WO1994022429A1 - Procede de traitement d'une tumeur solide - Google Patents

Procede de traitement d'une tumeur solide Download PDF

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Publication number
WO1994022429A1
WO1994022429A1 PCT/US1994/003457 US9403457W WO9422429A1 WO 1994022429 A1 WO1994022429 A1 WO 1994022429A1 US 9403457 W US9403457 W US 9403457W WO 9422429 A1 WO9422429 A1 WO 9422429A1
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liposomes
tumor
liposome
antibody
peg
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PCT/US1994/003457
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English (en)
Inventor
Theresa M. Allen
Francis J. Martin
Martin C. Woodle
Samuel Zalipsky
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Liposome Technology, Inc.
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Priority to AU65272/94A priority Critical patent/AU6527294A/en
Publication of WO1994022429A1 publication Critical patent/WO1994022429A1/fr

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    • C—CHEMISTRY; METALLURGY
    • C07—ORGANIC CHEMISTRY
    • C07F—ACYCLIC, CARBOCYCLIC OR HETEROCYCLIC COMPOUNDS CONTAINING ELEMENTS OTHER THAN CARBON, HYDROGEN, HALOGEN, OXYGEN, NITROGEN, SULFUR, SELENIUM OR TELLURIUM
    • C07F9/00—Compounds containing elements of Groups 5 or 15 of the Periodic Table
    • C07F9/02—Phosphorus compounds
    • C07F9/547—Heterocyclic compounds, e.g. containing phosphorus as a ring hetero atom
    • C07F9/553—Heterocyclic compounds, e.g. containing phosphorus as a ring hetero atom having one nitrogen atom as the only ring hetero atom
    • C07F9/5537—Heterocyclic compounds, e.g. containing phosphorus as a ring hetero atom having one nitrogen atom as the only ring hetero atom the heteroring containing the structure -C(=O)-N-C(=O)- (both carbon atoms belong to the heteroring)
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
    • A61K47/50—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates
    • A61K47/69—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the conjugate being characterised by physical or galenical forms, e.g. emulsion, particle, inclusion complex, stent or kit
    • A61K47/6905—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the conjugate being characterised by physical or galenical forms, e.g. emulsion, particle, inclusion complex, stent or kit the form being a colloid or an emulsion
    • A61K47/6911—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the conjugate being characterised by physical or galenical forms, e.g. emulsion, particle, inclusion complex, stent or kit the form being a colloid or an emulsion the form being a liposome
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
    • A61K47/50—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates
    • A61K47/69—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the conjugate being characterised by physical or galenical forms, e.g. emulsion, particle, inclusion complex, stent or kit
    • A61K47/6905—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the conjugate being characterised by physical or galenical forms, e.g. emulsion, particle, inclusion complex, stent or kit the form being a colloid or an emulsion
    • A61K47/6911—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the conjugate being characterised by physical or galenical forms, e.g. emulsion, particle, inclusion complex, stent or kit the form being a colloid or an emulsion the form being a liposome
    • A61K47/6913—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient the non-active ingredient being chemically bound to the active ingredient, e.g. polymer-drug conjugates the conjugate being characterised by physical or galenical forms, e.g. emulsion, particle, inclusion complex, stent or kit the form being a colloid or an emulsion the form being a liposome the liposome being modified on its surface by an antibody
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/10—Dispersions; Emulsions
    • A61K9/127—Liposomes
    • A61K9/1271—Non-conventional liposomes, e.g. PEGylated liposomes, liposomes coated with polymers
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S424/00—Drug, bio-affecting and body treating compositions
    • Y10S424/812—Liposome comprising an antibody, antibody fragment, antigen, or other specific or nonspecific immunoeffector

Definitions

  • the present invention relates to a liposomal composition for treatment of a tumor, and in particular, to a composition employing long- circulation liposomes.
  • Uncontrolled cell proliferation is a characteristic of a number of disease states.
  • Such growth is observed, for example, in benign and malignant tumors.
  • drugs used to treat cellular abnormalities characterized by uncontrolled cell growth target important biochemical steps or processes that are part of the cell growth cycle.
  • An object of the present invention is to provide a liposome composition for use in tumor treatment.
  • the composition includes liposomes containing an anti-tumor compound in liposome- entrapped form, a surface coating of polyethylene glycol chains, at a surface concentration thereof sufficient to extend the blood circulation time of the liposomes severalfold over that of liposomes in the absence of such coating, and antibodies or antibody fragments effective to bind specifically to tumor-associated antigens.
  • the polyethylene glycol chains contain, in a portion thereof, functionalized reactive groups at the chain ends to which the antibodies or antibody fragments are covalently attached.
  • the liposomes have sizes preferably in the range 0.05 to 0.3 microns, and for targeting to a solid tumor, have sizes preferably in a selected size range between 0.05 to 0.12 microns.
