Pharmaceutical formulations for the sustained release of one or more active principles and therapeutic applications thereof
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- 1Zastrzeżenia patentowe 1. Preparat farmaceutyczny ciekły do przedłużonego uwalniania substancji aktywnej(ych) -PA-, przy czym ten preparat obejmuje co najmniej jedną substancję aktywną PA, korzystnie w roztworze wodnym oraz zawiesinę koloidalną, wodną, o niskiej lepkości, na bazie cząstek submikronowych polimeru (PO) zdolnego do biologicznego rozkładu, rozpuszczalnego w wodzie i niosącego grupy hydrofobowe (GH), i przy czym wymienione cząstki są zasocjowane niekowalencyjnie ze wspomnianą substancją aktywną (PA), znamienny:♦ tym, że środowisko dyspersyjne zawiesiny jest zasadniczo utworzone przez wodę, ♦ i tym, że jego stężenie [PO] jest ustalone na wartości wystarczająco wysokiej, tak że wymieniony preparat farmaceutyczny nadaje się do wstrzyknięć drogą pozajelitową i następnie do tworzenia in vivo galeretowatego osadu, przy czym to tworzenie galeretowatego osadu: ◦ jest z jednej strony co najmniej częściowo wywołane przez co najmniej jedno białko fizjologiczne obecne in vivo, ◦ i z drugiej strony umożliwia przedłużenie i kontrolowanie czasu uwalniania PA in vivo, powyżej 24 godzin po podaniu, ♦ i tym, że jest ciekły w warunkach wstrzyknięcia, ♦ i tym, że jest również ciekły w temperaturze i/lub w pH fizjologicznych, i/lub w obecności: * elektrolitu fizjologicznego o stężeniu fizjologicznym, * i/lub co najmniej jednego środka powierzchniowo czynnego. 2. Preparat farmaceutyczny ciekły do przedłużonego uwalniania substancji aktywnej(ych) -PA-, przy czym ten preparat: ◦ jest ciekły w atmosferze otoczenia, ◦ jest również ciekły w temperaturze i/lub w pH fizjologicznych i/lub w obecności: ♦ elektrolitu fizjologicznego o stężeniu fizjologicznym, ♦ i/lub co najmniej jednego środka powierzchniowo czynnego, ◦ i obejmuje co najmniej jedną substancję aktywną PA, korzystnie w roztworze wodnym i zawiesinę koloidalną, wodną, o niskiej lepkości, na bazie cząstek submikronowych polimeru PO zdolnego do biologicznego rozkładu, rozpuszczalnego w wodzie i niosącego grupy hydrofobowe GH, przy czym wymienione cząstki są zasocjowane niekowalencyjnie z co najmniej jedną wymienioną substancją aktywną PA i środowisko dyspersyjne zawiesiny jest zasadniczo utworzone przez wodę, znamienny tym, że jego stężenie [PO] jest ustalone na wartości wystarczająco wysokiej dla umożliwienia tworzenia galeretowatego osadu in vitro, w obecności co najmniej jednego białka. 3. Preparat według któregokolwiek z zastrz. poprzednich, znamienny tym, że jego stężenie [PO] jest takie, że: [PO] > 0,9.C1, korzystnie 20.C1 > [PO] > C1, i jeszcze lepiej 10.C1 > [PO] > C1 z C1 oznaczającym stężenie "wywołanego żelowania" cząstek PO, takie jak zmierzone w teście GI. 4. Preparat według któregokolwiek z zastrz. poprzednich, znamienny tym, że jego lepkość jest równa lub mniejsza od 5 Pa.s. 5. Preparat według któregokolwiek z zastrz. poprzednich, znamienny tym, że modyfikowane polimery hydrofobowe (PO) są dobrane z grupy obejmującej: poliaminokwasy, polisacharydy - korzystnie z podgrupy obejmującej pullulany i/lub chitozany i/lub mukopolisacharydy, żelatyny lub ich mieszaniny. 6. Preparat według któregokolwiek z zastrz. poprzednich, znamienny tym, że grupy hydrofobowe (GH) znajdują się z boku łańcucha. 7. Preparat według któregokolwiek z zastrz. poprzednich, znamienny tym, że polimer PO jest poliaminokwasem utworzonym przez jednostki kwasu asparaginowego i/lub jednostki kwasu glutaminowego, przy czym co najmniej część tych jednostek niesie grupy wszczepiane, obejmujące co najmniej jedną grupę hydrofobową (GH). 8. Preparat według zastrz. 7, znamienny tym, że polimer (lub polimery) PO jest lub (są) określony(e) następującym ogólnym wzorem (I): w którym: 1 R oznacza H, alkil liniowy o C2 do C w lub rozgałęziony o C3 do C w , benzyl, terminalną jednostkę aminokwasu lub -R 4 -[GH];R 2 oznacza H, grupę acylową liniową o C2 do C w lub rozgałęzioną o C3 do C w , piroglutaminian lub -R 4 -[GH];R 3 oznacza H lub jednostkę kationową, korzystnie dobraną z grupy obejmującej: - kationy metaliczne korzystnie wybrane z podgrupy obejmującej: sód, potas, wapń, magnez, - kationy organiczne korzystnie wybrane z podgrupy obejmującej: • kationy na bazie aminy, • kationy na bazie oligoaminy, • kationy na bazie poliaminy (polietylenoiminajest szczególnie korzystna) • kationy na bazie aminokwasu(ów) korzystnie wybrane z klasy obejmującej kationy na bazie lizyny lub argininy, - lub poliaminokwasy kationowe korzystnie wybrane z podgrupy obejmującej polilizynę lub oligolizynę;R 4 oznacza wiązanie bezpośrednie lub "spacer" na bazie od 1 do 4 jednostek aminokwasu;A oznacza niezależnie grupę -CH2- (jednostka asparaginowa) lub -CH2-CH2- (jednostka glutaminowa);n/(n+m) jest określone jako molowy wskaźnik szczepienia i jego wartość jest wystarczająco niska, aby PO rozpuszczony w wodzie o pH 7 i w 25°C, utworzył zawiesinę koloidalną cząstek submikronowych PO, korzystnie n/(n + m) jest zawarte między 1 do 25% molowych i jeszcze lepiej między 1 i 15% molowych;n + m zmienia się od 10 do 1000, korzystnie między 50 i 300;GH oznacza grupę hydrofobową. 9. Preparat według zastrz. 7, znamienny tym, że polimer (lub polimery) PO odpowiada(ją) następującym ogólnym wzorom (II), (III) i (IV): w których: GH oznacza grupę hydrofobową;R oznacza grupę alkilową liniową o C 2 do C 6 ;3 R ' oznacza H lub jednostkę kationową, korzystnie dobraną z grupy obejmującej: - kationy metaliczne korzystnie wybrane z podgrupy obejmującej: sód, potas, wapń, magnez, - kationy organiczne korzystnie wybrane z podgrupy obejmującej: • kationy na bazie aminy, • kationy na bazie oligoaminy, • kationy na bazie poliaminy (szczególnie korzystna jest polietylenoimina) • kationy na bazie aminokwasu(ów) korzystnie wybrane z klasy obejmującej kationy na bazie lizyny lub argininy, - lub poliaminokwasy kationowe korzystnie wybrane z podgrupy obejmującej polilizynę lub oligolizynę;R oznacza grupę alkilową, dialkoksy lub diaminę o C 2 do C 6 ;R 4 oznacza wiązanie bezpośrednie lub "spacer" na bazie od 1 do 4 jednostek aminokwasu;A oznacza niezależnie grupę -CH 2 - (jednostka kwasu asparaginowego) lub -CH 2 -CH 2 - (jednostka kwasu glutaminowego);n' + m' lub n" jest określony jako stopień polimeryzacji i zmienia się od 10 do 1000, korzystnie między 50 i 300. 10. Preparat według zastrz. 8 albo 9, znamienny tym, że każda z grup GH w PO oznacza niezależnie od siebie grupę jednowartościową o następującym wzorze: (GH) w którym: 5 - R oznacza metyl (alanina), izopropyl (walina), izobutyl (leucyna), sec-butyl (izoleucyna), benzyl (fenyloalanina);- R 6 oznacza grupę hydrofobową, obejmującą od 6 do 30 atomów węgla;-1 zmienia się od 0 do 6. 11. Preparat według zastrz. 10, znamienny tym, że całość lub część grup hydrofobowych R 6 z PO jest niezależnie wybrana z zespołu grup obejmującego: grupę alkoksy liniową lub rozgałęzioną, zawierającą od 6 do 30 atomów węgla i mogącą obejmować co najmniej jeden heteroatom (korzystnie O i/lub N i/lub S) i/lub co najmniej jedno wiązanie nienasycone, grupę alkoksy obejmującą 6 do 30 atomów węgla i zawierającą jedną lub kilka izocyklicznych grup pierścieniowych i zawierającą ewentualnie co najmniej jedno nienasycone wiązanie i/lub co najmniej jeden heteroatom (korzystnie O i/lub N i/lub S), alkoksyaryl lub aryloksyalkil o 7 do 30 atomów węgla i mogący obejmować co najmniej jedno nienasycone wiązanie i/lub co najmniej jeden heteroatom (korzystnie O i/lub N i/lub S). 12. Preparat według zastrz. 10 albo 11, znamienny tym, że grupa hydrofobowa R 6 grupy wszczepianej z PO pochodzi z prekursora alkoholowego, wybranego z grupy obejmującej: oktanol, dodekanol, tetradekanol, heksadekanol, oktadekanol, alkohol oleilowy, tokoferol lub cholesterol. 13. Preparat według zastrz. 7, znamienny tym, że PO jest utworzony z homopolimeru alfa-L-glutaminianu lub kwasu alfa-L-glutaminowego. 14. Preparat według zastrz. 7, znamienny tym, że PO jest utworzony z homopolimeru alfa-L-asparaginianu lub kwasu alfa-L-asparaginowego. 15. Preparat według zastrz. 7, znamienny tym, że PO jest utworzony z kopolimeru alfa-L-asparaginian/alfa-Lglutaminian lub kwas alfa-L-asparaginowy/alfa-L-glutaminowy. 16. Preparat według zastrz. 15, znamienny tym, że wPO rozłożenie jednostek kwasu asparaginowego i/lub kwasu glutaminowego, niosących grupy wszczepiane, zawierające co najmniej jedno ugrupowanie GH, jest takie, że polimer tak utworzony jest albo przypadkowy, albo typu bloku, albo typu wielobloku. 17. Preparat według zastrz. 1, znamienny tym, że masa molowa PO sytuuje się między 2000 i 100 000 g/mol, a korzystnie między 5000 i 40 000 g/mol. 18. Preparat według zastrz. 7, znamienny tym, że PO jest nośnikiem co najmniej jednej grupy wszczepianej typu glikolu polialkilenowego związanego z jednostką glutaminianu i/lub asparaginianu. 19. Preparat według zastrz. 