Patent Application
20140141072
The present invention relates to a preparation of a drug characterized by a specific physical form and a method for preparation thereof. The above physical form is a form of a core-shell type polymer micelle in which mainly a drug is encapsulated in a core part and in which a shell part comprises a hydrophilic polymer segment.
For the purpose of stably holding an active ingredient of medicine, the active ingredient is lyophilized and turned into a solid form. However, the stability of the active ingredient is not yet satisfactory in a certain case in such operation or even in the resulting solid form. It is described in JP-11/125635-A that in order to stabilize a gold colloid-containing lyophilized product sensitizing protein (particularly an antibody), saccharides such as sucrose and 6-cyclodextrin, threonine and aspartic acid are added to a sensitized gold colloid solution in lyophilization. Further, a lyophilized composition having the purpose of stabilizing an emulsion system regarded as containing a drug-encapsulating liposome using a phospholipid is described in JP-62/29513-A, and a solid carbohydrate which is pharmaceutically allowable is added to the above composition for the purposes of facilitating the reconstruction by water and enhancing the storage stability.
Thereafter, a drug-encapsulating liposome system using various modified phospholipids and a drug-encapsulating polymer micelle system using an amphiphilic block polymer have been proposed in order to achieve a specific drug delivery to the target. Both systems have intrinsic characteristics respectively, and therefore a large variety of the systems has been developed according to the purposes. It is known that in general, a polymer micelle system maintains an intermolecular micelle structure even when diluted to a so-called critical micelle concentration or lower and therefore has a solubilizing power as compared with the liposome system, so that it can stably be maintained to some extent.
As described above, it is said that a polymer micelle can relatively stably hold an encapsulated or sealed drug in a micelle, but from a practical point of view, the stability is not necessarily satisfactory in a state of an aqueous dispersion or solution of a micelle. Then, it is tried to lyophilize a polymer micelle solution. However, the polymer micelle particles are associated or coagulated in lyophilization due to various factors, and a growth in the particles and a deterioration in the resolubility in water are brought about in a certain case.
On the other hand, a large variety of methods is proposed as a method for preparing an aqueous dispersion or solution of such drug-encapsulating polymer micelle, but the aqueous dispersion or the solution obtained by any method has not been able to avoid causing the association or the coagulation described above between the polymer micelle particles when it is lyophilized as it is. The following typical methods for preparing a drug-encapsulating polymer micelle aqueous dispersion or solution (composition) are known.
A water-scarcely soluble drug is dissolved, if necessary, in a water-miscible organic solvent, and the resulting solution is mixed with a block copolymer-dispersed aqueous solution by stirring. Heating in mixing by stirring makes it possible in a certain case to accelerate sealing of the drug in a polymer micelle.
A water-immiscible organic solvent solution of a water-scarcely soluble drug is mixed with a block copolymer-dispersed aqueous solution, and the organic solvent is volatilized while stirring.
A water-scarcely soluble drug and a block copolymer are dissolved in a water-miscible organic solvent, and then the resulting solution is dialyzed to a buffer solution and/or water using a dialysis membrane.
d) Others (not described in the official gazettes described above)
A water-scarcely soluble drug and a block copolymer are dissolved in a water-immiscible organic solvent, and the resulting solution is mixed with water and stirred to form an oil-in-water (O/W) type emulsion, followed by volatilizing the organic solvent. Meanwhile, it is said that the respective methods described above have both merits and demerits. For example, in a) and b), an encapsulating rate of the drug into the polymer micelle is usually low; in c), the operation is complicated, and the polymer micelle can not be formed depending on the kind of the drug; and in d), the solution viscosity grows high depending on the kind of the block polymer and the kind of the drug, and the stirring operation is difficult in a certain case.
Accordingly, an object of the present invention is to provide a lyophilized preparation of a drug-encapsulating polymer micelle and which is inhibited particularly from association or coagulation between the polymer micelles and a composition which can conveniently be used for preparing such preparation.
The present inventors have found that even if a hydrophilic polymer segment is a drug-encapsulating polymer micelle system formed using a certain block copolymer comprising polyethylene glycol, the problems described above can be solved without exerting any adverse effect on the stability of the polymer micelle by carrying out lyophilization after adding polyethylene glycol and/or saccharides as a stabilizing agent.
Further, they have found that in producing a drug-encapsulating polymer micelle system (an aqueous dispersion or an aqueous solution), an aqueous dispersion or an aqueous solution of a drug-encapsulating polymer micelle can efficiently be obtained by preparing an aqueous solution of a block copolymer containing polyethylene glycol and/or saccharides and, if necessary, inorganic salts and a solution of a drug dissolved in a water-insoluble organic solvent and mixing and stirring both solutions thus obtained and that a lyophilized product showing an excellent solubilizing property without bringing about the problems described above, that is, association or coagulation between the polymer micelle particles is obtained by lyophilizing such dispersion or aqueous solution as it is.
