Patent Application
20070292524
The present invention is directed to a delivery vehicle containing nanoparticles. The present invention is further directed to a pharmaceutical composition, comprising said drug delivery vehicle. Further, the invention pertains to a method for manufacturing of said delivery vehicles as well as to the use of these vehicles in medicine.
While many drugs are able to cross biological barriers like the bbb, others do not pass those barriers efficiently or not at all and are only effective when given directly into the target tissue. Thus, many potentially potent drugs are not useful clinically due to their inability to pass biological barriers like the bbb.
A number of approaches have been described in the prior art to increase drug penetration through the biological barriers.
One approach has been to alter the function of the barrier, for example the bbb itself. For instance, osmotic agents, when given peripherally (such as by intravenous injection), result in the opening of the bbb. Further, some drugs acting on the CNS can change the permeability of the bbb for other substances; cholinomimetic arecolines, for instance, have been reported to induce changes of drug penetration through the bbb [Saija, A., Princi, P., De Pasquale, R., Costa, G., “Arecoline but not haloperidol produces changes in the permeability of the blood-brain barrier in the rat.” J. Pharm. Pha. 42:135-138 (1990)].
Another approach resides in the modification of the drug molecules themselves. For instance, macromolecules, such as proteins, do not pass the bbb at all. For example, one can first isolate the macromolecule active site, i.e., the portion of the molecule which triggers the biologically desirable event, and then use only this active site. Since size is one of the factors in allowing permeability of the bbb, the reduced size is used in the hope that the smaller molecule can now pass the bbb. Other modifications of macromolecules to attempt passage of the bbb include glycating the proteins, thereby enhancing their permeability of the bbb, or forming a prodrug.
U.S. Pat. No. 5,260,308 discusses glycating proteins, while U.S. Pat. No. 4,933,324 and WO 89/07938 disclose the formation of a prodrug. These prodrugs are formed from a fatty acid carrier and a neuroactive drug which is unable to pass the bbb on its own. A similar system is disclosed in WO89/07938.
Still another approach is the implantation of controlled release polymers which release the active ingredient from a matrix-system directly into the nervous tissue. However, this approach is invasive and requires surgical intervention if implanted directly into the brain or spinal cord [see Sabel et al., U.S. Pat. No. 4,883,666; and Sabel et al., U.S. patent application Ser. No. 07/407,930].
To overcome these limitations, another approach has been tried in which drug carrier systems are used such as liposomes, erythrocyte ghosts, antibody-conjugates, and monoclonal antibody conjugates. One of the major problems in targeted drug delivery is the rapid opsonization and uptake of injected carriers by the reticuloendothelial system (RES), especially by the macrophages in the liver and spleen. This obstacle may be partially overcome in the case of liposomes by incorporation of so-called “stealth” lipids, such as phosphatidylinositol, monosialoganglioside, or sulfogalactosylceramide. However, all of these systems lack the versatility to permit a wide-range application in medicine.
A further approach to carry and direct drugs to a desired target tissue is disclosed in WO 95/022963. Therein, a drug targeting system is disclosed comprising nanoparticles made of a polymeric material, said nanoparticles comprising a drug to be delivered to said mammal and a surfactant coating deposited thereon; and a physiologically acceptable carrier and/or diluent allowing the transport of said nanoparticles to the target within the mammal after administration. In this approach, nanoparticles are used comprising polymeric particles having a diameter of preferably <1.000 nm. In
WO 95/022963 does neither contain any information regarding a multilayered polymer coating on a core particle comprising a drug, nor regarding the precise thickness of the coating layer. Furthermore, the nanoparticles used therein are designed as “targeting system” having the object to allow non-penetrating and penetrating drugs to pass the bbb more easily. The term “nanoparticle” as used therein denotes a carrier structure which is sufficiently resistant to chemical and/or physical destruction by the environment of use such that a sufficient amount of the nanoparticles remain substantially intact after injection into the blood stream, or given intraperitoneally or orally, so as to be able to reach the brain at the bbb. WO 95/022963 does not disclose to design and use nanoparticles as a drug delivery vehicle which is a) capable of crossing all major types of biological barriers, for example bbb or mucosa barriers and b) which can achieve a modified release, for example a sustained release or prolonged release, activity in the target tissue after having crossed the biological barrier.