18, znamienny tym, że szczepiona grupa typu glikolu polialkilenowego wykazuje następujący wzór (V): (V) w którym: - R' 4 oznacza wiązanie bezpośrednie lub "spacer" na bazie 1 do 4 jednostek aminokwasu;- X stanowi heteroatom wybrany z grupy obejmującej tlen, azot lub siarkę;- R 7 i R 8 oznaczają niezależnie H, alkil liniowy o C-ι do C 4 ;- n"' zmienia się od 10 do 1000, korzystnie od 50 do 300. 20. Preparat według zastrz. 18 albo 19, znamienny tym, że glikol polialkilenowy stanowi glikol polietylenowy. 21. Preparat według któregokolwiek z zastrz. 18 do 20, znamienny tym, że procent molowy szczepienia glikolu polialkilenowego zmienia się od 1 do 30%. 22. Preparat według któregokolwiek z zastrz. poprzednich, znamienny tym, że PA stanowi białko, glikoproteinę, białko związane z jednym lub kilkoma łańcuchami glikolu polialkilenowego [korzystnie glikolu polietylenowego (PEG): „białko-PEG-owane”], polisacharyd, liposacharyd, oligonukleotyd, polinukleotyd lub peptyd, korzystnie wybrany spośród hemoglobin, cytochromów, albumin, interferonów, cytokin, antygenów, przeciwciał, erytropoetyny, insuliny, hormonów wzrostu, czynników VIII i IX, interleukin lub ich mieszanin, czynników stymulujących czynność krwiotwórczą. 23. Preparat według któregokolwiek z zastrz. 1 do 21, znamienny tym, że substancją aktywną jest „mała” cząsteczka organiczna hydrofobowa, hydrofilowa lub amfifilowa. 24. Preparat według któregokolwiek z zastrz. 1 do 22, znamienny tym, że jego frakcja masowa PA niezasocjowanej z cząstkami submikronowymi [PA niezasocjowana] w % wagowych jest taka, że: ◦ [PA niezasocjowana] < 1 ◦ korzystnie [PA niezasocjowana] < 0,5. 25. Preparat według któregokolwiek z zastrz. poprzednich, znamienny tym, że nadaje się do wstrzyknięć drogą pozajelitową, podskórną, domięśniową, śródskórną, dootrzewnową, śródmózgową lub do guza. 26. Preparat według któregokolwiek z zastrz. poprzednich, znamienny tym, że jest przeznaczony do wytwarzania leków, w szczególności do podawania pozajelitowego, podskórnego, domięśniowego, dootrzewnowego, śródmózgowego lub do guza, a nawet drogą doustną, donosową, dopochwową lub do oczu. 27. Sposób wytwarzania leków, w szczególności do podawania pozajelitowego, podskórnego, domięśniowego, dootrzewnowego, śródmózgowego lub do guza, a nawet drogą doustną, donosową, dopochwową lub do oczu, znamienny tym, że polega zasadniczo na na zastosowaniu co najmniej jednego preparatu według któregokolwiek z zastrz. 1 do 26. 28. Produkt pochodny, znamienny tym, że obejmuje cząstki submikronowe, utworzone przez asocjacje niekowalencyjne PO/PA, takie jak określone w zastrz 1, i tym, że jest otrzymany z preparatu według któregokolwiek z zastrz. 1 do 26. 29. Produkt pochodny według zastrz. 28, znamienny tym, że jest utworzony przez proszek lub przez żel. 30. Sposób wytwarzania preparatu według któregokolwiek z zastrz. 1 do 26, znamienny tym, że polega on zasadniczo: ♦ na użyciu zawiesiny koloidalnej nanocząstek co najmniej jednego PO, ♦ na zmieszaniu tej zawiesiny koloidalnej nanocząstek PO z co najmniej jedną PA, korzystnie w roztworze wodnym, ♦ na dodaniu ewentualnie co najmniej jednej zaróbki, ♦ w razie potrzeby na regulowaniu pH i/lub osmolarności oraz ♦ ewentualnie na przesączeniu tak otrzymanej zawiesiny. 31. Sposób według zastrz. 30, znamienny tym, że substancja aktywna (lub substancje aktywne) PA jest (są) w postaci zawiesiny lub roztworu wodnego dla zmieszania z zawiesiną koloidalną nanocząstek PO. 32. Sposób wytwarzania preparatu według któregokolwiek z zastrz. 1 do 26, znamienny tym, że polega on zasadniczo: ♦ na użyciu proszku nanocząstek co najmniej jednego PO, ♦ na zmieszaniu tego proszku z zawiesiną lub roztworem wodnym co najmniej jednej PA, korzystnie w roztworze wodnym, ♦ na dodaniu ewentualnie co najmniej jednej zaróbki, ♦ w razie potrzeby na regulacji pH i/lub osmolarności oraz ♦ ewentualnie na przesączeniu tak otrzymanej zawiesiny. 33. Sposób wytwarzania preparatu według któregokolwiek z zastrz. 1 do 26, znamienny tym, że polega on zasadniczo: ♦ na użyciu proszku pochodzącego z suszenia ciekłego preparatu według któregokolwiek z zastrz. 1 do 26, ♦ na zmieszaniu tego proszku z ciekłym środowiskiem wodnym, korzystnie przy mieszaniu, ♦ na dodaniu ewentualnie co najmniej jednej zaróbki, ♦ w razie potrzeby na regulacji pH i/lub osmolarności oraz ♦ ewentualnie na przesączeniu tak otrzymanej zawiesiny. 34. Sposob wytwarzania proszku pochodnego preparatu według któregokolwiek z zastrz. 1 do 26, znamienny tym, że wymieniony proszek jest otrzymany przez suszenie preparatu według któregokolwiek z zastrz. 1 do 26. Ol Ol t("juj/6d) (Ndll 4500 45000 ·, FIG.2
300 paragraphs in 9 sections, as filed
The present invention relates to new pharmaceutical preparations based on stable and liquid aqueous colloidal suspensions for the sustained release of active substance (s), in particular protein (s) and peptide (s), as well as applications, especially therapeutic, of these preparations.
[0002] These active pharmaceutical preparations relate equally well to human treatment as to veterinary treatment.
[0003] In the field of sustained release of active pharmaceutical substances, especially therapeutic proteins, in many cases there is a need for the best reconstitution in a patient of a plasma concentration of a protein or peptide close to that observed in a healthy individual.
[0004] This target collides with the short life span of plasma proteins, leading to repeated injections of therapeutic protein. The plasma concentration of the therapeutic protein thus exhibits a "sawtooth" profile characterized by high concentration peaks and very low concentration minima. Concentration peaks, much higher than the basal concentration in a healthy individual, have a very visible detrimental effect due to the high toxicity of therapeutic proteins such as interleukin IL2. In addition, the concentration minima are lower than the concentration needed to have a therapeutic effect, which entails poor therapeutic coverage of the patient and secondary dangerous effects in the long run.
[0005] Also, to restore a patient's plasma therapeutic protein concentration close to the ideal value for treating a patient, it is important that the pharmaceutical preparation in question allows the release of the therapeutic protein over a prolonged period, so as to limit changes in plasma concentration over time. [0006] Furthermore, this active preparation should preferably satisfy the following list of requirements already known to the skilled person:
1- sustained release of active therapeutic and non-denatured protein, e.g. human or synthetic, such that the plasma concentration remains at the therapeutic level;
- liquid form, sufficiently fluid for convenient injection and sterilization by filtration on filters in which the pore size is equal to or smaller than 0.2 microns;
- stable liquid form;
- biocompatibility and biodegradability;
- no toxicity;
- lack of immunogenicity;
- excellent local tolerance.
[0007] In attempting to achieve these goals, several approaches have been proposed in the prior art.
[0008] In a first approach, the native therapeutic protein is modified by covalent vaccination of one or more polymer chains or also by covalent vaccination of a protein such as human serum albumin (HSA). The protein thus modified has a lower affinity for its receptors and its half-life in the general circulation increases significantly. The amplitude of the concentration changes between the peaks and decreases in plasma protein concentration is thus significantly reduced. So the company
Shering Plow sells under the name VIRAFERON® PEG interferon alfa 2b chemically modified by grafting a 12kD polyethylene glycol chain. This chemical modification is manifested by increasing the patient's half-life from 6.8 to 33 hours. This chemical modification treatment of the therapeutic protein generally has two major disadvantages. First, the irreversible modification of the protein, which, no longer being a human protein, can lead to toxicity and immunogenicity problems in the long run. The second drawback comes from the partial loss of bioactivity of the modified therapeutic protein.
[0009] In a second approach, it has been proposed to extend the duration of action due to formulations comprising at least one polymer and one active substance, liquid at ambient temperature and atmosphere, injectable and increasing its viscosity after injection, e.g. due to a change in pH and / or temperature.
[0010] Thus, in this list, US-B-6143 314 discloses an organic polymer solution for the controlled release of PA, forming a solid implant after injection. This solution includes:
◦ (A) 10 to 80% by weight of a thermoplastic base polymer, biocompatible, capable of biological degradation and insoluble in water or physiological fluids (e.g. polylactide and / or polyglycolide);
◦ (B) an organic solvent such as N-methylpyrrolidone dispersing in physiological fluids;
◦ (C) active substance (PA);
◦ (D) and finally 1 to 50% by weight of controlled release agent formed by a block copolymer of the type polylactyl glycolide / polyethylene glycol.
After injection, (B) disperses or disperses in physiological fluids. (A) forms an enclosed implant (C) that is not covalently attached to either (A) or (D) and which is then released slowly in vivo.
