in WO 2005/118672 (Lavasanifar and Kwon), and U.S. Patent Application Publication Nos. 2004/0005351 (Kwon et al.), 2004/0116360 (Kwon), 2006/0251710 (Kwon and Forrest), each of which is incorporated herein by reference.
Micelles can be suitably formulated into pharmaceutical compositions for administration to human subjects in a biologically compatible form suitable for administration in vivo. Accordingly, in certain embodiments, a pharmaceutical composition is provided that includes micelles as described herein, in admixture with a suitable diluent or carrier.
The compositions containing micelles can be prepared by known methods for the preparation of pharmaceutically acceptable compositions that can be administered to subjects, such that an effective quantity of the therapeutic agent within the micelles is combined in a mixture with a pharmaceutically acceptable vehicle. Suitable vehicles are described, for example, in Remington's Pharmaceutical Sciences (2003, 20th Ed.), in The United States Pharmacopeia: The National Formulary (USP 24 NF19) published in 1999, and in the Handbook of Pharmaceutical Additives (compiled by Michael and Irene Ash, Gower Publishing Limited, Aldershot, England (1995)). On this basis, the compositions include, albeit not exclusively, solutions of the micelles in association with one or more pharmaceutically acceptable vehicles or diluents, and contained in buffered solutions with a suitable pH and iso-osmotic with the physiological fluids. In this regard, reference can be made to U.S. Pat. No. 5,843,456 (Paoletti and Maki). In one embodiment, the pharmaceutical compositions can be used to enhance biodistribution and drug delivery of therapeutic agents, such as drugs.
In accordance with the methods of the invention, the described micelles, may be administered to a subject in a variety of forms depending on the selected route of administration, as will be understood by those skilled in the art. The micelles of the invention may be administered, for example, by oral, parenteral, buccal, sublingual, nasal, rectal, patch, pump, or transdermal administration and the pharmaceutical compositions formulated accordingly. Parenteral administration includes intravenous, intraperitoneal, subcutaneous, intramuscular, transepithelial, nasal, intrapulmonary, intrathecal, rectal and topical modes of administration. Parenteral administration may be by continuous infusion over a selected period of time.
A micelle may be orally administered, for example, with an inert diluent or with an assimilable edible carrier, or it may be enclosed in hard or soft shell gelatin capsules, or it may be compressed into tablets, or it may be incorporated directly with the food of the diet. For oral therapeutic administration, the micelle of the invention may be incorporated with excipient and used in the form of ingestible tablets, buccal tablets, troches, capsules, elixirs, suspensions, syrups, wafers, and the like. A micelle may also be administered parenterally.
Solutions of a micelle can be prepared in water suitably mixed with suitable excipients. Under ordinary conditions of storage and use, these preparations can contain a preservative to prevent the growth of microorganisms.
The pharmaceutical forms suitable for injectable use include sterile aqueous solutions or dispersion and sterile powders for the extemporaneous preparation of sterile injectable solutions or dispersions. The form should be sterile and should be fluid to the extent that easy syringability exists.
Compositions for nasal administration may conveniently be formulated as aerosols, drops, gels and powders. Aerosol formulations typically comprise a solution or fine suspension of the active substance in a physiologically acceptable aqueous or non-aqueous solvent and are usually presented in single or multidose quantities in sterile form in a sealed container, which can take the form of a cartridge or refill for use with an atomizing device. Alternatively, the sealed container may be a unitary dispensing device such as a single dose nasal inhaler or an aerosol dispenser fitted with a metering valve which is intended for disposal after use. Where the dosage form comprises an aerosol dispenser, it will contain a propellant which can be a compressed gas such as compressed air or an organic propellant such as fluorochlorohydrocarbon. The aerosol dosage forms can also take the form of a pump-atomizer.
Compositions suitable for buccal or sublingual administration include tablets, lozenges, and pastilles, wherein the active ingredient is formulated with a carrier such as sugar, acacia, tragacanth, or gelatin and glycerine. Compositions for rectal administration are conveniently in the form of suppositories containing a conventional suppository base such as cocoa butter.
The compositions described herein can be administered to an animal alone or in combination with pharmaceutically acceptable carriers, as noted above, the proportion of which is determined by the solubility and chemical nature of the compound, chosen route of administration and standard pharmaceutical practice. In an embodiment, the pharmaceutical compositions are administered in a convenient manner such as by direct application to the infected site, e.g. by injection (subcutaneous, intravenous, etc.). In case of respiratory infections, it may be desirable to administer the micelles of the invention and compositions comprising same, through known techniques in the art, for example by inhalation. Depending on the route of administration (e.g. injection, oral, or inhalation, etc.), the pharmaceutical compositions or micelles or biologically active agents in the micelles of the invention may be coated in a material to protect the micelles or agents from the action of enzymes, acids, and other natural conditions that may inactivate certain properties of the composition or its encapsulated agent.
In addition to pharmaceutical compositions, compositions for non-pharmaceutical purposes are also included within the scope of the present invention, such as for diagnostic or research tools. In one embodiment, the biologically active agents or micelles comprising such agents can be labeled with labels known in the art, such as florescent or radio-labels or the like.
The present invention includes a delivery system that can be used to deliver biologically active agents or formulations or pharmaceutical compositions. In one embodiment, the invention includes the delivery of nucleic acids. In another embodiment, the invention includes delivery of biologically active agents by loading them into micelles comprising a amphiphilic core and a hydrophilic outer surface, thus improving their delivery in aqueous mediums, such as blood and body fluids. In other aspects, the invention includes the delivery of biologically active agents while reducing their toxicity profile. The invention also includes a method for reducing aggregation of the micelle delivery vesicles of the invention. As such, it provides for better biodistribution of biologically active agents resulting in decreased toxicity and/or improved therapeutic efficacy.
Another aspect of the invention includes a method of delivering biologically active agents to treat a disease, condition, or disorder in a subject in need thereof comprising administering an effect amount of an agent-loaded micelle to a subject. In one embodiment, the disease, condition or disorder is cancer or drug resistant cancers, infectious disease or an autoimmune disease.
The dosage of the micelles of the invention can vary depending on many factors such as the pharmacodynamic properties of the micelle, the biologically active agent, the rate of release of the agent from the micelles, the mode of administration, the age, health and weight of the recipient, the nature and extent of the symptoms, the frequency of the treatment and the type of concurrent treatment, if any, and the clearance rate of the agent and/or micelle in the subject to be treated.
One of skill in the art can determine the appropriate dosage based on the above factors. The micelles may be administered initially in a suitable dosage that may be adjusted as required, depending on the clinical response. For ex vivo treatment of cells over a short period, for example for 30 minutes to 1 hour or longer, higher doses of micelles may be used than for long term in vivo therapy.
The micelles can be used alone or in combination with other agents that treat the same and/or another condition, disease or disorder. In another embodiment, where either or both the micelle or biologically active agent is labeled, one can conduct in vivo or in vitro studies for determining optimal dose ranges, drug loading concentrations and size of micelles and targeted drug delivery for a variety of diseases.
