Patent Application
20080260850
This present invention relates to a delivery system and a method for the intracellular delivery of bioactive agents using polymeric drug carriers. More particularly, it relates to a method for the intracellular delivery of bioactive agents using polymeric drug carriers formed from (a) an amphiphilic block copolymer which is comprised of a hydrophilic block and a hydrophobic block, wherein said hydrophobic block has a terminal hydroxyl group that is substituted with a tocopherol or cholesterol group, and (b) a polylactic acid derivative having at least one terminal carboxyl group at the end of the polymer.
In order to achieve the desired therapeutic effect of a bioactive agent, an appropriate amount of the administered drug should enter the target cells in a body. In order to increase the cellular internalization of a drug, an appropriate concentration of the drug should be maintained for a desired time period in the target tissue; furthermore, the drug should enter the target cells in the tissue. A high drug concentration in a tissue can be achieved by a formulation exhibiting a long blood circulation time. Therefore, great effort has been made to develop drug delivery systems by the use of nanoparticulate drug carriers, including liposome and polymeric micelles, having long circulation times.
Many approaches have been suggested for enhancing the intracellular uptake of bioactive agents. Delivery vehicles such as liposomes have also been described for use in the intracellular delivery of bioactive agents such as oligonucleotides (Felgner, et al., U.S. Pat. No. 5,264,618 (1993); Eppstein, et al., U.S. Pat. No. 4,897,355 (1990); and Wang, et al., Proc. Nat. Acad. Sci. 84: 7851-7855 (1987); U.S. Pat. No. 5,759,519 (1998)). The use of liposomes as drug carriers, however, is limited due to such problems as low entrapment efficiency, drug instability, rapid drug leakage, and poor storage stability. Small molecular surfactant micelles are easily dissociated when they are diluted with body fluids after being administered into the body; so it is difficult for them to perform their role as drug carriers.
In recent years, efforts have been made for the preparation, characterization and pharmaceutical application of polymeric micelles. These were well reviewed by V. Torchilin in Journal of Controlled Release 73 (2001) pp. 137-172. Polymeric micelles are characterized by a core-shell structure in aqueous media which results from the amphiphilic block copolymers having hydrophobic (core) and hydrophilic (shell) segments. A poorly water soluble drug is entrapped within the hydrophobic core of the micelle. There has been considerable research into the development of A-B, A-B-A, or B-A-B block copolymers having a hydrophilic A block and a hydrophobic B block. For use as a drug carrier, it is preferred that the hydrophobic B (inner micelle core block) comprises a biodegradable polymer such as poly-DL-lactide, poly-ε-caprolactone or poly(γ-benzyl-L-aspartate) and that the hydrophilic A (outer micelle shell block) be a polymer which is capable of interacting with plasma proteins and cell membranes, such as polyethylene glycol (PEG).
Polymeric micelles provide attractive characteristics in that they can avoid uptake of the drug by the reticuloendothelial system (RES) or the mononuclear phagocyte system (MPS) in vivo, and hence, they can circulate in the blood for a long period of time. This advantage comes from the structure of a micelle. The hydrophilic portions of an amphiphilic block copolymer form the outer shell and are exposed to body fluid, and hence, effectively protect the micelles from interactions with the cell membranes and plasma proteins in the blood [V. Torchilin et al., Advanced Drug Delivery Reviews 16 (1995) pp. 141-155].
R. Savic et al. showed experimental evidence that micelles formed from poly(caprolactone)-b-poly(ethylene oxide) block copolymers can deliver a bioactive agent into living cells by using micelles with tetramethylrhodamine-5-carbonyl azide (TMRCA) covalently attached to the PCL end of the polymer [R. Savic et al., Science 300 (2003) pp. 615-618]. However, the fluorescent micelles were detected only in the cytoplasmic but not in the nuclear compartment and thus bioactive agents such as DNA binding anticancer drugs are not appropriate for use with the micelles.
In view of the foregoing, development of a polymeric micelle or nanoparticle which can deliver bioactive agents into the targeted cells is desired. Thus, the present invention provides a method for the targeted intracellular delivery of bioactive agents using a polymeric micelle or nanoparticle drug carrier.
It is an object of the present invention to provide a method for the intracellular delivery of bioactive agents using polymeric drug carriers formed from compositions comprising (a) an amphiphilic block copolymer which is comprised of a hydrophilic block and a hydrophobic block, wherein said hydrophobic block has a terminal hydroxyl group that is substituted with a tocopherol or cholesterol group, and (b) a polylactic acid derivative having at least one terminal carboxyl group at the end of the polymer. Optionally, 0.01 to 10 equivalents of a di- or tri-valent metal ion is bound to 1 equivalent of the carboxyl terminal group of said polylactic acid derivative.
It is another object of the present invention to a delivery system for the intracellular delivery of bioactive agents comprising bioactive agents and a polymeric drug carrier with said bioactive agents entrapped therein in the aqueous solution, wherein the polymeric drug carrier is prepared by a polymeric composition comprising (a) an amphiphilic block copolymer consisting of a hydrophilic block and a hydrophobic block in which said hydrophobic block has a terminal hydroxyl group that is substituted with a tocopherol or cholesterol group and (b) a polylactic acid derivative having at least one carboxyl group at the end of the polymer; and wherein said bioactive agents entrapped in the polymeric drug carrier are allowed to be delivered into a cell in a greater quantity when the drug carrier contact with said cell. It is another object of the present invention to a composition for the intracellular delivery of bioactive agents comprising bioactive agents and a polymeric drug carrier with said bioactive agents entrapped therein in the aqueous solution, wherein the polymeric drug carrier is prepared by a polymeric composition comprising (a) an amphiphilic block copolymer consisting of a hydrophilic block and a hydrophobic block in which said hydrophobic block has a terminal hydroxyl group that is substituted with a tocopherol or cholesterol group and (b) a polylactic acid derivative having at least one carboxyl group at the end of the polymer; and wherein said bioactive agents entrapped in the polymeric drug carrier are allowed to be delivered into a cell in a greater quantity when the drug carrier contact with said cell.
The present invention relates to polymeric drug carriers which can deliver a bioactive agent into a targeted cell.
Before the present invention is disclosed and described, it should be understood that this invention is not limited to the particular configurations, process steps, and materials disclosed herein, and such configurations, process steps, and materials may be varied. It should be also understood that the terminology employed herein is used for the purpose of describing particular embodiments only and is not intended to limit the scope of the present invention which will be limited only by the appended claims and equivalents thereof.
It must be noted that, as used in this specification and the appended claims, the singular forms “a,” “an,” and “the” include plural referents unless the context clearly dictates otherwise. Thus, for example, reference to a polymer containing “a terminal group” includes reference to two or more such groups.
In describing and claiming the present invention, the following terminology will be used in accordance with the definitions set out below.
