US 20070269504 A1
Amphoteric liposomes are proposed, which comprise positive and negative membrane-based or membrane-forming charge carriers as well as the use of these liposomes.
1. A method of loading nucleic acids in amphoteric liposomes having an isoelectric point of between 4 and 8 comprising the steps of:
a. providing a mixture of at least one amphipatic cationic lipid, at least one amphipatic anionic lipid and at least one neutral lipid and nucleic acids and at least one solvent at a pH of between 3-6; and
b. forming liposomes of said lipids and nucleic acids
c. changing the pH of said mixture to pH 7-9.
2. The method of
3. A method of loading nucleic acids in amphoteric liposomes having an isoelectric point of between 4 and 8 comprising the steps of:
a. providing a mixture of at least one amphipatic lipid with both a positive and a negative charge, at least one neutral lipid, and nucleic acids and at least one solvent, wherein said mixture has a pH between about 3-6;
b. forming liposomes in said mixture; and
c. changing the pH of said liposomes to pH 7-9
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d. removing non-encapsulated nucleic acids from said mixture.
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30. A method of loading active ingredients in amphoteric liposomes having an isoelectric point of between 4 and 8, wherein said liposomes are permeabilized and closed at a defined pH.
31. A method of
This application is a continuation of U.S. application Ser. No. 10/081,617 filed Feb. 21, 2002, which claims benefit of German Application 101 09 897.9, filed Feb. 21, 2001.
This invention relates to amphoteric liposomes, which simultaneously comprise positive and negative membrane-based or membrane-forming charge carriers as well as to the use of these liposomes.
The concept of lipids comprises three classes of natural products, which can be isolated from biological membranes: phospholipids, sphingolipids and cholesterol with its derivatives. However, it also comprises synthetically produced materials with similar characteristics. As representatives of these, diacyl glycerols, dialkyl glycerols, 3-amino-1,2-dihydroxypropane esters or ethers and also N,N-dialkylamines are mentioned.
These substances are of technical interest for the preparation of liposomes. On of the uses of these liposomes is as a container for active ingredients in pharmaceutical preparations. For this purpose, an efficient and stable packaging of the cargo, compatibility with body fluids and a controllable and optionally site-specific release of the content are desirable.
It is a disadvantage that it is difficult to combine the two requirements. The tighter and more stable the packaging, the more difficult it is to release the enclosed active ingredient once again. For this reason, liposomes were developed, which change their properties in reaction to external stimuli. Heat-sensitive and pH-sensitive liposomes are known. The pH-sensitive liposomes are of special interest, since this parameter may change under physiological circumstances, such as during the endocytotic absorption of a liposome in cells or during passage through the gastrointestinal tract. According to the state of the art, pH-sensitive liposomes comprise, in particular, cholesterol hemisuccinate (CHEMS).
Cholesterol hemisuccinate is used in admixture with phosphatidyl ethanolamine for the preparation of pH-sensitive liposomes (Tachibana et al. (1998); BBRC 251: 538-544, U.S. patent 4,891,208). Such liposomes can be endocytized by many cells and in this way are able to transport cargo molecules into the interior of cells, without injuring the integrity of the cellular membrane.
The anionic character of CHEMS is a significant disadvantage. The liposomes, prepared with it, have an overall negative charge and absorbed by cells only with a low efficiency. Therefore, in spite of the transfer mechanism described above, they are hardly suitable for transporting macromolecules into cells.
Cationic liposomes with the highest possible and constant surface charge are used to transport active ingredients into cells (transfection). The overall positive charge of such particles leads to an electrostatic adhesion to cells and, consequently, to an efficient transport into cells. The use of these compounds and of the liposomes, produced therewith is, however, limited to in vitro or ex vitro uses, since such positively charged liposomes form uncontrolled aggregates with serum components.
The limitation to very few pK values, generally to that of the carboxyl group in the cholesterol hemisuccinate (approximately 4.5) is a disadvantage of the pH-sensitive liposomes, which are available according to the state of the art. A further disadvantage of the compounds is the limitation to negative charge carriers. These are not suitable for binding nucleic acids and, frequently also, proteins efficiently.