The polymers and compositions described herein can be prepared by any of the applicable techniques of organic synthesis and the related arts. Many such techniques are well known to the skilled artisan. Accordingly, many of the known techniques are elaborated in, for example, Compendium of Organic Synthetic Methods (John Wiley & Sons, New York), Vol. 1, Ian T. Harrison and Shuyen Harrison, 1971; Vol. 2, Ian T. Harrison and Shuyen Harrison, 1974; Vol. 3, Louis S. Hegedus and Leroy Wade, 1977; Vol. 4, Leroy G. Wade, Jr., 1980; Vol. 5, Leroy G. Wade, Jr., 1984; and Vol. 6, Michael B. Smith; as well as March, J., Advanced Organic Chemistry, Third Edition, (John Wiley & Sons, New York, 1985); Comprehensive Organic Synthesis. Selectivity, Strategy & Efficiency in Modern Organic Chemistry. In 9 Volumes, Barry M. Trost, Editor-in-Chief (Pergamon Press, New York, 1993 printing); Advanced Organic Chemistry, Part B: Reactions and Synthesis, Second Edition, Cary and Sundberg (1983); Protecting Groups in Organic Synthesis, Second Edition, Greene, T. W., and Wutz, P. G. M., John Wiley & Sons, New York; and Comprehensive Organic Transformations, Larock, R. C., Second Edition, John Wiley & Sons, New York (1999).
In one embodiment, a polyamide chain can be prepared by methods known to those of skill in the art. These and other methods, such as those provided in the Examples below, provide for the efficient synthesis of various polyamides. The amino acid side chains of the polyamides can then be modified, for example, by attaching hydrophilic groups, such as PEG chains, and PEG chain derivatives. Various linkers can be used to prepare polyamides with side groups that degrade under certain physiological conditions. For example, hydrazone linkers can be used to link PEG chains to the polyamide backbone. Hydrazone linkers provide the advantage of molecular stability at neutral pH, while allowing for the hydrolysis of PEG groups via hydrazone bonds in an acidic environment.
Also, in several embodiments the polyamide polymers of the invention are di-block copolymers. However, this concept can be varied by attaching additional blocks to one end or the other of this di-block, for example, to form a triblock polymer. The third block can be the same as one of the di-block groups, or it can be a different block, such as a physiologically acceptable poly(amino acid) of about 5 to about 150 repeating units. Additionally, the two blocks of the di-block polymers described herein can be separated by an organic linking group by methods well known to those of skill in the art. In other embodiments, one of the blocks of the polymer can be replaced with a octa-poly(arginine) block, or one or more octa-poly(arginine) units can be conjugated to the polymer through a hydrazide group to provide additional cell-penetrating peptide properties to the polymer.
It should also be noted that while some side chain modification reactions go to near completion (such as forming hydrazides), other side chain modification reactions afford much lower yields. The result is a somewhat random arrangement of side chains on a particular block that have been chemically modified, often in order to tune the properties of a micelle that can be formed from the polymer. Accordingly, it is unlikely that PEG groups and other similar groups are spaced equally throughout a polymer block.
The following Examples are intended to illustrate the above invention and should not be construed as to narrow its scope. One skilled in the art will readily recognize that the Examples suggest many other ways in which the present invention could be practiced. It should be understood that many variations and modifications may be made while remaining within the scope of the invention.
Poly(ethylene glycol) (“PEG”) reduces immunogenicity, protects against enzymatic degradation and improves tumor accumulation of conjugates when attached to various liposomes, enzymes, and polycations.1-5 In vivo studies in mice have demonstrated that PEGylated-PEI25 complexes are taken into RES organs less than PEI25.6 However, PEG minimizes interactions with cells and can reduce transfection efficiency.7 Wagner et al. have recently shown already that pH-triggered deshielding of PEG from PLL resulted in better in vivo gene transfer in mice compared to polyplexes with covalent linkages of PEG.8 In their study, they linked PEG via a pH-sensitive hydrazone bond to poly(l-lysine) (PLL) and PEI-25.
It was hypothesize that through the use of a degradable poly(amino acid) block-co-polymer, one for condensing pDNA and the other for pH-sensitive linkage to PEG, it may be possible to study structure-property relationships, varying PEG size as well as block-copolymer sizes. One of the important aspect lies in the methodology through which the acid-labile PEG groups are attached to the polymer. The DNA condensing polymer block can be designed to interact with pDNA at physiologic pH. The second block containing hydrazine groups will remain exposed to the outer-particle environment at this pH; thus polymers containing PEG “brushes” for pre- and post-PEGylation of polyplexes can be prepared.
This approach will allow for the formation of more stable polyplexes for in vivo delivery because pre-PEGylation may hinder the formation of well-packed polyplexes for pH-sensitive release of PEG from polyplexes after endocytosis of the complexes. Furthermore, the pH-triggered release of PEG from complexes in endosomal compartments will aid in unpackaging the pDNA from the polymer and facilitate therapeutic agent, e.g., pDNA, escape into the cytoplasm. See for example, the schematic diagram shown in
β-Benzyl L-aspartate N-carboxyanhydride (“BLA-NCA”) was synthesized by the Fuchs-Farthing method. Three grams of BLA-NCA (12 mM, MW=249 g/mol) was dissolved in an anhydrous cocktail mixture of 1:10 DMF to CH2Cl2 (40.5 mL CH2Cl2, 4.5 mL DMF) under vacuum. To the same flask, 340 μL of butylamine, 10× diluted with CH2Cl2 (MW=74.14 g/mol, d=0.74), was added to initiate polymerization of BLA-NCA. The flask was quickly moved to a 35° C. water bath with a stir bar to react for 24 hours.
Extent of polymerization was evaluated after 24 hours through IR spectral analysis, by monitoring the disappearance of three distinctive NCA peaks (1850 cm−1: C═O asymmetric stretching; 1780 cm−1: C═O symmetric stretching; 910 cm−1: C═O stretching) and polymer purity was evaluated by GPC analysis (mobile phase: 10 mM LiCl in DMF).
The final product poly(β-benzyl L-aspartate), or “PBLA”, was precipitated from cold ether and the pellet of fine crystals was collected by centrifugation (10,000 RPM at 4° C., 10 minutes). After carefully pouring out the supernatant, a small amount of CH2Cl2 was added to the white crystal pellet to aid dissolution and the solution was transferred to a new flask where 100 mL of benzene was added for overnight freeze-drying. Degree of polymerization of PBLA was checked by 1H-NMR measurement in DMSO-d6 at 80° C. with respect to the methyl peak of butylamine (CH3—: δ 0.8).
One gram of PBLA was used as an initiator for each block-copolymer to be synthesized (134 μM, DP=36, MW=7453 g/mol) and 15 mL of CH2Cl2 was added to the reaction flasks under vacuum. The PBLA polymer was allowed to completely dissolve at RT for 15 minutes to ensure complete chain extension into the solvent before the next step. In the case of Lys(Z)-NCA (scheme (a) above), 2.26 grams was added to 30 mL of dry DMF under vacuum (55 equiv, MW=306 g/mol) and the contents of the flask were immediately drawn with a syringe and added to the PBLA flask. The reaction was kept under an inert argon atmosphere.
Similarly, 1.98 grams of Lys(TFA)-NCA (scheme (b) above) was added to 30 mL of dry DMF (55 equiv, MW=268 g/mol) and immediately added to the second flask of PBLA. Both reactions were opaque in color and an additional 30 mL of CH2Cl2 was added to each flask to improve the solubility of both PBLA and Lys monomers. The flasks were moved to a 35° C. water bath with stirring to polymerize for 20 hours.
Extent of block-copolymer polymerization was checked via IR and purity of the block-copolymers was checked through TLC and GPC analysis. Both poly(P-benzyl L-aspartate)-poly(l-lysine(Z)) (PBLA-PLL(Z)) and poly(β-benzyl L-aspartate)-poly(l-lysine(TFA)) (PBLA-PLL(TFA)) reaction mixtures were evaporated under reduced pressure to remove excess CH2Cl2 before precipitating the polymers in a cold ether bath. The polymers were centrifuged to sediment the product and transferred to two new flasks for freeze-drying in benzene overnight. Degree of block-copolymer polymerization was measured by 1H-NMR spectral analysis in DMSO-d6 at 80° C. with respect to peak ratios of the butylamine methyl (CH3—: δ 0.8) to three lysine methylene groups.
