Matrices formed of polymer and hydrophobic compounds for use in drug delivery
Abstract
A lipid or other hydrophobic or amphiphilic compound (collectively referred to herein as "hydrophobic compounds") is integrated into a polymeric matrix for drug delivery to alter drug release kinetics. In embodiments where the drug is water soluble, the drug is released over longer periods of time as compared to release from the polymeric matrix not incorporating the hydrophobic compound into the polymeric material. In contrast to methods in which a surfactant or lipid is added as an excipient, the hydrophobic compound is actually integrated into the polymeric matrix, thereby modifying the diffusion of water into the microparticle and diffusion of solubilized drug out of the matrix. The integrated hydrophobic compound also prolongs degradation of hydrolytically unstable polymers forming the matrix, further delaying release of encapsulated drug.
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39 claims: 4 independent, 35 dependent
- 1Zastrzeżenia patentowe 1. Matryca polimeryczna do dostarczania środka terapeutycznego albo profilaktycznego, utworzona z biokompatybilnego polimeru i wprowadzonego do niego środka terapeutycznego albo profilaktycznego, znamienna tym, że zawiera skuteczną ilość związku hydrofobowego wprowadzonego do matrycy jak czynnika modyfikacji dyfuzji wody do matrycy i uwalniania środka terapeutycznego albo profilaktycznego z matrycy, zaś związek hydrofobowy jest wybierany z grupy zawierającej kwasy tłuszczowe i pochodne, jedno-, dwu-i trójglicerydy, fosfolipidy, sfingolipidy, steroidy i pochodne steroidów, oleje, witaminy, terpeny, tryptofan, tyrozynę, izoleucynę, leucynę, walinę, paraben alkilowy i kwas benzoesowy albo ich kombinacje, przy czym matryca jest matrycą porowatą otrzymywalną na drodze emulsyfikacji czynnika tworzącego pory z wymienionym polimerem rozpuszczonym w rozpuszczalniku i następnie usunięcia czynnika tworzącego pory i rozpuszczalnika polimeru, ponadto korzystnie czynnik tworzący pory jest solą lotną.
- 2Matryca polimeryczna według zastrz. 1, znamienna tym, że matryca ma postać mikrocząstek.
- 3Matryca polimeryczna według zastrz. 1, znamienna tym, że związek hydrofobowy jest wprowadzony do matrycy przy stosunku wagowym masy związku hydrofobowego do masy polimeru wynoszącym pomiędzy 0,01 do 60.
- 4Matryca polimeryczna według zastrz. 3, znamienna tym, że związek hydrofobowy jest lipidem wprowadzonym do matrycy przy stosunku wagowym masy lipidu/masy materiału matrycy mieszczącym się pomiędzy 0,01 a 30.
- 5Matryca polimeryczna według zastrz. 4, znamienna tym, że lipid jest fosfolipidem wybieranym z grupy korzystnie zawierającej kwasy fosfatydowe, fosfatydylocholiny z lipidami zarówno nasyconymi jak i nienasyconymi, etanoloaminy fosfatydylowe, fosfatydylogliceryny,fosfatydyloseryny,fosfatydyloinozytole, pochodne lizofosfatydyli, kardiolipinę i β-acylo-g-alkilo fosfolipidy.
- 6Matryca polimeryczna według zastrz. 5, znamienna tym,żefosfolipid jest wybieranyzgrupy korzystnie zawierającej dwuoleilofosfatydylocholina, dwumirystoilofosfatydylocholina, dwupentadekanoilofosfatydylocholina, dwulauroilofosfatydylocholina, dwupalmitoilofosfatydylocholina, dwustearoilofosfatydylocholina, dwuarachidoilofosfatydylocholina, dwubehenoilofosfatydylocholina, dwutrikozanoilofosfatydylocholina, dwulignoceroilofosfatydylocholina i fosfatydyloetanoloaminy.
- 7Matryca polimeryczna według zastrz. 1, znamienna tym, że środek jest środkiem terapeutycznym.
- 8Matryca polimeryczna według zastrz. 1, znamienna tym, że matryca jest utworzona z użyciem polimeru bioadhezyjnego.
- 9Matryca polimeryczna według zastrz. 1, znamienna tym, że matryca jest utworzona zpolimeru wybieranego z grupy zawierającej korzystnie poli(kwasy wodorotlenowe), polibezwodniki, poliortoestry, poliamidy, poliwęglany, polialkileny,poliglikolealkilenowe,politlenkialkilenowe,politereftalany alkilenowe, polialkohole winylowe, poliwinyloetery, poliestry winylu, polihalogenki winylu, poliwinylopirolidon,polisiloksany,poli(alkoholewinylowe),poli(octan winylu), polistyren, poliuretany i ich kopolimery, celulozy syntetyczne, kwasy poliakrylowe, poli(kwas masłowy), poli(kwas walerianowy) i poli(laktydo-ko-kaprolakton), etylenowy octan winylu, ich kopolimery i mieszanki.
- 10Matryca polimeryczna według zastrz. 1, znamienna tym, że korzystnie matryca jest utworzona z użyciem polimeru naturalnego w postaci białka albo z wielocukru.
- 11Matryca polimeryczna według zastrz.1, znamienna tym, że matryca jest w farmaceutycznie akceptowalnym nośniku do nakładania miejscowego albo do zastosowania na powierzchni śluzówki.
- 12Matryca polimeryczna według zastrz. 1, znamienna tym, że matryca jest w farmaceutycznie akceptowalnym nośniku do wstrzyknięcia poprzez zastrzyk.
- 13Matryca polimeryczna wedługzastrz.1, znamienna tym,żematryca jest utworzona do podawania doodbytniczego albo dopochwowego. PL 196 159 B1
- 14Matryca polimeryczna według zastrz. 2, znamienna tym, że matryca jest utworzona do podawania dopłucnego.
- 15Sposób wytwarzania matrycy polimerycznej do dostarczania terapeutycznego albo profilaktycznego czynnika, utworzonej z biokompatybilnego polimeru i wprowadzonego do niego środka terapeutycznego albo profilaktycznego, znamienny tym, że polimer rozpuszcza się w rozpuszczalniku, po czym do tego roztworu dodaje się związek hydrofobowy, wprowadzając wymieniony środek terapeutyczny albo profilaktyczny i środek tworzący pory, a tak otrzymany roztwór poddaje się emulsyfikacji, a po jej zakończeniu usuwa się rozpuszczalnik polimeru i również środek tworzący pory dla wytworzenia matrycy polimerycznej porowatej, przy czym czynnik tworzący pory korzystnie jest solą lotną, zaś związek hydrofobowy jest wybierany z grupy zawierającej kwasy tłuszczowe i pochodne, jedno-, dwui trójglicerydy, fosfolipidy, sfingolipidy, steroidy i pochodne steroidów, oleje, witaminy, terpeny, tryptofan, tyrozynę, izoleucynę, leucynę, walinę, paraben alkilowy i kwas benzoesowy albo ich kombinacje.
- 16Sposób wytwarzania matrycy według zastrz. 15, znamienny tym, że matryca jest utworzona w postaci mikrocząstek.
- 17Sposób wytwarzania matrycy według zastrz. 15, znamienny tym, że związek hydrofobowy jest wprowadzony do matrycy przy stosunku wagowym masy związku hydrofobowego do masy polimeru wynoszącym pomiędzy 0,01 do 60.
- 18Sposób wytwarzania matrycy według zastrz. 17, znamienny tym, że związek hydrofobowy jest lipidem wprowadzonym do matrycy przy stosunku wagowym masy lipidu/masy materiału matrycy mieszczącym się pomiędzy 0,01 a 30.
- 19Sposób wytwarzania matrycy według zastrz. 17, znamienny tym, że lipid jest fosfolipidem wybieranym z grupy zawierającej korzystnie kwasy fosfatydowe, fosfatydylocholiny z lipidami zarówno nasyconymi jak i nienasyconymi, etanoloaminy fosfatydylowe, fosfatydylogliceryny, fosfatydyloseryny, fosfatydyloinozytole, pochodne lizofosfatydyli, kardiolipinę i β-acylo-g-alkilo fosfolipidy.
