LIPOSOME-FORMULATIONS FOR TREATMENT OF VIRAL DISEASES

Abstract: A method is disclosed for the treatment of viral diseases comprising the administration of antiviral agents encapsulated in liposomes. Also provided are formulations of liposomes for the treatment of viral diseases and more particularly for the treatment of infectious caused by viruses like human immunodeficiency virus (HIV) and cytomegalovirus (CMV). These formulations of liposomes are composed of specific classes of lipid components and contain an entrapped drug effective against the viral disease. These liposomal formulations of antiviral drugs allow high cellular penetration in different cell lines, good in vitro antiviral efficacy against HIV and CMV replication, efficient in vivo targeting of HIV reservoirs and a marked improvement of the pharmacokinetics of drugs.

Description: TiTu or TAB IMYBWTIOW LI P0S0ME- FORMULATIONS FOR TREATMENT OF VIRAL DISEASES Field o-f -the invention This invention relates to formulations of liposomes and method for use in the treatment of viral diseases and particularly in the treatment of infections caused by viruses like human immunodeficiency virus and cytomegalovirus . Background of -hha Invention Many antiviral agents have been developed for the treatment of patients with human immunodeficiency virus (HIV) infection. However, only temporary and limited benefits are observed in HIV-infected patients treated with any of the actual antiretrovirals or combinations of them. The limited ability of these agents to decrease viral burden, the rapid development of resistance and the toxic side-effects of most drugs have limited their long-term efficacy. One major problem associated with the administration of antiviral agents to patients is their poor ability to penetrate and target infected cells . Rapid drug clearance and the toxicity of parent compounds or metabolites constitute also some of the major drawbacks which may slow down the development and use of many antiviral agents. Given the severe toxicity of antiviral agents actually available to treat AIDS and other viral diseases and their limited ability to target infected cells, strategies aimed at reaching therapeutic levels of drugs into infected cells and reducing toxicity should be explored. Entrapment of drugs into liposomes constitutes an attractive approach to improve the delivery of active agents to infected cells and to reduce toxic effects associated with their administration. Liposomes are microscopic vesicles in which a variety of drugs can be incorporated. Because of the similarity of the primary components of liposomes with natural membranes, liposomes are generally non-toxic and biodegradable. We believe that a better understanding of the SUBSTITUTESHEET role of liposomes as carriers of antiviral agents may lead to new strategies which may improve the efficacy and safety of drugs used for the treatment of AIDS and other viral diseases. There is now much evidence showing that macrophages play a central role in HIV pathogenesis, acting as reservoirs for dissemination of virus throughout the immune system (Gendelman et al., 1989, AIDS 3:475-495; Meltzer et al. , 1990; Ann. Rev. Immunol. 8:169-194) . It was recently reported that in the early-stage of the infection and throughout the clinically latent stage, HIV accumulates and replicates actively in the lymphoid organs despite a minimal viral activity in peripheral blood (Pantaleo et al., 1993, Nature 362:355-358; Embretson et al., 1993, Nature 362:359-362; Fox et al . , 1994, Nature 370:256) . The high viral burden observed in the lymphoid tissues was reported to be associated to trapped HIV particles in the follicular dendritic cells of the germinal centers. Over the course of HIV infection, the follicular dendritic cells network was gradually disrupted and ultimately destroyed. As the microenvironment of lymphoid tissues is crucial for effective immune response, it is primordial to reduce or abrogate the accumulation of HIV into the lymphoid tissues in order to preserve the integrity of the microenvironment network. The use of liposomes as a drug delivery system is particularly relevant to control the progression of HIV disease. Since liposomes are naturally taken up by cells of the mononuclear phagocyte system (MPS) , liposome-based therapy should concentrate the antiviral agents within cells susceptible to HIV infection and, at the same time, reduce the quantity of drugs at sites where it might be potentially toxic. Liposome-encapsulated drugs could therefore represent