Cationic liposomes show good bonding of nucleic acids and proteins and are in a position to bring these active ingredients into cells. It is a disadvantage that they cannot be used for in vivo applications.
It was therefore an objective to produce the liposomal structures, which
The inventive object is accomplished by amphoteric liposomes, which comprise at least one positive and at least one negative charge carrier, which differs from the positive one, the isoelectric point of the liposomes being between 4 and 8. This objective is accomplished owing to the fact that liposomes are prepared with a pH-dependent, changing charge.
Liposomal structures with the desired properties are formed, for example, when the amount of membrane-forming or membrane-based cationic charge carriers exceeds that of the anionic charge carriers at a low pH and the ratio is reversed at a higher pH. This is always the case when the ionizable components have a pKa value between 4 and 9. As the, pH of the medium drops, all cationic charge carriers are charged more and all anionic charge carriers lose their charge.
The following abbreviations are used in connection with the invention:
The membrane-forming or membrane-based charge carriers have the following general structure of an amphiphile:
charge group-membrane anchor
The naturally known systems or their technically modified forms come into consideration as membrane anchors. These include, in particular, the diacyl glycerols, diacyl phosphoglycerols (phospholipids) and sterols, but also the dialkyl glycerols, the dialkyl- or diacyl-1-amino-2,3-dihydroxypropanes, long-chain alkyls or acyls with 8 to 25 carbon atoms, sphingolipids, ceramides, etc. These membrane anchors are known in the art. The charge groups, which combine with the these anchors, can be divided into the following 6 groups:
Examples of weakly anionic compounds are: His-Chol-histaminyl-cholesterol hemisuccinate, Mo-Chol morpholine-N-ethylamino-cholesterol hemisuccinate or histidinyl-PE.
Examples of neutral compounds are: cholesterol, ceramides, phosphatidyl cholines, phosphatidyl ethanolamines, tetraether lipids or diacyl glycerols.
Examples of weakly anionic compounds are: CHEMS cholesterol hemisuccinate, alkyl carboxylic acids with 8 to 25 carbon atoms or diacyl glycerol hemisuccinate. Additional weakly anionic compounds are the amides of aspartic acid, or glutamic acid and PE as well as PS and its amides with glycine, alanine, glutamine, asparagine, serine, cysteine, threonine, tyrosine, glutamic acid, aspartic acid or other amino acids or aminodicarboxylic acids. According to the same principle, the esters of hydroxycarboxylic acids or hydroxydicarboxylic acids and PS are also weakly anionic compounds.
Strongly anionic compounds are, for example: SDS sodium dodecyl sulfate, cholesterol sulfate, cholesterol phosphate, cholesteryl phosphocholine, phosphatidyl glycerols, phosphatid acids, phosphatidyl inositols, diacyl glycerol phosphates, diacyl glycerol sulfates, cetyl phosphate or lyosophospholipids.
Amphoteric compounds are, for example,
The inventive liposomes contain variable amounts of such membrane-forming or membrane-based amphiphilic materials, so that they have an amphoteric character. This means that the liposomes can change the sign of the charge completely. The amount of charge carrier of a liposome, present at a given pH of the medium, can be calculated using the following formula:
At the isoelectric point, the net charge of the liposome is 0. Structures with a largely selectable isoelectric point can be produced by mixing anionic and cationic portions.
The structures can also be constructed so that, in particular, as the pH drops, the charge on the molecule as a whole is actually changed from negative to positive. Such a reversal of charge is advantageous particularly when the liposomes, produced with these structures, are to be used in physiological interrelationships. Only liposomes with an overall negative charge are compatible with blood and serum components. A positive charge leads to aggregations. Liposomes with a positive charge are, however, very good fusogenically and can transport active ingredients into cells. A pH-dependent reversal of charge therefore permits compounds to be constructed, which are compatible with serum because they have a negative charge; however, after their endocytotic absorption, their charge is reversed and they become fusogenic only in the cell.
In a preferred embodiment of an embodiment of the invention, the amphoteric liposomes have an isoelectric point between 5 and 7.
The invention also relates to amphoteric liposomes, which comprise at least one amphoteric charge carrier, the amphoteric charge carrier having an isoelectric point of between 4 and 8.