  • Fig. 1 illustrates a portion of a liposome in the liposome ocomposition of the invention, having antibodies or antibody fragments attached to the free ends of polyethylene glycol (PEG) chains carried on the liposome;
  • PEG polyethylene glycol
  • Fig. 2 shows steps in forming a PE derivatized by a PEG spacer chain having a maleimide group at its free end
  • Fig. 3 illustrates the preparation of a biotinylated PE-PEG for use in preparing liposomes with PEG-bound biotin;
  • Fig. 4 shows coupling of an antibody to PE derivatized with a PEG chain having a hydrazide moiety at its free end
  • Fig. 5 shows the coupling of an antibody to PE derivatized by a PEG chain having a reactive maleimide group at its free end;
  • Fig. 6 shows the coupling of an antibody to a liposome-attached PEG having a hydrazide group at its free end
  • Fig. 7 is a plot of drug residence time in the blood, expressed in terms of percent injected dose, as a function of hours after IV injection in rats, for liposomes containing 67 Gallium and a bound antibody IgG (•) or liposomes with no bound antibody (A) ;
  • Fig. 8 shows 125 dUrd uptake in normal and tumor-bearing DBA/2 mice (3/group) 45 days after i.v. injection of 2 x 10 s KLN-205 cells;
  • Fig. 9 shows survival times for DBA/2 mice inoculated i.v. with 2 x 10 s KLN-205 cells and treated on the 3rd day with 6 mg/kg of either free DOX (A) , liposomal DOX ( ⁇ ) , mAb-liposomal DOX ( ⁇ ) or mAb-liposomes ( ⁇ ) (12 ⁇ g mAb, no DOX) , control groups (•) were treated with sterile PBS.
  • Tumor-associated antigens refers to antigens that are expressed at higher levels in tumor tissue relative to healthy tissue. The term also refers to antigens expressed uniquely in tumor tissue.
  • Antibody fragments refers to the F ⁇ antibody domain carrying the antigen binding sites formed by cleavage of the antibody.
  • Fig. 1 illustrates the antibody-liposome composition of the present invention.
  • the figure shows a portion of the outer bilayer 10 of a liposome 12 having an outer surface 14.
  • the liposome may include additional bilayers.
  • the outer bilayer itself is composed of confronting lipid layers 10a and 10b which are the interior and exterior lipid layers, respectively, of the bilayer, each layer being composed of vesicle- forming lipids, such as phospholipids and cholesterol.
  • Methods for forming liposomes suitable for use in the composition are described below. More generally, the liposome is representative of a particle support forming part of the composition.
  • the composition includes an antibody or an antibody fragment, such as antibody 16, which is bound to the outer liposome surface by covalent attachment to hydrophilic polymer chains, such as chains 20, which are also carried on the liposome's outer surface.
  • the polymer chains form a polymer layer about the liposome surface which allows the liposomes to circulate in the bloodstream over an extended period of time compared to liposomes lacking the polymer coating.
  • the antigen recognition region, such as antigen recognition region 22, of the antibody molecule is accessible for binding to antigens at a target site.
  • the polymer coating on the liposome surface does not affect antigen-antibody interactions.
  • Antibody molecules suitable for use in the invention, and methods of their preparation are described below.
  • the polymer chains are preferably polyethylene glycol (PEG) chains having molecular weights between about 1,000 and 10,000 daltons. corresponding to polymer chain lengths of about 22 to 220 ethylene oxide units.
  • the polymer chains are covalently attached to the polar head groups of vesicle-forming lipids as described in co-owned U.S. Patent No. 5,013,556, herein incorporated by reference.
  • the polymer chain is attached to the liposome through the polar head group of a lipid, such as lipid 18, in the outer layer 10 of the liposome bilayer.
  • the chain contains a reactive functionalized group at its free end for coupling the antibody, by methods to be described.
  • the antibody in the composition is attached to the liposome outer surface by a polymer chain.
  • the antibody is positioned at the distal, or free, ends of the polymer chains, which in the illustration are shown to be of the same length.
  • the antibodies or antibody fragments are attached to a polymer chain of a different molecular weight or chain length, generally a shorter chain length.
  • This embodiment allows the antibody in the polymer layer to be positioned at a selected depth in the layer to increase or decrease the extent to which the antibody is buried in the polymer layer. For example, if the antibody is a xenogeneic antibody which elicits an immunogenic.
  • the antibody is preferably buried to hide immunogenic sites while retaining the antigen recognition region accessible for binding to a target site. If the antibody is nonimmunogenic, the antibody can be localized on the outer surface coating of polyethylene glycol chains. Functionalization of PEG chains for this purpose, referred to herein as a spacer chain, for attachment of an antibody is described below.
  • the antibody is a biotinylated antibody attached to the distal ends of liposome-attached polymer ends via a biotin- strepavidin (or biotin-avidin) linkage.
  • a DSPE-PEG-NH j is converted to DSPE-PEG-biotin.
  • each avidin molecule contains four high-affinity biotin binding sites and to one or more of these sites is attached the liposome bound biotin.