a convenient strategy to reduce the dissemination of HIV to the lymphoid tissues and preserve the follicular dendritic cells microenvironment that will likely protect the infected host from developing the characteristic immunodeficient state. SUBSTITUTE SHEET The use of liposomes as drug delivery system could offer important benefits when compared to the parent drug. For instance, liposomes could protect drugs against enzymatic degradation, improve their pharmacokinetics and tissue distribution and may allow a controlled release of therapeutic agents to appropriate cells. In addition, the distribution and therapeutic availability of liposomes can be modulated through variations of their size, lamellarity, lipid composition, charge and surface properties. It is thus primordial to adapt the physicochemical properties of liposomes with the desired therapeutic objective. It is an object of the present invention to generate liposomal formulations of drugs for the treatment of AIDS and other viral diseases. Such targeted delivery system should hopefully result in an increased efficacy and reduced toxicity of antiviral agents in humans suffering from AIDS or other vira- diseases. In addition, the improved drug bioavailability upon encapsulation of drugs into liposomes could reduce the dosing interval and consequently improve the quality of life of patients infected with HIV and other viruses. <tι.mm»Λ- r Λ f fc -i invention The invention relates to a method for the treatment of viral diseases comprising the administration of antiviral agents encapsulated in liposomes. The invention also concerns formulations of liposomes for the treatment of viral diseases and more particularly for the treatment of infections caused by viruses like HIV and CMV. The formulations of liposomes are composed of specific classes of lipid components and contain an entrapped drug effective against the viral disease. The originality of the present invention is that these liposomal formulations of drugs allow high cellular penetration in different cell lines, good in vitro antiviral activity against HIV and CMV, efficient in vivo targeting of HIV reservoirs and a marked improvement in the pharmacokinetics of drugs (see Examples) . SUBSTITUTE SHEET In a preferred embodiment, formulations of liposomes are composed of distearoylphosphatidylcholine (DSPC) : distearoylphosphatidylglycerol (DSPG) in a molar ratio of 10:3, have a mean particle diameter between about 0.05 and 0.5 μm, and contain 2 '-3 '-dideoxyinosine (ddl) as an antiviral drug. In another preferred embodiment, formulations of liposomes are composed of DSPC:DSPG: distearoylphosphatidyl- ethanolamine-polyethyleneglycol (DSPE-PEG) in a molar ratio of 10:3:1.45, have a mean particle diameter between about 0.05 and 0.5 μm, and contain 2 '-3 '-dideoxyinosine (ddl) as an antiviral drug. In another preferred embodiment, polyethyleneglycol has a molecular weight between about 500 and 5000 daltons . In another preferred embodiment, formulations of liposomes are composed of dipalmitoylphosphatidylcholine (DPPC) :dicetylphosphate (DP) : cholesterol (CHOL) in a molar ratio of 4:1:5, have a mean particle diameter between about 0.05 and 0.5 μm, and contain 2'-3 '-dideoxycytidine (ddC) as an antiviral drug. In still another preferred embodiment, formulations of liposomes are composed of DPPC:dipalmitoylphosphatidylglycerol (DPPG) in a molar ratio of 10:3, have a mean particle diameter between about 0.05 and 0.5 μ , and contain foscarnet as an antiviral drug. Brief daaeri-pfcion of the drawinoa Figures la and lb illustrate the accumulation of free and liposomal ddl (20 μM ddl) as a function of time, in U937 cells (Fig. la) and RAW 264.7 cells (Fig. lb) . Figures lc and Id illustrate the accumulation of free and liposomal ddC (25 μM ddC) as a function of time, in U937 cells (Fig. lc) and RAW 264.7 cells (Fig. Id) . Figures le and If illustrate the accumulation of free and liposomal ddC and foscarnet, respectively, as a function of drug concentration in RAW 264.7 cells. Figures 2a, 2b and 2d show the antiviral activity of free and liposomal ddl (40 μM ddl), ddC (0.01 μM ddC) and foscarnet SUBSTITUTESHEET (1 μM foscarnet), respectively, in U937 cells infected with HIV-liiiB- Figures 2c and 2e show the antiviral activity of free and liposomal ddC (0.01 μM ddC) and foscarnet (1 μM foscarnet), respectively, in Molt-4 clone-8 cells infected with HIV-IIIIB. Figure 2f shows the antiviral activity of free and liposomal foscarnet (1 μM) in Supt-1 cells infected with HIV-IIIIB- Figure 2g