In a preferred variation, the amphoteric charge carrier of the liposomes has an isoelectric point of between 5 and 7.
The invention also relates to amphoteric liposomes, the liposomes comprising at least one amphoteric charge carrier and an anionic arid/or cationic charge carrier.
It is appropriate that, in a preferred variation, the amphoteric liposomes have an isoelectric point between 5 and 7.
In a special variation of the invention, the inventive liposomes comprise phosphatidyl choline, phosphatidyl ethanolamine, diacyl glycerol, cholesterol, tetraether lipid, ceramide, sphigolipid, and/or diacyl glycerol. However, the preparation of the liposomes can, of course, be carried out with many lipid combinations of the inventive teachings. For examples, liposomes can be synthesized using a large amount of CHEMS (about 40%) and a smaller amount of DOTAP (about 30%). At the pK of the carboxyl group of the CHEMS, the negative charge of this component is already suppressed so far, that the positive charge carrier predominates overall. An alternative formulation is the mixing of CHEMS with HisChol the stronger charging of the positive charge carrier HisChol going along synergistically with the discharging of the negative CHEMS.
If Hist-Chol, which in itself is amphoteric, is incorporated in a neutral membrane of, for example, phosphatidyl choline, an amphoteric liposome with an isoelectric point, which largely corresponds to that of Hist-Chol, also results.
It is known to those skilled in the art how the important parameters can be adapted by manifold variations of the inventive teachings:
In a further variation of the invention, the liposomes have an average size of between 50 and 1000 nm, preferably of between 70 and 250 nm and particularly between 60 and 130 nm. The amphoteric liposomes are synthesized by methods known in the art, such as the injection of ethanol into a lipid solution in an aqueous buffer, by hydrating dry lipid films or by detergent dialysis. The size of the liposomes can vary, generally between 50 nm and 10,000 nm. Homogeneous populations can be produced by high-pressure homogenization or by extrusion.
In a preferred variation of the invention, the liposomes comprise an active ingredient.
Advisably, in a preferred variation, the active ingredient is a protein, a peptide, a DNA, an RNA, an antisense nucleotide and/or a decoy nucleotide.
In a further preferred variation of the invention, at least 80% of the active ingredient in the interior of the liposome.
The invention also relates to a method for charging a liposome with active ingredient, a defined pH being used for the encapsulation and the pH being adjusted to a second value for separating the unbound material.
The invention furthermore also relates to a method for charging a liposome with active ingredient, the liposomes being permeabilized and closed at a defined pH.
The invention also relates to the use of the liposomes for the preparation of nanocapsules by depositing polymers or polyelectrolytes on the lipid layer. Such substances can be precipitated once or several times on the surface. With a repeated deposition, which optionally can be carried out in the absence of cross-linking agents, liposomal nanocapsules of the type described in the WO 00/28972 or in the WO01/64330 are formed. It is advantageous that the electrostatic interaction with the polyelectrolyte can be interrupted when the substances described here are used. It is known that the interaction of a polyelectrolyte with charge carriers of the liposomal membrane can lead to the de-mixing of membrane components and to the formation of lipid clusters. In many cases, this de-mixing is associated with a permeabilization of the liposome. The inventive substances enable this interaction to be switched off after the coating process. The liposomes are enclosed only sterically in the nanocapsules if the pH is increased at this time and there no longer is any interaction between the membrane and the polyelectrolyte. Cluster formation of the lipids and the permeabilization of the membrane, associated therewith, can thus be avoided.
The invention also relates to the use of the inventive liposomes for packaging and releasing active ingredients. In this variation, the liposomes bring about, in particular, the efficient packaging of active ingredients, such as nucleic acids. Nucleic acids are incubated with said lipids particularly at a low pH (about 3 to 6). After the formation of the liposomes, nucleic acids, adhering to the outside, can be washed off by changing to a high pH (about 7 to 9).
An analogous procedure can be used to package proteins. Advantageously, the pH of the medium is adjusted to a value here, which lies between the pI of the liposome and that of the protein. It has proven to be particularly advantageous, if the two pI values are more than one unit apart.
In a further variation of the invention, the liposomes are used to prepare release systems in diagnostics.
