RO114740B1

Controlled release composition, process for preparing the same and method of treatment

Abstract

This record has no abstract on file.

RO114740B1, drawing sheet 1 — Sheet 1 of 1

Term

Term ended

Expired 13 April 2015, 11.4 years ago.

65 claims: 5 independent, 60 dependent

1
Revendicări 1. Compoziție cu eliberare controlată pe bază de azitromicină, caracterizată prin aceea că conține azitromicină și un purtător acceptabil din punct de vedere farmaceutic, care,după ingerarea de către mamifer care are nevoie de aceasta, eliberează azitromicina în tractul gastrointestinal a respectivului mamifer cu o astfel de viteză încât cantitatea totală de azitromicină eliberată este:nu mai mare de circa 4 mg pe kg corp în primele 15 min după ingerare, nu mai mare de circa 10 mg pe kg corp în prima oră după ingerare, nu mai mare de circa 20 mg pe kg corp în primele două ore după ingerare, nu mai mare de 30 mg pe kg corp în primele patru ore după ingerare și nu mai mare de 40 mg pe kg corp în primele șase ore după ingerare.
2
Compoziție cu eliberare controlată pe bază de azitromicină, caracterizată prin aceea că conține azitromicină și un purtător acceptabil din punct de vedere farmaceutic, care,după ingerarea de către mamifer care are nevoie de aceasta, eliberează azitromicina în tractul gastrointestinal a respectivului mamifer cu o astfel de viteză încât cantitatea totală de azitromicină eliberată acolo este:nu mai mare de circa 200 mg pe kg corp în primele 15 min după ingerare, nu mai mare de circa 500 mg pe kg corp în prima oră după ingerare, nu mai mare de circa 1000 mg pe kg corp în primele două ore după ingerare, nu mai mare de 1500 mg pe kg corp în primele patru ore după ingerare , nu mai mare de 2000 mg pe kg corp în primele șase ore după ingerare.
3
Compoziție cu eliberare controlată conform revendicării 1 sau 2, caracterizată prin aceea că azitromicina este înglobată într-o matrice care eliberează azitromicina respectivă prin difuzie.
4
Compoziție cu eliberare controlată conform revendicării 3, caracterizată prin aceea că matricea respectivă rămâne substanțial intactă în timpul perioadei de eliberare a medicamentului.
5
Compoziție cu eliberare controlată conform revendicării 3, caracterizată prin aceea că azitromicina este încorporată într-o matrice care eliberează azitromicina prin erodare.
6
Compoziție cu eliberare controlată conform revendicării 5 , caracterizată prin aceea că matricea cuprinde hidroxipropil metilceluloză.
7
Compoziție cu eliberare controlată conform revendicării 5 , caracterizată prin aceea că matricea cuprinde hidroxipropil celuloză.
8
Compoziție cu eliberare controlată conform revendicării 5, caracterizată prin aceea că matricea cuprinde polietilen oxid.
9
Compoziție cu eliberare controlată conform revendicării 5, caracterizată prin aceea că matricea cuprinde acid poliacrilic.
10
Compoziție cu eliberare controlată conform revendicării 1 sau 2, RO 114740 Bl caracterizată prin aceea că cuprinde un rezervor de azitromicină încastrat într-o 2735 membrană, care limitează viteza de eliberare a azitromicinei în tractul gastro-intestinal prin difuzie.
11
Compoziție cu eliberare controlată conform revendicării 1, caracterizată prin aceea că este sub forma unei tablete acoperite cu o membrană.
12
Compoziție cu eliberare controlată conform revendicării 2, caracterizată 2740 prin aceea că este sub forma unor particule multiple, care este acoperită cu o membrană care limitează viteza de eliberare a azitromicinei prin difuzie.
13
Compoziție cu eliberare controlată conform revendicării 3, caracterizată prin aceea că o porțiune a suprafeței exterioare a matricei este acoperită cu acoperire impermeabilă, iar restul respectivei suprafețe exterioare este neacoperit. 2745
14
Compoziție cu eliberare controlată conform revendicării 13, caracterizată prin aceea că este sub forma unui cilindru acoperit pe una sau ambele suprafețe opuse cu o acoperire impermeabilă.
15
Compoziție cu eliberare controlată conform revendicării 13, caracterizată prin aceea că este sub forma unui cilindru în care respectiva acoperire impermeabilă 2750 acoperă numai suprafața acesteia.
16
Compoziție cu eliberare controlată conform revendicării 13, caracterizată prin aceea că este sub forma unei tablete în care suprafața neacoperită este sub forma unei deschideri prin acoperirea impermeabilă.
17
Compoziție cu eliberare controlată conform revendicării 13, caracterizată 2755 prin aceea că este sub forma unei tablete în care suprafața neacoperită este sub forma unui canal care pătrunde prin întregul dispozitiv.
18
Compoziție cu eliberare controlată conform revendicării 13, caracterizată prin aceea că este sub forma unei tablete în care suprafața neacoperită este sub forma uneia sau mai multor crestături prin respectiva acoperire impermeabilă 2760 sau sub forma a una sau mai multe fâșii îndepărtate de pe aceasta.
19
Compoziție cu eliberare controlată conform revendicării 13, caracterizată prin aceea că este sub forma unui con, în care suprafața neacoperită cuprinde o deschidere pentru transportul medicamentului la sau aproape de vârful conului.
20
Compoziție cu eliberare controlată conform revendicării 13, caracterizată 2765 prin aceea că este sub forma unei semisfere cu suprafață neacoperită, este forma unei deschideri pentru transportul medicamentului la sau aproape de centrul feței plate a semisferei.
21
Compoziție cu eliberare controlată conform revendicării 13, caracterizată prin aceea că este sub forma unei jumătăți de cilindru, în care suprafața neacoperită 2770 este sub forma uneia sau mai multor crestături la sau aproape de fața plată a jumătății de cilindru.
22
Compoziție cu eliberare controlată pe bază de azitromocină, caracterizată prin aceea că conține azitromicină și un purtător acceptabil din punct de vedere farmaceutic, care eliberează nu mai mult de 10% din azitromicina încorporată în 2775 stomacul mamiferului și care eliberează nu mai mult de încă 10% în timpul primelor 15 min după pătrunderea în duodenul mamiferului respectiv.
23
Compoziție cu eliberare controlată conform revendicării 22, caracterizată prin aceea că mamiferul este o ființă umană.
24
Compoziție cu eliberare controlată conform revendicării 22, caracterizată 2780 prin aceea că cuprinde o particulă multiplă, care are un diametru între 0,1 mm și RO 114740 Bl circa 0,5 mm.
25
Compoziție cu eliberare controlată conform revendicării 22, caracterizată prin aceea că cuprinde o particulă multiplă, care are un diametru între 0,5 mm și circa 3 mm.
26
Compoziție cu eliberare controlată conform revendicării 22, caracterizată prin aceea este sub forma unei tablete.
27
Compoziție cu eliberare controlată conform revendicării 22, caracterizată prin aceea că este o tabletă acoperită cu o membrană cuprinzând un polimer în mare măsură insolubil și/sau impermeabil la azitromicină la pH-ul stomacului și este solubil și/sau permeabil la azitromicină la pH-lui intestinului subțire și al colonului.
28
Compoziție cu eliberare controlată conform revendicării 27, caracterizată prin aceea că polimerul utilizat este selectat dintre ftalat acetat de celuloză, ftalat de polivinil acetat, ftalat de hidroxipropil metilceluloză și copolimeri, cuprinzând acid acrilic și cel puțin un ester acid acrilic.
29
Compoziție cu eliberare controlată conform revendicării 25, caracterizată prin aceea că această particulă multiplă este acoperită cu o membrană cuprinzînd un polimer substanțial insolubil și /sau impermeabil la azitromicină la pH-ul stomacului și este solubil și/sau permeabil la ph-ul intestinului subțire și al colonului.
30
Compoziție cu eliberare controlată conform revendicării 29, caracterizată prin aceea că acest polimer este selectat dintre ftalat acetat de celuloză, ftalat de polivinil acetat, ftalat de hidroxipropil metilceluloză și copolimeri cuprinzând acid acrilic și cel puțin un ester acid acrilic.
31
Compoziție cu eliberare controlată conform revendicării 24, caracterizată prin aceea că aceste multiparticule sunt acoperite cu o membrană cuprinzînd un polimer substanțial insolubil și /sau impermeabil la azitromicină la pH-ul stomacului și este solubil și/sau permeabil la azitromocină în intestinul subțire sau colon.
32
Compoziție cu eliberare controlată conform revendicării 31, caracterizată prin aceea că polimerul respectiv este selectat dintre ftalat acetat de celuloză, ftalat de polivinil acetat, ftalat de hidroxipropil metilceluloză și copolimeri cuprinzând acid acrilic și cel puțin un ester acid acrilic.
33
Compoziție cu eliberare controlată conform revendicării 26, caracrerizată prin aceea că tableta cuprinde, opțional, în plus, unul sau mai mulți agenți osmotici, tableta fiind înconjurată de o membrană semipermeabilă care este permeabilă la apă și substanțial impermeabilă la azitromicină și respectivii agenți osmotici.
34
Compoziție cu eliberare controlată conform revendicării 25, caracrerizată prin aceea că particulele multiple cuprind,opțional, în plus, unul sau mai mulți agenți osmotici, particula multiplă fiind înconjurată de o membrană semipermeabilă, care este permeabilă la apă și substanțial impermeabilă la azitromicină și respectivii agenți osmotici.
35
Compoziție cu eliberare controlată conform revendicării 26, caracterizată prin aceea că tableta mai cuprinde, suplimentar, cel puțin un material gonflabil, tableta fiind înconjurată de o membrană semipermeabilă,care este permeabilă la apă și substanțial impermeabilă la azitromicină și material gonflabil.
36
Compoziție cu eliberare controlată conform revendicării 25, caracterizată prin aceea că tableta mai cuprinde, suplimentar, cel puțin un material gonflabil, fiecare din multiparticule fiind înconjurate de o membrană semipermeabilă,care este permeabilă la apă și substanțial impermeabilă la azirtomicină și material gonflabil.
37
Compoziție cu eliberare controlată conform revendicării 25, caracterizată RO 114740 Bl prin aceea că tableta cuprinde un miez conținând azitromicină și cel puțin un agent 2830 osmotic,un perete care înconjoară tableta respectivă cuprinzând o membrană semipermeabilă, care este permeabilă la apă și substanțial impermeabilă la azitromicină, și un agent osmotic, un mijloc declanșator sensibil la pH atașat la respectiva membrană semipermeabilă pentru declanșarea dezagregării tabletei, mijlocul declanșâdu-se la un pH între 3 și 9. 2835
38
Compoziție cu eliberare controlată conform revendicării 26 .caracterizată prin aceea că fiecare particulă multiplă mai cuprinde unul sau mai mulți agenți osmotici, fiecare particulă multiplă fiind înconjurată de un perete ce cuprinde o membrană semipermeabilă, care este permeabilă la apă și substanțial impermeabilă la azitromicină, și un agent osmotic și un mijloc declanșator sensibil la pH atașat la respectiva 2840 membrană semipermeabilă pentru declanșarea dezagregării tabletei, mijlocul declanșându-se la un pH între 3 și 9.
39
Compoziție cu eliberare controlată conform revendicării 37, caracterizată prin aceea că miezul respectiv mai conține cel puțin un material de gonflare.
40
Compoziție cu eliberare controlată conform revendicării 38, caracte- 2845 rizată prin aceea că fiecare particulă multiplă mai conține cel puțin un material de gonflare.
41
Compoziție cu eliberare controlată conform revendicării 26, caracterizată prin aceea că tableta cuprinde un miez ce conține azitromicină și cel puțin un agent osmotic, o membrană care înconjoară miezul tabletei, în care membrana respectivă 2850 este fabricată dintr-un material microporos , hidrofob, de suport, un lichid antrenat în membrana respectivă, care este substanțial impermeabil la apă și azitromicină, dar fiind capabil să se schimbe pentru a deveni substanțial permeabil la apă și azitromicină.
42
Compoziție cu eliberare controlată conform revendicării 25, caracterizată 2855 prin aceea că fiecare dintre particule cuprinde un miez ce conține azitromicină și cel puțin un agent osmotic, o membrană care înconjoară miezul din particulele multiple în care membrana respectivă este fabricată dintr-un material microporos , hidrofob, un lichid hidrofob antrenat în membrana respectivă, acest lichid hidrofob este substanțial impermeabil la apă și azitromicină, dar fiind capabil să se schimbe, devenind 2860 substanțial permeabil la apă și azitromicină.
43
Compoziție cu eliberare controlată conform revendicării 26, caracterizată prin aceea că tableta cuprinde un miez ce conține azitromicină și cel puțin un material de gonflare, o membrană care înconjoară miezul tabletei, în care membrana respectivă este fabricată dintr-un material microporos , hidrofob, un lichid antrenat 2865 în membrana respectivă, lichidul hidrofob fiind substanțial impermeabil la apă și azitromicină, dar fiind capabil să se schimbe, devenind substanțial permeabil la apă și azitromicină.
44
Compoziție cu eliberare controlată conform revendicării 25, caracterizată prin aceea că acea multiparticulă cuprinde un miez ce conține azitromicină și cel 2870 puțin un material de gonflare, o membrană care înconjoară miezul din particulele multiple în care membrana respectivă este fabricată dintr-un material microporos , hidrofob, de suport, un lichid hidrofob antrenat în membrana respectivă care este substanțial impermeabil la apă și azitromicină, dar fiind capabil să se schimbe, devenind substanțial permeabil la apă și azitromicină. 2875
45
Compoziție cu eliberare controlată conform revendicării 26, caracterizată prin aceea tableta cuprinde un miez constituit din azitromicină și cel puțin un agent RO 114740 Bl 2880 2885 2890 2895 2900 2905 2910 2915 2920 de gonflare și /sau un agent osmotic, o membrană care înconjoară miezul tabletei, care este substanțial impermeabilă la azitromicină labilă și enzimele produse de bacterii care populează colonul.
46
Compoziție cu eliberare controlată conform revendicării 25, caracterizata prin aceea cuprinde un miez constituit din azitromicimă și cel puțin un agent de gonflare și /sau un agent osmotic, o membrană care înconjoară miezul particulei multiple, în care membrana respectivă este substanțial impermeabilă la azitromicină și labilă la enzimele produse de bacterii care populează colonul.
47
Compoziție cu eliberare controlată conform revendicării 45, caracterizată prin aceea membrana respectivă conține un polimer care conține cel puțin un monomer nesaturat etilenic, reticulat de un divinilazobenzen, substituit sau nesubstituit.
48
Compoziție cu eliberare controlată conform revendicării 46, caracterizată prin aceea membrana respectivă conține un polimer care conține cel puțin un monomer nesaturat etilenic, reticulat de un divinilazobenzen, substituit sau nesubstituit.
49
Compoziție cu eliberare controlată conform revendicării 45, caracterizată prin aceea că membrana respectivă cuprinde cel puțin o polizaharidă.
50
Compoziție cu eliberare controlată conform revendicării 46, caracterizată prin aceea că membrana respectivă cuprinde cel puțin o polizaharidă.
51
Compoziție cu eliberare controlată conform revendicării 22, caracterizată prin aceea că este sub forma unei capsule,care cuprinde două piese care se interpenetrează, o primă piesă masculină cuprinzând un material gonflabil cu apa, care se gonflează pentru a efectua dizlocarea unei a doua piese femelă la administrarea la mamifer.
52
Compoziție cu eliberare controlată conform revendicării 1, caracterizată prin aceea că cuprinde o tabletă cuprinzând azitromicină și un material gonflabil, o membrană în jurul tabletei, în care membrana respectivă posedă pori prin care azitromicină și agentul gonflabil pot ieși sau în care membrana respectivă conține porogeni solubili în apă, care ies din membrană în mediul apos de utilizare, formând pori prin care pot ieși azitromicină și materialul gonflabil.
53
Compoziție cu eliberare controlată conform revendicării 1 .caracterizată prin aceea că cuprinde un miez din particule multiple, cuprinzând azitromicină și un material gonflabil și o o membrană în jurul fiecărui miez de particulă, în care membrana respectivă posedă pori prin care azitromicină și agentul gonflabil pot ieși sau în care membrana respectivă conține porogeni solubili în apă, care ies din membrană în mediul apos de utilizare, formând pori prin care pot ieși azitromicină și materialul gonflabil.
54
Compoziție cu eliberare controlată conform revendicării 1 sau 2, caracterizată prin aceea că este sub forma unei tablete acoperite cu două straturi, în care un strat al tabletei cuprinde o compoziție gonflabilă în apă și al doilea strat cuprinde o compoziție dispersabilă de azitromicină, tableta respectivă fiind acoperită cu o membrană permeabilă la apă, care este substanțial impermeabilă la azitromicină și care conține una sau mai multe perforații sau canale pentru expunerea compoziției conținând azitromicină la mediul de utilizare.
55
Compoziție cu eliberare controlată conform revendicării 2, caracterizată prin aceea că este sub forma unei tablete care conține o sare solubilă a azitromicinei, tableta respectivă având o acoperire permeabilă la apă, care este substanțial 2925 RO 114740 Bl impermeabilă la azitromicină și substanțial neapoasă, acea acoperire conține una sau mai multe perforații sau canale pentru expunerea interiorului tabletei la mediul de utilizare.
56
Compoziție cu eliberare controlată conform revendicării 1 sau 2, caracterizată prin aceea că este sub forma unei tablete acoperite .cuprinzând 2930 azitromicină, tableta respectivă având o acoperire poroasă care permite transportul atât al apei și al azitromicinei, prin acoperirea poroasă.
57
Compoziție cu eliberare controlată conform revendicării 1 sau 2, caracterizată prin aceea că este sub forma unei formulări de particulă multiplă acoperită, fiecare particulă cuprinzând azirtomicină și având o acoperire poroasă care permite 2935 transportul atât al apei și al azitromicinei, prin acoperirea poroasă.
58
Compoziție cu eliberare controlată conform revendicării 1, caracterizată prin aceea că este sub forma unei particule multiple, conținând particule acoperite cu o membrană care limitează viteza de eliberare θ azitromicinei prin difuzie a azitromicinei în tractul gastrointestinal. 2940
59
Compoziție cu eliberare controlată conform revendicării 1, caracterizată prin aceea că este sub forma unei tablete care conține o sare solubilă în apă a azitromicinei, tableta respectivă având o acoperire permeabilă la apă, care este substanțial impermeabilă la azitromicină și substanțial neapoasă și care conține una sau mai multe perforații sau canale pentru expunerea interiorului tabletei la mediul de 2945 utilizare.
60
Procedeu de preparare a compoziției cu eliberare controlată, caracterizată prin aceea că cuprinde etapele de:a) granulare a azitromicinei sub formă de masă de substanță medicamentoasă cu un liant, pentru a obține o granulare care are o dimensiune medie a particulei de 2950 la circa 50 la circa 300 m, b) acoperirea, practic imediat după aceea, a azitromicinei cu un material formator de membrană cu eliberare susținută, într-o cantitate de circa 5 la 30% din greutatea totală a produsului acoperit, c) acoperirea suplimentară după aceasta a produsului din etapa b] cu un 2955 polimer adițional,până când cantitatea totală de acoperire polimerică este de la circa 25% la circa 70% din greutatea totală a produsului acoperit.
61
Procedeu de preparare a compoziției cu eliberare controlată conform revendicării 60, caracterizată prin aceea că cuprinde etapa suplimentară de acoperire a produsului din etapa c], cu un polimer sensibil la pH, care este solubil la un 2960 pH 6, dar insolubil la un pH 4.
62
Procedeu de preparare a compoziției cu eliberare controlată conform revendicării 60, caracterizată prin aceea că polimerul cu acoperire susținută este etilceluloza și polimerul sensibil la pH este un copolimer al acidului metacrilic și al metacrilatilui sau ftalat acetat de celuloză. 2965
63
Metodă de tratament cu o compoziție cu eliberare controlată, carac- terizată prin aceea că poate fi administrată la mamifere,incluzând și omul, ca o compoziției cu eliberare controlată într-un dozaj al căror efecte eliberează azitromicina în tractul gastro-intestinal cu o astfel de viteză încât cantitatea totală de azitromicină eliberată acolo este:2970 nu mai mare de circa 200 mg de azitromicină pe kg al greutății în primele 15 min după ingerare, nu mai mare de circa 500 mg de azitromicină pe kg al greutății în prima oră după ingerare, RO 114740 Bl nu mai mare de 1000 mg pe kg al greutății în primele două ore după ingerare, nu mai mare de 2000 mg pe kg al greutății în primele patru ore după ingerare Ș· nu mai mare de circa 2000 mg de azitromicină pe kg al greutății în primele șase ore după ingerare.
64
Metodă de tratament conform revendicării 63, cu o incidență redusă a efectelor secundare gastro-intestinale față de o doză orală sub formă de bolus, caracterizată prin aceea că cuprinde dozarea unor forme de bol conținând azitromicină, așa cum a fost definită în revendicarea 1.
65
Metodă de tratament conform revendicării 62, cu o incidență redusă a efectelor secundare gastro-intestinale față de o doză orală sub formă de bolus, caracterizată prin aceea că cuprinde azitromicină, așa cum a fost definită în revendicarea 22.

Independent claims65

782 paragraphs in 1 section, as filed

The present invention relates to a controlled-release composition and to a process for preparing the dosage form and method of treatment, which consists of administering azithromycin in such a controlled-release dosage form to the mammal, including a human patient requiring a such treatment.

Azithromycin is the generic name (USAN) for 9a-aza-9a-methyl-9deoxo-9a-homoerithromycin A, a broad-spectrum antimicrobial compound derived from erythromycin A. Azithromycin has been independently discovered by Bright, US Patent 4474768 and by Kobrehel et al., U.S. Patent No. 4,517,359. These patents indicate that azithromycin and certain derivatives thereof have antimicrobial properties and are therefore useful as antibiotics.