- 20Sposób wytwarzania matrycy według zastrz. 19, znamienny tym, że fosfolipid jest wybierany z grupy zawierającej korzystnie dwuoleilofosfatydylocholina, dwumirystoilofosfatydylocholina, dwupentadekanoilofosfatydylocholina, dwulauroilofosfatydylocholina, dwupalmitoilofosfatydylocholina, dwustearoilofosfatydylocholina, dwuarachidoilofosfatydylocholina, dwubehenoilofosfatydylocholina, dwutrikozanoilofosfatydylocholina, dwulignoceroilofosfatydylocholina i fosfatydyloetanoloaminy.
- 21Sposób wytwarzania matrycy według zastrz. 15, znamienny tym, że środek jest środkiem terapeutycznym.
- 22Sposób wytwarzania matrycy według zastrz. 15, znamienny tym, że matryca jest tworzona z użyciem polimeru bioadhezyjnego.
- 23Sposób wytwarzania matrycy według zastrz. 15, znamienny tym, że matryca jest utworzona z polimeru wybieranego z grupy zawierającej korzystnie poli(kwasy wodorotlenowe), polibezwodniki,poliortoestry,poliamidy,poliwęglany, polialkileny,poliglikolealkilenowe,politlenkialkilenowe,politereftalany alkilenowe, polialkohole winylowe, poliwinyloetery, poliestry winylu, polihalogenki winylu, poliwinylopirolidon, polisiloksany, poli(alkohole winylowe), poli(octan winylu), polistyren, poliuretany i ich kopolimery, celulozy syntetyczne, kwasy poliakrylowe, poli(kwas masłowy), poli(kwas walerianowy) i poli(laktydo-ko-kaprolakton), etylenowy octan winylu, ich kopolimery i mieszanki.
- 24Sposób wytwarzania matrycy według zastrz.15, znamienny tym, że korzystnie matryca jest tworzona z użyciem polimeru naturalnego w postaci białka albo z wielocukru.
- 25Sposób wytwarzania matrycy według zastrz. 15, znamienny tym, że matryca jest w farmaceutycznie akceptowalnym nośniku do nakładania miejscowego albo do zastosowania na powierzchni śluzówki.
- 26Sposób wytwarzania matrycy według zastrz. 15, znamienny tym, że matryca jest tworzona przez topienie polimeru ze związkiem hydrofobowym.
- 27Sposób wytwarzania matrycy według zastrz. 15, znamienny tym, że matryca jest tworzona poprzez rozpuszczenie polimeru razem ze związkiem hydrofobowym.
- 28Sposób wytwarzania matrycy według zastrz. 16, znamienny tym, że matryca jest tworzona w postaci mikrocząstek poprzez suszenie rozpyłowe.
- 29Sposób przygotowania terapeutycznego albo profilaktycznego środka z wykorzystaniem matrycy polimerycznej, utworzonej z polimeru i wprowadzonego do niego czynnika terapeutycznego albo profilaktycznego, znamienny tym, że z biokompatybilnego polimeru z wprowadzonym do niego środkiem terapeutycznym albo profilaktycznym i skuteczną ilością związku hydrofobowego do modyfikacji dyfuzji wody w matrycę i uwalniania środka terapeutycznego albo profilaktycznego z tej matrycy, PL 196 159 B1 jako matrycę polimeryczną tworzy się matrycę porowatą otrzymywalną poprzez rozpuszczenie polimeru w rozpuszczalniku, wprowadzenie do roztworu związku hydrofobowego, środka tworzącego pory i wymienionego środka terapeutycznego albo profilaktycznego i emulsyfikację tego roztworu, a następnie usunięcie środka tworzącego pory i rozpuszczalnika polimeru dla wytworzenia matrycy polimerycznej porowatej, przy czym czynnik tworzący pory korzystnie jest solą lotną, zaś związek hydrofobowy jest wybierany z grupy zawierającej kwasy tłuszczowe i pochodne, jedno-, dwu- i trójglicerydy, fosfolipidy, sfingolipidy, steroidy i pochodne steroidów, oleje, witaminy, terpeny, tryptofan, tyrozynę, izoleucynę, leucynę, walinę, paraben alkilowy i kwas benzoesowy albo ich kombinacje.
- 30Sposób przygotowania według zastrz. 29, znamienny tym, że matryca ma postać mikrocząstek.
- 31Sposób przygotowania według zastrz. 29, znamienny tym, że związek hydrofobowy jest wprowadzony do matrycy przy stosunku wagowym masy związku hydrofobowego do masy polimeru wynoszącym pomiędzy 0,01 do 60.
- 32Sposób przygotowania według zastrz. 31, znamienny tym, że związek hydrofobowy jest lipidem wprowadzonym do matrycy przy stosunku wagowym masy lipidu/masy materiału matrycy mieszczącym się pomiędzy 0,01 a 30.
- 33Sposób przygotowania według zastrz. 31, znamienny tym, że lipid jest fosfolipidem wybieranym z grupy zawierającej korzystnie kwasy fosfatydowe, fosfatydylocholiny z lipidami zarówno nasyconymi jak i nienasyconymi, etanoloaminy fosfatydylowe, fosfatydylogliceryny, fosfatydyloseryny, fosfatydyloinozytole, pochodne lizofosfatydyli, kardiolipinę i β-acylo-g-alkilo fosfolipidy.
- 34Sposób przygotowania według zastrz. 32, znamienny tym, że fosfolipid jest wybierany z grupy zawierającej korzystnie dwuoleilofosfatydylocholina, dwumirystoilofosfatydylocholina, dwupentadekanoilofosfatydylocholina, dwulauroilofosfatydylocholina, dwupalmitoilofosfatydylocholina, dwustearoilofosfatydylocholina, dwuarachidoilofosfatydylocholina, dwubehenoilofosfatydylocholina, dwutrikozanoilofosfatydylocholina, dwulignoceroilofosfatydylocholina i fosfatydyloetanoloaminy.
- 35Sposób przygotowania według zastrz. 29, znamienny tym, że środek jest środkiem terapeutycznym.
- 36Sposób przygotowania według zastrz. 29, znamienny tym, że matryca jest utworzona z użyciem polimeru bioadhezyjnego.
- 37Sposób przygotowania według zastrz. 29, znamienny tym, że matryca jest utworzona z polimeru wybieranego z grupy zawierającej korzystnie poli(kwasy wodorotlenowe), polibezwodniki, poliortoestry, poliamidy, poliwęglany, polialkileny, poliglikole alkilenowe, politlenki alkilenowe, politereftalany alkilenowe, polialkohole winylowe, poliwinyloetery, poliestry winylu, polihalogenki winylu, poliwinylopirolidon, polisiloksany, poli(alkohole winylowe), poli(octan winylu), polistyren, poliuretany i ich kopolimery, celulozy syntetyczne, kwasy poliakrylowe, poli(kwas masłowy), poli(kwas walerianowy) i poli(laktydo-ko-kaprolakton), etylenowy octan winylu, ich kopolimery i mieszanki.
- 38Sposób przygotowania według zastrz. 29, znamienny tym, że korzystnie matryca jest utworzona z użyciem polimeru naturalnego w postaci białka albo z wielocukru.
- 39Sposób przygotowania według zastrz. 29, znamienny tym, że matryca jest w farmaceutycznie akceptowalnym nośniku do nakładania miejscowego albo do zastosowania na powierzchni śluzówki.