  • a biotinylated antibody which is derivatized by a biotin molecule.
  • the particle supports should be biodegradable, have surface chemical groups through which polymer chains of polypeptide molecules can be attached to the surface, and preferably have sizes in a selected size range between about 50-300 n .
  • Exemplary particle supports of this type include sized polylactic acid particles, or microcapsules formed of poly(amino acids) .
  • the liposomes of the present invention are generally composed of at least three types of lipid components.
  • a first type which will form the bulk of the liposome structure, includes any amphipathic lipids having hydrophobic and polar head group moieties, and which (a) can form spontaneously into bilayer vesicles in water, as exemplified by phospholipids, or (b) are stably incorporated into lipid bilayers, with its hydrophobic moiety in contact with the interior, hydrophobic region of the bilayer membrane, and its polar head group moiety oriented toward the exterior, polar surface of the membrane.
  • the vesicle-forming lipids of this type are preferably ones having two hydrocarbon chains, typically acyl chains, and a polar head group. Included in this class are the phospholipids, such as phosphatidylcholine (PC) , PE, phosphatidic acid (PA) , phosphatidylglycerol (PG) , phosphatidylinositol (PI) , and sphingomyelin (SM) , where the two hydrocarbon chains are typically between about 14-22 carbon atoms in length, and have varying degrees of unsaturation.
  • PC phosphatidylcholine
  • PE phosphatidic acid
  • PG phosphatidylglycerol
  • PI phosphatidylinositol
  • SM sphingomyelin
  • the above- described lipids and phospholipids whose acyl chains have a variety of degrees of saturation can be obtained commercially, or prepared according to published methods.
  • a second lipid component includes a vesicle- forming lipid which is derivatized with a polymer chain.
  • the vesicle-forming lipids which can be used are any of those described above for the first vesicle-forming lipid component.
  • Vesicle- forming lipids with diacyl chains, such as phospholipids, are preferred.
  • One exemplary phospholipid is phosphatidylethanola ine (PE) with a reactive amino group which is convenient for coupling to the activated polymers.
  • An exemplary PE is distearyl PE (DSPE) .
  • the preferred polymer in the derivatized lipid is polyethyleneglyc ⁇ l (PEG) , preferably as a PEG chain having a molecular weight between 1,000-10,000 da1tons, more preferably between 2,000 and 5,000 daltons.
  • PEG polyethyleneglyc ⁇ l
  • the polyethylene glycol chains provide a surface coating of hydrophilic chains sufficient to extend the blood circulation time of the liposomes in the absence of such a coating.
  • hydrophilic polymers which may be suitable include polyvinylpyrrolidone, polymethyloxazoline, polyethyloxazoline, polyhydroxypropyl methacrylamide, polymethacrylamide, polydimethylacrylamide, polylactic acid, polyglycolic acid, and derivatized celluloses, such as hydroxymethylcellulose or hydroxyethylcellulose.
  • a third type of lipid component are vesicle- forming lipids which have been modified for coupling antibody molecules to the liposome outer surface.
  • These modified lipids may be of different types.
  • the modified lipid may contain a hydrophilic polymer spacer chain attached to the lipid.
  • the spacer chain as described above, has a different chain length than the polymer chains forming the liposome surface polymer coating for positioning the antibody at a selected depth in the polymer coating.
  • the hydrophilic polymer is typically end-functionalized for coupling antibodies to its functionalized end.
  • the functionalized end group is preferably a maleimide group for selective coupling to antibody sulfhydryl groups.
  • Suitable functionalized end groups include bromoacetamide and disulfide groups for reaction with antibody sulfhydryl groups, activated ester and aldehyde groups for reaction with antibody amine groups.
  • Hydrazide groups are reactive toward aldehydes, which can be generated on numerous biologically relevant compounds. Hydrazides can also be acylated by active esters or carbodiimide- activated carboxyl groups. Acyl azide groups reactive as acylating species can be easily 10 obtained from hydrazides and permit the attachment of amino containing ligands.
  • a preferred polymer in the derivatized lipid is polyethylene glycol (PEG) .
  • PEG polyethylene glycol
  • Other hydrophilic polymers which may be suitable for lipid derivatization include end-functionalized polyvinylpyrrolidone, polymethyloxazoline, polyethyloxazoline, polyhydroxypropyl methacrylamide, polymethacrylamide, polydimethylacrylamide, polylactic acid, polyglycolic acid, and derivatized celluloses, such as hydroxymethylcellulose or hydroxyethylcellulose.
  • This polymer spacer chain is preferably shorter than the polymer chain forming the liposome surface polymer coating layer.
  • the spacer arm is generally of 100-5,000 daltons, preferably 600-4,000 daltons.
  • the phospholipid may be modified by a biotin molecule.
  • a biotin molecule to attach the antibody molecule to the biotinylated liposome surface, once the liposome is formed, the antibody molecule is also modified with biotin and then incubated in the presence of the avidin.
  • Biotinylated lipids such as biotinylated PE, are commercially available.