It is well known that oral dosing of azithromycin can give rise, in some patients, to adverse gastrointestinal (Gl) side effects, such as cramps, nausea, diarrhea and vomiting. In the combined clinical trials of azithromycin, including 3995 patients (all combined dose levels), 9.6% of patients had gastrointestinal side effects. The most common of these side effects are diarrhea (3.6%), nausea (2.6%) and abdominal pain (2.5%) (Hopkins, Am. J.Med. 91 (supplement 3A) (1991) 40 S-45 S).

The incidence of gastrointestinal side effects is higher at higher doses than at lower doses. For example, a typical azithromycin therapy within 5 days consists of 500 mg on the first day, followed by 250 mg on days 2, 3, 4 and 5. For this therapy, the reported incidence of various effects Secondary gastrointestinal was: 5% diarrhea / soft stools, 3% nausea (Zitromax packed as capsules).

It is also known that azithromycin can cause gastrointestinal side effects in non-human mammals, such as dogs.

An improved dosage form of azithromycin which allowed oral dosing of a higher dose of azithromycin (eg, 2 g), with relatively small side effects, would allow for the broader application of a single dose azithromycin therapy and would therefore provide a significant improvement in the acceptability and suitability of the dosage. Similarly, an improved dosage form that reduced the incidence of gastrointestinal side effects at lower doses would also be of significant value.

This invention provides a controlled-release dosage form of azithromycin, which reduces the incidence and / or severity of gastrointestinal side effects, as compared to the current-marketed dosage forms of immediate-release azithromycin capsule. The dosage form can be exploited by delivering azithromycin at a rate sufficiently low to ameliorate side effects. The dosage form can also be exploited by releasing most azithromycin contained in the portion of the Gl tract distal to the duodenum. Specific embodiments may be in the form of a sustained-release oral dosage form or, alternatively, in the form of a delayed-release oral dosage form or, alternatively, in the form of an oral dosage form having a combination of sustained release and delayed release. The term "controlled" is generic for the term "sustained" and "delayed". Dosage forms that release more than 70% of their azithromycin content in an hour and a half or less are not "controlled releases" and these forms are not part of the present invention.

In a specific aspect, the present invention provides a sustained-release dosage form, comprising azithromycin and a pharmaceutically acceptable carrier,

RO 114740 Bl which, after ingestion by a mammal in need of such treatment, 50 releases azithromycin into the gastrointestinal tract of said mammal at such a rate that the total amount of azithromycin released here is not more than about 4 mg of azithromycin per kg mammal weight in the first 15 min after ingestion, greater than about 10 mg azithromycin per kg mammal weight in the first hour after ingestion, greater than about 20 mg of azithromycin per kg of mammal weight, within the first 55 hours after ingestion, greater than about 30 mg of azithromycin per kg of mammal, within the first four hours after ingestion and not more than about 40 mg of azithromycin per kg of mammal weight in the first six hours after ingestion.

The above criteria are presented as "weight criteria".

In a further specific aspect, the invention provides a delayed-release dosage form of azithromycin, comprising azithromycin and a pharmaceutically acceptable carrier, which does not release more than about 10% of the erythromycin incorporated into the stomach and releases no more than an additional 10% during the first 15 minutes after the dosage form has entered the duodenum. Once it has entered the duodenum and moved to the distal side through and through this 65 segment of the intestine for at least 15 minutes, the rate at which the dosage form releases azithromycin is not critical as long as substantially all azithromycin is released here for absorption instead of being excreted.

In a further specific aspect, the present invention relates to a sustained release dosage form, comprising azithromycin and a pharmaceutically acceptable carrier, which releases a total amount of azithromycin at the following rate, after ingestion by a mammal: not more than about 200 mg of total azithromycin in the first 15 minutes after ingestion, not more than about 500 mg of total azithromycin in the first hour after ingestion, not more than 1000 mg of total azithromycin in the first two hours after ingestion, high of 1500 mg of total azithromycin 75 in the first four hours after ingestion and no more than 2000 mg of total azithromycin in the first six hours after ingestion. The preceding criteria referred to here are "time criteria". Release rates of azithromycin lower than the speed just described are also within the scope of the invention and may produce better side effects profiles, in particular for patients under 50 kg, such as 80 children. Thus, a release rate of azithromycin (each amount representing the total amount released (eg cumulative)), for example less than 200 mg in the first 15 minutes after ingestion, less than 400 mg in the first hour after ingestion, less than 750 mg in the first two hours after ingestion, less than 1250 mg in the first four hours after ingestion and less than 1500 mg in the first six hours after ingestion, represents a release profile in the field of the invention and may be even more effective for ameliorating side effects. Once six hours have elapsed since ingestion, the rate at which the dosage form releases azithromycin (for example, if the dosage form contains more than 2 g azithromycin at first) is not critical.

The velocity must, of course, be sufficiently high to produce therapeutic efficacy, 90 which is therapeutically sufficient amount of azithromycin to be released from the dosage form before the dosage form is excreted with the faeces.

For example, FIG. 1 presents the hypothetical release profiles 3 and 4 for a dosage form that is within the scope of the invention. Profile 1 in thick bold steps defines in fact the release profile of the temporal criterion. Profile 2 represents 95 a hypothetical release profile outside the scope of the invention.

It should be noted that although the time criterion and the weight criterion define a release profile that extends over a period of six hours, a dosage form

In accordance with the invention it can essentially release all its azithromycin before six hours, as long as it is otherwise suited to the defined speeds. The dosage forms according to the invention which contain relatively low amounts of azithromycin (for example, less than 1000 mg) can essentially release all of their azithromycin within a few hours.

The term "ingestion" as used here is essentially synonymous with "swallowing".

The invention is particularly useful for administering relatively large amounts of azithromycin to a patient. The amount of azithromycin contained in the dosage form is preferably at least 1 g and may be as large as or greater than 7 g. The amount contained in the dosage form is preferably 1.5 to 4 g, more preferably 1, 5 to 3 g. The dosage form may be unitary as in the case of a bowl or divided, for example, consisting of two or more units (such as capsules or tablets), which are taken at or about the same time. Azithromycin can be used in dosage forms according to the invention, in the form of its pharmaceutically acceptable salts and also in anhydrous or hydrated form. All such forms are within the scope of this invention. The azithromycin used is preferred as dihydrate, described for example in European Patent Application Publication 0298650 A2. The reference to "azithromycin" in terms of therapeutic quantities or release rates within the claims refers to the active azithromycin and not to the salt molecule or macrolide hydrate molecules, having molecular weight 749.

The dosage forms that are the subject of the invention are, as mentioned, controlled release formulations.

In the case of embodiments of sustained release formulations, the dosage form may be in the form of a tablet, capsule, multiple particle form, or single dose package (sometimes referred to in the art as "envelope"). ).

The term "tablet" is intended to include compressed tablets, coated tablets, matrix tablets, osmotic tablets and other forms known in the art, as described more comprehensively below.

The term "capsule" is intended to encompass capsules in which the capsule body disintegrates upon ingestion, to release the content of particles exhibiting the desired sustained release behavior, and also encompasses capsules for which the capsule body remains substantially intact during stay. the Gl tract.

The term "multiple particles" is intended to encompass a dosage form comprising a plurality of particles which, in total, represents the dose of azithromycin that is therapeutically useful. Generally, the particles are in diameter from about 50 microns to about 0.3 cm, with a preferred range from 100 microns to 1 mm. The use of these terms and other terms is better specified below. The multiple particle shape is a preferred embodiment for sustained release, because they are responsible for use in staggered dosage forms or according to the weight of an individual animal (eg, a horse), according to the weight criterion indicated above, by simply staggering of the number of particles in the dosage form, to be consistent with the weight of the animal.

In a further aspect, the present invention provides a process for preparing sustained-release dosage forms of azithromycin, which comprises granulating steps of the majority substance, azithromycin, with a binder, essentially immediately after coating the granulate with a polymer coating, with controlled permeability to azithromycin, and thereafter additional coating of the granulate

EN 114740 Bl mentioned with an additional polymer with controlled permeability for azithromycin, until sufficient polymer was applied to achieve the desired sustained release rate or profile.

In a further aspect, the present invention relates to a method for treating a microbial infection in a mammal requiring such treatment, including a human patient, of a therapeutically effective amount of azithromycin in a controlled-release oral dosage form. , which release azithromycin according to the release rate described above.

In the case of the delayed release embodiment, the dosage form may be in the form of a tablet, capsule, multiple particles, suspension, or envelope, provided that the dosage form releases most of its azithromycin in the gastrointestinal tract region distal to the duodenum .

□ Variety of variations of dosage forms and / or structures can be used to achieve this objective, as described in detail below. Multiple particle dosage forms, beads or other particle dosage forms, may be introduced in large numbers into a gelatin capsule or may be compressed into a tablet.

It is an object of this invention to describe the incidence and severity of azithromycin-induced Gl side effects. This is especially important at high doses, for example 2 g and above, where the incidence of gastrointestinal side effects may be relatively high. This objective is achieved by minimizing the exposure of the duodenum to azithromycin, at least in a portion, of patients treated with azithromycin, thereby reducing the incidence and overall severity of gastrointestinal side effects induced by azithromycin.

The inventors carried out a series of human studies, in which the incidence and severity of gastrointestinal side effects were evaluated after dosing of intravenous, oral, duodenal azithromycin (by nasoenteric intubation) and ileal (by nasoenteric intubation). Studies have shown that the incidence of gastrointestinal side effects is relatively low after intravenous dosing, even at doses that are equivalent to an oral dose of 5.4 g. Thus, without the desire to be limited, by or to any theory or mechanism, the gastrointestinal side effects of oral dosing with azithromycin appear to be mediated by local interactions between azithromycin and the intestinal wall. In addition, nasoenteric intubation studies have shown that duodenal dosing of azithromycin results in more severe gastrointestinal side effects than ileal dosing. Accordingly, the inventors determined that dosing azithromycin in a manner that reduces the exposure of the duodenum to high concentrations of the drug leads to a decrease in gastrointestinal side effects.

Oral dosing of azithromycin in conventional capsules, with uncontrolled release, leads to relatively prolonged exposure of the drug to the duodenum. Dosage of azithromycin in conventional enteric dosage forms, which prevent significant drug dissolution in the stomach, may also expose the duodenum to a large proportion of the azithromycin dose.

Another object of the invention is to provide dosage forms which deliver therapeutic doses of azithromycin, while reducing localized exposure of azithromycin along the Gl tract, especially in the duodenum, contributes to the decrease of gastrointestinal side effects.

It is to be noted that controlled release dosage forms of different types are conventionally known and used in the art, to ensure the reduced dosing frequency for short half-life compounds and to

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RO 114740 Bl reduces fluctuations in plasma concentration, sometimes resulting in an improved safety / efficiency profile. Because the elimination of azithromycin from the human body is characterized by a half-life of approximately 69 hours, it is surprising, however, that a controlled-release dosage form (either sustained or delayed) will provide some benefit.

Fig. 1 is a graphical illustration of a broad release profile, as defined by the temporal criterion (profile 1), of certain hypothetical azithromycin release profiles, according to the present invention (profiles 3 and 4) and of a hypothetical release profile. outside the scope of the invention, (profile 2).

For the purpose of this application, different variants of the "controlled release dosage forms of azithromycin" as sustained release variants "and as delayed release variants" have been described for ease of description. Without the intention of limitation, the dosage forms of azithromycin are those that readily release azithromycin.

Delayed azithromycin dosage forms are those that release little azithromycin or do not release azithromycin for a predetermined period of time, then release azithromycin rapidly or in a sustained manner. It will be appreciated by those skilled in the art that certain "sustained release" variants will be included under the general "delayed release" variant and vice versa. For example, sustained release osmotic pumps generally have a "delay time" after ingestion, during which time the osmotic pressure in the pumping device is increased and during which time little or no drug is released. Thus, an osmotic pumping device for azithromycin can be considered both a sustained release and a delayed release device. Variants of the present invention include all azithromycin controlled-release dosage forms encountered in one or both of the in vitro assays described herein for a "sustained-release dosage form" or a "delayed-release dosage form". The sustained release dosage forms of the present invention can be widely implemented. To achieve the objective of the discussion, without limitation, many variants below can be grouped into classes according to the model or operating principle.

□ First class includes matrix systems, in which azithromycin is introduced or dispersed in a matrix of another material that causes delay in the release of azithromycin in an aqueous medium (eg lumenal fluid in the Gl tract). When azithromycin is dispersed in a matrix of this type, drug delivery occurs mainly from the surface of the matrix. Thus, the drug is released from the surface of a device incorporating the matrix or when the surface of the device is eroded, exposing the drug. In some embodiments, both mechanisms can be exploited simultaneously. Matrix systems can be large, for example, tablets sized (about 1 cm) or small (less than 0.3 cm). The system may be unitary (eg, a bowl), may be divided (as discussed above) due to the fact that it is composed of different subunits (eg, different capsules constituting a single dose), which are administered substantially simultaneously or may comprise a plurality of particles, herein referred to as multiple particles A multiple particle dosage form may have numerous formulation applications. For example, a multi-particle dosage form may be used as a powder for filling a capsule shell or used as such for mixing with foods (eg ice cream) to enhance the taste.

The size of the matrix system may affect the release of azithromycin

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250 that a large matrix system, such as a tablet, generally has a different composition from a small one, such as a multiple particle shape. The effects of the size of the matrix system on the kinetics of azithromycin release follow a well-known staggered behavior in the study of diffusion. By way of illustration, the following table shows the diffusion coefficient of azithromycin required to achieve a characteristic release time of 10 h for matrix systems of different sizes.

Radius (cm) □, 0025 (50 / zm diameter) 0.1 (2 mm diameter)

0.5 (1 cm diameter)

Diffusion coefficient (cm2/ s) 1.7 x 1O10 3 x 1O '10 x 1O6

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The table above illustrates that, the diffusion coefficients change their order of size according to the desired size of the device. The high and low values represent the upper and lower limits for matrix devices. Thus, materials with a diffusion coefficient less than about 1010 are unsuitable for this invention, being almost completely impermeable to azithromycin. Materials with a diffusion coefficient greater than about 7 x 106 are also unsuitable for this invention, being a device for immediate release or for rapid release. The materials at the low end of the diffusion coefficient scale are polymers, such as cellulose acetate. Accordingly, the materials at the upper end of the diffusion coefficient scale are materials such as hydrogels. The diffusion speed for any particular device can be made according to the material or materials selected.

In the same manner, but in generally different terms, the sustained release devices of this invention should be implemented for the release of azithromycin contained within them over a period of up to 6 hours and possibly longer. The device can be properly designed according to the equation RT = 12/ D, where RT is responsible for the total dose release time contained in the device, r represents the radius of the device and D refers to the diffusion coefficient of azithromycin in the matrix material. The equation illustrates that the appropriate dosage forms can be designed as a counterpart exchange between the device dimensions and the diffusion coefficient of the matrix material. If a spherical dosage form will not be used, then it will be replaced by other suitable dimensions known in the art, such as 1/2 from the side of a cube, the short axis for an ellipsoid and the like.

For the purpose of further illustration, to obtain a sustained release matrix in a particle about 5D μίτι in diameter, a matrix material, of a polymer such as cellulose acetate or a material thereof, will be required. slow diffusing matrix material tending to balance the tendency of small particles to diffuse rapidly. By contrast, in order to achieve sustained release in a large device (for example 1 cm), a material that is usually liquid (such as a hydrogel, see below) will be required. For devices with intermediate dimensions, for example about 1 mm in diameter, a matrix material with intermediate characteristics can be used.

It is also to be noted that the effective diffusion coefficient of azithromycin in a dense material can be increased to a desired value by adding plasticizers, pores or additives including pores, as known in the art. Slowly hydrating materials can also be used to give diffusion rates

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335 desired intermediaries. The multitude of variables that affect the release of azithromycin from matrix devices allows for greater flexibility of device models from different materials, dimensions and release times. Examples of modification of azithromycin release profiles from specific embodiments of the examples in the field of the invention are described in detail below.

A preferred embodiment, a multiple particle matrix, comprises a plurality of particles containing azithromycin, each particle comprising a mixture of azithromycin with one or more excipients, selected to form a matrix capable of limiting the rate of dissolution of azithromycin in an aqueous environment. The matrix materials useful in this embodiment are generally water insoluble materials such as waxes, cellulose and other water insoluble polymers. If desired, the matrix materials may optionally be formulated with water-soluble materials which may be used as binders or as permeability altering agents. The matrix materials useful for making these dosage forms include microcrystalline cellulose, such as Avicel (Trademark FMC Corp., Philadelphia, PA), including qualities of microcrystalline cellulose, to which binders were added, such as hydroxypropylmethyl cellulose, waxes, such as paraffin, modified vegetable oils, carnauba wax, castor oil, beeswax and the like and, to the same extent, synthetic polymers, such as vinyl polychloride, vinyl polyacetate, vinyl acetate and ethylene copolymers, polystyrene and the like. Water-soluble binders or release-modifying agents, which can be optionally formulated in a matrix that includes water-soluble polymers, such as hydroxypropyl cellulose (HPC), hydroxypropylmethylcellulose (HPMC), methylcellulose.po ^ (N-vinyl2-pyrrolidinone (PVP) ), polyethylene oxide (PEO), polyvinyl alcohol (PVA), xanthan gum, carrageenan and other such natural and synthetic materials. In addition, materials that act as release-modifying agents include water-soluble materials, such as sugars or salts. Preferred water soluble materials include lactose, sucrose, glucose and mannitol and in the same HPC, HPMC and PVP.

A preferred process for making multiple particle matrices is an extrusion / spheronization process. For this process, azithromycin is wet agglomerated with a binder, extruded through a perforated plate or mold and placed on a rotating disk. The ideal extrudate breaks into pieces that are shaped into spheres, spheroids or round rods on the rotary plate. A preferred process and compositions for this method involve the use of water to wet agglomerate a mixture comprising about 20 to 75% microcrystalline cellulose, suitably mixed with about 80 to 25% azithromycin.

An additional preferred process for the preparation of multi-particle matrices is the preparation of wax granules. In this process, a desired amount of azithromycin is stirred with liquid wax to form a homogeneous mixture, cooled and then forced to pass through a sieve to form the granules. Preferred matrix materials are waxy substances. Particularly preferred are hydrogenated castor oil and carnauba wax and stearyl alcohol.

An additional preferred method for making the multi-particle matrix involves the use of an organic solvent, to help mix azithromycin with the matrix material. This technique can be used when it is desired to use a matrix material with a high melting point, which is not usable, which, if the material was used in a melt state, will cause the drug or matrix material to decompose or will lead. at an unacceptable melt viscosity, thereby preventing the mixing of azithromycin with the matrix material. Azithromycin and matrix material can be combined with an amount

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345 modest solvent, to form a paste and then forced through a sieve to form granules from which the solvent is then removed. Alternatively, azithromycin and matrix material may be combined with enough solvent to completely dissolve the matrix material, and the resulting spray solution (which may contain solid drug particles) was dried to form the particulate dosage form. This technique is preferred when the matrix material is a high molecular weight synthetic polymer, such as a cellulose ether or cellulose ester. Typical solvents used in the process include acetone, ethanol, isopropanol, ethyl acetate and mixtures of two or more.

Once formed, multiple azithromycin particles in the matrix may be mixed with compressible excipients, such as lactose, microcrystalline cellulose, dicalcium phosphate and the like, and the mixture compressed to form tablets. Disintegrating, such as sodium starch glycolate or branched polyvinylpyrrolidone, are also used. The tablets prepared by this method disintegrate when placed in an aqueous medium (such as the Gl tract), thereby exposing the multiple particle matrix that releases azithromycin from it.

An additional embodiment of a matrix system is in the form of a hydrophilic matrix tablet containing azithromycin and an amount of a hydrophilic polymer, sufficient to provide a useful degree of control over the dissolution of azithromycin. The hydrophilic polymers used for matrix formation include hydroxypropylmethyl cellulose (HPCM), hydroxypropyl cellulose (HPC), polyethylene oxide, polyvinyl alcohol, xanthan gum, carbomer, carrageenan and zooglane. A preferred material is HPCM. Other similar hydrophilic polymers can also be used. When used, the hydrophilic material is swollen and eventually dissolved in water. Azithromycin is released both by diffusion from the matrix and by erosion of the matrix. The rate of dissolution of azithromycin from these hydrophilic matrix tablets can be controlled by the amount and molecular weight of the hydrophilic polymer used. In general, the use of a larger amount of polymer decreases the rate of dissolution, as achieved, using a polymer of higher molecular weight. The use of a polymer with a lower molecular weight increases the dissolution rate. The rate of dissolution can also be controlled by the use of water-soluble additives such as sugars, salts or soluble polymers. Examples of such additives are sugars, such as lactose, sucrose or mannitol, salts, such as NaCl, CaCl, NaHCO3 and water soluble polymers such as PNVP or PVP, HPC or HPMC or low molecular weight methylcellulose. In general, increasing the fraction of soluble material in the formulation increases the release rate. A tablet with characteristic matrix comprises approx. 20 to 90% by weight azithromycin and approx. 80 to 10% by weight of polymer.

A preferred tablet, with matrix, weighs approx. 50% to about 80% azithromycin, approx. 15 c. 35% HPMC, 0% c. 35% lactose, 0% c. 15% PVP, 0% at about 20% microcrystalline cellulose and about 0.25% at about 2% magnesium stearate.

Systems as a class often have inconsistent drug delivery from the matrix. This result may be a consequence of the drug delivery diffusion mechanism and changes in dosage form may be used to encourage the drug delivery rate to be more consistent, as detailed below.

In a further embodiment, a matrix azithromycin tablet is coated with an impermeable coating and is provided with an orifice (eg, a circular cavity or a rectangular opening), through which the tablet contents are exposed to the aqueous Gl tract. These variants are in line with those presented in

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US 4792448 by Ranade, incorporated herein by reference. The opening is typically of such a size that the surface of the exposed base azithromycin composition constitutes less than about 40% of the surface area of the device, preferably smaller than about. 15%.