PBLA-PLL(Z) (500 mg) was dissolved in 10 mL of dry DMF in a reaction flask stored under vacuum. To the flask, 140 μL of anhydrous hydrazine (5 equiv, MW=32.05 g/mol) was added to the reaction. Similarly, 500 mg of PBLA-PLL(TFA) was dissolved in dry DMF in a separate flask and 155 μL of anhydrous hydrazine (5 equiv, MW=32.05 g/mol) was added. Both reactions were allowed to proceed for 3 hours in a 35° C. water bath. After 3 hours, p(Asp-Hyd)-PLL(TFA/Z) reactions were evaporated under reduced pressure to remove DMF and the polymers were ether precipitated in an ice bath. The polymers were centrifuged and the pellet was transferred to new flasks for overnight freeze-drying in benzene.
1H-NMR of Ace-PEG4k/7k-NH2 in D2O was obtained to confirm the molecular weight of each polymer. PEG4k molecular weight was determined to be 4K and PEG7k had a molecular weight of 7K. One gram of PEG4k/7k was weighted into a reaction flask under an inert argon atmosphere and dried under high vacuum for 30 minutes. Twenty mL of dry DMF was added to each reaction flask, for a final concentration of 50 mg/mL. Triethylamine (275 μL, 5 equiv, MW=101.19 g/mol, d=0.72) and 102 μL of acetic anhydride (3 equiv, MW=102 g/mol) were added to the PEG4k reaction flask. Similarly for PEG7k, 117 μL of triethylamine and 51 μL of acetic anhydride were added. The reactions were allowed to proceed for 1 hour in a 35° C. water bath, after which the polymers were ether precipitated, centrifuged to collect the polymers and freeze-dried in benzene overnight.
In separate reaction flasks, 500 mg of Ace-PEG4k/7k-COCH3 was weighted and 4.5 mL of acetic acid and 0.5 mL of H2O was added to each flask (10:1 AcOH to H2O) for a final concentration of 100 mg/mL. The flasks were transferred to a 35° C. water bath for 5 hours with stirring. The polymers were ether precipitated to remove excess acetic acid and were filtered to collect the crystals. Acetonitrile was used to solubilize the polymer crystals one more time for another round of ether precipitation.
The final polymer crystals were filtered and collected and freeze-dried overnight in 50 mL of benzene. 1H-NMR spectra in CDCl3 at 25° C. of the polymers were taken to determine extent of acetal deprotection with respect to the peak ratios of the methylene protons of PEG (—OCH2CH2—: δ 3.5) and the aldehyde proton (CHO—: δ 9.8) introduced after acetal deprotection. Purity and quantitation of dimer formation after PEG activation was analyzed via GPC.
Varying molar ratios of 1:1, 1:0.5 and 1:0.1 p(Asp-Hyd)-PLL(TFA) to CHO-PEG7K-COCH3 were reacted together in anhydrous DMSO. Assuming 100% hydrazine substitution of PBLA-PLL(TFA), 240 μL of p(Asp-Hyd)-PLL(TFA) (stock concentration 10 mg/mL in DMSO) was respectively reacted with 672 μL, 336 μL and 68 μL of activated PEG7k (stock concentration 50 mg/mL in DMSO). More DMSO was added to each of the 3 reaction vials for a total volume of 2 mL. The reaction vials were allowed to shake at RT for up to 5 days. GPC of each reaction was taken on day 2 and day 5 to monitor PEGylation progress of p(Asp-Hyd)-PLL(TFA).
Poly(β-benzyl L-aspartate), or “PBLA”, was prepared by the ring-opening polymerization of BLA-NCA initiated by the terminal —NH2 of butylamine. The ratio of butylamine initiator to use was in proportion to the desired chain length of PBLA. In this case, theoretical calculations were made for a chain length of 35 and hence a 1:35 molar ratio of initiator to BLA-NCA was used. BLA-NCA is quite sensitive to moisture and it is important to seal the system under inert argon gas and/or store under vacuum to ensure good polymerization results. NCA's are hydrophobic molecules and the best solvent for solubilizing various types of NCA's will vary but in the case of BLA-NCA, a suitable solvent for the reactions was anhydrous CH2Cl2.
After 24 hours, an IR spectra of the final product was taken before proceeding further. At t=0 hours, there were three distinctive peaks present that are characteristic of the carbonyl groups on NCA; at 1850 cm−1 a peak corresponding to asymmetric stretching of C═O, at 1780 cm−1 a peak corresponding to C═O symmetric stretching and at 910 cm−1 a peak corresponding to C═O stretching. After 24 hours, these three distinctive peaks disappeared, suggesting the end of polymerization, i.e., all BLA-NCA monomers were incorporated into the polymer.
To analyze the polydispersity of the newly synthesized PBLA, an RI detector on a GPC was employed. A single peak corresponding to the homopolymer PBLA appeared. GPC conditions employed (mobile phase: 10 mM LiCl in DMF at a flowrate of 0.8 mL/minute) were optimized for PEGylated polymers. It was expected that this hydrophobic homopolymer may interact differently with the column and would appear broader than PEGylated polymers. Nevertheless a calculated polydispersity index Mw/Mn of 1.197 was obtained with an estimated molecular weight of 7,829 g/mol according to calibration curves used.
The actual degree of polymerization obtained for PBLA was calculated by analyzing its 1H-NMR spectra (DMSO-d6 at 80° C.) and integrating peaks with respect to the methyl group present on PBLA that originated from butylamine (CH3—: δ 0.8). From this integration, the peak intensity ratio of the phenyl protons on PBLA (δ 7.2) revealed the degree of polymerization of PBLA to be 36. This allowed calculation of an exact molecular weight of 7,453 g/mol for PBLA. From 3 grams of starting BLA-NCA, 2.204 grams of PBLA36 were obtained, compared to a calculated theoretical yield of 2.4 grams (92% yield).
Poly(β-benzyl L-aspartate)-poly(l-lysine(Z)) (“PBLA36-PLL(Z)”) and poly(β-benzyl L-aspartate)-poly(l-lysine(TFA)) (“PBLA36-PLL(TFA)”) were prepared in order to verify whether the deprotection approach of PLL has detrimental effects on reactivity of hydrazine towards PEG. PBLA36-PLL(Z) requires deprotected under acidic conditions whereas PBLA36-PLL(TFA) can be deprotected under more basic conditions. One goal was to synthesize acid-labile pre- and post-PEGylated complexes for gene transfection. Investigations as to whether it would be a better strategy to deprotect PLL after PEG attachment to hydrazine groups or before PEG attachment were desired. If PEG groups were attached via acid labile bonds to hydrazine groups and then deprotect PLL, the acidity could also cause PEG groups to be removed. However, if PLL is deprotected under acidic conditions first, the reactivity of hydrazine towards PEG in such acidic conditions may be affected.
The pKa of hydrazine is approximately 3-4 versus that of lysine, which is closer to 10. At lower pH (near endosomal pH of 4-5), both hydrazine and lysine terminal —NH2 would be protonated and formation of a Schiff base with activated aldehyde-PEG would be hindered. As reaction conditions approach physiologic pH of 7.4 or higher, hydrazine moieties would being to deprotonate and only PLL should carry a charge on its terminal amine. This is ideal because it is desirable for PLL to condense DNA at physiologic pH, exposing the hydrazine groups. Hence, two types of PBLA36-PLL(X) block-copolymers were prepared to investigate effects of deprotection on hydrazine reactivity to aldehyde-PEG.
