EP1737426A2 - Cholinesterase inhibitors in liposomes and their production and use - Google Patents

Abstract

The invention relates to a pharmaceutical composition based on an active ingredient that is enclosed in liposomes for topical, transdermal application. The interior of said liposomes comprises an acidic, aqueous medium containing at least one cholinesterase inhibitor, preferably from the group containing donepezil, rivastigmine, galantamine, physostigmine, heptylphysostigmine, phenserine, tolserine, cymserine, thiatolserine, thiacymserine, neostigmine, huperzine, tacrine, metrifonate and dichlorvos, or an enantiomer or derivative of at least one of said compounds. In addition, the invention relates to a method for producing said composition, optionally in a sterile form and also to the use of the liposomes charged with the active ingredient in various galenic formulations for topical, transdermal application with a depot effect in the epidermis, for the prophylaxis and/or treatment of cutaneous neuropathic pain or the loss of cutaneous sensory function as a result of neuropathy.

Description

CHOLINESTERASE INHIBITORS IN LIPOSOMES AND THEIR PRODUCTION AND USE

TECHNICAL FIELD The present invention relates to pharmaceutical

Compositions based on cholinesterase inhibitors in liposomes, on the preparation of such compositions and on their therapeutic applications.

BACKGROUND OF THE INVENTION

Central inhibitors of cholinesterases are used for the pharmacotherapy of mild and moderate Alzheimer's disease in order to partially restore the reduced function of the cholinergic conduction system in the brain caused by this syndrome. Recent research has shown that many cholinesterase inhibitors not only block acetyl and butyryl cholinesterase through different mechanisms, but also have direct effects on neuronal nicotinic acetylcholine receptors. These receptors, the natural ligand of which is acetylcholine, are found not only on cholinergic nerves, but also in the serotonergic and gluta-atergenic nervous system, where they control the release of the respective neurotransmitter.

This effect occurs at very different concentrations of the agent in question, occurs at different receptor binding sites of the receptor, and can - in part depending on the concentration of the cholinesterase inhibitor itself and / or on the concurrent acetylcholine concentration - in one Blockage or an increase in the action of acetylcholine on the receptor result.

A particularly prototypical role in this regard is galantamine, since at concentrations that produce a therapeutically effective cholinesterase inhibition, it is an allosterically modulating ligand at a binding site distinct from the acetylcholine binding site (Samochocki et al., Acta Neurol Scand Suppl. 2000/176: 68-73; Dalas-Bailador et al., Mol Pharmacol. 2003; 64 (5): 1217-26). This will have the effect of inhibiting cholinesterase of galantamine potentiated increased concentration of acetylcholine additionally. Tacrine apparently also binds to this and another binding site of the receptor (Svensson and Nordberg, Neuroreport 1996; 7 (13): 2201-5). Comparable information also exists for physostigmine (Onkojo et al., Eur J Biochem 1991; 200 (3): 671-7) and for Donepezil. A non-cholinergic anti-apoptotic effect was also reported for galantamine (Arroyo et al., Rev Neurol. 2002; 34 (11): 1057-65), as was an effect corresponding to the nerve growth factor (NGF) (Capsoni et al ., Proc Natl Acad Sei US A. 2002; 99 (19): 12432-7).

Although these studies were carried out with a view to treating Alzheimer's dementia with its specific cholinergic deficit and the associated neurodegeneration, they are also of great importance for degenerative and painful diseases of the peripheral nervous system, in particular the sensory nerves. On the one hand, anti-nociceptive effects of nicotine and other substances that act agonistically at nicotinic receptors have been known for some time. On the other hand, in the early stages of diabetic sensory neuropathy as well as acute nerve lesions, the concentration of NGF in the affected areas of the skin is greatly reduced. NGF or a neurotrophic activity corresponding to this, which is mediated directly or via the cholinergic system closely linked to NGF, could restore the sensory function here. Studies in this regard were not very successful, presumably because sufficiently high local NGF concentrations could not be achieved without systemic side effects (Anand, Prog Brain Res. 2004; 146: 477-92). Nicotinic agonists have also been shown to be impaired in their therapeutic applicability by side effects such as high blood pressure and neurosuscular paralysis. Peripheral cholinesterase inhibitors are considered unsuitable for analgesic therapy in humans, mainly due to the problem of side effects (Ghelardini et al., Presynaptic Auto- and Heteroreceptors in the Cholinergic Regulation of Pain. In: Trends in Receptor Research, Elsevier Science Publishers BV , 1992). Transdermal formulations of cholinesterase inhibitors based on plasters which contain the active ingredient dissolved or distributed in a dermal penetration enhancer are known. Examples of such passive transdermal systems include: EP-0376067, EP-0377147, EP-0667774, EP-0599952 and EP0517840 for Physostig in; WO-9934782 for rivastigmine; EP-0680325 for galantamine and WO-0132115 for huperzine. Moriearty et al. (Methods Find Exp Clin Pharmacol 1993; 15 (6): 407-12) describe such systems for metrifonate or its hydrolysis product, which is active as a cholinesterase inhibitor

Dichlorvos and for heptylphysostigmine. Two further synthetic derivatives of physostigmine, thiacymserine and thiatolserine, are expressly described by their developer as being particularly suitable for transdermal use.

These transdermal systems are all designed for applications that require systemic administration of the respective active ingredient. In these cases, the choice of the transdermal route is given by the desire to release the active substance slowly and evenly into the bloodstream and / or to avoid the "first pass" breakdown in the liver that occurs when taken orally, so that therapeutically optimal plasma levels over a long period of time The systemic effect is achieved in that the active ingredient penetrates the skin by means of passive diffusion and is absorbed into the blood stream by subdermal capillary vessels. The active ingredient can also be temporarily deposited or bound in the subcutaneous fatty tissue in order to get from there In the skin itself there is intentionally only little retention of the active substance, and the systems mentioned are therefore unsuitable for the therapy of neuropathic pain or the impairment of the dermal sensory function by neurodegeneration controlled fre Is known active pharmaceutical ingredients (eg see overview in Ulrich, Biosci Rep. 2002; 22 (2): 129-50), in particular also for use in special transdermal “plaster” systems (for example disclosed in WO-8701938 and US-5718914) and in gels (US-5064655). Also the formulation of local anesthetics in topical applied liposomes are known to the person skilled in the art, eg describes US-4937078 Liposomes containing common sodium channel blockers such as tetracaine, lidocaine, etc.

A liposomal formulation of the cholinesterase inhibitor neostigmine for use as an analgesic has been described (Grant et al., Acta Anaesthesiol Scand. 2002; 46 (1): 90-4), but was administered intrathecally (ie into the connective tissue) so that the observed analgesic effect was a central.