Hence, according to the present invention, provided is an aqueous composition comprising a drug-encapsulating polymer micelle for preparing a lyophilized preparation of the drug-encapsulating polymer micelle, wherein:
(A) the composition further comprises at least one stabilizing agent selected from the group consisting of saccharides and polyethylene glycol and
(B) the above drug-encapsulating polymer micelle originates in a block copolymer having in a molecule, a hydrophilic polymer segment and a polymer segment which is hydrophobic or chargeable or which comprises the repetitive units of both of them, and it is a substantially spherical core-shell type micelle in which the drug is encapsulated principally in a core part and in which a shell part is constituted by the above hydrophilic polymer segment.
Provided as the present invention of a different embodiment is a drug-encapsulating polymer micelle preparation staying in a lyophilized form, wherein:
(a) the preparation comprises at least one stabilizing agent selected from the group consisting of saccharides and polyethylene glycol as an additional component,
(b) the above drug-encapsulating polymer micelle is formed from a block copolymer having in the molecule, a hydrophilic polymer segment and a hydrophobic or chargeable polymer segment or a polymer segment comprising the repetitive units of both of them, and it is a core-shell type micelle in which the drug is carried principally in a core part and in which a shell part is constituted by the above hydrophilic polymer segment and
(c) a drug-encapsulating polymer micelle solution which is homogeneously dispersed or solubilized is formed when the preparation is mixed with an aqueous medium.
Provided as the present invention of a further different embodiment are a novel process for producing a drug-encapsulating polymer micelle which can conveniently be utilized for preparing the aqueous composition and the drug-encapsulating polymer micelle preparation staying in a lyophilized form each described above, comprising the steps of
(A) preparing an aqueous dispersion comprising a block copolymer having a hydrophilic segment and a hydrophobic or chargeable polymer segment or a polymer segment comprising the repetitive units of both of them and at least one additive selected from the group consisting of saccharides, inorganic salts and polyethylene glycol,
(B) preparing an organic solution of a fat-soluble drug using a water-immiscible organic solvent and
(C) mixing the aqueous dispersion and the organic solution each obtained in the step (A) and the step (B) and volatilizing the organic solvent while stirring the mixed solution thus obtained to prepare an aqueous dispersion or an aqueous composition of a drug-encapsulating polymer micelle, and a production process for a drug-encapsulating polymer micelle preparation staying in a lyophilized form, comprising as an additional step, a step of lyophilizing the aqueous dispersion or the aqueous solution of the drug-encapsulating polymer micelle obtained in the step (C) described above.
The “drug-encapsulating polymer micelle” referred in the present invention is a molecular aggregate in which a block copolymer is associated in an aqueous medium and is a structural matter (or a particulate matter) staying in a state in which the drug is sealed or carried in an intramolecular micelle structure (mainly a core part). Usually, it is substantially spherical. When referred to as “substantially spherical” in the present specification, it means that at least 80%, preferably 90% or more and more preferably 98% or more of a particulate matter is spherical. Such drug-encapsulating polymer micelle maintains an intramolecular micelle structure even after diluted and can be present in an aqueous medium in a solubilizing state. The “aqueous medium” described above means water including deionized water, distilled water and sterilized water, buffer or isotonic water or a mixed solvent of a water-miscible organic solvent (for example, ethanol, acetone, acetonitrile, tetrahydrofuran and dimethylforamide) and water. The “aqueous composition” means a composition in which a drug-encapsulating polymer micelle stays in a solubilizing or dispersing state using the “aqueous medium” described above as a solvent or a dispersant. The aqueous composition stays preferably in a state containing substantially no organic solvent.
A block copolymer comprising a hydrophilic polymer segment (hereinafter referred to as the segment A) and a hydrophobic or chargeable polymer segment or a polymer segment comprising the repetitive units of both of them (hereinafter referred to as the segment B) can be used as a block copolymer which can form such polymer micelle. Such block copolymer includes “segment A-segment B” (AB type) and “segment A-segment B-(segment A)i” (wherein i is an integer of 1 or more). However, the AB type can be given as the preferred block copolymer.
A polymer constituting the segment A shall not be restricted, and polyethylene glycol (or polyoxyethylene), polysaccharide, polyvinylpyrrolidone and polyvinyl alcohol can be given. Among them, a polyethylene glycol segment can be given as the preferred segment. In general, the segment comprising 10 to 2500 repetitive units of oxyethylene is preferred, though shall not be restricted. The segment A may have any low molecular functional group or a molecular part (for example, a lower alkyl group, an amino group, a carboxyl group and a saccharide group, and among them, preferably a protein residue) at an end side opposite to a bonding end with the segment B as long as an adverse effect is not exerted in forming the polymer micelle.