The main disadvantage of this method is the use of an organic solvent (B), potentially denaturing PA (C) (e.g. therapeutic proteins) and toxic to the patient. In addition, the in vivo hydrolysis of polymer (A) produces an acid that can lead to local tolerance problems.
PCT applications WO-A-99/18142 and WO-A-00118821 relate to aqueous solutions of polymers that contain PA in dissolved or colloidal form, which are suitable for administration to warm-blooded animals, especially by injection, and which form a PA sediment (e.g. Insulin) gelled in vivo because the physiological temperature is higher than their gelation temperature. The gel formed in this way releases PA in a prolonged manner. These specific polymers that are biodegradable are triblock ABA or BAB with A = polylactide-ciclycolide (PLAGA) or polylactide (PLA) and B = polyethylene glycol. Liquid gel transition temperatures of these triblock polymers are e.g. 36, 34, 30 and 26 ° C. Similar to polymers (A) according to US-B-6,143,314, hydrolysis of these ABA or BAB triblock polymers in vivo leads to acids that may not be locally tolerated properly.
[0012] PCT Application WO-A-98/11874 describes pharmaceutical preparations including a lipophilic active substance, gelling polymer (Gelrite® = Gellan gum, deacetylated or ethylhydroxy cellulose) and a surfactant. The polymer / surfactant interaction and, optionally, the working Gelrite® polymer, the mere presence of electrolytes such as Ca ++ at physiological concentration leads to the formation of a gel formed by the polymer / surfactant aggregate to which the non-covalently lipophilic active substance binds. This formulation is intended for local administration to the target organ (e.g. eye). The aggregate / active substance association, which is formed in situ, allows the slow release of the active substance in the target organ.
[0013] The third approach used to attempt to prolong the duration of action of a protein, while fully retaining its bioactivity, was to use non-denatured therapeutic protein and incorporate it into microspheres or implants based on biocompatible polymers. This approach is explained in particular by patent US-B-6 500 448 and application US-A-2003/0133980, describing a composition for sustained release of human growth hormone (hGH), in which the hormonal protein, previously stabilized by metal complexation, is then dispersed in the matrix biocompatible polymer. The biocompatible polymer is e.g. polylactide, polyglycolide or poly (lactide-co-glycolide) copolymer. The composition occurs e.g. in the form of a suspension of microspheres in sodium carboxymethyl cellulose solution. This approach has several drawbacks: first, during the microsphere production method, the protein is contacted with potentially denaturing organic solvents. In addition, the microspheres have large dimensions (1 to 1000 microns), which is an obstacle to injection and convenient sterilization on filters. Finally, local tolerance problems may occur during in situ hydrolysis of the polymer.
[0014] According to a fourth approach, sustained-release therapeutic protein forms formed by liquid and low-viscous suspensions due to nanoparticles loaded with therapeutic proteins have been improved. These suspensions allow convenient administration of native therapeutic proteins.
[0015] Patent FR-B-2 822 834 describes a colloidal suspension of submicron particles that can be used, in particular for the vectorization of active substance (s) (PA), wherein these particles have individualized supermolecular configurations and these particles constitute at least one amphiphilic copolymer, comprising at least one polyalkylene glycol (PAG) type hydrophyte polymer block, preferably polyethylene glycol (PEG) and at least one linear amphiphilic copolyamino acid (PAA), on apeptide chains. This patent specifically discloses a colloidal suspension obtained by mixing 10 mg of amphiphilic copolymer with 1 ml of 1.4 mg / ml insulin solution at pH 7.4.
[0016] The first form of sustained release nanoparticle suspensions is formed by liposome suspensions in which the unmodified native therapeutic protein is encapsulated. After injection, the protein is released gradually from liposomes, which prolongs the time the protein is present in the general circulation. So e.g. Frossen et al. they describe in the article Cancer Res. 43, pp. 546,1983 encapsulation of anti-cancer agents in liposomes to increase therapeutic efficacy. Release of funds is, however, too fast to achieve real sustained release. The company Liposome Company Inc in its patent US-B-5 399 331 proposes to extend the in vitro release time of interleukin 2 by grafting it covalently in a liposome. One then enters the "modified protein" approach referred to above.
[0017] To alleviate the instability of liposomes, while fully maintaining the benefits of a liquid and low-viscosity nanoparticle formulation, Flarnel Technologies proposed another way in which the therapeutic protein is associated with nanoparticles of water-soluble "hydrophobically modified" polyamino acid, i.e. vaccination of hydrophobic groups. This polymer is selected in particular from polyamino acids (polyglutamates or polyaspartates) of grafted hydrophobic groups.
[0018] One of the significant benefits of these modified hydrophobic polymers is the self-assembly spontaneously in water to form nanoparticles.
[0019] Another advantage of these systems is that proteins or peptides, in particular therapeutic proteins, spontaneously associate with hydrophobically modified polymer nanoparticles. This association is non-covalent and occurs without the help of a surfactant and a potentially denaturing transformation method. This is not about encapsulating the protein in a microsphere, as patent US-B-6 500 448 and application US-A-2003/0133980. In a completely different way, these nanoparticles of hydrophobically modified copolyamino acids spontaneously adsorb proteins in solution, without chemical modification or denaturation, and without subjecting them to aggressive "emulsification" and "solvent evaporation" treatment steps. The preparations can be stored in liquid or lyophilized form.
After injection, e.g. via the subcutaneous route, these suspensions of protein-loaded nanoparticles gradually release undenatured and bioactive protein in vivo. Such non-covalent active substance (PA) / poly [Glu] or poly [Asp] associations are disclosed in patent application WO-A-00/30618. This application especially describes colloidal suspensions at pH 7.4, including the association of human insulin with "hydrophobically modified" polyglutamate nanoparticles. The table below summarizes the "hydrophobically modified" polyamino acids used and the degree of association obtained in the examples of WO-A-00/30618.
<td>EXAMPLE</td><td>POLYMER</td><td>Degree of association (%)</td>
<td> 1</td><td>poly [(Glu-O-Na)<sub>0]63</sub>blok- (Glu-O-methyl)<sub>0]37</sub>]</td><td> 55</td>
<td> 2</td><td>poly [Glu-O-Na)<sub>0]66</sub>-blok- (Glu-O-ethyl)<sub>0]34</sub>]</td><td> 26</td>
<td> 3</td><td>poly (Glu-O-Na)<sub>0]65</sub>-blok- (Glu-O-hexadecyl)<sub>0]35</sub>]</td><td> 36</td>
<td> 4</td><td>poly [(Glu-O-Na)<sub>0]88</sub>-blok- (Glu-O-dodecyl)<sub>0]12</sub>]</td><td> >90</td>
The titres of these colloidal suspensions are 1.4 mg / ml insulin and 10 mg / ml "hydrophobically modified" polyamino acid. FIG. 1 of WO-A-00/30618 shows that the in vivo release time of the vectorized insulin by the suspensions mentioned above is 12 hours. You get longer this release time.
So even if this PCT application is already a significant improvement, its technical content can still be optimized, taking into account the list of requirements expressed above, and especially with regard to the prolongation of the in vivo release time.
[0020] Unpublished French patent applications No. 02 07008 from 07/06/2002, 02 09670 from 30/07/2002, 03 50 190 from 28/05/2003 and 01 50641 from 03/10/2003, relate to new soluble amphiphilic polyamino acids in water and including aspartic acid units and / or glutamic acid units in which at least one part of these units are carriers of hydrophobic implanted groups. Similar to the modified hydrophobic polyamino acids disclosed in application WO-A-00/30618, these new polymer raw materials spontaneously form colloidal nanoparticle suspensions in a liquid aqueous environment that can be used for sustained release of PA (insulin). They are biocompatible, capable of biological degradation and proteins, in particular therapeutic proteins, adsorb spontaneously on these nanoparticles without undergoing chemical modification or denaturation.
These applications also relate to new pharmaceutical, cosmetic, dietary or phytosanitary compositions based on these polyamino acids.
[0021] "Hydrophobically modified" amphiphilic polyamino acids according to French Patent Application No. 02 07008 include aspartic acid units and / or glutamic acid units carrying hydrophobic implanted groups containing at least one alpha-tocopherol moiety, e.g. (polyglutamate or polyaspartate grafted by alpha -tocopherol of synthetic or natural origin).
This unpublished application specifically announces a colloidal suspension which contains nanoparticles formed by a polymer / active protein association and which is obtained by mixing 1 mg of alpha-tocopherol grafted polyglutamate and 7 mg of insulin in 1 ml of water at pH 7.0.
[0022] The "hydrophobically modified" amphiphilic polyamino acids of French Patent Application No. 02 09670 contain aspartic acid units and / or glutamic acid units carrying hydrophobic implant groups, including at least one hydrophobic moiety associated with the aspartic acid and / or glutamic acid units flexible connection containing two functional amide groups, more precisely through a lysine or ornithine spacer. This unpublished application specifically announces a colloidal suspension containing nanoparticles formed by polymer / active protein associations and which are obtained by mixing 10 mg of palmitic acid-grafted polyglutamate by "spacer" with lysine and 200 UI insulin (7.4 mg) in 1 ml of water, at pH 7.4.
[0023] The "hydrophobically modified" amphiphilic polyamino acids according to French Patent Application No. 03 50190 contain aspartic acid units and / or glutamic acid units, of which some units carry at least one grafted group, associated with the aspartic or glutamic acid unit, via a spacer "" Amino acid "based on Leu, and / or ILeu, and / or Val, and / or Phe, with the hydrophobic group C<sub>6</sub>-C<sub>30</sub> is bound by an ester bond to "walk".
This unpublished application specifically announces a colloidal suspension that contains nanoparticles formed by polymer / active protein associations and which are obtained by mixing an aqueous solution containing 10 mg of polyglutamate grafted with an implanted group-Leu-OC8, -Val-OC12 or -Valcholesteryl and 200 UI insulin (7.4 mg), per milliliter of water, at pH 7.4.
[0024] French patent application FR-A-01 50641 discloses linear, amphiphilic, anionic homopolyamino acids, including aspartic acid units or glutamic acid units, wherein the ends carry hydrophobic groups, containing from 8 to 30 carbon atoms.