Independent claims39
242 paragraphs in 7 sections, as filed
(12) PATENT DESCRIPTION (19) PL (11) 196159 (13) B1 (21) Application number: 343691 <sup>(13)</sup> (22) Date of notification: 08/03/1999 <sup>(51) Int.Cl.</sup>
A61K 9/22 (2006.01) (86) Date and number of international application: A61K 9/52 (2006.01)
March 8, 1999, PCT / US99 / 05187 (87) International application publication date and number:
11.11.1999, WO99 / 56731 PCT Gazette No. 45/99
<td colspan="2">Polymer matrix to deliver a therapeutic or prophylactic agent,<sub>(54)</sub> a method of producing a polymeric matrix for therapeutic delivery, or<sup>(54)</sup> prophylactic agent and method of therapeutic preparation either prophylactic agent using a polymer matrix</td>
<td>(30) Priority: 1998-04-30, US, 60/083,636</td><td>(73) The right holder of the patent: ACUSPHERE, INC., Cambridge, US (72) Inventor (s): Howard Bernstein, Cambridge, US</td>
<td>(43) Application was announced:</td><td>Donald Chickering, Framingham, US</td>
<td>27.08.2001 BUP 18/01</td><td>Sarwat Khattak, Cambridge, US Julie Straub, Winchester, US</td>
<td>(45) The grant of the patent was announced:</td><td></td>
<td>31.12.2007 WUP 12/07</td><td>(74) Representative: Szykuła Mirosław, Dr. Andrzej Au & Co. sc, Patent Attorneys</td>
(57) 1. A polymeric matrix for the delivery of a therapeutic or prophylactic agent made of a biocompatible polymer and a therapeutic or prophylactic agent incorporated therein, characterized in that it comprises an effective amount of a hydrophobic compound incorporated into the matrix as a water diffusion modification agent into the matrix and release of the therapeutic or prophylactic agent from the matrix, and the hydrophobic compound is selected from the group consisting of fatty acids and derivatives, mono-, di- and triglycerides, phospholipids, sphingolipids, steroids and steroid derivatives, oils, vitamins, terpenes, tryptophan, tyrosine, isoleucine, leucine, valine, alkyl paraben and benzoic acid or combinations thereof, the matrix being a porous matrix obtainable by emulsifying the agent forming a pore with said polymer dissolved in a solvent and then removing the pore forming agent and the polymer solvent, moreover, preferably, the pore-forming agent is a volatile salt.
15. A method of producing a polymer matrix for the delivery of a therapeutic or prophylactic agent, made of a biocompatible polymer and a therapeutic or prophylactic agent incorporated therein, characterized in that the polymer is dissolved in a solvent, and a hydrophobic compound is added to this solution, introducing said therapeutic or prophylactic agent. and a pore-forming agent, and the solution thus obtained is subjected to emulsification, and upon completion, the polymer solvent and also the pore former are removed to form the porous polymeric matrix, the pore former preferably being a volatile salt and the hydrophobic compound selected from the group consisting of fatty acids and derivatives, mono-, di- and triglycerides, phospholipids, sphingolipids, steroids and steroid derivatives, oils, vitamins, terpenes, tryptophan, tyrosine, isoleucine, leucine, valine, alkyl paraben and benzoic acid or combinations thereof.
29. A method of preparing a therapeutic or prophylactic agent using a polymeric matrix made of a polymer and a therapeutic or prophylactic agent incorporated therein, characterized in that the biocompatible polymer with the therapeutic or prophylactic agent incorporated therein and an effective amount of a hydrophobic compound to modify the diffusion of water into the matrix and releasing the therapeutic or prophylactic agent from the matrix, as a polymer matrix, a porous matrix is formed, obtainable by dissolving the polymer in a solvent, introducing into a solution a hydrophobic compound, a pore forming agent, and said therapeutic or prophylactic agent, and emulsifying the solution, and then removing the pore former and the polymer solvent to form a porous polymer matrix, while which the pore-forming agent is preferably a volatile salt, and the hydrophobic compound is selected from the group consisting of fatty acids and derivatives, mono-, di- and triglycerides, phospholipids, sphingolipids, steroids and steroid derivatives, oils, vitamins, terpenes, tryptophan, tyrosine, isoleucine, .......... .....
PL 196 159 B1
Description of the invention
The invention relates to a polymer matrix for the delivery of a therapeutic or prophylactic agent, a method of making a polymeric matrix for the delivery of a therapeutic or prophylactic agent, and a method of preparing a therapeutic or prophylactic agent using a polymeric matrix, these embodiments generally being intended for use in the field of drug delivery. in particular, they relate to polymer matrices containing the drug and having active agents incorporated therein to modify the kinetics of drug release therefrom, in particular preferably used for parenteral delivery, preferably in the form of microparticle matrices.
The present teachings are claimed with priority in US Application No. 06 / 083,636, filed April 30, 1998, for "Lipid Polymer Compositions for Enhanced Drug Delivery" by Howard Bernstein, Donald E. Chickering, and Julie Ann Straub.
Controlled-release or sustained-release compositions have been developed over the past twenty to thirty years to increase the amount of drug delivered by any of a variety of routes, to prolong the release of the drug in a controlled manner, thereby avoiding the sudden release that can cause increased but transient levels of the drug, and to provide resources. for individual adaptation of the release profiles.
These formulations have taken many forms, including microparticles such as microspheres and microcapsules made of drug encapsulated or mixed with a natural or synthetic polymer, drug particles mixed with excipients such as surfactants to reduce particle agglomeration, and devices such as silastic controlled release bases, in whose drug release is a function of the diffusion of water into the device, where it dissolves and releases the drug exiting the same path.
It is difficult to achieve sustained release when the delivery means consists solely of drug or drug and excipient because the drug tends to dissolve relatively quickly.
In contrast, non-biodegradable devices such as silastic devices must be disposed of after use.
The microparticles have been shaped using a wide variety of techniques including spray drying, hot melting, solvent evaporation, and mechanical means such as milling and rolling.
Microparticles are typically formed from biodegradable material having the desired release properties, as well as being workable by techniques compatible with the drug to be delivered.
Many drugs are unstable and cannot be encapsulated by harsh organic solvents or heat.
Many of these methods result in a formation with a structure in which the drug is released by diffusion of the drug out of the microparticle and / or degradation of the microparticle.
In some cases, further restriction or a controlled diffusion is desirable.
International Application Publication WO96 / 03984 discloses pharmaceutical compositions containing polymer matrices which in turn contain a biocompatible polymer and a chemotherapeutic agent, the polymeric matrix serving to deliver the chemotherapeutic agent to the appropriate tumor sites.
This publication also discloses the preparation of compositions containing a chemotherapeutic agent, such as taxol, incorporated into a biocompatible polymeric matrix (see page 22, lines 10-22).
The polymer according to this publication may be a biodegradable polymer such as a copolymer of polylactic acid and polyglycolic acid [PLGA] (page 10, lines 5-8).
This solution further indicates that additives [admixtures] such as buffers, acids, bases [page 19, lines 24-27], fillers [page 19, lines 28-33], spheronization enhancers [ page 19, line 34 to page 20, lines 11], disintegrators [page 20, lines 12-25], surfactants [page 20, lines 26-31], binders [page 20, line 32 up to pages 21, line 5 ], membranes [page 21, lines 6-37] introduced into this polymeric matrix.
In addition, other biologically active compounds [such as steroids] may be introduced in combination with this chemotherapeutic agent [page 16, lines 15 to page 19, line 16].
PL 196 159 B1
The steroid is introduced into the matrix solely for the purpose of improving the therapeutic effect by its therapeutic interaction.
An object of this invention is to provide microparticles which have incorporated means to limit the diffusion of the drug out of the microparticle.
It is a further object of this invention to provide biodegradable microparticles incorporating means for modifying the degradation kinetics of the microparticles.
Yet another object of the present invention is to provide microparticles particularly well suited for parenteral drug delivery.
The polymeric matrix for the delivery of a therapeutic or prophylactic agent according to the invention, formed from a biocompatible polymer and a therapeutic or prophylactic agent incorporated therein, is characterized in that it contains an effective amount of a hydrophobic compound incorporated into the matrix as a water diffusion modification agent into the matrix and release of the therapeutic or prophylactic agent from the matrix, and the hydrophobic compound is selected from the group preferably comprising at least fatty acids and derivatives, mono-, di- and triglycerides, phospholipids, sphingolipids, steroids and steroid derivatives, oils, vitamins, terpenes, tryptophan, tyrosine, isoleucine, leucine, valine, alkyl paraben and benzoic acid or combinations thereof, wherein the matrix is a porous matrix obtainable by emulsifying the pore former with said polymer dissolved in a solvent and then removing the pore former and the polymer solvent, further preferably, the pore former is a volatile salt.
Preferably, the polymer matrix according to the invention is in the form of microparticles.
The hydrophobic compound is incorporated into the matrix preferably at a weight ratio of the weight of the hydrophobic compound to the weight of the polymer of between 0.01 to 60.
Preferably the hydrophobic compound is a lipid incorporated into the matrix at a weight lipid weight / matrix material weight ratio of between 0.01 and 30.