On the other hand, the hydrophobic segment of the segment B shall not be restricted, and capable of being given are polyamino acid ester (polyaspartic acid ester, polyglutamic acid ester or partially hydrolyzed products thereof), poly(meth)acrylic acid ester, polylactide and polyester. Also, polyamines (for example, poly-di-lower alkylaminoalkylene (meth)acrylate), polyaspartic acid and polyglutamic acid can be given as the chargeable segment.
The AB type or ABA type block copolymer comprising such segment can form a polymer micelle by itself (no drug) in an aqueous medium if the segment B contained therein is a hydrophobic segment.
If a polymer micelle is formed in the coexistence of a fat-soluble drug, the drug is encapsulated or sealed in the polymer micelle, particularly a core part formed by a hydrophobic segment. On the other hand, if the segment B is a chargeable segment (for example, polyamine), a polymer micelle can usually be formed by an interaction with a drug (for example, oligo- or polynucleotide, to be specific, ribozime, oligo DNA such as antisense DNA, RNA or peptide) which can be charged to a charge reverse to that of polyamine. The segment B can have the low molecular functional group or the molecular part each described above as long as an adverse effect is not exerted on the interaction of the drug with the segment B when a polymer micelle is formed at an end opposite to a bonding end with the segment A.
Polymers themselves or polymers derived from them described in, for example, JP-2777530-B (or U.S. Pat. No. 5,449,513-B), WO96/32434, WO96/33233, WO97/06202 and Kataoka K. et al., Macromolecules, 1999, 32, 6892 to 6894 can be given as the typical ones of the block copolymer described above.
The typical example of the bloc copolymer in which the segment A contains a polyethylene glycol segment and in which the segment B comprises a polyamino acid ester (in a certain case, −CO— polyamino acid) segment can be represented, though not restricted, by the following Formula (I) or (II):
wherein
R1 and R3 each represent independently a hydrogen atom or a lower alkyl group substituted or not substituted with a functional group which may be protected;
R2 represents a hydrogen atom, a saturated or unsaturated C1 to C29 aliphatic carbonyl group or an arylcarbonyl group;
R4 represents a hydroxyl group, a saturated or unsaturated C1 to C30 aliphatic oxy group or an aryl-lower alkyloxy group;
R5 represents a phenyl group, a C1 to C4 alkyl group or a benzyl group;
L1 and L2 each represent independently a linkage group;
n is an integer of 10 to 2500;
x and y are different or the same and are an integer in which the total of them is 10 to 300; either one of x and y is 0 or x to y falls in a range of 7:3 to 1:3; and when both are present, x and y each are present at random. The functional group allowed to be protected includes a hydroxyl group, an acetal group, a ketal group, an aldehyde group, a sucrose residue. When R1 and R3 represent a lower alkyl group which is substituted with a functional group allowed to be protected, the hydrophilic segment can be formed according to the methods described in WO96/33233, WO96/32434 and WO97/06202.
The linkage group can be changed principally according to the production process of the block copolymer and therefore shall not be restricted. To be specific, L1 is a group selected from the group consisting of —NH—, —O—, —O—Z—NH—, —CO—, —CH2—, —O—Z—S—Z— and —OCO—Z—NH— (wherein Z is independently a C1 to C4 alkylene group), and L2 is a group selected from the group consisting of —OCO—Z—CO— and —NHCO—Z—CO— (wherein Z is a C1 to C4 alkylene group).
The aqueous composition for preparing a lyophilized preparation of a drug-encapsulating polymer micelle according to the present invention can be obtained by adding a stabilizing agent in preparing a polymer micelle under the coexistence of the block copolymer and the drug each described above according to a conventionally known method (for example, the methods described in the publications described above) or after preparing the polymer micelle and, if necessary, after exchanging an aqueous medium for solubilizing or dispersing the polymer micelle and, if necessary, by homogeneously mixing them. Accordingly, the above composition usually contains the drug-encapsulating polymer micelle and the stabilizing agent in the aqueous medium.
The stabilizing agent which can be used in the present invention may be a combination of at least one selected from the group consisting of any saccharides and polyethylene glycol. Such saccharides shall not be restricted, and maltose, trehalose, xylitol, glucose, sucrose, fructose, lactose, mannitol and dextrin can be given.
On the other hand, polyethylene glycol having 4 to 5000, preferably 10 to 2500, more preferably 20 to 800 and particularly preferably 20 to 200 oxyethylene (that is, —(OCH2CH2)—) units can be given as polyethylene glycol. Macrogol 1000, 1540, 4000, 6000, 20000 and 35000 each described in, for example, a medical additive cyclopedia can be used for such polyethylene glycol.