In particular, "hydrophobic modified" telechelic homo-polyamino acids are, for example, poly [GluONa] with PheOC18 / C18 ends or poly [GluONa] with PheOC18 / alpha-tocopherol ends. This unpublished application also describes a colloidal suspension which contains nanoparticles formed by a polymer / active protein association and which are obtained by mixing 10 mg of one of the polymers mentioned above and 200 UI insulin (7.4 mg) per milliliter of water, at pH 7.4 .
According to these unpublished applications, the in vivo release time of the "vectorized" insulin by suspensions is prolonged.
In every state of affairs, all this prior art regarding colloidal suspensions of hydrophobic modified polyamino acid nanoparticles does not discover a preparation enabling:
(I) a sufficient increase in the release time of the active protein after parenteral, in particular subcutaneous injection;
(II) and / or a decrease in the peak plasma concentration of the active protein after injection of the formulation containing it.
[0025] Under these conditions, one of the main objectives of the present invention is therefore to propose a liquid pharmaceutical preparation for the sustained release of the active substance (s), preventing the absence of prior art and in particular enabling injection after parenteral (e.g. subcutaneous) injection, obtaining a prolonged release time. vivo for non-denatured active substances -PA- (e.g. proteins, therapeutic peptides and small molecules), e.g. human or synthetic proteins.
[0026] Another essential object of the invention is to propose a liquid pharmaceutical formulation for sustained release of PA in vivo that is fluid enough to be convenient for injection and sterilization by filtration on filters in which the pore size is equal to or less than 0.2 microns.
[0027] Another essential object of the invention is to propose a liquid pharmaceutical preparation for sustained release of PA in vivo that is stable in both physicochemical and biological storage.
[0028] Another essential object of the invention is to propose a liquid pharmaceutical formulation for sustained release of PA in vivo that exhibits at least one of the following properties: biocompatibility, biodegradability, non-toxicity, good local tolerance.
[0029] Another essential object of the invention is to propose a liquid pharmaceutical preparation for slow sustained release of PA in vivo, wherein the preparation is a low viscosity aqueous colloidal suspension comprising submicron particles of PO polymer spontaneously associating with at least one PA and the PO polymer is a capable polymer for biological decomposition, water-soluble and carrier of hydrophobic groups.
[0030] Another essential object of the invention is to propose a liquid pharmaceutical formulation for the slow sustained release of PA in vivo, wherein the formulation is a low viscosity, colloidal aqueous suspension comprising PO polymer submicron particles spontaneously associating with at least one PA, and the PO polymer is e.g. a polyamino acid formed by aspartic acid units and / or glutamic acid units, wherein at least one part of these units carries implantable groups including at least one hydrophobic (GH) group and PO is also biodegradable, water soluble and amphiphilic.
[0031] Another essential object of the invention is to propose derivative products and / or precursors to the formulation that is pursued for the purposes stated above.
[0032] It is in particular the merit of the Applicant to develop low-viscosity liquid aqueous pharmaceutical preparations at physiological temperature that unexpectedly form a gelatinous precipitate in vivo after parenteral administration, easy for humans or warm-blooded mammals, the formation of this precipitate is not stopped by changing the pH, or temperature during parenteral injection, neither by the presence of electrolyte (s) (such as Ca ++ ions) at physiological concentration and / or at least one surfactant, or by dispersion of an organic solvent in a physiological environment. The gelatinous precipitate thus formed significantly increases the time of PA release in vivo.
It follows that the invention relates to a liquid pharmaceutical preparation for the sustained release of the active substance (s) -PA-, said preparation comprising a low-viscosity, colloidal aqueous suspension based on submicron particles of a polymer (PO) capable of biodegradable, water-soluble and carrying hydrophobic groups (GH), and said particles are non-covalently associated with at least one active substance (PA), characterized by:
♦ in that the dispersion medium of the suspension is essentially formed by water, ♦ in that it is suitable for injection by parenteral route and then for the formation in vivo of a gall-like precipitate, with the formation of a gall-like precipitate:
◦ on the one hand, is at least partly caused by at least one physiological protein present in vivo, ◦ and on the other hand enables extension and control of the time of PA release in vivo, over 24 hours after administration, ♦ in that it is liquid under injection conditions, ♦ and in that it is also liquid at temperature and / or at physiological pH, and / or in the presence of:
* physiological electrolyte at physiological concentration, * and / or at least one surfactant.
[0033] Preferably, this in vivo gelation is not due to a change in pH and / or temperature, nor to the presence of electrolytes (e.g. Ca ++) at physiological concentration and / or at least one surfactant, nor to the in vivo dispersion of one or more organic solvents, optionally contained in the injected preparation. Without wishing to be bound by theory, it can be thought that physiological proteins present in vivo at physiological concentrations allow clustering of nanoparticles of PO associated with at least one PA. Such gelation takes place, inter alia, e.g. within one or several hours, 24 hours, 48 hours or 72 hours.
[0034] According to the invention, the concentration [PO] in the formulation has a fixed value high enough to allow the formation of a gall-like precipitate in vivo, after parenteral injection, in the presence of at least one physiological protein.
[0035] According to an embodiment of the definition, which is no longer based on in vivo behavior as mentioned above but on in vitro behavior, the invention relates to a liquid pharmaceutical preparation for the sustained release of the active substance (s) -PA-, wherein the preparation:
◦ is liquid in the ambient atmosphere, ◦ is also liquid at a temperature and / or physiological pH and / or in the presence of:
* physiological electrolyte with physiological concentration, * and / or at least one surfactant, ◦ and includes a colloidal, aqueous, low viscosity suspension based on submicron particles of PO polymer capable of biological degradation, soluble in water and carrying hydrophobic GH groups, wherein said particles are non-covalently associated with at least one active substance PA, preferably in an aqueous solution and the dispersion medium of the suspension is essentially formed by water, it is characterized in that the concentration [PO] in it has a set value high enough to allow the formation of a gall-like precipitate in vitro in the presence of at least one protein.
[0036] Preferably, the liquid pharmaceutical preparation according to the invention is characterized in that the concentration [PO] therein is such that:
[PO]> 0.9.C1, preferably 20.C1> [PO]> C1, and even better 10.C1> [PO]> C1 with C1 denoting the concentration of "induced gelation" of PO particles, such as those measured in the GI test .
[0037] The galleret-like precipitate obtained after parenteral injection of the formulation allows interesting prolongation of the release time of PA (eg, therapeutic protein) as well as a decrease in the plasma concentration peak. The release time of PA is in particular significantly increased compared to the time of the prior art preparations, in particular those described in PCT patent applications published WO-A-00/30618 and French unpublished patent applications No. 02 07008, 02 09670, 03 50 190 and 01 50641.
[0038] The prolongation of the release time of PA in vivo induced by the formulations of the invention is all the more valuable because PA (e.g. therapeutic proteins) are still fully bioactive and undenatured.
[0039] Throughout the present description, the supermolecular configurations of the PO polymer associated or unassociated with PA will be designated by "submicron particles" or "nanoparticles" without distinction. This corresponds to particles (liquid or solid) with an average hydrodynamic diameter (measured according to the operating mode Md defined below in the examples) e.g. comprised between 1 and 500 nm, preferably between 5 and 250 nm.
[0040] In addition, it is important to note that these preparations are liquid, that is to say they preferably have a very low viscosity that makes their injection convenient. They only gel in vivo. According to the invention, the terms "liquid", "low" or "very low viscosity" preferably correspond to dynamic viscosity at 20 ° C equal to or less than 5 Pa.s. The viscosity reference measurement can be made, e.g. at 20 ° C, using an AR 1000 hydrometer (TA Instruments) equipped with a cone measuring system (4 cm, 2 °).
Viscosity v is measured for a shear stress gradient of 10 s<sup>-</sup> .
Thus, the viscosity of the preparations according to the invention may e.g. be between 1.10 'and 5 Pa.s, preferably between
-3 -3
1.10<sup>-</sup> and 0.8 Pa.si even more preferably between 1.10<sup>-</sup> and 0.5 Pa.s.
This low viscosity makes the preparations according to the invention not only conveniently injectable by parenteral route, in particular by intramuscular or subcutaneous route, but also convenient and cheaper to sterilize by filtration through sterilizing filters with 0.2 mm pore size.
This liquid state or this low viscosity of the formulations according to the invention exists equally well at injection temperatures corresponding to ambient temperatures e.g. between 4 and 30 ° C, as well as physiological temperatures.
[0041] The formulation according to the invention is preferably an aqueous colloidal suspension of nanoparticles associated with one or more PAs. This means that according to the invention, the dispersion environment of this suspension is essentially formed by water. In practice, this water makes e.g. at least 50% by weight based on the total weight of the formulation.
[0042] For the purposes of the invention, the term "protein" means also a protein as a peptide. Wherein this protein or this peptide may be modified or unmodified e.g. by grafting one or more polyoxyethyl ene groups.
[0043] By "physiological proteins" is meant for the purposes of the invention, endogenous proteins and / or peptides of warm-blooded mammals present at the injection site.
[0044] By "physiological temperature" is meant for the purposes of the invention, the physiological temperature of warm-blooded mammals, namely, e.g., about 37-42 ° C.
[0045] By "physiological pH" is meant, for the purposes of the invention, a pH between e.g. between 6 and 7.6.
[0046] By "gel" is meant, for the purposes of the invention, a semi-solid state into which the liquid preparation of the invention is transformed and spontaneously only by the presence of physiological protein (s), without substantial intervention of physiological pH and / or physiological temperature and / or the presence of physiological electrolyte (e.g. Ca ++) and / or dispersion (or dispersion) in vivo of the organic solvent optionally present in the injectable formulation.
[0047] By "physiological electrolyte" is meant for the purposes of the invention, any electrolyte element (e.g., Ca ++ ions) present in warm-blooded mammals.
[0048] By "physiological concentration" is meant for the purposes of the invention, any physiological concentration encountered in warm-blooded mammals, for the physiological environment under consideration.
[0049] Furthermore, the formulations of the invention are non-toxic, well-tolerated locally and stable. [0050] It is also the merits of the inventors to develop an in vitro GI test enabling the selection of populations of preferred preparations according to the invention and determination of the respective PO concentrations in the preparations.
[0051] According to the invention, the GI test for measuring C1 gelation concentration is a reference test enabling the determination of the critical concentration of C1, hereinafter referred to as the induced C1 gelation concentration, which characterizes each colloid preparation according to the invention.