In a preferred embodiment, an azithromycin matrix tablet is coated with an impermeable material on the side of its surface, for example on one or both sides of the tablet or on the radial surface of the tablet.

In a preferred embodiment, an azithromycin matrix tablet is coated with a waterproof material and is provided with an opening for transporting the drug, produced by drilling a hole through the coating. The orifice may be covered only or may be expanded as a passageway into the tablet.

In a further preferred embodiment, an azithromycin matrix tablet is coated with an impermeable material and with a drug delivery pathway produced by drilling an entire tablet passageway.

In a further preferred embodiment, an azithromycin matrix tablet is coated with an impermeable material and one or more drug delivery pathways are produced by removing one or more strips from the impermeable coating or by cutting one or more cover grooves, preferably on the radial surface or along the perimeter of the tablet.

In a preferred embodiment, an azithromycin matrix tablet is processed as a cone and coated completely with a waterproof material. A passageway for drug transport is produced by separating the type of cone.

In a further preferred embodiment, an azithromycin matrix tablet is processed as a hemisphere and completely coated with a waterproof material. A passageway for drug transport is produced by drilling a hole in the center or flat face of the hemisphere.

In a further preferred embodiment, an azithromycin matrix tablet is processed as a semi-cylinder and completely coated with a waterproof material. A passageway for the transport of the drug is produced by cutting a groove through (or removing a strip) from the impermeable coating along the semicylinder axis along the center line of the flat face of the semicylinder.

Those skilled in the art will appreciate that the geometrical modifications of the variants described above can be produced equivalently by more than one method. For example, cutting or drilling to draw a bypass for the transport of the drug can be accomplished by other operations, such as a technique that directly produces the desired partial coverage.

"Waterproof material" means a material that has sufficient thickness and impermeability to azithromycin so that no significant transport of azithromycin occurs through the material at the desired drug delivery time scale (eg 7 hours a day ). Thus, a coating can be obtained by selecting a coating with a diffusion coefficient small enough for azithromycin and the application is sufficiently thin.

The materials for forming the impermeable coatings of these variants include substantially all materials in which the diffusion coefficient of azithromycin is less than approx. 1D+7 cm2/ S. It is to be noted, that, the previous diffusion coefficient can be sufficiently amplified for a matrix device as discussed above. in a device of the type now being discussed, which was provided with a macroscopic opening, however, a material with this coefficient of

RO 114740 Bl

445 diffusion (and almost any non-liquid membrane material) is exposed to contained azithromycin, by contrast, although it is impermeable, because most of the transport is by opening. Preferred coatings include polymers that form films and waxes. Particularly preferred are thermoplastic polymers, such as ethylene-vinyl acetate copolymer, vinyl polychloride and cellulose acetate. These materials show the penetration rate of azithromycin, low when applied in coatings of thicknesses greater than approx. 100 gm.

An additional sustained release matrix system comprises azithromycin dispersed in a hydrogel matrix. This variant differs from the hydrophilic matrix tablet discussed above, in that the hydrogel in this variant is not a tablet compressed with erodible granular material, but even a monolithic polymer network. As is known in the art, a hydrogel is a polymer with an inflatable network in water. Hydrogels are preferable materials for matrix devices, because they absorb or are made to contain a large volumetric percentage of water, thereby allowing diffusion of the solvated drug into the matrix. The diffusion coefficients of the drug in the hydrogels are typically high and for the gels with high water swelling, the diffusion coefficient of the drug in the gel can be close to the value in pure water. This diffusion coefficient allows practical release rates from relatively large devices (for example, it is not necessary to form microparticles). Although hydrogel devices can be prepared, filled with azithromycin, stored, dispensed and dosed in a completely hydrated state. It is preferable that they be stored, dispensed and dosed in a dry state. With regard to stability and convenience, the dry metering of the hydrogel devices ensures a good kinetics of azithromycin release. Preferred materials for hydrogel formation include vinyl and acrylic hydrophilic polymers, polysaccharides, such as calcium alginate and polyethylene oxide. Particularly preferred are 2-hydroxyethyl polymethacrylate, polyacrylic acid, polymethacrylic acid, poly (N-vinyl-2-pyrrolidinone), polyvinyl alcohol and their copolymers and with hydrophobic monomers such as methyl methacrylate, vinyl acetate and the like. Also preferred are hydrophilic polyurethanes containing polyethylene oxide blockopolymers. Other preferred materials include hydrogels comprising interlocking polymer networks, which may be formed by polymerization, addition or condensation, components which may comprise hydrophilic and hydrophobic monomers, such as those already listed.

□ A secondary class of azithromycin sustained release dosage forms of this invention include moderate membrane systems or reservoir systems. In this class, an azithromycin reservoir is surrounded by a speed limiting membrane. Azithromycin crosses the membrane through the mass transport mechanism well known in the art, which includes, but does not limit, dissolution in the membrane, followed by diffusion through the membrane or diffusion through pores filled with membrane fluid. These dosage forms in the individual reservoir system may be wide, as in the case of a tablet containing a single large reservoir, or may be of multiple particles, as in the case of a tablet containing a plurality of reservoir particles, each coated in a manner individually with a membrane. The coating may be porous, still permeable to azithromycin (for example, azithromycin may diffuse directly through the membrane) or may be porous. As in other embodiments of the present invention, the particular mechanism of the invention is not believed to be critical.

Sustained release coating, as known in the art, can be used to manufacture membranes, in particular polymeric coatings, such as cellulose ester or ether, acrylic polymer or polymer mixture. materials

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Preferred include ethyl cellulose, cellulose acetate and cellulose butyrate acetate. The polymer can be applied as a solution in an organic solvent or an aqueous dispersion or latex. The roofing operation can be carried out in standard equipment, such as a fluidized bedding machine, a Wurster type coating machine or a rotating bed coating machine.

If desired, the permeability of the coating may be corrected by mixing two or more materials. A process particularly useful for realizing the porosity of the coating comprises the addition of a predetermined amount of a finely divided water-soluble material, such as sugars or salts or water-soluble polymers to a solution or dispersion (eg, an aqueous latex) of the membrane-forming polymer. what's going on. When the dosage form is ingested in an aqueous medium of the Gl tract, these water-soluble membrane additives are extracted out of the membrane, leaving pores that facilitate drug delivery. The membrane coating can also be modified by the addition of plasticizers, as is known in the art.

Q A particularly useful variation of the process for applying a membrane coating comprises dissolving the coating polymer in a mixture of solvents, chosen so that the coating dries, a phase inversion occurs in the applied coating solution, resulting in a membrane with a porous structure. Numerous examples of this type of coating system are given in European Patent Specification 0357369 Bl published March 7, 1990, incorporated herein by reference. In general, a support for mechanical membrane strengthening is not required.

The morphology of the membrane is not of critical importance as long as the permeability characteristics listed here are met. The membrane can have any category of morphology produced by a particular process and can be, for example, an interfacial polymerized membrane (comprising a thin film that limits the velocity, disposed on a porous support), a hydrophobic porous membrane, a hydrophilic porous membrane , a hydrogel membrane, an ionic membrane and other such materials which are characterized by controlled permeability to azithromycin.

A variant of a useful reservoir system is a capsule having a coating comprising the rate limiting membrane material, including any of the membrane materials discussed above and filled with an azithromycin drug composition. A particular advantage of this configuration is that the capsule can be prepared independently from a drug composition, so that the process conditions, which could adversely affect the drug, can be used to prepare the capsule. A preferred embodiment is a capsule having a coating made of a porous or permeable polymer, made by a heat forming process. A particularly preferred embodiment is a capsule shell in the form of an asymmetrical membrane; for example, a membrane that has a thin film on a surface and whose thickness is mostly made of a high permeable porous material. A preferred process for preparing an asymmetrical membrane capsule comprises a solvent change phase reversal, wherein a polymer solution covering a capsule-shaped mold is determined to separate the phases by changing the solvent with a miscible solvent. Examples of asymmetrical membranes useful in this invention are described in European Patent Specification 0357369 B1 mentioned above.

A preferred embodiment of the class of reservoir systems comprises a multiple particle system, wherein each particle is coated with a designated polymer.

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540 to achieve sustained release of azithromycin. Each particle with multiple particles contains azithromycin and one or more excipients necessary for manufacturing and performance. The size of the individual particles, as mentioned above, is generally between about 50 gm and about 3 mm, although granules with a size outside this range may also be useful. Generally, the granules contain azithromycin and one or more binders. As it is generally desirable to produce dosage forms, those which are small and easily inflated are preferred, the beads containing a fraction of azithromycin over excipients. Binders useful in the manufacture of these granules include microcrystalline cellulose (e.g. Avicel(R), FMC Corp.), hydroxypropyl cellulose (HPC), hydroxypropyl methyl cellulose (HPMC) and related materials or combinations thereof. In general, binders that are useful in granulation and tableting, such as starch, pregelatinized starch and poly (N-vinyl-2-pyrrolidinone) (PVP) can also be used to form multiple particles.

The azithromycin multiple particle reservoir system can be prepared using techniques known to those skilled in the art, which include, but are not limited to, wet granulation extrusion and spheronization, fluid bed granulation and rotary bed granulation. In addition, the granules may also be prepared by building the azithromycin (drug plus excipient) composition on a germ core (such as a non-apparent germ), by a drug layering technique, such as powder coating or by applying the azithromycin composition by spraying a solution or dispersing azithromycin in a suitable binder solution in a sowing core in a fluidized bed, such as a Wurster coating device or a rotary processor. An example of a suitable composition and method is spraying a dispersion of an azithromycin / hydroxypropyl cellulose composition in water. Advantageously, azithromycin may be filled in the composition above its water solubility limit.

A preferred process for the preparation of multiple particle cores of this variant is the extrusion / spheronization process, as discussed above for the multiple particle matrix. A preferred process and composition for this method involves the use of water in the wet mass of the mixture of about 5 to 75% microcrystalline cellulose, suitably, with 95 to 25% azithromycin. Particularly preferred is the use of about 5 to 30% microcrystalline cellulose, corresponding to about 95 to 70% azithromycin.

□ sustained release coating, as known in the art, especially polymeric coatings can be used to manufacture membranes, as discussed previously for reservoir systems. Polymeric coating materials, suitable and preferred coating equipment and methods also include those discussed above.

The rate of release of azithromycin from multiple coated particles can also be controlled by such factors as the content of the composition and the binder content of the drug-containing core, the thickness and permeability of the coating, and the surface to volume ratio of the multiple particles. It will be appreciated by those skilled in the art that increasing the coating will decrease the release rate, while increasing the permeability of the coating or the volume surface ratio of the multiple particles will increase the release rate. If desired, the permeability of the coating may be corrected by mixing two or more materials. 0 Useful coatings include mixtures of water-insoluble polymers and water-soluble polymers, for example ethyl cellulose and hydroxypropylmethyl cellulose, respectively. A particularly useful modification of the coating is the addition of a finely divided water soluble material such as sugars and salts. When placed in one

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EN 114740 In aqueous medium, these water-soluble membrane additives are removed from the membrane, remaining pores that facilitate drug delivery. The membrane type coating may also be modified by the addition of plasticizers, as known to those skilled in the art. A particularly useful variant of membrane coating uses a mixture of solvents so chosen that the coating dries, a phase inversion occurs in the applied coating solution, resulting in a membrane with a porous structure.

A preferred embodiment is a multiple particle comprising about 95% azithromycin, the individual particles being coated with an aqueous dispersion of ethyl cellulose which is dried to form a continuous film.

□ A further preferred embodiment is obtained when the azithromycin granules are smaller than 400 μητι in size and are coated with an aqueous dispersion of ethyl cellulose, which is dried to form a continuous film.

An even more preferred embodiment is obtained when the granules are smaller than 300 / zm and are coated with an aqueous dispersion of ethyl cellulose which dries to form a continuous film.

A third class of release dosage forms supported by azithromycin includes osmotic delivery devices or "osmotic pumps", as known in the art. The osmotic pumps comprise a core that contains an osmotically effective composition, surrounded by a semipermeable membrane. The term "semipermeable" in this context means that water can pass through the membrane, but solutions dissolved in water cannot pass through the membrane.

In use, when placed in an aqueous environment, the device soaks water due to the osmotic activity of the core composition. Due to the semipermeable nature of the surrounding membrane, the contents of the device (including the drug and any excipients) cannot pass through the nonporous region of the membrane and are guided by osmotic pressure to leave the device through an opening or a preconfused passageway in the dosage form or alternatively formed in situate in the Gl tract by cracking the weak spots of the coating intentionally incorporated under the influence of osmotic pressure. The osmotically effective composition includes water-soluble species that generate colloidal osmotic pressure and water-inflatable polymers. The drug itself (if highly soluble in water) can be an effective osmotic component of the mixture. Azithromycin fumarate has a solubility at pH 7 of about 100 mg / ml, corresponding to an osmotic pressure of about 3 at, sufficient to contribute to a strong osmotic force. However, the solubility of azithromycin dihydrate in an acute-buffered solution (pH> 8] is much lower. Therefore, the osmotic efficiency of azithromycin depends on the presence of acid buffers in the formulation. The composition of the drug can be separated from the osmotic-efficient components by mobile or piston separation.

Materials useful for forming the semipermeable membrane include polyamides, polyesters and cellulose derivatives. Preferred are cellulose ethers and esters. Particularly preferred are cellulose acetate, cellulose acetate butyl ether and cellulose. Particularly useful materials include those that spontaneously form one or more exit pathways, either during preparation or when placed in the environment of use. These preferred materials comprise porous polymers whose pores are formed by phase inversion during preparation, as described above, or by dissolving a water-soluble component present in the membrane.

□ class of materials that have particular utility for forming semipermeable membranes for use in osmotic release devices is

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640 that of the porous hydrophobic polymers described as in the US Patent Application during examination Series No. 08/096, registered July 22, 1993, incorporated herein by reference. These materials are highly permeable to water, but impervious to water-dissolved solutions. These materials owe their high water permeability to the presence of numerous microscopic pores (for example, pores that are larger than the molecular dimensions). despite their porosity, these materials are impermeable to molecules in aqueous solution due to the fact that the liquid water does not water the pores. The vapor phase water is able to easily cross the membranes made of these materials.

preferred embodiment of this class of osmotic release devices of a two-layer coating tablet. The coating of such a tablet comprises a water-permeable membrane, but essentially impermeable to azithromycin and the excipients contained therein. The coating contains one or more exit pathways in connection with the azithromycin-containing layer for drug delivery. The core of the tablet consists of two layers: one layer containing the azithromycin composition and another layer consisting of an expandable hydrogel! with or without additional osmotic agents.

When placed in an aqueous medium, the tablet is soaked with water through the membrane, causing the azithromycin composition to form a dispersible aqueous composition, and causing the hydrogel layer to expand and push the azithromycin composition to exit through the exit ring.

The rate of release of azithromycin is also controlled by factors such as permeability and thickness of the coating, water activity in the hydrogel layer and the surface area of the device. Those skilled in the art will appreciate that increasing the thickness of the coating will reduce the release rate, while increasing the permeability of the coating or the water activity of the hydrogel layer or the surface area of the device will increase the release rate.

Representative materials that are used to form the azithromycin composition in addition to azithromycin include hydroxypropylmethyl cellulose, polyethylene oxide, poly (N-vinyl-2-pyrrolidinone) or PVP and other pharmaceutically acceptable carriers. In addition, osmotic agents, such as sugars or salts, in particular sucrose, mannitol or sodium chloride may be added. Materials that are useful for forming the hydrogel layer include sodium carboxymethylcellulose, polyethylene oxide, polyacrylic acid, sodium polyacrylate and other high molecular weight hydrophilic materials. Particularly useful are polyethylene oxides having a molecular weight of from about 40,000 to about 75,000,000 and sodium carboxymethylcellulose having a molecular weight of about 200,000 to about 10,000,000.

Materials that are useful for coating formation are cellulose esters, cellulose ethers and cellulose esters. Preferred are cellulose acetate and ethyl cellulose.

The exit pathway can be located on the side of the tablet containing the azithromycin composition. There may be several such exit routes. The output path may be produced by mechanical drilling or laser drilling or by creating a region difficult to cover on the tablet by using a special chip during tablet compression. The rate of release of azithromycin from the device can be optimized so as to provide a method of delivering azithromycin to a mammal for optimal therapeutic effect.

The fourth class of azithromycin sustained release dosage forms according to the invention comprises coated hydrogel tablets and multiple particles, such as

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RO 114740 Bl has been described in US Patent Application Serial No.07 / 296464 filed January 12, 1989 (published as EP 378404 B1 August 31, 1994), incorporated herein by reference. The coated hydrogel tablets comprise a core of the tablet containing azithromycin and a bulging material, preferably a membrane-coated hydrogel polymer containing holes or pores through which, in the aqueous use medium, the hydrogel may carry out azithromycin. Alternatively, the membrane may contain polymeric water-soluble porogens or low-molecular-weight porogens that dissolve in the aqueous media, producing pores through which the hydrogel and azithromycin may extrude. Examples of porogens are water soluble polymers such as hydroxypropylmethyl cellulose and low molecular weight compounds such as glycerin, sucrose, glucose and sodium chloride. In this fourth class of sustained-release dosage forms of azithromycin, the membranes can comprise any film-forming polymer, including polymers that are permeable or waterproof, provided that the membrane deposited on the core of the tablet is porous or contains porogenic agents. water soluble. The multiple particles (or granules) may be similarly prepared with an azithromycin core / inflatable material covered by a porous membrane or containing a porogenous agent.

As an object of this invention is to reduce the exposure of the upper Gl tract to high concentrations of azithromycin, a fifth special class of dosage forms includes those forms that incorporate a delay before beginning sustained release of azithromycin. A representative embodiment can be illustrated by a tablet comprising a core containing azithromycin, coated with a first coating of a polymeric material of a type useful for sustained release of azithromycin and a second coating of a type useful for delayed release of azithromycin. of the drug, when the dosage form is ingested. The first coating is applied to and around the tablet. The second coating is applied to and around the first coating.

The tablet may be prepared by techniques well known in the art and contains an amount of therapeutically useful azithromycin, plus such excipients required to form tablets by such techniques.

The first coating may be a sustained release coating, as is known in the art, especially polymeric coatings for fabricating the membrane, as discussed previously for reservoir systems. Suitable and preferred coating materials, equipment and methods of coating also include those discussed above.

Materials useful for the preparation of the second coating on the tablet include polymers known in the art as enteric coatings for delayed release pharmaceutical forms. These are usually pH-sensitive materials, such as cellulose acetate phthalate, cellulose acetate trimethylate, hydroxypropylmethyl cellulose phthalate, polyvinyl acetate phthalate and acrylic copolymers, such as Eudragit L 100 (Rohm Pharma) and related materials, as noted. more broadly in the chapter "Delayed Release". The thickness of the late release coatings is corrected to give the desired delay properties. In general, thicker coatings are more resistant to erosion and consequently give a longer delay. Preferred coatings range from about 300 μηπ in thickness to about 3 mm in thickness.

After ingested, the coated tablet twice passes through the stomach, where the second coating prevents the release of azithromycin under the acid conditions existing here. When the tablet passes through the stomach and enters the small intestine where pH is higher, the second coating is eroded and dissolved in accordance with the physico-chemical properties of

RO 114740 Bl of the chosen material. Upon erosion and dissolution of the second coating, the first coating prevents the immediate and rapid release of azithromycin and modulates the release in such a way as to prevent the production of high concentrations, thereby minimizing side effects.

□ Further preferred embodiment comprises multiple particles wherein each particle is double coated, as described above for tablets, first with a polymer designated to give sustained release of azithromycin and then coated with a polymer designated to initiate timing of release into the Gl tract environment when the dosage form is ingested. The granules contain azithromycin and may contain one or more excipients, as needed for manufacture and performance. Multiple particles containing a large fraction of azithromycin over the binder are preferred. The multiple particle can be a composition and can be manufactured by any of the techniques described above for multiple particles used for the preparation of reservoir systems (including extrusion and spheronization), wet granulation, fluid bed granulation and rotary bed granulation, seed building and the like. .

The sustained release coating may be as known in the art, in particular polymeric coatings for membrane fabrication, as presented above.

The release rate of azithromycin from multiple sustained release coated particles (eg, multiple particles before receiving delayed release coating) and the methods of changing the coating are also controlled by the factors presented above for multiple azithromycin particles in the reservoir system.

The second membrane or double-coated multiple-particle coating is a delayed-release coating that is applied over the first sustained-release coating, as previously described for tablets, and may be made of the same materials.

It should be noted that the use of so-called "enteric" materials to apply this variant differs significantly from their uses to produce conventional enteric dosage forms. In conventional enteric forms, the goal is to delay drug delivery until the dosage form has passed through the stomach and then to release the dose into the duodenum. The dosage of azithromycin directly and completely in the duodenum is however undesirable, due to the side effects that have been sought to be minimized or avoided by this invention. Therefore, if conventional enteric polymers are used in this embodiment, they need to be applied significantly thicker than in conventional practice, in order to delay drug delivery until the dosage form reaches the lower Gl tract. However, sustained or controlled release of azithromycin is preferred after the delayed release coating has been eroded and dissolved, so the benefits of this variant can be achieved with an appropriate combination of the delayed release type and the sustained release type and the part with delayed release alone may or may not comply with the USP enteric criterion. The thickness of the delayed release coating is corrected to give the desired delay properties. In general, thicker coatings are more resistant to erosion and consequently give a longer delay.

A first delayed variant according to the invention is a "pH dependent coated tablet", which comprises a tablet core containing azithromycin, a disintegrant, a lubricant and one or more pharmaceutical carriers,

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Such core being coated with a material, preferably a polymer, which is substantially insoluble and impermeable to the pH of the stomach and which is more soluble and permeable to the pH of the small intestine. Preferably, the coating polymer is essentially insoluble and impermeable to pH <5.0 and water soluble to pH> 5.0. It is also preferred that the core of the tablet is covered with a sufficient amount of polymer, which ensures that substantially no release from the dosage form runs until the dosage form has come out of the stomach and remained in the small intestine for about 15 min or more, preferably about 30 min or more, thus ensuring that minimal azithromycin is released into the duodenum. Mixing a pH-sensitive polymer with a water-insoluble polymer can also be used. The tablets are coated with an amount of polymer comprising from about 10% to about 80% by weight of the tablet core containing azithromycin. Preferred tablets are coated with an amount of polymer comprising about 15% to about 50% by weight of the azithromycin tablet core.