According to the invention, preferably the lipid is a phospholipid selected from the group which preferably comprises at least phosphatidic acids, phosphatidylcholines with both saturated and unsaturated lipids, phosphatidyl ethanolamines, phosphatidylglycerins, phosphatidylserines, phosphatidylinositols, β-phosphatidyls, β-phosphatidyls and β-phosphatidyls.
It is also preferred according to the invention that the phospholipid is selected from the group consisting of preferably at least dioleoylphosphatidylcholine, dwumirystoilofosfatydylocholina, dwupentadekanoilofosfatydylocholina, dwulauroilofosfatydylocholina, dipalmitoylphosphatidylcholine, dwustearoilofosfatydylocholina, dwuarachidoilofosfatydylocholina, dwubehenoilofosfatydylocholina, dwutrikozanoilofosfatydylocholina, dwulignoceroilofosfatydylocholina ifosfatydyloetanoloaminy.
It is also preferred according to the invention when the agent is a therapeutic agent and also when the matrix is formed using a bioadhesive polymer.
Preferably, according to the invention, the matrix is formed from a polymer selected from the group preferably comprising at least poly (hydroxy acids), polyanhydrides, polyorthoesters, polyamides, polycarbonates, polyalkylenes, polyalkylene glycols, polyalkylene oxides, polyalkylene terephthalates, polyvinyl estcohols, polyvinyl ethers, polyvinylpyrrolidone, polysiloxanes, poly (vinyl alcohols), poly (vinyl acetate), polystyrene, polyurethanes and their copolymers, synthetic celluloses, polyacrylic acids, poly (butyric acid), poly (valeric acid) and poly (lactide-co-caprolactone), ethylene vinyl acetate, copolymers and blends thereof.
Preferably also according to the invention, the matrix is formed from a natural polymer in the form of a protein or from a polysaccharide.
Preferably, according to the invention, the matrix is in a pharmaceutically acceptable carrier for topical application or for application to the mucosal surface.
Preferably according to the invention, the matrix is in a pharmaceutically acceptable vehicle for injection by injection.
Preferably, according to the invention, the matrix is formed for rectal or vaginal administration or the matrix is formed for pulmonary administration.
In the method of producing a polymer matrix for the delivery of a therapeutic or prophylactic agent according to the invention, made of a biocompatible polymer and a therapeutic or prophylactic agent incorporated therein, the essence of the solution consists in dissolving the polymer in a solvent and then adding a hydrophobic compound to this solution, introducing said therapeutic or prophylactic agent and pore-forming agent, and the solution thus obtained is subjected to emulsification, after which the polymer solvent is removed
And also a pore former for forming a porous polymeric matrix, the pore former preferably being a volatile salt and the hydrophobic compound being selected from the group preferably comprising at least fatty acids and derivatives, mono-, di- and triglycerides, phospholipids, sphingolipids, steroids and steroid derivatives, oils, vitamins, terpenes, tryptophan, tyrosine, isoleucine, leucine, valine, alkyl paraben and benzoic acid or combinations thereof.
Preferably according to the invention, the matrix is formed of microparticles.
Preferably according to the invention, the hydrophobic compound is incorporated into the matrix at a weight ratio of the weight of the hydrophobic compound to the weight of the polymer of between 0.01 and 60.
Preferably according to the invention, the hydrophobic compound is a lipid incorporated into the matrix at a weight lipid weight / matrix material weight ratio of between 0.01 and 30.
Preferably, according to the invention, the lipid is a phospholipid selected from the group comprising preferably at least phosphatidic acids, phosphatidylcholines with both saturated and unsaturated lipids, phosphatidyl ethanolamines, phosphatidylglycerins, phosphatidylserines, phosphatidylinositides, β-phosphatidyls, β-phosphatidyls and β-phosphatidylcholines.
Preferably the phospholipid of the invention is selected from the group consisting of preferably at least dioleoylphosphatidylcholine, dwumirystoilofosfatydylocholina, dwupentadekanoilofosfatydylocholina, dwulauroilofosfatydylocholina, dipalmitoylphosphatidylcholine, dwustearoilofosfatydylocholina, dwuarachidoilofosfatydylocholina, dwubehenoilofosfatydylocholina, dwutrikozanoilofosfatydylocholina, dwulignoceroilofosfatydylocholina and phosphatidylethanolamine.
In the method of the invention, it is preferred that the agent is a therapeutic agent and also that the matrix is formed using a bioadhesive polymer.
In the process according to the invention, it is advantageous if the matrix is made of a polymer selected from the group preferably comprising at least poly (hydroxy acids), polyanhydrides, polyorthoesters, polyamides, polycarbonates, polyalkylenes, polyalkylene glycols, polyalkylene oxides, polyalkylene terephthalates, polyvinyl alcohol polyols, vinyl, polyvinyl halides, polyvinylpyrrolidone, polysiloxanes, poly (vinyl alcohols), poly (vinyl acetate), polystyrene, polyurethanes and their copolymers, synthetic celluloses, polyacrylic acids, poly (butyric acid), poly (valeric acid) and poly (lactide-co-caprolactone), ethylene vinyl acetate, their copolymers and blends.
In the process according to the invention, it is advantageous if the matrix is formed using a natural polymer in the form of a protein or a polysaccharide.
In the method according to the invention, it is preferred that the matrix is in a pharmaceutically acceptable carrier for topical application or for application to the mucosal surface.
In the process according to the invention, it is preferable that the matrix is formed by melting the polymer with a hydrophobic compound.
In the method according to the invention, it is preferable that the matrix is formed by dissolving the polymer together with the hydrophobic compound.
In the method according to the invention, it is preferable that the matrix is formed in the form of microparticles by spray drying.
In the method of preparing a therapeutic or prophylactic agent using a polymeric matrix made of a polymer and a therapeutic or prophylactic agent introduced into it, the essence of the solution is that the polymeric matrix is formed as a porous matrix obtained by dissolving the polymer in a solvent, introducing a hydrophobic compound into the solution , the pore-forming agent and said therapeutic or prophylactic agent and emulsifying said solution, and then removing the pore-forming agent and polymer solvent to form a porous polymer matrix, wherein the pore-forming agent is preferably a volatile salt and the hydrophobic compound is selected from the group consisting of fatty acids and derivatives, mono-, di- and triglycerides, phospholipids, sphingolipids, steroids and steroid derivatives, oils, vitamins, terpenes, tryptophan, tyrosine, isoleucine, leucine, valine, alkyl paraben, and benzoic acid or combinations thereof.
Preferably, the matrix is in the form of microparticles.
It is also preferred that the hydrophobic compound is incorporated into the matrix in a weight ratio of the weight of the hydrophobic compound to the weight of the polymer of between 0.01 to 60.
Preferably according to the invention, the hydrophobic compound is a lipid incorporated into the matrix with a weight lipid weight / matrix material weight ratio of between 0.01 and 30.
It is also preferred that the lipid is a phospholipid selected from the group preferably comprising at least phosphatidic acids, phosphatidylcholines with both saturated and unsaturated lipids,
Phosphatidyl ethanolamines, phosphatidylglycerins, phosphatidylserines, phosphatidylinositols, lysophosphatidyl derivatives, cardiolipin and β-acyl-g-alkyl phospholipids.
It is also preferred when phospholipid is selected from the group consisting of preferably at least dioleoylphosphatidylcholine, dwumirystoilofosfatydylocholina, dwupentadekanoilofosfatydylocholina, dwulauroilofosfatydylocholina, dipalmitoylphosphatidylcholine, dwustearoilofosfatydylocholina, dwuarachidoilofosfatydylocholina, dwubehenoilofosfatydylocholina, dwutrikozanoilofosfatydylocholina, dwulignoceroilofosfatydylocholinaifosfatydyloetanoloaminy.
According to the invention, it is preferred that the agent is a therapeutic agent and also that the matrix is formed using a bioadhesive polymer.