The GI test for determination of C1 induced gelation is as follows:
To determine the C1 concentration, colloidal preparations are prepared with different concentrations of the amphiphilic polymer according to the invention and with a constant concentration of therapeutic protein. To this end, increasing amounts of dry polymer powder dissolve in ionized water. The solutions are kept at 25 ° C. with magnetic stirring for 16 hours and then mixed with concentrated therapeutic protein solution. The volume and concentration of this therapeutic protein solution are adjusted to obtain the desired protein concentration for the formulation [e.g. 0.3 mg / ml interferon alfa 2b or 2.5 mg / ml interleukin 2 (IL2)].
[0052] The colloidal preparations thus prepared are mixed with an aqueous solution of bovine serum albumin (BSA) at a concentration of 30 mg / ml, then centrifuged for 15 minutes at 3000 rpm. The mixtures are allowed to stir gently for 24 hours, after which they are recovered for characterization. [0053] Viscoelasticity measurements are made in a TA Instruments AR 1000 rheometer equipped with a cone system on a plate (diameter 4 cm and angle 1.59 °). Deformation by 0.01 rad, located in the domain of linear viscoelasticity, is imposed in a sinusoidal manner in the frequency range between 0.1 and 300 rad / s. The sample temperature is kept constant at 20 ° C via a Peltier cell.
[0054] The frequency spectra of the modulus of elasticity G 'and the modulus of viscosity or loss G ", allow the determination of the characteristic relaxation time Tr, defined here as the inverse of the frequency at which the modulus of elasticity G' crosses the modulus of viscosity G". A detailed lecture on these issues is in the study of Ferry, Viscoelastic Properties of Polymers, JDFerry, J. Wily, NY, 1980 and in the article by J. REGALADO et al. Macromolecules 1999, 32, 8580.
[0055] The measurement of the relaxation time Tr depending on the concentration of the polymer in the formulation allows the determination of the concentration C1, for which this time Tr increases by 1 second. Examples of C1 gelation concentration values will be given in Example 8 below.
[0056] The concentrations C0.1 and C10 for which the relaxation time exceeds 0.1 s and 10 s, respectively, can be determined. These concentrations are classified in the following ascending order: C0.1 <C1 <C10.
[0057] According to a variant of the preparation according to the invention:
► [PO]> C0.1, ► preferably [PO]> C1, ► and even more preferably [PO]> C10.
[0058] According to an additional advantageous feature: [PO] <20.C1 [0059] For the purposes of the invention throughout the present description, the terms "association" or "associate" used to classify the relationship between one or more active substances and PO polymers (e.g. polyamino acids) means, in particular, that the active substance or substances are bound to the PO polymer (s) [e.g. polyamino acid (s)] by a non-covalent bond, e.g. by electrostatic and / or hydrophobic interaction and / or hydrogen bonding and / or spatial obstacle.
[0060] The PO polymers of the invention are biodegradable polymers, water-soluble and bearing GH hydrophobic groups. The hydrophobic groups may be reduced in number relative to the rest of the chain and may be on the side of the chain or be inserted into the chain, and may be randomly distributed (statistical copolymer) or distributed in the form of sequences or implanted groups (block copolymers or random copolymers).
[0061] Non-limiting hydrophobic modified PO polymers can be selected from the group consisting of amphiphilic copolyamino acids, polysaccharides - preferably from a subgroup consisting of pullulans and / or chitosans and / or mucopolysaccharides, gelatin or mixtures thereof.
[0062] According to a preferred embodiment of the invention, PO is selected from amphiphilic acid copolyamino acids. For the purposes of the present invention and throughout the present specification, the term "polyamino acid" also covers oligoamino acids comprising from 2 to 20 "amino acid" units as polyamino acids containing more than 20 "amino acid" units.
[0063] Preferably, the polyamino acids of the present invention are oligomers or homopolymers comprising repeating units of glutamic or aspartic acid or copolymers comprising mixtures of these two types of "amino acid" units. The units in these polymers are amino acids of the D or L or D / L configuration and are bound in their alpha or gamma positions for the glutamate or glutamic acid unit and alpha or beta for the aspartic acid or aspartate unit.
[0064] Preferred polyamino acid main chain "amino acid" units have an L configuration and an alpha type bond.
[0065] According to yet a more preferred embodiment of the invention, the PO polymer is a polyamino acid formed by aspartic acid units and / or glutamic acid units, wherein at least one part of these units carries implantable groups including at least one hydrophobic GH group. These polyamino acids are especially of the type described in PCT patent application WO-A00 / 30618.
[0066] According to a first possibility, the PO polymer or polymers of the formulation are defined by the following general formula (I):
<img file="PL1689425T3_D0001.tif" />
wherein:
R<sup>1</sup> is H, a linear alkyl of C2 to C<sub>in</sub> or branched at C3 to C<sub>in</sub>, benzyl, terminal amino acid unit or -R<sup>4</sup>- [HG];
R<sup>2</sup> is H, a C2 to C linear acyl group<sub>in</sub> or branched C3 to C<sub>in</sub>, pyroglutamate or -R<sup>4</sup>- [HG];
R<sup>3</sup> is H or a cationic unit, preferably selected from the group consisting of:
- metal cations preferably selected from the subgroup comprising: sodium, potassium, calcium, magnesium,
- organic cations preferably selected from the subgroup comprising:
• amine based cations, • oligoamine based cations, • polyamine based cations (polyethyleneimine is particularly preferred) • amino acid (s) based cations preferably selected from the class including lysine or arginine based cations,
or cationic polyamino acids preferably selected from the subgroup comprising polylysine or oligolysine;
R<sup>4</sup> means a direct bond or "spacer" based on 1 to 4 amino acid units;
A is independently -CH2- (aspartic unit) or -CH2-CH2- (glutamine unit);
n / (n + m) is defined as the molar graft index and its value is low enough that PO dissolved in water opH 7 and at 25 ° C forms a colloidal suspension of submicron particles PO, preferably n / (n + m) is between 1 to 25 mole% and even better between 1 and 15 mole%;
n + m is defined as the degree of polymerization and varies from 10 to 1000, preferably between 50 and 300;
GH is a hydrophobic group.
[0067] According to a second possibility, the PO polymer or polymers of the formulation correspond to one of the following general formulas (II), (III) and (IV):
<img file="PL1689425T3_D0002.tif" />
<img file="PL1689425T3_D0003.tif" />
in which:
GH is a hydrophobic group;
R is a linear alkyl group with C<sub>2</sub> to C.<sub>6</sub>;
<sub>3</sub>
R 'is H or a cationic unit, preferably selected from the group consisting of:
- metal cations preferably selected from the subgroup comprising: sodium, potassium, calcium, magnesium,
- organic cations preferably selected from the subgroup comprising:
• amine based cations, • oligoamine based cations, • polyamine based cations (polyethyleneimine is particularly preferred) • amino acid (s) based cations preferably selected from the class including lysine or arginine based cations
or cationic polyamino acids preferably selected from the subgroup comprising polylysine or oligolysine;
R<sup>50</sup> is an alkyl, dialkoxy or diamine C group<sub>2</sub> to C.<sub>6</sub>;
R<sup>4</sup> means a direct bond or "spacer" based on 1 to 4 amino acid units;
A is independently -CH<sub>2</sub>- (aspartic unit) or -CH<sub>2</sub>CH<sub>2</sub>- (glutamine unit);
n '+ m' or n "is defined as the degree of polymerization and varies from 10 to 1000, preferably between 50 and 300.
[0068] Preferably, each of the GH groups in PO is independently of one another a monovalent group having the following formula:
<img file="PL1689425T3_D0004.tif" />
wherein:
- R<sup>5</sup> is methyl (alanine), isopropyl (valine), isobutyl (leucine), sec-butyl (isoleucine), benzyl (phenylalanine);
- R<sup>6</sup> is a hydrophobic group consisting of from 6 to 30 carbon atoms;
-1 varies from 0 to 6.
[0069] According to the outstanding characteristics of the invention, all or part of the hydrophobic groups R<sup>6</sup>from PO is independently selected from a group of groups including:
a linear or branched alkoxy group containing from 6 to 30 carbon atoms and which may include at least one heteroatom (preferably O and / or N and / or S) and / or at least one unsaturated bond, an alkoxy group containing 6 to 30 carbon atoms and containing one or more isocyclic ring groups and optionally containing at least one unsaturated bond and / or at least one heteroatom (preferably O and / or N and / or S), alkoxyaryl or aryloxyalkyl with 7 to 30 carbon atoms and which may include at least one unsaturated bond and / or at least one heteroatom (preferably O and / or N and / or S).
[0070] In practice and not limiting the hydrophobic group R<sup>6</sup> implanted with PO comes from an alcohol precursor selected from the group consisting of: octanol, dodecanol, tetradecanol, hexadecanol, octadecanol, oleyl alcohol, tocopherol or cholesterol.
[0071] According to a first embodiment of the invention, the main chains of polyamino acids are alpha-L-glutamate or alpha-L-glutamic acid homopolymers.
[0072] According to a second embodiment of the invention, the main chains of the polyamino acids are alpha-L-aspartate or alpha-L-aspartic homopolymers.
[0073] According to a third embodiment of the invention, the main chains of polyamino acids are alphaL-aspartate / alpha-L-glutamate or alpha-L-aspartic / alpha-L-glutamic acid copolymers.
[0074] Preferably, the distribution of aspartic acid and / or glutamic acid units in the main polyamino acid chain of PO is such that the polymer-formed polymorph is either random, of either block type or multi-block type.
[0075] According to another embodiment of the definition, the PO used in the preparation according to the invention has a molar mass that is between 2,000 and 100,000 g / mol and preferably between 5,000 and 40,000 g / mol.
[0076] According to a variant, the PO of the formulation according to the invention is a carrier of at least one grafted polyalkylene glycol type group bonded to the glutamate and / or aspartate unit.
Preferably, this implanted group is of the polyalkylene glycol type having the following formula (V):
R<sup>7</sup> (V) in which:
- R '<sup>4</sup> means a direct bond or "spacer" based on 1 to 4 amino acid units;
- X is a heteroatom selected from the group consisting of oxygen, nitrogen or sulfur;
- R<sup>7</sup> and R<sup>8</sup> are independently H, linear alkyl with C<sub>1</sub> to C.<sub>4</sub>;
- n "'varies from 10 to 1000, preferably from 50 to 300.