WO 00/041647 relates to a sustained delivery of nucleic acids and other polyionic bioactive agents. In particular, it describes compounds and methods for delivering a polyionic bioactive composition such as a nucleic acid to a tissue of an animal. The compounds include compounds which comprise a matrix comprising the polyionic bioactive agent and wherein at least most of the polyionic bioactive agent at the exterior portion of the matrix is present in a condensed form.
WO 96/20698 provides a sustained release drug delivery system comprising nanoparticles, preferably surface-modified nanoparticles. The nanoparticles have a core of biodegradable, biocompatible polymer or biomaterial. The average diameter of the nanoparticles is typically less than about 300 nm, preferably in the range of 100 nm to 150 nm, and more preferably 10 nm to 50 nm, with a narrow size distribution. The polymeric core may have a bioactive, or bioinactive, agent or combination of agents, incorporated, embedded, entrained, or otherwise made part of the polymer matrix comprising the nanoparticle core. The incorporated bioactive agent is released as the polymer hydrolyzes and dissolves, thereby biodegrading. In WO 96/20698, the sustained release is not achieved by one or more polymeric layers coated on a drug core, but by the degradation of the polymer matrix, in which the drug is distributed. The bioactive agent is added to the polymeric material in forming the nanoparticles.
Therefore, it is an object of the invention to provide a delivery vehicle for a pharmaceutical agent which can be specifically adapted to desired release characteristics. It is in particular an object of the invention to provide a delivery vehicle which is suitable to be used for varying medical conditions and which is able to specifically cross the major physiological or biological barriers of the animal or human body and which subsequently is showing modified release characteristics such as sustained release or prolonged release of the drug in the target tissue. It is a further object of the present invention to provide a method of producing nanoparticles for drug delivery. It is also an object of the present invention to provide an improved method for the manufacture of drug delivery vehicles, which vehicles can be obtained in high yield and solid content. Furthermore, it is an object of the present invention to provide a method for the manufacture of drug delivery vehicles, which is suitable for the large-scale production of said vehicles. These objects are achieved by the subject-matter of the independent claims. Preferred embodiments are set forth in the dependent claims.
The present invention provides, according to one aspect, a new delivery vehicle containing nanoparticles, said nanoparticles comprising:
a) a core particle comprising one or more pharmaceutical agents; and
b) one or more coating layers having a thickness of between 10 and 200
A coated on said core particle, the coating layers comprising one or more biodegradable polymeric materials.
In other words, the present invention provides a targeting system, wherein the pharmaceutical agent or drug forms the core component which is coated by one or more layers of one or more polymeric materials. Thus, the core component preferably is essentially free of any polymeric material and thus is consisting only of the pharmaceutical agent(s) and optionally one or more carriers. According to a preferred embodiment, the delivery vehicle is comprising at least two coating layers of one or more polymeric materials.
The present invention offers a new approach of nanoparticle based drug delivery vehicles in that nanoparticles were developed containing a core comprising a pharmaceutical agent and a multilayered coating comprising distinct layers of polymeric materials. Thus, the present invention for the first time offers the possibility to construct a delivery vehicle, which is
a) capable of transporting drugs across physiological barriers as defined below in order to reach a target tissue or organ, and
b) providing specific release characteristics, which are precisely adapted to the individual medical condition/disease.
For example, the delivery vehicle or the pharmaceutical composition in which it is contained may show a prolonged release or sustained release of the one or more pharmaceutical agents in vivo.
Additionally, the multilayered structures open up the possibility of designing nanoparticles having combined characteristics of initial release (or burst release) of one drug, and, subsequently, of sustained or prolonged release of the same or a different drug, to the target tissue or organ.
Such a nanoparticle could, for example, comprise a drug core as indicated above coated with a first polymeric material, which polymeric coating layer provides a sustained or prolonged release of the drug contained in the core, and, coated thereon, a layer containing a further dose of a pharmaceutical agent. This outer layer could additionally be coated by a rapidly degradable coating layer of a polymeric material or, alternatively, could be uncoated, in order to provide a rapidly releasing initial dose of the pharmaceutical agent.
In the present invention, it unexpectedly turned out that coating layers having a thickness of between 10 A and 200 A are suitable for achieving the above results.