As used herein, the term “bioactive agent” means an organic compound or drug which has a desirable biological activity or function, i.e. a biological effect or pharmacological effect, in vivo. For example, bioactive agent consisting of therapeutic agents may alter cellular functions, such as gene function. Alternatively, bioactive agents consisting of diagnostic agents, such as magnetic resonance imaging (“MRI”) or computerized tomography (“CT”) agents, have the biological function of enhancing the diagnostic images of tissues and/or organs.
As used herein, the term “biodegradable” or “biodegradation” is defined as the conversion of materials into less complex intermediates or end products by solubilization hydrolysis, or by the action of biologically formed entities which can be enzymes or other products of the organism.
As used herein, the term “biocompatible” means materials or the intermediates or end products of materials formed by solubilization hydrolysis, or by the action of biologically formed entities which can be enzymes or other products of the organism and which cause no adverse effects on the organisms.
“Poly(lactide)” or “PLA” shall mean a polymer derived from the condensation of lactic acid or by the ring opening polymerization of lactide. The terms “lactide” and “lactate” are used interchangeably.
Reference will now be made to the exemplary embodiments and specific language will be used herein to describe the same. It will nevertheless be understood that no limitation of the scope of the invention is thereby intended. Alterations and further modifications of the inventive features illustrated herein, and additional applications of the principles of the invention as illustrated herein, which would occur to one skilled in the relevant art and having possession of this disclosure, are to be considered within the scope of the invention.
The present invention provides a method for the intracellular delivery of bioactive agents using polymeric drug carriers formed from polymeric compositions comprising an amphiphilic block copolymer which is comprised of a hydrophilic block and a hydrophobic block, wherein said hydrophobic block has a terminal hydroxyl group that is substituted with a tocopherol or cholesterol group, and a polylactic acid derivative having at least one terminal carboxyl group at the end of the polymer.
The present invention also provides a method for the intracellular delivery of bioactive agents using drug carriers formed from polymeric compositions comprising an amphiphilic block copolymer which comprised of a hydrophilic block and a hydrophobic block, wherein said hydrophobic block has a terminal hydroxyl group that is substituted with a tocopherol succinic acid or cholesterol succinic acid group, a polylactic acid derivative having at least one terminal carboxyl group at the end of the polymer and 0.01 to 10 equivalents of a di- or tri-valent metal ion with respect to 1 equivalent of the carboxyl terminal group of the polylactic acid derivative.
The present invention further provides a delivery system for the intracellular delivery of bioactive agents comprising bioactive agents and a polymeric drug carrier with said bioactive agents entrapped therein in the aqueous solution, wherein the polymeric drug carrier is prepared by a polymeric composition comprising (a) an amphiphilic block copolymer consisting of a hydrophilic block and a hydrophobic block in which said hydrophobic block has a terminal hydroxyl group that is substituted with a tocopherol or cholesterol group and (b) a polylactic acid derivative having at least one carboxyl group at the end of the polymer; and wherein said bioactive agents entrapped in the polymeric drug carrier are allowed to be delivered into a cell in a greater quantity when the drug carrier contact with said cell.
In an embodiment of the present invention, the bioactive agents are allowed to be delivered into a cell in a greater quantity, and preferably, in more efficient manner. than those in absence of the polymeric drug carrier.
The present invention further provides polymeric drug carriers which can deliver a bioactive agent into targeted cell.
Specifically the present invention provides a method for the intracellular delivery of bio active agents comprising the steps of:
The bioactive agents of the present invention can be any organic compound or any drug which exerts a desirable biological activity. This includes, but is not limited to, proteins, hormones such as testosterone, estradiol, estrogen, progesterone, triamcinolon acetate, dexamethasone, etc., genes, polypeptides, oligonucleotides, nucleotides, antibodies, drugs such as anticancer agents, anti-inflammatory agents, antifungal agents, antibiotics, anesthetics, antihypertensive agents, and agents for the treatment of diabetes, antihyperlipidemic agents, antiviral agents, agents for the treatment of Parkinson's disease, antidementia agents, antiemetics, immunosuppressants, antiulcerative agents, laxatives, antimalarial agents, and diagnostic imaging agents. Examples of anticancer drugs include paclitaxel, epirubicin, dactinomycin, bleomycin, mitomycin, docetaxel, 5-fluorouracil, methotrexate, camptothecin, etoposide, doxorubicin, dausorubicin, idarubicin, ara-C, cyclosporine A, etc., and derivatives thereof.
The above bioactive agent may be added to the polymeric composition in a weight-by-weight ratio of 0.1˜20:80.0˜99.9 to be appropriately contained in the core of the micelles formed from the amphiphilic block copolymer and the polylactic acid derivative.
The amphiphilic block copolymer of the present invention is preferably an A-B type diblock copolymer or B-A-B type triblock copolymer comprising a hydrophilic A block and a hydrophobic B block. The amphiphilic block copolymer, when placed in an aqueous phase, forms core-shell type polymeric micelles wherein the hydrophobic B block forms the core and the hydrophilic A block forms the shell. Preferably, the hydrophilic A block is a member selected from the group consisting of polyalkylene glycol, polyvinyl alcohol, polyvinyl pyrrolidone, polyacryl amide and derivatives thereof. More preferably, the hydrophilic A block is a member selected from the group consisting of monomethoxypolyethylene glycol, monoacetoxypolyethylene glycol, polyethylene glycol, polyethylene-co-propylene glycol, and polyvinyl pyrrolidone. Preferably, the hydrophilic A block has a number average molecular weight of 500 to 50,000 Daltons. More preferably, the hydrophilic A block has a number average molecular weight of 1,000 to 20,000 Daltons.
The hydrophobic B block of the amphiphilic block copolymer of the present invention is a highly biocompatible and biodegradable polymer selected from the group consisting of polyesters, polyanhydrides, polyamino acids, polyorthoesters and polyphosphazine. More preferably, the hydrophobic B block is one or more selected from the group consisting of polylactides, polyglycolides, polycaprolactone, polydioxan-2-one, polylactic-co-glycolide, polylactic-co-dioxan-2-one, polylactic-co-caprolactone, and polyglycolic-co-caprolactone. The terminal group of the hydrophobic block has a hydroxyl group, and the hydroxyl terminal group of the hydrophobic B block is substituted with a hydrophobic tocopherol or cholesterol group, both having excellent hydrophobicity, with the aim of increasing the hydrophobicity of the hydrophobic B block while maintaining its molecular weight. Tocopherol or cholesterol group is chemically bound to the hydroxyl terminal group of the hydrophobic B block using a linkage agent, e.g. a dicarboxylic acid such as succinic acid, malonic acid, glutaric acid, adipic acid. Tocopherol and cholesterol are biocompatible and hydrophobic compounds having a ring structure, which can increase the interior hydrophobicity of the polymeric micelles thereby enhancing the physical stability of the polymeric micelles. Preferably, the hydrophobic B block of the amphiphilic block copolymer has a number average molecular weight of 500 to 50,000 Daltons. More preferably, the hydrophobic B block of the amphiphilic block copolymer has a number average molecular weight 1,000 to 20,000 Daltons.