In practice, the polyalkylene glycol is e.g. polyethylene glycol.
[0079] It is desirable according to the invention that the molar percentage of grafting of the polyalkylene glycol varies from 1 to 30%.
[0080] Polyamino acids PO are also extremely interesting, because of the adjustable graft index, they disperse in water at pH 7.4 (e.g. with phosphate buffer) to give colloidal suspensions.
[0081] In addition, PA active substances such as proteins, peptides or small molecules can spontaneously associate with nanoparticles including these polyamino acids.
[0082] It should be understood that POs based on polyamino acids contain carboxyl functional groups that are either neutral (COOH form) or ionized (COO- anion) depending on pH and composition. For this reason, the solubility in the aqueous phase is directly dependent on the free COOH index of PO (not grafted with the hydrophobic moiety) and on the pH. In an aqueous solution, the countercation may be a metal cation such as sodium, calcium or magnesium, or an organic cation such as triethanolamine, tris (hydroxymethyl) aminomethane or polyamine such as polyethyleneimine.
[0083] PO types of polyamino acids suitable for use in the formulation of the invention are e.g. obtained by methods known to a person skilled in the art. Statistical polyamino acids can be obtained by grafting with a hydrophobic implanted group, with functional groups previously introduced by "spacer", directly on the polymer through a classical coupling reaction. PO polyamino block or multi-block acids can be obtained by sequential polymerization of the anhydrides of the corresponding N-carboxyamino acids (NCA).
[0084] According to classical methods, e.g. polyamino acid, homopolyglutamate, homopolyaspartate or glutamate / aspartate, block, multi-block or random is prepared. [0085] To obtain an alpha-type polyamino acid, the most common method is based on the polymerization of N-carboxyamino acid anhydrides (NCAs), described for example in the article "Biopolymers, 1976, 15, 1869 and in HR Kricheldorf" alpha-Aminoacid-N-carboxy Anhydrides and related Heterocycles "Springer Verlag (1987). NCA derivatives are preferably NCA-O-Me, NCA-O-Et or NCA-O-Bz derivatives (Me = methyl, Et = ethyl and Bz = benzyl). The polymers are then hydrolysed under appropriate conditions to obtain the polymer in its acid form. These methods are modeled on the description given in patent FR-A-2 801 226 of the Applicant. A certain amount of polymers suitable for use according to the invention e.g. types of poly (alpha-Lasparaginic acid), poly (alpha-L-glutamic acid), poly (alpha-D-glutamic acid) and poly (gammaL-glutamic acid) with different weights are commercially available. Poly-aspartic acid of the alpha-beta type is obtained by condensation of aspartic acid (to obtain polysuccinimide) followed by basic hydrolysis (see Tomida et al. Polymer 1997, 38, 4733-36).
[0086] Coupling of the implanted group with the polymer's acid function is conveniently carried out by reacting the polyamino acid in the presence of carbodiimide as coupling agent and choosing a catalyst such as 4-dimethylaminopyridine and in a suitable solvent such as dimethylformamide (DMF), N-methylpyrrolidone (NMP) or dimethyl sulfoxide (DMSO). Carbodiimide is e.g. dicyclohexylcarbodiimide or diisopropylcarbodiimide. Vaccination rate is chemically controlled by stoichiometry of components and reagents or reaction time. Implanted hydrophobic groups with functional groups introduced via "spacer" are obtained by classical peptide coupling or by direct condensation by acid catalysis. These methods are well known to the skilled person.
[0087] For the synthesis of block or multi-block copolymer, NCA derivatives previously synthesized with an implanted hydrophobic group are used. For example, the hydrophobic NCA derivative is copolymerized with NCA-O-benzyl, then the benzyl groups are removed by selective hydrolysis.
[0088] The synthesis of polyamino acids PO preferably leads to aqueous suspensions of nanoparticles of PO.
[0089] Such suspensions can be converted into PO nanoparticle powders by drying, in a manner suitable and known to the skilled person, such as: heating (dryer ...), reduced pressure, use of drying agents, freeze drying, atomization.
[0090] These PO nanoparticles, in suspension or in powder state, are a raw material for the preparation of the formulations of the invention.
[0091] In this connection, it can be clarified that the preparations according to the invention are the result of a non-covalent association of nanoparticles based on at least one PO and at least one PA in a liquid aqueous environment.
[0092] To form, the PO and / or PA may be in solid (preferably powder) and / or liquid (preferably aqueous colloidal suspension) form.
[0093] The PA / PO association means, for the purposes of this specification, that the active substance (s) PA associates with the PO polymer (s) [e.g. with one or more polyamino acid (s)] through one or more bonds (s) other than the covalent chemical bond (s).
[0094] Methods for associating one or more PAs with POs according to the invention are described in particular in patent application WO-A-00/30618. They consist in incorporating at least one PA into a liquid environment containing PO nanoparticles, so as to obtain a colloidal suspension of nanoparticles charged or associated with one or more active substance (s).
[0095] The invention therefore also relates to a method for producing the above-mentioned formulation. [0096] According to a first preferred embodiment, the method is characterized in that it consists essentially of:
♦ using colloidal suspension of nanoparticles of at least one PO, ♦ mixing this colloidal suspension of nanoparticles of PO with at least one PA, preferably in an aqueous solution, ♦ adding at least one excipient, ♦ if necessary adjusting the pH and / or osmolarity and ♦ optionally filtering the suspension thus obtained.
[0097] Preferably, the active substance (or substances) of the PA is (are) in the form of a suspension or aqueous solution for mixing with the colloidal suspension of nanoparticles of PO.
[0098] According to a second embodiment, the method is characterized in that it consists essentially of:
♦ using powder of at least one PO polymer, ♦ mixing this powder with a suspension or an aqueous solution of at least one PA, preferably in an aqueous solution, ♦ adding at least one excipient, ♦ if necessary adjusting the pH and / or osmolarity and ♦ optionally filtering the suspension thus obtained.
[0099] The formulations thus obtained may also be shaped in the form of gels, powder or foil by conventional methods known to the skilled person, such as concentration by diafiltration or evaporation, application, atomization or lyophilization, among others. Alternatively, these methods can be combined.
[0100] From now on, there will be a third embodiment of the method for producing the liquid formulations of the invention, the third embodiment essentially consisting of:
♦ using powder resulting from drying the liquid formulation according to the invention as defined above, ♦ mixing this powder with a liquid aqueous medium, preferably while mixing, ♦ adding at least one excipient, ♦ if necessary adjusting the pH and / or osmolarity and, optionally, by filtration of the suspension thus obtained.
[0101] Excipients suitable for addition are, for example, antibacterial agents, buffers, antioxidants, agents for regulating isotonicity which are known to the skilled person. For example, refer to the work: Injectable Drug Development, PK Gupta et al., Interpharm Press, Denver, Colorado 1999.
[0102] The optional filtration of the liquid formulation through filters with a porosity of eg 0.2 mm, allows its sterilization. It can thus be injected directly into the patient.
[0103] All these examples of preparation of the liquid formulations of the invention are preferably carried out at an atmosphere and at an ambient temperature (e.g. 25 ° C).
[0104] According to another of its aspects, the invention encompasses any derivative product obtained from the liquid formulation of the invention as defined above and including submicron particles formed by non-covalent PO / PA associations as defined above.
In practice, these derivative products may in particular be formed by, inter alia, powders, gels, implants or films.
[0105] In addition, the invention relates to any precursor of an injectable liquid formulation as defined above.
[0106] Still referring to these derivative products, it should be emphasized that the invention also relates to a process for the preparation of a powder derivative of a formulation as defined above, wherein the method is characterized in that said powder is obtained by drying a formulation such as the specified higher.
[0107] According to the invention, the PA may be a protein, glycoprotein, protein associated with one or more polyalkylene glycol chains [preferably polyethylene glycol (PEG): "PEG-protein"], polysaccharide, liposaccharide, oligonucleotide, polynucleotide or peptide.
Preferably, the PA is selected from hemoglobins, cytochroms, albumin, interferons, cytokines, antigens, antibodies, erythropoietin, insulin, growth hormones, factors VIII and IX, interleukins or mixtures thereof, hematopoietic factors and mixtures thereof.
[0109] According to a variant, the active substance is a "small" hydrophobic, hydrophilic or amphiphilic organic molecule of the type belonging to the anthracycline family, taxoid or camptothecin family or type of molecule belonging to the peptide family such as leuprolide or cyclosporin and mixtures thereof.
For the purposes of this specification, a "small" molecule is especially a small non-protein molecule.
[0110] According to an interesting disposition of the preparation according to the invention, which applies to all PA except small molecules, the mass fraction of the active substance PA not associated with the PO polymer nanoparticles is such that (expressed in% relative to the total mass of the preparation):
► [Unassociated PA] <1 ► preferably [Unassociated PA] <0.5.
[0111] Among the essential qualitative characteristics of the preparation according to the invention, its injectable nature and its ability to form a precipitate at the injection site in vivo, by gelation or by the concentration of nanoparticles in the presence of physiological or analogous proteins are mentioned. [0112] In particular, the preparation of the invention may be injected by parenteral, subcutaneous, intramuscular, intradermal, intraperitoneal, intracerebral or intratumoral routes.
[0113] The formulation of the invention may also be administered by the oral, nasal, vaginal, ocular or buccal route.
[0114] Preferably, the formulation is intended for the manufacture of medicaments, in particular for parenteral, subcutaneous, intramuscular, intraperitoneal, intracerebral or tumor administration, and even by oral, nasal, vaginal or ocular route.
[0115] Although the formulation according to the invention is preferably pharmaceutical, it does not, however, exclude cosmetic, dietary or phytosanitary preparations containing at least one PO as defined above and at least one suitable active substance.
According to yet another aspect of the invention, the invention relates to a method for the preparation of medicaments, in particular for parenteral, subcutaneous, intramuscular, intradermal, intraperitoneal, intracerebral or tumor administration, and even by oral, intranasal, vaginal or ocular route, characterized by this that consists essentially in the use of at least one of the aforementioned formulation and / or any derivative product and / or any precursor of said formulation.