PH-sensitive polymers that are relatively insoluble and impermeable to stomach pH, but which are more soluble and permeable to the pH of the small intestine and colon, include polyacrylamides, acid phthalate derivatives of carbohydrates, phthalate amylase acetate, phthalate acetate cellulose, other cellulose esters, phthalates, cellulose ethers, hydroxypropyl phthalate cellulose, hydroxypropylethyl cellulose phthalate, hydroxypropylmethyl cellulose phthalate, methyl cellulose phthalate, polyvinyl acid phthalate, polyvinyl acetate phthalate, sodium cellulose phthalateacetate, starch acid phthalate, dibutyl phthalate copolymer maleic-styrene acid, polyvinylacetate copolymer maleic-styrene acid, maleicstyrene acid copolymer, polyacrylic acid derivatives acrylic and copolymers of acrylic ester, polymethylacrylic acid and its esters, methacrylicpolyacrylic acid copolymers, shellac, vinyl acetate and crotonic acid copolymers.

PH-sensitive polymers include shell, phthalate derivatives, in particular cellulose acetate phthalate, polyvinyl acetate phthalate and hydroxypropylmethyl cellulose phthalate; derivatives of polyacrylic acid, in particular polymethyl methacrylate mixed with acrylic acid and copolymer of acrylic ester, and copolymer of vinyl acetate and crotonic acid.

Phthalate cellulose acetate (CAP) can be applied to azithromycin tablets to ensure delayed release until the tablet containing azithromycin has passed the sensitive duodenal region, that is, to delay the release of azithromycin into the gastrointestinal tract by about 15 minutes and preferably about 30 minutes, after the tablet containing azithromycin passed from the stomach into the duodenum. The CAP coating solution may also contain one or more plasticizers. Such as diethylphthalate, polyethylene glycol-400, triacetin, triacetin citrate, citrate, propylene glycol and the like in the art. Preferred plasticizers are diethylphthalate and triacetin. Formulation of CAP coatings may also contain one or more emulsifiers, such as polysorbate-80.

Anionic acrylic copolymers of methacrylic acid and methyl methacrylate are also useful coating materials for delaying the release of azithromycin from tablets containing azithromycin, until the tablets have moved to a position in the small intestine that is distal to the duodenum. Copolymers of this type are available from Rohm Pharma Corp, under the trade name Eudragit-L(R | and Endragit-SR) which are anionic copolymers of methacrylic acid and methyl methacrylates. The ratio of free carboxyl groups to esters is about 1: 1 in Eudragit-L(R and about 1: 2 in Eudragit-S(R. Mixtures of these two substances can also be used. For the coating of tablets containing azithromycin, these coating polymers must be dissolved in an organic solvent or mixtures of

RO 114740 Bl organic solvents. The solvents useful for this purpose are acetone, isopropyl alcohol and methylene chloride. In general, it is advisable to include 5-20% plasticizer in the formulation of acrylic copolymers. Useful plasticizers are polyethylene glycols, propylene glycols, diethyl phthalates, dibutyl phthalates, castor oil and triacetin.

The delay time before azithromycin release after the dosage form as a "pH-dependent coated tablet" has come out of the stomach can be controlled by choosing the relative amounts of Eudragit-L(R) and Eudragit-s(R in coverage and by choosing the thickness of the coating. Eudragit-L films(R1 dissolves at pH greater than 6.0 and Eudragit-S films(R) dissolve above pH 7.0 and mixtures dissolve at intermediate pHs. If the pH of the duodenum is about 6.0 and the pH of the colon is about 7.0, the coatings made up of Eudragit-L mixtures(R) and Eudragit-S(R1 provides protection of the duodenum against azithromycin. If delayed release of azithromycin is desired until the "pH-dependent coated tablet" containing azithromycin has reached the colon, Eudragit-S can be used.(R1 as coating material, as described by Dew et al. (Br.J.Chi.Pharmac. 14 (1982), 405-408). For the purpose of delayed delivery of azithromycin for about 15 minutes or more, preferably 30 minutes or more, after the dosage form has come out of the stomach, the preferred coatings range from about 9: 1 to about 1: 9 Eudragit-LHR) by Eudragit-SLRL, preferably from about 9: 1 to about 1: 4 Eudragit-L(R by Eudragit-S(R). The coating may comprise from about 3% to about 70% by weight of the uncoated tablet core. Preferably, the coating comprises from about 5% to about 50% by weight of the tablet core.

In an additional embodiment of "pH dependent coated granule", the granules (about 0.5 to 3.0 mm in diameter) comprising azithromycin plus carrier are coated with one or more of the pH sensitive polymers. The coated granules may be inserted into a capsule or may be compressed into a tablet carefully to avoid damage to the polymer coating on the individual granules during tablet compression. Preferred coated granules are those that do not substantially release azithromycin from the dosage form until the granules have come out of the stomach and remained in the small intestine for about 15 min or more, preferably about 30 min or more, thus ensuring as minimal azithromycin is released into the duodenum. Mixtures of a pH-sensitive polymer with a water-insoluble polymer are also included. As previously described, granules containing azithromycin can be coated with mixtures of polymers whose solubility varies at different pHs. For example, preferred coatings range from about 9: 1 to about 1: 9 Eudragit-L[R) by Eudragit-S(R), preferably from 9: 1 to 1: 4 Eudragit-Lt) by Eudragit-SR). The coating may comprise from about 5% to about 200% by weight of the core of the uncoated granule. Preferably, the coating comprises from about 10% to about 100% by weight of the granule core.

In a further embodiment of "pH dependent coated particle", particles containing little azithromycin (about 0.01 to 0.5 mm in diameter, preferably 0.05 to 0.5 mm in diameter) are coated with one or more many pH-sensitive polymers mentioned above. The coated particles may be inserted into a capsule or carefully compressed into a tablet to avoid degradation of the polymeric coating on a polymeric particle during particle compression. Preferred coated particles are those that do not substantially exhibit azithromycin release from the dosage form until the particles have come out of the stomach and remained in the small intestine for 15 min or more. Preferably 30 min or more, thus ensuring minimal azithromycin to be released into the duodenum. mixtures

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Also included are a pH-sensitive polymer with a water-insoluble polymer. Particles containing azithromycin are coated with an amount of polymer comprising about 25% to about 200% by weight of the core of the uncoated particle containing azithromycin.

An additional embodiment is a modification of the pH-dependent coated tablet, pH-dependent coated granules and variants of pH-dependent coated particles. The tablet, granule or particle whose core contains azithromycin is first coated with a barrier coating and then coated with a pH-dependent coating. The function of the barrier coating is to separate azithromycin from the pH-dependent coating. Since azithromycin is a base, hydration of azithromycin in the core may serve to increase the pH in the pH-dependent coating microclimate, thus prematurely initiating the permeabilization or dissolution of the pH-dependent coating resulting in the premature release of a portion of the azithromycin dose or total dose of azithromycin in the stomach or duodenum. Suitable barrier coatings are made of water soluble materials such as sucrose sugars or water soluble polymers such as hydroxypropyl cellulose, hydroxypropylmethyl cellulose and the like. Hydroxypropyl cellulose and hydroxypropyl methyl cellulose are preferred.

The barrier coating may comprise from about 1% to about 15%, preferably from about 2% to about 10% by weight of the core of the tablet, granule or particle containing azithromycin. Coatings of tablets, granules and particles containing azithromycin can be made using equipment well known in the art. For example, tablet cores containing azithromycin may be coated with a plate coating device, such as a Hi-Coater (Freund Corp.) or Accela-Cota (Manesty Corp. Liverpool).

Granules and particles containing azithromycin are preferably coated using a fluidized bed coating device, such as a Wurster coating device, using available coating equipment, for example from Glatt Corporation (Ramsey, NJ). The granules can also be coated using a rotary granulator, such as a CF granulator available from Freund Corp.

In an additional embodiment ("osmotic sliding core device"), azithromycin is incorporated into an osmotic exploding device, which comprises a tablet core or a granule core containing azithromycin and optionally one or more osmotic agents. The device of this type has generally been described by Baker in US 3952741, which is incorporated herein by reference. Examples of osmotic agents are sugars, such as glucose, sucrose, mannitol, lactose and the like, and salts, such as sodium chloride, potassium chloride, sodium carbonate and the like, water-soluble acids, such as tartaric acid, fumaric acid and others like that. The tablet core or granule core containing azithromycin is coated with a polymer that forms a semipermeable membrane, i.e. a membrane that is permeable to water, but is substantially impermeable to azithromycin. Examples of polymers that provide a semipermeable membrane are cellulose acetate, cellulose butyrate acetate and ethyl cellulose, preferably cellulose acetate. Semi-permeable coating membranes may alternatively consist of one or more waxes, such as insect waxes and animal waxes, such as beeswax and vegetable waxes, such as carnauba wax and hydrogenated vegetable oils. A melt mixture of a polyethylene glycol, for example polyethylene glycol-6OOD and a hydrogenated oil, for example hydrogenated castor oil, can be used as a coating as described for ionoside tablets by Yoshino (Capsugel Symposia Series, "Current Situation

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935 on the delivery of the targeted drugs, in the gastrointestinal tract ”, 1993, p.185 ... 190). Preferred semipermeable coatings are cellulose esters and cellulose ethers, polyacrylic acid derivatives, such as polyacrylates and polyacrylate esters and polyvinyl alcohol and polyalkanes, such as ethylene-vinyl alcohol copolymers. Particularly preferred semi-permeable coating materials are cellulose acetate and cellulose acetate butyrate.

When a tablet or granule coated with the "osmotic explosion core" variant of the invention is introduced into an aqueous media, the water passes through the semipermeable membrane into the core, dissolving a portion of azithromycin and the osmotic agent, thus generating a colloidal osmotic pressure. leading to bursting of the semipermeable membrane and release of azithromycin into the aqueous environment. By choosing the size and geometry of the granule or tablet core, the nature and quantity of the osmotic agent and the thickness of the semipermeable membrane, the delay time can be chosen between introducing the dosage form into the aqueous medium for use and releasing the azithromycin included. It will be appreciated by those skilled in the art that, increasing the surface ratio, volume of the dosage form and increasing osmotic activity of the osmotic agent leads to a decrease in the delay time, which is why increasing the coating thickness will increase the delay time. Preferred osmotic explosion devices according to the invention are those which do not substantially deliver azithromycin from the dosage form until the dosage form has come out of the stomach and remained in the small intestine for about 15 min or more, preferably about 30 min or more. much, thus ensuring that minimal azithromycin is released into the duodenum. An osmotic exploding core tablet or granule has a tablet or granule core that may contain from about 25 ... 95% azithromycin, about 0.90% osmotic agent, as described above, and about 5. .2O% other pharmaceutical additives such as binders and lubricants. The semipermeable membrane coating on a tablet, preferably the cellulose coating, is present at the weight corresponding to about 2% to about 30%, preferably from about 3% to about 10% by weight of the core of the tablet. The coating with a semipermeable membrane on a granule, preferably a cellulose coating thereof, is presented at a weight corresponding from about 2% to about 80%, preferably from 3% to 30% by weight of the granule core.

An osmotic exploding core device does not have a mechanism for "detecting" the fact that the device exited the stomach and entered the duodenum. Such devices release azithromycin at a predetermined time after entering the aqueous environment, for example after non-disintegrating solids, such as the "osmotic exploding core devices" of the invention have been inflated in the rapid stage. stomach during stage III of the myoelectric interdigestion migration complex (BMI) that occurs approximately every two hours in the human body. Depending on the stage of IMMC at the time of dosing in the rapid stage, a osmotic exploding core device may exit the stomach almost immediately after dosing or to the same extent two hours after dosing. In the feeding situation, the non-digestible solids that do not disintegrate, which are <11 mm in diameter, will slowly drain the stomach of the contents of the food (Khosla and Davis Int. If the non-disintegrating solid, which does not disintegrate, has a diameter greater than 11 mm, for example, the size of a standard tablet, it will be retained in the stomach during food digestion and will exit into the duodenum during phase III of IMMC, after food they were temporarily digested and left the stomach. It is preferable to delay the release of azithromycin up to ca. 15 min or more,

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1020 preferably 30 min or more after the dosage form has come out of the stomach. A core device that osmotically explodes with the release of azithromycin about 1.5 hours after ingestion has occurred, will decrease the incidence and severity of gastrointestinal effects in a population of patients receiving azithromycin in such devices. A preferred core device with osmotic explosion begins to release azithromycin at approx. 2.5 h after entering the aqueous environment, for example after ingestion which to ensure the release of the azithromycin distal to the duodenum by the device when dosed in the rapid stage. A more preferred osmotic exploding core device will begin to release azithromycin at approx. 4 hours after entering an aqueous environment. These 4 hours of delay allow dosing in the feeding stage and allow retention in the food stomach for approx. 3.5 h, followed by a delay of approximately 30 minutes after the dosage form exited the stomach. In this way, the release of azithromycin in the most sensitive portion of the gastrointestinal tract, the duodenum, is minimized.

In a further embodiment, an "explosive swelling coated core" is a tablet or granule containing azithromycin, also comprising 27 ... 70% of an inflatable material, such as an inflatable colloid (e.g. gelatin). as described by Milosovich in US 3247066, incorporated herein by reference.

Preferred bulking core materials are hydrogels, hydrophilic polymers that take up water and swell, such as polyethylene oxides, polyacrylic acid derivatives, such as polymethylmethacrylates, polyacrylamides, polyvinyl alcohol, poly / AN-vinyl-2-pyrrolidone, carboxymethylene, other carboxymethylene, also. Preferred inflating hydrogels for this variant are polyethylene oxides and carboxymethyl cellulose. The tablet or granule containing the colloid-hydrogel containing azithromycin is covered at least in part by a semipermeable membrane. Examples of polymers that provide a semipermeable membrane are cellulose acetate, cellulose acetate butyl cellulose acetate, preferably cellulose acetate. The semipermeable coating membrane may alternatively be composed of one or more waxes, such as insect and animal waxes, such as beeswax, and vegetable waxes, such as carnauba wax and hydrogenated vegetable oils. A melt mixture of a polyethylene glycol, for example a polyethylene glycol-6000 and a hydrogenated oil, for example hydrogenated castor oil, can be used as a coating, as described for isoniazid tablets by Yoshino [Capsugelshy Symposia Series' , “Listening situation of the delivery of the targeted drugs in the gastrointestinal tract”; 1993, pp. 185 ... 189).

Preferred semipermeable coatings are cellulose esters and cellulose ethers, polyacrylic acid derivatives, such as polyacrylates and polyacrylate esters and polyvinyl and polyalkylene alcohols, such as ethylene-vinyl alcohol copolymer. Particularly preferred semi-permeable coating materials are cellulose acetate and cellulose acetate butyrate.

As much as one coated tablet or pellet having an explosive-coated coated core is introduced into an aqueous use medium, the water passes through the semipermeable membrane into the core, inflating the core and leading to bursting of the semipermeable membrane and release of azithromycin into the aqueous medium.

By choosing the size and geometry of the core of the pellet or tablet, the nature and quantity of the blowing agent and the thickness of the semipermeable membrane, the delay time can be chosen between the positioning of the dosage form in the aqueous use environment and the release of the included azithromycin. according to the invention are those which do not substantially exhibit azitro1025 release

RO 114740 Bladder of the dosage form. Until the dosage form came out of the stomach and remained 1030 in the small intestine approx. 15 min or more, preferably approx. 30 min or more, thus ensuring that at least azithromycin is released into the duodenum. A tablet or a coated granule that bursts with explosion may contain approx. 25 ... 75% azithromycin, ca. 15 ... 60% inflating material, for example hydrogel, optionally approx. 0 ... 15% osmotic agent and about 5 ... 20% other pharmaceutical additives such as binders and 1035 lubricants. The semipermeable membrane coating on a tablet, preferably a cellulose acetate coating, is presented at a weight corresponding to about 2% to about one. 30%, preferably from 3% to 10% by weight of the tablet core. The coating with a semipermeable membrane on a granule, preferably a cellulose acetate coating, is presented at a weight corresponding to approx. 2% to about 80%, 1040 preferably from 3% to 30% by weight of the granule core.

A blown core device that blows with explosion can not have a mechanism for detecting the output of the device from the stomach and entering the duodenum. Devices of this type release azithromycin contents at a predetermined time after entering the aqueous environment, for example after swelling, as discussed above for core osmotic explosion devices, and the same considerations and preferences are applied to prepare explosive-coated core devices.

In a further embodiment, a pH-triggered osmotic burst device ", azithromycin is incorporated in a device of the type described in US Pat. No. 1050 5358502 belonging to the same applicants, issued on October 25.1944, incorporated herein by reference. The device comprises azithromycin and optionally one or more osmotic agents surrounded at least in part with a semipermeable membrane. The semipermeable membrane is water permeable and substantially impermeable to azithromycin and the osmotic agent. Useful osmotic agents or the same as those described 1055 above for osmotic explosion core devices. The materials for the useful semipermeable membranes are the same as those described above for the osmotic explosion core devices. A pH trigger means that it is attached to the semipermeable membrane. The pH trigger means that it is activated by a pH greater than 5.0 and soon triggers the release of azithromycin. In this embodiment, the pH trigger comprises a membrane coating or a polymeric coating surrounding the semipermeable coating. The pH trigger coating contains a polymer that is substantially impermeable and insoluble in the pH range of the stomach, but which becomes permeable and solid at the pH value of douden, ca.pH 6.0. 1065

Representative pH sensitive polymers are polyacrylamides, phthalate derivatives, such as carbohydrate acid phthalates, amylose phthalate acetate, cellulose phthalate acetate, other phthalate cellulose esters, phthalate cellulose ethers, hydroxypropal phthalate, hydroxypropal phthalate, cellulose hydroxypropyl cellulose hydroxypropylmethyl cellulose, methyl cellulose phthalate, polyvinyl acetate phthalate, polyvinyl acid phthalate acetate, 1070 sodium cellulose acetate phthalate, starch acid phthalate, dibutylphthalate-maleic acid-styrene copolymer, polyvinyl acetate-maleic acid-styrene copolymer, maleic acid and styrene copolymers, polyacrylic acid derivatives, such as copolymers of acrylic acid and acrylic esters, acid copolymers. polymethacrylic and its esters, methacrylicpolyacrylic acid copolymers, shellac and vinyl acetate and protonic acid copolymers. 1075

Preferred pH-sensitive polymers, including: shellac, derivatives, phthalates, in particular phthalate, cetate, cellulose, polyvinyl acetate phthalate and hydroxypropylmethyl cellulose phthalate; derivatives of polyacrylic acid, in particular polymethylacrylates mixed with copolymers of

RO 114740 Acrylic acid bl and acrylic ester copolymers; and vinyl acetate copolymers and protonic acid copolymers. As described above, phthalate cellulose acetate is available as a latex under the trademark Aquateric (registered trademark of FMC Corp; Philadephia, PA) and acrylic copolymers are available under the trade names Eudragit-R(R) and Eudragit-L(R1. For similar applications in this embodiment, these polymers must be laminated using the plasticizers described above. The pH trigger coating may also comprise a mixture of polymers, for example cellulose acetate and phthalate cellulose acetate. Another suitable mixture comprises Eudragit-L(R1 and Eudragit-S(R), the ratio of the two and the thickness of the coating define the sensitivity of the "trigger", for example the pH at which the coating outside the pH trigger is softened or dissolved.

A pH-triggered osmotic explosion device generally operates as follows. After oral ingestion, the pH-triggered coating that surrounds the semi-permeable coating that, in turn, surrounds the core of the tablet or granule containing azithromycin, remains undissolved and intact in the stomach. In the stomach, the water may or may not begin to penetrate by pH-triggered coating and semi-permeable coating thus starting the hydration of the azithromycin-containing core and optionally the osmotic agent. After the device exits the stomach and enters the small intestine, the coating containing the pH trigger rapidly disintegrates and dissolves and the water passes through the semipermeable coating, dissolving azithromycin and the optional osmotic agent in the core. As the colloidal osmotic pressure along the semi-permeable coating exceeds some limit values, the semi-permeable coating is destroyed and the device explodes, releasing azithromycin; it is preferable that this explosion and release of azithromycin should proceed at approx. 15 min or more, preferably 30 min or more, after the osmotic burst device with pH trigger exits the stomach and enters the duodenum, thereby minimizing exposure of the azithromycin sensitive duodenum.

For a pH-triggered osmotic burst device, the timing period and the delay time are controlled by the nature and amount of osmotic agent in the core, by choosing the semi-permeable coating and the thickness of the semi-permeable coating.

It will be appreciated by those skilled in the art that a more severe semi-permeable coating will lead to a greater delay after the device has come out of the stomach. A preferred device triggered by pH-triggered osmotic is a tablet or granule core of azithromycin with osmotic agent optionally coated with a membrane of 3 ... 20% by weight cellulose acetate, coated with a membrane of

3 .. .20% by weight consisting of approx. 1: 1 cellulose acetate / phthalate cellulose acetate. Another preferred device for pH-triggered osmotic bursting is an azithromycin granule or tablet core with osmotic agent optionally coated with a membrane of 3 ... 20% by weight cellulose acetate, coated with a membrane of

3 .. .20% by weight, made up of approx. 9: 1 to approx. 1: 1 Eudragit-L| R and EudragitS{R) Advantageously, because a pH-triggered osmotic burst device has a mechanism for controlling whether the device has come out of the stomach, the variation from one patient to another in gastric emptying is not significant.