The term “nanoparticles” as used herein generally denotes a carrier structure which is biocompatible and sufficiently resistant to chemical and/or physical destruction by the environment of use such that a sufficient amount of the nanoparticles remain substantially intact after entry into the human or animal body following intraperitoneal or oral or intravenous administration so as to be able to reach the desired target organ or tissue, e.g. the brain, the liver, the kidneys, the lungs etc.
According to a preferred embodiment, said nanoparticles have a diameter of between 1 nm and 20 μm, preferably between 10 nm and 10 μm and most preferably between 100 nm and 1,000 nm.
Furthermore, the nanoparticles as defined above preferably comprise a surfactant coating deposited thereon. A treatment of the nanoparticles with a sufficient coating of an appropriate surfactant allows the adsorbed drug to better traverse physiological barriers as the bbb. Reference is made to several documents disclosing this effect, in particular to WO 95/22963, which is incorporated herein in its entirety.
According to a further embodiment, in the drug delivery vehicle of the present invention, the nanoparticles comprise between 2-100, preferably 5-50, most preferably 10-20 coating layers each comprising one or more biodegradable polymeric materials.
As mentioned above, the present invention opens up the possibility of combining different pharmaceutical agents and/or several coating layers containing one or more polymeric materials in order to achieve the desired result. Thus, in an embodiment, the one or more coating layers may comprise different biodegradable polymeric materials or mixtures of biodegradable polymeric materials in each layer.
The biodegradable polymeric material preferably comprises solid or film forming polymers, preferably alkylcyanoacrylates, more preferably butylcyanoacrylates, polylactic acid and polybutyric acid and mixtures and derivatives thereof.
As used herein, the terms “biodegradable polymer” denotes any synthetic or naturally-derived polymeric material which is known as being suitable for uses in the body of a living being, i.e., is biologically inert and physiologically acceptable, non-toxic, and, in the delivery systems of the present invention, is biodegradable in the environment of use, i.e., can be resorbed by the body.
Illustrative biodegradable materials suitable for use in the practice of the invention include naturally derived polymers, such as acacia, gelatin, dextrans, albumins, alginates/starch, and the like; or synthetic polymers, whether hydrophilic or hydrophobic.
Biodegradable synthetic polymers which may be also used to formulate nanoparticles include, but are not limited to, polyesters, such as polyglycolides and polylactic polyglycolic copolymers (PLGA); polyethers, such as such as hydroxy-terminated poly(ε-caprolactone)-polyether or polycaprolactone (PCL); polyanhydrides; polyacrylamides; poly(orthoesters); polyamino acids; and biodegradable polyurethanes. It is to be understood that the term polymer is to be construed to include copolymers and oligomers.
The term “pharmaceutical agents” as used herein comprises both, therapeutic agents and diagnostic agents. It is noted that the terms “drug” and “therapeutic agent” are used interchangeably herein.
The therapeutic agent is preferably selected from substances which are incapable or not sufficiently capable of crossing physiological barriers without a delivery vehicle or carrier. This physiological barrier is preferably selected from, although not restricted to, the group consisting of blood-brain barrier (bbb), blood-air barrier, blood-cerebrospinal fluid barrier and buccal mucosa. Additionally, the one or more therapeutic agents may have central nervous system activity but cannot cross the blood brain barrier without a delivery vehicle.
According to a preferred embodiment, the delivery vehicle of the invention comprises one or more therapeutic agents selected from the group consisting of drugs acting at synaptic sites and neuroeffector junctional sites; general and local analgetics; hypnotics and sedatives; drugs for the treatment of psychiatric disorders such as depression and schizophrenia; anti-epileptics and anticonvulsants; drugs for the treatment of Parkinson's and Huntington's disease, aging and Alzheimer's disease; anti-obesity drugs; excitatory amino acid antagonists, neurotrophic factors and neuroregenerative agents; trophic factors; drugs aimed at the treatment of CNS trauma or stroke; drugs for the treatment of addiction and drug abuse; antacoids and anti-inflammatory drugs; chemotherapeutic agents for parasitic infections and diseases caused by microbes; immunosuppressive agents and anti-cancer drugs; vitamines; hormones and hormone antagonists; heavy metals and heavy metal antagonists; antagonists for non-metallic toxic agents; cytostatic agents for the treatment of cancer; diagnostic substances for use in nuclear medicine; immunoactive and immunoreactive agents; transmitters and their respective receptor agonists and receptor antagonists, their respective precursors and metabolites; transporter inhibitors; antibiotics; antispasmodics; antihistamines; antinauseants; relaxants; stimulants; sense and antisense oligonucleotides; cerebral dilators; psychotropics; antimanics; vascular dilators and constrictors; anti-hypertensives; drugs for migraine treatment; hypnotics, hyperglycemic and hypoglycemic agents; anti-asthmatics; antiviral agents, preferably anti HIV agents; genetic material suitable for the DNA or anti-sense treatment of diseases; and mixtures thereof.