[0117] The invention also relates to the therapeutic use of a preparation as described herein consisting essentially of administering said preparation by parenteral, subcutaneous, intramuscular, intradermal, intraperitoneal, intracerebral or tumor route, and even by oral, intranasal, intravaginal or ocular route so that it forms a gelatinous / cross-linked deposit at the injection site.
[0118] The invention will be better understood and its benefits and application options will be well derived from the examples which follow and which describe the synthesis of POs formed by hydrophobic group grafted polyamino acids, their transformation into a PA sustained release system, i.e. the formulation of the invention (aqueous stable colloidal suspension) and demonstrating the ability of such a system not only to associate with the therapeutic protein, but especially for gelation / crosslinking for very sustained in vivo release of the therapeutic protein.
DESCRIPTION
[0119]
Fig. 1: IFN plasma concentration curves (picogram / ml) recorded in the dog after subcutaneous injection:
• the IFN (A) preparation according to the invention (examples 9 and 10): curve - and the control IFN (D) preparation, outside the invention (example 10): curve ▲ - ▲ -, depending on the time T in hours and dose IFN 60 mg / kg.
Fig. 2: IL2 plasma concentration curves (picogram / ml) recorded for the monkey after subcutaneous injection:
• an IL2 preparation according to the invention (example 11):
curve • of the IL2 (F) control formulation outside the invention (example 11):
curve - · - · -, and of the control IL2 (G) preparation, outside the invention (example 11):
curve ---, depending on the time T in hours and the dose of IL2 0.5 mg / kg.
EXAMPLES:
Example 1: P1 amphiphilic polymer
Synthesis of polyglutamate grafted by synthetic alpha-tocopherol [0120] 5.5 g alpha-L-polyglutamate (equivalent to about 10,000 Da) is dissolved relative to the polyoxyethylene standard obtained by NCAGluOMe polymerization followed by hydrolysis as described in patent application FR-A-2 801 226 in 92 ml dimethylformamide (DMF), with heating at 40 ° C for 2 hours.
After dissolution, the polymer is allowed to reach 25 ° C and 1.49 g D, Lalfa-tocopherol (> 98% obtained from Fluka®) previously dissolved in 6 ml DMF, 0.09 g 4-dimethylaminopyridine previously dissolved in 6 ml are added successively DMF and 0.57 g diisopropylcarbodiimide previously dissolved in 6 ml DMF.
After 8 hours at 25 ° C with stirring, the reaction medium is poured into 800 ml of water containing 15% sodium chloride and hydrochloric acid (pH 2). The precipitated polymer is then obtained by filtration, washed with 0.1N hydrochloric acid and then with water. The polymer is then redissolved in 75 ml of DMF and then re-precipitated in water containing salt and acid as before to pH 2. After two washes with water, it is washed several times with diisopropyl ether. The polymer is then dried in an oven under reduced pressure at 40 ° C. An efficiency of 85% is obtained.
Example 2: P2, P3, P4, P5 and P6 amphiphilic polymers. [0121] These polymers are obtained in the same way as for obtaining the P1 polymer. Table 1 below summarizes the properties of these polymers. The characteristics of the P1 polymer are given as a comparison.
array1
<td>Polymer</td><td>Mn<sup>1</sup> g / mol polyglutamate</td><td>Hydrophobic group</td><td>% vaccination (NMR)<sup>2</sup></td><td>Mn<sup>1</sup> g / mole of polymer</td>
<td>P1</td><td> 10 000</td><td>alpha-tocopherol<sup>3</sup></td><td> 7</td><td> 13 900</td>
<td>P2</td><td> 10 000</td><td>alpha-tokopherol<sup>3</sup></td><td> 4</td><td> 14 400</td>
<td>P3</td><td> 16 900</td><td>alpha-tocopherol<sup>3</sup></td><td> 4</td><td> 15 200</td>
<td>P4</td><td> 10 000</td><td>cholesterol</td><td> 5</td><td> 11 500</td>
<td>P5</td><td> 16 900</td><td>cholesterol</td><td> 5</td><td> 12 900</td>
<td>P6</td><td> 10 000</td><td>n-Dodecanol</td><td> 15</td><td> 11 500</td>
<td colspan="5"><sup>1</sup> In the equivalent of polyoxyethylene.<sub>2</sub>Molar grafting index assessed by proton NMR.<sub>3</sub>Synthetic origin</td>
Example 3: Preparation of 30 ml of interferon alfa 2b (IFN) preparation based on the P6 polymer (a) Preparation of the colloidal amphiphilic polymer solution:
[0122] 1.5 g of the lyophilized polyaminophilic P6 powder of Example 1 above is introduced into the flask. This powder is dissolved in 30 ml of sterile water for injection. The polymer solution is kept for 16 hours at 35 ° C with magnetic stirring. The osmolarity of the solution is adjusted to 275 ± 20 mOsmols using a Fiske Mark 3 osmometer, introducing the required amount of 5.13M NaCl aqueous solution (30% by weight). If necessary, the pH is adjusted to pH 7.4 ± 0.2 by adding 1N NaOH solution. The polymer concentration is adjusted to 45 mg / ml by adding 0.15M sterile NaCl aqueous solution. The polymer solution is then filtered through a 0.8 and 0.2 micron filter and then stored at 4 ° C.
(b) Association of protein with polymer:
26.65 ml of the colloidal solution of the previous P6 polymer and 1.85 ml of the IFN solution (PC GEN; concentrated solution mg / ml) are then mixed in the glass flask. Osmolarity and pH are again adjusted as needed to 300 ± 20 mOsmols and pH 7.4 ± 0.2 by adding 0.1N sodium hydroxide and 0.9% sterile sodium chloride. The protein-charged solution is matured for 5 hours at 25 ° C in a dryer, then filtered through 0.8-0.2 microns. 30 ml of a ready-to-inject preparation containing 0.15 mg / ml of IFN and 40 mg / ml of a P6 polymer are thus obtained.
Example 4: Preparation of the long-acting IFN formulation according to the present invention, based on one of the P1 to P5 polymers. [0124] The production is carried out as in Example 3, preparing in the first step a colloidal solution of the polymer with the final concentration sought 1.25 times mixing this solution with a concentrated interferon solution by 2.42 mg / ml. The volume of protein solution is determined by choosing the ratio of polymer concentration to target protein concentration. As in Example 3, concentration and pH adjustment is made by the addition of NaCl solution and sodium hydroxide.
Example 5: Preparation of the long-acting interleukin-2 (IL2) preparation of the present invention based on the P3 polymer [0125] The required amount of freeze-dried amphiphilic polymer powder and sterile water are introduced into the flask to obtain a polymer concentration equal to X = 1.3 times the concentration sought final in the preparation. The polymer dissolution is prolonged up to 16 hours with magnetic stirring.
The amount of lyophilized IL2 (Prospec) needed is concentrated to X / (X-1) times the final concentration sought. The exact concentration of the concentrated IL2 solution is determined by UV titration at 280 nm, using a Perkin Elmer Lambda 35 UV spectrophotometer.
This IL2 solution is filtered through 0.8-0.2 mm and stored at 4 ° C. Its pH is adjusted to pH 11 by the addition of 1M NaOH. The ratio of the protein concentration in this solution to the desired concentration in the formulation is determined by Y. Then the protein solution and polymer solution are mixed at ambient temperature. X -1 volume of protein solution is added for one volume of polymer. The pH and osmolarity are adjusted to pH 7.4 ± 0.2 and 300 ± 20 mOsm. Thus, to prepare the long-acting IL2 formulation of the invention based on the P3 polymer containing 20 mg / mL of P3 polymer and 2.5 mg / mL of IL2, the initial polymer solution is concentrated to 26 mg / mL. The initial IL2 solution is concentrated to 11 mg / ml. 0.3 volume of protein solution is added per volume of polymer.
Example 6: Measuring the average hydrodynamic diameter of nanoparticles of various PO polymers according to the invention [0126] The average hydrodynamic diameter of the PO polymer particles according to the invention is measured according to the operating mode Md as defined below:
PO solutions of 1 or 2 mg / ml are prepared in 0.15M NaCl medium and left under stirring for 24 hours. Then these solutions are filtered through 0.8-0.2 mm and then analyzed by dynamic light scattering using a Brookhaven type apparatus operating with a 488 nm wavelength laser beam and with vertical polarization. The hydrodynamic diameter of PO polymer nanoparticles is calculated from the electric field autocorrelation function by the semi-invariant method, as described in "Surfactant Science Series" vol. 22, Surfactant Solutions, Ed. R Zana, ch. 3, M. Dekker, 1984. The following results are obtained for polymers PO P2 P3 P4 and P6 from example 2:
TABLE 2
<td>Polymer</td><td>Average hydrodynamic diameter (nm)</td>
<td>P2</td><td> 60</td>
<td>P3</td><td> 90</td>
<td>P4</td><td> 30</td>
<td>P6</td><td> 15</td>
Example 7: Spontaneous association of protein with PO polymer nanoparticles. [0127] A 25 mM phosphate buffer solution is prepared from NaH powder<sub>2</sub>AFTER<sub>4</sub> (Sigma pos. S-0751) and adjusted to pH = 7.2 with 1N sodium hydroxide (SDS pos. 3470015).
A colloidal suspension of polymer P1 nanoparticles is prepared by dissolving the 5 mg / ml lyophilized polymer overnight in a solution of the above phosphate buffer.
A BSA stock solution (Sigma A-2934) is prepared by dissolving the 10 mg / ml protein in the same buffer within two hours.
Stock solutions as well as the buffer are filtered through 0.22 mm.
Mixtures are prepared by adding predetermined volumes of two stock solutions and diluting in phosphate buffer to finally obtain a range of samples with a constant polymer concentration (0.1 mg / ml) and increasing protein concentrations (0 to 1.8 mg / ml) .
[0128] Samples are allowed to associate for 5 hours at 25 ° C, after which they are analyzed by capillary electrophoresis by a frontal method in which protein and protein-polymer complex can be visualized separately. More details of this method can be found in the following article: Gao JY, Dublin PL, Muhoberac BB, Anal. Chem. 1997, 69, 2945. Analyzes are performed on an Agilent G16000A apparatus equipped with a fused silica capillary capillary (type G1600-62-232). The height of the first plateau corresponding to the free protein allows determination of the concentration of unassociated BSA. Experience shows that for amounts of protein less than 0.1 g of protein per g of polymer, the protein is associated with polymer nanoparticles.
