Field of invention

The present invention relates to the preparation and use of reversibly PEGylated

nanocarriers. The reversibly PEGgylated nanocarrier system comprises an inner core comprising or consisting of a nanoparticle and/or at least one pharmaceutical compound; optionally at least one lipid bilayer on the surface of the inner core; a first ligand bound to the surface of said inner core, or if present, to the surface of the at least one lipid bilayer; a second ligand bound to the first ligand, the second ligand being covalently bound to poly(ethylene glycol) or a derivative thereof. The reversibly PEGgylated nanocarrier system is characterized in that binding of the second ligand to the first ligand is non-covalent and reversible. Pharmaceutical compositions and use of such compounds and compositions in the field of e.g. cancer therapy, gene therapy, inflammatory diseases and pain therapy are also disclosed.

Background of invention

Pharmaceutical nanoparticles or nanocarriers, such as liposomes, micelles, etc., are an essential component in the emerging field of nanomedical imaging and therapy. Unmodified pharmaceutical nanoparticles or nanocarriers are typically rapidly shuttled out of circulation to the liver, spleen or bone marrow, and nonspecific binding to non-targeted or non-diseased areas may occur.

In the field of such pharmaceutical nanoparticles/nanocarriers surface coating with polyethylene glycol (PEGylation) has therefore been established as the most popular and elaborated method to prepare drug delivery systems which provide for a prolonged circulation time of the nanoparticles/nanocarriers in the blood. PEGylation protects these carriers from an immediate uptake by the reticuloendothelial (RE) system (macrophage uptake). PEGylated nanocarriers generally accumulate in the liver a half to a third of the amount of non-PEGylated nanocarriers and most importantly demonstrate e.g. higher tumor accumulation versus background.

Such prolonged circulation is often required to provide a sufficient time for effective accumulation of drug-loaded (drug, si NA, pDNA) nanocarriers in target organs or tissues. In this context, PEGylation improves the stability of nanoparticles.

PEG is inexpensive, versatile and is FDA approved for many applications. However, PEGylation of such pharmaceutical nanoparticles/nanocarriers also has some severe drawbacks.

Particularly, the high stabilization of nanoparticles/nanocarriers with PEG leads to prolonged circulation times but most often also results in poor endosomal escape via membrane fusion and in well degradation of cargos in lysosomes, digestive compartments, etc. This problem, also referred to as the 'PEG dilemma', may significantly hamper efficiency of the use of PEG and PEGylated nanoparticles/nanocarriers for drug delivery or in gene delivery.

An example especially demonstrated for passive targeting in cancer tissues is discussed in Allen & Cullis (see Theresa M. Allen, Pieter R. Cullis, Advanced Drug Delivery Reviews 65 (2013) 36-48). As described by Allen and Cullis (2013) "Long circulating (PEGylated) liposomes were shown to have extensive accumulation in Kaposi's sarcoma and head and neck cancers, with intermediate accumulation in lung cancer and lower accumulation in breast cancer in an initial study using small numbers of patients. However, to draw specific conclusions about the relationship between tumor types, stage of tumor development and liposome accumulation these studies need to be repeated with larger cohorts. The extent of liposomal accumulation may be related, at least in part, to the degree of angiogenesis of the tissues." ... "In clinical applications, liposomal drugs have been proven to be most useful for their ability to

"passively" accumulate at sites of increased vasculature permeability, when their average diameter is in the ultrafilterable range (200 nm in diameter), and for their ability to reduce the side effects of the encapsulated drugs relative to free drugs. This has resulted in an overall increase in therapeutic index, which measures efficacy over toxicity."

Also Hatakeyama et al. (see Hatakeyama et al., Advanced Drug Delivery Reviews 63 (2011)) found that PEGYIation is a useful tool but hampered by slow or even minimal endosomal release of the targets. Hatakeyama et al. (2011) noted that "despite the great success of delivering chemotherapeutic drugs to tumors using PEGylated nanoparticles via passive targeting based on the EPR effect, PEGylation hampers in vivo applications of nanoparticles as gene carriers of pDNA and siRNA to tumor delivery. For pDNA or siRNA to be therapeutically efficacious, gene carriers must deliver their cargos to the appropriate intracellular compartment where pDNA or siRNA functions, that is, the nucleus or the cytosol. They must pass through the cell membrane and undergo sequential endosome/lysosome degradation, unlike chemotherapeutic drugs such as doxorubicin, which spontaneously accumulate in the nucleus due to their capability to intercalate into double-stranded DNA. The surface aqueous phase formed by the PEG moiety inhibits the interaction of the gene carrier with the tumor cell surface. As a result, cellular uptake is nil or minimal.

In sum, PEGylation is a useful method for achieving a longer circulation time for delivery to a tumor via the enhanced permeability and retention effect. However, PEGylation strongly inhibits cellular uptake and endosomal escape, which results in significant loss of activity for the delivery system. For successful drug delivery for cancer treatment, the crucial issue associated with the use of PEG, the 'PEG dilemma', must be addressed successfully.

Several attempts have been carried out meanwhile to provide PEGylated

nanoparticles/nanocarriers which address the 'PEG dilemma'. Such attempts comprise both passive targeting but also a triggered release of PEG from PEGylated

nanoparticles/nanocarriers upon providing a "cleavable" PEG system.

In this regard in Allen & Cullis (2013) summarized in their review presently available methods, which allow releasing the target of such PEGylated nanoparticles/nanocarriers either upon a local or an external stimuli. In this context two main types of triggers have been explored, remote triggers such as heat, ultrasound and light, and local triggers that are intrinsic to the disease site or cellular organelles such as enzymes and pH changes. Such triggers particularly comprise triggers based on induction of hyperthermia: Temperature dependent PEG cleavage (local, e.g. increased temperature in inflamed or neoplastic tissue, or externally applied), pH dependent PEG cleavage (local, e.g. low pH in tumor tissue), enzymatic cleavage by system specific (local) proteases (phospholipases, alkaline phosphatase, metalloproteionases); s.a. patent CN: metalloproteinase secreted by tumor cells, ultrasonic release (externally applied; remote trigger), light or magnetically triggered (externally applied; remote trigger), combinations of the above, or a combination of such triggers with targeting agents (e.g. Hyperthermia-triggered & Her2 -targeted intracellular doxorubicin delivery ).

However, even though such triggers appeared to provide a good alternative to release PEG in the cells to facilitate endosomal release, such approaches have been disappointing in practice as also documented by Allen & Cullis (2013). Particular drawbacks of current cleavable PEG systems are inter alia that local stimuli like e.g. pH, temperature are not switchable systems on demand and are typically quiet weak, thus resulting in a poor efficiency. If switchable systems are used these are often hindered by the PEG shell (e.g. when using proteases as a trigger), they are not easy to administrate in deep-tissue regions (e.g. when using light, temperature or ultrasonic as a trigger) and in case the liposomes are destroyed, release occurs outside the cells (e.g. when using temperature or ultrasonic as a trigger). Also, metastatic disease is a common cause of death in advanced cancer, but small metastatic tumors are not accessible via remote triggers. Hence, applications for remote triggered formulations should be carefully chosen and would include such applications as locally advanced disease and cancer where tissue sparing is preferred for reasons of preserving quality of life

Hence, no suitable applications have yet been presented in the prior art for efficiently overcoming the PEG dilemma, based on the manipulation of intracellular trafficking of cellular uptake and endosomal release using functional devices such as specific ligands or cleavable PEG systems.

It is therefore the object of the present invention to provide a PEGylated nanocarrier system which allows to efficiently aid transport to and preferably also allows to release its target at the site of treatment and thereby at least in part overcomes the PEG dilemma as described before. For a complete understanding of the present invention and the advantages thereof, reference is made to the following detailed description taken in conjunction with the accompanying figures and examples.

Summary of invention

The present invention pertains to a reversibly PEGylated nanocarrier system comprising: an inner core comprising a nanoparticle and/or at least one pharmaceutical compound;

optionally at least one lipid bilayer on the surface of the inner core; a first ligand bound to the surface of said inner core, or if present, to the surface of the at least one lipid bilayer; a second ligand bound to the first ligand, the second ligand being covalently bound to poly(ethylene glycol) or a derivative thereof, characterized in that binding of the second ligand to the first ligand is non-covalent and reversible. Such reversibility can be achieved in vitro and in vivo and is preferably triggered upon addition of a non-bound excess amount of the first ligand or the second ligand to the reversibly PEGylated nanocarrier system, or by addition of any other competitively acting ligand, leading to a competitive release of the second ligand and hence of the PEGylation. Further preferred aspects are outlined below. According to a further embodiment, the present invention provides a pharmaceutical composition comprising the inventive reversibly PEGylated nanocarrier system as described herein and optionally a pharmaceutically acceptable carrier and/or vehicle.

According to another embodiment, the present invention discloses the use of the inventive reversibly PEGylated nanocarrier system as a medicament.

Likewise, according to a further embodiment the present invention discloses the use of the inventive reversibly PEGylated nanocarrier system in cancer therapy or in gene therapy. Further preferred aspects of the inventive embodiments are outlined below and in dependent claims. Brief description of Figures

The following Figures shall illustrate the above described invention in further detail and are not intended to limit the scope of the claims thereto.

Figure 1: shows the setup of the inventive reversibly PEGylated nanocarrier system.

Nanocarriers carrying a first ligand, e.g. fluorescein, on the surface are bound by PEGylated FITC-E2 (scFv) as a specific FITC binding protein with high specificity, the FITC-E2 (scFv) acting as a second ligand as defined herein to which PEG is covalently bound. This set up leads to a protection of the nanoparticle and/or pharmaceutical compound (inner core) and a controlled release. Controlled release can be achieved by addition of an excess of free (first) ligand (e.g. again fluorescein, or any other competitively acting ligand), wherein the competing effects lead to a disruption of the interaction between the first and second ligand, e.g. PEGylated scFv and the fluorescein bound on the nanocarrier. The nanocarrier can be also provided with at least one lipid bilayer around the inner core, wherein the first ligand is then preferably bound to the lipid bilayer. Figure 2: shows a 12% SDS PAGE of the FITC-E2. MM represents the molecular marker.

scFv represents FITC-E2, scFv+PEG represents the single short chain fragment FITC-E2 modified with PEG (PEGylated; In lane "scFV" 20 μΙ FITC-E2 (18mg/ml) were loaded in the corresponding lane. In the lane "scFv+PEG" scFv was reacted with 6x excess of NHS-mPEG2000 with the same loading conditions as for scFv.