In the present specification, the term of “poly” is used when referring to polyethylene glycol, the segment A and the segment B, and it is understood that the meaning of so-called “oligo” is included as well therein in a suited example as can be seen in the example of polyethylene glycol described above.
In the foregoing composition of the present invention, polyethylene glycol alone (allowed to contain a plurality of polyethylene glycols described above having different molecular weights) or a combination of polyethylene glycol and saccharides in a proportion of 1 to 0.1:0.1 to 1 in terms of a weight ratio is added as the stabilizing agent. In respect to an addition proportion of the drug-encapsulating polymer micelle to the stabilizing agent, the suitable proportion thereof is varied depending on the kinds of the drug-encapsulating polymer micelle and the stabilizing agent and therefore can not be restricted, and a proportion of the micelle thereto is usually 1 to 0.1:0.01 to 1 in terms of a weight of the block copolymer used.
When a concentration (in terms of a polymer weight) of the drug-encapsulating polymer micelle in the above composition is 1 to 90 (weight) %, a concentration of polyethylene glycol added to the micelle solution which is such composition is preferably 0.5 to 10% by weight. On the other hand, a concentration of saccharides is 0 to 15% by weight (when added, it can be 0.5 to 15% by weight). Further, such composition is preferably adjusted to a pH of 4.0 to 7.5 from the viewpoint of subsequent lyophilization. Accordingly, the above composition can contain a buffering agent, salts and an antioxidant (for example, ascorbic acid, ascorbates and thiosulfates).
The drug which is encapsulated or sealed in the drug-encapsulating polymer micelle described above may be any drug as long as they are such drugs as can achieve the objects of the present invention, and drugs falling in a category of a fat-soluble drug can usually be given. In this case, the term “fat-soluble” means a property of a compound which can be dissolved in, for example, an organic solvent such as dichloromethane, diethyl ether and ethyl acetate capable of being applied to a production process for a drug-encapsulating polymer micelle described later, and it means as well a property of a compound which can be dissolved in a mixed solvent of dimethylformamide and dimethylsulfoxide.
The examples of the fat-soluble drug include, though not restricted, anticancer drugs comprising paclitaxel, topotecan, camptothecine, cisplatin, daunorubicin, methotrexate, mitomycin C, docetaxel, binclestin and derivatives thereof, polyene base antibiotics, for example, anphoterisin B and nystatin and in addition thereto, fat-soluble drugs such as prostaglandins and derivatives thereof.
Among them, paclitaxel, topotecan and docetaxel are strongly intended to be used in the present invention.
The drug-encapsulating polymer micelle described above may be obtained by a conventionally known production process as described above, and it can conveniently be obtained as well by the following production process for a drug-encapsulating polymer micelle which is another embodiment of the present invention.
According to the production process of the above present invention, prepared is an aqueous dispersion comprising the block copolymer described above and at least one additive selected from the group consisting of saccharides, inorganic salts and polyethylene glycol. Saccharides and polyethylene glycol which can be used as the additive can be the same as those given as the examples of the “stabilizing agent” described above. On the other hand, any compounds can be used as the inorganic salts in the present invention as long as they meet the objects of the present invention and are pharmaceutically allowable, and the preferred salts include chlorides such as sodium chloride, potassium chloride, magnesium chloride and calcium chloride.
The aqueous dispersion described above can be prepared by adding the block copolymer and the respective additives to water at the same time and stirring them or preparing in advance the aqueous solution of the additives and adding the block copolymer thereto, or preparing a mixture in an inverse order to the above and stirring and mixing it. A supersonic wave as well as conventional stirrers may be used for stirring. Such dispersion shall not be restricted, and capable of being usually added are the block copolymer in a concentration of 0.1 to 40% by weight, the saccharides in a concentration of 0.5 to 15% by weight, polyethylene glycol in a concentration of 0.5 to 10% by weight and the inorganic salts in a concentration of 0.5 to 10% by weight.
According to the present invention, an organic solution in which the drug described above is dissolved in a water-immiscible organic solvent is prepared. Such solvent shall not be restricted and includes dichloromethane, chloroform, diethyl ether, dibutyl ether, ethyl acetate, butyl acetate and mixed solvents thereof. A suitable drug concentration in the above solution is varied depending on the combination of the solvent and the drug used, and it can usually be a concentration of 0.1 to 10% by weight. The mixing operation described above can be carried out at a room temperature or a lower temperature.
Both of the aqueous dispersion and the organic solution thus prepared are mixed at one time or the latter is slowly added to the former, or a reverse procedure thereto is carried out to prepare a mixed solution, and the mixed solution is subjected to stirring treatment (including supersonic treatment) for enough time for the drug to be encapsulated or sealed in a polymer micelle. Such treatment is better carried out at a room temperature or a lower temperature (about 5° C.). The organic solvent may be volatilized through the stirring treatment.