Example 8: Determination of the C1 gelation concentration for PO polymers P1 to P4 and P6.
[0129] The GI test was applied to the IFN and IL2 preparations associated with the P1 to P6 polymers from Examples 1 and 2. The protein concentrations in these preparations are given in the table below. Measurement of the relaxation time of preparations in the presence of BSA (concentration 30 mg / ml) is performed according to the GI test operating procedure. Critical concentration C1 for which the relaxation time exceeds 1 s is given in tables 3 and 4 respectively for IFN and IL-2:
TABLICA3:
<td colspan="6">Induced gel concentration for IFN preparations</td>
<td>Polymer</td><td>P1</td><td>P2</td><td>P3</td><td>P4</td><td>P6</td>
<td>IFN concentration (mg / ml)</td><td> 0,3</td><td> 0,15</td><td> 0,15</td><td> 0,15</td><td> 0,3</td>
<td>C1 concentration (mg / ml)</td><td> 17</td><td> >30</td><td> 16</td><td> 17</td><td> >50</td>
TABLE 4
<td colspan="4">Induced gelation concentrations for IL2 preparations</td>
<td>Polymer</td><td>P1</td><td>P3</td><td>P6</td>
<td>IL2 concentration (mg / ml)</td><td> 2,5</td><td> 2,5</td><td> 2,5</td>
<td>C1 concentration (mg / ml)</td><td> 17</td><td> 17</td><td> > 50</td>
Example 9: Pharmacokinetics of IFN in a dog following subcutaneous injection of the IFN formulation of the invention.
[0130] According to the operating mode described in example 3, preparation (A) IFN (concentration 0.3 mg / ml) and amphiphilic polymer P1 at concentration 30 mg / ml is prepared.
This preparation is injected subcutaneously via Beagle dogs (n = 3) at a dose of 60 mg / kg). Serum samples are taken at 1.5, 11.24, 36, 48, 72, 96, 120, 144, 168 and 240 hours. IFN plasma concentration is measured in these samples by ELISA (IM 3193 immunotech kit).
This results in a mean plasma concentration profile, such as that shown in Figure 1, which clearly shows the sustained release of the serum protein relative to the (D) IFN control formulation, outside the invention (concentration 0.3 mg / ml) and polymer 40 mg / ml amphiphilic P6 (compare Table 5, Example 10). In quantitative terms, the prolongation of IFN release by the formulations of the invention is evaluated by measuring:
a) time Tmax, the median time for which the plasma concentration is highest,
b) time T50, the average time at the end of which the area under the plasma concentration curve reaches 50% of its measured maximum value.
For this preparation, Tmax and T50 take the following values:
Tmax = 48 hours
T50 = 54.2 hours
Example 10: Pharmacokinetics of IFN in a dog after subcutaneous injection of various IFN preparations based on polyaminophilic acids [0131] According to the operating mode described in Example 3, the following preparations are prepared:
TABLICA5
<td>Preparation</td><td>Polymer</td><td>Polymer concentration (mg / ml)</td><td>IFN concentration (mg / ml)</td><td>Relaxation time Tr (s)</td>
<td>AND</td><td>P1</td><td> 30</td><td> 0,3</td><td> > 10</td>
<td>B</td><td>P1</td><td> 10,5</td><td> 0,15</td><td> < 0,3</td>
<td>C</td><td>P2</td><td> 15</td><td> 0,15</td><td> < 0,03</td>
<td>D</td><td>P6</td><td> 40</td><td> 0,3</td><td> 0,4</td>
[0132] Formulation A has a polymer concentration higher than the gelation concentration C1 measured in the example
8. In other words, the relaxation time, measured by the GI test, is longer than 1 second. This formulation A therefore belongs to the selection according to the invention. In contrast, formulations B, C and D show lower concentrations than their gelation concentrations and do not belong to the selection according to the invention.
[0133] These preparations are injected at a dose of 60 mg / kg to Beagle dogs. Plasma samples are taken at time 1,
5, 11.24, 36, 48, 72, 96, 120, 144, 168 and 240 hours. IFN plasma concentration is measured as in the previous example.
The times Tmax and T50 for preparations A, B, C and D are given in Table 6 below.
TABLE 6
<td>Reference preparation</td><td>Tmax (h)</td><td>T50 (h)</td>
<td>AND</td><td> 48</td><td> 54,2</td>
<td>B</td><td> 5</td><td> 16,7</td>
<td>C</td><td> 11</td><td> 19,3</td>
<td>D</td><td> 5</td><td> 17,3</td>
Thus, formulation A, which belongs to the selection according to the invention, has a release time significantly increased compared to formulations B, C, and D, which do not belong to the selection according to the invention.
Example 11: Pharmacokinetics of interleukin 2 (IL2) in monkeys after subcutaneous injection of various preparations based on poly-amphiphilic acids [0134] According to the operating mode described in Example 5, the following preparations are prepared:
TABLICA7
<td>Reference</td><td>Polymer</td><td>Polymer concentration (mg / ml)</td><td>IL2 concentration (mg / ml)</td>
<td>E</td><td>P1</td><td> 30</td><td> 2,5</td>
<td>F</td><td>P3</td><td> 20</td><td> 2,5</td>
<td>G</td><td>P6</td><td> 40</td><td> 2,5</td>
[0135] Formulations E and F, which have a higher polymer concentration than the gelation concentration C1 measured in Example 8, therefore belong to the inventive selection. In contrast, formulation G has a concentration lower than the gelation concentration C1 and is not chosen according to the invention.
These preparations are injected at a dose of 0.5 mg / kg to Cynomolgus monkeys. Plasma samples are taken at 1.5, 11.24, 36, 48, 72, 96, 120, 144, 168 and 240 hours. IL2 plasma concentration is measured in these samples by ELISA assay (IM 3583 immunotech kit).
[0136] The times Tmax and T50 for formulations E, Fi G are given in Table 8 below.
TABLICA8
<td>Reference preparation</td><td>Tmax (h)</td><td>T50 (h)</td>
<td>E</td><td> 32</td><td> 34,5</td>
<td>F</td><td> 32</td><td> 37,5</td>
<td>G</td><td> 4</td><td> 10,5</td>
Thus, formulations E and F, which belong to the selection according to the invention, have a release time significantly extended compared to formulation G, which is not selected according to the invention.
Example 12: Observation of in vivo gelation of the formulations of the invention after subcutaneous injection.
[0137] The subcutaneous behavior of the formulations of the invention was studied in domestic pigs. Injections were made under the skin of the abdomen 4 mm deep, six domestic pigs, 0.3 ml each of the following preparations:
Formulation A: isotonic aqueous solution with a pH of 7.3 polymer P6 from Example 2 concentrated to 45 mg / ml.
Formulation B: isotonic aqueous solution at pH 7.3 of the polymer P1 from Example 1 concentrated to 20 mg / ml.
Injection sites were taken 72 hours after administration. Histological examination reveals the presence of a gall-like polymer deposit for preparation B. It occurs in the form of evenly colored fields. On the contrary, this phenomenon is not observed for formulation A, in which the polymer penetrates between collagen fibers. It can be emphasized that the polymer matrix B is perfectly biodegradable because the tissue completely returns to its normal state after 21 days.
Contents9
36 members in 22 offices
Priority claims2
| Document | Office | Kind | Date |
|---|---|---|---|
| 0350887 | France | A | |
| 2004050603 | France | W |
Members36
| Document | Office | Kind | |
|---|---|---|---|
| FR2862536A1 | France | A1 | |
| AU2004292369A1 | Australia | A1 | |
| CA2546675A1 | Canada | A1 | |
| WO2005051416A1 | World Intellectual Property Organization (WIPO) | A1 | |
| TW200518775A | Taiwan Province of China | A | |
| EP1689425A1 | European Patent Office (EPO) | A1 | |
| IL175768A0 | Israel | A0 | |
| IL175768D0 | Israel | D0 | |
| KR20060130076A | Republic of Korea | A | |
| CN1886151A | China | A | |
| MXPA06005717A | Mexico | A | |
| BRPI0416779A | Brazil | A | |
| JP2007511586A | Japan | A | |
| US2007196497A1 | United States of America | A1 | |
| FR2862536B1 | France | B1 | |
| ZA200603950B | South Africa | B | |
| EP1689425B1 | European Patent Office (EPO) | B1 | |
| AT451116T | Austria | T | |
| ATE451116T1 | Austria | T1 | |
| DE602004024571D1 | Germany | D1 | |
| EP1689425B8 | European Patent Office (EPO) | B8 | |
| PT1689425E | Portugal | E | |
| DK1689425T3 | Denmark | T3 | |
| SI1689425T1 | Slovenia | T1 | |
| ES2338012T3 | Spain | T3 | |
| PL1689425T3This record | Poland | T3 | |
| AU2004292369B2 | Australia | B2 | |
| KR101092547B1 | Republic of Korea | B1 | |
| US8084045B2 | United States of America | B2 | |
| IL175768A | Israel | A | |
| JP4988352B2 | Japan | B2 | |
| CN1886151B | China | B | |
| CA2546675C | Canada | C | |
| CY1110612T1 | Cyprus | T1 | |
| BRPI0416779B1 | Brazil | B1 | |
| BRPI0416779B8 | Brazil | B8 |
Numbers
- Application
- 4805846
Titles2
- English
- PHARMACEUTICAL FORMULATIONS FOR THE SUSTAINED RELEASE OF ONE OR MORE ACTIVE PRINCIPLES AND THERAPEUTIC APPLICATIONS THEREOF
- Polish
- Preparaty farmaceutyczne do przedłużonego uwalniania substancji aktywnej(ych) oraz ich zastosowanie, zwłaszcza lecznicze
Classification
- CPC, 8
- A61K9/0024
- A61K9/08
- A61K47/42
- A61K51/1217
- A61K38/2013
- A61K38/212
- A61K47/645
- A61K38/21
- IPC, 7
- A61K38 21
- A61K9 14
- A61K38 17
- A61K38 20
- A61K47 42
- A61K47 48
- A61K51 12