The ratio of the hydrophilic A block to the hydrophobic B block of the amphiphilic block copolymer of the present invention is preferably within the range of 3:7 to 8:2 by weight, and more preferably within the range of 4:6 to 7:3. If the content of the hydrophilic A block is too low, the polymer may not form polymeric micelles in an aqueous solution, and if the content is too high, the polymeric micelles formed are not stable.
In one embodiment, the amphiphilic block copolymer of the present invention may be represented by the following Formula:
R1′—O—[R3′]1′—[R4′]m′—[R5′]n′—C(═O)—(CH2)x′—C(═O)—O—R2′ (I′)
wherein R1′ is CH3—, H—[R5′]n′—[R4′]m′—, or R2′—O—C(═O)—(CH2)x′—C(═O)—[R5′]n′—[R4′]m′—;
R2′ is tocopherol or cholesterol;
R3′ is —CH2CH2—O—, —CH(OH)—CH2—, —CH(C(═O)—NH2)—CH2—, or
R4′ is —C(═O)—CHZ′-O—, wherein Z′ is a hydrogen atom or methyl group;
R5′ is —C(═O)—CHY″—O—, wherein Y″ is a hydrogen atom or methyl group, —C(═O)—CH2CH2CH2CH2CH2—O—, or —C(═O)—CH2OCH2CH2—O—;
l′ is an integer from 4-1150;
m′ is an integer from 1-300;
n′ is an integer from 0-300; and
X′ is an integer from 0-4.
The block copolymer having the hydrophobic block whose hydroxyl terminal group is substituted with tocopherol or cholesterol can be prepared according to the following methods. In one embodiment, a suitable linker, e.g. a dicarboxylic acid such as succinic acid, malonic acid, glutaric acid or adipic acid, is introduced into the hydroxyl group of tocopherol or cholesterol, and the carboxylated tocopherol or cholesterol is chemically bound to the hydroxyl terminal group of the hydrophobic B block.
In one embodiment, according to the method of U.S. Pat. No. 6,322,805, the amphiphilic block copolymer (mPEG-PLA) comprised of monomethoxypolyethylene glycol (mPEG; Mn=2,000) and polylactide (PLA; Mn=1,750) is weighed, and dehydrated using a vacuum pump at 120° C., and then dissolved in acetonitrile or methylene chloride. Thereto is added tocopherol succinate or cholesterol succinate, and dicyclohexylcarbodiimide (DCC) and 4-dimethylaminopyridine (DMAP) are weighed and added thereto as an initiator and a catalyst, respectively, and the reaction is performed at room temperature. The reactant becomes opaque due to dicyclohexylurea (DCU) formed in the reaction between the terminal —OH of mPEG-PLA and —COOH of the hydrophobic compound. After 24 hours, DCU is removed by using a glass filter, and DMAP is extracted and removed with a hydrochloric acid aqueous solution. To this purified product solution is added MgSO4 to remove any residual moisture, and then, precipitates are formed in a hexane/diethyl ether solvent in order to obtain the amphiphilic block copolymer to which tocopherol succinyl or cholesterol succinyl is bound, mPEG-PLA-tocopherol or mPEG-PLA-cholesterol (in which tocopherol or cholesterol is bound to PLA via succinic acid diester). The precipitated polymeric product is filtered, and then dried under vacuum to obtain the polymer as white particles.
In another embodiment, a carboxylated hydrophobic compound is activated with oxalyl chloride without any catalyst, and bound to the end of mPEG-PLA. That is, tocopherol (or cholesterol) succinate is reacted with oxalyl chloride, and then, excessive oxalyl chloride is removed under vacuum at room temperature. The mPEG-PLA is weighed and added thereto, and the reaction is performed at 100° C. for 12 hours to obtain mPEG-PLA-tocopherol (or cholesterol). The synthesized polymer is dissolved in acetonitrile or methylene chloride, precipitated in hexane/diethyl ether, and filtered.
In the above two preparation processes, tocopherol (or cholesterol) malonate, tocopherol (or cholesterol) glutarate, or tocopherol (or cholesterol) adipate, etc. can be used instead of tocopherol (or cholesterol) succinate.
In another embodiment, tocopherol or cholesterol is bound to the end of mPEG-PLA by using a dichloride compound as a linkage agent. Specifically, tocopherol or cholesterol is weighed and dehydrated by using a vacuum pump at 50° C. Excessive linkage agent is added thereto, and the reaction is performed for 12 hours. After the reaction is completed, the excessively added linkage agent is removed under vacuum at 100° C. Thereto is added weighed mPEG-PLA, and the reaction is performed at 100° C. for 12 hours. The synthesized polymer is dissolved in methylene chloride, and precipitated in hexane/diethyl ether in order to obtain the amphiphilic block copolymer in which tocopherol or cholesterol is bound to PLA via succinic acid diester, i.e. mPEG-PLA-tocopherol or mPEG-PLA-cholesterol. The precipitated polymeric product is filtered, and dried under vacuum to obtain the polymer as white particles. The linkage agent which can be used in the reaction may be selected from such dichloride compounds as succinyl chloride, oxalyl chloride, malonyl chloride, glutaryl chloride, adipoyl chloride, etc.
One or more ends of the polylactic acid derivative of the present invention are covalently bound to at least one carboxylic acid or carboxylate salt. The other end of the polylactic acid derivative of the present invention may be covalently bound to a functional group selected from the group consisting of hydroxyl, acetoxy, benzoyloxy, decanoyloxy and palmitoyloxy groups. The carboxylic acid or carboxylate salts function as a hydrophilic group in an aqueous solution of pH 4 or higher which enables the polylactic acid derivative to form polymeric micelles therein. When the polylactic acid derivatives of the present invention are dissolved in an aqueous solution, the hydrophilic and hydrophobic components present in the polylactic acid derivative should be balanced in order to form polymeric micelles. Therefore, the number average molecular weight of the polylactic acid derivative of the present invention is preferably within the range of 500 to 2,500 Daltons. The molecular weight of the polylactic acid derivative can be adjusted by controlling the reaction temperature, time, and the like, during the preparation process.
The polylactic acid derivative is preferably represented by the following formula:
RO—CHZ-[A]n-[B]m—COOM (I)
wherein A is —COO—CHZ-; B is —COO—CHY—, —COO—CH2CH2CH2CH2CH2— or —COO—CH2CH2OCH2; R is a hydrogen atom, acetyl, benzoyl, decanoyl, palmitoyl, methyl or ethyl group; Z and Y each are a hydrogen atom, methyl, or phenyl group; M is H, Na, K, or Li; n is an integer from 1 to 30, and m is an integer from 0 to 20.