In a further embodiment, "a coated core that inflates by bursting with pH, a tablet or granule core containing azithromycin and a swelling material is coated with a semipermeable coating, which is further coated with a pH sensitive coating. Core composition, including

EN 114740 Bl the choice of material that is inflating, is described as above for the coated core variant that inflates by exploding. The choice of semipermeable coating material and pH sensitive coating material as described above 1130 for the "pH-triggered osmotic core" variant is described in detail in US Patent Application 08/023227 belonging to the same applicants, registered in February 25, 1993, incorporated herein for references.

□ Inflating core variant bursting with pH trigger operates as follows. After oral ingestion, the pH-trigger coating surrounding the 1135 semi-permeable coating, which, in turn, surrounds the tablet or granule core containing azithromycin, remains undissolved and intact in the stomach. In the stomach, water may or may not begin penetration by pH-triggered coating and semi-permeable coating thus beginning hydration of the azithromycin-containing core and water-inflatable material, preferably a hydrogel. When the pH-triggered 1140 core device exits the stomach and enters the small intestine, the pH-triggered coating disintegrates rapidly and dissolves and the water passes through the semi-permeable coating, dissolving azithromycin and inflating the inflatable material into the water in the core. As the inflation pressure along the semi-permeable coating exceeds certain limit values, the semi-permeable coating is destroyed and the device 1145 exploding releasing azithromycin. It is preferable that this explosion and release of azithromycin should be approx. 15 minutes or more, preferably 30 minutes after the bursting, pH-triggered core device exits the stomach and enters the duodenum, minimizing exposure to azithromycin of the sensitive duodenum.

For the "core that inflates at a burst pH," the timing period and the delay time can be controlled by the choice and quantity of the core inflation material, by choosing the semi-permeable coating and the thickness of the semi-permeable coating. It will be appreciated by those skilled in the art, for example, that a thicker semi-permeable coating will lead to a longer delay after the device has come out of the stomach. A preferred swelling device bursting from 1155 pH-containing contains a pellet core or tablet of azithromycin with systemic hydrogel, preferably carboxymethylcellulose, coated with a membrane of 3 ... 20% by weight cellulose acetate coated with a membrane of 3 ... 20% by weight, made up of approx. 1: 1 cellulose acetate / phthalate cellulose acetate. Another preferred device of pH-inflating exploding core contains a granule core or 1160 tablet of azithromycin with synthetic hydrogel, preferably carboxymethylcellulose, coated with a membrane of 3 ... 20% by weight cellulose acetate coated with a membrane with 3 ... 20% in grooves. 9: 1 to about 1: 1 Eudragit-L(R) and EudragitS(R1.

Advantageously, because the inflating core device bursting at 1165 triggered by pH has a mechanism for detecting whether the device has come out of the stomach, the variability from one patient to another in gastric emptying is insignificant.

In a further embodiment, a "liquid membrane device deposited on triggered enzyme support" comprises azithromycin formulated in a dosage form of the type described in PCT / US Patent Application 93/07463, published as Ul / O 94/1170 12159 on June 9, 1994, incorporated herein by reference. This variant generally has the form of a tablet or granule containing azithromycin and excipients, a microporous hydrophobic support membrane which is at least partially surrounded by an advantageous agent and a hydrophobic fluid entrained in the pores of the support membrane. Alternatively, azithromycin and excipients may be incorporated in a capsule shell which comprises a microporous hydrophobic membrane with a hydrophobic fluid entrained in the pores.

RO 114740 Bl

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1220 of the capsule shell. The hydrophobic liquid is substantially impermeable both to the aqueous environment and to the azithromycin core formulation as a tablet or granule. The hydrophobic fluid is capable of change, so that it becomes substantially permeable both in the aqueous environment and in the formulation of azithromycin. After ingestion of this variant by a mammal, including a human, the release of azithromycin into the gastrointestinal system is delayed up to about 15 min or more, preferably about 30 min, after the dosage form has come out of the stomach and moved into the duodenum.

In a liquid membrane device deposited on the carrier with azithromycin enzyme trigger, the hydrophobic liquid deposited on the carrier is preferably a changing fluid, which is enzymatically catalyzed in the lumen of the small intestine and not in the stomach. Representative hydrophobic liquids are triglycerides, fatty anhydrides, cholesterol fatty acid esters, hydrophobic amino acid esters and the like. Preferred triglycerides include triolein, tricaprilin, trilaurine, olive oil, palm oil, coconut oil, sesame seed oil, peanut oil, soybean oil and the like. Preferred fatty acid anhydrides include caprylic anhydride, lauric anhydride, myristic anhydride and the like. Mixtures of hydrophobic liquids may be used. Representative materials for microporous hydrophobic support membranes include cellulose esters, polycarbonates, polyalkylenes, polystyrene, polyvinyl esters, polixiloxane, polyacrylates and polyethers. The preferred hydrophobic microporous membrane that drives the hydrophobic fluid is impermeable to azithromycin until the gastrointestinal enzymes catalyze a change in hydrophobic oil as described below.

In the environment of use, for example in the lumen of the small intestine, lipases and esterases degrade the aforementioned hydrophobic oils, releasing surface active products into the pores of the microporous membrane of this variant, thus producing aqueous channels through which azithromycin from the core of the device may exit through the hydrophobic support membrane. microporous. The release of azithromycin can result from simple diffusion, osmotic pumping, osmotic explosion or explosion, due to the presence of an inflatable material, for example hydrogel, in the core of the device containing azithromycin.

Hydrophobic oils that are subtracted from proteases of the small intestine, such as carboxypeptidase and chemotrypsin, can be used in a fluid membrane device supported on the substrate, with azithromycin enzyme trigger. Representative oils are hydrophobic esters of amino acid derivatives.

In a further embodiment, a "bacterial degradable coating device", tablets or granules containing azithromycin are coated with a material that is substantially impermeable to azithromycin in the stomach and small intestine, the coating material being degraded by bacteria or by bacteria that release enzymes (eg, azoreductases) into the colon, thus releasing azithromycin. After degradation of the coating material in the colon, azithromycin is released. Variants of this scheme minimize exposure of the upper sensitive region (duodenum) of the small intestine to azithromycin. Examples of coatings of this variant are polymers from unsaturated, substituted or unsubstituted ethylene monomers, branched with divinylazobenzene, as described in US Patent Nos. 4663308 and 5032575, each incorporated herein by reference. Other examples of coatings of this embodiment are degradable polysaccharides, such as spectin and algin, and mixtures of these degradable polysaccharides with film-forming polymers, such as ethyl cellulose, methyl cellulose, hydroxypropylmethyl cellulose and the like. Polysaccharide coatings of this type were

1225

RO 114740 Bl described in EP 485840 Depascali et al and Roher and Steinick in DD 296840 and Ashford and Fell in Capsugel Symposia Series, Current Status on Targeted Drug Delivery to the Gastrointestinal Tract 1993, pp. 133-142.

Examples of bacterially degradable coating devices include a pellet or tablet core containing approx. 25 ... 90% azithromycin with additional additives 1230 tablets. As are binders and lubricants, coated with a membrane of azo-polymers or polysaccharide whose weight corresponds to approx. 5 ... 80%, preferably 10 ... 50% of the tablet or granule core thickness.

In a further embodiment, a device with "inflating shutters", azithromycin and the appropriate excipients and carriers are incorporated in a non-dissolving semicapsule 1235, which is sealed at one end by a hydrogel shutter. This hydrogel filler swells in an aqueous medium and after swelling. After a certain time, it exits the capsule, thus opening a passage through which azithromycin can leave the capsule and can be released into the aqueous medium. The capsules filled with hydrogel are those that do not substantially release azithromycin from the dosage form 1240, until the dosage form has come out of the stomach and remained in the small intestine for approx. 15 min or more, preferably about 30 min or more, thus ensuring that minimal azithromycin is released into the duodenum. Capsules filled with hydrogel of this type have been described in patent application WO 90/19168, which is incorporated herein by reference. An azithromycin device with inflating shutters 1245 can be prepared by loading azithromycin into a non-dissolving semicapsule shell, which can be made of a wide variety of materials, including, but not limited to, polypropylene, methyl polymethacrylate. , vinyl polychloride, polystyrene, polyurethanes, polytetrafluoro-ethylene, nylon, polyformaldehyde, polyesters, cellulose acetate and nitrocellulose. The open end of the capsule shell is then "sealed" with a cylindrical obturator 1250 formed of a hydrogel-forming material, including but not limited to a branched homo- or copolyalkenoxide, by reaction with isocyanate with ether groups. unsaturated cyclic, as described in PCT Application WO 90/09168. The composition and length of the hydrogel "shutter" are selected so as to minimize the release of azithromycin in the stomach and duodenum to decrease the incidence of 1255 and / or the severity of gastrointestinal side effects.

The obturated semicapsule is finally sealed with a water soluble material, for example gelatin, a semicapsule placed over the hydrogel-filled end of the non-dissolving semicapsule, continuing azithromycin. In a preferred embodiment of the "inflating shutter device", the sealed device is coated with a "polymer 1260 or a mixture of pH-sensitive etheric polymers", for example phthalate, cellulose acetate or copolymers of methacrylic acid and methacrylate. methyl. The weight of the enteric polymer coating will generally be from 2 to 20%, preferably from 4 to 15%, by weight of the uncoated sealed capsule. When this "enteric coated device with inflating obturator" is ingested orally, the enteric coating prevents the release of azithromycin into the stomach. The etheric coating dissolves rapidly, for example in approx. 15 min in the duodenum, triggering swelling of the hydrogel shutter, elimination of the hydrogel shutter and release of azithromycin embedded in the gastrointestinal tract at a time greater than ca. 15 min, and preferably greater than about 30 min, after the dosage form has passed from the stomach into the duodenum. The unfinished prototype of the 1270 "inflating shutter device" can be obtained from Scherer DDS Limited, Clydebank, Scotland. Under the name "Pulsincap".

It will be appreciated by those skilled in the art that the various variants of tablets, granules or particles coated with azithromycin described above may be

RO 114740 Bl coated using standard roofing equipment, such as plate coating device (eg, Hi-Coater available from Freund Corp.; Accela-Share available from Manesty, Liverpool], fluidized bed coating devices, example Wurster type (available from Glatt Corp, Ramsey, NJ and Aeromatic Corp., Columbia, MD) and rotary granulators, for example -CF granulator (available from Freund Corp.). The core of the tablets is made on presses for standard tablets, such as the Killian press. The granules and particles containing azithromycin are obtained on fluidized bed granulators, rotary granulators and extruder superposed extruders. Delayed release variants according to the invention in solid dosage forms for oral administration, containing azithromycin and a pharmaceutically acceptable carrier releasing 10% of azithromycin, have been incorporated into a mammal's stomach and release no more than a 10% addition. during the first 15 min after entry into the mammalian duodenum. Synchronization of azithromycin release into the stomach and duodenum can be tested using a variety of pathways, including, but not limited to, X-ray assessment, nuclear magnetic resonance imaging, gamma scientifigraphy, or directly by taking gastric and duodenal content samples by intubation. Although these tests are possible, they can still be difficult to conduct in the human body. A more convenient assay for a delayed release variant of the present invention is a two-step in vitro dissolution assay, which includes a 15 min azotrimycin release assay in a similar gastric fluid and an azithromycin release assay at 15 min in simulated intestinal fluid. This in vitro two-step assay for delayed-release dosage form is described in detail below. For certain late-release variants presented in this specification, azithromycin release is “triggered” by the presence of pancreatic lipase in the duodenum; for in vitro evaluation of delayed release dosage forms triggered by lipase, 5 mg / ml of swine pancreatic lipase (Sigma Chem .; St. Louis, MO) is included in the dissolution medium for the second stage of the dissolution test. The invention will now be illustrated by the following examples, which are not limiting. In general, the examples demonstrate that the incidence of gastrointestinal side effects on the oral, IV, duodenal, and ileal-caecal dosage of azithromycin and the preparation of dosage forms with controlled release of azithromycin are within the scope of this invention. In the following examples, the following definitions and tests were used:

1. "Q" is used to refer to the amount of azithromycin in either mg or percent (%), as indicated. Q is associated with an "extraction point" at which an aliquot part of the azithromycin test solution is removed, the removal time or extraction point being indicated in hours as a subscription. Thus, “Q0 25"15 mg means that 15 mg of azithromycin dissolved in a quarter of an hour.

2. Specifying a quantity in percent (%) means percent by weight compared to the total weight, when there are no other indications.

3. "Eudragit LRL"Is a registered trademark of Rohm Pharma GmbH, Germany. For a family of methacrylate enteric polymers.

4. "Opadry" is a trademark of Colorcon Inc., West Point, PA for a family of cellulose ethers plasticizers including hydroxypropylmethyl cellulose, hydroxypropyl cellulose and methyl cellulose which are supplied as powders for reconstitution in water.

5. "Surelease" is the trademark of Colorcon Inc., West Point, PA for a fully polymerized polymerized ethyl cellulose dispersion.

6. "MgA" is an abbreviation for "milligrams of active azithromycin." Of

For example, "250 mgA" means 250 mg of active azithromycin.

7. "Multiple particle XmgA" (where X is a number) represents the 1325 quantity of multiple particles containing XmgA. For example, “250 mgA of multiple particles means the weight of multiple particles containing 250 mgA.

8. "MgAm" is an abbreviation for "milligrams A of multiple particles".

9. “Usage environment is the aqueous environment of the gastrointestinal tract.

10. In vitro dissolution tests. The following two in vitro assays can be used 1330 to sketch the sustained release and delayed release variants of this invention to be suitable in vivo. If a particular dosage form meets the criteria described below for each test, it is within the scope of the invention.

Sustained Release Dosage Test: Azithromycin sustained release dosage forms are tested in a rotary bladder, type 1335 USP standard, as described in United States Pharmacopea XXIII (USP), Dissolution Test, Chapter 711, apparatus 2. The pallets are rotated at 50 rpm and the dissolution test is conducted in, as a test medium, 900 ml of sodium acid phosphate buffer at pH 6.0 at 37 ° C. If capsules are used, then 0.1 mg / ml trypsin enzyme should be used in buffer, at the indicated time following the initiation of the test (eg, 1340 inserting the dosage sample into the apparatus), filtering aliquots (typically 5 or 10 ml) from the medium. to be tested are analyzed for azithromycin by high performance liquid chromatography (HPLC), as described below. Dissolution results are reported as mg azithromycin dissolved over time. The sustained-release dosage forms that meet the following criteria are within the scope of the invention: 1. Q025 <200 mg today - 1345 dissolved thromycin; 2. Q., <500 mg azithromycin dissolved; 3. Q2 <1000 mg azithromycin dissolved; 4. Q4 <1500 mg dissolved azithromycin; 5.Q6<20,000 mg dissolved azithromycin, where Q is defined as above.

Delayed-release dosing test: Azithromycin delayed-release dosage forms are also tested in a USP standard 1350 rotary vane as described above. The blades are rotated at 50 rpm and the dissolution is conducted in two steps at 37 ° C. A first acid step is implemented by inserting a delayed-release dosage form into an acidic medium of 750 ml of 0.1 N Hcl. At 15 min, an aliquot part of the acid test medium is filtered and analyzed for azithromycin content by HPLC. A second 1355 step is implemented immediately after the first step, by adding 250 ml of 0.2 M tribasic sodium phosphate buffer, thereby converting the first stage acidic medium to a buffer having a pH of about 6.8. If the measured pH has an excess or minus 0.05 units of pH compared to 6.8, it will need to be properly corrected by the addition of alkali metal hydroxide or hydrochloric acid (both 2N), as appropriate 1360 . At 15 minutes after the addition of the phosphate buffer, a second aliquot of the test medium is filtered and analyzed for azithromycin content by HPCL. Dissolution results are reported as percent of azithromycin dissolved over time. Delayed-release dosage forms that meet the following criteria are within the scope of the invention: 1. Qq 25 <10% dissolved azithromycin; 2. Οθ5 < 0^25 < 0325 1365 + 10% azithromycin dissolved. The test is real for dosage forms containing up to 7000 mgA.

The criteria in each test are also found in the examples as "dissolution criteria".

11. HPLC quantification. When the dissolution tests described above are 1370 conducted in vitro, azithromycin is quantitatively determined by high performance liquid chromatography with reverse phase and electrochemical detection, as follows:

An aliquot of the test solution is filtered to remove the particles and diluted to a desired concentration of approximately // g / ml. A fixed volume of 50 µ \ is injected into a pre-column (5 cm x 4.6 mm diameter) with 5 micron spherical alumina (80 pore diameter) based on hydrocarbon stationary phase (Gamma RP-1 , ES Industries, Berlin, NJ], The precolumn is followed by a column with a diameter of 15 cm x 4.6 mm, containing the same stationary phase. The chromatography system is practically that described in Shepard et al., J. Chromatography, 565: 321337 (1991). An isocratic mobile phase, containing 72% potassium monobasic phosphate buffer, 0.02 M and 28% acetonitrile (v / v, final pH 11), is used at a flow rate of 1.5 ml / min. The electrochemistry detector uses dual-glass carbon electrodes (Model LC-4B Amperometric Detector, Bioanalytical Systems, West Lafayette, IN), which operate with oxidative with reference electrode suitable at about + 0.7 V and working electrode suitable at about + 0 , 8 V. in the sustained release test environment, the actual quantitative determination of azithromycin is performed, by comparing the ratio of the peak height of the sample chromatogram to the internal standard of diphenhydramine with a ratio of the height of the peak of the standard azithromycin chromatogram to the same internal standard. In the delayed release (acid) test medium, because azithromycin can hydrolyze to deosaminylazithromycin, the amount of dissolved azithromycin it has hydrolyzed is determined and converted to its equivalent as azithromycin (conversion factor 1.26). In the delayed release test medium, diphenhydramine is again used as an internal reference standard for peak height, for both sample and standard azithromycin / deosaminyl azithromycin chromatograms.

12. Where values are not given in the tables, they have not been determined.

Test no. 1 below shows that an oral dose of 2 g azithromycin gives a similar incidence of gastrointestinal side effects, as if 2 g are given as a single oral dose or as eight doses of 250 mg given as 250 mg every half hour for 3.5 hours.

In a randomized, double-blind, placebo-controlled, parallel study, healthy male subjects are divided into three groups. Group A receives a single dose of 2g azithromycin as eight doses of 250 mg capsules with azithromycin (bolus dosing group). Group B receives the same total dose, administered as a 250 mg capsule every 30 minutes for 3.5 hours (the "split dosage" group). Group C is given appropriate placebo capsules. All subjects receive eight capsules of medicine or placebo at time □ and one capsule of medicines or placebo every half hour for 3.5 hours. All subjects are dosed after one night of fasting. Blood samples are taken before dosing and at 0.5, 1, 1.5, 2, 2.5, 3, 3.5, 4, 6, 8, 12, 16, 24, 48, 72, 96, 144, 192 and 240 h after dosing. Serum azithromycin concentration is determined by the high performance liquid chromatography test described by Shepard et al., J. Chromatography, 565: 321-337 (1991). The total systemic exposure to azithromycin was determined by measuring the surface area below the concentration of serum azithromycin versus the temporal cube (AUC) for each subject in a given group and then calculating an AUC average for the group. Cmax is the highest serum concentration achieved on a subject. Tmax is the time at which Cmax is achieved. Serum pharmacokinetic data for this example are presented in Table 1.

before dosing and at each time the blood sample is taken, each subject completes a questionnaire that consists of a series of "analogous visual scales" in which the subject is asked to scale on a scale from □ to 10. The severity of certain

Potential side effects: subjects are instructed to "indicate an absence of effects and that" 10 indicates the worst possible effect. Subjects are trained to interpolate between O and 10 for moderate side effects.

A total of 45 subjects complete this study: 16 with placebo, 15 with 1425 single dose of 2g and 14 with 250 mg every half hour for 3.5 hours. For four side effects evaluated at 20 times, a total evaluation of 3600 individual analog visual scales is obtained.

The analysis of the data on the analogical visual scale of the side effects is done in two forms. 1430 in the first format (Table II), the analysis focuses on the general incidence of side effects for a certain time. For each side effect time (eg, abdominal pain), Table II reports the number of subjects with a score <1 at any time during the 240 hours after dosing and the number of subjects having a score <4 at any time during 240 hours after 1435 dosing. This analysis assumes that all scores <1 represent a real occurrence of a side effect, however mild or severe. A score <4 is assumed to reflect a moderate to severe onset of side effect.

In the second format (Table III), the analysis reflects the severity and overall duration of the side effects. For a certain side effect (for example, abdominal pain 1440), in a certain subject, all scores of the analogous visual scale (after the 240 h period after dosing) are summed to give a "cumulative score" over the entire time period. of the evaluation. The “Cumulative Score” for all members of a treatment group are summed and divided by the number of subjects in the group, to give an average cumulative score. The scale of this average cumulative score does not correspond to the original 1445 O ... 10 scale because it reflects the sum of all scores other than O over the entire assessment period. Table III presents the average cumulative scores for abdominal pain, nausea, regurgitation and abdominal cramps.

Table I shows that the total systemic exposure to azithromycin of the two dosage groups reflected in the AUC is similar. For the divided dosage group 1450, Cmax is lower and Tmax is longer, after which it is expected that the dosage will occur after 3.5 h, rather than in a single bolus dose.

Table II demonstrates that abdominal pain, nausea, and abdominal cramps are frequently secondary effects in the act of a bolus dose of 2 g, during regurgitation. The dosage divided over 3.5 h gives a similar incidence profile of 1455 of secondary t.

Table III shows that the severity of the side effects induced by azithromycin for bolus and split dosage treatments are similar.

The data presented in Tables II and III show that releasing the 2 g dose in an amount of 500 mg / h does not lead to an increased incidence of the side effect, 1460 compared to a single bolus dose of 2 g. this example divided dose is reflected in the exposure of the upper gastrointestinal tract, ie stomach and duodenum, to the entire divided dose.