It is also preferred that the matrix is made of a polymer selected from the group preferably comprising at least poly (hydroxy acids), polyanhydrides, polyorthoesters, polyamides, polycarbonates, polyalkylenes, polyalkylene glycols, polyalkylene oxides, polyalkylene terephthalates, polyvinyl esters, polyvinyl esters, polyvinyl esters. vinyl, polyvinylpyrrolidone, polysiloxanes, polyvinyl alcohols, polyvinyl acetate, polystyrene, polyurethanes and their copolymers, synthetic celluloses, polyacrylic acids, poly (butyric acid), poly (valeric acid) and poly (lactide-co-caprolactone), ethylene vinyl acetate, copolymers and blends thereof.
Preferably, the matrix is made of a natural polymer in the form of a protein or a polysaccharide.
It is also preferred according to the invention when the matrix is in a pharmaceutically acceptable carrier for topical application or for application to the mucosal surface.
In embodiments of the present invention, a lipid or other hydrophobic or amphiphilic compound (collectively referred to herein as "hydrophobic compounds") is integrated into the polymeric matrix for drug delivery to alter the kinetics of drug release.
In one embodiment, where the drug is water-soluble, the drug is released for longer periods of time as compared to release from the polymeric matrix without the hydrophobic compound incorporated into the polymeric material.
In a further embodiment, where the drug has lower water solubility, the drug is released in shorter periods of time as compared to matrix release without incorporation of the hydrophobic compound into the polymeric material.
Unlike known methods in which a surfactant or lipid is added as an excipient, the hydrophobic compound is indeed integrated into the polymer matrix, thereby modifying the diffusion of water into the microparticle and the diffusion of the dissolved drug from the matrix.
The integrated hydrophobic compound also prolongs the degradation of the hydrolytically unstable polymers forming the matrix, further retarding the release of the encapsulated drug.
The hydrophobic compound must be incorporated into the matrix and the matrix shaped using a technique that results in integration of the hydrophobic compound into the polymeric matrix rather than onto the outer surface of the matrix.
In a preferred embodiment as stated in essence, the matrix is formed into microparticles. Microparticles are produced with a diameter appropriate to the intended route of administration.
For example, between 0.5 and 8 microns in diameter for intravascular administration, 1-100 microns in diameter for subcutaneous or intramuscular administration, and between 0.5 and 5 mm in diameter for oral administration for delivery to the gastrointestinal or other ducts.
The preferred size for administration into the respiratory system is the aerodynamic diameter between one and three micrometers, with an actual diameter of five micrometers or more.
In a preferred embodiment, the polymers are synthetic biodegradable polymers.
Most of the preferred polymers are hydrolytically unstable polymers that are biodegradable, such as polyhydric acids such as polylactic acid together with glycolic acid, polylactide, polyglycolide or polylactide together with polyglycolide, which can be conjugated to polyethylene glycol or other materials that inhibit reticuloendothelial uptake. ).
The hydrophobic compounds can be hydrophobic compounds such as certain lipids or amphiphilic compounds (which contain both hydrophilic and hydrophobic components or regions).
The most preferred amphiphilic compounds are phospholipids, most preferably dipalmitoylphosphatidylcholine (DPPC), distearoylphosphatidylcholine (DSPC), diarachidoylphosphatidylcholine (DAPC),
Diphenoylphosphatidylcholine (DBPC), Dtricosanoylphosphatidylcholine (DTPC), Dulignoceroylphosphatidylcholine (DLPC), incorporated in a ratio between 0.01-60 (lipid weight / polymer weight), most preferably 0.1-30 (lipid weight / polymer weight).
The properties of the matrix surface may also be additionally modified. For example, adhesion can be enhanced by the selection of bioadhesive polymers, which may be particularly desirable when the matrix is in the form of a microparticle for administration to a mucosal surface, such as intranasal, pulmonary, vaginal or oral.
The target value can also be achieved by the appropriate selection of the polymer or by introducing into or conjugating with the polymer ligands that specifically bind to particular types of tissues or cell surface molecules.
In addition, ligands can be bound to the microparticles, which results in charging, lipophilicity or hydrophilicity of the particle.
The subject of the invention is presented in more detail in the following examples of implementation.
Methods are provided for synthesizing polymeric delivery systems comprised of polymer matrices that contain an active agent, such as a therapeutic or prophylactic agent (generally referred to herein as "drug").
The matrices are useful in a variety of drug delivery applications, and may be administered by injection, aerosol or powder, orally or at the destination.
The recommended route of administration is by inhalation or injection.
Incorporation of a hydrophobic and / or amphiphilic compound (generally referred to herein as a "hydrophobic compound") into a polymeric matrix modifies the release period of the drug compared to the same polymeric matrix without the hydrophobic compound incorporated, by changing the rate of water diffusion into and out of the matrix and / or the degradation rate of the matrix.
Reagents for making a matrix having a hydrophobic compound incorporated
In the following description, the term "matrix" refers to a structure including one or more materials in which the drug is dispersed, encapsulated, or encapsulated.
The material can be crystalline, semi-crystalline, or amorphous. The matrix may be in the form of granules, tablets, plates, rods, disks, hemispheres or microparticles, or have an undefined shape.
In contrast, the term microparticle includes microspheres and microcapsules as well as microparticles, unless otherwise stated. The microparticles may have, for example, a spherical shape or they may have a shape other than spherical.
Microcapsules are defined as microparticles having an outer polymer shell surrounding a core of another material, in this case the active agent.
Microspheres are substantially solid polymeric spheres that may include a honeycomb structure formed by pores in the polymer that are filled with an active agent, as described below.
Polymers
The matrix can be formed from non-biodegradable and biodegradable polymers, although biodegradable polymers are preferred, particularly for parenteral administration.
Non-erodible polymers can be used for oral administration. In general, synthetic polymers are preferred due to more reproducible synthesis and degradation, although natural polymers can be used and have equivalent or even better properties, especially some of the natural biopolymers that degrade by hydrolysis, such as polyhydroxybutyrate.
The polymer is selected based on the time required for in vivo stability, i.e. the time required to be brought to the site where delivery is desired and the time required for delivery.
Representative synthetic polymers are: poly (hydroxy acids) such as poly (lactic acid), poly (glycolic acid) and poly (lactic acid together with glycolic acid), polylactide, polyglycolide, polylactide-co-glycolide, polyanhydrides, polyorthoesters, polyamides, polycarbonates, polyalkylenes such such as polyethylene and polypropylene, polyalkylene glycols such as polyethylene glycol, polyalkylene oxides such as polyethylene oxide, polyalkylene terephthalates such as polyethylene terephthalate, polyvinyl alcohols, polyvinyl ethers, polyvinyl esters, polyvinyl halides such as polyvinyl chloride, polyvinylpyrrolidone, polysiloxanes, polyvinyl alcohols, polyvinyl acetate, polystyrene, polyurethanes and their copolymers.
Also cellulose derivatives such as alkyl cellulose, hydroxyalkyl cellulose, cellulose ethers, cellulose esters, nitrocelluloses, methyl cellulose, ethyl cellulose, hydroxypropyl methyl cellulose, hydroxybutyl methyl cellulose, cellulose acetate, cellulose acetate phthalate, cellulose acetate phthalate
Carboxyethyl cellulose, cellulose triacetate and sodium cellulose sulfate salt (collectively referred to herein as "synthetic celluloses"), acrylic acid polymers, methacrylic acid or copolymers or derivatives thereof containing esters, poly (methyl methacrylate), poly (ethyl methacrylate), poly (butyl methacrylate), poly (isobutyl methacrylate), poly (hexyl methacrylate), poly (isodecyl methacrylate), poly (lauryl methacrylate), poly (phenyl methacrylate), poly (methyl acrylate), poly (isopropyl acrylate), poly (isobutyl acrylate), poly (octadecanol acrylate) (collectively referred to herein as "polyacrylic acids"), poly (butyric acid), poly (valeric acid) and poly (lactide-co-caprolactone), copolymers and blends thereof.
The term "derivatives" as used herein includes polymers having substitutions, additions of chemical groups, for example, alkyl, alkylene, hydroxyl attachments, oxidations, and other modifications routinely performed by those skilled in the art.
Examples of preferred biodegradable polymers include polymers of hydroxy acids such as lactic acid, glycolic acid and PEG copolymers, polyanhydrides, poly (ortho) esters, polyurethanes, polybutyric acid, poly (valeric acid) and poly (lactide). caprolactone), their blends and copolymers.