BRIEF DESCRIPTION OF THE INVENTION

It was therefore the object of the invention to find a way to administer cholinesterase inhibitors with a known effect on neuronal nicotinic receptors and / or NGF-like neurotrophic activity in such a way that both the known disadvantages of plaster applications (for example the need for a surface that is as flat as possible for the application of the patch; possible skin irritation; active substance concentration in the patch must be very high; penetration enhancers can cause skin damage), as well as reducing or avoiding the disadvantages of invasive application methods and other systemic uses, in particular the undesirable systemic side effects associated with the required high dosage can be.

It is therefore an object of the present invention to provide a pharmaceutical composition with cholinesterase inhibitors which permits an overall low, but at the same time sufficiently high local dosage of these active substances in the area of the sensory nerve endings of the skin while at the same time largely avoiding their systemization.

It is a further object of the invention to provide a composition which can be used anywhere on the body, in particular also in "uneven" areas which are unsuitable for use in plasters, e.g. can be applied to feet with diabetic neuropathy, in the face with trigeminal neuralgia.

It is a further object of the invention to provide a composition which does not lead to any signs of maceration on the skin, particularly in those which have already been damaged and / or fragile skin, for example in diabetics, is essential.

It is another object of the invention to provide a composition which is manufactured as a sterile product and thereby e.g. Herpes zoster can be applied as a therapeutic agent at the blister stage or in the healing phase.

Finally, it is also an object of the invention to provide a composition which produces an active substance depot in the skin from which substance is continuously released, which also achieves better bioavailability and a longer half-life compared to systemic use.

According to the invention, these goals are achieved by providing a liposomal system for the topical administration of cholinesterase inhibitors.

Surprisingly, it was found that the inclusion of cholinesterase inhibitors in liposomes of a certain composition and size and subsequent formulation of these liposomes in suitable galenical systems for transdermal administration can achieve the aforementioned goals. The scalable process for active substance encapsulation disclosed in WO-0236257 has proven to be particularly advantageous for the production and loading of the liposomes with active substance on account of its high efficiency and at the same time extremely gentle process conditions. However, other methods known in the art for the production and loading of liposomes can also be used.

DETAILED DESCRIPTION OF THE INVENTION

The loading of liposomes with active substances can be divided into two main categories: loading the membrane and loading the intraliposomal aqueous phase. After galantamine base is soluble in ethanol, an attempt was first made to incorporate the active substance molecules into the liposomal membrane, but this was not successful. The more galantamine is not included in the membrane and instead, the more removed from the membrane, the more was released from the membrane. The proportion of membrane-bound and unbound galantamine was about the same. For this reason, an attempt was subsequently made to include the intraliposomal aqueous phase

Loading galantamine. This process can be accomplished in two ways: by active and passive loading. Based on experiments with passive loading of liposomes with galantamine HBr / base in PBS solution, it soon became apparent that no stable galantamine liposome suspensions could be produced with it. As in the previous membrane experiments, the active ingredient now diffused out of the aqueous environment of the liposomes as soon as the non-enclosed active ingredient was removed from the surrounding medium.

It was therefore necessary to take a closer look at the active ingredient galantamine. It was found that galantamine has chemical properties similar to doxorubicin and can be enclosed in liposomes by pH gradient-controlled loading. For this type of active loading, the most important characteristic is the liposome membrane / liposome medium distribution coefficient. The octanol / buffer distribution coefficient was found to be a good one

Provides information for the transmembrane diffusion of a substance and is therefore relevant for the loading with active substance or for the release profile. In addition, the active ingredient must contain protonatable amino groups, so that the active ingredient is hydrophilic at low pH and lipophilic at neutral or alkaline pH.

On the basis of this theoretical model, liposomes with different lipid compositions (preferably with long-chain phospholipids and low cholesterol concentrations) were prepared in a suitable loading buffer, preferably in a citric acid / sodium carbonate buffer. After the liposomes were made at low pH, the surrounding medium was alkalized and a pH gradient was created. After adding galantamine to the alkalized medium, the active ingredient migrated into the liposomes thanks to this pH gradient, where it was protonated and remained stable in the liposomes.

When using this technique, the extent of the loading or the loading capacity is primarily determined by the ratio of the pH values inside and outside the liposomes. In the experiments carried out, active substance / lipid ratios in the range of 200-400 nmol active substance per μmol lipid were able to achieve values similar to those known from the literature on actively loaded liposomes. An increase in the active substance concentration in the loading medium did not lead to an increase in the loading capacity.

The active loading described above is a three-stage process consisting of vesicle formation, addition of active ingredients and alkalization. It was therefore a further object of the invention to establish a one-step manufacturing process which could be implemented using the cross-flow module disclosed in WO-0236257. For this purpose, galantamine was dissolved in citric acid solution using

Cross-flow injection technique enclosed in liposomes and immediately afterwards the remaining citric acid solution alkalized with a dilution buffer (citric acid / sodium carbonate pH 9.0 - 9.5).

The examples below show, among other things, that the quality of the liposomes loaded with active ingredients can be improved by variation, in particular by reducing the cholesterol content in the vesicle membrane, especially with regard to their ability to penetrate the skin. In addition, stability tests for the products from the three-stage and the one-stage process prove that both products even after more than six months Storage, the product stability and quality has remained unchanged.

Where necessary or desired, the loading capacity can be further increased by increasing the average liposome size from approximately 150-200 nm (as is mostly used in the experiments described herein) to 300 to 500 nm. In addition, the efficiency of the process, i.e. the amount of liposomally enclosed active ingredient per ml of suspension, by increasing the

Increase the lipid concentration either during production or during the subsequent filtration of the vesicles.

BRIEF DESCRIPTION OF THE FIGURES

Fig.l shows a schematic representation of a device for producing the liposomes. Fig.2 shows HPLC results from galantamine inclusion experiments in liposomes. Dark bars represent galantamine in the retentate (i.e. liposomal galantamine), light bars on the other hand in the filtrate (not included galantamine) and the empty bar the total amount of galantamine; Ordinate: galantamine in μg / ml. Fig.3 shows HPLC results of galantamine inclusion experiments in liposomes. Dark bars represent galantamine in the retentate (i.e. liposomal galantamine), light bars, on the other hand, in the filtrate (not included galantamine) and the empty bars represent the total amount of galantamine; first three bars: positively charged liposomes with stearylamine; last three bars: negatively charged liposomes with E-PG; 3A: galantamine HBr; 3B: Galantamine base.