Typical active ingredients (e.g., drugs) can be any substance affecting the nervous system or used for diagnostic tests of the nervous system. These are described by Gilman et al. (1990), “Goodman and Gilman's—The Pharmacological Basis of Therapeutics”, Pergamon Press, New York, and include the following agents:
acetylcholine and synthetic choline esters, naturally occurring cholinomimetic alkaloids and their synthetic congeners, anticholinesterase agents, ganglionic stimulants, atropine, scopolamine and related antimuscarinic drugs, catecholamines and sympathomimetic drugs, such as epinephrine, norepinephrine and dopamine, adrenergic agonists, adrenergic receptor antagonists, transmitters such as GABA, glycine, glutamate, acetylcholine, dopamine, 5-hydroxytryptamine, and histamine, neuroactive peptides; analgesics and anesthetics such as opioid analgesics and antagonists; preanesthetic and anesthetic medications such as benzodiazepines, barbiturates, antihistamines, phenothiazines and butylphenones; opioids; antiemetics; anticholinergic drugs such as atropine, scopolamine or glycopyrrolate; cocaine; chloral derivatives; ethchlorvynol; glutethimide; methyprylon; meprobamate; paraldehyde; disulfuram; morphine, fentanyl and naloxone; psychiatric drugs such as phenothiazines, thioxanthenes and other heterocyclic compounds (e.g., halperiodol); tricyclic antidepressants such as desimipramine and imipramine; atypical antidepressants (e.g., fluoxetine and trazodone), monoamine oxidase inhibitors such as isocarboxazid; lithium salts; anxiolytics such as chlordiazepoxyd and diazepam; anti-epileptics including hydantoins, anticonvulsant barbiturates, iminostilbines (such as carbamazepine), succinimides, valproic acid, oxazolidinediones and benzodiazepines. Anti-Parkinson drugs such as L-DOPA/CARBIDOPA, apomorphine, amatadine, ergolines, selegeline, ropinorole, bromocriptine mesylate and anticholinergic agents;
antispasticity agents such as baclofen, diazepam and dantrolene; neuroprotective agents, such as excitatory amino acid antagonists, neurotrophic factors and brain derived neurotrophic factor, ciliary neurotrophic factor, or nerve growth factor; neurotrophine (NT) 3 (NT3); NT4 and NT5; gangliosides; neuroregenerative agents; drugs for the treatment of addiction and drug abuse include opioid antagonists and anti-depressants; autocoids and anti-inflammatory drugs such as histamine, bradykinin, kailidin and their respective agonists and antagonists; chemotherapeutic agents for parasitic infections and microbial diseases; anti-cancer drugs including alkylating agents (e.g., nitrosoureas) and antimetabolites; nitrogen mustards, ethylenamines and methylmelamines; alkylsulfonates; folic acid analogs; pyrimidine analogs, purine analogs, vinca alkaloids; and antibiotics.
According to a preferred embodiment, the diagnostic agent is selected from the group consisting of diagnostics useful in the diagnosis in nuclear medicine and in radiation therapy.
The surfactant coating and/or the stabilizer preferably comprises one or more of the following substances:
fatty acid esters of glycerols, sorbitol and other multifunctional alcohols, preferably, glycerol monostearate, sorbitan monolaurate, or sorbitan monoleate; polysorbates, preferably polysorbate 60 and most preferably polysorbate 80; poloxamers, preferably poloxamer 188, 338 or 407; poloxamines, preferably poloxamine 904, 908 or 1508; polyoxyethylene ethers and polyoxyethylene esters; ethoxylated triglycerides; ethoxylated phenols and ethoxylated diphenols; surfactants of the Genapol™ and Bauki series; metal salts of fatty acids, metal salts of fatty alcohol sulfates, sodium lauryl sulfate; and metal salts of sulfosuccinates; preferably polyoxyethylene glycols, more preferably Lutensol 50 or 80; sodium dodecyl sulfate; and mixtures of two or more of said substances.