A drug-encapsulating polymer micelle dispersion is obtained by the operations described above, and saccharides and polyethylene glycol are added, if necessary, to the above dispersion as described above, whereby the drug-encapsulating polymer micelle can be stabilized in, for example, lyophilization treatment which shall be carried out subsequently or coagulation between the micelle particles can be inhibited. Saccharides and/or polyethylene glycol are preferably added so that the respective final concentrations thereof based on the total weight of the drug-encapsulating polymer micelle composition are 0.1 to 15% by weight in the case of saccharides and 0.5 to 10% by weight in the case of polyethylene glycol, considering whether or not they are added in preparing the drug-encapsulating polymer micelle dispersion described above. However, they may be added in such concentrations as exceeding the concentrations described above as long as an adverse effect is not exerted in preparing the lyophilized product of the drug-encapsulating polymer micelle and restructuring the resulting lyophilized product in an aqueous medium. Further, a pH in preparing the preparation of the present invention is preferably 4.0 to 7.5, and a pH controlling agent and an antioxidant (ascorbic acid, sodium ascorbate and sodium thiosulfate) can be added if necessary.
In the production process of the present invention described above in details, the raw materials and the additives used are common to those of the aqueous composition of the present invention as described above. Accordingly, the drug-encapsulating polymer micelle dispersion obtained by the above production process can be the above aqueous composition as it is.
The drug-encapsulating polymer micelle dispersion or the aqueous composition of the present invention produced according to the production process of the present invention can provide a lyophilized drug-encapsulating polymer micelle preparation by a normal process for lyophilization, for example, by freezing the above liquid composition at −1 to −60° C. and then drying it under reduced pressure. The drug-encapsulating polymer micelle preparation thus obtained having a lyophilized form falls as well in one embodiment of the present invention. Such drug-encapsulating polymer micelle preparation forms a homogeneously dispersed or solubilized drug-encapsulating polymer micelle solution when mixed with an aqueous medium. Further, an average particle diameter of the above micelle present in the above solution (restructure after lyophilization) is scarcely different from an average particle diameter of the drug-encapsulating polymer micelle present in the composition described above before lyophilization, or if different, it usually grows large up to about twice, and nothing more.
The present invention shall be explained below in further details with reference to specific examples, but the present invention shall not be intended to be restricted to these examples.
Polyethylene glycol (molecular weight: 12000)-co-50% partially hydrolyzed polybenzyl aspartate (n=50) (hereinafter referred to as PEG-PBLA12-50. PH. 50%) 500 mg was weighed in a screw tube bottle, and 50 mL of dichloromethane was added thereto and stirred to dissolve it. Next, the dichloromethane solution was concentrated up to 5 mL by blowing nitrogen gas, and 50 mL of water was added thereto and vigorously stirred for 30 minutes. Then, the stopper was opened, and the solution was stirred in a cold place for a whole day and night to prepare a polymer micelle. Then, supersonic treatment was carried out, and various saccharides shown in Table 1 were added and dissolved in a concentration of 40 to 160 mg/mL. The solution was frozen in a dry ice-acetone freezing mixture to prepare a lyophilized preparation. Further, a preparation in which no saccharides were added was prepared as a comparative lyophilized preparation.
A micelle solution before lyophilization and a micelle solution obtained by lyophilizing the micelle solution and then redissolving it in water were measured for a particle size by means of a dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.), and the resolubility after lyophilization was visually evaluated after adding 10 mL of water to 50 mg of the lyophilized product. (Evaluation criteria; good: redissolved in shorter than 15 seconds when lightly shaken by a hand at a room temperature, average: redissolved in 15 seconds or longer and shorter than 2 minutes when lightly shaken by a hand at a room temperature, bad: redissolved in 2 minutes or longer or partially not redissolved when lightly shaken by a hand at a room temperature, and a block remained). The results thereof are shown in Table 1.
PEG-PBLA12-50. PH. 50% can be shown by the following formula:
PEG-PBLA12-50. PH. 50% 500 mg was weighed in a screw tube bottle, and 50 mL of dichloromethane was added thereto and stirred to dissolve it. Next, the dichloromethane solution was concentrated up to 5 mL by blowing nitrogen gas, and 50 mL of water was added thereto and vigorously stirred for 30 minutes. Then, the stopper was opened, and the solution was vigorously stirred in a cold place for a whole day and night to prepare a polymer micelle. Thereafter, supersonic treatment was carried out, and various Macrogols shown in Table 2 were added and dissolved in a concentration of 20 mg/mL. The solution was frozen in a dry ice-acetone freezing mixture to prepare a lyophilized preparation.
A micelle solution before lyophilization and a micelle solution obtained by lyophilizing the micelle solution and then redissolving it in water were measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.), and the resolubility after lyophilization was visually evaluated after adding 10 mL of water to 50 mg of the lyophilized product. The results thereof are shown in Table 2 (the evaluation criteria are the same as in Table 1).