PBLA was used to initiate the ring opening polymerization of NCA-Lys(Z) and NCA-Lys(TFA). A target degree of polymerization of 55 was attempted for both types of PLL chains and appropriate PBLA as initiator was used. The reaction was allowed to proceed for 20 hours at which point an IR spectra was taken to confirm that polymerization had ended. Once again, the three distinctive peaks characteristic of NCA C═O stretches (1850 cm−1, 1780 cm−1 and 910 cm−1) were absent in the product spectra, suggesting that all NCA-Lys(TFA/Z) monomers have been incorporated into the product polymer.
GPC of both block-copolymers were obtained. Mobile phase used was 10 mM LiCl in DMF (0.8 mL/minute). Both PBLA36-PLL(TFA) and PBLA36-PLL(Z) chromatograms were not completely unimodal. However this was likely due to the mobile phase employed (DMF), which is not an optimal solvent for these new block-copolymers. Furthermore, these polymers are more hydrophobic than PEGylated polymers analyzed under similar conditions. The hydrophobic nature of these polymers may lead to more polymer interactions with the column, resulting in thinning chromatogram tails. Even though a few new peaks appeared in the chromatograms, they were all determined to be the same polymers in different conformations. To confirm that these additional peaks were not unreacted PBLA polymers, TLC analysis was conducted. Comparisons of the additional block-copolymer peaks with unreacted PBLA were conducted using a CH2Cl2 solvent system. No visible spots corresponding to PBLA were observed on the TLC plates for the block-copolymer aliquots.
Finally, to estimate degree of polymerization for PBLA36-PLL(TFA), a 1H-NMR spectra was taken in DMSO-d6 at 80° C. by integrating with respect to the methyl group of butylamine (CH3—: δ 0.8), followed by analysis of the peak intensity ratio of the three lysine methylene groups (—CH2—: δ 1.26, 1.56, 1.95). For PBLA36-PLL(TFA), the degree of polymerization was found to be 53. Similarly for PBLA36-PLL(Z), a 1H-NMR spectra was taken in DMSO-d6 at 80° C. The degree of polymerization was determined by integration with respect to the methyl group of butylamine (CH3—: δ 0.79), followed by analysis of the peak intensity ratio of the three lysine methylene groups (—CH2—: δ 1.32, 1.92, 2.45). For PBLA36-PLL(Z), the degree of polymerization was 49.
Heterobifunctional (Diethyl)Acetal-PEG4k-NH2 and (Diethyl)Acetal-PEG7k-NH2 were analyzed for purity via GPC (mobile phase=10 mM LiCl in DMF) and unimodal peaks were observed for each. For Ace-PEG4K-NH2, a PDI of 1.038 was obtained and for Ace-PEG7K-NH2 a PDI of 1.027 was obtained. A 1H-NMR spectra of each Ace-PEG4k/PEG7k-NH2 was taken in D2O at 25° C. to determine actual molecular weight. PEG4k was found to be about 4K and PEG7k was found to be about 7K.
The ω-terminal amine of heterobifunctional poly(ethylene glycol) was acetylated and the acetal group was deprotected into an aldehyde to yield activated aldehyde PEG. Because the activated PEG is quite reactive, there is possibility of polymer coupling to form dimers. GPC of activated PEG4k and PEG7k, however, revealed almost unimodal curves. Mobile phase was 10 mM LiCl in DMF at a flowrate of 0.8 mL/min. From analysis of GPC runs of the activated PEG4k, about 4.8% of the reaction formed dimers and for activated PEG7k, about 2.1% formed dimers.
In order to verify acetal conversion into aldehyde, 1H-NMR spectra of both activated PEG polymers were taken in CDCl3 at 25° C. It was determined that for PEG4k, about 87% of acetal groups were converted to aldehyde functionalities. Degree of acetal conversion into aldehyde was calculated by integrating and measuring peak ratios of methylene protons of PEG to the aldehyde proton. For PEG7k, abut 91% of acetal groups were converted to aldehyde functionalities. Thus, activated PEG-aldehyde was successfully prepared in high yield.
Poly(Asp-Hyd)-PLL(TFA) was pre-PEGylated at three different molar ratios of hydrazines to PEG7k. Assuming that all 36 monomers of PBLA reacted with hydrazine, equivalent molar ratios of PEG7k for 1:1, 1:0.5 and 1:0.1 were calculated. Several different organic solvents (CH2Cl2, DMF, AcN, DMSO, MeOH) were investigated before the pre-PEGylation reaction was carried out. None of the aforementioned organic solvents, except DMSO, was able to fully solubilize the block-copolymer. Despite any disadvantages of using DMSO (low volatility), it appeared to be a suitable solvent for carrying out the pre-PEGylation reaction. It is important that the block-copolymer be extended into a good solvent in order to increase level of PEG attachment. It is also favorable if the reaction between hydrazine and the PEG-aldehyde were to proceed quickly because long reaction periods may decrease the reactivity of the aldehyde-PEG.
The reactions were allowed to proceed with shaking at RT for up to 5 days. A GPC of the reactions was taken at day 2 and day 5 to monitor extent of pre-PEGylation over time. The GPC solvent used was 10 mM LiCl in DMF, which was suitable but a more different solvent or solvent system may solubilizing these hydrophobic block-copolymers in a more optimal manner. During GPC analysis of p(Asp-Hyd)36-PLL(TFA)50 with aldehyde-PEG7k at a 1:0.1 molar ratio, block-copolymer appeared to interact with the column, either due to low PEGylation levels or due to lack of PEGylation from loss of PEG-aldehyde reactivity over this long reaction period, causing some decomposition (
Thus, poly(Asp-Hyd)-poly(L-lysine(TFA)) and p(Asp-Hyd)-poly(L-lysine(Z)) have been successfully synthesized. It has been shown, using p(Asp-Hyd)-poly(L-lysine(TFA)), that hydrazide groups on a block-copolymer can interact with PEG-aldehydes to form an acid-sensitive Schiff bases (pre-PEGylation strategy for forming polyplexes). Formation of p(Asp-Hyd-PEG)-poly(L-lysine(TFA)) at three different molar ratios did not increase much beyond the second day of incubation due to steric hindrance from earlier PEG attachment and/or lost of aldehyde-PEG reactivity. The acid sensitivity of p(Asp-Hyd-PEG)-poly(L-lysine(TFA)) was analyzed by verifying release of PEG from the block-copolymer with GPC through the addition of various amounts of TFA and incubating overnight (
The non-mammalian enzyme yeast cytosine deaminase (yCD) has shown potential in activating the prodrug 5-fluorocytosine (5FC) into cytotoxic 5-fluorouracil (5FU) in several tumor models. Unfortunately yCD's instability limits its bolus delivery in enzyme-prodrug type applications. A degradable poly(amino acid) block-copolymer poly(aspartatehydrazide)-poly(L-lysine) with acid-labile PEG attached through the formation of Schiff bases to hydrazide groups was synthesized. PEG provides ‘stealth properties’ to the complex at physiologic pH, minimizing immunogenic responses and prolonging systemic circulation. PEG release is pH-triggered from the polymer under acidic conditions (pH<7). The yCD gene was subcloned into the Hermes HRIgfp vector for regulation by a transactivator (RetroTet RTAb(+)) that binds to its promoter only in the presence of tetracycline. The results from this study provide valuable data supporting the low toxicity effects to cells in the presence of PEG and the importance of PEG release inside the cells for greater gene expression.
The non-mammalian enzyme yeast cytosine deaminase (yCD) has shown potential in activating the therapeutic prodrug 5-fluorocytosine (5FC) into cytotoxic 5-fluorouracil (5FU) in several tumor models. Unfortunately, yCD's instability limits its bolus delivery in prodrug-type applications. Therefore, this Example is directed to enhancing the delivery of the corresponding nucleic acid to the tumor site through a novel non-viral gene carrier system. The design of a pH-sensitive poly(aspartatehydrazide-PEG)-poly(L-lysine) block-copolymer addresses these issues.