  • lipids may be modified by a substrate for use in binding a targeting molecule to a liposome surface.
  • substrates as exemplified with biotin, are relatively small, e .g. , less than about 5,000 daltons, to allow their incorporation into multilamellar liposomes with a minimum of disruption of the lipid bilayer structures.
  • the substrate is preferably one capable of binding irreversibly to a targeting 11 molecule, to ensure that the targeting molecule remains bound to the liposomes over its lifetime in the bloodstream.
  • the liposomes may include lipids that can stabilize a vesicle or liposome composed predominantly of phospholipids.
  • the most frequently employed lipid from this group is cholesterol at between 25 to 40 mole percent.
  • cholesterol at between 0 to 20 mole percent cholesterol in a bilayer, separate domains exist containing cholesterol and phospholipids and pure phospholipid (Mabrey) . These bilayers show an increased permeability to water (Tsong) . At mole percentages above 50% cholesterol starts destabilizing the bilayer.
  • Liposome-Entrapped Compound A variety of therapeutically active compounds are suitable for delivery by the liposome composition.
  • the compound is useful, preferably, for treatment of a tumor. More generally, the therapeutic compound in liposome-entrapped form is used to treat diseased cells accessible to liposome-entrapped compounds in the bloodstream.
  • One general class includes water soluble, liposome permeable compounds which are characterized by a tendency to partition into the aqueous compartment of the liposome composition, and to equilibrate over time into the outer bulk phase of the liposome composition.
  • Preferred drugs are those that have a low liposome permeability.
  • Representative drugs of this kind include cytarabine, cyclophosphamide, methotrexate, gentamicin, and bleomycins, among others. 12
  • a second general class of compounds are those which are water-soluble, but liposome impermeable. These compounds include peptide or protein molecules, such as peptide hormones, enzymes, enzyme inhibitors, and higher molecular weight carbohydrates. Representative compounds include peptide hormones, such as vasopressin, cytokines, such as interferons (alpha, beta, gamma) , interleukins, and colony stimulating factors (macrophage, granulocyte, granulocyte and macrophage), viral or bacterial vaccines, melanoma vaccine, streptokinase, or other anti-thrombolytic peptides, and superoxide dis utase.
  • peptide hormones such as vasopressin, cytokines, such as interferons (alpha, beta, gamma) , interleukins, and colony stimulating factors (macrophage, granulocyte, granulocyte and macrophage)
  • viral or bacterial vaccines mel
  • a third class of drugs are lipophilic molecules that tend to partition into the lipid bilayer phase of the liposomes, and which are therefore associated with the liposomes predominantly in a membrane-entrapped form.
  • the drugs in this class include adrenocorticosteroids, prostaglandins, amphotericin B, nitroglycerin, polymyxins, carmustine, dacarbazine, dexamethasone, daunomycin and doxorubicin.
  • the liposome-entrapped compound may also be an imaging agent for tracking progression of a disease, such as tumor metastasis.
  • Imaging agents include chelates of radionuclides, such as technetium-99, indium-Ill, and iodine-124.
  • the antibodies are monoclonal antibodies or antibody fragments, e .g. , F ⁇ fragments, which are used for targeting tumor-associated antigens in the treatment of cancer. These antibodies or antibody fragments are typically derived from hybridomas that show positive reactivity toward the tumor tissue and negative reactivity toward healthy tissue (Samuel) .
  • monoclonal antibodies are known which react with tumor-associated antigens.
  • the antibody may be a monoclonal antibody that reacts with a high-molecular mucin expressed on several types of human carcinoma (Slavin-
  • the antibody may be an antibody that targets an antigen of tumor vascular epithelium. This type of targeting may be applicable to many types of solid tumors since many tumors require a blood supply, and epithelial cells are readily accessible from the bloodstream (Burrows) .
  • the liposomes can be used, for example, for targeting spontaneous liver metastases by use of an antibody that binds to an antigen expressed on metastasizing liver cells, but not on normal liver tissue (Schmid) .
  • the antibodies may also be used to localize a liposome-entrapped compound at non-tumor cells.
  • the antibody may be used to target liposomes to sites of myocardial necrosis (Nedelman) . Liposome entrapped compounds administered to these site may be superoxide dismutase or antithrombolytic compounds for treatment of symptoms associated with myocardial infarction.
  • the antibody may also be used for targeting a virus or a bacterium, and the antibody recognizes an antigen associated with either virus or bacterium.
  • IgG j monoclonal antibodies, 174H.64 (mAb) were used to target a liposome- entrapped drug to lung tumor cells. These antibodies recognize a unique epitope on proliferating cells of murine lung squamous carcinoma, KLN-205, as well as of human and bovine squamous carcinoma (Samuel) . 14
  • This section describes the synthesis of some exemplary modified lipids for use in coupling antibodies or antibody fragments to a liposome surface. Also described are methods of preparing liposomes which incorporate the modified lipids, and for coupling antibodies to a liposome surface via the modified lipids.