shows the inhibition of CMV p72 protein expression in human lung fibroblast cells (MRC-5 cell line) by free and liposomal foscarnet (PFA and L-PFA, respectively) . Figures 3a, 3b, 3c represent the plasma and tissue distribution of free ddl (Fig. 3a), liposomal ddl (Fig. 3b) and liposomal lipids (Fig. 3c) in rats after the administration of free ddl or ddl entrapped in liposomes composed of DSPC:DSPG in a molar ratio of 10:3 and having a mean size particle diameter of 0.175 μm. Figures 3d and 3e represent the plasma and tissue distribution of liposomal ddl (Fig. 3d) and liposomal lipids (Fig. 3e) in rats after the administration of ddl entrapped in liposomes composed of DSPC:DSPG:DSPE-PEG in a molar ratio of 10:3:1.45 and having a mean size particle diameter of 0.150 μm. Figures 3f, 3g, 3h and 3i represent the plasma and tissue distribution of free and liposomal ddC (ddC and L-ddC) in rats, 1 hour (Fig. 3f and 3h) and 3 hours (Fig. 3g and 3i) after the intravenous (Fig. 3f and 3g) or intraperitoneal (Fig. 3h and 3i) administration of free ddC or ddC entrapped in liposomes composed of DPPC:DP:CHOL in a molar ratio of 4:1:5 and having a mean size particle diameter of 0.300 μm. Figures 3j, 3k and 31 show the plasma and tissue distribution of liposomal foscarnet (Fig. 3j), free foscarnet (Fig. 3k) and liposomal lipids (Fig. 31) in rats after the administration of free foscarnet or foscarnet entrapped in liposomes composed of DPPC:DPPG in a molar ratio of 10:3 and having a mean size particle diameter of 0.165 μm. In figures 3a to 31, values represent means (± SEM) obtained from 4 to 6 animals per group per time point. SUBSTITUTESHEET Detailed deaerip-tion of the iflY-an JQn Lipid components In liposome-based products, it is necessary to use liposome bilayer characteristics which allow high efficiency of drug encapsulation as well as reduced leakage of entrapped drug to take advantage of the ability of liposomes to deliver high quantity of antiviral agents into infected cells. In the case of the drugs under the scope of this invention, these requirements are obtained by using liposomes composed of i) a mixture of diacylphosphatidylcholine and diacylphosphatidyl- glycerol (in a molar ratio ranging between 10:1 and 1:1) wherein the acyl chains are either saturated or unsaturated and have between 14 and 18 carbon atoms in length or ii) a mixture of diacylphosphatidylcholine :dicetylphosphate : cholesterol in a molar ratio of 4:1:5 wherein the acyl chains of phosphatidylcholine are either saturated or unsaturated and have between 14 and 18 carbon atoms in length. The liposomes of the present invention include sterically stabilized liposomes, defined herein as, liposomes composed of the lipid components mentioned above and which are modified by the incorporation of polymers, such as poloxamers and poloxamines, or of amphipathic lipids derivatized with a polymer such as DSPE-PEG or dioleoylphosphatidylethanolamine- PEG (DOPE-PEG) . Details for the synthesis of DSPE-PEG are provided in Example 1. The liposomes of the present invention also include immunoliposomes, defined herein as, liposomes or sterically stabilized liposomes composed of the lipid components mentioned above and which are modified by the coupling of antibody molecules which enhance the targeting of specific cells. Not all the liposomal formulations tested have shown efficient drug encapsulation and drug retention. For instance, the entrapment of ddl in liposomes composed of egg phosphatidylcholine:cholesterol in a molar ratio of 55:45 showed an efficiency of drug encapsulation which was about 30 SUBSTITUTE SHEET times lower than that observed for liposomes composed of DSPC:DSPG in a molar ratio of 10:3. On the otner hand, over 90% of ddl was released from multilamellar vesicles composed of egg PC:cholesterol:cardiolipin in a molar ratio of 35:45:10 after only 1 hour of incubation in human serum. In contrast, only 10% of ddl was released from multilamellar vesicles composed of DSPC:DSPG in a molar ratio of 10:3 in similar conditions after 5 hours of incubation in human serum. Even though the following examples describe specific liposomal formulations, it is deemed that a family of liposomal formulations can be easily derived therefrom, without affecting the valuable properties thereof. Therefore, this family of compounds comprises other acyl chains of given phospholipids formulations that have been tested in the practice. Preparation of Hposomes A large number of techniques of preparation of liposomes has been developed in the past few years in response to the growing number of specific applications of liposomes as drug delivery system. The preparation of liposomes in the present invention can be done by a variety of techniques such as those described in the literature (Szoka and Papahadjopoulos, 1980, Ann. Rev. Biophys. Bioeng. 