PEG-PBLA12-50. PH. 50% 500 mg was weighed in a screw tube bottle, and 50 mL of dichloromethane was added thereto and stirred to dissolve it. Next, the dichloromethane solution was concentrated up to 5 mL by blowing nitrogen gas, and 50 mL of water was added thereto and vigorously stirred for 30 minutes. Then, the stopper was opened, and the solution was vigorously stirred in a cold place for a whole day and night to prepare a polymer micelle. Thereafter, supersonic treatment was carried out, and maltose was added and dissolved in a concentration of 40 mg/mL. Further, various Macrogols shown in Table 3 were added and dissolved in a concentration of 20 mg/mL, and the solution was frozen in a dry ice-acetone freezing mixture to prepare a lyophilized preparation.
A micelle solution before lyophilization and a micelle solution obtained by lyophilizing the micelle solution and then redissolving it in water were measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.), and the resolubility after lyophilization was visually evaluated after adding 10 mL of water to 50 mg of the lyophilized product. The results thereof are shown in Table 3.
PEG-PBLA12-50. PH. 50% 500 mg was weighed in a screw tube bottle, and 50 mL of dichloromethane was added thereto and stirred to dissolve it. Next, the dichloromethane solution was concentrated up to 5 mL by blowing nitrogen gas, and 50 mL of water was added thereto and vigorously stirred for 30 minutes. Then, the stopper was opened, and the solution was stirred in a cold place for a whole day and night to prepare a polymer micelle. Thereafter, supersonic treatment was carried out, and various saccharides shown in Table 4 and Macrogol 4000 were added and dissolved in a concentration of 20 to 40 mg/mL and a concentration of 0 to 40 mg/mL respectively. The solution was frozen in a dry ice-acetone freezing mixture to prepare a lyophilized preparation.
A micelle solution before lyophilization and a micelle solution obtained by lyophilizing the micelle solution and then redissolving it in water were measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.), and the resolubility after lyophilization was visually evaluated after adding 10 mL of water to 50 mg of the lyophilized product. The results thereof are shown in Table 4.
Paclitaxel 100 mg and PEG-PBLA12-50. PH. 50% 500 mg were weighed in a screw tube bottle, and 50 mL of dichloromethane was added thereto and stirred to dissolve them. Next, the dichloromethane solution was concentrated up to 5 mL by blowing nitrogen gas, and 50 mL of a 5% sodium chloride aqueous solution was added thereto and vigorously stirred for 30 minutes. Then, the stopper was opened, and the solution was vigorously stirred in a cold place for a whole day and night. After desalinating by means of ultrafiltration, supersonic treatment was carried out, and various saccharides shown in Table 5 and Macrogol 4000 were added and dissolved in a concentration of 40 mg/mL and a concentration of 10 to 30 mg/mL respectively. The solution was frozen in a dry ice-acetone freezing mixture to prepare a lyophilized preparation. Further, a preparation in which the saccharides and Macrogol 4000 were not added was prepared as a comparative lyophilized preparation.
A micelle solution before lyophilization and a micelle solution obtained by lyophilizing the micelle solution and then redissolving it in water were measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.), and the resolubility after lyophilization was visually evaluated after adding 10 mL of water to 50 mg of the lyophilized product. The results thereof are shown in Table 5.
Paclitaxel 60 mg and PEG-PBLA12-50. PH. 50% 300 mg were weighed in a screw tube bottle, and 30 mL of dichloromethane was added thereto and stirred to dissolve them. Next, the dichloromethane solution was concentrated up to 3 mL by blowing nitrogen gas, and 30 mL of a 40 mg/mL maltose aqueous solution was added thereto. The bottle was tightly stoppered and vigorously stirred in a refrigerator for 30 minutes. Then, the stopper was opened, and supersonic treatment was carried out while vigorously stirring in the refrigerator for a whole day and night. Further, Macrogol 4000 was added and dissolved in a concentration of 20 mg/mL, and the solution was sterilized, filtered and then frozen in a dry ice-acetone freezing mixture to prepare a lyophilized preparation.
A micelle solution before lyophilization and a micelle solution obtained by lyophilizing the micelle solution and then redissolving it in water were measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.), and the resolubility after lyophilization was visually evaluated after adding 10 mL of water to 50 mg of the lyophilized product. The results thereof are shown in Table 6.