A promising two-step therapy approach for tackling the shortcomings of chemotherapy was revived in 1987 by Bagshawe et al. and is generally known as enzyme-prodrug therapy (see Br. J. Cancer 1987, 56:531-532). The core idea behind enzyme-prodrug therapy is to deliver a specific enzyme that will synergistically activate an explicit prodrug in tumor cells. The nontoxic prodrug is systemically injected only after sufficient time has been allowed for the enzyme to localize at the tumor site. Only prodrug molecules in the tumor vicinity are activated, hence minimizing normal cell exposure to toxic drugs. The systemic injection of the gene corresponding to the enzyme in the form of a vector is called gene-directed enzyme prodrug therapy (GDEPT).
The S. cerevisiae yeast cytosine deaminase (yCD) enzyme was cloned and expressed. The resulting 474 bp gene was subcloned into pET-15b to facilitate purification of the protein via a fused histidine tag and transformed into competent BL21(DE3) cells for protein expression. An estimate of about 25-30 mg of pure yCD-His was collected from a 1-liter culture. Thrombin cleavage of the histidine tag on yCD-His was achieved by incubating the protein for 2 hours at 23° C. in thrombin cleavage buffer. Enzyme activity characteristics for yCD and yCD-His was investigated using both the prodrug 5FC and the enzyme's natural substrate, the DNA base cytosine. Five-FC turnover rates remained within 105 M−1·s−1 (Table 1) for both proteins (see E. Kievit et al. Cancer Res. 2000, 60:6649-6655). The diffusion controlled limit for extremely efficient enzymes and their substrates in solution is in the range 108-109 M−1·s−1, therefore it was concluded that yCD was a very efficient pretargeting enzyme for catalyzing 5FC to 5FU conversion, especially applicable to GDEPT. Table 1 shows enzyme activity of yCD and His-yCD, with average values ±SE, with the number of experiments shown in parentheses.
aAmount of enzyme used was 10 uL drawn from a stock of 4.52 ug/mL
bAmount of enzyme used was 10 uL drawn from a stock of 4.23 ug/mL
The PEG block-copolymer (PBC), e.g., poly(Asp-Hyd-PEG)-poly(L-lysine) of Example 1, successfully mediates gene delivery at about the same order of magnitude as the BC but shows dramatically less toxicity in C2C12 and MDA-MB-231 cell lines, especially evident at higher N/P ratios 70 to 100.
The BC buffers better at pH<7.0 than PLL alone due to the presence of hydrazide groups (
The yCD gene was subcloned into the Hermes HRIgfp vector for regulation by a transactivator (RetroTet RTAb(+) or RetroTet RtAb(−)) that will bind to its promoter only in the presence or absence of tetracycline (see A. M. Kringstein et al. Proc. Natl. Acad. Sci. USA 1998, 95, 13670-13675). This allows controlled studies of yCD expression in cells when looking at 5FC or 5FU toxicities.
The results from this study provide valuable data supporting the low toxicity effects to cells in the presence of PEG and the importance of PEG release inside the cells for greater gene expression. The toxicity of 5FU and 5FC on various cell lines have also been confirmed.
An ion exchange column was used to purify the poly(Asp-Hyd-PEG)-b-PLL reaction to remove excess PEG. The ionic strength of the wash was kept low (50 mM phosphate, pH 8.0) with the flowthrough (unreacted PEG) being collected while the cationic polymer with PEG remains remained on the column. The polymer was collected by using a high ionic strength buffer (50 mM phosphate, 2 M NaCl, pH 8.0) and was dialyzed against 50 mM phosphate (pH 8.0) to remove the salt, before lyophilizing. NMR was used to estimate the average degree of PEG substitution on each polymer chain.
Post-PEGylation can be carried out using variously protected block-copolymers or by deprotecting the block-copolymer first followed by formation of a polyplex. The block-copolymers may be suitably soluble in an aqueous environment once deprotected. Suitable solubility is advantageous because polyplexes form via electrostatic interactions with various therapeutic agents, e.g., DNA, which does not occur in an optimal manner in many organic solvent systems.
The intelligent design and characterization of dynamic cationic nanoparticles formed from the self-association of a pH-responsive block copolymer is described in this Example. The platform allows pH-sensitive multilevel PEGylation and imparts nanoparticles with the ability to transition from neutral to charged at a pH of about 5.
In gene therapy, the cytotoxicity of many polycations is undesirable and has been attributed to nonspecific membrane destabilizing effects and intracellular polyplex-mediated toxicity. To help prolong the pharmacokinetic profile of nonviral vehicles for gene delivery, the cationic surface charge of current systems can be shielded through the conjugation of polyethylene glycol (PEG) chains to the particle surface. However, the design of an intelligent polycation with environment-sensing charge modulations is needed to minimize cytotoxicity and enhance gene expression. This Example describes the a novel di-cationic block copolymer, poly(aspartate-hydrazide)-block-poly(L-lysine), which is capable of pH-mediated endosomal membrane disruption based on charge interactions. The block copolymer has negligible toxicity elsewhere to the cell.
The poly(L-lysine) segment, with a high pKa value of ˜9.4, preferentially forms a poly-ion complex with the negative phosphate groups of pDNA, whereas the pH-responsive poly(aspartate-hydrazide) segment, with the comparatively lower pKa, ˜5.0, is characterized by a substantial fraction of unprotonated amino groups at physiological pH. As a consequence, complexation between such a polymer and pDNA leads to the formation of a two-layered nanoparticle. In particular, the nanoparticle possesses an unprotonated pH-responsive segment to serve as both a scaffold for acid-labile linkages of various moieties, such as aldehyde-PEG, and to transition from neutral to charged for disrupting endosomal membranes, and safely enhancing gene expression. This system supports an endosomal escape mechanism based on charge interactions rather than the proton-sponge effect, providing a new classes of nonviral vectors.
Intelligent biomaterials that can emulate natural viruses by adapting to their environment with minimal toxicity to the cell are highly desired for gene therapy. These synthetic vehicles are often internalized in many different cell lines through receptor-mediated endocytosis into clathrin-coated vesicles that fuse to form early endosomes (pH 7.4-6), which become late endosomes (pH 6.0-5.5), and eventually lysosomes (pH 5.0).[1-3] Research to date has primarily emphasized gene delivery carriers equipped with endosomal buffering, also known as the proton sponge effect (PSE),[4] to escape acidic endolysosomes for mediating gene expression.[5,6] However, natural viruses are not equipped with endosomal buffering properties. Instead, they frequently exploit the decrease in pH to expose fusogenic domains that can disrupt the endosomal or lysosomal membrane, resulting in release of the virus into the cytoplasm. Similarly, endosomal membrane disruptions with charged surfaces may also play an important role in helping particles escape from endosomes.[7,8]
Despite their positive attributes, many common polycations are cytotoxic due to nonspecific membrane destabilizing effects and intracellular polyplex-mediated toxicity.[9-12] From these observations, it is postulated that the appreciable effect of charge interaction on endosomal escape would be observed even in the absence of the PSE by designing a pH-responsive polycation with dual functional pKa values (high and low) to emulate the escape mechanism used by natural viruses.