9:467-508; Nassander et al., 1990, Liposomes in Biodegradable polymers as drug delivery systems, p.261-338) . Among them, the thin lipid film hydration technique constitutes a rapid and simple procedure to generate liposomes. Liposomes generated by this technique are mostly multilamellar vesicles and generally range in size from 0.2 to 10 μm. The thin lipid film hydration technique is detailed in Example 2. Another common technique of preparation of liposomes is the reverse phase evaporation technique described by Szoka et al. in U.S. Patent No. 4,235,871. Liposomes generated by this technique are unilamellar or plurilamellar and generally range in size from 0.2 to 5 μm. The reverse phase evaporation technique is detailed in Example 3. SUBSTITUTESHE Antiviral agents Any inhibitor of viral DNA and/or RNA synthesis and/or HIV protease is under the scope of this invention. Included in this class are antiviral agents such as 3'-azido-3'- deoxythymidine (AZT) , ddl, ddC, foscarnet, ribavirin, ganciclovir and saquinavir. Incorporation of these drugs into liposomes can be achieved by one or more methods of active and/or passive loading such as those described in the literature (Mayer et al., 1986, Chem. Phys . Lipids 40:333- 345) . Formulations of liposomes of the present invention include those having a mean particle diameter of any size but most preferably those between about 0.05 and 0.5 μm. The formulations of liposomes of the present invention also include those prepared with any drug/lipid molar ratio. As previously mentioned, the propensy of liposomes to be taken up by cells of the MPS should concentrate the entrapped antiviral agents within cells susceptible to HIV or other viral infections, improving therefore their antiviral efficacy and reducing their toxicity. Therefore, the following examples are intended to demonstrate the preparation of specific liposomal formulations of antiviral drugs which could be very efficient for the treatment of HIV and CMV infections, but are in no way intented to limit the scope thereof. In addition, even though the effect of liposomal formulations of drugs has been specifically verified on two viral species, HIV and CMV, any virus sensitive to the effect of inhibitors of viral DNA and/or RNA synthesis and/or HIV protease is under the scope of this invention. EXAMPLE 1 Syn hesis of DSPE-PEG Distearoylphosphatidylethanolamine-polyethyleneglycol (DSPE-PEG) was prepared as previously described (Gabizon and Papahadjopoulos, 1989, Proc. Natl. Acad. Sci. USA 85:6949- 6953; Klibanov et al., 1990, FEBS Letters 268:235-237) . SUBSTITUTE SHEET Briefly, methoxypolyethyleneglycol succinimidyl succinate (PEG-OSu; MW 5000) , DSPE and triethylamine in a molar ratio of 3 : 1 : 3 . 5 c on t a i n i n g 0 . 0 1 μC i o f [ 1 C ] - dioleoylphosphatidylethanolamime DOPE ( [ 14 C] -DOPE) by μmol of lipid were incubated overnight at room temperature in CHCI3 . Solvent was then evaporated under a stream of nitrogen and the resulting dry mixture was hydrated with bidistilled water . The micelles solution was filtered through a column (32 x 2 cm) containing Bio-Gel A-1 .5 M (50-100 mesh) to remove uncoupled PEG-OSu . Peak fractions containing DSPE-PEG were determined by both scintillat ion count ings ( for [ - 1 4 C ] -DOPE-PEG ) and absorbance readings at 225 nm ( for free PEG-OSu) . Fractions containing DSPE-PEG were pooled and dialysed for 24 hrs against water using dialysis membrane with a nominal molecular weight cut-off (MWCO) of 300 , 000 ( Spectra-Por , Spectrum Medical , Los Angeles, CA) and then lyophilized . DSPE-PEG can be also obtained commercially in a variety of molecular weights . EXAMPLE 2 2 '-3 '-dideoxyinosine (ddl) was encapsulated into liposomes composed of DSPC:DSPG in a molar ratio of 10:3 and DSPC:DSPG:DSPE-PEG in a molar ratio of 10:3:1.45 using the thin lipid film hydration. DSPE-PEG can be synthetized according to Example 1 or obtained commercially. In brief, the lipid mixture was dissolved in chloroform:methanol (2:1 v/v) in presence of a small proportion of [ 14 C]-DPPC (<0.002% mol/mol) and solvent was next evaporated in a round bottom flask to form a thin lipid film on the wall of the ilask. The lipid film was then hydrated with a phosphate buffered solution (PBS, 145 mM, pH 7.4) of ddl in a drug/lipid molar- ratio of 2 in which a small proportion of radiolabeled [^H]- ddl was added. After approximately a 30 minutes stand at room temperature, multilamellar vesicles (MLVs) were formed upon mechanical ag'tation of the liposomal preparation at a temperature above the gel to fluid phase transition of the lipid mixture. MLVs were extruded with a stainless steel SUBSTITUTE SHEET extrusion device (Lipex Biomembrane, Vancouver, BC) through polycarbonate membranes (Nuclepore, Cambridge, MA) of 0.2 μ . Vesicles size distribution and homogeneity were evaluated by quasi-elastic light scattering (QELS) with a submicron particle analyzer (model N4SD Coulter Electronics, Hialeah, FL) . The mean diameter of the extruded liposomes was 0.175 ± 0.035 μm and 0.15 ± 0.01 μm for the DSPC:DSPG and DSPC:DSPG:DSPE-PEG formulations, respectively. Unencapsulated drug was removed either by centrifugation (300g for 15 min at 4°C) of the liposomal preparation (1 ml) through a 10 ml column of coarse Sephadex G-50 (Pharmacia LKB, Montreal, QC) , ultracentrifugation (160000g for 90 min at 4°C) or by dialysis against a determined volume of PBS. Efficiency of drug entrapment has been determined with the use of a liquid scintillation counter (model LS 6000TA, Beckman Instruments Canada Inc., Mississauga, ON). EXAMP E 3 2 '-3'-dideoxycytidine (ddC) was encapsulated into liposomes composed of DPPC:DP:CHOL in a molar ratio of 4:1:5 using the reverse phase evaporation method (Szoka and Papahadjopoulos, 1978, Proc. Natl. Acad. Sci. USA 75:4194- 4198) . In brief, the lipid mixture was dissolved in chloroform:methanol (2:1 v/v) in presence of a small proportion of cholesteryl [1- 14 C] oleate and solvent was next evaporated in a round bottom flask to form a thin lipid film on the wall of the flask. The lipid film was then redissolved in isopropylether:methanol (3:0.8 v/v). To this organic phase was added a phosphate buffered solution (PBS, 145 mM, pH 7.4) of ddC in a drug/lipid molar ratio of 3.6 containing a small proportion of radiolabeled [-^Hl-ddC. The mixture of the two phases was next sonicated for 5 min in an ultrasonic bath at room temperature to give an homogeneous solution. The organic solvent was eliminated under vacuum in controlled conditions by retroevaporation at 50°C. The liposome suspensions were then extruded through polycarbonate membranes of 0.4 μm. Vesicles size distribution and homogeneity were evaluated by SUBSTITUTESHEET QELS . The mean diameter of the extruded liposomes was 0 . 300 ± 0 . 08 μm . Unencapsulated drug was removed as described a~ove and encapsulat ion ef f iciency of ddC was estimated by radioactivity countings . EXAMPLE 4 Foscarnet was encapsulated into liposomes using the reverse phase evaporation method as described for the liposomal preparation of ddC (Example 3) except that the lipid components was DPPC:DPPG in a molar ratio of 10:3. In this case, the drug/lipid molar ratio was 5, and [-^H.-DPPC and [1 C]-foscarnet were used as lipid and drug markers, respectively. The liposome suspensions were extruded through polycarbonate membranes of 0.2 μm generating liposomes with a mean diameter of 0.165 ± 0.030 μm. Unencapsulated drug was removed as described above and encapsulation efficiency of foscarnet was estimated by radioactivity countings. ExaaPlOS eomparin<-r lipoaomal drups with £χ_fi£ drugs Cellular uptake We have performed in vitro experiments to evaluate the accumulation of free and liposome-encapsulated anti-HIV agents in murine monocyte-macrophage RAW 264.7 cells and in human premonocytoid U937 cells. In brief, experiments were performed by incubating confluent cells in culture medium in presence of different concentrations of free and liposome-encapsulated anti-HIV agents in which a small proportion of radiolabeled drugs and lipids were added. At different incubation times, the medium was removed and cells were washed and treated with a Triton X-100 solution. Drug and lipid uptake were determined by measuring the radioactivity le- el with a liquid scintillation counter. The protein cc ^entration for each sample was determined with a Pierce bicinchoninic acid protein assay (Rockford, IL) in microtiter plates. Results showed that the incorporation of ddC in liposomes greatly enhanced the drug uptake in both RAW 264.7 and U937 cells (Figures lc. Id and le) . Similarly, liposomal foscarnet accumulated much SUBSTITUTE better than the free drug in RAW 264.7 cells (Figure If) . In contrast, although the uptake level of liposomal ddl in