In a further preferred variation of the invention, the liposomes are used as transfection systems, that is, for bringing active ingredients into cells.
In a further variation of the invention, the liposomes are used for the controlled release of their contents by fusion or permeabilization of the membrane. For example, liposomes of a lipid, which by itself is not membrane-forming, can be stabilized by the incorporation of charge carriers, such as PE. If the charge carrier is transformed into a neutral, uncharged or zwitterionic state, the permeability of the membrane is increased. Known liposomes of the state of the art (PE/CHEMS, Tachibana et al.) permit such a permeabilization at the low pH values, which are attained under physiological conditions only in the interior of endosomes or during passage through the stomach. Amphoteric liposomes can be produced by the measures listed above in such a manner, that their neutral point lies at any desirable pH between 4 and 9. Under these conditions, the liposomes are permeable and can deliver cargo to the medium.
However, the liposomal formulations can be produced, processed and stored under conditions of lesser permeability. In a preferred embodiment of the invention, liposomes are produced so that they release of their cargo under conditions of a physiological pH, but enclose their cargo securely at a low pH. Such liposomes are suitable particularly for the preparation of formulations with slow release kinetics, the release being initiated only by contact with body fluids and not during storage or transport.
A preferred embodiment of the inventive teaching therefore consists of the use of such liposomes for therapeutic purposes, especially for such uses, which employ the specific targeting of the liposomes. The slight nonspecific binding is a prerequisite here for transporting the liposomes to the target place. In contrast to this, a high nonspecific binding would prevent any transport of the liposomes to the target place. A specific binding can be attained by further measures of the state of the art, that is, by selecting the size of the liposomes or also by binding the ligands to the liposomal surface, which binds to a target receptor of the cell surface. Ligands may, for example, be antibodies or their fragments, sugars, hormones, vitamins, peptides, such as arg-gly-asp (RGD), growth factors, bilirubin or other components.
The preferred variation of the inventive teachings relates to the use of the liposomes for therapeutic or diagnostic applications under in vivo conditions. Preferably, such liposomes are ones, which have a slight nonspecific binding and, with that, a slight tendency to fuse under physiological conditions, but are combined strongly and with a high fusion competence under changed conditions. Such liposomes are amphoteric liposomes, which have an overall anionic particle charge under physiological conditions and an increasingly cationic charge at a pH below 6.5. Such pH values occur during the endocytosis of the liposomes into cells. Such pH values also occur in the interior of tumors and in the external layers of the skin. Low pH values can also be obtained by perfusing an organ ex vivo for a certain period of time. A high binding strength and fusion competence is therefore limited to those liposomes, which were already taken up by cells or special tissue. The binding strength and increasing fusion competence support the fusion of the liposomal membrane with the cell membrane. This event leads to a direct release of the cargo into the interior of the cell without releasing components of the lysis of the endosome and, with that, endangering the cargo or cell components.
Furthermore, the use of the liposomes as a sustained release formulation and/or as a circulating depot is appropriate. The liposomes can also be used advantageously for intravenous or peritoneal application. In a particularly preferred variation of the invention, the liposomes are: used as a vector for the in vivo, in vitro and ex vivo transfection of cells.
The inventive liposomes have several advantages. Cationically chargeable liposomes of 40 percent HisChol and PC bind the nucleic acids, such as DNA, to their membrane even under conditions of a neutral pH. Surprisingly, this binding is suppressed completely if the above-mentioned liposomes are produced using 5 percent of PG in addition and then have amphoteric properties. However, the binding of nucleic acids to the membrane can be restored once again by decreasing the pH. The inventive liposomes are therefore particularly well suited for the pH-dependent binding of nucleic acids.
Furthermore, it was surprisingly found that a series of proteins also behaves in the manner described for nucleic acids. For example, antibodies bind not at a neutral pH, but under slightly acidic conditions effectively to the membrane of the inventive liposomes. Such a behavior cannot be observed in the case of pH-sensitive liposomes from a neutral lipid and CHEMS nor from such a liposomes from a neutral lipid and HisChol. It is therefore a special property of the amphoteric liposomes. Surprisingly, it was also found that inventive liposomes, contrary to the known, constitutive, cationic liposomes, are compatible with serum. An appropriate embodiment of the inventive teachings therefore consists of the use of such liposomes for therapeutic properties. It is an advantage of the liposomes that, in comparison to known, constitutive, cationic liposomes, the nonspecific binding to cells is significantly less.