RO 114740 Bl

Table I

Pharmacokinetics of azithromycin for a dose of 2 g given as a single dose or as eight doses of 250 g every half hour for 3.5 hours (mean values) AUCai44

<td>TREATMENT</td><td>Cmax (/ zg / ml)</td><td>Tmax [hours]</td><td>AUCq_144 (Mg-h / ml)</td>

<td>single dose of 2 g</td><td> 1,69</td><td> 1.3</td><td> 18,8</td>

<td>250 mg / 1/2 for 3.5 hours</td><td> 1,13</td><td> 4,4</td><td> 18,9</td>

Table II

The incidence of analogue-visual scale scores exceeding 1 or 4 at any time during the 240 ha of the dose evaluation period, for the determination of side effects: abdominal pain, nausea, regurgitation and abdominal cramps, dosed every half hour, for 3.5 hours:

<td></td><td colspan="2">Abdominal pain</td><td colspan="2">Nausea</td><td colspan="2">regurgitation</td><td colspan="2">Abdominal cramp</td>

<td>Treatment T</td><td> > 1</td><td> > 4</td><td> > 1</td><td> >4</td><td> > 1</td><td> > 4</td><td> > 1</td><td> > 4</td>

<td>placebo</td><td> 0/16</td><td> 0/16</td><td> 0/16</td><td> 0/16</td><td> 0/16</td><td> 0/16</td><td> 0/16</td><td> 1/16</td>

<td>2 g single dose</td><td> 6/15</td><td> 2/15</td><td> 1/15</td><td> 1/15</td><td> 0/15</td><td> 0/15</td><td> 6/15</td><td> 1/15</td>

Note: Results reported as (# patient score) / (total # patients)

Table III Average cumulative score

Cumulative mean data of the Visual Analog Scale for Side Effects: Abdominal Pain, Nausea, Regurgitation, and Abdominal Cramps, over the entire 240 h post-dose evaluation period [See text for explanation of "average cumulative score"].

<td>TREATMENT</td><td>n *</td><td>Abdominal pain</td><td>Nausea</td><td>Regurgitate and</td><td>Abdominal cramp</td>

<td>placebo</td><td> 16</td><td> 0,19</td><td> 0,25</td><td> 0,06</td><td> 1,19</td>

<td>Single dose 2 g</td><td> 15</td><td> 6,4</td><td> 1,93</td><td> 0,53</td><td> 4,67</td>

* the average number of subjects

Test no. 2: This test demonstrates that dosing at 2 g of azithromycin directly into the human duodenum leads to a higher incidence and severity of gastrointestinal side effects than those seen when azithromycin (2 g) is dosed directly in the ileocecal region of the small intestine. supports the conclusion that the incidence and severity of gastrointestinal side effects of azithromycin may be

RO 114740 Bl reduced by decreasing duodenal exposure to orally administered azithromycin. This example also demonstrates that direct delivery of azithromycin into the duodenum or ileocecal region of the small intestine does not result in any loss of systemic bioaccessibility compared to oral dosing. 1510

Healthy male subjects are divided into two groups. Group A received a dose of 2 g azithromycin administered directly into the duodenum as a solution through a nasoenteric tube. Group B received the same dose of azithromycin solution, administered directly into the ileocecal region of the small intestine through a nasoenteric tube. The nasoenteric tube is a single lumen, a 4.5 m tube with a side hole for 1515 drug delivery. The placement of the tube for release into the duodenum and ileocecal is confirmed by floroscopy. Infusions in the duodenal and ileocecal region are administered at a concentration of 40 mg / ml for 5 minutes. All subjects were dosed after one night of fasting. Subjects were randomized to receive azithromycin and placebo through the nasoenteric tube and intravenous infusion in a 1520 double-blind placebo-controlled manner. Two weeks later, the subjects were switched to the alternative route of administration of the active drug.

Blood samples were taken before dosing and at 0.08, 0.17, 0.33, 0.66, 1, 2, 4, 8, 12, 24, 48, 72 and 9 h after dosing. Serum azithromycin concentrations were determined using the high-performance liquid chromatography test 1525 described by Shepard et.al; J. Chromatography, 565; 321 - 337 (1991), Total systemic exposure to azithromycin is determined by measuring the surface area with serum azithromycin concentration versus time curve (AUC) for each subject in a given group and then calculating an average AUC for the group. Cmax is the highest concentration of azithromycin reached in a subject. Tmax is the time at which 1530 Cmax is reached. Serum pharmacokinetic data for this example are presented in Table IV. In one form of this study, all subjects received an intravenous dose of 2 g azithromycin. Intravenous AUC is determined to calculate absolute duodenal and ileocecal bioaccessibilities, as described below.

before the time of dosing and taking blood samples, each subject completed a questionnaire, 1535, which consisted of a series of "visual analogous scales" in which the subject was asked to falsify quantitatively, on a scale from O to 10, the severity of certain potential side effects.

The subjects were instructed that 0 indicates an absent effect and “10 indicates the worst possible effect. 1540

Subjects were trained to interpolate between 0 and 10 for moderate side effects.

A total of 11 subjects completed this study: 5 with duodenal and ileocecal dosing. For four side effects, the evaluation at 14 temporary points obtained 616 individual assessments of the analog-visual scale. 1545

The analysis of the side effects from the visual analog scale was performed in two forms. In the first form. Table V, the analysis focused on the general incidence of side effects of a particular type. For each type of side effect (eg, abdominal pain), Table V shows the number of subjects who reported a score> 1 at any time during the 96-hour post-dosing period and the number of 1550 subjects who reported a score> 4 at any time during the 95 h after dosing. This analysis assumes that all scores> 1 represent the appearance of a real side effect, however, mild or severe. A score> 4 is supposed to reflect the appearance of a moderate to severe side effect.

In the second form (Table VI), the analysis reflects the overall quantity and duration 1555

RO 114740 Bl side effects. For a particular side effect (eg, abdominal pain) in a particular subject, all visual analogue scores (over the 96-fold post-dosing period) are summed to give a "cumulative score" over the entire period. evaluation. The “cumulative scores” for all treatment group members are summed and divided by the number of subjects in a treatment group to give an Average Cumulative Score. The scale of this Average Cumulative Score does not correspond to the initial scale O ... 10, because it reflects the sum of all non-zero scores throughout the entire evaluation period. Table VI presents the Average Cumulative scores for abdominal pain, nausea, regurgitation and abdominal cramps.

Table VI shows that absorption of a dose of abdominal azithromycin solution is rapid, as evidenced by a short Tmax, 0.3 h, and a higher Gmax. The ileocecal dosing results in slower absorption, with a measured Tmax (1.39 h), which is similar to the Tmax observed for oral capsule dosages in Example 1 (1.3 h, Table I). Total systemic drug exposure (AUC) is 15% lower in ileocecal dosing compared to duodenal dosing. When compared with intravenous dosing in the same subjects, bioaccessibility for duodenal dosing is 43.8% and bioaccessibility for ileocecal dosing is 39.1%; where bioaccessibility, for example duodenal bioaccessibility, is defined as AUCduodenal/ AUC |V x 100. The duodenal bioaccessibility of the azithromycin solution is slightly higher than the oral bioaccessibility of an azithromycin capsule, which is typically about 38%. The ileocecal bioaccessibility of the azithromycin solution is similar to that of an orally dosed capsule.

Table V (same format as Table II) shows that the incidence of gastrointestinal side effects is generally higher for duodenal dosing than for ileocecal dosing. Table VI shows that the overall severity of gastrointestinal side effects is higher for duodenal dosing than for dosing. ileocecal.

Table IV

The pharmacokinetics of azithromycin for a dose of 2 g in solution administered in the duodenal (n = 5) or ileocecal (n = 6) region of the small intestine through the nasoenteric tube (mean values).

<td>TREATMENT</td><td>Cmax (Mg / ml)</td><td>Tmax (hours)</td><td>AUC.</td>

<td>duodenal</td><td> 3,24</td><td> 0,3</td><td> 17,0</td>

<td>lleocecal</td><td> 0,77</td><td> 1,39</td><td> 14,5</td>

Table V

The incidence of visual analogue scale scores exceeding 1 or 4 at any time during the 96-hour post-dosing evaluation period, for side effects: abdominal pain, nausea, regurgitation and abdominal cramps.

Compare the direct administration of 2 g of azithromycin in the duodenal (n = 5) and ileocecal [n = 6) regions of the small intestine.

<td></td><td colspan="2">Pain abdominal</td><td colspan="2">Nausea</td><td colspan="2">regurgitation</td><td colspan="2">Cramps abdominal</td>

<td>Treatment</td><td> > 1</td><td> > 4</td><td> > 1</td><td> > 4</td><td> > 1</td><td> > 4</td><td> > 1</td><td> > 4</td>

<td>duodenal</td><td> 4/5</td><td> 0/5</td><td> 2/5</td><td> 1/5</td><td> 3/5</td><td> 0/5</td><td> 5/5</td><td> 0/5</td>

<td>lleocecal</td><td> 2/6</td><td> 0/6</td><td> 2/6</td><td> 0/6</td><td> 9/6</td><td> 0/6</td><td> 2/6</td><td> 0/6</td>

RO 114740 Bl

Table VI

Average cumulative score

Average Cumulative Average Visual Analog Scale Data for Side Effects: Abdominal Pain, Nausea, Regurgitation, and Abdominal Cramps, throughout 1605 over the entire 96-h evaluation period after dosing. See the text for explanations of the average cumulative score. Dosage of a solution of 2 g azithromycin is done directly in the duodenal and ileocecal regions of the small intestine.

<td>Treatment</td><td>n *</td><td>Abdominal pain</td><td>Nausea</td><td>regurgitation</td><td>Abdominal cramps</td>

<td>duodenal</td><td> 5</td><td> 13,4</td><td> 11,6</td><td> 7,2</td><td> 13,2</td>

<td>lleocecal</td><td> 6</td><td> 2,7</td><td> 2,0</td><td> 0</td><td> 3,3</td>

Test number 3: This test shows that when azithromycin is administered intravenously, the incidence and severity of gastrointestinal effects are low, 1615 compared to the incidence and severity of side effects resulting from oral dosing at an equivalent dose. These observations support the conclusion that the side effects of orally administered azithromycin are mediated locally in the gastrointestinal tract by direct contact between the oral dosage drug and the intestinal wall and do not result primarily from side effects related to the presence of azithromycin in the systemic circulation. 1620

Healthy male subjects are divided into four groups. Group A receives a 2-hour intravenous infusion with a placebo solution (O g of azithromycin). Group B receives a 2-hour intravenous infusion with a dose of 1 g azithromycin. Group C is given an intravenous infusion with a dose of 2 g azithromycin. Group D is given an intravenous infusion with a dose of 4 g azithromycin. Based on an oral bioaccessibility 1625 of 37%, these intravenous doses of 0.1, 2 and 4 g are equivalent to oral doses of 0.2, 7, 5, 4 and 10.8 g, respectively. All subjects are dosed after a night of eating.

Blood samples are collected before dosing and at 0.25, 0.75, 1, 1.5, 2, 4, 8, 12, 18.24, 72, 96, 144, 192 and 240 h after dosing. Serum azithromycin concentrations are determined using high performance liquid chromatography as described by Sephard et.al J. Chromatography, 565: 321-337 (1991). The total systemic exposure to azithromycin is determined by measuring the area under serum azithromycin concentration versus time curve (AUC) for each subject in a given group and then calculating an average AUC for the group. Cmax 1635 is the highest serum concentration of azithromycin obtained in a subject. Tmax is the time at which Cmax is reached. Serum pharmacokinetic data for this example are presented in Table VII.

before the time of dosing and each blood test, each subject completed a questionnaire consisting of a series of "Analog and 1640 visual scales" in which the subject is asked to rank, on a scale from O to 10, the severity of certain potential side effects. The subjects are instructed that "It indicates an absent side effect and that" 10 indicates the worst possible effect. Subjects are trained to interpolate between O and 10 for moderate side effects.

This study was completed by 22 subjects: 5 with placebo, 6 with a total dose of 1,645 azithromycin, 6 with a total dose of azithromycin of 2 g and 5 with a total dose of azithromycin of 4 g. For four effects secondary evaluations at 18 time points obtained 1584 individual assessments on the analogous scale

RO 114740 Bl visual.

Data analysis of visual analog scale was done in two formats. In the first format (Table VIII), the analysis focused on the general incidence of side effects of a particular type. For each type of secondary (eg, abdominal pain), Table VIII reports the number of subjects who reported a score> 1 at any time during the 240 hours after dosing. This analysis assumes that all these scores> 1 represent the appearance of a real side effect, however mild or severe. A score> 4 is supposed to reflect the appearance of a moderate to severe side effect.

In the second format (Table IX), the analysis reflects the overall severity and duration of side effects. For a particular side effect (eg Abdominal Pain) in a particular subject, all scores of the visual analogue scale (over the 240 h post-dosing period) are summed to give the "cumulative score" over the entire evaluation time period. . Cumulative scores ”for all members of a treatment group are summed and divided by the number of subjects in the group to give an Average Cumulative Score. The scale of this average Cumulative Score does not correspond to the scale from O to 10 initial, because it reflects the sum of all scores other than O over the entire evaluation period. Table IX presents the Average Cumulative Scores. For abdominal pain, nausea, regurgitation and abdominal cramps.

Table VII presents the pharmacokinetic data for intravenous dosing of azithromycin in this example. Comparison with Table I in Example 1 shows that intravenous dosing of azithromycin results in systemic exposure than oral dosing does. For example, an intravenous 2 g dose of azithromycin gives an AUC of 45.6, ^ gh / ml (Table VII), while an oral dose of 2 g gives an AUC of 18.8 ^ gh / ml (Table I ). Thus, to compare the gastrointestinal side effects of oral and intravenous azithromycin administration, it is generally appropriate to compare an oral dose of 2 g with an intravenous dose of 1 g. In fact, systemic exposure to the drug obtained with an intravenous dose of 1 g (AUC = 23.4 µg / ml) is greater than the systemic exposure to the drug given by a two-gram oral dose (AUC) = 18.8 µg - h / ml.

Table VIII also indicates that, at higher intravenous doses of azithromycin, for example 2 g, gastrointestinal side effects occur. An intravenous dose of azotrimycin of 2 g is equivalent to an oral dose of 5.4 g of azithromycin from the point of view of equivalent systemic exposure to the drug. At a higher intravenous dose, an increased incidence of the side effect is observed. While side effects G and I can be highlighted by high intravenous doses, these observations agree with the finding that the side effects Gl of azithromycin are mediated by direct drug contact with the intestinal wall in the light, based on the following additional study: In twelve subjects with ileostomy is given an IV infusion with 500 mg azithromycin for 1 h. Serum is collected before the dose and at 0.17, 0.33, 0.5, 1.2, 4.8, 12.24, 48.72, 96.120 and 144 h after the initiation of the infusion. In addition, the contents of the ileostomic sacs are collected at the following intervals: 12 h before dose, O ... 6 after dose, 6 ... 12 h after dose and 12 ... 24 h after dose. The azithromycin concentrations in the serum and the ileostomy fluid are determined. In the 24 hours following an IV dose of azithromycin, 13% of the dose is recovered intact in the ileostomy fluid, indicating that IV administered azithromycin penetrates through the lumen of the small intestine, probably through biliary excretion and / or transintestinal excretion. Thus, it is not surprising that doses

Large intravenous azithromycin Bl may cause gastrointestinal side effects, as a portion of the IV dose is distributed between the lumen and the small intestine.

Table IX demonstrates that the overall severity of gastrointestinal side effects resulting from an intravenous dose of 1, □ g is low and is even lower than that observed for an oral dose of 2 g (compared to Table III). Based on an oral bioaccessibility of 37%, these intravenous doses are equivalent to oral doses of 0.2, 7.5, 4 and 10.8 g, respectively. At higher IV doses (eg, 4 g), gastrointestinal side effects. However, it is possible that these 1705 Gl side effects are due to the distribution of dose 4 in the lumen of the small intestine, as clearly demonstrated in the ileostomy study above.

Table VII

Pharmacokinetics of azithromycin: for an infusion of 2 ha at doses of 1 g (n

<td>Total IV dose</td><td>Equivalent oral dose * (g)</td><td>Cmax ^ g / ml)</td><td>Tmax (hours)</td><td>AUC0-inf / zg-hour / ml</td>

* Calculated by dividing the dose of 4 by the bioaccessibility of azithromycin (0.37) 1715

Table VIII

The incidence of the Visual Analog Scale exceeding 1 or 4 at any time during the 240 hours of the post-dosing period, for the side effects: pain

Compare intravenous doses of O g (placebo), 1 g, 2 g and 4 g azithromycin 1720 infused over a period of 2 hours. Based on 37% oral accessibility, these intravenous doses are equivalent to the oral doses of 0.2 , 7 and 5.4 g, respectively. The reported incidences for doses of 1.0, 2.0 and 4.0 g were not corrected for placebo effects.

1725

<td></td><td colspan="2">Abdominal pain</td><td colspan="2">Nausea</td><td colspan="2">regurgitation</td><td colspan="2">Abdominal cramps</td>

Table IX

Average cumulative score

Average cumulative visual analogue scale data for side effects: 1735 abdominal pain, nausea, regurgitation and abdominal cramps, over the entire 240 h post-dose evaluation period. See text for explanation of "average cumulative score", azithromycin is given intravenously in a total dose of 1 g, 2 g or 4 g O (placebo). Based on a 37% oral bioavailability, these intravenous doses are equivalent to doses oral doses of 0.2, 7.5, 4 and 10.8 g, respectively. 1740

RO 114740 Bl

Mean cumulative scores for 1.0, 2.0, and 4.0 g were not corrected for placebo effects.

<td>Dose IV (g)</td><td>n *</td><td>Abdominal pain</td><td>Nausea</td><td>regurgitation</td><td>Abdominal cramps</td>

* Number of subjects for which the media was made

EXAMPLE 1 This example illustrates a composition of a moderate-release membrane system with sustained release of azithromycin in the form of multiple particles, which releases azithromycin in varying amounts, depending on the film thickness of a diffusion barrier coating. This process comprises (1) the preparation of azithromycin multiple particle cores; and (2), applying diffusion barrier coating over the cores. This example also illustrates the sustained release in vitro assay test procedure for evaluating the breakdown and release of azithromycin from the dosage form.

Multiple particle cores containing azithromycin are prepared by mixing azithromycin with microcrystalline cellulose (AvicelR PH101, FMC Corp., Philadelphia, PA = in relative quantities of 95: 5 [g [g], mass-moistening the mixture in a Hobart mixer with water equivalent to approximately 27% by weight of the mixture, extruding the wet mass through a perforated plate ( extruder Luwa EXKS-1, Fuji Paudal Co., Osaka Japan), spheronizing the extrudate (Luwa EXKS-1 device, Fiji Paudal, co., Osaka Japan), spheronizing the extrudate (Luwa QJ-230 device, Fuji Paudal Co.) and drying the final cores which are about 1 mm in diameter. The final granules with sustained release are obtained by coating the core particles with a plasticized ethyl cellulose dispersion (Surelease).R, Colorcon, West Point, PA, commonly applied in a concentration of 15% solids). For example, 4A (a batch size of about 100 g), the final coating is conducted in a Wurster fluid bed cover with bottom spray (Aeromatic Strea-1, Niro Inc., Bubendorf, Switzerland). For example 4B, 4C and 4D (batch sizes of about 1 kg), the final coating is conducted in a rotary granulator (CF-360 granulator, Freund Indust., Tokyo Japan). The amount of coverage applied is varied, in order to obtain different behaviors of the disintegration rate. Example 4A has an additional 2% Opadry coverageR over 13% coverage with SureleaseR.

Finished sustained-release multiple particles are tested using the previously described in vitro sustained-release assay procedure, and the results are presented in Table 4-1. Example 4D is tested in the form of 1,500 mgA microparticles and Examples 4a to 4C are tested in the form of 250 mgA microparticles in a capsule. Examples 4a to 4D meet the in vitro sustained release disaggregation criterion and are variants of sustained release which are within the scope of the invention.

RO 114740 Bl

1785

Table 4-1

<td colspan="3">Disaggregation criterion</td><td> 0(3.25</td><td>sheep</td><td> 02</td><td>a4</td><td>a6</td>

<td colspan="3">With Sustained Release</td><td> <200</td><td> <500</td><td> <1000</td><td> <1500</td><td> <2000</td>

<td colspan="8">In vitro</td>

<td colspan="2">Coating with</td><td> 0(3.25</td><td>sheep</td><td>Bone</td><td> 04</td><td>a6</td><td>Initial dose</td>

<td>Example</td><td>SureleaseR (%]</td><td>mgA</td><td>mgA</td><td>mgA</td><td>mgA</td><td>mgA</td><td>tested (M.qA)</td>

<td colspan="8">2.0 Opadry "</td>

1790

1795

Test 4: This test illustrates that the use of temporal criteria, together with the in vitro disaggregation test, leads to the design of a dosage form, such as a pouch, which has a desired disintegration profile.

Using the in vitro disaggregation test, as shown in Example 4B, 1800 is desired to obtain a release dosage form, a scalar maximum m.gA is calculated for the multiple particles for each temporal criterion and shown in Table 5-1.

Table 5-1

Maximum dose escalated 1805

<td colspan="2">Example 4B</td><td>The maximum scaled in mqA</td>

<td>Temporary criterion</td><td>The results of Dezaqreqarii</td><td>For Multiple Particles</td>

Each maximum scalar value is calculated by scaling the results from example 4B, to obtain the highest value that corresponds to the temporal criterion 1815. For example, the maximum scalar value at 15 min (12500 mgAm) is calculated as 200 mgA x (250 mgAm + 4 mgA), where 250 mgAm corresponds to the initial dose tested. The maximum value scaled to 2 h (2212 mgAm) is similarly calculated as 1000 mgA x (250 mgAm +113 mgA).

Table 5-1 indicates that the maximum scaled dose in Example 4B of multiple particles 1820 to be used to obtain a dosage form that is part of this invention is 2212 mgAm, the minimum of the maximum calculated values.

Maximum scaled doses are also calculated using the time criterion,

EN 114740 Bl together with the data in Examples 4a, 4C and 4D, in the same manner as above. Table 5-2 summarizes the maximum dose escalation for the examples from 4A to 4D.