these cells was similar to that of liposomal formulations of ddC or foscarnet, a higher accumulation of free ddl was observed in both cell lines (Figures la and lb) suggesting a greater membrane permeability of these cell lines to ddl compared to the other anti-HIV agents. In vi tro antiviral efficacy The antiviral efficacy of the liposomal formulations of antiviral drugs have also been evaluated in different cell lines. Briefly, cells were infected with different strains of HIV with a multiplicity of infection of 1 (virus/target cell) and were treated with different concentrations of free and liposome-encapsulated drugs. Virus replication was monitored at different time intervals by measuring either the reverse transcriptase activity in cell-free supernatants or the viral p24 protein using an enzymatic test. Virus transcription was also monitored by polymerase chain reaction (PCR) analysis 24 hours after treatment using an HIV primer pair (M661/M667) . The PCR evaluation was normalized with respect to the amount of human β-globin gene in cells. Cell viability was assessed using a tetrazolium-based colorimetric (MTT) assay. Results showed that the incorporation of ddC in liposomes has resulted in comparable or even better anti-HIV efficacy than the free agent against HIV-IIHB replication in U937 and Molt-4 clone-8 cells (Figures 2b and 2c) . Similarly, liposomal foscarnet showed comparable or even better antiviral efficacy than that of the unencapsulated drug against HIV-1T.HB replication in U937, Molt-4 clone-8 and Supt-1 cells (Figures 2d, 2e, and 2f) . Although the antiviral efficacy of the liposomal formulation of ddl was lower than that of the free agent against HIV-IHIB replication in U937 cells (Figure 2a) , a greater anti-HIV efficacy was observed for liposomal ddl against HIV-lAda-M replication in monocyte-derived macrophages (Table 1) . It is appreciated that, as liposomes are preferentially taken up by cells of the MPS, the much higher SUBSTITUTESHEET anti-HIV efficacy of the liposomal drugs over the free drugs will be most likely observed under in vivo situations. Table 1: Antiviral eficacy of free and liposomal ddl in primary monocyte-derived macrophages infected with HIV-l Ad a-M. a Treatment Concentration p24 (ng/ml) (Days post-infection) (μM) 7 13 17 Untreated 0 161 1,263 7,700 Liposomal 0.1 0 0 0 ddl 1 0 0 0 10 0 0 0 Free ddl 0.1 0 20 280 1 0 0 0 10 0 0 0 a Peripheral blood mononuclear cells were suspended in seeding medium in a 48 well-plate at a density of 3 x 10^ cells/ml. Five days after initiation of the cultures, nonadherent cell were removed by rinsing the cultures four times with PBS. Adherent cells were first preincubated in the presence or absence of drug-containing medium for 2 hours prior to inoculation with 10,000 cpm/well of the Ada-M monocytotropic strain of HIV-1. Thereafter, medium was changed once every 4 to 5 days and was replaced with medium supplemented or not with ddl. Virus replication was monitored by measuring p24 levels using an enzymatic assay. The anti-CMV activity of free and liposome-encapsulated foscarnet has been also evaluated in embryonic lung fibroblast cells (MRC-5 cell line) . In brief, cells were infected with the AD169 strain of human CMV and were treated with serial SUBSTITUTE SHEET dilutions of free and liposomal foscarnet. After a 96 hours incubation, cells were fixed and immunoperoxydase staining was performed using a monoclonal antibody directed against a 72- kDa immediate early CMV protein. Labeled plaques were counted and results were expressed as percent of untreated infected control cells versus concentraton of foscarnet. Results showed that free and liposomal foscarnet have comparable inhibitory activity against CMV p72 protein expression in MRC-5 cell line (Figure 2g) . In vivo studies The pharmacokinetic properties and tissue distribution of free and liposome-encapsulated anti-HIV agents have been investigated in rats. In brief, free and liposome-encapsulated drugs were injected to female Sprague-Dawley rats as a single intravenous bolus dose via a catheter inserted through the jugular vein of animals. At specific time points, animals were sacrificed and blood was collected in heparinized tubes and separated by centrifugation. At the same time, selected tissues were removed, washed, weighed and homogenized. Tissues and plasma were then treated according to a commercial tissue solubilizer procedure. The determination of drug and lipid levels in all samples were monitored with radioactive tracers. Results clearly showed that