Figure 3: shows a test of the functionality of the inventive reversibly PEGylated

nanocarrier system on THP-1 cells. For this purpose, THP-1 cells were incubated 90 minutes with different formulations of liposomes (liposomes, liposomes + scFv-PEG or liposomes + scFv-PEG + fluorescein) or just buffer (HEPES). Cells were washed three times with PBS 37 °C and then detached with PBS + 2 mM EDTA. The resulting fluorescence of THP-1 cells was afterwards determined with a flow cytometer.

As could be seen in Figure 3, the fluorescence of the cells correlates with the uptake of DiD stained liposomes. The determined uptake rate is comparable with the figures obtained with "normal" PEGylated liposomes (see Blume G, Cevc G (1990) Biochim Biophys Acta, 1029(l):91-7), and is nearly 100% reversible after addition of fluorescein to a final concentration of 1 mM. shows fluorescein-dependent scFv-PEG de-shielding of the nanocarrier (liposome) in the presence of THP-1 cells. THP-1 cells were incubated 90 minutes with bare liposomes or liposomes with scFv-PEG and different concentrations of fluorescein (500 μΜ, 250 μΜ, 125 μΜ, 60 μΜ, 30 μΜ, 15 μΜ and just HEPES-buffer). Cells were washed three times with PBS 37 °C and then lysed with HEPES 2% Triton-X. The uptake was quantified by measuring the DiD fluorescence, which the liposomal membranes were stained with (L: liposomes; F: fluorescein). shows a test of different concentration of scFv-PEG to provide the scFv-PEG shell protection to the nanocarrier (liposome) in the presence of THP-1 cells. THP-1 cells were incubated 90 minutes with bare liposomes or liposomes with different scFv-PEG concentrations (5mol%-PE-FITC in liposomal membrane; molar ratio scFv-PEG:PE-FITC: 1:2; 1:1; 2:1, 4:1, or BSA 4:1). Cells were washed three times with PBS 37 °C and then lysed with HEPES 2% Triton-X. The uptake was quantified by measuring the DiD fluorescence, which the liposomal membranes were stained with (L: liposomes). shows a test of the functionality of the inventive reversibly PEGylated nanocarrier system in a CHO-cell proliferation assay. For this purpose, CHO cells were incubated 4 hours with doxorubicin or doxorubicin loaded liposomes in combination with the protective shell with or without the addition of fluorescein (HEPES, Doxorubicin, Doxorubicin liposomes + scFv- PEG or doxorubicin liposomes + scFv-PEG + fluorescein). Cells were washed three times with PBS 37 °C and then further cultivated for 24 h. To quantify the cell proliferation a WST-1 assay (Roche) was performed. Figure 7: Plasma half-life of doxorubicin loaded into liposomes with PEGylated scFv in

Rattus norvegicus (dosage 3.75 mg/rat). A prolonged half-life (19.5 h) of the protected liposomal doxorubicin can be seen compared to literature data for free doxorubicin (<lh) or liposomal, unprotected, doxorubicin (l-2h).

Detailed description

The object underlying the present invention has been solved by the attached independent claims. Further preferred embodiments are defined in the dependent claims as attached. However, It should be appreciated that the various aspects of the disclosure herein are illustrative of the specific ways to make and use the invention and do not limit the scope of the invention when taken into consideration with the claims and the following detailed description. It will also be appreciated that features from one aspect of the invention may be combined with features from another aspect of the invention.

A first embodiment of the present invention is directed to a reversibly PEGgylated nanocarrier system. The inventive system comprises:

an inner core comprising or consisting of a nanoparticle and/or at least one pharmaceutical compound;

- optionally at least one lipid bilayer on the surface of the inner core;

a first ligand bound to the surface of said inner core, or if present, to the surface of the at least one lipid bilayer;

a second ligand bound to the first ligand, the second ligand being covalently bound to poly(ethylene glycol) or a derivative thereof,

characterized in that binding of the second ligand to the first ligand is non-covalent and reversible. Reversibility is preferably triggered upon addition of a non-bound excess amount of the first ligand or the second ligand to the reversibly PEGgylated nanocarrier system or by addition of any other competitively acting ligand. The inventive reversibly PEGgylated nanocarrier system provides a multiplicity of advantages over systems of the art.

Generally, the inventive reversibly PEGgylated nanocarrier system provides a PEGylated carrier which efficiently accumulates at least passively in the selected target tissue. Upon administration of an excess of free ligand (remote trigger) the cargo is more easily released. The inventive reversibly PEGgylated nanocarrier system also allows providing a (targeted or passive) interaction with surrounding tissue since the inventive system is a highly modular system and can be adopted to a variety of pharmaceutical compositions and be selected to target selectively a certain target region. In the context of the inventive reversibly

PEGgylated nanocarrier system a large variety of nanocarriers are applicable, e.g. liposomal Doxirubicin, etc., wherein the components of the herein described first ligand - second ligand system are highly exchangeable. Particularly the herein outlined exemplary first ligand - second ligand systems, e.g. second ligand FITC-E2 scFV and first ligand fluorescein, are safe and approved for humans. The interaction of the components of these selected first ligand - second ligand systems nevertheless is highly specific and reversible. Since the second ligand is covalently bound to PEG, the inventive nanocarrier system is effectively PEGylated via its interaction between the first and the second ligand, but at the same time allows to efficiently detach its PEGylation at the target region or any desired location upon adding a specific trigger as described herein and thereby to release its cargo.

Advantageously, the interaction between the components of the selected first ligand - second ligand systems can be disrupted again by competing the binding with addition of e.g. free first ligand or second ligand or any other competitively acting ligand, which then represents an externally applied, effective trigger. Such a trigger can be administered at any desired, most beneficial point of time. Such a trigger is highly independent of local tissue specific factors and may even allow targeting small metastatic tumors. The inventive

PEGylation system can therefore be released on demand, which results in increased drug specificity and hence also in reduced drug-related side effects, reduced adverse body reactions against PEGylated particles due to shortened circulation after triggered release, etc. Furthermore, different and preferably optimized rates of PEGylation could be adjusted and the preferential cargo can be selected from a variety of small molecule anticancer drugs either individually or in combination.

In the context of the present invention the term "PEGylated" refers to the modification of a herein described nanocarrier system with a poly(ethylene glycol) (PEG) or a derivative thereof, preferably using the herein described system of first and second ligands and their combinations as outlined below. In the context of the present invention a "reversibly PEGylated nanocarrier system" is preferably to be understood as a PEGylated nanocarrier system, wherein poly(ethylene glycol) (PEG) or a derivative thereof has been attached to the herein described nanocarrier system such that the attachment is reversible. Such a reversible attachment typically occurs via a non-covalent bond, such as via electrostatic interactions, van-der-Waals interactions, etc., or any further interactions to be subsumed as a non-covalent bond. The reversible attachment in the context of the present invention is specifically based on the (non-covalent) interaction between the corresponding first and second ligands as described herein. Since the second ligand is covalently bound to PEG or a derivative thereof the reversibility and the detachment of PEG or a derivative thereof can be induced upon addition of a non-bound excess amount of the first ligand or of the second ligand to the reversibly PEGgylated nanocarrier system, or by addition of any other competitively acting ligand. This addition leads to a competitive release of the interaction between the first and the second ligand and hence to a release of the PEGylation.

In the context of the present invention the term "covalent", e.g. in terms "covalent bond" or "covalent binding", preferably means any covalent bond known to a skilled person. A covalent bond as defined herein may be formed by chemical reactions known to a skilled person, e.g. by adding chemical groups, able to react with each other or a functional group and thereby forming a chemical bond. Examples of such coupling reactions are known to a skilled person and reviewed e.g. in the publication Bioanalytik", Springer Verlag, Lottspeich, Friedrich; Engels, Joachim W. (publisher), chapter 7, Chemische Modifikation von Proteinen und Proteinkomplexen. Likewise, in the context of the present invention a "nanocarrier system" is preferably to be understood as a transport system for nanoparticles and/or at least one or more

pharmaceutical compound(s), wherein the nanoparticles in the context of the present invention are provided such as to exhibit a size in the range of several nanometers and preferably of less than 1 μιτι, as further defined below. Hence, the inventive reversibly PEGylated nanocarrier comprises an inner core comprising or consisting of a nanoparticle and/or at least one pharmaceutical compound. The inner core may be solid or semi-solid/semi-liquid. The inner core may also be hollow or non-hollow. Such a nanoparticle in the context of the present invention may be any type of particle and preferably defines particles with a spherical or substantially spherical shape typically between 10 and 1000 nm, more preferably with a size of between 10 to 800 nm, more preferably between 10 and 600 nm, even more preferably between 50 and 400 nm. Such a nanoparticle may be preferably selected from solid or semi-solid/semi-liquid particles. Solid particles may be, for example, selected from or formed by chemical or pharmaceutical compounds, which are provided in a nanoparticulate form. Preferably, the term

"pharmaceutical compound" as defined herein is to be understood as a "pharmaceutically active compound". Such a chemical or pharmaceutical compound may be any suitable chemical or pharmaceutical compound as defined as described herein below. Solid particles also may be selected or prepared from compositions of the at least one or more chemical or pharmaceutical compounds, e.g. a mixture of the at least one or more chemical or pharmaceutical compounds, which are preferably provided in a nanoparticulate form. Solid particles may also comprise or be formed by polymers, e.g. mixtures of such chemical or pharmaceutical compounds or compositions thereof with polymers, preferably hydrophilic polymers selected e.g. from PEG, PLA, PLGA, etc. The nanoparticle may be furthermore comprise Dextran, e.g. Dextran beads, inert compounds, polymers selected e.g. from PEG, PLA, PLGA, etc. Semisolid/semi-liquid particles may be obtained e.g. from solutions or preferably highly viscous solutions, either with or without such a chemical or pharmaceutical compound as defined herein below, or from solutions, such as e.g. highly viscous solutions, formed e.g. by polymers, preferably hydrophilic polymers selected e.g. from PEG, PLA, PLGA, etc. Nanoparticles may be also selected from vesicles. Likewise, the vesicles may comprise a pharmaceutical compound as described herein below. Preferably, the nanoparticle contained in the inner core is hydrophilic or lipophilic at its outer surface.