Fig.4 shows HPLC results of galantamine inclusion experiments in liposomes. Dark bars represent galantamine in the retentate (ie liposomal galantamine), light bars on the other hand in the filtrate (not included galantamine) and the empty bar the total amount of galantamine. Fig.5 shows the results of a stability test with actively loaded galantamine liposomes at different pH values aqueous phase; Ordinate: active substance concentration in nmol active substance per μmol lipid; Abscissa: period in weeks since the preparation of the preparations. Fig.6 shows HPLC data of loading preformed liposomes with galantamine as a function of temperature and loading time. Data in percent of the presented galantamine concentration. Fig.7 shows HPLC data of actively loaded liposomes in the presence of an excess of galantamine from two production attempts. Dark bars represent the amount of non-trapped, light bars that of liposomally trapped galantamine. The light line between the triangle symbols (associated values: right ordinate) indicates the stable lipid / drug ratio.

Fig.8 shows stability data of a liposome preparation, in which the liposomes were actively loaded with galantamine in a one-step process. Ordinate: active substance concentration in nmol active substance per μmol lipid; Abscissa: period in weeks since the preparation of the preparations. Fig. 9 shows stability data of actively loaded galantamine liposomes: A) produced in a three-step process; B) produced in a one-step process.

Fig.10 shows galantamine inclusion rates and stability of actively loaded DMPC liposomes. Fig.11 shows the galantamine intake in DPPC liposomes depending on the cholesterol content. Fig.12 shows a stability test of galantamine liposomes, produced according to the ammonium sulfate gradient method. Fl, F2, F3 denote filtrate samples, R stands for retentate. Fig.13 shows the stability of galantamine liposomes with lipids of different chain lengths (A: C16 and B: C14) in hydrogel formulations.

Fig. 14 shows the result of in vitro skin penetration studies with liposomal galantamine preparations with different lipid compositions. Ordinate: ng galantamine absolutely in the respective sample; Abscissa: variations in lipid composition. Fig.15 shows the result of in vitro skin penetration studies with liposomal galantamine preparations after repeated application. Fig. 16 shows the result of in vitro skin penetration studies with liposomal galantamine preparations depending on the amount of sample and the duration of penetration. Fig.17 shows the result of in vitro skin penetration studies with liposomal galantamine preparations depending on the hydrogel concentration. Fig. 18 shows the result of in vitro skin penetration studies with galantamine preparations in the form of microemulsions. Fig. 19 shows the result of in vitro skin penetration studies with hydrogel preparations based on freely available galantamine in comparison to galantamine enclosed in liposomes.

Fig.20 shows the result of in vitro skin penetration studies with liposomal galantamine preparations in the form of a suspension or as a gel. Fig. 21 shows the result of in vitro skin penetration studies with liposomal galantamine preparations on various skin samples.

For better illustration, the invention is further explained with the aid of the following examples. The experiments were carried out using galantamine as the active ingredient, either in the form of the free base or as the HBr salt. However, it is clear to the person skilled in the art that galantamine can also be used in the form of its enantiomers and all of its pharmacologically acceptable salts in the context of the present invention. Likewise within the scope of the present invention are chemical derivatives of galantamine and their enantiomers, such as the molecules claimed in WO-9612692, WO-9740049 and WO-0174820, insofar as these are cholinesterase inhibitors and / or nicotinic receptor modulators and / or neurotrophic , NGF-like effects unfold, including, the composition and size of the

Liposomes can be adapted to the physicochemical properties of these molecules.

In the same sense, it is obvious to the person skilled in the art that substances other than galantamine and its salts and Derivatives insofar as these are cholinesterase inhibitors and / or nicotinic receptor modulators and / or have neurotrophic, NGF-like effects also fall within the scope of this invention. These include, in addition to all the substances mentioned in the introductory description of the prior art, in particular also the molecules mentioned in WO 02059074, as well as the derivatives of donepezil mentioned in WO 0178728 and WO 0198271, in particular also its fluoro derivative ER-127528.

Example 1: Preparation and stability test of the galantamine liposomes

Synthetic dipalmitoylphosphatidylcholine (DPPC, Genzyme, Switzerland) and cholesterol (Solvay, The Netherlands) were used to produce the vesicles.

Some experiments were carried out either with hen's egg phosphatidylglycerol (E-PG; Lipoid, Germany) or with stearylamine (Sigma, USA) to introduce positive or negative charges into the liposomal membrane. Galantamine (Sanochemia AG, Austria) was used as the free base or as the HBr salt for the inclusion experiments. PBS (phosphate buffered saline) or citric acid in combination with sodium carbonate were used as buffer solutions.

The liposomes were preferred by means of the shear force-free ones

Cross-flow injection technology according to WO-0236257. This technique is very reproducible and allows the inclusion of any active ingredient in liposomes. This continuously executable, one-step method allows unilamellar liposomes with a lipid bilayer membrane ("bilayer") with a defined, selectable average size and size distribution to be stably produced by varying the process conditions, in particular the injection pressure of the lipid phase. It can also be carried out under extremely mild process conditions and allows the use of potentially damaging solvents and in particular the use of shear forces to form vesicles to be completely dispensed with. Further advantages of this method are described in detail in WO-0236257. In addition, this method makes it possible to provide all reagents in sterile or aseptic form and to carry out liposome production and loading under aseptic conditions, so that ultimately a sterile or aseptic product results in the form of drug-laden liposomes.

The detection of entrapped galantamine was carried out after ultrafiltration and / or diafiltration in a stirred cell (Amicon, USA) or after gel filtration over Sephadex G25 columns (Pharmacia, Germany) by means of rp-HPLC (reversed phase high performance liquid chromatography). The in-house rp-HPLC technology allows the quantitative determination of the membrane component cholesterol and the active ingredient galantamine within a single run. Liposome size and distribution were determined using photon correlation spectroscopy (PCS).

Liposome production: The liposomes are preferably produced using cross-flow technology. As shown in Fig.l, the device for liposome production consists of a cross-flow injection module 1, containers for the polar phase (injection buffer 2 and dilution buffer 3), a container for the ethanol / lipid solution 4 and a nitrogen compressor 5. The injection opening in Cross-flow module has a diameter of approx. 250 μm. The lipid mixture is preferably dissolved in 96% ethanol at a temperature in the range of - depending on the lipid selection or lipid composition - 25 to 60 ° C, for example in the case of DPPC liposomes at a temperature of 50 to 55 ° C, with stirring. The buffer solutions are also preferably heated to the same temperature, for example 55 ° C. During the polar phase through the cross current module by means of a pump 6, e.g. a peristaltic pump, the ethanol / lipid solution is simultaneously injected into the polar phase under any preselectable pressure.