As indicated above, polysorbate 80 is most preferred.
The one or more coating layers of the nanoparticles of the invention each have a thickness of preferably between 20 A and 150 A, more preferably 30 and 100 A.
According to a further aspect, the present invention is directed to a pharmaceutical composition, comprising the delivery vehicle as defined herein and a pharmaceutically acceptable carrier and/or diluent.
In order to use the nanoparticles in a practical embodiment, they may be reconstituted into a suspension with distilled water or normal saline at physiological pH and osmolarity.
Typically, the nanoparticles are present in the injectable suspension at a concentration ranging from 0.1 mg nanoparticles per ml suspending fluid to 100 mg nanoparticles per ml suspending fluid. 10 mg nanoparticles per ml is preferred. The amount of nanoparticles used will strongly depend on the amount of pharmaceutical agent contained in an individual nanoparticle and the skilled artisan or the physician in charge will be readily able to adapt the dosage of the nanoparticles to the specific circumstances.
Preferably, the delivery vehicle or the pharmaceutical composition are showing a prolonged release or sustained release of said one or more pharmaceutical agents in vivo. Those nanoparticles made in accordance with the principles of the invention biodegrade in periods of time ranging from a few hours to 6 months or more.
Alternatively, the pharmaceutical composition may take other forms required to transfer the delivery vehicle of the invention to and across other physiological barriers, for example to and across the blood-air barrier. Then it may, for example have the form of an aerosol or the like in order to deliver the composition by inhalation to the barrier in question.
According to a further aspect, the present invention provides a method for the manufacture of a delivery vehicle for a pharmaceutical agent, comprising the steps of:
In an embodiment, step c) is once or more repeated by adding the nanoparticles isolated in step c) to the same or a different solution containing monomers of the one or more biodegradable polymeric materials and polymerizing said monomers in order to provide a polymeric coating on said particles and isolating said nanoparticles.
As an alternative, in step b) also a solution of said agents in a suitable solvent is used or the one or more pharmaceutical agents are provided in pure form. In the subsequent step c), the solution of said agents or the one or more pharmaceutical agents in pure form are added to a mixture containing a liquid and monomers of one or more biodegradable polymeric materials and polymerizing said monomers in order to provide nanoparticles.
Basically, it is noted that if in step b) a suspension is prepared, a system containing solid and fluid components is established. It is then essential that the pharmaceutical agent remains unsolved in that suspension. Thus, whenever a hydrophilic pharmaceutical agent is used, it should be suspended in a lipohilic solvent or vice versa. In case of a suspension, the solid component preferably has the form of a crystal, in particular of a nanocrystal.
As an alternative, the one or more pharmaceutical agents may be used in pure form in step c), for example in their natural state (fluid or solid, e.g. an oil or a powder). In this case, the method of the present invention will lead to nanoparticles, in which the one or more pharmaceutical agents are dispersed throughout the nanoparticles thus leading to a polymeric matrix by which the one or more pharmaceutical agents are released in vivo in a controlled way.
The present invention for the first time presents a method of forming pharmaceutical agent containing nanoparticles, wherein the pharmaceutical agents are contacted and mixed with the monomers before the polymerisation step is performed. Therefore, the one or more pharmaceutical agents may be incorporated in a different way then in the prior art approaches, in which the agent usually is coated on the nanoparticles subsequent to the polymerisation step (thus not incorporating same into the particles).
A preferred method of polymerisation is the miniemulsion technique as developed by K. Landfester et al.
Miniemulsions are dispersions of critically stabilized oil droplets with a size between 50 and 500 nm prepared by shearing a system containing oil, water, a surfactant and a hydrophobe. Polymerizations in such miniemulsions result in particles which have about the same size as the initial droplets. The principle of miniemulsion polymerization is schematically shown in
The nanoparticles in the prior art were prepared for example by what is generically termed as an “in-solvent emulsification-evaporation technique” using single (oil-in-water) or multiple emulsifications (water-in-oil-in-water) depending upon whether the incorporated pharmaceutical agent is hydrophobic or hydrophilic (as explained above).