It is, however, also surprising that the fusion competence of the inventive liposomes depends on the pH of the medium. In comparison to biological membranes of cells, the fusion competence is determined by the lipid selected and also by the charging of the liposomes. Usually, a binding step precedes the actual fusion. However, strong binding of the liposomes to cell membranes is not always desirable and should take place, as described above, only under controlled conditions in particular cells or tissue.
The liposomes cane therefore by used to construct liposomal vectors for the transport of active ingredients into cells. All materials, which do not form micelles, come into consideration as active ingredients. Water-soluble materials are particularly suitable as active ingredients. They include many proteins and peptides, especially antibodies or enzymes or antigens, all nucleic acids, independently of their molecular weight and their derivation from RNA or DNA. However, they include also other biological macromolecules, such as complex sugars, natural products and other compounds, as well as low molecular weight active ingredients of synthetic or natural origin, which otherwise cannot penetrate through the cell membrane as barrier. With the help of vectors, such materials can then be transported into the interior of cells and initiate actions, which are not possible without this transport.
Accordingly, with the help of the inventive teachings, liposomes can be prepared, the fusion and binding properties of which differ at different pH values. Serum-compatible liposomes, which are laden with a large amount of active ingredients and transport these into the interior of cells, can therefore be produced in this way. Someone, skilled in the art, is able to combine elements of the inventive teachings with one another and, with that, produce liposomes, which are optimally suitable for a particular purpose.
The invention is described in greater detail in the following by means of examples without being limited to these examples.
Preparation and Charge Properties of Amphoteric Liposomes with Charge Carriers, which can be Charged Positively and are Constantly Charged Negatively
His-Chol (5 mg) and 7.8 mg of POPC and 2 mg of DPPG are dissolved in 4 ml of a 1:1 (v/v) mixture of chloroform and methanol and dried completely in a rotary evaporator. The lipid film is hydrated with 4.3 mL of the appropriate buffer (10 mM KAc, 10 mM HEPES, 150 mM NaCl, pH 7.5, in a lipid concentration of 5 mM by a five-minute treatment with ultrasound. Subsequently, the suspension is frozen and, after thawing, extruded several times (Avestin LiposoFast, polycarbonate filter with a 200 nm pore width). For measuring the zeta potential, the final concentration of the liposomes is adjusted to a value of 0.2 mM. For the dilution, the buffer system, named above, is used at a pH of 7.5 or 4.2. The zeta potentials measured lie between −18 mV (at pH 7.5) and +35 mV (at pH 4.2).
Preparation and Charge Properties compatible of Amphoteric Liposomes with Constant Positive and Variable Negative Charge Carriers
POPC, DOTAP and CHEMS are dissolved in the molar ratios given below in 4 mL of a 1:1 (v/v) mixture of chloroform and methanol and evaporated completely in the rotary evaporator. The lipid film is hydrated with 4.3 mL of the appropriate buffer (10 mM KAc, 10 mM HEPES, 150 mM NaCl, pH 7.5, in a total lipid concentration of 5 mM by a five-minute treatment with ultrasound. Subsequently, the suspension is frozen and, after thawing, excluded repeatedly (Avestin LiposoFast, polycarbonate filter with a 200 nm pore width). The Table below shows the zeta potentials as a function of pH.
The height of the zeta potential and its slope can be selected within why limits by means of a suitable composition.
Preparation and Charge Properties of Amphoteric Liposomes with Complete Switchability in One Compound
His-Chol (5 mg) and 9.8 mg of POPC are dissolved in 4 ml of a 1:1 (v/v) mixture of chloroform and methanol and dried completely in a rotary evaporator. The lipid film is hydrated with 4.3 mL of the appropriate buffer (10 mM KAc, 10 mM HEPES, 150 mM NaCl, pH 7.5, in a lipid concentration of 5 mM by a five-minute treatment with ultrasound. Subsequently, the suspension is frozen and, after thawing, extruded several times (Avestin LiposoFast, polycarbonate filter with a 200 nm pore width). The course of the zeta potential at different pH values and ionic strengths is shown in the table below (Table 2).