Table 5-2

Maximum dose escalated

<td rowspan="2"></td><td>Maximum Dose Scaling for Multiple Particles with Release</td>

<td>supported</td>

<td>Example</td><td>supported</td>

Test 5: This test illustrates that the use of the weight criterion, together with the in vitro disaggregation test, leads to the design of suitable dosage forms for a given weight animal. The data in Example 4B are used to calculate the minimum body weight for each weight criterion.

Table 6-1

The maximum dose for a given body weight

<td></td><td>Example B</td><td>Maximum Scaled mgA Multiple Particles</td>

<td>Weight criterion</td><td>The results of Dezaqreqarii</td><td>For a Body Weight of 100 Kq</td>

Each maximum scaled value is calculated by scaling the results of Example 4B for an animal weight of 100 kg, to obtain the highest value that corresponds to the corresponding weight criterion. For example, the maximum value scaled at 15 min (25000 mgAm] is calculated as: 4 mg / kgx100 kg x (250 mgAm +4 mgA], where 250 mgAm corresponds to the initial dose tested. The maximum value scaled at 2 h is similarly 20 mg / kgx100 kgx (25O mgAm + 113 mgA).

Table 6-1 indicates that the maximum scaled dose of the multiple particle to be used to obtain dosage forms that fall within the scope of the invention is 4,425 mgAm, the minimum dose of the calculated scaled values.

In the same way as above, table 6-2 lists the maximum calculated quantities of sustained release multiple particles for Examples 4A, 4B, 4C and 4D to be used for a given body weight of 100 kg, to obtain shapes.

The dosage block which is part of the field of the invention.

Table 6-2 ____________The maximum dose to be released for a given body weight 18 65

<td></td><td>Maximum Dose of Multiple Particles with Release</td>

<td>Example</td><td>Supported at 100 kcj Body Weight</td>

Test © This test illustrates that the use of the weight criterion, together with the in vitro disaggregation test, leads to the determination of the minimum weight of the animal to be used with the sustained release dosage form. 1875

With the multiple particles in Example 4B, a sustained release bag containing 2ODO mgAm is made. A minimum body weight was calculated for the use of this bag, according to each of the weight criteria.

Table 7-1 1880

Minimum body weights

<td colspan="2">Disaggregation results</td><td>Minimum Scaled Body Weight</td>

<td>Weight criterion</td><td>From Example 4 B</td><td>For use with 2000 mqAm</td>

Each scaled minimum weight is calculated by using the data from 1890 example 4B and assuming a dose of 2000 mgAm to calculate the lowest body weight that matches each individual weight criterion. For example, the value scaled to 15 min (8 kg) is calculated as: 2000 mgAm x [4 mgA / 250 mgAm) + (4 mgA / kg). The maximum value scaled to 2 h (45.2 kg) is calculated similarly as: 2000 mgAm x (113 mgA / 250 mgAm) + (20 mgA / kg).

Table 7-1 indicates that the minimum body weight to which a bag containing 2000 mgAm from Example 4B should be administered is 45.2 kg, the maximum scaled body weight.

The average body weights were also calculated, using the weight criterion, together with the disaggregation data from examples 4A, 40 and 4D, in the same way as above. Table 7-2 shows the minimum body weights for total doses of 25 mgAm and 2000 mgAm in Examples 4A4B, 40 and 4D, to obtain a dosage that is part of the scope of the invention.

RO 114740 Bl

Table 7-2

Minimum body weight at a given dose

<td>Example</td><td>Minimum Body Weight For Multiple Particles with Sustained Release of 250 sqm</td><td>Minimum Body Weight for Multiple Particles with Sustained Release of 2000 mo</td>

Example 2.This example illustrates a composition and a process for obtaining moderate, sustained-release membrane systems of azithromycin in the form of multiple particles, at different speeds, depending on the thickness of a diffusion barrier coating. The process comprises applying a diffusion barrier coating directly on the azithromycin multiple particles. This example further evaluates the release profile by the in vitro sustained release assay.

Multiple particles containing azithromycin are prepared by loading 1000 g of azithromycin compound directly into a rotary granulator / film (Freund CF-360 granulator). Then, on the bed rotating with azithromycin particles, a coating suspension of ethyl cellulose diluted to 15% solids is sprayed. During spray application, both agglomeration of the azithromycin particles into larger particles takes place and the coating of these agglomerates with the diffusion barrier membrane. In some examples, a water-soluble coating of Opadry (usually diluted to 10% solids for spraying) was applied over the barrier membrane.

Finished sustained-release multiple particles were tested using the in vitro sustained-release assay procedure described above, and the results are presented in Table 8-1. Examples 8A to 8G meet the sustained release criterion by in vitro disaggregation and sustained release variants of the invention.

Table 8-1

<td colspan="3">Disaggregation criterion</td><td>Qd 25</td><td>Qi</td><td>q2</td><td> □4</td><td>Q6</td>

<td colspan="3">With Sustained Release</td><td> <200</td><td> <500</td><td> <1000</td><td> <1500</td><td> <2000</td>

<td colspan="8">In vitro Example</td>

<td>Sun. ie somewhere apart (fzg)</td><td>Coating with</td><td>Qq.25</td><td>Qi</td><td>q2</td><td> □4</td><td>q6</td><td>Initial dose</td>

RO 114740 Bl

Table B-1 (continued)

950

<td></td><td>SureleaseR [%1</td><td>MQA</td><td>MQA</td><td>MQA</td><td>MQA</td><td>MQA</td><td>Tested mqAl</td>

<td colspan="8">0.5 OpadryR</td>

<td colspan="8">1.6 Opadr /</td>

<td>BFGUzg)</td><td> 35,6</td><td> —</td><td> —</td><td> 32</td><td> —</td><td> 77</td><td> 166</td>

<td colspan="8">0.7 OpadryR</td>

955

960

Examples 8B, 8C and 8G have a protective coating to Example 8B, 0.5% Opadry coverageR over 16.6% coverage was made with SureleaseR.

Example 3.This example illustrates a composition and process for obtaining multiple sustained release particles, which release azithromycin at different speeds, depending on the thickness of the diffusion barrier coating. The process comprises (1) the preparation of azithromycin-coated multi-particle cores, and (2) the application of a diffusion barrier as a coating over the cores. This example further evaluates the multiple particle release profile.

Azithromycin-containing multiple particle cores are prepared using a fluid bed processor with an inserted rotor [Glatt GPCG-5 from Glatt Air Techniques, Ramsey, NJ). The rotating vessel is initially loaded with 2500 g of azithromycin and over the rotating bed, a solution of plasticized hydroxypropyl binder (Opardy) is tangentially sprayed.R) (10% solids concentration), until an average particle size of 250 / xg is obtained. Then, a coating suspension with plasticized ethyl cellulose (Surelease) is sprayed over the particle cores.R), diluted to 15% solids. A first batch of coated particles was made with 40% coverage. Then, a second batch was made with 50% coverage.

The finished sustained release granules are tested using the in vitro assay procedure of the sustained release dosage described above, and the results are presented in Table 9-1. Examples 9A and 9B are variants of the sustained release of this invention.

1965

1970

1975

1980

1985

RO 114740 Bl

<td colspan="3">Disaggregation criterion</td><td>Qd.25</td><td>Qi</td><td>q2</td><td>q4</td><td>qb</td>

<td colspan="3">With Sustained Release</td><td> <200</td><td> <500</td><td> <1000</td><td> <1500</td><td> <2000</td>

<td colspan="8">In vitro</td>

<td colspan="2">Coating with</td><td> ^0.25</td><td></td><td> 02</td><td>q4</td><td>q6</td><td>Initial dose</td>

<td>Example</td><td>SureleaseR [%1</td><td>MQA</td><td>MQA</td><td>MQA</td><td>MQA</td><td>MQA</td><td>tested [MgA]</td>

This test illustrates that using the sustained release disaggregation criterion, together with the in vitro disaggregation test, results in the design of a dosage form having a desired release configuration.

As in Test 4, the data in Example 9, Example 3 are used together with the time criterion to calculate the maximum scaled mgAm, corresponding to both Examples 9A and 9B, which should be used to obtain a dosage form according to the invention. Table 10-1 summarizes the maximum dose escalation for examples 9A and 9B.

Table 10-1

Maximum dose escalated

<td rowspan="2"></td><td>Maximum Dose Climbing for</td>

<td>Multiple Particles with Release</td>

<td>Example</td><td>supported</td>

Test 6: This test illustrates that the use of the weight criterion, together with the in vitro test, leads to the design of an ordinary dosage form suitable for a given weight animal.

The data in examples 9A and 9b are used to calculate, as in example 6, the maximum dose that should be given to an animal of 100 kg. Table 11-1 lists the maximum quantities of multiple release multiple particles for examples 9A and 9B that should be used for a given body weight of 100 kg, according to the breakdown criterion and the body weight criterion, to obtain a particle dosage form. multiple embodiments of the invention.

<td rowspan="2">Example</td><td>Maximum Dose of Multiple Particles with Sustained Release for one</td>

<td>Body weight of 100 kq</td>

Test 7: This test illustrates that the use of the weight criterion, together with the breakdown test, leads to the determination of the minimum body weight at which it would

EN 114740 A sustained-release dosage form should be used.

The minimum body weights are calculated in the same way as in test 6. Table 12-1 shows the minimum body weights for the total doses of 250 mgAm and 1000 mgAm from examples 9A and 9B.

2030

Table 12-1

Minimum body weight at a given dose

<td>Example</td><td>Minimum Body Weight for Multiple Particles with Sustained Release of 250 mo</td><td>Minimum Body Weight for Multiple Particles with Sustained Release of 2000 sqm</td>

Example 4.This example illustrates the composition and process for obtaining multiple sustained-release azithromycin particles, in the form of a moderate reservoir, with phase reversing membrane. The process comprises direct application on the multiple particles containing azithromycin of a phase reversed membrane coating. This example further evaluates the multiple release profile of the multiple release particles.

Multiple particles containing azithromycin are prepared by loading 1000 g of particles containing azithromycin directly into a rotary film granulator (Freund CF-360 granulator). The rotating particle bed is sprayed with a solution containing 7.5% ethyl cellulose Dow Ethocel s-10, dow chemical, Midland, Ml), 2.5% polyethylene glycol (PEG 3350), 10% isopropanol, 22% ethanol, 54% acetone and 45 water. When 300 g of solids from the coating solution were applied to the initial batch of 1000 g, a multiple-release multiple particle is formed, with an average particle size of about 450 μηη.

Finished sustained release multiple particle is tested using the sustained release assay in vitro testing procedure. The results are presented in table 13-1. Example 13A meets the in vitro release criterion and is a sustained release variant of the invention.

2040

2045

2050

2055

Table 13-1

<td colspan="3">Disaggregation criterion</td><td> ^0,25</td><td>gb</td><td></td><td>q4</td><td>qb</td>

<td colspan="3">With Sustained Release</td><td> <200</td><td> <500</td><td> <1000</td><td> <1500</td><td> ±2000</td>

<td colspan="8">In vitro</td>

<td colspan="2">Coating with</td><td> ^0.25</td><td> □1</td><td>Qs</td><td>Q4</td><td>q6</td><td>Initial dose</td>

<td>Example</td><td>Solid [%)</td><td>MQA</td><td>MQA</td><td>MQA</td><td>MQA</td><td>MQA</td><td>Tested mqAl</td>

<td>13A</td><td> 23,1</td><td> —</td><td> —</td><td> 160</td><td> —</td><td> 236</td><td>Capsule of 250 mgA</td>

2060

Example 5.This example illustrates a process for obtaining a sustained release tablet containing azithromycin with hydrophilic matrix which 2065 releases azithromycin at different speeds, depending on their composition. The process comprises (1), the mixing of all components, except for stearate

RO 114740 Magnesium bl; (2), seating and re-mixing the same components; (3), adding and mixing magnesium stearate and compressing the final mixture into tablets.

In batches of 150 g, azithromycin is stirred for about 15 minutes in a suitable large vessel, with all components, except for magnesium stearate, using a Tubula stirring system (Basel, Switzerland). Then, the mixture is passed through a 40 mesh sieve and stirred again for ten minutes. Then, magnesium stearate is added and the mixture is stirred for five minutes. Using a Manesty F type press (Manestry Machines, Liverpool, England), the final mixture is compressed to Examples 14A to 14 1, or standard 3/4 inch flat faces for Examples 14 J and 14K. A summary of the compositions from 14 A to 14 K is shown in table 14-1.

Table 14-1

Tablet compositions with sustained release with hydrophilic matrix

<td></td><td>Compound</td><td> %</td><td> %</td><td> %</td><td>Cellulose</td><td>Stearate of</td>

<td>Example</td><td>azithromycin</td><td>Lactose</td><td>HPMC1</td><td>PVPp</td><td>microcrystalline</td><td>Maqneziu</td>

1hpmc stands for hydroxypropyl methylcellulose. All examples use Dow Methocel K4M-CR (Dow Chemical, Midland, Ml)2PVP stands for polyvinylpyrrolidone, Kolloidon (BASH corp., Parsippany, NJ) 3The microcrystalline cellulose used is AvicelR PH-102 (FMC Corp).

Finished sustained release tablets are tested using the in vitro sustained release assay procedure and the results are presented in Table 14-2. Examples 14 A to 14 K meet the disaggregation criterion and are sustained release variants of this invention.

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Table 14-2 Supported release tablet compositions with hydrophilic matrix

<td>Disaggregation criterion</td><td> ^0.25</td><td> □1</td><td> □2</td><td>Qa</td><td colspan="2">aB</td>

<td>With Sustained Release</td><td> <200</td><td> <500</td><td> <1000</td><td> <1500</td><td colspan="2"> <2000</td>

<td colspan="7">In vitro</td>

<td></td><td>Qo.25</td><td>Qi</td><td> 02</td><td>□ a</td><td>a6</td><td>Initial dose</td>

<td>Example</td><td>mgA</td><td>mgA</td><td>mgA</td><td>mgA</td><td>mgA</td><td>Tested (mgA)</td>

<td>8A</td><td> —</td><td> 37</td><td> —</td><td> 69</td><td> 85</td><td>Tablet of 250 mgAm</td>

<td>8B</td><td> —</td><td> 42</td><td> —</td><td> 92</td><td> 111</td><td>Tablet of 250 mgAm</td>

<td>8C</td><td> —</td><td> —</td><td> 69</td><td> 105</td><td> 124</td><td>Tablet of 250 mgAm</td>

<td>8D</td><td></td><td> —</td><td> 113</td><td> 158</td><td> 200</td><td>Tablet of 250 mgAm</td>

<td>8E</td><td> —</td><td> 148</td><td> 175</td><td> 236</td><td> 249</td><td>Tablet of 250 mgAm</td>

<td>8F</td><td> —</td><td> —</td><td> 52</td><td> —</td><td> 94</td><td>Tablet of 250 mgAm</td>

<td>8G</td><td> —</td><td> —</td><td> 51</td><td> —</td><td> 91</td><td>Tablet of 250 mgAm</td>

<td>8H</td><td> —</td><td> —</td><td> 167</td><td> 218</td><td> 233</td><td>Tablet of 250 mgAm</td>

<td>8I</td><td> —</td><td> —</td><td> 109</td><td> 135</td><td> 150</td><td>Tablet of 250 mgAm</td>

<td>8J</td><td> 80</td><td> 201</td><td> 276</td><td> 413</td><td> 481</td><td>1000 mgAm tablet</td>

<td>8K</td><td> 88</td><td> 144</td><td> 183</td><td> 245</td><td> 290</td><td>1000 mgAm tablet</td>

EXAMPLE 6 This example illustrates a composition and process for obtaining multiple particles for use in making sustained release dosage forms, designed to deliver azithromycin 2130 predominantly beneath the duodenum. The process comprises (1), the preparation of coated cores with multiple azithromycin particles; [2], applying a first sustained release coating over the cores and (3), applying a second delayed release, pH sensitive, over the first coating. This example further illustrates the in vitro release test procedure for evaluating the breakdown of dosage form 2135 and the release of azithromycin.

RO 114740 Bl

Multiple particle cores containing the drug are prepared using a fluidized bed processor with inserted rotor (Model GPCG-5). The rotor vessel is initially loaded with 2500 g of azithromycin and over the rotating bed a solution of laminated hydroxypropyl methylcellulose (Opadry) is sprayed.9) (10% solids concentration), until an average particle size of about 250 / zm is reached. Then, a coating suspension diluted to 15% solids with plasticized ethyl cellulose (Surelease) is sprayed over the particle cores.R). A first batch of coated particles is prepared, with a total coverage of 30%. Then, the second batch is prepared with 40% coverage. Finally, both batches of multiple particles are coated with a delayed release film in a rotary fluid bed processor (Glatt Model GOCEGE1 J. until a desired coverage end point is obtained (indicated in% in table 15-1) Delayed release film is a suspension containing 12.3% methacrylic acid copolymers (EudragitR-L 30 D-559, 6.2% talc, 1.5% triethyl citrate and 80% water). At the first batch that was covered with 40% Surelease coverage9, 20% delayed release overlay is applied. The second batch was covered by 30% SureleaseR, 33.7% overcoat is applied with a delayed release. The final product is composed of multiple late-release particles, with particles having an average size of about 300 μνπ.

The results of the delayed release disaggregation are presented in table 15 and include the disaggregation test criterion. Example 15A is a comparative example of an immediate release capsule, which is outside the scope and scope of the invention. Examples 15B and 15C are variants of the delayed release, prepared with the multiple particles in these examples.

Table 15

<td colspan="3">Delayed Dosing Test</td><td> ^0.25</td><td>Qq.5</td>

<td colspan="2">Disaggregation criterion</td><td></td><td> 5 10%</td><td>Qq 25 + 1 0%</td>

<td></td><td>Composition</td><td>θΟ, Ξ5</td><td> ^0.5</td><td>Initial dose</td>

<td>Example</td><td>Formulation</td><td>(Acidl stage</td><td>Stamp Stadium]</td><td>(MgAm)</td>

<td>15 A.</td><td>Immediate Release Capsule</td><td> 81%</td><td> 98%</td><td> 250</td>

<td>15B</td><td>Multiple particles with Delayed Sustained Release</td><td></td><td></td><td></td>

<td></td><td>43.6% azithromycin</td><td></td><td></td><td></td>

<td></td><td>4.4% Solid OpadryR</td><td></td><td></td><td></td>

<td></td><td>32.0% Solid SureleaseR</td><td></td><td></td><td></td>

<td></td><td>12.3 Solid EudragitR</td><td></td><td></td><td></td>

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2175

Table 15 [continued]

<td></td><td>1.5% Triethyl citrate</td><td></td><td></td><td></td>

<td>15C</td><td>Multiple particles with sustained + delayed release</td><td></td><td></td><td></td>

<td></td><td>42.2% azithromycin</td><td></td><td></td><td></td>

<td></td><td>4.2% Solid 0padryR</td><td></td><td></td><td></td>

<td></td><td>19.9% Solid SureleaseR</td><td></td><td></td><td></td>

<td></td><td>20.8% Solid Eudragit "</td><td></td><td></td><td></td>

<td></td><td>2.5% Triethyl citrate</td><td></td><td></td><td></td>

2180

2185

Example 7. This example illustrates a composition and process for obtaining sustained-release azithromycin tablets, hydrophobic matrix, which release azithromycin at different speeds depending on the extent of the surface coating film with a water-insoluble polymeric barrier material, as well as the core composition. tablet with hydrophobic matrix. 2190

Tablet cores are first obtained by shaking (Turbula System), in a mortar of suitable size, about 15 minutes, of the following: 105 g azithromycin, 15 g hydroxypropyl, methyl cellulose (HPMC, Dow, MethocelR, E4M-CR) and 27.75 g microcrystalline cellulose (Avicel Ph-102, FMC Corp.]. The resulting mixture is then passed through a 40 mesh sieve and stirred for a further ten minutes. 25 g of magnesium stearate and the mixture is stirred for five minutes Using a Manesty F type press, fitted with 13/32 inch standard round concave (SRC) punches, the final mixture is compressed into tablet cores.

Then the barrier insoluble polymeric material is prepared by adding 159 g HPMC (Dow MethocelR K100LV premium CR) in a Hobart mixer. During 2200 mixing at medium speed, add 27 g of castor oil slowly and continue stirring for a further 15 min. In a separate container, prepare a solution of ethyl cellulose by slowly adding to 10 g of ethyl cellulose (Dow EthocelR S10) and 190 g ethanol, with stirring. After ethyl cellulose enters the solution, the 200 g of ethyl cellulose solution is added slowly to the Hobart mixer and the contents are mixed for 15 2205 min. The resulting wet mass is spread over a polyethylene film-coated tray and dried in a dryer with hot air ventilation at 50 ° C for four hours. After drying, 78 g of dry mass is forced through a 25 mesh screen and collected in a container. 2 g of magnesium stearate and 1 g of colloidal silicon dioxide are added to the container and stirred for five minutes. 2210

Using the Manesty F type press and 13/32 inch standard concave round punch (SRC), the barrier polymer material is compressed into a variety of configurations across the core of the tablet matrix. In one configuration, the core is placed

EN 114740 Bl in the punch and above the core of the tablet matrix various amounts of barrier polymer material are compressed. The finished tablets thus produced have a polymeric barrier coating above the core of the tablet matrix. In a second configuration, different amounts of barrier polymer material are placed on the mold of the punch. below the core of the matrix, as well as above the core of the matrix, and the composite is compressed into the final tablets. The finished tablets produced in this second way have a polymeric barrier film both above. And on the lower surface of the core of the tablet matrix.

In another process for obtaining hydrophilic matrix tablets, coated with polymeric barrier material, a polymeric adhesive (Epoxy-Pacth, Hysol Corp. Olean, NZ) is used and applied to various surfaces of the core of matrix tablets. The polymeric barrier coatings are applied not only on the upper surface and / or the lower surface of the core of the tablet matrix, but also on the sides of the tablet.