A polyethylene glycol-poly(α,β-aspartic acid) block polymer PEG-P(Asp)BP and a poly(α,β-aspartic acid) block homopolymer P(Asp)HP were dissolved in a cisplatin (hereinafter referred to as CDDP) aqueous solution of 15 mg/mL (5 mmmol/mL) so that a mole ratio (CDDP/Asp) of cisplatin to an Asp residue was 1.0, and the solution was shaken at 37° C. for 72 hours to thereby prepare a micelle. The micelle solution thus obtained was refined by carrying out ultrafiltration through a membrane having a fractioned molecular weight of 100,000, and maltose and Macrogol 4000 were added to this refined micelle aqueous solution and dissolved in a concentration of 40 mg/mL and a concentration of 10 mg/mL respectively. The solution was frozen in a dry ice-acetone freezing mixture to prepare a lyophilized preparation.
A micelle solution before lyophilization and a micelle solution obtained by lyophilizing the micelle solution and then redissolving it in water were measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.), and the resolubility after lyophilization was visually evaluated after adding 10 mL of water to 50 mg of the lyophilized product. The results thereof are shown in Table 7.
Beraprost 50 mg and PEG-PBLA12-50. PH. 50% 300 mg were weighed in a screw tube bottle, and 30 mL of dichloromethane was added thereto and stirred to dissolve them. Next, the dichloromethane solution was concentrated up to 3 mL by blowing nitrogen gas, and 30 mL of a 40 mg/mL maltose aqueous solution was added thereto. The bottle was tightly stoppered and vigorously stirred in a refrigerator for 30 minutes. Then, the stopper was opened, and supersonic treatment was carried out while vigorously stirring in the refrigerator for a whole day and night. Further, Macrogol 4000 was added and dissolved in a concentration of 20 mg/mL, and the solution was sterilized, filtered and then frozen in a dry ice-acetone freezing mixture to prepare a lyophilized preparation.
A micelle solution before lyophilization and a micelle solution obtained by lyophilizing the micelle solution and then redissolving it in water were measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.), and the resolubility after lyophilization was visually evaluated after adding 10 mL of water to 50 mg of the lyophilized product. The results thereof are shown in Table 8.
Further, the present invention shall more specifically be explained below with reference to comparative production examples of drug-encapsulating polymer micelles and production examples thereof according to the present invention.
Paclitaxel 20 mg and polyethylene glycol (molecular weight: 12000)-co-50% partially hydrolyzed polybenzyl aspartate (n=50) (hereinafter referred to as PEG-PBLA12-50. PH. 50%) 100 mg were weighed in a screw tube bottle, and 10 mL of dichloromethane was added thereto and stirred to dissolve them. Next, dichloromethane was volatilized by blowing nitrogen gas to dry up the solution. Further, 1 mL of dichloromethane was added thereto and slowly stirred so that the sample adhered on the tube wall was dissolved as well, whereby the residue was redissolved so that a homogeneous state was obtained. A 5% sodium chloride aqueous solution 10 mL was added thereto, and the bottle was tightly stopper and vigorously stirred for 30 minutes. Then, the stopper was opened, and the solution was vigorously stirred in a cold place for a whole day and night. After desalinating by means of ultrafiltration, supersonic treatment (130 W, 1 sec Pulse, 10 minutes) was carried out, and a part of the sample was taken and measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.). Further, maltose and Macrogol 4000 were added and dissolved in a concentration of 40 mg/mL and a concentration of 20 mg/mL respectively, and the solution was frozen in a dry ice-acetone freezing mixture to prepare a lyophilized preparation. The average particle diameter after the supersonic treatment was 97.5 nm. Time passing up to the supersonic treating step was 32 hours.
Paclitaxel 60 mg and PEG-PBLA12-50. PH. 50% 300 mg were weighed in a screw tube bottle, and 30 mL of dichloromethane was added thereto and stirred to dissolve them. Next, dichloromethane was volatilized by blowing nitrogen gas to dry up the solution. Further, 3 mL of dichloromethane was added thereto and slowly stirred so that the sample adhered on the tube wall was dissolved as well, whereby the residue was redissolved so that a homogeneous state was obtained. A 40 mg/mL maltose aqueous solution 30 mL was added thereto, and the bottle was tightly stoppered and vigorously stirred in a refrigerator for 30 minutes. Then, the stopper was opened, and the solution was vigorously stirred in the refrigerator for a whole day and night. Supersonic treatment (130 W, 1 sec Pulse, 10 minutes) was carried out, and a part of the sample was taken and measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.). Further, Macrogol 4000 was added and dissolved in a concentration of 20 mg/mL, and the solution was sterilized, filtered and then frozen in a dry ice-acetone freezing mixture to prepare a lyophilized preparation.
The average particle diameter after the supersonic treatment was 111.4 nm.
Time passing up to the supersonic treating step was 25 hours.