After forming the polymeric particles containing a pharmaceutical agent, the solvent is evaporated from the emulsion. The nanoparticles are separated from the remainder by centrifugation, or preferably ultracentrifugation (120,000 to 145,000 g), washed with water, and re-centrifuged and decanted. Organic solvents which remain in the nanoparticles formed, however, may cause problems in subsequent in vivo applications (what is not the case in the miniemulsion method explained above).
Therefore, the present invention is also and preferably directed to a method of preparing nanoparticles containing the steps of:
As a general remark, the nanoparticles of the present invention are formed by a “miniemulsion method”, which is per se well known and is, for example, disclosed in K. Landfester, “Polyreactions in miniemulsions”, Macromol. Rapid Comm. 2001, 896-936. K. Landfester, N. Bechthold, F. Tiarks, and M. Antonietti, “Formulation and stability mechanisms of polymerizable miniemulsions”. This technology basically differs from the well known conventional methods by involving a different order of manufacturing steps: in this approach, a miniemulsion, containing dispersed hydrophobic, monomer containing droplets in a hydrophilic continous phase, are formed to polymeric particles. In the conventional approach, the polymers are directly formed from the solution containing monomers.
Thus, the term “miniemulsion” as used herein generally means a technology, by which a dispersion is made containing a continuous W (hydrophilic) and an O (hydrophobic) phase, dispersed in the continuous phase. Further, this term is directed to emulsion droplets formed of 1 to 1.000 nm, usually approximately between 50 and 500 nm (the size of the particles following polymerization is identical or almost identical).
One of the major drawbacks of the conventional approach can be seen in the fact that only suspensions containing about 1% of nanoparticles (solid content) may be obtained therewith. In contrast, the present miniemulsion approach allows a solid content of nanoparticles of even 15-24% or more based on a monomer content of 25% w/w (based on the overall weight of the O/W reaction system). Thus, the yield of solid nanoparticles is dramatically increased and corresponds to about 60-96% of the employed monomers.
With this method, it is possible to obtain nanoparticle suspensions of high solid content (range: 15%-24%) and thus in a high yield (60-96%), which is very important in terms of up-scaling. The process is reproducible. The mean diameter of the generated nanoparticles is 200-300 nm (range <1 μm).
As an example, if the O phase is consisting of 6 g monomer+250 mg hydrophobe, the W phase is 24 g 0.01 N HCl+stabilizer, the maximum content of solids will be 25% w/w (6/24×100) corresponding to a yield of 100%. A content of 20% w/w then corresponds to a yield of 80%. In this case, the remaining 20% are represented by monomers, which were lost during polymerization, for example by polymerizing at the vessel surface or at the homogenizer or the like.
Preferably, the one or more pharmaceutical agents and the monomers are contained in the O phase. In this case, the pharmaceutical agents are finely distributed into the nanoparticles formed by the polymerisation step. As an alternative, the one or more pharmaceutical agents are present in the W phase and the monomers are contained in the O phase. It turned out that also in this case, a remarkable amount of the pharmaceutical agent is incorporated into the nanoparticles formed. We do not want to be bound to any specific theory, however, it is assumed that the pharmaceutical agents contained in the W phase are intimately contacted with the O phase by preparing the miniemulsion, for example by applying high shear forces, leading to a distribution of the agent also in the O phase.
Additionally, solution mediators may be used to bring agents into solution, which under normal circumstances would not dissolve in a sufficient amount in the solvent. Examples for this group of substances are dimethylsulfoxide, dimethylformamide, polysorbate 80, vitamine E, polyethylenglycole (PEG 400), Cremophor, or glycerol.
It is furthermore possible to add the one or more pharmaceutical agents to both, the O and the W phase, if this is desired.
In a preferred embodiment, the stabilizer used is contained in the W phase.
As mentioned above, the already known miniemulsion technique as, for example, disclosed in Landfester et al. (supra), may be used to prepare the miniemulsion. This may, for example be done by at first combining monomers in an O phase and a W phase and a stabilizer (defined below). It is noted that the W phase may contain further ingredients, for example HCl for setting a suitable pH value. Second, the reaction system may be mixed by, for example, a homogenizer or the like, in order to mix all ingredients.