Some of these Asp-Hyd residues are coupled to aldehyde-PEG chains (ALD-PEG) through acid-labile hydrazone linkages to impart favorable stealth properties to the PIC (
The backbone of the block copolymer is derived from poly(β-benzyl-L-aspartate)-block-poly(L-lysine) (PBLA-b-PLL; see Example 1). PBLA was prepared by the ring-opening polymerization of β-benzyl-L-aspartate N-carboxyanhydride (BLA-NCA), initiated by the terminal —NH2 group of butylamine to yield a polymer with narrow distribution and degree of polymerization (DP) of 36. The terminal amine on PBLA was used to initiate ring-opening polymerization of lysine(TFA) N-carboxyanhydride monomers (Lys-NCA) to yield PBLA-b-PLL(TFA) with DP=53, in accordance with previous work in which a PLL length of ˜50 was determined optimal for gene expression.[5,13]
Hydrazide groups were then conjugated with a substitution efficiency near 100 mol % on PBLA, using a procedure reported by Bae et al.,[14,15] to give poly(Asp-Hyd)-b-PLL(TFA) (TFA=trifluoroacetyl). When deprotected, this polymer yields BC. Finally, ALD-PEG (MW=7000 g mol−1) was synthesized following procedures reported by Nagasaki et al.[16] and characterized with 1H NMR (CDCl3; determined 91% acetal conversion into aldehyde groups) and gel permeation chromatography (GPC) (TSK-gel G3000PWXL and TSK-gel G4000PWXL; 10 mm LiCl in N,N-dimethylformamide (DMF); 0.8 mL min−1; polydispersity index (PDI): 1.03).
The final PEGylated block copolymers [poly(Asp-Hyd-PEG)-b-PLL] had either about five ALD-PEG chains conjugated to each poly-(Asp-Hyd) block to form the acid-labile hydrazone linkage (pH-PBC), or about six COOH-PEG chains conjugated covalently by amide linkages to hydrazide groups to generate the non-hydrolysable control (cov-PBC), as shown in
The protonation profile of BC reveals that hydrazide groups do not significantly buffer in the critical range known to be essential for PSE-mediated escape of endosomes (pH 5.0-6.0), similar to PLL (
The effect of pH on colloidal properties of the PIC was also investigated (
At pH 7.4, PICs formed with BC have mostly unprotonated hydrazide groups exposed on the surface (˜5.0 mV), and counterion screening causes particles to exhibit aggregation behavior (diameter ˜440 nm). However, as hydrazide groups on PICs become protonated with decreasing pH, charged cationic surfaces are generated (˜35 mV), overcoming van der Waals interactions and resulting in electrostatic repulsions between individual particles (˜100 nm).
For pH-PBC, the size and ξ profiles are more informative than the averages reported (
Thus, the lactate dehydrogenase (LDH) release studies show that the dual-cationic polymer does not cause membrane toxicity when complexed with pDNA. At physiological pH, free PEI, PLL, and BC polymer chains have cationic properties that cause high levels of membrane toxicity to cells, relative to PEG-shielded polymers (
The metabolic activity of the polymers was then compared, both in free form and in complex with pGL3, to investigate the potential intracellular toxicity often associated with cationic polyplex-mediated uptake.[12] The free polymers (PEI and BC) with accessible cationic components caused greater metabolic toxicity to the cell following internalization (
Finally, the transfection efficiency of these polymers was studied in five very different cell lines. It was found that pH-PBC and BC (both nontoxic) consistently resulted in higher gene expression relative to cov-PBC (
It is of significant interest that the dual-cationic PICs described herein suggest an endosomal escape mechanism for polyplexes attributed to disruptions based on cationic-mediated cellular membrane interactions rather than through the PSE. In other words, selectively controlling interactions between polyplexes and the cell membrane is a new and facile approach for the design of effective and high-performance nonviral gene vectors. This results in nonviral vectors that are both safe to the cell while retaining high transfection efficiencies. Indeed, unlike PEI, which induces effective transfection activity but also causes high levels of nonspecific membrane-associated toxicity (
Upon sensing a decrease in pH, PEG chains are released from pH-PBC PICs, and the remaining BC particle acquires favorable cationic properties for disrupting endosomal membranes. After the particles escape into the cytosol (pH 7.4), hydrazide groups start to deprotonate upon sensing the new pH, imparting neutral properties to the PIC again. This is very similar to how natural viruses respond to their environment by exposing a fusogenic domain at low pH and concealing it at higher pH, and which explains the low metabolic toxicity of PICs in the cell.
In summary, an polycation polymer with dual functional pKa values capable of safely emulating the escape mechanism used by natural viruses has been described herein. This novel dual-cationic block copolymer, poly(Asp-Hyd)-b-PLL, is pH-mediated to disrupt endosomal membranes based largely on charge interactions, and is therefore minimally toxic to the cell elsewhere. This is a mechanism separate from the traditional PSE followed by osmotic rupture of the vesicle. Furthermore, the significant presence of unconjugated hydrazides on the block copolymer can serve as a scaffold for easily incorporating many additional pH-sensitive functionalities, in addition to ALD-PEG, to the PIC to boost gene expression further. Examples of this include PEG-shielded fusogenic peptides for endosomal escape, nuclear localization signals (NLS), dynein-binding moieties, and additional masked targeting peptides for nuclear localization.[21,22] Therefore, these findings offer a new platform for generating more effective and complex multifunctional biomaterials for increasing gene expression.
General materials. Branched polyethylenimine (MW=25000 g mol−1) and poly(L-lysine) hydrobromide (MW=9200 g mol−1) were purchased from Sigma-Aldrich (Milwaukee, Wis., USA). All materials were used without further purification. The pDNA encoding firefly luciferase (pGL3, 5.3 kb) was obtained from Promega (Madison, Wis., USA), transformed into electrocompetent DH5α cells, propagated in LB broth (1 L) supplemented with ampicillin (100 μg mL−1), and purified with a plasmid Maxiprep kit (BioRad, Hercules, Calif., USA). All pDNA had purity levels of 1.8 or greater by UV/Vis (A260/A280). For cell culture work, Dulbecco's modified Eagle's medium (DMEM), RPMI 1640, phosphate buffered saline (PBS), fetal bovine serum (FBS), trypsin-EDTA (0.25% trypsin, 2.21 mm EDTA in Hank's balanced salt solution (HBSS)) and penicillin/streptomycin were purchased from Cellgro (Mediatech, Herndon, Va., USA).
Physical characterization. pH titration measurements for polymers were obtained with an Orion micro-combination pH/sodium electrode (Thermo Electron Corporation, Waltham, Mass., USA; see Supporting Information for general procedures). Dynamic light scattering and ξ potential data were obtained with a nanoZS 90 or a Malvern 3000HS series zetasizer (Malvern Instruments, UK). Polymers were mixed to form PICs at N/P=20 by addition of polymer to an equal volume of pGL3 in Milli-Q water. The sample was allowed to incubate at room temperature for at least 15 minutes before dilution with the appropriate buffer ranging from pH 7.4 to pH 3.0. Particle diameters and ξ potentials were measured following dilution at each pH value.
Cellular LDH release studies. Polymer interactions with cell membranes were evaluated by monitoring LDH release from MDA-MB-231 human breast cancer cells by using the CytoTox 96 non-radioactive assay from Promega (Madison, Wis., USA). One-way ANOVA was used to statistically compare LDH data. MDA-MB-231 cells were seeded in 96-well plates at 25000 cellswell−1. After 18 hours, the plates were washed with PBS (2×) and serum-free DMEM (90 μL) was added. Each 96-well plate was divided into two sections: maximum LDH and experimental LDH release.
Polymer (free or complexed to 1 μg of pGL3) was added to both sections appropriately and incubated with the cells for 4 or 8 hours. At the end of each incubation period, PBS was added to the experimental LDH wells (10 μL for volume correction) and 50 μL of the final supernatant was removed and put into a separate 96-well plate. Next, 10 μL of lysis solution (Triton-X, 9% v/v) was added to the remaining maximum release wells and incubated for 1 hour at 37° C. Then, 50 μL of the supernatants from these lysed cells were used as controls for determining maximum LDH release. LDH substrate (50 μL) was then added to the separate 96-well plates containing supernatants, covered with aluminum foil, and shaken at room temperature for 30 minutes before reading the absorbance (λ=492 nm).