Examples of preferred natural polymers include proteins such as albumin and prolamines, for example zein, polysaccharides such as alginate, cellulose and polyhydric alkanates, for example polyhydric butyrate.
The in vivo stability of the matrix can be controlled during production by the use of polymers such as polylactide-co-glycolide copolymerized with polyethylene glycol (PEG). PEG, if exposed to the exterior surface, can extend the circulation time of these materials because it is hydrophilic.
Examples of preferred non-biodegradable polymers include ethylene vinyl acetate, poly (meth) acrylic acid, polyamides, copolymers, and blends thereof.
Bioadhesive polymers of particular interest for use on mucosal surfaces such as in the gastrointestinal tract include polyanhydrides, polyacrylic acid, poly (methyl methacrylates), poly (ethyl methacrylates), poly (butyl methacrylate), poly (isobutyl methacrylate), poly ( hexylmethacrylate), poly (isodecyl methacrylate), poly (lauryl methacrylate), poly (phenyl methacrylate), poly (methyl acrylate), poly (isopropyl acrylate), poly (isobutyl acrylate), poly (octadecanol acrylate).
Solvents
The solvent for the polymer is selected based on its biocompatibility as well as the solubility of the polymer and, where appropriate, its interaction with the agent to be delivered.
For example, the ease with which the agent is dissolved in the solvent and the absence of deleterious effects of the solvent on the agent to be delivered are factors to consider when selecting a solvent.
Aqueous solvents can be used to make matrices made of water-soluble polymers.
Organic solvents will typically be used to dissolve hydrophobic and some hydrophilic polymers.
The preferred organic solvents are volatile or have a relatively low boiling point or can be removed in vacuo and those that are accepted for human administration in trace amounts, such as methylene chloride.
Other solvents such as ethyl acetate, ethanol, methanol, dimethylformamide (DMF), acetone, acetonitrile, tetrahydrofuran (THF), acetic acid, dimethyl sulfoxide (DMSO), and chloroform and combinations thereof may also be used.
Preferred solvents are those classified as class 3 residual solvents by the Food and Drug Administration as published in the Federal Register Vol. 62, Number 85, pp. 24301-24309 (May 1997).
Generally, the polymer is dissolved in a solvent to form a polymer solution having a concentration between 0.1 and 60% weight to volume (w / V), more preferably between 0.25 and 30%.
The polymer solution is then processed as described below to obtain a polymer matrix having hydrophobic components incorporated therein.
Hydrophobic and amphiphilic compounds
In general, compounds that are hydrophobic or amphiphilic (i.e., having both a hydrophilic and a hydrophobic component or region) can be used to modify penetration and / or uptake
Water through the matrix, thereby modifying the rate of drug diffusion from the matrix, and in the case of hydrolytically unstable materials, changes in degradation and hence drug release from the matrix.
Lipids that can be used include, but are not limited to, the following classes of lipids: fatty acids and derivatives, mono-, di- and triglycerides, phospholipids, sphingolipids, cholesterol and steroid derivatives, terpenes and vitamins.
Fatty acids and their derivatives may include, but are not limited to, the following: saturated and unsaturated fatty acids, odd and even-numbered fatty acids, cis and trans isomers, and fatty acid derivatives including alcohols, esters, anhydrides, hydroxy fatty acids and prostaglandins.
Saturated and unsaturated fatty acids that can be used include, but are not limited to, molecules that have between 12 carbon atoms and 22 carbon atoms in linear or branched form.
Examples of saturated fatty acids that can be used include, but are not limited to, compounds such as lauric, myristic, and stearic acids.
Examples of unsaturated fatty acids that can be used include, but are not limited to, lauric, phenicol, myristoleic, palmitoleic, petroselinic, and oleic acids.
Examples of branched fatty acids that can be used include, but are not limited to, compounds such as isolauric, isomistyric, isopalmitic, and isostearic acids, and isoprene derivatives.
Fatty acid derivatives include 12 - (((7'-diethylaminocoumarin-3-yl) carbonyl) methylamino) octadecanoic acid; N- [12 - (((7'-diethylaminocoumarin-3-yl) carbonyl) methylamino) octadecanoyl] -2-aminopalmitic acid, N succinyl dioleylphosphatidylethanolamine and palmitoyl homocysteine and / or combinations thereof.
Mono-, di- and triglycerides or derivatives thereof that may be used include, but are not limited to, molecules that have fatty acids or mixtures of fatty acids between 6 and 24 carbon atoms, digalactosyl diglyceride, 1,2-dioleyl-sn-glycerin; 1,2-dimitoyl-sn-3-succinylglycerin and 1,3-dimitoyl-2-succinylglycerin.
Phospholipids that may be used include, but are not limited to, compounds such as phosphatidic acids, phosphatidylcholines with both saturated and unsaturated lipids, phosphatidyl ethanolamines, phosphatidylglycerins, phosphatidylserines, phosphatidylinositides, alkyl-acylinositides, and lysophosyl-phosphatides derivatives, phospholipids.
Examples of phospholipids include, but are not limited to compounds such as phosphatidylcholines such as dioleoylphosphatidylcholine, dwumirystoilofosfatydylocholina, dwupentadekanoilofosfatydylocholina, dwulauroilofosfatydylocholina, dipalmitoylphosphatidylcholine (DPPC), dwustearoilofosfatydylocholina (DSPC), dwuarachidoilofosfatydylocholina (DAPC), dwubehenoilofosfatydylocholina (DBPC), dwutrikozanoilofosfatydylocholina (DTCP) diglignoceroylphosphatidylcholine (DLPC) and phosphatidylethanolamines such as dioleylphosphatidylethanolamine or 1-hexadecyl-2-palmitoylglycerophosphoethanolamine.
Synthetic phospholipids with asymmetric acyl chains (e.g., with one 6 carbon acyl chain and a second 12 carbon acyl chain) may also be used.
Sphingolipids that may be used include ceramides, sphingomyelins, cerebrosides, gangliosides, sulfatides, and lysosulfatides.
Examples of sphingolipids include, but are not limited to, compounds such as gangliosides
GM1 and GM2.
Steroids that may be used include, but are not limited to, compounds such as cholesterol, cholesterol sulfate, cholesterol hemisuccinate, 6- (5-cholesterol-3-yloxy) hexyl-6-amino-6-deoxyl-1-thio-αD -galactopyranoside, 6- (5-cholestene-3β-yloxy) hexyl-6-amino-6-deoxyl-1-thio-α-D-mannopyranoside and choresteryl (4'-trimethyl ammonium) butanoate. Additional lipid compounds that may be used include tocopherol and derivatives and oils and oils derived therefrom such as stearylamine.
A variety of cationic lipids such as DOTMA, N- [1- (2,3-dioleoyloxy) propyl-N, N, N-trimethylammonium chloride; DOTAP, 1,2-dioleoyloxy-3- (trimethylammonium) propane; and DOTB, 1,2-dioleoyl-3- (4'-trimethylammonium) butanoyl sn glycerin.
The most preferred lipids are phospholipids, preferably DPPC, DDSPC, DAPC, DSPC, DTPC, DBPC, DLPC and most preferably DPPC, DAPC and DBPC.
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Other preferred hydrophobic compounds include amino acids such as tryptophan, tyrosine, isoleucine, leucine, and valine, aromatics such as alkyl paraben, for example, methyl paraben, and benzoic acid.
The content of hydrophobic compounds is in the range of 0.01-60 (by weight hydrophobic compound / polymer); most preferably between 0.1-30 (w / w hydrophobic compound / polymer).
Targeting
Microparticles can be targeted specifically or not specifically by selecting the polymer forming the microparticle, the size of the microparticle, and / or introducing or attaching a ligand to the microparticles.
For example, biologically active molecules, or molecules affecting the charge, lipophilicity, or hydrophilicity of the particle, can be attached to the surface of the microparticle.
In addition, the molecules can be attached to the microparticles, which minimizes tissue adhesion or facilitates special targeting of the microparticles in vivo.
Representative target molecules include antibodies, lectins, and other molecules that are specifically bound by receptors on the surfaces of a particular cell type.
Inhibition of uptake by RES (reticuloendothelial system)
Uptake and removal of microparticles can also be minimized by polymer selection and / or the incorporation or coupling of molecules which minimize adhesion or uptake.