Lipid films are prepared as in Example 1. A lipid mixture, which did not contain any DPPG, was used as comparison sample. The lipid films were hydrated in buffer (10 mM of phosphate, 150 mM of sodium chloride, pH of 7.4) and extruded as above. Human serum is diluted with an equal amount of buffer (10 mm of phosphate, 150 mM of sodium chloride, pH of 7.4), particular components and fat being removed by centrifuging (20 minutes, 13,000 rpm, 4° C.); the clear serum is filtered sterile with a filter having a pore width of 0.2 μm.
The liposomes, prepared above are added to the serum in concentration of 1 mM and incubated for 15 minutes at 37° C. After the incubation, the suspension of the DPPG-containing liposomes is uniformly cloudy; however, flocculation cannot be observed. The diameter of the liposomes is determined by means of dynamic light scattering and is changed by less than 10% from that of the starting sample. The suspension of the DPPG-free liposomes clearly shows flocculation.
Serum Stability of the Membrane
Aside from serum aggregation, the precipitation of an active ingredient (carboxyfluorescein, CF) in the presence of human serum was also investigated. For this purpose, POPC/DOTAP/CHEMS liposomes of different decomposition were prepared by the method of Example 2: POPC 100% (as control), POPC/DOTAP/CHEMS 60:30:10, 60:20:20 and 60:10:30 (in mole %). Any CF, which is not enclosed, was removed by gel filtration. For the measurement, the liposomes were diluted to 0.1 mM in serum and incubated at 37° C. A 30 μl sample was removed at certain times and diluted to 300 μL with 100 mM of tris buffer, having a pH of 8.2 and the fluorescence was measured. The 100% values were obtained by dissolving the liposomes with 10 μl of Triton X-100 (10% in water). The enclosed CF as a function of time is shown in the Table below.
The liposomes lose only a little CF into the serum during the 4-hour period of measurement. POPC/DOTAP/CHEMS 60:30:10 and 60:20:20 still contain about 75%, POPC and POPC/DOTAP/CHEMS 60:10:30 even 100% of their original CF content (see Table 3).
Liposomes of the following compositions (in mole %) are prepared as in Example 1 (all data is in mole %).
The liposomes are suspended in a concentration of 0.2 mM in buffer (10 mM of potassium acetate, 10 mM of HEPES, pH 4.2 or 7.5). A DNA solution (45 μL, 1 mg of DNA (Hering sperm, SIGMA D3 159) in 1 mL of water) are added in each case to 1 mL of the different liposomes samples and mixed quickly. After an incubation period of 15 minutes, the sample is filled up with 6 mL of the appropriate buffer and the zeta potential of the liposomes is measured (Table 4).
Under the conditions of an excess of cationic charges (pH 4:2), there is a strong reversal of the charge of the particles. At a neutral pH of 7.5, the CHEMS in high concentration (liposome C) can overcompensate the charge of the HisChol and the particles have a negative zeta potential. Only slight amounts of DNA bind to such particles.
Liposomes having the compositions POPC/DOTAP/CHEMS in the ratio of 60:15:25 and POPC/DCChol/CHEMS in the ratio of 60:15:25 (in mole %), were prepared by the method of Example 2. The binding of the DNA was carried out at a pH of 4.2 by the method of the above example and the zeta potentials were determined. Subsequently, the pH of the samples was adjusted to a value of 7.5 and the zeta potential was measured once again.
In the presence of DNA, a negative zeta potential is measured at a low pH; however, the original particles were charged positively. After the change to the neutral pH, this charge, which is due to the DNA, is decreased. The zeta potentials approach that of the untreated liposomes (−11 mV at a pH of 7.5).
DNA Inclusion and Detachment of Material not Encapsulated
Two liposome formulations, having compositions of POPC60/DOTAP15/CHEMS25 and POPC85/DOTAP15 respectively, are prepared as dry lipid films as described above. In each case, the total amount of lipid was. 4 μmoles. For hydration, Herings DNA was dissolved in 10 mM of potassium acetate, 10 mM of HEPES and 100 mM of sodium chloride at a pH of 4.0. The DNA (4 mg) was added directly to the lipid films. The resulting liposomes were frozen and thawed repeatedly and subsequently extruded through a 200 nm filter.