Cellular metabolic toxicity studies. Metabolic toxicity was assessed through the resazurin dye (Sigma-Aldrich, Milwaukee, Wis., USA) by incubating the respective polymers (free or complexed with 1 μg pGL3) in serum-containing media and monitoring the toxic effects of the polymers on the metabolic rates of cells through reduction of the dye. Briefly, 96-well plates were seeded at 20000 cellswell−1 and incubated for 24 hours. Free polymer at increasing concentrations of 0-50 μg mL−1 was added to wells and incubated in serum-containing media for 4 hours before refreshing the media. After 18 hours incubation, 10 μL of resazurin dye (60 μm in PBS) was added to each well and incubated for 4 hours before measuring fluorescence (λex=560 nm, λem=590 nm). Cell viability is reported as relative metabolic rate with respect to controls without polymers. Two-way ANOVA was used to compare the data.
Cell transfection studies. MDA-MB-231 (human breast cancer), C2C12 (murine myoblast) and MCF-7 (human breast cancer) cell lines were obtained and cultured according to ATCC protocols. COS-7 cells (Green African monkey kidney) were obtained from David M. Lynn (University of Wisconsin). 4T-1 cells (murine colon cancer) were obtained from the Small Molecule Screening Facility Center (University of Wisconsin) and cultured in RPMI 1640 supplemented with 10% FBS and 1% penicillin/streptomycin.
The luciferase assay system was purchased from Promega. Luminescence was measured with a microplate Tropix luminometer (Applied Biosystems). Protein content was obtained using the DC protein assay kit from BioRad (Hercules, Calif., USA), absorbance was measured with the Spectramax 190 microplate reader (Molecular Devices, Sunnyvale, Calif., USA), and results were fit to a known protein calibration curve. Cells were seeded at either 300000 cells well−1 in 6-well plates or 150000 cells well−1 in 12-well plates and cultured for 24 hours. The next day, wells were aspirated, washed with PBS (2×1 mL), and appropriate medium for each cell line was added (supplemented with 10% FBS and 1% penicillin/streptomycin).
Complexes (2 μg pGL3well−1) formed at the indicated N/P ratio (N/P=1 is defined as the minimum amount of polymer required to retard 1 μg of pGL3 on a 0.75% agarose electrophoretic gel) were added to wells 4 hours before refreshing the media. After 12 hours, plates were assayed with the Promega luciferase assay system. Luciferase relative light units (RLUs) were converted into units of concentration by using known luciferase concentration standards. One-way ANOVA was used to compare transfection data. A value of p<0.05 was considered statistically significant.
Experimental Details.
β-benzyl L-aspartate N-carboxyanhydride (BLA-NCA) and N-carboxyanhydride lysine(TFA) (NCA-Lys(TFA)) monomers were synthesized by the Fuchs-Farthing method. Poly(β-benzyl L-aspartate) or PBLA was prepared by the ring-opening polymerization of BLA-NCA initiated by the terminal —NH2 of butylamine. The ratio of butylamine initiator to monomer used was in proportion to the desired chain length of PBLA. In this case, theoretical calculations were made for a chain length of 35 and hence a 1:35 mole ratio of initiator to BLA-NCA was used. The final product poly(β-benzyl L-aspartate) or PBLA was precipitated in cold diethyl ether and the resulting pellet of fine crystals formed was collected by centrifugation and freeze-dried in benzene (100 mL) overnight. The degree of polymerization (DP) of PBLA was checked with 1H-NMR in DMSO-d6 at 80° C. by integrating the phenyl protons (—CH2C6H5—: δ 7.3 ppm) with respect to the methyl peak of butylamine (CH3—: δ 0.8 ppm) and found to be 36 with a polydispersity index (PDI) of 1.20 (TSK-gel G3000PWXL and TSK-gel G4000PWXL; 10 mM LiCl in DMF; 0.8 mL/min).
The terminal amine of PBLA was used to initiate the ring opening polymerization of NCA-Lys(TFA). A target DP of 55 was attempted for the PLL chain, and appropriate amounts of PBLA as initiator was used. The final composition of the block-copolymer was checked with IR, GPC and TLC. 1H-NMR was taken in DMSO-d6 at 80° C. by integrating with respect to the methyl group of butylamine (CH3—: δ 0.8 ppm) and then looking at the peak intensity ratio of the three lysine methylene groups (—CH2—: δ 1.26, 1.56, 1.95 ppm). For PBLA36-PLL(TFA), the degree of polymerization was 53. Next, the benzyl groups of PBLA-PLL(TFA) were substituted with hydrazide groups. Hydrazine reactivity towards PBLA benzyl groups is quite efficient, yielding nearly 100 mol % substitution[14,15].
pH-sensitive coupling. p(Asp-Hyd)36-b-PLL(TFA)53 (MW 16,500 g/mol) was reacted in DMSO at the desired hydrazide to ALD-PEG (MW 7000 g/mol) ratio for 24 hrs. This was attempted both for 2 PEG chains/polymer and 5 PEG chains/polymer. After the reaction, poly(Asp-Hyd-PEG)-PLL(TFA)53 deprotection was done under basic conditions to prevent acid-sensitive release of PEG chains from the block-copolymer. The deprotection method was done in MeOH/H2O (20:1) using K2CO3 as a base catalyst. The polymer was slightly insoluble in MeOH/H2O due to the hydrophobic PLL(TFA) and free hydrazide groups (despite presence of PEG) and DMSO was added as needed to improve the solubility of the block-copolymer. The reaction proceeded for 3 hrs under reflux at 60° C. The expected product would have a molecular weight of 51,500 g/mol, hence it was filtered against water 3× using Millipore Amicon Ultra centrifugal filter devices (MWCO 30,000 g/mol) and the filtrate containing the deprotected pH-sensitive polymer was lyophilized. Again, 1H-NMR in D2O as before revealed that either 2 or 5 PEG chains were conjugated to each polymer.
Covalent coupling. Standard DCC/DMAP/NHS chemistry was used to couple methoxy-capped carboxylic terminated PEG (COOH-PEG) (MW 7000 g/mol, Polymer Source, Montreal, Canada) to hydrazide groups on poly(Asp-Hyd)36-b-PLL(TFA)53. For a theoretical yield of 6 PEG chains/polymer (or 1:0.24 hydrazide to COOH-PEG), 297 mg COOH-PEG (42 μmol) and 109 mg of the polymer (MW 16,500 g/mol, 178 μmol hydrazides) were each dissolved in 4.5 mL of DMSO to stir until fully solubilized. Next, 432 mg DCC (50 equiv), 48 mg NHS (10 equiv) and 2.8 mg DMAP (0.2 equiv) were added to the polymer vial and stirred to dissolve fully before COOH-PEG solution was added (concentration 10 mg/mL). The reaction was stirred at room temperature overnight. The following day, the solution was diethyl ether precipitated and centrifuged to collect the pellet. The pellet was dissolved in 11 mL of 0.1N NaOH to deprotect TFA groups. DMSO was added to the reaction to increase solubility (since the solution became cloudy in appearance) and was stirred for 1 hr at RT. The reaction was again filtered 3× with water using spin-tubes as before (MWCO 30,000 g/mol, Millipore Centriplus filter tubes) and lyophilized. 1H-NMR (Varian 400 MHz, D2O) reveals that there are experimentally 6 PEG chains/polymer.
pH titration method. An initial pH measurement was taken with the micro pH electrode, then 5 μL increments of 0.1N HCl was titrated into the solution, and the pH response following each addition of HCl was measured (n=3). The pH response was plotted versus degree of protonation for each polymer, based on the change in H+ levels in solution and amount of polymer used:
and assuming that initial pH=pKa of the amines on the polymer. The total percentage of protonable amines in this batch of commercial PEI was experimentally measured using an inverse gated decoupled 13C-NMR experiment to minimize NOE contributions, as described by von Harpe et al (Varian 500 MHz; D2O; delay=30 sec; pw=90; T=30° C.)[23].