One end of the polylactic acid derivative of the present invention is covalently bound to a carboxyl group or an alkali metal salt thereof, preferably, an alkali metal salt thereof. The metal ion in the alkali metal salt which forms the polylactic acid derivative is monovalent, e.g. sodium, potassium or lithium. The polylactic acid derivative in the metal ion salt form is a solid at room temperature, and is very stable because of its relatively neutral pH.
More preferably, the polylactic acid derivative is represented by the following formula:
RO—CHZ-[COO—CHX]p—[COO—CHY′]q—COO—CHZ-COOM (II)
wherein X is a methyl group; Y′ is a hydrogen atom or phenyl group; p is an integer from 0 to 25; q is an integer from 0 to 25, provided that p+q is an integer from 5 to 25; R, Z and M are the same as defined in Formula (I).
In addition, polylactic acid derivatives of the following formulas (III), (IV) and (V) are also suitable for the
RO—PAD-COO—W— (III)
wherein W-M′ is
the PAD is a member selected from the group consisting of D,L-polylactic acid, D-polylactic acid, polymandelic acid, a copolymer of D,L-lactic acid and glycolic acid, a copolymer of D,L-lactic acid and mandelic acid, a copolymer of D,L-Lactic acid and caprolactone, and a copolymer of D,L-lactic acid and 1,4-dioxan-2-one; R and M are the same as defined in Formula (I).
S—O—PAD-CC (IV)
wherein S is
L is —NR1— or —O—; R1 is a hydrogen atom or C1-10alkyl; Q is CH3, CH2CH3, CH2CH2CH3, CH2CH2CH2CH3, or CH2C6H5; a is an integer from 0 to 4; b is an integer from 1 to 10; R and M are the same as defined in Formula (I); and PAD is the same as defined in Formula (III).
wherein R′ is —PAD-O—C(O)—CH2CH2—C(O)—OM and M is the same as defined in formula (I); PAD is the same as defined in Formula (III); a is an integer from 1 to 4 (when a=1, it is a 3-arm PLA-COONa; if a—2, it is a 4-arm PLA-COONa; when a=3, it is a 5-arm PLA-COONa, and if a=4, it is 6-arm PLA-COONa).
The initiator for the synthesis of the polymers (Formula V) includes glycerol, erythritol, threltol, pentaerytritol, xylitol, adonitol, sorbitol and mannitol.
The polymeric composition of the present invention may contain 0.1 to 99.9 wt % of the amphiphilic block copolymer and 0.1 to 99.9 wt % of the polylactic acid derivative based on the total weight of the amphiphilic block copolymer and the polylactic acid derivative. Preferably, the polymeric composition of the present invention contains 20 to 95 wt % of the amphiphilic block copolymer and 5 to 80 wt % of the polylactic acid derivative. More preferably, the polymeric composition of the present invention contains 50 to 90 wt % of the amphiphilic block copolymer and 10 to 50 wt % of the polylactic acid derivative.
Although the polylactic acid derivatives of the present invention alone can form micelles in an aqueous solution with a pH 4 or higher, the polymeric compositions comprising amphiphilic block copolymer and polylactic acid derivatives can form micelles in an aqueous solution irrespective of the pH of the solution, and the polymeric compositions of the present invention may be used at a pH within the range of 1 to 10, preferably at a pH within the range of 4 to 8. The particle size of the micelles or nanoparticles prepared from the polymeric compositions of the present invention may be adjusted to be within the range of 1 to 400 nm, and preferably from 5 to 200 nm, depending on the molecular weight of the polymers and the ratio of the polylactic acid derivative to the amphiphilic block copolymer.
In one embodiment of the present invention, the carboxyl terminal group of the polylactic acid derivative is bound or fixed with a di- or tri-valent metal ion. The metal ion-fixed polymeric composition can be prepared by adding the di- or tri-valent metal ion to the polymeric composition of the amphiphilic block copolymer and the polylactic acid derivative. The polymeric micelles or nanoparticles may be formed by changing the amount of the di- or tri-valent metal ion added for binding or fixing the carboxyl terminal group of the polylactic acid derivative.
The di- or tri-valent metal ion is preferably a member selected from the group consisting of Ca2+, Mg2+, Ba2+, Cr3+, Fe3+, Mn2+, Ni2+, Cu2+, Zn2+, and Al3+. The di- or tri-valent metal ion may be added to the polymeric composition of the amphiphilic block copolymer and the polylactic acid derivative in the form of a sulfate, chloride, carbonate, phosphate or hydroxylate, and preferably, in the form of CaCl2, MgCl2, ZnCl2, AlCl3, FeCl3, CaCO3, MgCO3, Ca3(PO4)2, Mg3(PO4)2, AlPO4, MgSO4, Ca(OH)2, Mg(OH)2, Al(OH)3, or Zn(OH)2.
Either polymeric micelles or nanoparticles can be prepared by changing the number of equivalents of the metal ion added. Specifically, if a divalent metal ion is added at 0.5 equivalents or less with respect to the carboxyl terminal groups, the metal ion that can form bonds with the carboxyl terminal group of the polylactic acid derivative is insufficient; and thus, polymeric micelles are formed. If a divalent metal ion is added at 0.5 equivalents or more, the metal ion that can form bonds with the carboxyl terminal group of the polylactic acid derivative is sufficient to firmly fix the micelles; and thus, nanoparticles are formed.
In addition, the drug release rate from the polymeric micelles or nanoparticles may be adjusted by changing the number of equivalents of the metal ion added. If the metal ion is present at 1 equivalent or less with respect to that of the carboxyl group of the polylactic acid derivative, the number available to bond to the carboxyl terminal group of the polylactic acid derivative is decreased, and so the drug release rate is increased. If the metal ion is present at 1 equivalent or more, the number available to bond to the carboxyl terminal group of the polylactic acid derivative is increased, and so the drug release rate is decreased. Therefore, to increase the drug release rate in the blood, the metal ion is used in a small equivalent amount, and to decrease the drug release rate, the metal ion is used in a large equivalent amount.
The metal ion-fixed polymeric compositions of the present invention may contain 5 to 95 wt % of the amphiphilic block copolymer, 5 to 95 wt % of the polylactic acid derivative and 0.01 to 10 equivalents of the di- or tri-valent metal ion with respect to the number of equivalents of the carboxyl terminal groups of the polylactic acid derivatives. Preferably, they contain 20 to 80 wt % of the amphiphilic block copolymer, 20 to 80 wt % of the polylactic acid derivative and 0.1 to 5 equivalents of the di- or tri-valent metal ion, and more preferably, 20 to 60 wt % of the amphiphilic block copolymer, 40 to 80 wt % of the polylactic acid derivative and 0.2 to 2 equivalents of the di- or tri-valent metal ion.