Each 500 μL of particles was mixed with 2.5 mL of a sucrose solution (0.8M sucrose in the above buffer, at a pH of 4.0 or 7.5). Over this, 1.5 mL of a 0.5 M sucrose solution and 0.5 mL of the buffer were placed.
Liposomes were then separated by flotation from unbound DNA. After the flotation, the liposomes were removed from the buffer/0.5 M sucrose interface. The amount of bound DNA was determined by intercalation of propidium iodide. The Stewart assay was used to determine the amount of lipid. Only the PC used responds in the Stewart assay. The other lipids were not calculated by means of this value. The results are shown in the Table below (Table 5).
With the amphoteric liposomes, only about half of the bound DNA floats up after the change in pH to 7.5. This material is the actually enclosed material. Similar results are obtained by digesting with DNAse
DNA cannot be detached once again from constitutively cationic liposomes by changing the pH or by additionally increasing the ionic strength and always remains on the outside.
Liposomes with the following compositions are prepared as in Example 1 (all data in mole %):
The facultative cationic liposomes A or B are incubated with the neutral liposomes X or the anionic liposomes Y in the buffer (10 mM HEPES, 10 mM potassium acetate, pH 4.2 or 7.5). The possible fusion of liposomes is analyzed by size measurement by means of dynamic light scattering (Table 6).
The starting sizes of the liposomes were 161.8 nm at pH 4.2 and 165.9 nm at pH 7.5
The size of the pairs with the complementary charge (YA and YB) differs clearly from the size of the mixed suspensions with the neutral liposome X. The extent of the interaction is determined by the magnitude of the charge of the facultative cationic liposomes. The extent of the fusion to larger units does not depend on the fusogenic lipid PE.
Permeability to Macromolecules
DOPE (13.75 μmoles), 2.5 Emotes of CHEMS and 10 μmoles of HisChol are dissolved in isopropanol and the solvent is drawn off under a vacuum. A solution (2.5 mL) of proteinase K in buffer (1 mg/mL of proteinase K, 10 mM of potassium acetate, 10 mM HEPES, 150 mM of sodium chloride, pH 4.2) is added to the dried lipid film. After the film is hydrated, the liposomes formed are extruded through a 400 nm membrane. Proteinase, which is not enclosed, is removed by floatation of the liposome in the sucrose gradient. The liposomes, so produced, are incubated with 7.5 mL of buffer at a pH of 4.2 and 7.2 (buffer as above, starting pH 4.2 and 8.0). After the combination, the proteinase K released is removed using a 0.1 μm membrane. The liposomes, remaining in the filter, are then treated with 7.5 mL of a solution of Triton X-100 in buffer (as above, pH 8.0).
All filtrates are tested for the presence of proteinase K. For this purpose, a solution of azocasein (6 mg/mL of azocasein in 1 M urea, 200 mM tris sulfate, pH 8.5) is used. This solution (500 μL) is mixed with 100 μL of filtrate or buffer and incubated for 30 minutes at 37° C. The reaction is terminated by the addition of 10% trichloroacetic acid. Precipitated proteins are removed by centrifuging. The coloration is measured at 390 nm (Table 7).
If the incubation of the liposomes is carried out at a pH of about 4.2, very little if any proteinase K is released. Only the dissolution of the liposomes with Triton X-100 leads to the release of the enzyme. If the liposomes are incubated at a pH of 7.2, the bulk of the enzyme is released already without the addition of the Triton and is found in the first filtrate. Hardly any additional enzyme is then dissolved from the liposomes by the addition of Triton.
Liposomes, having the composition POPC50/DOTAP10/CHEMS40 (all data in mole %) are prepared as in the preceding examples. A solution of 0.26 mg/mL of lysozyme in buffer (10 mM MES of pH 5.0 or pH 6.0 or 10 mM of HEPES of pH 7.0 or pH 8.0) is used to hydrate the lipid film. After the hydration, all samples were frozen and thawed repeatedly. Subsequently the liposomes are homogenized by ultrasound and extruded through a 200 nm filter.