The inner core may likewise comprise directly at least one pharmaceutical compound as defined herein below. Typically, the at least one pharmaceutical compound may be provided as a nanoparticle as described before. However, the at least one pharmaceutical compound may also be provided in form of a powder, e.g. a nanopowder, or as a fine or ultrafine powder, or as agglomerates of ultrafine particles, nanoclusters, nanocrystals. Likewise, the at least one pharmaceutical compound may be liquid or semi-liquid/semi-solid, and/or may be formulated as a suspension, e.g. with higher viscosity, so as to form a nanoparticle material. Preferably, the at least one pharmaceutical compound contained in the inner core is hydrophilic or lipophilic.

Exemplary pharmaceutical compounds or pharmaceutically active compounds include, without being limited thereto, e.g. tumorigenic agents such as 2,4,6-triethylene melamine compound, 6-mercaptopurine, ACNU, actinomycin D, adenosinediialde-hgde, adriamycin, AE- 941, AG3340, andaminopterin, anti-VEGF antibody, Bay 12-9556, BCNU, bleomycin, BM S- 275291, busulfan, CA I, camptothecin, carboplatin, CCNU, Chlorambucil, cisplatin, COL-3, cyclophosphamide, cytarabine, dacarbazine, dasatinib, daunorubicin, doxorubicin, EMD 121974, endostatin, epirubicin, erlotinib, etoposide, floxuridine, fluorouracil, ftorafur, furtulon, gefitinib, guanazole, harringtonine, HXM, hydroxy camptothecin, hydroxyurea, ifosfamide, IM8624, imatinib, indirubin, inosine dialdehyde, interferon [alpha], interleukin 12, irinotecan, lapatinib, liposomal p53 DNA, marimastat, methotrexate, methyl CCNU, mithramycin, mitomycin A, mitomycin B, mitomycin C, mitoxantrone, navelbine, neovastat, nilotinib, nitrogen mustard, N-methyl-N-nitrosourea, olivomycin, oxaliplatin, paclitaxel, pingyangmycin, pirarubicin, PKN3siRNA, procarbazine, sorafenib, squalamine, streptozotocin, SU5416, SU6668, sunitinib, suramin, taxotere, tegadifur, tegafur-uracil, thalidomide, thiotepa, TNP-470, vinblastine, vincristine, vindesine, vinorelbine, vitaxin, etc.,

gene therapeutic agents, such as DNA, pDNA, RNA, siRNA, miRNA, or a combination thereof, preferably encoding a therapeutic protein, or any further suitable protein, etc.

The nanoparticle and/or at least one pharmaceutical compound forms an inner core of the inventive reversibly PEGylated nanocarrier system. Such an inner core preferably has a spherical or substantially spherical shape, preferably of a size as described above for the nanoparticle, more preferably with a size of between 10 to 1000 nm, more preferably between 10 and 800 nm, even more preferably between 50 and 600 nm or even between 50 and 400 nm. In the context of the inventive reversibly PEGylated nanocarrier system a "spherical or substantially spherical shape" is not necessarily limited to regular globular forms but may also comprise more irregularly shaped forms, ellipsoid formed spheres, etc.

The inner core of the reversibly PEGgylated nanocarrier system may comprise optionally at least one lipid bilayer, the (first) lipid bilayer preferably attached on the surface of the inner core. Such a lipid bilayer is typically prepared by a skilled person following established techniques in the art. A lipid bilayer as preferably used in the context of the present invention is typically formed by phospholipids, cholesterol, and/or glycolipids, wherein phospholipids usually form the basic component of such lipid bilayers. Compounds used in this context include either naturally occurring or synthetic phospholipids, e.g. naturally occurring phospholipids, such as e.g. lecithin or phosphatidylcholin, modified naturally occurring phospholipids, such as e.g. hydrated phosphatidylcholin, semisynthetic phospholipids, such as phospholipids with modified alkylchains and full synthetic phospholipids. Preferably, phospholipids, without being limited thereto, may be selected from the group consisting of DSPE (l,2-distearoyl-sn-glycero-3-phosphoethanolamine), PI (phosphatidyl inositol), PS (phosphatidyl serine), DPG (bisphosphatidyl glycerol), PA (phosphatidic acid), PEOH (phosphatidyl alcohol), PG (phosphatidyl glycerol), phosphatidylcholin, hydrogenated soy phosphatidylcholin (HSPC), dimyristoyl phosphatidylcholine (DMPC), etc.

More preferably, without being limited thereto, the phospholipid is a phosphoethanolamine and/or a phosphatidylcholin, most preferably DSPE (l,2-distearoyl-sn-glycero-3- phosphoethanolamine) and/or hydrogenated soy phosphatidylcholin (HSPC). Even more preferably, formation of a lipid bilayer occurs by using cholesterol and a phospholipid as defined before, most preferably cholesterol, DSPE (l,2-distearoyl-sn-glycero-3- phosphoethanolamine) and hydrogenated soy phosphatidylcholin (HSPC), or any derivative thereof, such as modified HSPC, modified cholesterol or modified DSPE, as further explained below.

An optional at least one lipid bilayer as described herein may be a unilamellar or a multilamellar lipid bilayer. Hence, on the inner core of the inventive reversibly PEGylated nanocarrier system an unilamellar or a multilamellar liposome may be formed, preferably selected from MLV, SUV and LUV as further defined below. In case that only one lipid biliayer is defined herein, such one lipid biliayer is preferably arranged on the inner core in form of a unilamellar liposome. In case that more than one lipid biliayer is defined herein, such lipid biliayers are preferably arranged on the inner core in form of a multilamellar liposome. In the inventive context multilamellar liposomes (MLV) in the context of the present invention usually range from 500 to 10,000 nm. Unilamellar liposomes in the context of the present invention can be distinguished into small (SUV) and large (LUV) unilamellar liposomes. SUV are usually smaller than 50 nm and LUV are usually larger than 50 nm. Liposomes of very large size are called giant liposomes (10,000 - 1,000,000 nm), which may be also formed within the context of the present invention. Such giant liposomes can be either unilamellar or multilamellar. Liposomes containing encapsulated vesicles are called multi-vesicular liposomes and are also encompassed by the present invention. Their size typically ranges from 2,000-40,000 nm. The optional at least one lipid bilayer may be formed on the inner core of the inventive reversibly PEGylated nanocarrier system by any method known to a skilled person. MLV may be prepared e.g. following the hydration method or the solvent spherule method. SUV may be prepared following e.g. the sonication method or the French Pressure method. LUV may be prepared using e.g. either the REV method, the modified REV method, the Freeze Thaw method, the microfluidization method or using a method based on extrusion through polycarbonate filters under nitrogen. Industrial methods for preparing the at least one lipid bilayer include inter alia Detergent Dialysis, Microlluidization, Proliposomes, Lyophilization, etc. Reference with regard to any of these methods is explicitly made in this regard to the publication of RIAZ (1996) (see RIAZ, Pakistan Journal of Pharmaceutical Sciences, Vol.19(1), January 1996, pp.65-77), the respective disclosure of which is entirely incorporated by reference with respect to the type of liposomes and their methods of preparation, particularly as referred to on pages 68 to 75. Other methods suitable for preparing the at least one lipid bilayer are likewise preferred. According to the present invention, the inventive reversibly PEGylated nanocarrier system comprises a first ligand bound to the surface of said inner core as defined above. Alternatively, if a lipid bilayer is present as defined above, a first ligand may be bound to the surface of said at least one lipid bilayer.

In the context of the present invention, such a first ligand is preferably selected from the

following first ligand/second ligand combinations, wherein the first ligand specifically but reversibly binds the second ligand upon addition of the first ligand to the second ligand, or vice versa. In this context, a first ligand/second ligand combination is typically to be

understood as a combination of ligands wherein a first ligand, e.g. a protein, such as a

restriction enzyme, specifically recognizes and reversibly binds to a second ligand, e.g. its specific DNA recognition sequence. Alternatively, a first ligand, e.g. an enzyme, is specifically bound by a second ligand, e.g. its specific inhibitor. These bonds are reversible, preferably non-covalent, and typically can be released again by competitive binding. Such a reversible attachment of a first ligand to the second ligand thus both allows binding and also

competitive binding of a first ligand to a second ligand as defined herein. Hence, according to one aspect of the present invention preferred first ligand/second ligand combinations may be selected from the following combinations, without being limited thereto:

First ligand Second ligand

Fluorescein, FITC scFv fragment FITC-E2

Fluorescein, FITC scFv fragment FITC-E2 according to SEQ ID NO: 1 or 19 or a sequence showing at least 80% identity to the sequence of SEQ ID NO: 1 or 19

Fluorescein, FITC FluA

coumarin antibiotics, selected from GyrB (DNA gyrase subunit B from Escherichia aminocoumarin antibiotics including novobiocin, coli)

chlorobiocin, coumermycin and

dihydronovobiocin, preferably novobiocin

coumarin antibiotics, selected from GyrB (DNA gyrase subunit B from Escherichia aminocoumarin antibiotics including novobiocin, coli) according to SEQ ID NO: 2 or a sequence chlorobiocin, coumermycin and showing at least 80% identity to the sequence of dihydronovobiocin, preferably novobiocin SEQ ID NO: 2 Heparin HBP (Heparin binding protein)

Rapamycin, FK506 and derivatives, FK1012, FKBP (FK-binding protein)

rapalogs, mTOR inhibitors;

Rapamycin, FK506 and derivatives, FK1012, FRB (FKBP-rapamycin-binding domain) rapalogs, mTOR inhibitors

Rapamycin, FK506 and derivatives, FK1012, F _M (F36M mutation of FK-binding protein) rapalogs, mTOR inhibitors

Cyclosporins, ascomycins, and derivatives Cyp (Cyclophilin)

thereof

Methotrexate, and derivatives thereof, DHFR (dihydrofolate reductase) antifolate, DHFR-inhibitors;