Mixing and Dissolving the Polymeric Composition and the Bioactive Agents in a Solvent and Evaporating the Solvent, and Formulation of a Solution of a Drug Carrier with a Bioactive Agent Entrapped Therein
The drug carrier of the present invention can be a polymeric micelle or a nanoparticle formed from polymeric compositions comprising an amphiphilic block copolymer which is comprised of a hydrophilic block and a hydrophobic block wherein said hydrophobic block has a terminal hydroxyl group that is substituted with a tocopherol or cholesterol group, and a polylactic acid derivative having at least one terminal carboxyl group at the end of the polymer.
The nanoparticles or micelles of the present invention can be formed from polymeric compositions of an amphiphilic block copolymer comprised of a hydrophilic block and a hydrophobic block, wherein the hydrophobic block has a hydroxyl terminal group which is substituted with a tocopherol or cholesterol group, a polylactic acid derivative having at least one terminal carboxyl group at the end which is bound or fixed with a di- or tri-valent metal ion.
The bioactive agents can be entrapped in the micelles or nanoparticles or they can be incorporated within the micelles or nanoparticles of the present invention by formation of a stable ionic complex with the carboxyl group of the biodegradable polylactic acid derivative according to the bioactive agents.
The amphiphilic block copolymer, the polylactic acid derivative, and the poorly water-soluble drug at certain ratios can be dissolved in one or more mixed organic solvents selected from the group consisting of acetone, ethanol, methanol, ethyl acetate, acetonitrile, methylene chloride, chloroform, acetic acid and dioxane. The organic solvent can be removed therefrom to prepare a homogenous mixture of the poorly water-soluble drug and the polymer. The homogenous mixture of the poorly water-soluble drug and the polymeric composition of the present invention can be added to an aqueous solution with a pH of 4 to 8, at 0 to 80° C., resulting in poorly water-soluble drug-containing mixed polymeric micelle aqueous solution. The above drug-containing polymeric micelle aqueous solution can then be lyophilized to prepare the polymeric micelle composition in the form of a solid.
An aqueous solution containing 0.001 to 2 M of the di- or tri-valent metal ion is added to the poorly water-soluble drug-containing mixed polymeric micelle aqueous solution. The mixture is slowly stirred at room temperature for 0.1 to 1 hour and then lyophilized to prepare the metal ion-fixed polymeric micelle or nanoparticle composition in the form of a solid.
Contacting the Drug Carrier with a Cell
For oral or parenteral administration of a bioactive agent, the bioactive agent is entrapped in the drug carrier and is thereby solubilized. Particularly, the metal ion-fixed polymeric micelles or nanoparticles are retained in the bloodstream for a long period of time and accumulate in the target lesions. The bioactive agent is released from the hydrophobic core of the micelles to exert a pharmacological effect while the micelles are degraded.
For parenteral delivery, the polymeric composition may be administered intravenously, intramuscularly, intraperitoneally, transnasally, intrarectally, intraocularly, or intrapulmonarily. For oral delivery, the bioactive agent is mixed with the drug carrier of the present invention, and then administered in the form of a tablet, capsule, or aqueous solution. The polymeric composition of the invention may be administered with various ranges according to the requirements of the particular drug. As is well known in the medical arts, dosages for any one patient depends upon many factors, including the patient's weight, body surface area, age, the particular compound to be administered, sex, time and route of administration general health, and other drugs being administered concurrently.
Cellular internalization of a bioactive agent can be studied with flow cytometry and confocal microscopy using drug-containing compositions. As an example of the present invention, human uterine cancer cell lines (MES-SA; MES-SA/Dx-5) and human breast cancer cell lines (MCF-7; MCF-7/ADR) were treated with the drug compositions of the present invention. Cell lines MES-SA and MCF-7 are doxorubicin-sensitive and cell lines MES-SA/Dx-5; MCF-7/ADR are doxorubicin-resistant.
As shown in
The confocal images in
Furthermore, the MTT assay results shown in
From the physical stability of the drug carrier of the present invention and the results of the cellular internalization study, it can be concluded that most of the bioactive agent-containing compositions of the present invention enter the cell cytoplasm in the form of a micelle or nanoparticle by endocytosis without collapse of its structure. This cellular internalization process is schematically shown in
A pharmacokinetic experiment was performed with Sprague-Dawley rats (200˜250 g) using doxorubicin-containing compositions of the present invention (Compositions 1 to 5) and the conventional doxorubicin formulation (Free-Dox). As shown in
The drug carriers of the present invention can provide for a prolonged systemic circulation time due to their small size (<100 nm), their hydrophilic shell which minimizes uptake by the MPS, and their high molecular weight which prevents renal excretion. The drug carriers of the present invention can be used as carriers for water-soluble drugs, peptides and proteins as well as for poorly water-soluble drugs. As illustrated by the cellular internalization study, the bioactive agent-containing compositions of the present invention form such stable micelles or nanoparticles in aqueous media that they enter the cytoplasm in the form of micelles or nanoparticles by endocytosis without collapse of their structure. Furthermore, higher accumulation of a bioactive agent in tumor tissue can be achieved with the composition of the present invention.
The following examples will enable those skilled in the art to more clearly understand how to practice the present invention. It is to be understood that while the invention has been described in conjunction with the preferred specific embodiments thereof, that which follows is intended to illustrate and not limit the scope of the invention. Other aspects of the invention will be apparent to those skilled in the art to which the invention pertains.
A mixture of 20 g of monomethoxy polyethyleneglycol (mPEG with a molecular weight of 2,000), 20 g of D,L-lactide which was recrystallized from ethyl acetate, and 0.2 g of stannous octoate which was dissolved in 5 ml toluene were added to a reactor equipped with a mechanical stirrer and a distillation set. Residual toluene was evaporated at 120° C. The reaction was carried out under vacuum (25 mmHg). After 6 hours of polymerization occurring, the resulting polymer was dissolved in dichloromethane and poured into cold diethyl ether (4° C.) to precipitate the polymer. The precipitated polymer was washed twice with diethyl ether and dried under vacuum (0.1 mmHg) for 24 hours. The molecular weight of the block copolymer determined by nuclear magnetic resonance (NMR) spectroscopy was 2,000-1,800 (2,000 for PEG block and 1,800 for PLA block).
A diblock copolymer (mPEG-PLGA, LA:GA=70:30 by weight) was prepared by the same procedure described in Preparation Example 1, using 14 g of D,L-lactide and 6 g of glycolide instead of 20 g of D,L-lactide. The molecular weight of the block copolymer determined by NMR was 2,000-1,750 (2,000 for the PEG block and 1,750 for the PLGA block).