  • Fig. 2 shows the synthesis of a DSPE derivatized with a PEG chain and having a maleimide group at the chain's free end.
  • PEG bis (amine) compound I
  • 2-nitrobenzene sulfonyl chloride compound II
  • TEA triethylamine
  • the compound is reacted with DSPE in TEA to form the derivatized PE lipid protected at one end with 2- nitrobenzyl sulfonyl chloride.
  • Fig. 3 shows the synthesis of a DSPE-PEG derivatized with a succinimide ester of biotin (compound VII) .
  • the biotinylated phospholipid (compound VIII) is incorporated into liposomes.
  • the liposomes are then incubated with avidin and biotinylated antibody.
  • a DSPE derivatized with a PEG chain having a hydrazide group at the chain's free end may be synthesized, as illustrated in Fig. 4.
  • a hydroxy acid derivative (IX) is prepared from PEG using ethyl isocyanatoacetate for partial introduction of a urethane-linked glycine residue.
  • the initial product is treated with base to remove the terminal ethyl ester group, and product IX is isolated by ion-exchange chromatography.
  • the liposomes may be prepared by a variety of techniques, such as those detailed in Szoka et al , 1980.
  • Multilamellar vesicles can be formed by simple lipid-film hydration techniques. In this procedure, a mixture of liposome-forming lipids of the type detailed above dissolved in a suitable organic solvent is evaporated in a vessel to form a thin film, which is then covered by an aqueous medium. The lipid film hydrates to form MLVs, typically with sizes between about 0.1 to 10 microns.
  • liposomes are prepared by vortexing dried lipid films in a buffered aqueous solution (Olson) .
  • Liposome compositions are typically prepared with lipid components present in a molar ratio of about 30-75 percent vesicle-forming lipids, 25-40 percent cholesterol, 1-20 percent polymer- derivatized lipid, and 0.01-10 mole percent of the lipid derivative employed for antibody coupling.
  • One exemplary liposome formulation includes hydrogenated soy phosphatidylethanolamine (HSPE) , cholesterol (CH) , DSPE-PEG at a molar ratio of 2:1:0.1.
  • the composition also includes 0.05 mole percent phosphatidylethanolamine derivatized with biotin (biotin-PE) .
  • Another exemplary liposome formulation includes hydrogenated soy phosphatidylethanolamine (HSPE) , cholesterol (CH) , and DSPE-PEG at a molar ratio of 2:1:0.1.
  • the composition also includes 1 mole percent DSPE-PEG derivatized with hydrazide (DSPE-PEG-Hz) .
  • a therapeutic drug is incorporated into liposomes by adding the drug to the vesicle- forming lipids prior to liposome formation, as described below, to entrap the drug in the formed liposome. If the drug is hydrophobic the drug is added directly to the hydrophobic mixture. If the drug is hydrophilic the drug can be added to the aqueous medium which covers the thin film of evaporated lipids. Alternatively, the drug may be incorporated into preformed liposomes by active transport mechanisms. Typically, in this case drug is taken up in liposomes in response to a potassium or hydrogen ion concentration differential (Mayer, 1986; Mayer 1989).
  • One effective sizing method for REVs and MLVs involves extruding an aqueous suspension of the liposomes through a series of polycarbonate membranes having a selected uniform pore size in the range of 0.03 to 0.2 micron, typically 0.05, 0.08, 0.1, or 0.2 microns.
  • the pore size of the membrane corresponds roughly to the largest sizes 17 of liposomes produced by extrusion through that membrane, particularly where the preparation is extruded two or more times through the same mem ⁇ brane.
  • Homogenization methods are also useful for down-sizing liposomes to sizes of lOOnm or less (Martin 1990) .
  • Antibodies may be attached to a liposome by covalent methods as have been described.
  • a derivatized lipid containing an end-functionalized polyethylene glycol chain is incorporated into liposomes. After liposome formation, the end- functionalized group can react with an antibody for antibody coupling to a liposome.
  • an antibody-lipid derivative may be first formed and then incorporated into a liposome.
  • an antibody is coupled to the maleimide group of a free DSPE-PEG molecule.
  • the antibody-coupled DSPE-PEG molecule is then employed to form vesicles.
  • the end- functionalized group is a maleimide group which is preferentially reactive with sulfhydryl groups.
  • Antibodies contain sulfhydryl groups which react at the maleimide group forming a thioether linkage to generate compound XII. Details of the reactions are given in Example 1.
  • the polymer end-functionalized group is a hydrazide group (see Figure 4 discussed above) .
  • the hydrazide can be coupled to the antibody through the carbohydrate moieties present in the antibody, as detailed in Figure 6 and Example l.VIII. Briefly, antibody hydroxyl groups are oxidized to aldehydes by mild periodate oxidation. The oxidized protein is then 18 added to liposomes containing DSPE-PEG-Hz and incubated overnight. Unbound antibodies are then separated from antibody-liposomes by gel filtration.