Variant I:

DPPC, cholesterol and stearylamine (molar ratio 7: 2: 1) are dissolved together with galantamine in 96% ethanol and in PBS- Buffer injected. After the liposomes have formed spontaneously, they are filtered and both the retentate and the filtrate are analyzed by rp-HPLC. As can be seen from Fig. 2, galantamine cannot be integrated into the liposomes in a stable manner. Filtrate (not included galantamine) and retentate (liposomally included galantamine) show identical drug concentrations. In Fig. 2, the 1st bar means: the total amount of galantamine provided; the 2nd and 3rd bars: the active ingredient distribution in filtrate and retentate after the first (2nd bar) and after a further diafiltration (3rd bar).

Variant II: The lipids were again dissolved in ethanol. For experiments with negatively charged liposomes, stearylamine was replaced by hen's egg phosphatidylglycerol (E-PG). The ethanol / lipid solution is injected either into a solution of PBS / galantamine base or into a PBS / galantamine HBr solution.

As can be seen from the figures Fig.3A and Fig.3B, galantamine could not be satisfactorily enclosed in liposomes even after this procedure. After filtration, equal amounts of galantamine were found in the filtrate and retentate. In Fig.3A and Fig.3B: the 1st and 4th bar mean the total amount of each submitted

galantamine; the 2nd and 3rd or 5th and 6th bars: the active ingredient distribution in

Filtrate and retentate after the first (2nd and 5th bar) or after a further diafiltration (3rd and 6th bar).

Variant III:

External loading of liposomes with galantamine using a pH gradient.

The lipids (molar ratio DPPC: cholesterol = 55: 45) were dissolved in ethanol and this solution was injected in 300 mM citric acid pH 3.5-4.5. After spontaneous vesicle formation, galantamine HBr is added and the solution alkalized with 500 mM sodium carbonate. In this way, a pH gradient is formed between the inside and outside of the lipid vesicles (liposomes). pH values below 2.5 are less due to the onset of hydrolysis problems suitable, likewise pH values greater than 5.5 are not preferred due to the increasingly flat pH gradient.

As can be seen in Fig., The proportion of galantamine in the filtrate is considerably lower than in the retentate, which confirms that a large part of the galantamine obviously migrates into the liposomes along this pH gradient, is protonated and remains in the acidic environment within the liposomes. In Fig. 4, the 1st bar means: the total amount of galantamine provided; the 2nd and 3rd bars: the active ingredient distribution in filtrate and retentate after the first (2nd bar) or after a further diafiltration (3rd bar).

This product was divided into several aliquots and subjected to a stability test. Fig. 5 shows the product stability over a period of 9 weeks.

To determine the kinetics of the active loading of liposomes with galantamine, the duration of the loading process was investigated and the optimal loading temperature was determined. Fig. 6 shows that the entire amount of galantamine migrates into the liposomes within about 15 minutes and that an incubation temperature in the region of room temperature (18 - 22 ° C) is favorable for both the absorption of active substances and the retention of active substances within the liposomes. The differences determined for a range of 22 - 40 ° C are small and in any case do not play a significant role. The negative influence of higher incubation temperatures appears to have an impact primarily on the stability of the loaded liposomes, whereby at a temperature of 60 ° C the loss of active ingredient is already in a range of approx. 20 - 25% after 3 h incubation (Fig. 6).

In order to increase the amount of liposomally entrapped galantamine, a solution with 8-10 mg

Galantamine prepared per ml of solution. As can be seen from Fig.7, however, an excess of galantamine (dark bars; left ordinate) cannot improve the ratio of active substance / lipid, which remains constant in this experiment at around 200 - 300 nmol galantamine per μmol lipid (light line between the triangle symbols ; right Ordinate). The effective loading amount with active external loading via a pH gradient thus appears to be primarily dependent on the gradient and less on the active substance concentration presented.

Variant IV:

After the first evaluation of the previous results, a one-step manufacturing process was established. The lipids (DPPC: cholesterol = 55: 45 mol%) were dissolved in ethanol and the solution was injected into a galantamine HBr / citric acid solution (pH 3.5-4.5), followed immediately by sodium carbonate / citric acid solution after spontaneous vesicle formation. Buffer solution (pH 9.0 - 9.5) for the purpose of dilution and alkalization of the reaction mixture, ie the resulting liposome suspension was added. By producing this pH gradient immediately after the vesicle formation, galantamine is not only absorbed into the liposomes in one step, but also retained there stably. The amount of galantamine taken up in such a liposomal manner - depending on the pH value or pH gradient - was in a range of at least 100 nmol galantamine per μmol lipid, preferably in a range of at least 150-400, for example at a pH value of 3 , 5 often in the range of 250 to 350 (Figures 8-11). The stability of this product was fully preserved over an observation period of 6 weeks (see Fig.8).

Example 2: Preparation and comparison of galantamine preparations in the form of liposomes or microemulsions with a variable lipid composition

In this example, synthetic dipalmitoylphosphatidylcholine (DPPC, Genzyme, Switzerland), dimyristoylphosphatidylcholine (DMPC, Genzyme, Switzerland) and cholesterol (Solvay, Netherlands) were used as lipids. Galantamine (Sanochemia AG, Austria) was used as the HBr salt for the liposomal inclusion studies. Citric acid / sodium carbonate was used as the buffer solution.

The ammonium sulfate gradient method was used as the second option for active loading. As aqueous phases an ammonium sulfate solution and a glucose solution were used for vesicle production. Cross-current technology was used again. After removal of non-entrapped galantamine by means of gel filtration, both the active substance and the lipid contents were determined by means of rp-HPLC. Liposome size and distribution were again determined using photon correlation spectroscopy (PCS).

In addition to liposomes, preparations in the form of microemulsions were also produced by vigorous mixing with gradual heating with several heating cycles (heating up to 80 ° C). Isopropyl myristate (IPM) was used as the oil phase. Tween and Span 20 were used as emulsifiers and co-emulsifiers.

Liposo endesign and stability:

Liposome preparation, loading and analysis were carried out as in Example 1. Stability tests of liposome samples with a molar lipid ratio DPPC: cholesterol = 55: 45 were continued. Results are shown in Figures 9A and 9B.

Fig.9A shows stability data of the first liposome sample successfully loaded with galantamine using the active method (three-stage method). The liposomes were prepared in the presence of 0.3 mol of citric acid (pH 3.5-4.5). After vesicle formation, galantamine was added and at the same time the pH of the solution outside the liposomes was raised to 7.5. The resulting pH gradient between the inside and outside of the liposomes led to the uptake of galantamine in the liposomes, depending on the H + ion concentration within the liposomes.