Beraprost 30 mg and PEG-PBLA12-50. PH. 50% 300 mg were weighed in a screw tube bottle, and 30 mL of dichloromethane was added thereto and stirred to dissolve them. Next, dichloromethane was volatilized by blowing nitrogen gas to dry up the solution. Further, 3 mL of dichloromethane was added thereto and slowly stirred so that the sample adhered on the tube wall was dissolved as well, whereby the residue was redissolved so that a homogeneous state was obtained. A 5% sodium chloride aqueous solution 30 mL was added thereto, and the bottle was tightly stoppered and vigorously stirred at a room temperature for 60 minutes. Then, the stopper was opened, and the solution was vigorously stirred at a room temperature for a whole day and night. Supersonic treatment (130 W, 1 sec Pulse, 10 minutes) was carried out, and a part of the sample was taken and measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.). Further, the solution was desalinated by means of ultrafiltration, sterilized and then filtered to obtain a preparation.
The average particle diameter after the supersonic treatment was 72.2 nm.
Time passing up to the supersonic treating step was 32 hours.
Paclitaxel 10 mg and PEG-PBLA12-50. PH. 50% were dissolved in 5 mL of DMSO (dimethylsulfoxide), and the solution was dialyzed to 100 mL of a physiological salt solution through a dialysis membrane (fractioned molecular weight: 12-14000) for 16 hours.
As a result thereof, the dialyzed sample was precipitated and did not have a micelle form.
Paclitaxel 10 mg and PEG-PBLA12-50. PH. 50% were dissolved in 5 mL of DMF (dimethylformamide), and the solution was dialyzed to 100 mL of a physiological salt solution through a dialysis membrane (fractioned molecular weight: 12-14000) for 16 hours.
As a result thereof, the dialyzed sample was precipitated and did not have a micelle form.
PEG-PBLA12-50. PH. 50% 300 mg was weighed in a screw tube bottle, and a 40 mg/mL maltose aqueous solution 30 mL was added thereto and stirred to prepare a dispersion. The dispersion was cooled down to 4° C. while further stirring. Further, a 20 mg/mL paclitaxel dichloromethane solution 3 mL was added thereto, and the mixture was stirred in a refrigerator for 16 hours without tightly stoppering. Then, supersonic treatment (130 W, 1 sec Pulse, 10 minutes) was carried out, and a part of the sample was taken and measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.). Further, the solution was sterilized, filtered and then frozen in a dry ice-acetone freezing mixture to prepare a lyophilized preparation.
The average particle diameter after the supersonic treatment was 107.3 nm.
Time passing up to the supersonic treating step was 19 hours.
PEG-PBLA12-50. PH. 50% 300 mg was weighed in a screw tube bottle, and a 40 mg/mL maltose aqueous solution 30 mL was added thereto and stirred to prepare a dispersion. The dispersion was cooled down to 4° C. while further stirring. Further, a 20 mg/mL paclitaxel dichloromethane solution 3 mL was added thereto, and the mixture was stirred in a refrigerator for 16 hours without tightly stoppering. Then, supersonic treatment (130 W, 1 sec Pulse, 10 minutes) was carried out, and a part of the sample was taken and measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.). Further, Macrogol 4000 was added and dissolved in a concentration of 20 mg/mL, and the solution was sterilized, filtered and then frozen in a dry ice-acetone freezing mixture to prepare a lyophilized preparation.
The average particle diameter after the supersonic treatment was 107 nm.
Time passing up to a supersonic treating step was 19 hours.
PEG-PBLA12-50. PH. 50% 300 mg was weighed in a screw tube bottle, and a 5% sodium chloride aqueous solution 30 mL was added thereto and stirred to prepare a dispersion. Further, a 10 mg/mL beraprost dichloromethane solution 3 mL was added thereto, and the mixture was then vigorously stirred at a room temperature for a whole day and night. Supersonic treatment (130 W, 1 sec Pulse, 10 minutes) was carried out, and a part of the sample was taken and measured for a particle size by means of the dynamic light scattering particle size meter (DLS-7000DH type, manufactured by Ohtsuka Electron Co., Ltd.). Then, the solution was desalinated by means of ultrafiltration, sterilized and filtered to obtain a preparation.
The average particle diameter after the supersonic treatment was 72.1 nm.
Time passing up to a supersonic treating step was 25 hours.
According to the present invention, provided are a composition capable of providing a stable aqueous medical preparation which does not substantially cause coagulation between micelle particles when a drug-encapsulating polymer micelle staying in a lyophilized state is redissolved in water, and a process in which the composition can conveniently be produced.
Accordingly, the present invention can be applied to the medical field, particularly the medicinal production industry.
| Number | Date | Country | Kind |
|---|---|---|---|
| 2001-213617 | Jul 2001 | JP | national |
| 2001-213652 | Jul 2001 | JP | national |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 13358025 | Jan 2012 | US |
| Child | 14164818 | US | |
| Parent | 10483677 | Jan 2004 | US |
| Child | 13358025 | US |