For example, tissue adhesion by the microparticle can be minimized by covalently bonding a poly (alkylene glycol) moiety to the surface of the microparticle.
The surface portions of the poly (alkylene glycol) have a high affinity for water, which reduces the adsorption of the protein on the particle surface.
The recognition and uptake of the microparticle by the reticuloendothelial system (RES) is therefore reduced.
In one method, the hydroxyl terminal group of the poly (alkylene glycol) is covalently attached to biologically active molecules, or molecules affecting the charge, lipophilicity, or hydrophilicity of the particle, on the surface of the microparticle.
The available technical methods can be used to attach any of a wide variety of ligands to microparticles to enhance the delivery properties, stability, or other properties of the microparticles in vivo.
Active measures
Active agents that can be incorporated into the matrix for delivery include therapeutic and prophylactic agents.
They can be proteins, peptides, sugars, oligosaccharides, nucleic acid molecules, or other synthetic or natural agents.
The agents may be labeled with a detectable label such as a fluorescent label, or an enzymatic or chromatographically detectable agent.
Recommended medications include antibiotics, antivirals, vaccines, vasodilators, vasoconstrictor agents, immunomodulatory compounds, including steroids, antihistamines, and cytokines such as interleukins, colony stimulating factors, tumor necrosis factor, and interferon (α, β, g) , oligonucleotides including genes and an anti-sensory agent, nuclease, bronchodilators, hormones including reproductive hormones, calcitonin, insulin, ertropoietin, growth hormones, and other types of drugs such as AntibanTM.
Methods of making the matrix
In the most preferred embodiment, the microparticles are produced using spray drying.
Techniques that can be used to make other types of matrices, as well as microparticles, include melt extrusion, compression molding, fluidized bed drying, solvent extraction, hot melt encapsulation, and solvent evaporation, as discussed below.
The main criterion is that the hydrophobic compound must be dissolved or fused with the polymer prior to forming the matrix.
As a result, the hydrophobic (or amphiphilic) compound is mixed throughout the matrix in a relatively uniform manner and not simply over the surface of the finished matrix.
The active agent can be introduced into the matrix as solid particles, as a liquid or liquid droplets, or by dissolving the agent in a polymeric solvent.
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Solvent evaporation
In this method, the polymer and the hydrophobic compound are dissolved in a volatile organic solvent such as methylene chloride.
The pore former may be added to the solution as a solid or as a liquid. The active agent can be added as either a solid or in solution to the polymer solution.
The mixture is treated with high frequency sounds or homogenized and the resulting dispersion or emulsion is added to an aqueous solution which may contain a surfactant such as TWEENTM 20, TWEENTM 80, PEG (polyethylene glycol) or poly (vinyl alcohol) and is homogenized for forming an emulsion.
The resulting emulsion is agitated until most of the organic solvent has evaporated, leaving the microparticles.
Many different polymer concentrations (0.05-0.60 g / ml) can be used. By this method, microparticles of various sizes (1-1000 micrometers) and morphologies can be obtained. This method is especially useful for relatively stable polymers like polyesters.
Solvent evaporation is described by E. Mathiowitz et al., J. Scanning Microscopy, 4, 329 (1990); LR Beck et al., Fertil. Steril., 31, 545 (1979) and S. Benita et al., J. Pharm. Sci., 73, 1721 (1984), whose teachings are included herein.
Particularly hydrolytically labile polymers such as polyanhydrides can degrade during the manufacturing process due to the presence of water. For these polymers, the following two methods are more useful, which are performed in completely organic solvents.
Hot melt microencapsulation
In this method, the polymer and the hydrophobic compound are first melted and then mixed with a solid or liquid active agent.
The pore former may be added to the solution as a solid or in solution. The mixture is suspended in an immiscible solvent (such as silicone oil) and, with continued stirring, heated to 5 ° C above the melting point of the polymer.
Once the emulsion is stabilized, it is cooled until the polymer particles solidify.
The resulting microparticles are washed by decantation with a non-polymeric solvent such as petroleum ether (fraction boiling at 20-135 ° C) to give a free flowing powder.
In this way, microparticles with sizes between 1 and 1000 micrometers can be obtained.
The outer surfaces of particles prepared by this technique are usually smooth and compact. This procedure is used to prepare microparticles made of polyesters and polyanhydrides.
However, this method is limited to polymers with molecular weights between 1000-50,000.
Hot melt microencapsulation is described by E. Mathiowitz et al., Reactive Polymers, 6, 275 (1987), the teachings of which are incorporated herein.
Preferred polyanhydrides include polyanhydrides made of dicarboxyphenoxypropane and sebacic acid with a molar ratio of 20:80 (P (CPP-SA) 20:80) (molecular weight 20,000) and poly (fumar-co-sebacin) microparticles (20:80) (molecular weight 15,000).
Solvent removal
This technique was originally intended for polyanhydrides. In this method, a solid or liquid active agent is dispersed or dissolved in a solution of the selected polymer and hydrophobic compound in a volatile organic solvent such as methylene chloride.
This mixture is suspended by stirring in an organic oil (such as silicone oil) to form an emulsion.
Unlike solvent evaporation, this method can be used to make microparticles from polymers with high melting points and different molecular weights.
The external morphology of the particles produced by this technique is very dependent on the type of polymer used.
Spray drying of microparticles
Microparticles can be produced by spray drying by dissolving a biocompatible polymer and a hydrophobic compound in an appropriate solvent, dispersing a solid or liquid active agent in the polymer solution, and then spray drying the polymer solution to form microparticles.
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As referred to herein, the "spray-drying" process of a polymer solution and active agent refers to a process in which the solution is nebulized to form a fine mist dried by direct contact with hot carrier gases.
When using a spray-drying device available in the art, the polymer solution can be supplied through the inlet of the spray dryer, passes through a pipe in the dryer, and is then sprayed through the outlet.
The temperature can be varied depending on the gas and polymer used.
The temperature of the inlet and outlet ports can be controlled to produce the desired products.
The particle size of the polymer solution is a function of the nozzle used to atomize the polymer solution, the pressure of the nozzle, the flow rate, the polymer used, the polymer concentration, the type of solvent and the atomization temperature (both inlet and outlet temperatures) and the molecular weight.
Basically, the higher the molecular weight, the larger the particle size, assuming the concentration is the same.
Typical spray drying parameters are as follows: polymer concentration = 0.005-0.20 g / ml, inlet temperature = 20-1000 ° C, outlet temperature = 10-300 ° C, polymer flow rate = 5-2000 ml / min and internal diameter nozzle = 0.2-4 mm.
Microparticles ranging in diameter between one and ten micrometers can be obtained, with a morphology that depends on polymer selection, concentration, molecular weight, and spray flow.
If the active agent is solid, the agent may be encapsulated as solid particles that are added to the polymer solution prior to spraying, or the agent may be dissolved in an aqueous solution which is then emulsified with the polymer solution prior to spraying, or the solid may be co-dissolved with the polymer solution prior to spraying. with the polymer in a suitable solvent before spraying.
Hydrogel microparticles
Microparticles made of gel-type polymers such as polyphosphazene or polymethyl methacrylate are produced by dissolving the polymer in an aqueous solution, suspending, if desired, a pore-forming agent and suspending the hydrophobic compound in the mixture, homogenizing the mixture, and extruding the material through a micro-droplet forming device producing microdroplets, which fall into a curing bath consisting of an oppositely charged solution or a polyelectrolyte solution, which bath is slowly stirred.
The advantage of these systems is the ability to further modify the surface of the microparticles by coating them with polycationic polymers, such as polylysine, after manufacture.
The microparticle particles are controlled by using extruders of various sizes.
Additives to facilitate the formation of the matrix
A variety of surfactants can be added to the continuous phase as emulsifiers, if used in the manufacture of the matrices.
Exemplary emulsifiers or surfactants that can be used (0.1-5% by weight) include most physiologically acceptable emulsifiers.
Examples include natural and synthetic forms of bile salts or bile acids, both conjugated with amino acids and unconjugated such as taurodeoxycholate and cholic acid.
Unlike the methods described herein, these surfactants will coat the microparticle and facilitate dispersion for administration.