The preparation of the miniemulsion itself is performed by applying high shear forces to the reaction system, for example by ultrasound and high pressure homogenizers. Furthermore, the shear forces may be applied for a time range of from 1-5 min. depending on the size of the reaction system and the homogenizer used. Basically, a time range of between 2 and 4 min. is regarded as being sufficient.
The ultrasound homogenizer may have an amplitude of about 60-100%, preferably about 70%.
According to an embodiment, the temperatures used in this process are preferably from −1 to 5° C., preferably 0° C.
Generally the weight ratio of 0 to W phase is from 15-40% w/w, preferably 20-30% w/w and more preferably about 25% w/w.
Following preparing the miniemulsion, the polymerisation process is started, for example by simply increasing the pH to a value of pH 7.0 or the like. This may be done, whenever PBCA monomers are used in the reaction system and the pH increase is performed, for example, by adding a sufficient amount of K2CO3 to the reaction system or by pouring the prepared miniemulsion into an aqueous solution of NaOH.
According to a further embodiment, the O phase is containing a hydrophobe, preferably selected from olive oil, miglyol and/or hexadecane. The amount of hydrophobe is usually relatively small and should be sufficient to prevent Ostwald ripening (about 2-10% w/w based on the overall weight of the O-phase (further containing the monomer)).
Preferably, the particles in step a) are prepared by spray drying a solution containing the one or more pharmaceutical agents. Alternatively, the particles in step a) may be prepared by grinding and optionally sieving or by high-pressure homogenization of the one or more pharmaceutical agents. The liquid used in step c) preferably comprises a lipophilic solvent, preferably n-hexane, hexadecane or miglyol.
In a preferred embodiment, the method of the present invention contains an additional step, wherein the stabilizer is at least partially removed from the obtained nanoparticles. This can preferably be done by dialysis or centrifugation. It surprisingly turned out that, although required in the method of manufacture per se, the stabilizers may be at least partially removed after the final nanoparticles were formed. In other words, an “excess” of stabilizers can be removed which is not required for maintaining the stability of the nanoparticles, but can cause potential risks for in vivo applications. It is assumed that the lowest possible amount of stabilizers in the nanoparticles should be regarded as having the lowest in vivo risk.
According to a further aspect, the present invention is directed to a delivery vehicle, which is obtainable by the method as defined above.
It is noted that, although the present disclosure is showing some embodiments only in connection with the method or the delivery vehicle/nanoparticles etc., their contents also extend to all respective other aspects contained in this application.
The present invention further provides the use of the delivery vehicle or a pharmaceutical composition as defined herein for the manufacture of a medicament for the treatment of diseases and conditions, requiring a pharmaceutical agent to cross one or more physiological barriers. It is in particular used for the treatment of diseases corresponding to the drugs listed hereinabove.
In particular, the delivery vehicle will find application in the treatment of diseases related to the CNS. Furthermore, this includes the treatment of AIDS, since in many people with advanced AIDS—possibly a third of adults and half of all children—HIV also infiltrates and harms the brain, triggering HIV-associated dementia. The disorder is marked by poor concentration, decreased memory and slow thinking and movements. However, it is particularly hard to target the virus in the brain. Here, the present invention may open up new therapeutic successes by delivering anti-HIV agents to the brain.
The invention is now further illustrated by the accompanying drawings, in which:
Two separate solutions are prepared.
Two separate solutions are prepared.
Two separate solutions are prepared.
Two separate solutions are prepared.
Compound A is a hydrophobic pharmaceutical compound.
Two separate solutions are prepared.
| Number | Date | Country | Kind |
|---|---|---|---|
| 04021855.4 | Sep 2004 | EP | regional |
| 04027997.8 | Nov 2004 | EP | regional |
This application is a continuation of PCT International Patent Application No. PCT/EP2005/009894, filed Sep. 14, 2005, which claims priority to European Patent Application No. 04021855.4, filed Sep. 14, 2004 and European Patent Application No. 04027997.8, filed Nov. 25, 2004, the disclosures of each of which are incorporated herein by reference in their entirety.
| Number | Date | Country | |
|---|---|---|---|
| Parent | PCT/EP05/09894 | Sep 2005 | US |
| Child | 11724013 | Mar 2007 | US |