Fig. 9B shows stability data of liposome samples with a similar composition, but the vesicle formation and galantamine loading were carried out using the cross-flow technique in a one-step process. The data clearly show that the pH gradient and thus the content of liposomally entrapped galantamine has remained constant over a period of more than half a year. To determine the best liposome formulation in terms of membrane flexibility and the associated skin penetration properties, various liposome suspensions with different lipid compositions were prepared and tested. In the first place

Phospholipids, optionally in combination with cholesterol, are used. However, it is within the scope of the invention to replace or supplement phospholipids with other lipids, for example with glycolipids, cerebrosides, sulfatides or galactosides. Typical representatives of the lipids that can be used are e.g. Phosphatidylethanolamine, phosphatidylcholine, phosphatidylserine, phosphatidylinositol, phosphatidylglycerol, cardiolipin, sphingomyeline, plasmalogens, glyceroglycolipids, ceramide, glycosphingolipids, neutral glycosphingolipids.

One way to improve the membrane fluidity, which is important for transdermal applications, is to reduce the phase transition of the liposomal double-layer membrane, which is primarily determined by the length of the acyl chains of the phospholipids, the amount of cholesterol and the saturation of the phospholipids. For this reason, DPPC, a phospholipid with an acyl chain length of 16 carbon atoms, was replaced by DMPC (chain length of 14 carbon atoms), which lowers the melting temperature TM from approx. 45 ° C. to 31 ° C.

Fig.10 shows inclusion rates of such liposome suspensions, which were prepared using pH gradients of 3.5 - 7.5 and 4.0 - 7.5. After satisfactory inclusion rates (comparable to those when using DPPC) were achieved, samples were taken and checked for their stability (Fig.10).

A second way to lower the membrane rigidity and to increase the fluidity is to reduce the cholesterol content in the membrane. Starting from a DPPC: cholesterol ratio of 55: 45 mol% (as described in the literature for liposome loading), the amount of cholesterol was successively reduced to 38 or 30%, based on the total lipid content. Figure 11 shows a slight decrease in the galantamine load compared to previous data with higher cholesterol levels. These liposomes showed however, improved skin penetration properties, as will be described below. Fig.11 also shows that the loaded liposomes remained stable in the long-term experiment and no galantamine was lost.

Contrary to the knowledge from earlier work, cholesterol-free liposomes could also be produced stably and successfully loaded with active substance, so that, according to the invention, the cholesterol content is in a range from 0 to 50 mol%, based on the total lipid content.

A third way to make liposomal membranes more flexible is to replace the fully saturated DPPC or DMPC lipids with chicken egg phosphatidylcholine (E-PC), a natural lipid mixture with unsaturated phospholipids. Next

Stability problems when using these natural lipids also required the liposomes to be made under a nitrogen atmosphere. Nevertheless, these vesicles gave neither good results in terms of vesicle size and homogeneity, nor improvements in skin penetration properties, as described in Examples 3-10.

In addition to the citric acid / sodium carbonate technique for creating a pH gradient, the ammonium sulfate gradient method is also frequently used. With this method, liposomes are formed in the presence of an ammonium sulfate buffer (125 mmol). After vesicle formation, the ammonium sulfate solution outside the liposomes is replaced by a 5% glucose solution by means of diafiltration, as a result of which small amphiphilic molecules can be loaded into the liposomes and protonated there, while in turn NH3 escapes from the liposomes. This process is known to be the milder process compared to the citric acid / sodium carbonate process.

Nevertheless, these attempts, at least when using galantamine as an active ingredient for loading the liposomes, did not give satisfactory results. The data in Fig.12 show that the galantamine inclusion failed because the same amount of active ingredient could be found in the retentate and in the filtrate. Therefore, for the inclusion of galantamine in liposomes Citric acid / sodium carbonate method is preferred for external, active loading, although it is within the scope of the present invention to use alternative, functionally equivalent acid / base systems known to the person skilled in the art to form the desired pH gradient. For example, citric acid could also be replaced by another suitable, pharmaceutically acceptable acid, for example a mineral acid such as phosphoric acid, or preferably by an organic acid, in particular from the group of edible organic acids, such as malic acid, fumaric acid, tartaric acid

Ascorbic acid. Likewise, sodium carbonate could also be replaced by another base, in particular by another alkali or alkaline earth carbonate or bicarbonate.

In this context, “functionally equivalent” is to be understood as the ability to be able to form a pH gradient across the lipid bilayer membrane of the liposomes and not to destroy the membrane integrity, so that the enclosed, in particular protonated, active ingredient is stable - in the sense of the stability criteria disclosed herein - remains in the liposomes.

Preparation and stability testing of a galantamine liposome gel: To use a liposomal galantamine composition as a topical therapeutic agent, the liposomes are preferably mixed into a hydrogel which is easier to apply to the skin than a pure suspension. However, it is within the scope of the present invention to also produce and topically apply other galenical formulations for the galantamine liposomes, in particular formulations in the form of solutions, lotions, emulsions, tinctures, sprays, ointments, creams or optionally also in the form of impregnated textile fabrics or dressing materials. Other possibilities are familiar to the person skilled in the art, as are the pharmaceutically permissible accompanying substances and additives required for producing the various pharmaceutical formulations.

Carbopol 981NF, a hydrogel that can be used in very low concentrations, has proven itself in previous experiments. It is approved for pharmaceutical use, relatively cheap to buy and in large quantities available.

The following liposome gels were produced for the penetration studies with the Franz diffusion cell: DPPC: cholesterol = 55: 45 / pH3, 5 DPPC: cholesterol = 62: 38 / pH3.5 DPPC: cholesterol = 70: 30 / pH3.5 DMPC: cholesterol = 55: 45 / pH3.5 E-PC: cholesterol = 63: 38 / pH3.5 E-PC: cholesterol = 70: 30 / pH3.5 For this purpose the vesicle suspensions were concentrated by ultrafiltration and subsequently stirred with a prefabricated, sterile gel base mixed. With this method, the liposomal galantamine concentrations can be varied either via the ultrafiltration or via the initial concentration of the gel base, which is diluted to a carbopol concentration of 0.5% with the vesicle suspension.

The standard tests were carried out for any loss of active ingredient that could result from membrane damage during the galenical production process and / or from long-term storage. For this purpose the gel was diluted with buffer and filtered. In the event of membrane damage, larger amounts of released galantamine would be detectable in the filtrate. As can be seen from the figures Fig. 13A and Fig. 13B, neither during the galenical formulation nor during the subsequent storage over 19 weeks at 4 ° C a significant proportion of active ingredient is released. Rather, the active ingredient remains in the liposomes even after the galenic formulation with Carbopol hydrogel and it shows a constant penetration profile in the skin test, which proves that both the liposomes and the pH gradient in the gel matrix remained intact.