  • antibodies can be attached to the PEG chain free ends without a significant loss in the blood circulation lifetime of the liposomes. This allows the antibody-coated liposomes to circulate for the time necessary to reach remote tumor sites and to localize at the sites through antibody-antigen specific interactions. As a result, a significant therapeutic enhancement in tumor treatment over long-circulating liposomes in the absence of surface attached antibodies is possible.
  • Liposomes like those above except containing entrapped 67 Gallium were prepared and administered to rats to measure the blood circulation time, as described in Example 2(11).
  • the levels of liposome-entrapped 67 GaIlium were measured at regular intervals following administration of the two liposome formulations and the results are shown in Fig. 7.
  • both liposome formulations gave good blood circulation lifetime, with more than 10% of the injected marker being retained in the bloodstream after 24 hours.
  • it is known from similar studies (Martin 1993) carried out with liposomes not containing PEG that standard, non-PEG coated liposomes show only about 5% marker retention in the blood 3 hours or less after iv administration and no measurable liposome label at 24 hours.
  • An antibody-liposome composition was prepared to contain on their outer surface IgG j monoclonal antibodies 174H.64 (mAb), which recognizes a unique epitope on proliferating cells of murine lung squamous carcinoma, KLN-205, as well as those for human and bovine squamous carcinoma.
  • the liposomes were tested for their therapeutic effectiveness for treatment of KLN-205 carcinoma.
  • the KLN-205 carcinoma lodges in the lung of DBA2 mice within 3 days following intravenous injection (Kaneko) .
  • Fig. 8 shows the growth inhibitory effect of doxorubicin intravenous injections as reflected by a decrease in deoxyuridine uptake by tumor cells in the lung.
  • mice were injected intravenously with KLN-205 cells. At three days post-injection the mice were treated by administering intravenously a single dose of doxorubicin (6 mg/kg body weight) .
  • Doxorubicin was administered in either free form (not encapsulated in liposomes) (DOX) , encapsulated in liposomes lacking the antibody (liposomal DOX) , or encapsulated in antibody-liposome compositions (mAb liposomal DOX) .
  • Uridine uptake into lung has been established to be directly proportional to the number of intravenous injections of KLN-205 tumor cells in the range of 10 5 to 10 6 injected cells and reflects the number of highly proliferating cells in a tissue. Uridine uptake in lungs from normal mice in the absence of tumor is low.
  • a single injection of mAb-liposomal DOX resulted in an 80% reduction in the growth of lung tumors as measured by radiolabelled deoxyuridine uptake.
  • Single injections of liposomal DOX resulted in a 65% reduction in the growth of the lung tumors.
  • Administration of free doxorubicin resulted in only a 40% reduction in lung tumor growth.
  • Example 4 histopathological studies were also performed as described in Example 4. These studies showed that the presence of tumor nodules was minimal after mAb-liposomal DOX administration. Animals that received single injections of liposomal DOX showed fewer nodules than those that received free DOX or no treatment. The number of discrete tumor foci/linear cm of lung were counted for both the right and left lungs for 1 or 2 mice from each treatment group of 5 mice, and mean tumor diameters were determined as compiled in Table 2. The number of tumor foci/linear cm was negligible for mice receiving mAb-liposomal DOX.
  • Liposome uptake in the lung was also examined and is described in Example 5. Uptake of liposomes containing radiolabeled tyraminylinulin in mAb-liposome-entrapped form by tumor lung tissue was greater than for liposomes lacking antibody bound at the liposome surface.
  • the results obtained indicate that liposomes containing entrapped doxorubicin, lipids derivatized with PEG, such as PEG-DSPE, and containing an antibody on the liposomes' outer surface (mAb-liposomal DOX) are valuable for increasing the therapeutic effectiveness of doxorubicin administration to a site in a subject.
  • the method of the present invention is likely applicable to the targeting of other therapeutic compounds to tumor sites, or other target sites.
  • the above described antibody-liposome composition containing an anti-tumor compound in liposome- entrapped form, is used for tumor treatment.
  • the antibody-liposome enhances the therapeutic efficacy of the compound by localizing the liposome, and the anti-tumor compound, selectively at the tumor site.
  • doxorubicin administered parenterally in antibody-liposome entrapped form substantially increased the survival time of mice with lung tumor.
  • Fig. 9 shows survival data for mice receiving various treatments of doxorubicin at doses of 6 mg/kg body weight, as described in
  • Example 3 The mean survival time (MST) for mice treated with mAb liposomal DOX, that died from their tumors was 99.2 ⁇ 36.1 days and was substantially longer than the MST for untreated mice (52.0 ⁇ 5.8 days).
  • the group treated with doxorubicin in mAb-liposome entrapped form showed a 50% survival rate.
  • the method of the present invention is of utility for the treatment of both "solid" tumors and blood-born tumors.
  • a solid tumor is defined as one that grows in an anatomical site outside the bloodstream (in contrast, for example, to blood-born tumors such as leukemias) and requires the formation of small blood vessels and capilla ⁇ ries to supply nutrients, etc. to the growing tumor mass.