Pore-forming agents
The pore formers can be included in an amount between 0.01% and 90% by weight and by volume to increase the porosity of the matrix and create pores during the production of the matrices.
The pore former may be added as solid particles to the polymer solution or polymer melt, or added as an aqueous solution that is emulsified with the polymer solution or co-dissolved in the polymer solution.
For example, in spray drying, solvent evaporation, solvent removal, hot melt encapsulation, a pore former such as a volatile salt, e.g., ammonium bicarbonate, ammonium acetate, ammonium chloride or ammonium benzoate, or other lyophilized salt, is first dissolved in water.
The pore-forming agent-containing solution is then emulsified with the polymer solution to form pore-forming droplets in the polymer.
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This emulsion is then spray dried or taken through a solvent evaporation / extraction process.
After precipitation of the polymer, the hardened microparticles can be frozen and lyophilized to remove pore forming agents not removed during the microencapsulation process.
Methods of using the drug delivery matrix through various drug delivery systems
The matrix can be administered orally, at its destination, to a mucosal surface (ie, nasal, pulmonary, vaginal, rectal), or by implantation or injection, depending on the form of the matrix and the agent to be delivered.
Useful pharmaceutically acceptable carriers include a saline solution containing glycerin and TWEENTM 20 and isotonic mannitol containing TWEENTM 20.
The matrix can also be in the form of powders, tablets, capsules, or a topical formulation such as an ointment, gel or lotion.
Microparticles can be administered as a powder or formed into tablets or capsules, suspended in a solution or in a gel (ointment, lotion, hydrogel).
As noted above, the size of the microparticles is determined by the mode of administration.
In a preferred embodiment, the microparticles are produced between 0.5 and 8 microns in diameter for intravascular administration, 1-100 microns in diameter for subcutaneous or intramuscular administration, and between 0.5 and 5 mm in diameter for oral administration for delivery to the gastrointestinal tract. or other lines or for application to other mucosal surfaces (rectal, vaginal, oral, nasal).
A preferred size for administration to the respiratory system is an aerodynamic diameter between one and three micrometers with an actual diameter of five micrometers or more, as described in US Patent No. 5,855,913, issued January 5, 1999 to Edwards et al.
Particle size analysis can be performed on a Coulter counter, by light microscopy, scanning electron microscopy, or transmittance electron microscopy.
In a preferred embodiment, the microparticles are combined with a pharmaceutically acceptable carrier such as phosphate buffered saline or saline or mannitol, then an effective amount is administered to the patient via an appropriate route, typically by injection into a blood vessel (iv), subcutaneously, intramuscularly (IM), or orally. .
The active agent-containing microparticles can be used for delivery to the vascular system as well as delivery to the liver and kidney systems, in cardiological applications, and in the treatment of tumors and neoplastic tissues.
For administration to the respiratory system, microparticles can be combined with pharmaceutically acceptable bulking agents and administered as a dry powder.
Pharmaceutically acceptable bulking agents include sugars such as mannitol, sucrose, lactose, fructose, and trehalose. Microparticles can also be associated with ligands that minimize tissue adhesion or that target the microparticles to specific regions of the body in vivo, as described above.
The methods of the invention, the polymeric matrix of the invention and their uses described above are illustrated in more detail in the following non-limiting examples.
Example 1: Preparation of PLGA: DAPC Drug Delivery Particles.
grams PLGA (50:50) (IV 0.4 dL / g Boehringer Ingelheim), 1.8 g diarachidoyl phosphatidylcholine (Avanti, Birmingham, AL) and 495 mg Azure A (Sigma Chemicals, St. Louis, MO) were dissolved in 1000 ml of methylene chloride.
The solution was pumped at a flow rate of 20 ml / min and spray dried using a Bucchi Lab spray dryer. The inlet air temperature was 40 ° C.
The dried microparticle powder was collected and stored at -20 ° C until analysis.
Analysis of the microparticle size was performed using a Coulter II multi-size analyzer.
The microparticles have a mean volume diameter of 5.982 micrometers.
Example 2 grams of PLGA (50:50) (IV 0.4 dL / g Boehringer Ingelheim), 1.08 g of diarachidoylphosphatidylcholine (Avanti, Birmingham, AL) was dissolved in 600 ml of methylene chloride. 38.9 mg of Eosin Y (Sigma Chemicals) was dissolved in 38.9 ml of a 0.18 g / ml ammonium bicarbonate solution.
The eosin solution was emulsified with the polymer solution using a Silverson homogenizer at 7,000 rpm for 8 minutes.
PL 196 159 B1
The solution was pumped at a flow rate of 20 ml / min and spray dried using a Bucchi Lab spray dryer.
The inlet air temperature was 40 ° C. The dried microparticle powder was collected and stored at 20 ° C until analysis.
Analysis of the microparticle size was performed using a Coulter II multi-size analyzer.
Contents7
41 members in 19 offices
Priority claims10
| Document | Office | Kind | Date |
|---|---|---|---|
| 8363698 | United States of America | P | |
| 8363698 | United States of America | P | |
| 25517999 | United States of America | A | |
| 25517999 | United States of America | A | |
| 9905187 | United States of America | W | |
| 9905187 | United States of America | W | |
| 60083636 | – | – | – |
| US19980083636P | – | – | – |
| US19990255179 | – | – | – |
| WO1999US05187 | – | – | – |
Members41
| Document | Office | Kind | |
|---|---|---|---|
| CA2329875A1 | Canada | A1 | |
| WO9956731A1 | World Intellectual Property Organization (WIPO) | A1 | |
| AU2995499A | Australia | A | |
| NO20005452D0 | Norway | D0 | |
| NO20005452L | Norway | L | |
| BR9910340A | Brazil | A | |
| EP1073422A1 | European Patent Office (EPO) | A1 | |
| US2001000230A1 | United States of America | A1 | |
| US2001000470A1 | United States of America | A1 | |
| KR20010043136A | Republic of Korea | A | |
| CN1301150A | China | A | |
| PL343691A1 | Poland | A1 | |
| US2001043948A1 | United States of America | A1 | |
| IL139252A0 | Israel | A0 | |
| IL139252D0 | Israel | D0 | |
| MXPA00010566A | Mexico | A | |
| AU746696B2 | Australia | B2 | |
| JP2002513752A | Japan | A | |
| US6423345B2 | United States of America | B2 | |
| NZ508470A | New Zealand | A | |
| US2003147962A1 | United States of America | A1 | |
| CA2329875C | Canada | C | |
| US6689390B2 | United States of America | B2 | |
| US6730322B1 | United States of America | B1 | |
| CN1201729C | China | C | |
| EP1073422B1 | European Patent Office (EPO) | B1 | |
| AT319433T | Austria | T | |
| ATE319433T1 | Austria | T1 | |
| DE69930240D1 | Germany | D1 | |
| US7052719B2 | United States of America | B2 | |
| PT1073422E | Portugal | E | |
| DK1073422T3 | Denmark | T3 | |
| ES2259472T3 | Spain | T3 | |
| IL139252A | Israel | A | |
| DE69930240T2 | Germany | T2 | |
| US7160557B2 | United States of America | B2 | |
| KR100703051B1 | Republic of Korea | B1 | |
| US2007104656A1 | United States of America | A1 | |
| NO324895B1 | Norway | B1 | |
| PL196159B1This record | Poland | B1 | |
| JP5153032B2 | Japan | B2 |
Numbers
- Publication
- 196159
- Publication, DOCDB
- 196159
- Publication, EPODOC
- PL196159B
- Application
- 343691
- Application, DOCDB
- 34369199
- Application, EPODOC
- PL19990343691
Titles2
- English
- MATRICES FORMED OF POLYMER AND HYDROPHOBIC COMPOUNDS FOR USE IN DRUG DELIVERY
- Polish
- Matryca polimeryczna do dostarczania środka terapeutycznego albo profilaktycznego, sposób wytwarzania matrycy polimerycznej do dostarczania terapeutycznego albo profilaktycznego czynnika i sposób przygotowania terapeutycznego albo profilaktycznego środka z wykorzystaniem matrycy polimerycznej
Classification
- CPC, 3
- A61K9/1617
- A61K9/20
- A61K9/1647
- IPC, 5
- A61K9 16
- A61K9 22
- A61K9 52
- A61K47 24
- A61K47 30