The liposome suspension, so prepared, is adjusted to a pH of 4.0 by the addition of acetic acid. Subsequently the liposomes are separated by flotation from protein, which has not been incorporated. The proportion of enclosed protein is given in the Table below (Table 8).
Liposomes of the composition used show a pI of 5; the lysozyme is a basic protein with a pI of 11.5. The two partners therefore have opposite charges at a pH between 6 and 8. An efficient inclusion in the liposomes is brought about by electrostatic attraction. Protein, not encapsulated, was removed at a pH of 4. The interaction between the partners is cancelled at this pH.
Transfection Into Cells
HeLa cells or CHO cells (3×105) were plated into each cavity of a 6-well titer plate and cultured for three days. Liposomes (POPC/DOTAP/CHEMS 60/30/10) were prepared in the presence of fluorescence-labeled dextran (TRITC dextran 10 mg/mL in the hydration buffer). TRITC dextran, which had not been incorporated, was removed by gel filtration. The liposomes, so prepared, were added to the cells and incubated for 6 hours at 37° C. Subsequently, the cells were washed twice with buffer. The absorption of dextran was followed in the microscopic image. The results are shown in
Ligand Binding and Transfection
Liposomes, having the composition of POPC/DOTAP/Chems/N-glutaryl-DPPE (50:10:30:10 (mole %)) are prepared as in Example 2. At the same time, they are hydrated with a solution of 3 mg/mL of TRITC-Dextran (having a molecular weight of about 4,400) in HEPES 10 mM and 150 mM of sodium chloride at a pH of 7.5. TRITC-Dextran, which is not enclosed, is removed by gel filtration through a Sephadex G-75 column. Activation of the N-glutaryl DEPPs with EDC (1-ethyl-3-(3-dimethylaminopropyl carbodiimide) (3.5 mg of EDC per 400 μL of liposome suspension) and subsequent stirring in the dark for 5 hours brings about the binding of the cyclic peptide RCDCRGDCFC to the liposomal surface. The RGD peptide (250 μg in 150 μL of buffer) was then added and stirring was continued overnight. The liposomes were separated by gel filtration from the peptide, which had not been bound.
Human endothelium cells (HUVEC) were cultured in a special medium. The liposomes, modified with ligand, and control liposomes without RGD ligand were added as a 0.5 mM suspension to the cells. After 2 hours, the liposomes are removed and the cell chambers rinsed 3 times with PBS buffer and viewed under the fluorescence microscope. The TRITC fluorescence of cells, which had been treated with RDG liposomes, is distinctly more red than that of the control liposomes.
Pharmacokinetics (Blood Level and Organ Distribution of pH-Switchable Liposomes)
Liposomes of POPC/Chol (60:40), POPC/Hist-Chol/Chol (60:20:20) and POPC/DOTAP/Chems (60:10:30) (500 μL) were injected into the tail vein of male Wistar rats.
Liposome suspensions (50 mM) were prepared by hydrating a lipid film of the corresponding formulation (addition of 0.03 moles of C-DPPC) with 2 mL of a solution of 1 mg H-insulin in HEPES 10 mM, sodium-chloride 150 nm at a pH of 7.5). After 3 freezing and thawing cycles, the suspensions were extruded repeatedly through a 400 nm membrane (LiposoFast, Avestin). H-Insulin which had not been enclosed, was removed by gel filtration though a G-75 Sephadex-column and subsequent concentration over CENTRIPREP (Millipore) centrifuging units.
Liposome suspension (0.5 mL) was administered to 4 experimental animals per formulation and blood samples were taken after 5 minutes, 15 minutes, 60 minutes, 3 hours, 12 hours and 24 hours. The radioactivity of the membrane fraction and of the soluble cargo was measured by scintillation and gave the following values:
With their relatively long half-life in the blood, the inventive liposomes fulfill the basic prerequisites for a vector system. They are not acutely toxic and not absorbed immediately by their reticuloendothelial system. Up to the end of the experiment, the ratio of the 3[H] to the 14[C] radioactivity of the blood samples was constant. Release of the cargo by complement lysis therefore does not take place in any of the cases.