the encapsulation of the antiviral agents into liposomes resulted in a much higher drug accumulation in macrophage-rich tissues in respect to that observed for unencapsulated drugs (Figures 3a to 31) . The delivery of a greater amount of antiviral agents in these tissues susceptible to HIV infection and the reduced delivery of drugs at sites where it might be potentially toxic should result in an increased efficacy and reduced toxicity of the anti-HIV agents. Of particular interest, we showed that the accumulation of liposomal foscarnet in the lymph nodes was 8 times greater than that of the free agent (Table 2; same formulation as in Figures 3j, 3k and 31: 10 mg foscarnet/kg) . SUBSTITUTE SHEET Table 2: Area under the curve of free and liposome- encapsulated foscarnet in different tissues, following the administration of a single intravenous dose (10 mg foscarnet/kg) in rats. a Tissues Liposomal Free foscarnet Ratio foscarnet L-foscarnet/ free foscarnet Lymph nodes 163.5 20.3 8.1 Brain 40.8 3.1 13.2 Eyes 86.9 22.9 3.8 Spleen 1151.4 0.8 1495.3 Liver 62.5 1.2 52.1 Lungs 59.7 1.5 39.8 a Values, expressed in nmol foscarnet/g tissue/h, were calculated from the mean values of the tissue distribution profile using the trapezoidal rule. An increased drug accumulation was also observed in the brain of animals when liposomal foscarnet rather than the free agent was injected to animals. Such characteristic is of prime importance as severe central nervous system diseases are involved in HIV pathology. In addition, as our data demonstrated an enhanced drug accumulation in the eyes after the injection of liposomal foscarnet rather than the free drug, administration of liposome-encapsulated foscarnet should improve the drug efficacy against CMV in patients infected with HIV and treated for CMV retinitis. Improved pharmacokinetics were also observed upon entrapment of the antiviral agents into liposomes (Tables 3 and 4; same βϋBSTrrUTE SHEET formulations as in Figures 3a to 3e and 3j to 31) . The systemic clearance of the entrapped drugs was found to be much lower than that of the free agents, resulting in a large increase in the elimination half-life of the liposomal drugs. The improved pharmacology of the antiviral agents upon encapsulation in liposomes could hopefully reduce the dose of antiviral agents used in conventional therapy as well as the frequency of administration of the anti-HIV agents improving therefore the quality of life of patients with AIDS and other viral diseases. Table 3: Pharmacokinetic parameters of free and liposomal ddl following the administration of a single intravenous dose (3 mg ddl/kg) in rats. a Parameters Sterically Conventional Free ddl stabilized liposomes liposomes DSPC:DSPG: PEG (10 : 3 : 1.45) DSPC:DSPG (10 : 3) [ 3 H] ddI [ 14 C] DPPC [ 3 H] ddI [ 14 C] DPPC [ 3 H] ddI tι/2 <h> 3.53 14.50 2.64 3.92 0.14 AUCn-oo 950.3 17420 649.9 4971 5.31 (nmol/ml/h) Kβi (h "1 ) 0.20 0.048 0.26 0.18 4.97 Vd ss (1/kg) 0.071 0.077 0.074 0.070 0.48 Cl (1/h/kg) 0.013 0.004 0.020 0.013 2.39 MRT (h) 5.31 21.04 3.79 5.51 0.20 a Parameters were calculated from the plasma concentration-time curves using a noncompartmental model . " ^Abbreviations : tι / 2, elimination hal f-life ; AUCo-oo, area under the plasma concentration-time curve from zero to infinity; K e ι , elimination rate constant ; Vd s s , steady state volume of distribution; Cl, systemic clearance ; MRT, mean residence time . SUBSTITUTE SHEET Table 4: Pharmacokinetic parameters of free and liposome- encapsulated PFA following the administration of a single intravenous dose (10 mg/kg) in rats. a Pharmacokinetic Free foscarnet Liposomal Liposomal parameters^ [ 14 C]-PFA foscarnet lipids [ 1 C] -PFA [ 3 H] -DPPC t i/2 (h) 0 . 71 ± 0 . 04 3 . 06 ± 0 .34 5 . 44 ± 0 . 79 AUC0->-» 48.0 ± 9.6 3687.5 ± 374.2 24277.8 ± 2962.8 (nmol/ml/h) K e i (h-1) 0.96 ± 0.06 0.24 ± 0.03 0.12 ± 0.02 Vd ss (I/kg) 0.80 ± 0.14 0.040 ± 0.004 0.050 ± 0.003 Cl (1/h/kg) 0.77 ± 0.15 0.010 ± 0.001 0.006 ± 0.001 MRT (h) 1.04 ± 0.07 4.52 ± 0.42 7.93 ± 1.12 a Values are expressed as means ± SD obtained from 6 animals per group per time point. ^Abbreviations: tχ/2, elimination half-life; AUCo- > •», area under the plasma concentration-time curve from zero to infinity; K e l, elimination rate constant; Vd ss , steady state volume of distribution; Cl, systemic clearance; MRT, mean residence time. SUBSTITUTE SHEET