Biotin, biotin analog Streptavidin

Biotin, biotin analog Avidin

Biotin, biotin analog Neutravidin

Biotin, biotin analog, digoxin DigA

steroid hormones, steroid hormone analogs steroid hormone receptors

Virstatin ToxT (ToxT Protein of V. cholerae)

ETR (operator ETR of MphR(A) protein) MphR(A) protein

operator PIR PIP protein of Streptomyces pristinaespiralis operator tetO TnlO-derived tetracycline repressor TetR operator argO arginine-responsive repressor ArgR operator arsO arsenic-responsive repressor ArsR operator hucO uric acid- responsive repressor HucR

Salicylic Acid Salicylic Acid Binding Protein 2 (SABP2)

PGP1, Quercetin FKBP42

In the above context also suitable compounds to dissolve the interaction between the first ligand and the second ligand as described in the above context, also include, for example, macrolide antibiotics (for E - ETR), streptogramin antibiotics (for PIP - PIR), tetracycline antibiotics (for TetR - tetO), arginine (for ArgR - argO), heavy metals (for ArsR - arsO), and u acid (for HucR - hucO). In the above context, a cyclosporin or an ascomycin can be, for example, Cyclosporin A (NEO AL( )), ISAtx- 247, FK506 (tacrolimus), FK778, ABT-281 or ASM981. An mTOR inhibitor can be, for example, rapamycin or a derivative thereof, e.g. Sirolimus (RAPAMUNE(R)), Deforolimus, Temsirolimus, Zotarolimus, Everolimus (Certican(R)), CCI779, ABT578, biolimus- 7, biolimus-9, a rapalog, e.g.AP23573, azathioprine, campath 1 H, a SI P receptor modulator, e.g. FTY720, or an analogue thereof. Rapalogs may include, among others, variants of rapamycin having one or more of the following modifications relative to rapamycin:

demethylation, elimination or replacement of the methoxy group at C7, C42 and/or C29; elimination, derivatization or replacement of the hydroxy group at C13, C43 and/or C28; reduction, elimination or derivatization of the ketone function at C14, C24 and/or C30; replacement of the 6-membered pipecolate ring with a 5-membered prolinyl ring; and alternative substitution on the cyclohexyl ring or replacement of the cyclohexyl ring with a substituted cyclopentyl ring. Further modifications considered are presented in the background sections of U.S. Pat. Nos. 5,525,610; 5,310,903 and 5,362,718, and also in U.S. Pat. No. 5,527,907. Further considered is selective epimerization of the C28 hydroxy group (WO 01/14387). Further considered is the use of rapamycin analogs containing various phosphorus-containing moieties, such as described in WO 03/064383 and WO 05/16252. Other rapalogs considered are described in US Pat. No. 6,984,635, US Pat. No. 6,649,595 and US Pat. No. 7,091,213. Antifolates may include, for example, compounds binding to DHFR like, for example, methotrexate, trimethoprim, diaminopyrimidines like brodimoprim and epiroprim, or iclaprim. Other DHFR inhibitors considered are those described in Hawser S. et al., Biochemical Pharmacology 71, 941-948, 2006. Finally, Biotin analogs may include, for example, compounds binding to streptavidin, neutravidin or avidin like, for example, biotin, HABA, desthiobiotin, iminobiotin or diaminobiotin.

The above defined "first ligands" and the above defined "second ligands" of a first ligand/second ligand combination as defined may also be interchanged, i.e. the first ligand may be used as a second ligand and the second ligand may be used correspondingly as a first ligand. According to a particularly preferred aspect, the second ligand as defined herein is selected from scFv fragment FITC-E2 and fluorescein compound FITC is selected as a first ligand. More preferably the first ligand/second ligand combination as defined herein is selected from the scFv fragment FITC-E2 according to SEQ ID NO: 1 as a second ligand and FITC as a first ligand. In this context, the scFv fragment FITC-E2 is a single chain variable fragment (scFv) of an antibody directed against fluorescein as published in Vaughan et al. 1996 (see Vaughan et al., (1996), Nat. Biotechnol 14 (3), S. 309-314). Such an scFv may be recombinantly produced as a C-terminal hexahistidine tagged version in established expression systems as described for example by Pedrazzi et al., (1997), FEBS Lett lb (3), S. 289-293), which shows an expression in the periplasm of E.coli, or by ippmann et al., (1998), Appl. Environ. Microbiol 64 (12), S. 4862-4869), which shows an expression in L-form cells of Proteus mirabilis. Expression in either E. coli or Proteus mirabilis is particularly preferred. A preferable protein sequence of the second ligand may be the amino acid sequence of the produced scFv as shown in SEQ ID NO: 1 or 19 (sequence depicted after removal of the periplasmic signal sequence), or an amino acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the sequence according to SEQ ID NO: 1 or 19. The first ligand bound by such a scFv fragment FITC-E2 is fluorescein, particularly FITC, and eventually also a derivative thereof. According to another particularly preferred aspect, the second ligand as defined herein is selected from GyrB, preferably from DNA gyrase subunit B from Escherichia coli, more preferably from the N-terminal sequence of DNA gyrase subunit B from Escherichia coli, even more preferably from the N-terminal sequence of DNA gyrase subunit B from Escherichia coli according to SEQ ID NO: 2, or an amino acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the sequence according to SEQ ID NO: 2, or may be encoded by a nucleic acid sequence according to SEQ ID NO: 3 or a nucleic acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the sequence according to SEQ ID NO: 3. The first ligand bound by GyrB as defined above in this context is preferably selected from a coumarin antibiotics, preferably selected from aminocoumarin antibiotics, including novobiocin, chlorobiocin, coumermycin and dihydronovobiocin, preferably novobiocin or any further compound capable of binding to DNA gyrase subunit B from Escherichia coli as defined above.

According to a further preferred aspect, the first ligand/second ligand combinations may be selected from any member of the lipocalin family or from further suitable proteins binding any of the proteins of the following first ligand/second ligand combinations: FluA - fluorescein, DigA - Biotin- digoxin - conjugate, Salicylic Acid Binding Protein 2 (SABP2) - Salicylic Acid, or from proteins interacting with each other such as FKBP42 and PGP1, which further interact with Quercetin as a competitor. Bonds formed between these first ligand/second ligand combinations may be dissolved again using stimuli that are licensed for human use and not harmful to the human organism.

In the inventive context, FluA is preferably understood as an artificial lipocalin with a high substrate specificity towards fluorescein. Preferably, FluA is selected from an amino acid sequence according to SEQ ID NO: 5 or an amino acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the sequence according to SEQ ID NO: 5, or may be encoded by a nucleic acid sequence according to SEQ ID NO: 4 or a nucleic acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the sequence according to SEQ ID NO: 4.

Furthermore, in the context of the present invention, DigA is preferably understood as an artificial lipocalin, which, however, comprises an engineered affinity towards digoxin. Preferably, DigA is selected from a sequence according to SEQ ID NO: 7, or an amino acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the sequence according to SEQ ID NO: 7, or may be encoded by a nucleic acid sequence according to SEQ ID NO: 6 or a nucleic acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the sequence according to SEQ ID NO: 6. Additionally, SABP2 belongs to the SABP2/SABP2-like family. This family includes several members that are not binding salicylic acid. Some display affinity towards stress-associated hormones like jasmonic acid or abscisic acid. In addition sequence analysis identified several plant hydroxynitrile lyases and lecithin (phosphatidylcholine) cholesterol acyl transferases from animals which are classified as SABP2L proteins.

In the context of the present invention, the Salicylic Acid Binding Protein 2 (SABP2) is preferably derived from tobacco and plays an important role in the plants systemic acquired resistance (SA ) which is comparable to the immune response in animals. Preferably, SABP2 is selected from an amino acid sequence according to SEQ ID NO: 9, from an amino acid sequence according to SEQ ID NO: 11 or from an amino acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the sequence according to SEQ ID NO: 9 or 11, or may be encoded by a nucleic acid sequence according to SEQ ID NO: 8, a nucleic acid sequence according to SEQ ID NO: 10, or a nucleic acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the sequence according to SEQ ID NO: 8 or 10. SEQ ID NO: 11 (amino acid sequence) comprises an S81A mutation in the sequence according to SABP2 as defined before. SEQ ID NO: 10 is the encoding nucleic acid sequence.

Additionally, most of FKBP family members bind FK506 and exhibit peptidylprolyl cis/trans isomerase (PPIase) activity (Kang, Cong Bao, Ye Hong, Sirano Dhe-Paganon, Ho Sup Yoon. "FKBP family proteins: immunophilins with versatile biological functions." Neuro-Signals 16 (2008) 318-25). FKBP42 is a FK506 binding protein. PGP1 belongs to the family of multidrug- resistance proteins (MDRs) or P-glycoproteins, a subgroup of the full-size ABC transporters. ABC transporters implicated in detoxification and ion-regulation processes as well as plant growth processes (Enrico Martinoia, Markus Klein, Markus Geisler, Lucien Bovet, Cyrille Forestier, Uner Kolukisaoglu, Bernd M uller-Rbber, Burkhard Schulz. "Multifunctionality of plant ABC transporters - more than just detoxifiers." Planta 214, (2002) 345-355).

In the context of the present invention the protein FKBP42 is preferably the Arabidopsis FK506 binding protein (FKBP42), which interacts with the C-terminal domain of Arabidopsis multidrugresistance-like ABC transporter AtPGPl. Preferably, FKBP42 is encoded by the nucleic acid sequence according to SEQ ID NO: 12 or is selected from an amino acid sequence encoded thereby, or from a nucleic acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the nucleic acid sequence according to SEQ ID NO: 12, or an amino acid sequence encoded thereby, or may be selected from an amino acid sequence according to SEQ ID NO: 14, or from an amino acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the amino acid sequence according to SEQ ID NO: 14, or may be encoded by a nucleic acid sequence according to SEQ ID NO: 13, or a nucleic acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the sequence according to SEQ ID NO: 13. SEQ ID NO: 14 (amino acid sequence) comprises aa 1-163 of the encoded aa sequence according to SEQ ID NO: 12 as defined before. SEQ ID NO: 13 is corresponding the encoding nucleic acid sequence.