For a comparison with regard to the skin penetration properties, free galantamine was also mixed and tested with hydrogel in the same way. Results are presented in Examples 3 to 10.

Alternative concepts: In addition to liposomes, microemulsions have also attracted increasing attention for topical applications of certain active ingredients in recent years. Microemulsions are dispersions of two immiscible components that are stabilized by a third, amphoteric component. However, due to the presence of surface-active substances such as emulsifiers and co-emulsifiers, microemulsions can damage the skin in a similar way to transdermal patches.

According to previous literature studies, several

Microemulsions (Tab. 1) prepared with galantamine as the active ingredient and then subjected to penetration tests with the Franz diffusion cell (results see Examples 3 to 10).

Table 1: Microemulsions lecithin ME W / O ME O / W ME 10 ml IPM 7.2 ml IPM 5.5 g H20 1.9 g SPC 0.2 g Chol 2.5 g IPM 135 μl H20 0.5 g H20 2 g Tween / Span20 10 mg Gal 2g Tween / Span20 11 mg Gal-HBr 10 mg Gal 5 mg Gal

ME = microemulsion; W / O = water in oil; O / W = oil in water In all of the experiments described here it was found that only a reduction in the cholesterol content in the liposome membrane brought about an improvement in the transdermal penetration properties. The liposome suspensions and liposomal gel preparations have been stable for more than half a year and show no changes in the product properties.

Examples 3 -10: Skin penetration tests of different lipid-based galantamine preparations

Franz diffusion cell:

The diffusion cell was from PermGear, USA. The equipment included three diffusion cells, each with a double jacket filled with water, mounted on a stirrer console and connected to a water bath for temperature control. The cells themselves have a volume of 8 ml each, a skin holder with a surface area of 0.78 cm2 and a feed chamber with 2 ml Volume capacity.

Skin integrity test:

Pig skin was used for the tests in the Franz diffusion cell. To ensure an intact skin surface, each piece of skin was tested before and after the experiment. After the skin had been attached to the skin holder of the diffusion cell, 2 ml of buffer were applied to the skin and the temperature was raised to 32 ° C. +1. After 30 minutes, electrical conductivity, a measure of skin resistance and skin quality, was measured. The measured value depends on the origin of the skin, its thickness, the buffer system used and the equipment used for the measurement. On the basis of several basic experiments, a limit value for the electrical conductivity of the intact skin of <1 mS / cm2 was determined before the application of a sample. Skin samples that did not meet this requirement were not approved for the penetration experiments.

Penetration buffer: After the liposomes according to the invention had been prepared in 0.3 M citric acid buffer, adjusted to pH 7.5 with 1 M sodium carbonate solution, the same buffer was also used for all penetration experiments.

Sample treatment after the penetration test:

After each experiment was completed, the excess galantamine sample was removed by washing the surface with buffer. The electrical conductivity was then measured again and the skin sample removed from the holder. For the purpose of separating the epidermis (epidermis) from the dermis (dermis), the

Skin sample placed on an electric hot plate and heated at 60 ° C for 30 seconds. After this heat treatment, the epidermis can easily be lifted off using tweezers. Immediately afterwards, the epidermis and dermis were each transferred separately into plastic tubes and frozen at -20 ° C. For the galantamine extraction, 300 μl buffer was added to the frozen sample in the presence of liquid nitrogen and the frozen sample was then pulverized in a cryogenic mill. The powder was immediately transferred to a centrifuge tube and centrifuged at 4 ° C, whereupon the clear supernatant in a clean tube was transferred and re-frozen at -20 ° C until analysis began.

Quantification of the galantamine supernatant: A modified, more sensitive and faster rp-HPLC method was established to determine small amounts of galantamine:

HPLC: Agilent 1100

Column: Thermo Hypersil Keystone 150 x 4.6 mm, 5μm, 190A

Gradient: linear gradient solvent A: H20 / 0.1% TFA solvent B: ACN / 0.1% TFA detection: DAD, 230nm quantification range: 30 - 1000 ng / ml injection volume: 100μl

Test material:

Several samples with different galantamine formulations were tested. Changes in task volume and

Penetration design was carried out and are summarized in the results.

Material: - Liposomal galantamine suspensions: C16 / 3, 5 / (55/45) C14 / 3, 5 / (55/45) liposomal galantamine gels: C16 / 3, 5 / (55/45) C16 / 3, 5 / (62 / 38) C16 / 3, 5 / (70/30) C14 / 3, 5 / (55/45) E-PC / 3, 5 / (62/38) E-PC / 3, 5 / (70/30 ) - free galantamine gels: 2 - 20 mg / g gel Galantamine microemulsions: lecithin-ME (1 mg / ml) water / oil (W / O) - ME (1 mg / ml) oil / water (O / W) - ME (1.6 mg / ml) The various liposomal galantamine formulations were produced using the cross-flow injection technique. The material was tested both in suspension and in a Carbopol (981NF) gel matrix. Variations in the

Membrane compositions of the liposomes were obtained by using different lipids and different cholesterol contents (see Examples 1 and 2). The following penetration studies were carried out with different sample volumes, single and multiple sample tasks, samples being taken at intervals to determine galantamine. The results shown in Figures 14 to 21 are each based on a triple penetration experiment. The diagrams show the results in ng galantamine absolutely for each sample analyzed. The results are subdivided into values that were determined from the receptor fluid REZ (= fluid collected in the collection container and penetrated through the skin) and those that were determined from the epidermis (EP) or dermis (DER).

Example 3:

In example 3, the results of various DPPC (C16) liposomes with different cholesterol contents are compared to those of DMPC (C14) liposomes and E-PC liposomes. A sample volume of 50 μl was applied once and allowed to penetrate over a period of 4 hours. All preparations tested had comparable amounts of entrapped galantamine and were suspended in 0.5% Carbopol 981NF. The most effective formulation in this experiment was the sample with the C16 / 70/30 (acyl chain length / mol% phospholipid / mol% cholesterol) lipid composition. In this gel, the cholesterol concentration in the liposomes was 30 mol%. The other two preparations had significantly higher cholesterol levels (38 and 45 mol%) and were therefore much more rigid. The data obtained from this experiment confirm the theory that more fluid liposomes, ie less rigid membranes, penetrate more efficiently (Fig. 14). In Fig.14 mean: 1 = C16 / 55/45; 2 = C16 / 62/38; 3 = C16 / 70/30; 4 = C14 / 55/45; 5 = E-PC / 62/38; 6 = E-PC / 70/30. Example 4:

In Example 4, the penetration properties of gel samples after repeated application to the skin were examined. Two different gels with different lipid compositions and the same cholesterol content were compared. The samples were applied three times with 50 μl each and every 4 hours. Excess material was removed before the next sample was applied.