Claims: WHAT IS CLAIMED IS ; 1. A formulation of liposomes for the treatment of a viral disease which comprises: i) a lipid component comprising a mixture of diacylphosphatidylcholine and diacylphosphatidylglycerol in a molar ratio ranging between 10:1 and 1:1, wherein the acyl chains are either saturated or unsaturated and have between 14 and 18 carbon atoms in length and ii) a therapeutic amount of an entrapped drug effective against said viral disease. 2. A formulation according to claim 1 wherein said lipid component further comprises a polyethyleneglycol derivative of a diacylphosphatidylethanolamine. 3. A formulation of liposomes for the treatment of a viral disease which comprises: i) a lipid component comprising a mixture of diacylphosphatidylcholine :dicetylphosphate : cholesterol in a molar ratio of 4:1:5, wherein the acyl chains are either saturated or unsaturated and have between 14 and 18 carbon atoms in length and ii) a therapeutic amount of an entrapped drug effective against said viral disease. 4. A formulation according to claim 3 wherein said lipid component further comprises a polyethyleneglycol derivative of a diacylphosphatidylethanolamine. 5. A formulation of liposomes according to claim 1 wherein the entrapped drug is selected from the group consisting of 3'-azido-3 '-deoxythymidine (AZT) , ddl, ddC, foscarnet, ribavirin, ganciclovir and saquinavir. 6. A formulation of liposomes according to claim 5 wherein the lipid component is diacylphosphatidylcholine diacylphosphatidylglycerol in a molar ratio of 10:3. SUBSTITUTE SHEET 7. A formulation of liposomes according to claim 2 wherein the entrapped drug is selected from the group consisting of 3 '-azido-3 '-deoxythymidine (AZT), ddl, ddC, foscarnet, ribavirin, ganciclovir and saquinavir. 8. A formulation of liposomes according to claim 7 wherein the lipid component is diacylphosphatidylcholine: diacylphosphatidylglycerol:diacylphosphatidylethanolamine- polyethyleneglycol in a molar ratio of 10:3:1.45. 9. A formulation of liposomes according to claim 3 wherein the entrapped drug is selected from the group consisting of 3 '-azido-3 '-deoxythymidine (AZT), ddl, ddC, foscarnet, ribavirin, ganciclovir and saquinavir. 10. A formulation of liposomes according to claim 4 wherein the entrapped drug is selected from the group consisting of 3'-azido-3 '-deoxythymidine (AZT), ddl, ddC, foscarnet, ribavirin, ganciclovir and saquinavir. 11. A formulation of liposomes according to any one of the claims 2, 4, 8 and 10 wherein the polyethyleneglycol has a molecular weight comprised between about 500 and about 5000 daltons. 12. A formulation of liposomes according to claim 6 wherein the lipid component is distearoylphosphatidylcholine: distearoylphosphatidylglycerol in a molar ratio of 10:3 and the entrapped drug is 2'-3'-dideoxyinosine. 13 . A formulation of liposomes according to claim 8 wherein the lipid component is distearoylphosphatidylcholine : distearoylphosphatidylglycerol : distearoylphosphat idyl- ethanolamine-polyethyleneglycol in a molar ratio of 10 : 3 : 1.45 and the entrapped drug is 2 ' -3 '-dideoxyinosine . SUBSTITUTE SHEET 14. A formulation of liposomes according to claim 6 wherein the lipid component is dipalmitoylphosphatidylcholine: dipalmitoylphosphatidylglycerol in a molar ratio of 10:3 and the entrapped drug is foscarnet. 15. A formulation of liposomes according to claim 9 wherein the lipid component is dipalmitoylphosphatidylcholine: dicetylphosphate:cholesterol in a molar ratio of 4:1:5 and the entrapped drug is 2'-3'-dideoxycytidine. 16. A formulation of liposomes according to any one of claims 1 to 10 and 12 to 15 having a mean particle diameter comprised between about 0.05 and 0.5 μm. 17. A formulation of liposomes according to claim 11 having a mean particle diameter comprised between about 0.05 and 0.5 μm. 18. A method for the treatment of a viral disease to a subject afflicted thereby comprising the step of administering a formulation of liposomes according to any one of claims 1 to 10, 12 to 15, and 17 to said subject. 19. A method for the treatment of a viral disease to a subject afflicted thereby comprising the step of administering a formulation of liposomes according to claim 11 to said subject. 20. A method for the treatment of a viral disease to a subject afflicted thereby comprising the step of administering a formulation of liposomes according to claim 16 to said subject. SUBSTITUTESHEET

Inventors: BERGERON MICHEL G, DESORMEAUX ANDRE, BERGERON, MICHEL, G., DESORMEAUX, ANDRE
Applicants: BERGERON MICHEL G, DESORMEAUX ANDRE, BERGERON, MICHEL, G., DESORMEAUX, ANDRE
Application year: 1995
Main classification: A61K31
IPC codes: A61K9, A61K31, A61P31