  • the anti-tumor compound which may be used is any compound, including the ones listed below, which can be stably entrapped in liposomes at a suitable loading factor and administered at a therapeutically effective dose (indicated below in parentheses after each compound) .
  • amphipathic anti-tumor compounds such as the plant alkaloids vincristine (1.4 mg/m 2 ) , vinblastine (4- 18 mg/m 2 ) and etoposide (35-100 mg/m 2 ) , and the anthracycline antibiotics including doxorubicin (60-75 mg/m 2 ) , epirubicin (60-120 mg/m 2 ) and daunorubicin (25-45 mg/m 2 ) .
  • the water-soluble anti-metabolites such as methotrexate (3 mg/m 2 ) , cytosine arabinoside (100 mg/m 2 ) , and fluorouracil (10-15 mg/kg)
  • the antibiotics such as bleomycin (10-20 units/m 2 ) , mitomycin (20 mg/m 2 ), plicamycin (25-30 ⁇ g/m 2 ) and dactinomycin (15 ⁇ g/m 2 )
  • the alkylating agents including cyclophosphamide (3-25 mg/kg), thiotepa (0.3-0.4 mg/Kg) and BCNU (150-200 mg/m 2 ) are also useful in this context.
  • the liposomes may contain encapsulated tumor-therapeutic peptides and protein drugs, such as IL-2, and/or TNF, and/or immunomodulators, such as M-CSF, which are present 24 alone or in combination with anti-tumor drugs, such as an doxorubicin.
  • IL-2 IL-2
  • TNF tumor-therapeutic peptides and protein drugs
  • immunomodulators such as M-CSF
  • an antibody modified by a ligand molecule such as a biotinylated antibody
  • a ligand molecule such as a biotinylated antibody
  • liposomes containing a liposome-entrapped compound, and a surface-bound anti-ligand molecule, such as avidin are administered parenterally. Liposomes with the surface-bound avidin will be retained at target sites by biotin molecules covalently attached to the antibodies.
  • multivalent species capable of binding multiple antibodies may be administered between about 24 to 48 hours after administration of the biotinylated antibodies to accelerate clearance of the antibodies from the bloodstream.
  • These multivalent species may be empty liposomes having surface-bound avidin, but not containing the liposome-entrapped compound.
  • the empty liposomes may or may not have a hydrophilic polymer surface layer.
  • the multivalent species may be avidin molecules.
  • multivalent species serve to chase nonspecifically-bound biotinylated antibodies from sites in the bloodstream.
  • liposomes containing the therapeutic compound in liposome-entrapped form the surface-bound anti- ligand molecules, such as avidin, and the PEG layer on the liposome surface are administered.
  • the chase with the multivalent species will prevent binding of liposomes containing liposome entrapped-drug at non-specific sites and 25 will maximize the specificity of therapeutic compound targeting in vivo.
  • the present method can be employed for improved targeting of an imaging agent to a tumor, for tumor diagnosis.
  • the imaging agent typically a radioisotope in chelated form, or a paramagnetic molecule
  • the imaging agent is entrapped in liposomes, which are then administered IV to the subject being examined.
  • the subject is then monitored, for example by gamma scintillation radiography in the case of the radioisotope, or by nuclear magnetic resonance (NMR) in the case of the paramagnetic agent, to detect regions of local uptake of the imaging agent.
  • NMR nuclear magnetic resonance
  • antibody-liposomes would be useful for delivery of anti-infective compounds to regions of infections. Sites of infection, like tumors, often exhibit specific antigens or antigens expressed at higher levels that may be targeted by the antibody- liposome compositions. It is expected that antibody-liposomes containing antibiotics (such as aminoglycosides, cephalosporins, and beta lactams) would improve compound localization at sites of infection, thereby improving the therapeutic index of such agents, particularly ones which exhibit dose-related toxicities, such as the aminoglycosides.
  • antibiotics such as aminoglycosides, cephalosporins, and beta lactams
  • IgG monoclonal antibody 174H.64 (mAb) directed against mammalian squamous carcinoma was 26 a generous gift of Biomira, Inc. (Edmonton, AB) .
  • Hydrogenated soy phosphatidylcholine (HSPC) was obtained from Asahi Chemicals, Japan.
  • Cholesterol (CH) was purchased from Sigma Chemicals (St. Louis, MO) .
  • Example 2 Biodistribution of Antibody-Liposomes The biodistribution and blood circulation lifetime of liposomes containing surface-bound antibodies was compared to that of liposomes lacking surface-bound antibodies.
  • the antibody- liposomes were composed of HSPC:CH:PEG hydrazide, at a 2:1:0.1 molar ratio, and sheep IgG covalently linked to PEG chain.
  • Liposomes lacking surface- bound antigens were liposomes composed of HSPC:CH:PEG at a 2:1:0.1 molar ratio and liposomes composed of HSPC:CH:PEG hydrazide. The average diameter of the liposomes was between 110 and 120 nanometers.