As can be seen from the diagram (Fig.15),

Finally, an increase in the galantamine concentration can be achieved, but penetration into the epidermis seems to be somehow hindered or slowed down when the material is applied three times. It may be a kind of saturation, caused by the small surface area of the clamped skin in combination with the high application doses. Comparable results were achieved for both samples, so that an influence of the lipid composition was not evident (Fig.15). In Fig.15 mean:

(Chain length / phospholipid / cholesterol / total sample amount) 1 = C16 / 55/45 / 50μl; 2 = C16 / 55/45 / 100µl; 3 = C16 / 55/45 / 150µl; 4 = C14 / 55/45 / 50µl; 5 = C14 / 55/45 / 100µl; 6 = Cl4 / 55/45 / 150µl;

Example 5:

In Example 5, gels with Cl6 liposomes with high and low cholesterol contents were compared after a single application. Sample volumes of 150 ul and 50 ul were allowed to penetrate for 4 and 10 hours, respectively. The highest levels of galantamine in the skin were found again when using liposomes with a low cholesterol content. Low doses seem to be more advantageous here too. After 4 and 10 hours, high amounts of galantamine were found in the epidermis when 50 μl was used. These results confirm the values that were achieved in Examples 3 and 4, ie the administration of liposomes with low cholesterol contents and at the same time a low application amount overall, could represent a favorable strategy for the topical application of the preparations according to the invention in prophylactic or therapeutic use ( Fig.16). In Fig.16 mean: (chain length / phospholipid / cholesterol / sample amount / penetration time r) l = C16 / 55/45 / 150μl / 4h; 2 = Cl6 / 70/30 / 150μl / 4h 3 = C16 / 55/45 / 50μl / 4h; 4 = C16 / 70/30/50 .mu.l / 4h; 5 = C16 / 55/45 / 150μl / 10h 6 = C16 / 70/30 / 150μl / 10h;

7 = C16 / 55/45/50 .mu.l / 10h; 8 = C16 / 70/30/50 .mu.l / 10h

Example 6:

In Example 6, the influence of the gel concentration in connection with three different concentrations of free galantamine suspended in the gel was investigated. 50 μl of each formulation was applied once and the penetration experiment was carried out over 4 or 10 hours (Fig.17). The first three bars in Fig.17 represent the results with 1% Carbopol 981NF after 4 h, the next three bars those with 0.5% Carbopol 981NF after 10 h. The results after 4 hours show that free galantamine diffuses into the skin tissue relatively quickly. However, as can be seen from the 10 h values, the free active ingredient was also found in high concentrations in the receptor fluid, so that only a slight depot effect can be expected (Fig. 17).

Example 7:

In Example 7, various application strategies were tested. It is known from the literature that microemulsions can be useful tools as carrier systems for the administration of small amphiphilic molecules. In order to check this concept, various microemulsions (lecithin; water in oil; oil in water) with 1 mg galantamine per ml each were produced (see Examples 1 and 2).

Sample volumes of 50 μl were applied once and the penetration was carried out over a period of 4 hours. As can be seen from the diagram (Fig.18), the absolute values were

The amount of galantamine in the skin is lower than when using the hydrogel with liposomes. In addition, the active ingredient was equally distributed in the dermis (dermis) and receptor fluid, which suggests that rapid penetration with at best marginal storage in the skin tissue took place (Fig.18). These findings are in line with those of other authors and indicate a similar penetration mechanism as when using transdermal galantamine patches.

Example 8:

In Example 8, the results with free galantamine in hydrogel and microemulsions were compared to those of the preferred liposome composition (C16 low cholesterol phospholipids). In all experiments, comparable concentrations of galantamine were examined under similar conditions.

As can be seen from the diagram (Fig. 19), considerable amounts of galantamine were found in the skin when using the hydrogel formulation with free galantamine. Acceptable values were also obtained with the liposome formulation, but less so with the microemulsions. However, as already explained in previous examples, the goal of a new topical active substance formulation is not primarily a quick one

Skin penetration but rather the ability to build up a drug depot in the skin from which the drug can be released with a delay. Such a depot could, on the one hand, reduce the frequency of use and, on the other hand, could result in a more uniform, controlled release of the active ingredient, which would increase the therapeutic effect. This is achieved if the active substance - as in the case of the liposomal formulations according to the invention - is stored in the upper skin layers and not in deeper areas.

In Fig. 19 it means:

1 = liposomes (C16 / 70/30); 2 = 1.8 mg galantamine free in hydrogel; 3 = 1.8 mg free in lecithin microemulsion; 4 = 1.8 mg free in W / O-ME; and 5 = 1.8 mg free in O / W-ME

Example 9:

In Example 9, liposomal formulations in suspension and in hydrogel were compared with one another. The administration of an excess of 1 ml of liposomal suspension over a period of at least 24 hours resulted in only a slight decrease Penetration effectiveness (Fig.20). So it seems to be confirmed that a suitable gel matrix not only stabilizes the liposomes and makes application more pleasant and convenient, but also brings the liposomes closer to the skin and thus increases the penetration effect. In Fig. 20 they mean: (chain length / phospholipid / cholesterol / sample amount / penetration time / type)

1 = C16 / 55/45 / lml / 24h / suspension; 2 = C14 / 55/45 / lml / 24h / suspension; 3 = Cl6 / 55/45 / 100μl / 8h / gel; 4 = C14 / 55/45 / 100μl / 8h / gel;

Example 10:

In general, in-vitro testing using the Franz diffusion cell appears to be a useful method for penetration studies with various liposomal formulations, even if certain limits of the applicability of the method, especially when using liposomal gel formulations, were revealed. Based on previous experience with various liposome gels in vivo, it was also to be expected for the in vitro penetration tests described here that each gel can penetrate the skin completely and without any remaining excess on the skin surface. However, it was not possible to administer the gel with the same success in the experiments with the Franz diffusion cell. In all experiments, a considerable excess of sample material remained on the skin surface. This disadvantage has probably negatively affected penetration efficiency. It is therefore expected that higher amounts of liposomal galantamine will penetrate the skin in vivo.

After all, even in the in vitro experiments described here with the various liposome formulations, up to 1.8 x 10 ml of active substance molecules per 0.78 cm 2 skin surface were transported into the epidermis.