A diblock copolymer (mPEG-PCL) was prepared by the same procedure described in Preparation Example 1, using 20 g of ε-caprolactone instead of D,L-lactide. The molecular weight of the block copolymer determined by NMR was 2,000-1,800 (2,000 for the PEG block and 1,800 for the PCL block).
A triblock copolymer (PLA-PEO-PLA) was prepared by the same procedure described in Preparation Example 1, using 20 g of polyethyleneglycol (PEG with a molecular weight of 2,000) instead of monomethoxy polyethyleneglycol (mPEG with a molecular weight of 2,000). The molecular weight of the block copolymer determined by NMR was 850-2,000-850 (2,000 for the PEO block and 900 for each PLA block).
A mixture of 8.6 g of tocopherol, 2.4 g of succinic anhydride and 2.9 g of 4-(dimethylamino) pyridine (DMAP) were dissolved in 100 ml of 1,4-dioxane in a reactor equipped with a mechanical stirrer. The reaction was carried out at room temperature. After 24 hours of stirring, the reaction mixture was introduced into an HCl solution to precipitate the tocopherol succinate (10.2 g; yield=96%).
Cholesteryl succinate was prepared (9.1 g; yield=94%) by the same procedure described in Preparation Example 5, using 7.7 g of cholesterol instead of tocopherol.
A mixture of 10.0 g (2.6 mmole) of mPEG-PLA prepared from Preparation Example 1 and 1.7 g (3.2 mmole) of tocopherol succinate prepared from Preparation Example 5 were dissolved in 50 ml of acetonitrile in a reactor equipped with a mechanical stirrer. 0.78 g (3.8 mmole) of dicyclohexylcarbodiimide (DCC) and 0.046 g (0.38 mmole) of 4-(dimethylamino)pyridine (DMAP) were used as catalysts. After stirring for 24 hours at room temperature, the mixture was filtered using a glass filter to remove dicyclohexylcarbourea. The remaining catalysts were extracted out with an aqueous HCl solution, and magnesium sulfate was added into the polymer solution to remove water. The resulting product (mPEG-PLA-Toco) was recrytallized from a cosolvent of n-hexane/diethyl ether (6/4, v/v). The recrytallized product was filtered and dried under vacuum to give a white powdered product (9.9 g; yield=87%).
An amphiphilic block copolymer (mPEG-PLGA-Toco) was prepared (9.5 g; yield=83%) by the same procedure described in Preparation Example 7, using 9.8 g (2.6 mmole) of mPEG-PLGA prepared from preparation example 2 instead of mPEG-PLA prepared from Preparation Example 1.
An amphiphilic block copolymer (mPEG-PCL-Toco) was prepared (10.1 g; yield 89%) by the same procedure described in Preparation example 7, using 10.0 g (2.6 mmole) of mPEG-PCL prepared from preparation example 3 instead of mPEG-PLA prepared from Preparation Example 1.
An amphiphilic block copolymer (Toco-PLA-PEO-PLA-Toco) was prepared (9.2 g; yield=84%) by the same procedure described in Preparation Example 7, using 9.6 g (2.6 mmole) of PLA-PEO-PLA prepared from Preparation Example 4 instead of mPEG-PLA prepared from Preparation Example 1.
An amphiphilic block copolymer (mPEG-PLA-Chol) was prepared (9.7 g; yield=86%) by the same procedure described in Preparation Example 7, using 1.6 g (3.2 mmole) of cholesteryl succinate) prepared from Preparation Example 6 instead of tocopherol succinate prepared from Preparation Example 5.
A mixture of 7.5 g of D,L-lactic acid (0.083 mole) and 2.5 g of D,L-mandelic acid (0.016 mole) were added to a reactor equipped with a mechanical stirrer and a distillation set. Moisture was evaporated at 80° C. for 1 hour under reduced pressure (25 mmHg) with an aspirator. The reaction was carried out at an elevated temperature of 180° C. for 5 hours under vacuum (10 mmHg). The resulting product was added to distilled water, the precipitated polymer was further washed with distilled water. The polymer product was then added to 0.1 liter of distilled water, and the pH of the aqueous solution was adjusted between 6 and 8 by the addition of sodium hydrogen carbonate portionwise thereto dissolving the polymer. The water-insoluble polymer was separated and removed by centrifugation or filtration. A 1 N hydrochloric acid solution was added dropwise thereto and the polymer was precipitated in the aqueous solution. The precipitated polymer was washed twice with distilled water, isolated and dried under reduced pressure to obtain a polymer having a carboxyl end group (6.7 g of PLMA-COOH, yield=67%). The number average molecular weight of the polymer determined by NMR was 1,100.
A solution of 5 g of PLMA-COOH polymer was dissolved in acetone in a reactor equipped with a mechanical stirrer and a distillation set. The solution was stirred slowly at room temperature, and sodium hydrogen carbonate solution (1 N) was slowly added thereto to reach a pH of 7. Anhydrous magnesium sulfate was added thereto to remove any residual moisture. The mixture was filtered, remaining acetone was evaporated with a rotary evaporator, and a white solid product was obtained therefrom. The solid product was dissolved again in anhydrous acetone, the solution was filtered to remove insoluble particles, the acetone was evaporated off to give the final product, PLMA-COONa, as a white solid (yield: 95%).
(1) Preparation of 3arm-PLA-OH
1.0 g (0.011 mole) of glycerol was added to a reactor equipped with a mechanical stirrer and a distillation set. Moisture was evaporated at 80° C. for 30 minutes. 0.036 g (0.089 mmole) of stannous octoate in toluene was added thereto, the residual toluene was evaporated at 120° C., and 36 g (0.25 mole) of D,L-lactide which was recrystallized from ethyl acetate was introduced into the reactor. The reaction was carried out at 130° C. under vacuum (20 mmHg). After 6 hours of polymerization, the resulting polymer was dissolved in acetone and an aqueous NaHCO3 solution (0.2 N) was added dropwise thereto to precipitate the polymer. The precipitated polymer was washed three times with distilled water and dried under reduced pressure to give a white powder form of the polymer (3arm-PLA-OH). The molecular weight of the polymer determined by NMR spectroscopy was 3,050.
(2) Preparation of 3arm-PLA-COOH
10 g (3.28 mmole) of 3arm-PLA-OH polymer prepared above was added to a reactor equipped with a mechanical stirrer and a distillation set. Moisture was evaporated at 120° C. for 1 hour. 1.96 g (19.6 mmole) of succinic anhydride was added thereto, and the reaction was carried out at 125° C. for 6 hours. The resulting polymer was dissolved in acetone and distilled water was added dropwise thereto to precipitate the polymer. The precipitated polymer was dissolved in an aqueous NaHCO3 solution (0.2 N) at 60° C., and aqueous HCl solution (1N) was added dropwise thereto to precipitate the polymer. The precipitated polymer was washed three times with distilled water and dried under vacuum to give a white powder form of the polymer (3arm-PLA-COOH). The molecular weight of the polymer determined by NMR spectroscopy was 3,200.