This Example provides several combinations of enzyme/prodrug systems that can be used for GDEPT (Table 3). It is worthwhile to note that most clinical trials of GDEPT have utilized viral vectors as gene delivery vehicles, but the success of these enzyme/prodrug combinations could very well translate to other carriers, especially as progress is being made in the non-viral field of gene delivery.
HSV-tk/ganciclovir. The most common gene used for GDEPT is the Herpes Simplex Virus type-1 gene which codes for the thymidine kinase enzyme (HSV-tk)[21]. When the gene is transfected into tumor cells, it renders them sensitive to the prodrug ganciclovir (GCV). This is the only GDEPT system that has reached Phase III clinical testing[22] and is commonly investigated for treating malignant gliomas[23,24]. Fusion proteins of GFP and HSV-tk reveal that the enzyme is localized mostly in the nuclei [25] Cells expressing HSV-tk (tk+) are capable of monophosphorylating GCV, which in turn gets triphosphorylated by cellular kinases, and induces cell death by incorporating into the DNA. It was found that the bystander effect of GCV was not due to passive diffusion but due to transfer through cellular gap junctions between cells[26]. GCV appeared to work better during S phase of mitosis when the cells were actively dividing, therefore this property could be a drawback in slower dividing hypoxic regions of a tumor[22].
CD/5FC. Cytosine deaminase (CD) is involved in the pyrimidine salvage pathway of bacteria and yeast, and is not endogenous to humans. CD can convert the non-toxic antifungal agent 5-fluorocytosine (5FC) into toxic 5-fluorouracil (5FU). The drug inhibits synthesis of DNA or RNA when its metabolite is incorporated into each respective chain, and the drug can also irreversibly bind to thymidylate synthase (an enzyme critical for DNA synthesis). Fungal CD has superior turnover rates both for the DNA base cytosine and 5FC, compared to bacterial CD[16], but is reportedly less stable[27]. Because 5FC and 5FU are small non-polar molecules, they can therefore freely diffuse across cell membranes, generating a good bystander effect. The toxicity of 5FU is not cell-cycle specific and the antitumor effect of CD/5FC has been demonstrated in a variety of tumor systems[22], Encouragingly, a colon cancer model revealed that when 4% of cells expressed CD, it was sufficient to give a 60% cure rate in tumor-bearing animals, compared to the HSV-tk/GCV system where 50% of the cells had to be expressing to give the same cure rate[28]. There have been two phase I clinical trials of the CD/5FC system using viral vectors for treating colon cancer metastasis in the liver, and prostate cancer[22]. The prostate clinical trial resulted in 2 out of the 16 patients being cancer-free 1-year after the treatment[29].
CE/CPT-11. Carboxylesterase (CE) can hydrolyze esters into acids and carbamates into alcohols. The enzyme is endogenously expressed as two major isoforms in the human liver, and is also present in tumor tissues[30]. The rabbit liver analogue of CE is reported to be up to 1000-fold more efficient than human CE at converting the prodrug irinotecan (7-ethyl-10[4-(1-piperidino)-1-piperidino] carbonyloxy-camptothecin, CPT-11) into the potent topoisomerase I inhibitor SN-38 (7-ethyl-10-hydroxycamptothecin)[31-33]. The SN-38 inhibitor binds to the topoisomerase I enzyme (which cleaves, unwinds and ligates DNA strands) and prevents the DNA from re-ligating after being unwound. CPT-11 demonstrates good bystander effects[34], which makes it suitable for GDEPT. The CE/CPT-11 conversion efficiency was evaluated in 59 patients undergoing surgery for treatment of liver or colorectal cancers in France to monitor prodrug conversion in normal vs. tumor tissues[24]. In 12 out of 53 patients, a ratio>5 for prodrug conversion in the tumor with respect to normal tissue was observed. This system shows promise in GDEPT since successful delivery and expression of rabbit CE may further increase prodrug/drug conversion at the tumor site[33].
bGlu/HMR-1826. This is an enzyme found in prokaryotes and eukaryotes. It is widely distributed in human tissues, especially liver and spleen[35], and beta-glucuronidase (bGlu) is also expressed at higher levels in tumor lysosomes[15,36]. The enzyme can hydrolyze beta-glucuronic linkages from glycosaminoglycans and is highly specific for the glucuronyl residue[37], hence the linker is useful in the design of various prodrugs such as doxorubicin (HMR-1826), paclitaxel or 5FU[33, 37-40]. Most prodrugs tend to be cell permeable for conversion into the active drug inside the cell, where the enzyme is being generated. However, HMR-1826 is hydrophilic and therefore cell impermeable. To overcome this issue, it was reported that cells transduced by a secretable form of bGlu (to establish an extracellular prodrug-drug depot of activating enzymes) showed great promise at converting HMR-1826 into lipophilic doxorubicin (DOX) and the effector drug generated resulted in a strong bystander effect with enhanced antitumor activity[37,41].
NTR/CB1954. Most of the GDEPT studies with this enzyme have used the NfsB gene coding for nitroreductase (NTR) from E. Coli[42]. The enzyme requires a flavin mononucleotide (a cofactor derived from vitamin B2) to efficiently reduce quinones and aromatic nitrogen groups into hydroxylamines[43]. NTR has broad substrate specificity for nitrogen mustards and carbamates[44], making this enzyme attractive for the design and activation of a variety of prodrugs. CB1954 is a prodrug that is efficiently reduced by NTR into the corresponding hydroxylamine, which is further metabolized by cellular kinases into the toxic agent capable of crosslinking DNA. CB 1954 demonstrates good bystander effect[45]. The first clinical trial for this system was reported in 2004 when 18 patients with liver or colorectal cancers were treated by direct intratumoral administration of a replicant-deficient adenovirus vector coding for NTR[46]. The study revealed that high expression of NTR was well-tolerated by patients.
GDEPT in cancer therapy has been clinically tested over the years using a variety of enzyme/prodrug combinations. Certain combinations appear to sufficiently kill cancer cells, and each has its advantages. However, they all aim to improve the therapeutic efficacy of a lethal drug by minimizing non-specific tissue toxicities. Despite some of these promising preclinical results with viral vectors, there still remain many obstacles that must be overcome before GDEPT becomes the treatment of choice for cancer therapy, namely the issue of the delivery vector, and ultimately levels of expression of the therapeutic gene. The micelles of the invention overcome these obstacles to provide a significantly improved method of delivering these drugs than current methods.
All publications, patents, and patent documents are incorporated by reference herein, as though individually incorporated by reference. The invention has been described with reference to various specific and preferred embodiments and techniques. However, it should be understood that many variations and modifications may be made while remaining within the spirit and scope of the invention.
This application is a U.S. National Stage Filing under 35 U.S.C. § 111(a) of International Application No. PCT/US2007/024966, filed Dec. 6, 2007, which claims priority under 35 U.S.C. § 119(e) to U.S. Provisional Patent Application No. 60/873,169, filed Dec. 6, 2006, which applications are incorporated herein by reference.
This invention was made with government support from the National Institutes of Health under NIH Grant R01 AI-43346-08. The United States Government has certain rights in this invention.