Various skin samples were tested in order to check whether skin removal with the dermatome or pretreatment of the skin could be responsible for the observed application problems (Fig. 21). However, no clear influence could be determined from the results. It is therefore to assume that the skin itself did not have a significant negative impact on the results achieved. In Fig. 21 mean:

1 = skin untreated; Liposomes: 70/30 (phospholipid / cholesterol); 2 = skin cleaned with ethanol; Liposomes: 70/30; 3 = skin treated with fatty gauze; Liposomes: 55/45; 4 = skin cleaned with ethanol and treated with grease; Liposomes: 55/45.

In any case, it can be said in summary that liposomal galantamine formulations in hydrophilic gel represent an advantageous dosage form if the place of treatment is in the dermal tissue (dermis), even if the active ingredient is only applied to the skin twice a day. A mild depot effect in the epidermis and a slow, uniform release of the active ingredient into the underlying dermal tissue can be achieved by the inventive, mild, non-invasive and non-irritating use of the liposomally enclosed active ingredient.

Abbreviations:

ACN acetonitrile

DAD diode array detector DER dermis (dermis)

DMPC dimyristoylphosphatidylcholine

DPPC Dipalmitoylphosphatidylcholine

E-PC natural phosphatidylcholine from eggs

E-PG natural phosphatidylglycerol from eggs EP epidermis (epidermis)

IPM isopropyl myristate

NGF Nerve Growth Factor

PBS Phosphate Buffered Saline

REZ receptor vessel (collecting container) rp-HPLC reversed phase High Performance Liquid

Chromatography

TFA trifluoroacetic acid

Claims

1. Pharmaceutical composition based on an active substance enclosed in liposomes for topical, transdermal application, characterized in that the

Liposomes have an acidic, aqueous environment in them and contain at least one cholinesterase inhibitor, preferably from the group donepezil, rivastigmine, galantamine, physostigmine, heptylphysostigmine, phenserine, tolserine, cymserine, thiatolserine, thiacymserine, neostigmine, muperetrifonin, tuperin, tacrine Dichlorvos, or an enantiomer or derivative of at least one of these compounds.

2. Composition according to claim 1, characterized in that the pH of the aqueous environment within the liposomes in one

Range of 2.5 - 5.5, in particular in a range of 3.5 - 4.5.

3. Composition according to claim 1 or 2, characterized in that the aqueous medium within the liposomes contains an organic acid, in particular citric acid.

4. Composition according to one of claims 1 to 3, characterized in that outside the liposomes there is an environment with a neutral or alkaline pH, preferably a pH of 7 to 8, in particular a pH of 7.5.

5. Composition according to one of claims 1 to 4, characterized in that the liposomes are unilamellar and have a lipid double-layer membrane.

6. Composition according to one of claims 1 to 5, characterized in that the liposomes contain phospholipids with an acyl chain length of at least 14 carbon atoms, preferably of at least 16 carbon atoms.

7. Composition according to one of claims 1 to 6, characterized in that the liposomes contain cholesterol in an amount of 0-50 mol%, preferably 30-45 mol%, of the total lipids.

8. Composition according to one of claims 1 to 7, characterized in that the liposomes have an average size in the range from 150 to 500 nm.

9. Composition according to one of claims 1 to 8, characterized in that the liposomes contain the active ingredient in a concentration of at least 100, in particular 150-400 nmol per μmol lipid.

10. Composition according to one of claims 1 to 9, characterized in that it is in the form of a suspension, lotion, emulsion, tincture, or a spray, gel, cream or ointment, preferably in sterile form.

11. A process for the preparation of a pharmaceutical composition based on an active substance enclosed in liposomes, characterized in that liposomes with an acidic, aqueous medium are spontaneously produced by injection of an ethanolic lipid phase into an acidic aqueous phase, whereupon the aqueous phase is neutralized or is alkalized so that a pH gradient forms between the inside and outside of the liposomes and the active ingredient is either a) placed in the acidic aqueous phase and absorbed into the liposomes in the course of the spontaneous liposome formation, or b) only after it has occurred Vesicle formation is added to the aqueous phase and migrated into the liposomes along the pH gradient.

12. The method according to claim 11, characterized in that the neutralization or alkalization is carried out immediately after liposome formation.

13. The method according to claim 12, characterized in that the aqueous phase before neutralization or alkalization has a pH of 2.5 - 5.5, preferably 3.5 - 4.5 and then a pH of 7 - 8, preferably 7.5.

14. The method according to any one of claims 11 to 13, characterized in that the acidic aqueous phase contains an organic acid, in particular citric acid, and the neutralization or alkalization is carried out by diluting the aqueous phase with an alkaline buffer, in particular with sodium carbonate.

15. The method according to any one of claims 11 to 14, characterized in that the lipid phase contains phospholipids with an acyl chain length of at least 14 carbon atoms, preferably of at least 16 carbon atoms.

16. The method according to any one of claims 11 to 15, characterized in that the lipid phase contains cholesterol in an amount of 0 - 50 mol%, preferably 30 - 45 mol%, of the total lipids.

17. The method according to any one of claims 11 to 16, characterized in that at least one cholinesterase inhibitor, preferably from the group donepezil, rivastigmine, as the active ingredient,

Galantamine, physostigmine, heptylphysostigmine, phenserine, tolserine, cymserine, thiatolserine, thiacymserine, neostigmine, huperzine, tacrine, metrifonate and dichlorvos, or an enantiomer or derivative of at least one of these compounds, is introduced in the aqueous phase or added to the aqueous phase after liposomes have been formed ,

18. The method according to any one of claims 11 to 17, characterized in that the pharmaceutical composition with the liposomes loaded with active ingredient in the form of a suspension,

Lotion, emulsion, tincture, or a spray, gel, cream or ointment, preferably in sterile form.

19. Use of a pharmaceutical composition according to any one of claims 1 to 10 as a medicament for topical application on the skin.

20. Use of a pharmaceutical composition according to one of claims 1 to 10 for the manufacture of a medicament with a depot effect in the skin, for the prophylaxis and / or therapy of the dermal neuropathic pain or loss of dermal sensory function due to neurophatics.

21. Use of at least one cholinesterase inhibitor, 5 preferably from the group donepezil, rivastigmine, galantamine, physostigmine, heptylphysostigmine, phenserine, tolserine, cymserine, thiatolserine, thiacymserine, neostigmine, huperzine, tacrine, metrifonate and at least one enlorantiomer or derivative, or at least one of dichlorvomer or derivative one of these compounds, for the manufacture of a pharmaceutical composition for topical application with a depot effect in the skin, for the prophylaxis and / or therapy of dermal neuropathic pain or the neurophatic loss of dermal sensory function.

15 22. Use according to any one of claims 19 to 21, for reducing or avoiding undesirable systemic side effects.