Likewise preferably, AtPGPl is selected from an amino acid sequence according to SEQ ID NO: 16, from an amino acid sequence according to SEQ ID NO: 18 or from an amino acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the sequence according to SEQ ID NO: 16 or 18, or may be encoded by a nucleic acid sequence according to SEQ ID NO: 15, a nucleic acid sequence according to SEQ ID NO: 17, or a nucleic acid sequence showing at least 50, 60, 70, or 80%, preferably at least 90%, more preferably at least 95%, and even more preferably at least 97.5% identity to the sequence according to SEQ ID NO: 15 or 17. SEQ ID NO: 18 (amino acid sequence) comprises aa 980 - 1286 of the amino acid sequence according to SEQ ID NO: 16 as defined before. SEQ ID NO: 17 is corresponding the encoding nucleic acid sequence.

Both AtPGPl and FKBP42 may be used as first/second ligands in the context of the present invention. Precisely, FKBP42 may be used as a second ligand in the context of the present invention and AtPGPl may be used as first ligand, or vice versa. Addition of quercetin disrupts the protein-protein interactions and thereby releases the second ligand from the inventive nanocarrier.

As defined before, the first ligand is bound to the surface of said inner core as defined above. Such a binding of the first ligand to the surface of the inner core as defined above occurs typically via covalent or non-covalent bonds, preferably via covalent bonds.

Furthermore, if the inventive reversibly PEGylated nanocarrier system comprises at least one lipid bilayer as defined before, the first ligand is preferably bound to the surface of said at least one lipid bilayer. If a monolamellar lipid bilayer is used, the first ligand is preferably bound to the outer surface of said monolamellar lipid bilayers. If multilamellar lipid bilayers are used, the first ligand is preferably bound to the most outer surface of said multilamellar bilayers, but may be generally also bound to any of the more inner lipid bilayers. Likewise, such a binding of the first ligand to the surface of the at least one lipid bilayer occurs typically via a covalent or non-covalent bond, preferably via a covalent bond. According to a particularly preferred aspect of the present embodiment, the first ligand is bound, preferably covalently bound, to a phospholipid, a cholesterol, and/or a glycolipid or a derivative thereof, as defined above. Such a first ligand, which is preferably covalently bound to a phospholipid, a cholesterol, and/or a glycolipid, can then be integrated into the at least one lipid bilayer when forming same around the inner core of the reversibly PEGylated nanocarrier system as defined herein.

Hence, following a preferred example a first ligand as defined above, is covalently coupled to a phospholipid, a cholesterol, and/or a glycolipid or a derivative thereof, as defined above, wherein such a phospholipid, a cholesterol, and/or a glycolipid or a derivative thereof is preferably used for forming the lipid bilayer structure of the optional at least one lipid bilayer as described above, e.g. monolamellar or multilamellar lipid bilayers structures. Covalent coupling preferably occurs by formation of a chemical bond between the first substrate and the phospholipid, cholesterol, and/or glycolipid or a derivative thereof. A covalent bond between the first ligand and the phospholipid, cholesterol, and/or glycolipid or a derivative thereof may be achieved e.g. by formation of a thiocarbamide adduct or bond between the first ligand and the phospholipid, cholesterol, and/or glycolipid or a derivative thereof, or any further suitable covalent bond known to a skilled person and suitable in the present context.

A particularly preferred example of such an adduct comprises as a first ligand a fluorescein or FITC as defined above, which is preferably coupled via a covalent bond, e.g. by formation of a thiocarbamide adduct, to the phospholipid, cholesterol and/or glycolipid or a derivative thereof. Such a phospholipid, cholesterol and/or glycolipid or a derivative thereof, which is modified by covalently binding a first ligand can then be integrated into the phospholipid bilayer. The formed lipid bilayer then preferably carries on its surface a first ligand as described herein, preferably covalently bound to a member of the lipid bilayer.

More preferably an adduct as described before between the first ligand and the

phospholipid, cholesterol, and/or glycolipid or a derivative thereof is provided comprising a fluorescein or FITC as defined above as a first ligand, which is furthermore coupled via a covalent bond, e.g. by formation of a thiocarbamide adduct, to a phophoethanolamine as described above, more preferably to DSPE (l,2-distearoyl-sn-glycero-3- phosphoethanolamine). Such an adduct between FITC and DSPE is preferably termed DSPE- FITC. According to the present invention, the inventive reversibly PEGylated nanocarrier system also comprises a second ligand, which is bound to the first ligand, the second ligand being furthermore covalently bound to at least one biocompatible, soluble and hydrophilic polymer, preferably selected from poly(ethylene glycol) or a derivative thereof. Preferably, the second ligand is selected in this context from the above defined first ligand/second ligand combinations. More preferably, the second ligand is selected from an scFv fragment FITC-E2, e.g. an scFv fragment FITC-E2 according to SEQ ID NO: 1 as defined above. The corresponding first ligand may be selected from e.g. a fluorescein, preferably FITC. Alternatively, a first ligand may be selected in this context from any compound binding to a scFv fragment FITC-E2 according to SEQ ID NO: 1. The first ligand is optionally modified by covalent coupling to a phospholipid, a cholesterol and/or a glycolipid or a derivative thereof as described before. Likewise preferred, the second ligand is selected in this context from DNA gyrase subunit B from Escherichia coli (GyrB), preferably DNA gyrase subunit B from Escherichia coli according to SEQ ID NO: 2 as defined above or as encoded according to SEQ ID NO: 3 as defined above, wherein the corresponding first ligand may be selected from a coumarin antibiotics, such as aminocoumarin antibiotics including, for example, novobiocin, chlorobiocin, coumermycin and dihydronovobiocin, preferably novobiocin. Alternatively, a first ligand may be selected in this context from any compound binding to DNA gyrase subunit B from Escherichia coli (GyrB) according to SEQ ID NO: 2 as defined above or as encoded according to SEQ ID NO: 3 as defined above. This first ligand may be optionally modified by covalent coupling to a phospholipid, cholesterol and/or glycolipid or a derivative thereof as described before.

The second ligand is covalently bound to at least one biocompatible, soluble and hydrophilic polymer, preferably at least one poly(ethylene glycol) (PEG) or a derivative thereof as defined herein. Preferably, the second ligand is covalently bound to PEG. Covalent binding of PEG or a derivative thereof to the second ligand may occur via free NH ₂ groups at the surface of the second ligand. As an example, the single chain antibody fragment FITC-E2 as defined above exhibits 8 lysines and the N-terminus, adding up to 9 potential PEGylation sites, i.e. sites, where PEG could be covalently bound. Binding may also occur via any further suitable groups or moieties of the second ligand, wherein such suitable groups or moieties are known to a skilled person.

PEG as used in the present invention is a biocompatible, soluble and hydrophilic polymer. Herein, the term "poly(ethylene glycol)" or "PEG" is preferably to be understood to be any such biocompatible, soluble and hydrophilic polymer soluble in water and containing ether groups linked by 2 or 3 carbon atom, optionally branched alkylene groups. The definition of a poly(ethylene glycol) includes branched or non-branched poly(ethylene glycol),

poly(propylene glycols), and also block or random copolymers including the two types of units.

Poly(ethylene glycol) as defined herein are water-soluble polymers that have been approved for the oral, parenteral and topical administration of drugs (FDA). Poly(ethylene glycol)s are produced by means of polymerization of ethylene oxide (EO) or propylene oxide (PO) in the presence of water, monoethylene glycol or diethylene glycol as reaction initiators in an alkaline medium (1,2-Epoxide Polymers: Ethylene Oxide Polymers and Copolymers" in Encyclopedia of Polymer Science and Engineering; Mark, H.F. (Ed.), John Wiley and Sons Inc., 1986, pp. 225-273 ). When the desired molecular weight (generally controlled by means of in- process measurements of viscosity) is reached, the polymerization reaction is preferably terminated by neutralizing the catalyst with an acid (lactic acid, acetic acid or the like). The result is a linear polymer having a very simple structure: HO-(CH2-CH ₂ -0) _n -H, wherein (n) is the number of EO monomers or units. The units alternatively contain propylene groups.

PEGylation as described herein also includes PEGylation with derivatives of poly(ethylene glycol) (PEG) as described above, e.g. derivatives of the terminal hydroxyl groups, which can be modified (one or both ends) so as to introduce, without being limited thereto, alkoxy, acrylate, methacrylate, alkyl, amino, phosphate, isothiocyanate, sulfhydryl, mercapto and sulfate groups. The polyethylene glycol or polypropylene glycol can have substituents in the alkylene groups. If they are present, these substituents are preferably alkyl groups.

For the purposes of the present invention and in correspondence with common definitions the term PEG is preferably used in combination with a numerical value. In the pharmaceutical industry the numerical value typically indicates the mean molecular weight. Typically, PEGs with a molecular weight of less than 400 are non-volatile liquids at room temperature. PEG 600 shows a melting point comprised between 17 and 22 °C, whereas PEGs with mean molecular weights comprised between 800 and 2000 are pasty materials with low melting points. Above a molecular weight exceeding 3000, PEGs are solid and commercially available up to PEG 35000. On the other hand, although the melting point of PEGs increases when the molecular weight increases, the boiling point increases up to a maximum value of 60°C. Likewise, when the molecular weight increases, its aqueous solubility decreases. In any case for PEG 35000, an amount close to 50% w/w can be dissolved in water. PEG derivatives as described and used herein have advantages that are similar to traditional PEGs such as their aqueous solubility, physiological inactivity, low toxicity and stability under very different conditions. These PEG derivatives include very different products and are characterized by the functional group substituting the hydroxyl, such as -NH ₂ (among the most reactive ones), phenol, aldehyde, isothiocyanate, -SH groups, etc. The following PEG derivatives are exemplarily listed as PEG derivatives suitable and provided for use within the context of the present invention, without being limited thereto:

polyoxyethylene esters: PEG monomethyl ether monosuccinimidyl succinate ester; PEG monomethyl ether monocarboxymethyl ether; PEG adipate; PEG distearate; PEG

monostearate; PEG hydroxystearate; PEG dilaurate; PEG dioleate, PEG monooleate, PEG monoricinoleate; PEG coconut oil esters.