(3) Preparation of 3arm-PLA-COOK
Finally, a biodegradable polyester (3arm-PLA-COOK) was prepared (yield=90%) by the same procedure described in Preparation Example 12, using 5 g of the 3arm-PLA-COOH polymer prepared above and a potassium hydrogen carbonate solution (1 N) instead of the PLMA-COOH polymer and sodium hydrogen carbonate solution (1 N).
(1) Preparation of 4arm-PLA-OH
A 4arm-PLA-OH polymer was prepared by the same procedure described in Preparation Example 13, using 1.5 g (0.011 mole) of pentaerythritol instead of glycerol. The molecular weight of the polymer (4arm-PLA-OH) determined by NMR spectroscopy was 3,100.
(2) Preparation of 4arm-PLA-COOH
A 4arm-PLA-COOH polymer was prepared by the same procedure described in Preparation Example 13, using 10 g (3.23 mmole) of the 4arm-PLA-OH polymer prepared above and 2.58 g (25.8 mmole) of succinic anhydride instead of 10 g (3.28 mmole) of the 3arm-PLA-OH polymer and 1.96 g (19.6 mmole) of succinic anhydride. The molecular weight of the polymer (4arm-PLA-COOH) determined by NMR spectroscopy was 3,300.
(3) Preparation of 4arm-PLA-COONa
Finally, a biodegradable polyester (4arm-PLA-COONa) was prepared (yield 92%) by the same procedure described in Preparation Example 12, using 5 g of the 4arm-PLA-COOH polymer prepared above instead of the PLMA-COOH polymer.
A PLA-COOH was prepared (yield=78%) by the same procedure described in Preparation Example 12, using 10 g of D,L-lactic acid (0.11 mmole). The number average molecular weight of the polymer determined by NMR was 1,100.
A biodegradable polyester (PLA-COONa) was prepared (yield=92%) by the same procedure described in Preparation Example 12, using 5 g of the PLA-COOH polymer prepared above instead of the PLMA-COOH polymer.
10 mg of doxorubicin hydrochloride was dissolved in 5 ml of ethanol-water (9:1 v/v) in a round-bottomed flask. 810 mg of the amphiphilic block copolymer prepared from preparation example 7 (mPEG-PLA-Toco) and 180 mg of the biodegradable polyester prepared from Preparation Example 12 (PLMA-COONa) are added thereto and completely dissolved giving clear solution. The solvent was evaporated at an elevated temperature (60° C.) under vacuum with a rotary evaporator. A 3 ml aqueous solution of lactose (20% by weight) was added and the flask was rotated at 100 rpm at 60° C. with a rotary evaporator to form micelles or nanoparticles in the aqueous medium. The solution was filtered using 0.22 μm PVDF membrane filter. The filtered solution was freeze-dried and stored in a refrigerator until use. Particle size of the micelles or nanoparticles in the filtered solution was measured by a dynamic light scattering method (DLS, ZetaPlus, Brookhaven Instruments Ltd.). The loading efficiency (wt. % of drug incorporated in the micelles or nanoparticles with respect to the initial drug used) was calculated from the doxorubicin content analyzed by HPLC using daunorubicin as the internal standard. The conditions for HPLC assay were as follows:
The results are summarized in Table 1.
A drug-containing composition (composition 2) was prepared by the same procedure described in Example 1, using mPEG-PLGA-Toco prepared from Preparation Example 8 instead of mPEG-PLA-Toco.
The results are summarized in Table 1.
A drug-containing composition (composition 3) was prepared by the same procedure described in Example 1, using mPEG-PCL-Toco prepared from Preparation Example 9 and 3arm-PLA-COOK prepared from Preparation Example 13 instead of mPEG-PLA-Toco and PLMA-COONa.
The results are summarized in Table 1.
A drug-containing composition (composition 4) was prepared by the same procedure described in Example 1, using Toco-PLA-PEO-PLA-Toco prepared from preparation example 10 and 4arm-PLA-COONa prepared from Preparation Example 14 instead of mPEG-PLA-Toco and PLMA-COONa.
The results are summarized in Table 1.
A drug-containing composition (composition 5) was prepared by the same procedure described in Example 1, using mPEG-PLA-Chol prepared from preparation Example 11 instead of mPEG-PLA-Toco.
A drug-containing composition (composition 6) was prepared by the same procedure described in Example 1, using epirubicin instead of doxorubicin.
The results are summarized in Table 1.
A mixture of 248.1 mg PLA-COONa prepared from Preparation Example 15, 7.5 mg of paclitaxel, and 744.3 mg of mPEG-PLA-Toco prepared from Preparation Example 7 were completely dissolved in 5 ml of ethanol to obtain a clear solution. Ethanol was removed therefrom to prepare a paclitaxel-containing polymeric composition. Distilled water (6.2 ml) was added thereto and the mixture was stirred for 30 minutes at 60° C. to prepare the paclitaxel-containing aqueous solution.
(2) Fixation with the Divalent Metal Ion
0.121 ml (0.109 mmol) of a 0.9 M aqueous solution of anhydrous calcium chloride was added to the paclitaxel-containing aqueous solution prepared above, and the mixture was stirred for 20 minutes at room temperature. The mixture was filtered using 0.22 μm PVDF membrane filter. The filtered solution was freeze-dried and stored in a refrigerator until use.
The results are summarized in Table 1.
A Mg2+-fixed paclitaxel-containing composition was prepared by the same procedure described in Example 7 except that 248.1 mg of PLMA-COONa (Mn: 1,096) of Preparation Example 12, 7.5 mg of paclitaxel, 744.3 mg of mPEG-PLGA-Toco of preparation Example 8 and 0.230 ml (0.113 mmol) of a 0.5M aqueous solution of magnesium chloride 6 hydrate (Mw: 203.31) were used.
The results are summarized in Table 1.
A Cg2+-fixed paclitaxel-containing composition was prepared by the same procedure described in Example 7 except that 248.1 mg of PLMA-COONa of Preparation Example 12, 7.5 mg of paclitaxel, 744.4 mg of mPEG-PLA-Toco of Preparation Example 7 and 0.230 ml (0.113 mmol) of a 0.9 M aqueous solution of anhydrous calcium chloride were used.
The results are summarized in Table 1.
A Ca2+-fixed paclitaxel-containing composition was prepared by the same procedure described in Example 7 except that 248.1 mg of PLMA-COONa of Preparation Example 12, 7.5 mg of paclitaxel, 744.4 mg of mPEG-PLA-Chol of Preparation Example 11 and 0.230 ml (0.113 mmol) of a 0.9 M aqueous solution of anhydrous calcium chloride were used.