  • the liposomes contained 125 I-tyraminylinulin in liposome-entrapped form (Example 2(1)).
  • the liposomes contained 67 Gallium in liposome-entrapped form.
  • the antibody-liposomes were prepared as described in Example l.VIII.
  • mice Female CD(ICR) BR (outbred) mice in the weight range of 23-30 grams were obtained from Charles River Canada (St. Constant, QUE) , and maintained in standard housing. Mice (three per group) were given a single bolus injection with 0.2 ml of liposomes containing approximately 10° 125 I-T1 cpm and 0.5 micromole phospholipid, and approximately 10 micrograms antibody, where applicable. Some groups of mice received injection of free radiolabelled TL. Injections were performed by intravenous injection via the tail vein. After specified periods of time, animals were anesthetized with halothane (M.T.C. Pharmaceutical, Ontario) and sacrificed by cervical dislocation.
  • halothane M.T.C. Pharmaceutical, Ontario
  • DBA2 mice (Jackson Laboratories) were injected i.v. with 2 x 10 5 KLN-205 cells. At 3 days post-injection of KLN-205 cells, the mice were injected i.v. with single injections of either 0.2 ml phosphate-buffered saline (PBS) (untreated controls) or with 6 mg/kg of either free DOX, 6 mg/kg of DOX entrapped in HSPC:CH:PEG- DSPE liposomes (liposomal DOX) , 6 mg/kg of DOX entrapped in HSPC:CH:PEG-DSPE liposomes containing attached antibody 174H.64 (mAb-liposomal DOX) or mAb-liposomes (11-39 ⁇ g mAb) lacking DOX, all in 0.2 ml of sterile saline.
  • PBS 0.2 ml phosphate-buffered saline
  • DOX free DOX
  • mice On the 45th day after injection, mice were injected with 2 ⁇ Ci each of 125 I-dUrd and 4 hr later the lungs were removed, cut into small pieces, washed with 10% trichloroacetic acid and counted in a gamma counter.
  • Liposomal DOX 10 0.31 ⁇ 0.06 19 0.39 ⁇ 0.23 mAb-liposomal DOX 0.3 0.22 0.7 0.18, 0.26
  • Uptake of liposomes labelled with 125 i- tyraminylinulin ( 125 I-TI) into lung in DBA/2 mice (3/group) at 15 minutes post-injection was determined. Uptake experiments provide a measure of uptake of intact liposomes. Liposome uptake was examined at 3 days and 45 days after i.v. injection of 2 x 10 s KLN-205 cells. Experimental groups were composed of tumor-free (control) animals receiving either HSPC:CH:PEG-DSPE or mAb- HSPC:CH:PEG-DSPE liposomes (2:1:0.1 molar ratio, no drug) , or tumor-bearing animals receiving similar liposomes.
  • Liposome uptake experiments were performed to confirm specific localization of the liposomes to the lungs.
  • the uptake of liposomes and mAb- liposomes into lung in tumor bearing mice at 3 days post-injection was 29.4 ⁇ 4.1 and 72.7 ⁇ 26.9 cpm/mg total lung tissue, respectively. This compares with 27.4 ⁇ 10.6 and 41.6 ⁇ 29.6 cpm/mg total lung tissue for tumor-free lungs.
  • the uptake of mAb liposomes was 121.9 ⁇ 35.4, as compared with tumor-free mice (42.9 ⁇ 6.2 cpm/mg total lung tissue) .
  • Lung uptake at 45 days postinjection of tumor was 5.0 ⁇ 1.1% of in vivo mAb liposomes for tumor-bearing mice compared to 1.3 ⁇ 0.2% for tumor-free mice at 24 hours post-injection of liposomes.
  • the increased uptake of mAb liposomes suggests that they are able to bind to proliferating tumor cells localized in the lung.

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Abstract

L'invention se rapporte à une composition de liposomes destinée au traitement d'une tumeur chez un sujet. La composition comprend des liposomes (12) contenant un composé antitumoral sous une forme piégée par les liposomes, et comportant en surface une couche de chaînes de polyéthylène glycol (20), en une concentration de surface suffisante pour multiplier plusieurs fois le temps de circulation dans le sang desdits liposomes par rapport à celui de liposomes dépourvus de cette couche PEG. Des anticorps ou fragments d'anticorps (16), efficaces pour se lier spécifiquement aux antigènes associés à la tumeur, présents sur le site tumoral, sont fixés aux extrémités libres d'une partie des chaînes polymères. Une composition de liposomes a une granulométrie prédominante comprise entre 0,05 et 0,12 microns, renferme de la doxorubicine sous forme piégée, et contient, sur les extrémités libres des chaînes PEG, un anticorps monoclonal spécifiquement dirigé contre des cellules fortement prolifératives d'un épithélioma épidermoïde bronchique.
PCT/US1994/003457 1993-03-31 1994-03-30 Procede de traitement d'une tumeur solide WO1994022429A1 (fr)

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