Polyoxyethylene alkyl ethers: PEG monomethyl ether or methoxy PEG (mPEG); PEG dimethyl ether.

Others: Poly(ethylene glycol terephthalate); polyoxyethylene derivatives and sorbitan esters and fatty acids; ethylene oxide and propylene oxide copolymers; ethylene oxide with acrylamide copolymers.

PEG derivatives: 0,0'-Bis-(2-aminoethyl)polyethylene glycol (DAE-PEG 2000); 0,0'-Bis-(2- aminopropyl)polypropylene glycol-polyethylene glycol-polypropylene glycol (DAP-PEG 2000).

Following another preferred aspect of the first embodiment a poly(ethylene glycol) derivative may be selected, without being limited thereto, from poly(ethylene glycol) methyl ether, preferably poly(ethylene glycol) methyl ether 2000 (mPEG 2000).

Following another preferred aspect of this embodiment of the invention the poly(ethylene glycol) used has terminal functional groups different from the hydroxyl group, such as amino groups. These amino groups can in turn be substituted and have functional groups. Hence, these amino groups can be used to further modify the poly(ethylene glycol). In a preferred variant the amino groups are -NH ₂ . It has been observed that with these groups, the oral administration of the nanoparticles accumulate on certain segments of the intestinal tract, which allows a specific administration.

According to an even further preferred aspect the polyethylene glycol used according to the present invention has amino groups and branches in the alkyl group. It has been found that with these substituents it is possible to form a brush-type structure, with one of the ends inside and the other one on the outside. The chemical structures of some suitable polyalkylene glycols corresponding to the previously mentioned groups with different types of functional groups are, without being limited thereto, illustratively selected from:

a) H(OCH ₂ CH ₂ ) _n OH

b) H ₃ C(OCH ₂ CH ₂ ) _n OH

c) H ₂ N(CH ₂ CH ₂ 0) _n CH ₂ CH ₂ NH ₂

d) H ₂ NCHCH ₃ CH ₂ (OCHCH ₃ CH ₂ )(OCH ₂ CH ₂ ) _n (OCH ₂ CHCH ₃ )NH ₂

wherein n is preferably between 200 to 6000, preferably e.g. 400, 1000, 2000, etc.

Particularly preferred examples of polyalkylene glycols and poly(ethylene glycol) include, without being limited thereto:

a) polyethylene glycol 1000 or 2000 (PEG 1000 or PEG 2000);

b) polyethylene glycol methyl ether 2000 (mPEG 2000);

c) 0,0'-Bis-(2-aminoethyl)polyethylene glycol 2000 (DAE-PEG 2000); and

d) 0,0'-Bis-(2-aminopropyl)polypropylene glycol- polyethylene glycol-polypropylene glycol (DAP-PEG 2000).

Following a preferred aspect of the first embodiment a poly(ethylene glycol) or a derivative thereof may be selected from e.g. PEG-PE (polyethyleneglycol- phosphatidylethanolamine),PLGA-PEG (block-copolymer of PEG and polylactide-glycolide), etc.

Following a preferred aspect of the first embodiment a poly(ethylene glycol) or a derivative thereof as used herein is not branched and does not have substituted hydroxyl groups. In this aspect the poly(ethylene glycol) or a derivative thereof as used herein preferably has a molecular weight between 400 and 35,000 Da. When the molecular weight is less than 400 Da it has been found that PEGylation typically does not efficiently occur. Therefore in one preferred aspect of the first embodiment the polyethylene glycol used in manufacturing inventive PEGylated nanocarriers has a molecular weight equal to or greater than 400 kDa, more preferably equal to or greater than 1,000 kDa, values between 1,500 kDa and 10,000 kDa are especially preferred, preferably between 500 kDa and 10,000 kDa, e.g. between 1,000 kDa and 10,000 KDa, between 1,000 kDa and 8,000 KDa or between 1,000 kDa and 5,000 KDa, e.g. 1,000 KDa, 2,000 KDa, 3,000 KDa, 4,000 KDa, or 5,000 KDa. According to a particularly preferred aspect poly(ethylene glycol) 2000 (PEG 2000) is used. Any range formed of one of the aforementioned values or ranges is also included, including combinations of the upper and/or lower ranges with any of the single values. According to the present invention, the second ligand of the reversibly PEGylated nanocarrier system preferably binds to the first ligand and binding of the second ligand to the first ligand is reversible.

Binding of the second ligand to the first ligand typically occurs by adding the second ligand being covalently bound to at least one PEG moiety as described above, usually under reaction conditions well known for a skilled person from the corresponding first ligand/second ligand combinations as described herein.

The binding of the second ligand to the first ligand and correspondingly the PEGylation is reversible. Such a detachment of the second linker from the first linker typically occurs via competitive binding, which is induced or caused by addition of an excess amount of the (non- modified) first ligand or second ligand to the reversibly PEGgylated nanocarrier system or by addition of any further compound capable of competitively binding to either the first or the second ligand. Such an addition of an excess amount of the first ligand or second ligand or any further suitable compound as mentioned above releases the nanocarrier system from its PEG-shell/PEGylation by detaching the second ligand from the inventive nanocarrier system. During competitive binding the detached second ligand with its covalently bound PEG- component binds to the added first ligand and thereby blocks the "binding site" of the detached second ligand for any further interaction with the first ligand of the nanocarrier system. Alternatively, of course, during competitive binding a second ligand may be added, which is not bound to a PEG or a derivative thereof, and then may bind competitively to the first ligand yet bound to the inventive nanocarrier system and thereby detaching the second ligand bound to PEG or a derivative thereof from its binding partner and the inventive nanocarrier system. In any case, detachment of the PEG-shell/PEGylation from the inventive the nanocarrier system occurs. The released inventive nanocarrier system then can further be degraded, preferably in the tumor cell and/or the contained cargo (inner core) may be released. A (free) first ligand suitable in this context to trigger competitive binding and thereby release of the second ligand with the PEG-component is typically any first ligand as described before in the context of the first ligand/second ligand combinations as outlined herein before or any other further compound capable of competitively binding to the second ligand. Preferably, such a suitable first ligand is a non-modified first ligand from said first ligand/second ligand combinations. A (non-modified) first ligand in the context of the present invention is preferably a first ligand as defined herein, wherein said first ligand is typically not bound, neither covalently nor non-covalently or via any further binding forces to any further compound, particularly preferably not to a member of the at least one lipid bilayer as defined above, i.e. a phospholipid, cholesterol, and/or a glycolipid.

Likewise, a second ligand suitable in this context to trigger competitive binding and thereby release of the second ligand with the PEG-component is typically any second ligand as described before in the context of the first ligand/second ligand combinations or any other further compound capable of competitively binding to the first ligand. Preferably, such a suitable second ligand is a non-modified protein or substrate from said protein/substrate combinations. A (non-modified) second ligand in the context of the present invention is preferably a second ligand as defined herein, wherein said second ligand is typically not bound, neither covalently nor non-covalently or via any further binding forces to any further compound, particularly preferably not to PEG or a derivative thereof as described herein.

The amounts required for competitive binding and hence detachment of the PEGylation from the herein described inventive PEGylated nanocarrier system are typically to be determined on basis of the patient to be treated and usually defined in amount/kg bodyweight of the patient. Such amounts can be readily determined by the skilled person on basis of clinical routine assessments.

According to a further aspect the inventive reversibly PEGylated nanocarrier system as described herein is modified to allow a specific targeting of the inventive reversibly PEGylated nanocarrier system to a specific location, such as a specific cell, specific tissue, etc. Such a specific targeting is typically effected by coupling a further third ligand either to the surface reversibly PEGylated nanocarrier system, for the purposes of the present invention termed "third ligand" or to any further component of the inventive reversibly PEGylated nanocarrier system as described herein. Such a third ligand may be any compound selected from an antibody, a protein, a peptide, a small molecule, a sugar, or any further compound, preferably as described in the table below, which is capable to target the inventive reversibly PEGylated nanocarrier system to a specific target region. Exemplary types of "third" ligands may be selected e.g. from the following: anti-HER2, anti-CD9, nucleosome-specific 2C5 mAb, transferrin, interleukin 13 (IL-13), Octreotide, LHRH-derived peptide, Arg-Gly-Asp (RGD), folate, estrone, anisamide, mannos, and/or lactose, etc. The target regions of such a third ligand are preferably selected, without being limited thereto, as depicted in the following table:

Table 1 Third ligands in the context of the present invention for specific targeting the inventive reversibly PEGylated nanocarrier system to a desired target region may be bound to the inventive reversibly PEGylated nanocarrier system via a non-covalent, e.g. electrostatic interactions, van-der-Waals interactions, etc., or any further interactions to be subsumed as a non-covalent bond, or via a covalent bond, more preferably via a covalent bond. Such a covalent bond is preferably a covalent bond as defined herein and may be formed accordingly as described herein.

The finally prepared reversibly PEGylated nanocarrier system of the present invention typically has a spherical form. The PEGylated nanocarrier system preferably has a size of about 10 to 1,500 nm, preferably 10 to 1,200 nm, likewise preferably 10 to 1000 nm, 10 to 800 nm, 10 to 600 nm or 10 to 400 nm even more preferably 20 to 300 nm, e.g. 50 to 250 nm or 50 to 200 nm.

According to a further embodiment, the present invention provides a pharmaceutical composition or medicament comprising the inventive reversibly PEGylated nanocarrier system as described herein. The inventive pharmaceutical composition preferably comprises as an active ingredient the reversibly PEGylated nanocarrier system as described herein and optionally a pharmaceutically acceptable carrier. In this context preferred is the use of such a herein described reversibly PEGylated nanocarrier system as a medicament or as a pharmaceutical composition. Likewise preferred is the use of a herein described reversibly PEGylated nanocarrier system in the treatment of any disease as described herein, preferably for the treatment of cancer or in the field of gene therapy. Hence, one aspect of the present embodiment is directed to a herein described nanocarrier system for use in cancer therapy, in gene therapy, in inflammatory diseases or in pain therapy/treatment, without being limited thereto.