The results are summarized in Table 1.
To evaluate the intracellular uptake of a bioactive agent, the doxorubicin-containing composition of the present invention (Composition 1 in example 1) and the conventional doxorubicin formulation (aqueous solution of doxorubicin hydrochloride, Free-Dox) were tested on the human uterine cancer cell lines, MES-SA (doxorubicin-sensitive cell line) and MES-SA/Dx-5 (doxorubicin-resistant cell line).
The flow cytometry study was performed with the FACStarPlus (Becton Dickinson) according to the method of Walker et al. (Experimental Cell Research 207: 142 (1993)). Briefly, cells (1.0×106) were incubated in McCoy's 5A medium (Invitrogen Corp.) supplemented with 10% fetal bovine serum and 1% penicillin streptomycin. After a 24-hour incubation period, the cells were treated with the drug composition at a dose of 1.0 μg/ml. Cells in 12×75 Falcon tubes were placed on the FACStarPlus and the fluorescence was observed at a wavelength of 488 nm (excitation) and 519 nm (emission). Data were analyzed by CellQuest software and the results are shown in
As shown in
To visualize the intracellular uptake of a bioactive agent, the doxorubicin-containing composition of the present invention (Composition 1 in Example 1) and the conventional doxorubicin formulation (aqueous solution of doxorubicin hydrochloride, Free-Dox) were tested on the human uterine cancer cell lines, MES-SA (doxorubicin-sensitive cell line) and MES-SA/Dx-5 (doxorubicin-resistant cell line).
The cells were imaged on a Zeiss (Thornwood, N.Y.) LSM 510 confocal imaging system with an inverted fluorescence microscope and an image analyzer. Briefly, cells (3×105) in 3 ml of McCoy's 5A medium (Invitrogen Corp.) supplemented with 10% fetal bovine serum and 1% penicillin streptomycin were incubated overnight on a glass coverslip at 37° C. After incubation, cells were treated with the drug composition at a dose of 1.0 μg/ml, and the coverslip was mounted on the microscope. At given time intervals, the fluorescence was observed at an excitation wavelength of 484 nm, and the results are shown in
The confocal images in
To visualize the intracellular uptake of a drug, an epirubicin-containing composition of the present invention (Composition 6 in Example 6) and the conventional epirubicin formulation (aqueous solution of epirubicin hydrochloride) were tested on the human breast cancer cell lines, MCF-7 (epirubicin-sensitive cell line) and MCF-7/ADR (epirubicin-resistant cell line).
The confocal images were obtained by the same procedure described in example 12A, using RPMI medium (Invitrogen Corp.) instead of McCoy's 5A medium, and the results are shown in
The confocal images in
For the in vitro cytotoxicity test of the composition of the present invention, the doxorubicin-containing composition of the present invention (Composition 1 in Example 1, Doxo-PNP) and the conventional doxorubicin formulation (aqueous solution of doxorubicin hydrochloride, Free-Dox) were tested on the human uterine cancer cell lines, MES-SA (doxorubicin-sensitive cell line) and MES-SA/Dx-5 (doxorubicin-resistant cell line). MTT assay is well established method for cytotoxicity test. When the cells are treated with MTT (methylthiazoletetrazolium), the MTT-formazan is produced from reduction of MTT-tetrazolium by enzymes present in living cells only (dead cells cannot reduce the MTT-tetrazolium to MTT-formazan). The fluorescence of the MTT-formazan is detected by a fluorescence reader and the optical density correlates with the number of cells. This procedure is automatized, and the cell viability and IC50 (50% inhibitory concentration of cell growth) values are calculated by the software installed in the microplate reader.
The cytotoxic activity of each composition was evaluated in both human tumor cell lines at five ten-fold dilutions ranging from 0.01 to 100 μg/ml. Following continuous exposure for 3 days, the cells were treated with MTT (methylthiazoletetrazolium). The MTT-formazan produced from reduction of MTT-tetrazolium by enzymes present in the living cells was detected by a fluorescence reader. The optical density correlates with the number of cells. The results of two independent experiments were expressed as IC50 (50% inhibitory concentration) values of each cell line. The MTT assay was performed essentially according to the method of Carmichael et al. (Cancer Research 47: 936 (1987)). Briefly, cells were harvested from an exponential phase culture growing in McCoy's 5A medium (Invitrogen Corp.) supplemented with 10% fetal bovine serum and 1% penicillin streptomycin, counted and plated in 96 well flat-bottomed microtiter plates (100 cell suspension, 5×104 cells/ml for each cell line). After a 24 h recovery to allow the cells to resume exponential growth, a culture medium (24 control wells per plate) or culture medium containing drug was added to the wells. Each drug concentration was plated in triplicate. Following 3 days of continuous drug exposure, the cells were treated with 25 μl of a MTT solution in sterile water (2 mg/ml). Fluorescence was measured using an automatic microplate reader (SpectraMax 190, Molecular Devices) at a wavelength of 549 nm, and the number of viable cells was calculated from the optical density.
The results of the cell viability study are shown in
The cytotoxic activity on the doxorubicin-sensitive cells was similar in both compositions as shown in
The drug concentrations in blood plasma were measured after intravenous administration of the doxorubicin-containing compositions in the present invention (Compositions 1 to 5 in examples 1 to 5) and the conventional doxorubicin formulation (aqueous solution of doxorubicin hydrochloride, Free-Dox) in 7- to 8-week old Sprague-Dawley rats (200˜250 g).
The rats (5 rats for each formulation) were injected intravenously through the tail vein at a dose of 5 mg/kg. The blood samples were collected from the tail vein at 1, 5, 15, 30 minutes and 1, 2, 4, 8, and 24 hours after the drug injection. The blood samples were immediately centrifuged, and the plasma was separated. The plasma samples were stored at −50° C. until analysis. Doxorubicin was analyzed by HPLC assay described in example 1. The blood concentration-time curve (C-t curve) is shown in
It is to be understood that the above-referenced arrangements are only illustrative of application of the principles of the present invention. Numerous modifications and alternative arrangements can be devised without departing from the spirit and scope of the present invention. While the present invention has been shown in the drawings and is fully described above with particularity and detail in connection with what is presently deemed to be the most practical and preferred embodiment(s) of the invention, it will be apparent to those of ordinary skill in the art that numerous modifications can be made without departing from the principles and concepts of the invention as set forth herein.
This application claims priority to and the benefit of U.S. Patent Application No. 60/568,945 in the United States Patent and Trademark Office on May 6, 2004, the entire content of which is incorporated hereinto by reference.
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/KR2005/001330 | 5/6/2005 | WO | 00 | 10/25/2006 |
| Number | Date | Country | |
|---|---|---|---|
| 60568945 | May 2004 | US |