In the context of the present invention the term "cancer therapy" may cover, without being limited thereto a range of possible cancers, such as e.g. Kaposis sarcoma, any cancer or tumor disease selected from melanomas, malignant melanomas, colon carcinomas, lymphomas, sarcomas, blastomas, renal carcinomas, gastrointestinal tumors, gliomas, prostate tumors, bladder cancer, rectal tumors, stomach cancer, oesophageal cancer, pancreatic cancer, liver cancer, mammary carcinomas (= breast cancer), uterine cancer, cervical cancer, acute myeloid leukaemia (AML), acute lymphoid leukaemia (ALL), chronic myeloid leukaemia (CML), chronic lymphocytic leukaemia (CLL), hepatomas, various virus-induced tumors such as, for example, papilloma virus-induced carcinomas (e.g. cervical carcinoma = cervical cancer), adenocarcinomas, herpes virus-induced tumors (e.g. Burkitt's lymphoma, EBV-induced B-cell lymphoma), heptatitis B-induced tumors (hepatocell carcinomas), HTLV-1 - and HTLV-2- induced lymphomas, acoustic neuroma, lung carcinomas (= lung cancer = bronchial carcinoma), small-cell lung carcinomas, pharyngeal cancer, anal carcinoma, glioblastoma, rectal carcinoma, astrocytoma, brain tumors, retinoblastoma, basalioma, brain metastases, medulloblastomas, vaginal cancer, pancreatic cancer, testicular cancer, Hodgkin's syndrome, meningiomas, Schneeberger disease, hypophysis tumor, Mycosis fungoides, carcinoids, neurinoma, spinalioma, Burkitt's lymphoma, laryngeal cancer, renal cancer, thymoma, corpus carcinoma, bone cancer, non-Hodgkin's lymphomas, urethral cancer, CUP syndrome, head/neck tumors, oligodendroglioma, vulval cancer, intestinal cancer, colon carcinoma, oesophageal carcinoma (= oesophageal cancer), wart involvement, tumors of the small intestine, craniopharyngeomas, ovarian carcinoma, genital tumors, ovarian cancer (= ovarian carcinoma), pancreatic carcinoma (= pancreatic cancer), endometrial carcinoma, liver metastases, penile cancer, tongue cancer, gall bladder cancer, leukaemia, plasmocytoma, lid tumor, prostate cancer (= prostate tumors), etc.

Additionally, the term "gene therapy" in the context of the present invention likewise includes genetic diseases, also termed (hereditary) diseases or monogenetic diseases. Such (mono-)genetic diseases, (hereditary) diseases, or genetic diseases in general are typically caused by genetic defects, e.g. due to gene mutations resulting in loss of protein activity or regulatory mutations which do not allow transcription or translation of the protein.

Frequently, these diseases lead to metabolic disorders or other symptoms, e.g. muscle dystrophy. Particularly, such (mono-)genetic diseases inter alia include Alzheimer disease, Breast cancer-1 (early onset), Breast cancer-2 (early onset), Creutzfeldt-Jakob disease , Diabetes mellitus (insulin-resistant); Diabetes mellitus (rare form); Diabetes mellitus (type II), Mucoviscidosis, Obesity, Osteoarthrosis, Pancreatic cancer, Parkinson disease(familial or juvenile), Sickle cell anemia, etc, without being limited thereto. The term "inflammatory diseases" in the context of the present invention likewise includes Pelvic Inflammatory Disease (PID) and Symptoms of Abdominal Pain, Fever and Painful Intercourse; gout, which Causes Pain, Sore, Swollen, Numb, Red, Hot Big Toe for Pain in Big Toe Uric Acid Diet Treatment; lupus, including systemic lupus erythematosus, which involves many parts of body such as heart, lungs, kidneys, brain, discoid lupus erythematosus, which mainly affects the skin with a red rash or pigment change of face, scalp, and drug- induced lupus, which is triggered by a few medicines, such as heart condition drugs, more common in men; and also inflammatory diseases such as asthma, pleurisy, eczema, arthritis, gastritis, splenitis,sinusitis, hepatitis, nephritis, psoriasis, vasculitis, laryngitis, thyroiditis, prostatitis, pharyngitis, sarcoidosis, atherosclerosis, allergic reactions, multiple sclerosis, some myopathies, rheumatoid arthritis, seborrheic dermatitis, Wegener's granulomatosis, IBS ~ Crohn's disease, ulcerative colitis, diverticulitis, inflammatory bowel disease (IBD), etc.

The inventive pharmaceutical composition as described above typically comprises the inventive reversibly PEGylated nanocarrier system as described herein and optionally pharmaceutically acceptable carrier and/or vehicle. In the context of the present invention, a pharmaceutically acceptable carrier typically includes the liquid or non-liquid basis of the pharmaceutical composition. Since the pharmaceutical composition is typically provided in liquid or at least semi-liquid/semi-solid form, the optional carrier will typically be pyrogen- free water; isotonic saline or buffered (aqueous) solutions, e.g. phosphate, citrate etc.

buffered solutions. Alternatively, no such carrier may be used. The injection buffer may be hypertonic, isotonic or hypotonic with reference to the specific reference medium, i.e. the buffer may have a higher, identical or lower salt content with reference to the specific reference medium, wherein preferably such concentrations of the afore mentioned salts may be used, which do not lead to damage of cells due to osmosis or other concentration effects. Reference media are e.g. liquids occurring in in vivo methods, such as blood, lymph, cytosolic liquids, or other body liquids, or e.g. liquids, which may be used as reference media in in vitro methods, such as common buffers or liquids. Such common buffers or liquids are known to a skilled person.

However, one or more compatible liquid fillers or diluents or encapsulating compounds may be used as well for the pharmaceutical composition, which are suitable for administration to a patient to be treated. The term "compatible" as used here means that these constituents of the pharmaceutical composition are capable of being mixed with the reversibly PEGylated nanocarrier system as defined herein in such a manner that no interaction occurs which would substantially reduce the pharmaceutical effectiveness of the pharmaceutical composition and its active ingredients under typical use conditions. Pharmaceutically acceptable carriers, fillers and diluents must, of course, have sufficiently high purity and sufficiently low toxicity to make them suitable for administration to a person to be treated. Some examples of compounds which can be used as pharmaceutically acceptable carriers, fillers or constituents thereof are sugars, such as, for example, without being limited thereto, lactose, glucose and sucrose; starches, such as, for example, corn starch or potato starch; cellulose and its derivatives, such as, for example, sodium carboxymethylcellulose, ethylcellulose, cellulose acetate; powdered tragacanth; malt; gelatin; tallow; solid glidants, such as, for example, stearic acid, magnesium stearate; calcium sulfate; vegetable oils, such as, for example, groundnut oil, cottonseed oil, sesame oil, olive oil, corn oil and oil from theobroma; polyols, such as, for example, polypropylene glycol, glycerol, sorbitol, mannitol and polyethylene glycol; alginic acid.

The inventive pharmaceutical composition may be administered, without being limited thereto, orally, parenterally, topically, rectally, nasally, buccally, vaginally or via an implanted reservoir. The term parenteral as used herein includes subcutaneous, intravenous, intramuscular, intra-articular, intra-nodal, intra-synovial, intrasternal, intrathecal, intrahepatic, intralesional, intracranial, transdermal, intradermal, intrapulmonal, intraperitoneal, intracardial, intraarterial, and sublingual injection or infusion techniques. Preferably, the inventive pharmaceutical composition may be administered by parenteral injection, more preferably by subcutaneous, intravenous, intramuscular, intra-articular, intranodal, intra-synovial, intrasternal, intrathecal, intrahepatic, intralesional, intracranial, transdermal, intradermal, intrapulmonal, intraperitoneal, intracardial, intraarterial, and sublingual injection or via infusion techniques. Particularly preferred is intradermal, subcutaneous and intramuscular injection. Sterile injectable forms of the pharmaceutical compositions may be aqueous or oleaginous suspension. The sterile injectable preparation may also be a sterile injectable solution or suspension in a non-toxic parenterally-acceptable diluent or solvent, for example as a solution in 1,3-butanediol. Among the acceptable vehicles and solvents that may be employed are water, Ringer's solution and isotonic sodium chloride solution. In addition, sterile, fixed oils are conventionally employed as a solvent or suspending medium. For this purpose, any bland fixed oil may be employed including synthetic mono- or di- glycerides. Fatty acids, such as oleic acid and its glyceride derivatives are useful in the preparation of injectables, as are natural pharmaceutically-acceptable oils, such as olive oil or castor oil, especially in their polyoxyethylated versions. These oil solutions or suspensions may also contain a long-chain alcohol diluent or dispersant, such as carboxymethyl cellulose or similar dispersing agents that are commonly used in the formulation of pharmaceutically acceptable dosage forms including emulsions and suspensions. Other commonly used surfactants, such as Tweens, Spans and other emulsifying agents or bioavailability enhancers which are commonly used in the manufacture of pharmaceutically acceptable solid, liquid, or other dosage forms may also be used for the purposes of formulation of the pharmaceutical composition. The inventive pharmaceutical composition as defined herein may also be administered orally in any orally acceptable dosage form including, but not limited to, capsules, aqueous suspensions, gels or solutions. For oral administration in a capsule form, useful diluents include lactose and dried cornstarch. When aqueous suspensions are required for oral use, the active ingredient, i.e. the complex, is combined with emulsifying and suspending agents. If desired, certain sweetening, flavoring or coloring agents may also be added.

The inventive pharmaceutical composition typically comprises a "safe and effective amount" of the active ingredients of the pharmaceutical composition, particularly of the reversibly PEGylated nanocarrier system as described herein. As used herein, a "safe and effective amount" means an amount of the active ingredients as such that is sufficient to significantly induce a positive modification of a disease or disorder as defined herein. At the same time, however, a "safe and effective amount" is small enough to avoid serious side-effects and to permit a sensible relationship between advantage and risk. The determination of these limits typically lies within the scope of sensible medical judgment. A "safe and effective amount" of the active ingredient of the inventive pharmaceutical composition will furthermore vary in connection with the particular condition to be treated and also with the age and physical condition of the patient to be treated, the body weight, general health, sex, diet, time of administration, rate of excretion, drug combination, the activity of the complex or of the antigen, the severity of the condition, the duration of the treatment, the nature of the accompanying therapy, of the particular pharmaceutically acceptable carrier used, and similar factors, within the knowledge and experience of the accompanying doctor. The

pharmaceutical composition may be used for human and also for veterinary medical purposes, preferably for human medical purposes, as a pharmaceutical composition in general or as a vaccine.

As used herein, the singular form of a word also includes the plural and vice versa unless the context clearly dictates otherwise. Thus the terms "a", "an" and "the" are generally meant to include the singular and the plurals of said terms. Similarly, the terms "comprise, "comprises" and "comprising" are to be interpreted inclusively rather than exclusively. Likewise, the terms "examples", "e.g.", and "such as", particularly when followed by a listing of terms is merely exemplary and illustrative and should not be deemed to be exclusive or comprehensive.

Unless defined otherwise, all technical scientific terms, terms of the art and acronyms as used herein have the meanings commonly understood by one of ordinary skill in the art in the field. Any references cited or referred to herein are entirely incorporated herein by reference to the extent allowed by law. The discussion of those references is intended to summarize the assertions made therein. No admission is made that any such references or any portion thereof are relevant material or prior art. The right to challenge the accuracy and pertinence of any assertion of such references as relevant material or prior art is specifically reserved.

Having thus described the present invention and the advantages thereof, it should be appreciated that the various aspects and embodiments of the present invention as disclosed herein are merely illustrative of specific ways to make and use the invention. Examples

The following Examples shall illustrate the above described invention in further detail and are not intended to limit the scope of the claims thereto. Example 1 Exemplary setup of the reversible PEGylation nanocarrier system - liposomal nanocarrier a) Reference Liposome preparation fDoxirubicin (Doxil ^® -like liposomes)^

As a reference system a liposomal formulation of Doxirubicin (Doxil ^® -like liposomes) was prepared following common protocols using HSPC, Cholesterol and DSPE-mPEG in the following amounts:

Hydrogenated soy phosphatidylcholin (HSPC): 9.58 mg/ml

Cholesterol (Choi): 3.19 mg/ml

N-(carbonylmethoxypolyethyleneglycol 2000)-l,2-distearoyl-sn-glycerol- 3-phosphoethanolamine sodium salt (DSPE-mPEG) 3.19 mg/ml

(see also www.doxil.com/assets/DOXIL_PI_Booklet.pdf) The Doxil ^® -like liposome preparation was carried out using the following protocol:

The liposomes were produced by the film-hydration method. The lipids were dissolved in chloroform to a final concentration of 16 mg/ml, followed by evaporation under vacuum. The resulting lipid film is afterwards rehydrated in HEPES-buffer pH = 7.4 in a water bath at 65°C. The resulting polydisperse liposome-solution is further downsized by extrusion through a polycarbonate membrane with a pore size of 80 nm. Size and dispersion was measured by dynamic light scattering to ensure uniformity of the liposomes.

(For further details of preparation: "Liposomes: A Practical Approach"; Vladimir P. Torchilin and Volkmar) Weissig)

Inventive Liposome preparation ^Doxirubicin (Doxil ^® -like liposomes)^ bl) Preparation of DSPE-FITC adduct

For the inventive purposes, the PEGylated DSPE as used in Example la) above was replaced by DSPE coupled to fluorescein. The coupling was carried out as a thiocarbamide adduct. The resulting compound has been termed DSPE-FITC. The reaction is exemplarily depicted in the following.

The compound DSPE-FITC has been then used to prepare a liposomal formulation of Doxirubicin (Doxil ^® -like liposomes) was prepared following common protocols using in a first step HSPC, Cholesterol and DSPE-FITC in the following amounts: In a second step FITC-E2 was coupled to DSPE-FITC and PEGylating the FITC-E2 via free NH ₂ - groups. b2) Preparation of liposomal formulation of Doxirubicin (Doxil ^® -like liposomes) with FITC-

E2/ DSPE-FITC

Due to the different molecular weights of DSPE-mPEG (2805 g/mol) and DSPE-FITC (1166 g/mol) the final composition was changed to:

Hydrogenated soy phosphatidylcholin (HSPC): 9.58 mg/ml

Cholesterol (Choi): 3.19 mg/ml

DSPE-FITC: 1.32 mg/ml The scFv used in the inventive example, FITC-E2 (see Pedrazzi G, Schwesinger F, Honegger A, Krebber C, Pluckthun A (1997) FEBS Lett, 415(3): 289-93), binds fluorescein with high specificity and has a molecular weight of ca. 28 kDa. The PEGylation of the protein was successfully achieved by reaction of NHS-mPEG2000 at free— NH ₂ groups (see above). FITC-E2 has 8 lysines and the N-terminus, adding up to 9 potential PEGylation sites.

PEGylation of the FITC-E2 was visualized on a 12% SDS PAGE (see Figure 2). MM represents the molecular marker. scFv represents FITC-E2, scFv+PEG represents the single short chain fragment FITC-E2 modified with PEG (PEGylated; In lane "scFV" 20 μΙ FITC-E2 (18mg/ml) were loaded in the corresponding lane. In the lane "scFv+PEG" scFv was reacted with 6x excess of NHS-mPEG2000 with the same loading conditions as for scFv.

Example 2 Test of the functionality of the inventive reversibly PEGylated nanocarrier system on THP-1 cells

The functionality of the setup was tested in a macrophage uptake assay using THP-1 cells (Human acute monocytic leukaemia cell where differentiated prior to the experiments to macrophage-like cells. This assay simulates the reaction of the immune system to an injection of the liposomes into the human body (see Blume G, Cevc G (1990) Biochim Biophys Acta, 1029(l):91-7).

Prior to the test, the liposomes were stained with DiD (Vybrant ^* DiD Cell-Labeling Solution). Then, the THP-1 cells were incubated 90 minutes with different formulations of liposomes (liposomes, liposomes + scFv-PEG or liposomes + scFv- PEG + fluorescein) or just buffer (HEPES). Cells were washed three times with PBS 37 °C and then detached with PBS + 2 mM EDTA. Relative fluorescence of THP-1 cells was afterwards determined with a flow cytometer. As could be seen in Figure 3, the fluorescence of the cells correlates with the uptake of DiD stained liposomes by the macrophages. The determined uptake rate is comparable with the figures obtained with "normal" PEGylated liposomes (see Blume G, Cevc G (1990) Biochim Biophys Acta, 1029(l):91-7), and is nearly 100% reversible after addition of fluorescein to a final concentration of 1 mM.

Figure 4, as outlined above, shows fluorescein-dependent scFv-PEG de-shielding of the nanocarrier (liposome) in the presence of THP-1 cells. For this purpose THP-1 cells were incubated 90 minutes with bare liposomes or liposomes with scFv-PEG and different concentrations of fluorescein (500 μΜ, 250 μΜ, 125 μΜ, 60 μΜ, 30 μΜ, 15 μΜ and just HEPES-buffer). Cells were washed then three times with PBS 37 °C and then lysed with HEPES 2% Triton-X. The uptake was quantified by measuring the DiD fluorescence, which the liposomal membranes were stained with (L: liposomes; F: fluorescein).

In Figure 5 further results can be seen. Figure 5 shows a test of different concentration of scFv-PEG to provide the scFv-PEG shell protection to the nanocarrier (liposome) in the presence of THP-1 cells. THP-1 cells were incubated 90 minutes with bare liposomes or liposomes with different scFv-PEG

concentrations (5mol%-PE-FITC in liposomal membrane; molar ratio scFv-PEG:PE- FITC: 1:2; 1:1; 2:1, 4:1, or BSA 4:1). Cells were washed three times with PBS 37 °C and then lysed with HEPES 2% Triton-X. The uptake was quantified by measuring the DiD fluorescence, which the liposomal membranes were stained with (L: liposomes).

Furthermore a test of the functionality of the inventive reversibly PEGylated nanocarrier system in a CHO-cell proliferation assay has been carried out. For this purpose, CHO cells were incubated 4 hours with doxorubicin or doxorubicin loaded liposomes in combination with the protective shell with or without the addition of fluorescein (HEPES, Doxorubicin, Doxorubicin liposomes + scFv-PEG or doxorubicin liposomes + scFv-PEG + fluorescein). Cells were washed three times with PBS 37 °C and then further cultivated for 24 h. To quantify the cell proliferation a WST-1 assay (Roche) was performed. Results are presented in Figure 6.

In addition plasma Half-life of Doxorubicin loaded into liposomes with PEGylated scFv was tested in Rattus norvegicus (Dosage 3.75 mg/rat). A prolonged half-life (19.5 h) of the protected liposomal doxorubicin can be seen compared to literature data for free doxorubicin (<lh) or liposomal, unprotected, doxorubicin (l-2h). Results are presented in Figure 7.

Example 3 Exemplary setup of the reversible PEGylation nanocarrier system - non- liposomal nanocarrier

a) Protocol for production of FITC modified dextran nanoparticles: Amino-modified dextran-nanoparticles are dissolved in 50% EtOH with 100 mM sodium bicarbonate. A 2-times molar excess of FITC in relation to amino-groups is dissolved in EtOH and an equimolar amount of triethanolamine is added. Afterwards the amino dextran particles are mixed with the FITC-solution and incubated for at least 4 hours at 4°C. The unreacted FITC is afterwards removed by dialysis (Cutoff 3,5 kDa) against PBS pH = 7.4.

Example 4 Exemplary setup of the reversible PEGylation nanocarrier system based on biotin -scFv interaction

Preparation of DSPE-biotin adduct

For the inventive purposes, the PEGylated DSPE as used in Example la) above was replaced by DSPE coupled to biotin. The coupling was carried out as N- hydroxysuccinimido adduct with the free amino group of the

phosphatidylethanolamine. The resulting compound has been termed DSPE-biotin.

The compound DSPE-biotin has been then used to prepare a liposomal formulation following common protocols using in a first step HSPC, Cholesterol and DSPE-Biotin in the above mentioned amounts. In a second step previous -NH ₂ PEGylated anti-biotin scFv was coupled to DSPE-biotin.

The various aspects and embodiments of the present invention do not limit the scope of the invention when taken into consideration with the appended claims, the foregoing detailed description and the accompanying figures. Features from one aspect and embodiment of the present invention as disclosed herein can be combined with features from other aspects and embodiments of the present invention.