Example 8.This example illustrates a composition and process for obtaining delayed-release azithromycin tablets with hydrophilic matrix, which are designed to release azithromycin predominantly below the duodenum.

Tablet cores are first obtained by stirring (Turbula System) for about 15 minutes in a mortar of 150 g azithromycin, 15 g hydroxypropyl, methyl cellulose (HPMC, Dow MethocelR E4M-CR) and 27.75 g of microcrystalline cellulose (Avicel PH-102 FMC body). This mixture is then passed through a 40 mesh sieve and stirred for 10 min. Then 2.25 g of magnesium stearate is added and then the mixture is stirred for 5 min. Using a Manesty type F press provided with 13/32 inch standard concave round (SRC) punches, the final mixture is compressed into cores. tablet.

A delayed-release coating suspension containing 12.3% methacrylic acid copolymers is prepared (EudragitR L30D-55), 6.2% talc, 1.5% triethyl citrate and 80% water and applied as a 10% coating, using a HCT-30 Hi-Coater (Vector freund) device to spray the solution onto tablet matrix cores. Because the coating is soluble in environments where the pH is higher than 5.5, the tablets thus prepared release azithromycin from the cores of tablets with hydrophilic matrix below the stomach, where the pH is higher than 5.5 and the cores do so in a continuous manner, which predominantly releases azithromycin under the duodenum.

Example 9. This example illustrates a process for obtaining a sustained release osmotic tablet of azithromycin, with a two-layer core (two compartments), surrounded by a semipermeable membrane with a passage between their surfaces. One layer of the tablet core has an osmotically effective composition, which contains azithromycin, and a second layer of the tablet core contains an expanding hydrogel.

The first layer of the tablet core is prepared by mixing in the Turbula system for about 15 minutes 70 g of polyethylene oxide, which has a molecular weight of 50,000,000 (PolyoxR Coagulant), 23 g of sodium chloride and 5 g of hydroxipyl methylcellulose (Dow MethocelR E4M), in a mortar. The content is passed through a 60 mesh screen and collected in a mortar. Then, 2 g of magnesium stearate is added and the mixture is stirred for 5 minutes in a Turbula system.

The second core layer material of the tablet containing azithromycin is prepared by mixing in a Turbula system, for about 15 minutes, 50 g of azithromycin, 150 g of polyethylene oxide, which has a molecular weight of 100,000 (PolyoxRN-2O, Union carbide Corp.; Danbury, CT), and 10 g of hydroxopropyl methylcellulose (Dow MethocelRE4M), in a mortar. The content passes through a screen of 60

RO 114740 Bl mesh and is collected in a mortar. Then 4 g of magnesium stearate is added and the mixture is mixed in a Turbula system for 5 min.

To obtain a 2-layer tablet core, use a 2265 F Manesty type press with 13/32 inch standard concave round pins (SRC). First, the first material of the tablet core layer is partially compressed into the punch. Then, the second material of the tablet core layer, which contains azithromycin, is loaded onto the first layer and a full compression is applied to obtain the bistratified cores of the tablets. 2270

Prepare a coating solution with 68% methylene chloride. 28.5% methanol, 3.3% cellulose acetate (Eastman CA-398-10) and 1.7% polyethylene glycol 3350. A HCT-30 Hl-Coater (Vector-Freund) coating device is used to spray the coating solution over the bistratified cores of the tablets. Sufficient coverage is applied to form a wall around the core of the tablet about 0.006 2275 inches thick. After coating, the rotation of the coating device is reduced and the cores are dried for 5 min. The coating forms a semipermeable barrier wall around the tablet core, which is water permeable and impermeable to azithromycin and other excipients of the tablet core.

By coating, a 0.5 mm hole is mechanically drilled to expose the 2280 layer containing azithromycin to the environment.

Example 10. This example illustrates a composition and process for obtaining an osmotic tablet containing sustained-release azithromycin, which is designed with a core containing an osmotically effective composition, surrounded by a semipermeable membrane with a passage to its surface. 2285

Tablet cores are first obtained by mixing in a Turbula system, for 10 minutes, in a mortar, 30 g of azithromycin fumarate with 70 g of lactose. The content is passed through a 40 mesh screen and collected in a mortar. Then add 2 g of magnesium stearate and the mixture is stirred in the Turbula for 5 min. Using a Manesty F type press, the final mixture is compressed into 2290 tablet cores, using standard round concave (SRC) punches of 13/32. inches.

Prepare a coating solution with 68% methylene chloride, 28.5% methanol, 3.3% cellulose acetate (Eastman CA-398-10) and 0.2% polyethylene glycol 3350. An HCT coating device is used. -30 Hl-Coater (Vector-Freund), to spray the coating solution over the tablet cores. Apply a coating sufficient 2295 to form a wall around the core of the tablet about 0.006 inch thick. After coating, the rotation of the coating device is reduced and the cores are dried for five minutes. The coating forms a semipermeable barrier wall around the core of the tablet, which is permeable to water and impermeable to azithromycin, and the other excipients of the core of the tablet. 2300

Then, through the upper part of the semipermeable wall, there are mechanically drilled crossings of different diameters, from 0.008 inches to 0.020 inches, which links the outside of the tablet with the core of the tablet containing azithromycin.

Example 11. This example illustrates a composition and process for obtaining multiple particles, for use in making delayed-release 2305 dosage forms, designed to deliver azithromycin predominantly below the duodenum. The process comprises: (1) preparation of uncoated azithromycin multiple particle cores; (2), applying a first release release sustained with diffusion barrier over the cores and (3), applying a second delayed release coating pH sensitive over the first coating. The azithromycin-containing multiple particles 2310 cores are prepared by mixing the azithromycin compound with

Microcrystalline cellulose (AvicelR PH101.FMC Corp., Philadelphia, PA) in relative amounts of 95: 5 (w / w), wetting the mixture in a small Hobart serum with water, equivalent to about 27% by weight of the mixture, extruding the wet mass through a plate. perforated (Luwa EXKS-1 extruder, Fuji Paudal Co., Osaka, Japan), spheronizing the extruder (Luwa QJ-23O, Fuji Paudal Co. extruder) and drying the end cores having a diameter of about 1 mm.

Then, a bottom-spraying fluid bed Wurster processor (Glatt GPCG-1) is used to coat the multiple particles containing azithromycin uncoated with diffusion barrier coating. A plasticized ethyl cellulose suspension (Surelease) is sprayed on the core particlesR) diluted to 15% solids. Typically, a diffusion barrier of 5% to 20% is applied. The amount of diffusion barrier coating determines the rate of release of azithromycin from the uncoated cores.

Finally, a spray bed fluidized Wurster processor at the bottom is used to apply a delayed release coating over the diffusion barrier coated particles. Typically, delayed release coatings are from 25% to 50%, to be sure that the delayed release breakdown criterion is met. The delayed release coating is a suspension containing 12.3% methacrylic acid copolymers ( EudragitR L-30D-55) 6.2%, talc, 1.5% triethyl citrate and 80% water.

Because the delayed release coating is soluble in environments where the pH is higher than 5.5, the multiple particles thus prepared release azithromycin from the barrier-coated particle cores below the stomach, where the pH is higher than 5.5, and the particles do this in a sustained manner, releasing azithromycin predominantly below the duodenum.

Example 12. This example illustrates a composition and process for obtaining multiple particles, for use in making delayed-release dosage forms, designed to deliver azithromycin predominantly below the duodenum. The process comprises: (1) preparation of coated cores with multiple azithromycin particles; (2), applying a protective coating over the core of the particles and (3), applying a second pH-sensitive delayed release coating over the first coating.

Multiple particle cores containing the drug are prepared using an embedded rotor fluid bed processor (Model GPCG-1). The rotor vessel is initially loaded with 400 g of azithromycin and over the rotating bed a binder solution containing 5% poly (ethyl acrylate, methyl acrylate) (Eudragit NE-30-D), 5% hydroxypropyl methylcellulose plasticized (5%) is sprayed. OpadryR) and 90% water, until an average grain size of about 250 μνη is achieved.

A binder solution containing 5% plasticized hydroxypropyl methylcellulose (Opadry) is applied to the core particles, in the same processor with fluid bed with inserted rotor.R) until a coverage of 10% is obtained. This intermediate coating increases the adhesion to the core particles of the late release final coating.

Delayed coverage is applied (typically 15% to 50% coverage is required to meet the delayed release criterion), using the same fluid bed processor as above. Delayed coating is a suspension containing 12.3% methacrylic acid copolymers (Eudragit9 L30D56), 6.2% talc, 1.5% triethyl citrate and 80% water. The final product is a delayed-release multiple particle, with particles having an average size of about 300 μΓη.

RO 114740 Bl

Example 13. This example illustrates a composition and preparation of azithromycin granules in the form of granules and their coating with a controlled release coating. The coating can be applied in conventional equipment. The release rate of the drug from the coated granules is dependent on the amount of coating applied. The drug-containing granules are prepared by mixing 2365 azithromycin fumarate with microcrystalline cellulose (AvicelR CL611, FMC] in relative amounts of 95: 5, wetting the mass mixture in a Hobart mixer with water, until a paste is obtained, extruding the wet mass through a perforated plate (Luwa extruder) and spraying the extrudate (Luwa spheronizer). The granules thus prepared are dried and coated in a Strea -1 Wurster benchtop (size 2370 batch of 100 g). The coating solution is prepared by dissolving 36 g of cellulose acetate (Eastman CA398-10), 7.9 g of polyethylene glycol (PEG 400) and the required amount of sorbitol in a mixture of methylene chloride, methanol and water ( 15: 10: 1) sufficient to bring the polymer concentration to about 2%. The coating is applied to the fluidized bed until the desired thickness is obtained. The following compositions 2375 give a sustained release of azithromycin:

<td>Sorbitol in Coating Solution</td><td colspan="2">Coating thickness</td>

2390

EXAMPLE 14 This example illustrates a composition for preparing tablets coated with a membrane where pores appear when placed in a medium for sustained release of azithromycin.

Oval tablets containing 750 mg of azithromycin fumarate, 100 mg of sorbitol and 10 mg of magnesium stearate are prepared by compressing a 2395 powder mixture on a Carver press device. The tablets are placed on a cover plate and covered with a polymer solution containing cellulose acetate (Eastman CA 383-40) and polyethylene glycol (PEG 400) in acetone, to which impalpable lactose was added, to obtain a ratio. of CA: PEG: lactose of 40:40:20 and a total solids content of 50 g / l. The coating process is continued until 2400 tablets have received the desired amount of coating. Coatings equivalent to 10%, 15%, 20%, 25% and 30% of the weight of the tablet give successive decreases in the rate of azithromycin release.

EXAMPLE 15 This example illustrates a composition and preparation of ethylcellulose-coated tablets that release azithromycin 2405 through a central orifice.

Tablets containing 750 mg of azithromycin fumarate and 100 mg of hydroxypropyl methylcellulose (Dow Methocel K 100LV) are prepared by compressing a powder mixture on a Carver press using a round mold and punches.

RO 114740 Round blade with 1.3 cm diameter flat face, standard. The tablets are coated on a cover plate with a solution containing 10% ethyl cellulose (Dow EC S-10) in acetone and ethanol, until the applied coating reaches 20% by weight of the tablet. The coated tablets are removed from the cover and further dried at 50 ° C overnight: A 2 mm hole is drilled through the center of each tablet to obtain a sustained release dosage form.

Example 16. This example illustrates a composition and preparation of cellulose acetate-coated tablets that release azithromycin through a central orifice.

Tablets containing 750 mg of azithromycin fumarate and 100 mg of hydroxypropyl methylcellulose (Dow Methocel K100LV) are prepared by compressing a mixture of powders on a Carver press, using a round mold and 1.3 cm diameter flat-faced round punches, standard. The tablets are coated on a coating plate with a solution containing 10% cellulose acetate (Eastman 39810) in acetone, until the applied coating reaches 20% by weight of the tablet. The coated tablets are removed from the cover and then, through the center of each tablet, a 2 mm hole is drilled to result in a sustained release dosage form.

EXAMPLE 17. This example illustrates a composition and preparation of coated tablets perforated with a coating of an ethylene / vinyl acetate copolymer, which releases azithromycin through a central orifice.

Tablets containing 750 mg of azithromycin fumarate and 100 mg of hydroxypropyl methylcellulose (Dow Methocel K100LV) are prepared by compressing a mixture of powders on a Carver press, using a round mold and 1.3 cm diameter flat-faced round punches. , standard. The tablets are immersed in a solution containing 10% ethylene vinyl acetate (Aldrich Chemical Co.) in methylene chloride. The coated tablets are further dried at 50 ° C overnight. A 2 mm hole is then drilled through the center of each tablet to result in a sustained release dosage form.

Example 18. This example illustrates a composition and preparation of perforated tablets using a geometric approach to uniformize the release of azithromycin.

Tablets are prepared as in Example 26, except that tapered punches are used to obtain a tablet whose thickness increases from the center to the edges with an angle of 30 °. These tablets are completely coated by immersion in a 20% cellulose acetate solution (Eastman CA 398-10) in acetone. The tablets are allowed to air dry, then dried at 50 ° C overnight. As before, a hole is drilled through the center of the tablet to result in a sustained release dosage form.

Example 19. This example illustrates a composition and preparation of hemispherical pellets, which have an orifice in the center of the flat face.

Prior to use, azithromycin and polyethylene dihydrate powders (PEP-315, Union Carbide) are each passed through a 60 mesh screen. The following mixtures are prepared:

azithromycin

3g g

polyethylene

5g 4 g

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Each mixture is prepared by mixing the powders for 5 min 2460 in a Turbula mixer. Then, an aliquot of each mixture is placed in a metal mold in the form of a hollow cylinder, which has a round bottom. The radius of curvature of the bottom of the mold is equal to that of the cylindrical section. (The mold is separated in two halves along the axis of the cylinder, to allow the compacting to be removed).

Two different sized molds are used to obtain different doses: 0 2465 0.5 cm radius is loaded with 260 mg of mixture, resulting in pellets containing 78, 104, 130, 156 and 182 mg of drug, for the mixtures described above. A mold with a radius of 1.0 cm is loaded with 2100 mg of mixture, resulting in pellets containing 630, 840, 1050, 1260 and 1470 mg of drug, for the mixtures described above. The charged mold is placed 2470 in an oven at 150 ° C for 30 minutes. After heating, the mixtures are compressed into the mold by inserting a metal piston, which fits in securely. The piston is removed and the mold is allowed to cool for 20 minutes at room temperature. The disassembled die and the hemispherical pellets containing the drug are removed and cleaned with a scalpel to remove any uneven edges. 2475 The hemispherical pellets are placed face down on a plate and covered with melted paraffin. The resulting paraffin block is removed and cut into sections, each section containing a pellet. The exposed face of each pellet is further covered with molten paraffin. After the paraffin coating has solidified, the coating is drilled in the center of the flat face of the hemisphere. The resulting hemispherical pellets show a sustained release of azithromycin 2480. These pellets can be used as such or more pellets can be placed in gelatin capsules to form high dose units for dosing in humans or animals. Four of the 1 cm radius pellets, of this example, each containing 1470 mg of azithromycin, are placed in a capsule with an internal diameter of 2 cm and a length of 4 cm, to obtain a capsule that contains 2485 mg of 4880 mg. of azithromycin.

Example 20. This example illustrates a composition and preparation of cylindrical tablets or coated boluses, which release azithromycin through notches operated at the periphery of the coating.

A mixture of azithromycin with 10% HPMC and 2% stearate of 2490 magnesium is prepared and compressed into molds in the form of cylinders of 1 cm long and 2 cm diameter. The length of the cylinders is dependent on the amount of mixture loaded into the mold, as shown in the table below:

<td>Diameter</td><td>Amount of mixture</td><td>The amount of azithromycin</td><td>Length</td>

<td>1 cm</td><td>1 g</td><td>880 mg</td><td>1.3 cm (approx.)</td>

2495

The cylinders thus prepared are completely coated with ethyl cellulose (Dow EC S100), by immersion in a 20% EC solution in acetone and drying overnight at

2500

RO 114740 Bl

50 ° C. A sharp blade is used to cut four equidistant longitudinal notches, approximately 0.5 mm long, along the periphery of each cylinder, to obtain sustained release dosage forms. These large dosage forms are especially useful for the treatment of animals, especially ruminants, which can retain the dosage form in rumen for an extended period of time.

Example 21. This example illustrates a composition and preparation of a delivery system consisting of a porous membrane capsule with an "pushing" osmotic compartment, to drive a piston acting on any dispensable azithromycin drug composition.

A hydrophobic porous membrane capsule is prepared by the following procedure:

First, glucose is ground to a mesh size of 230 mesh, 15 g of ground glucose is then mixed with 35 g of poly [d, 1-lactide) (average molecular weight of 200000) and the mixture is mixed and ground. An amount of 1.15 g of the resulting particles is then placed in a transfer mold, where the particles are molded as an open-ended membrane cup. The dimensions of the membrane cup are 2.6 cm long, with an internal diameter of 0.457 cm and a wall thickness of 0.06 ... 0.08 cm. The membrane cup is then cleaned with 70% ethanol / 30% water, followed by water, and dried in vacuo.

Then, sodium chloride is ground to 230 mesh. To 6 g of ground sodium chloride add 4 g of carboxymethyl cellulose and mix to produce an osmotically effective composition. The composition is compressed into osmotically effective tablets at a pressure of 1000 1b, to produce a 100 mg cylindrical tablet with a flat face and a convex end and a diameter of about 0.457 cm, to fit the shape. inner membrane cup. An internal spacer or piston is formed by combining 0.5 g of ultrathene and 0.5 g of vynathen and placing the mixture in a transfer mold with a shape to fit into the membrane cup.

The sodium chloride tablet is placed in the hydrophobic membrane capsule. The piston is inserted into the capsule above the sodium chloride tablet. A composition dispensable with azithromycin (such as a suspension of azithromycin in polyethylene glycol or other suspending agent) is then charged above the piston. Finally, the device is sealed with a lid that is equipped with a drug dispensing hole. When placed in an aqueous environment, the device is soaked with water through osmosis. This osmotic imbibing sets the piston, which, in turn, acts on the composition of azithromycin, forcing it out through the lid at a controlled speed.

Example 22. This example illustrates a composition and preparation of a pH-dependent coated tablet with a Cellulose Acetate Phthalate Coat.

The cores of azithromycin tablets are manufactured according to the formula described in Table 31-1. Tablet cores are prepared by wet granulation of all tablet ingredients (except magnesium stearate / sodium lauryl sulfate). The dried granules are mixed with the lubricating mixture of magnesium stearate / sodium lauryl sulphate, as follows on tabletop press. Tablet cores are then spray coated with a solution of acetate phthalate cellulose (CAP) in acetone in a HCT-60 Hi-Coater spray coating apparatus.9 (Freund Ind.Corp., Tokyo). Cellulose acetate phthalate is plasticized with 25% (by weight) diethylphthalate (DEP). Sufficient CAP is sprayed on tablets to obtain a final coating by weight with polymer, after drying, of 20%, compared to the weight of the bed

RO 114740 Blank tablet not covered.

2555

Table 31-1

Tablet core formulations with azithromycin

<td>component</td><td>Weight (mg / tablet)</td>

<td>Azithromycin dihydrate *</td><td> 524,10</td>

<td>Pregelatinized starch * *</td><td> 54,00</td>

<td>Debasic calcium phosphate, anhydrous</td><td> 277,68</td>

<td>Sodium croscarmellose #</td><td> 18,00</td>

<td>Magnesium Stearate / Sodium Lauryl Sulphate (90/30)</td><td> 26,22</td>

<td>Total</td><td> 900</td>

* Based on a theoretical power of 95.4% * * Starch 15OO # Ac-Di-Sol (FMC Corp.)

Example 23. This example illustrates a composition and preparation of a pH-Coated Tablet 2570 Barrier Covered pH Dependent.

Azithromycin tablets are manufactured as described in Example 22. The tablets are spray coated with a solution of hydroxypropyl methylcellulose (HPMC; Colorcon, Inc) in water, using a HCT-6D Hi-Coater device. In this way, the tablets are coated with 5% by weight barrier coating from HPMC, compared to 2575 the initial weight of the tablet. The tablets are further coated with cellulose acetate phthalate (CAP) and DEP plasticizer (as described in Example 22, in the HCT-60 Hi-Coater). Sufficient CAP is sprayed onto tablets to obtain a final coating with polymer, after drying, of 20% by weight, compared to the weight of the uncoated tablet. HPMC coating serves as a barrier between 2580 azithromycin and pH sensitive CAP coating. This barrier coating prevents premature disintegration (or weakening) of the CAP coating, for example, in the low pH environment of the stomach, potentially caused by a high local pH inside the tablet, due to the presence of azithromycin.

Example 24. This example illustrates a composition and preparation of a pH-Dependent Coated Tablet 2585 with Acrylic Resin Coating.

Azithromycin tablets are manufactured according to Example 22. The tablets are then spray coated with an acrylic resin in a HCT-60 Hi-Coater spray coating apparatus.R (Freund Ind.Corp., Tokyo). The resin consists of a 1: 1 mixture (g (g) of Eudragit-LR and Eudragit-SR, which are copolymers of methyl 2590 krylic acid / methyl methacrylate, accessible from Rohm Pharma Corporation (Darmstad, Germany). The formula for the ester coating solution given in table 33-1. The coating formulation with the Primary Eudragit-L / S layer is sprayed onto tablets in the Hi-Coater device, followed by the spray coating with the Covering Layer formulation. The total weight of the coating applied with the polymer is 15% of the 2595 weight of the uncoated tablet bed.

RO 114740 Bl

Table 33-1

Spray coating forms with

EudragitT for tablets

<td>Primary layer</td><td>Parts by weight</td>

<td>1: 1 Eudragit-L / S solution 12.5%</td><td> 2000</td>

<td>dibutylphthalate</td><td> 25</td>

<td>talcum</td><td> 50</td>

<td>Isopropyl alcohol / acetone</td><td>up to 4000</td>

<td>Coating (colored)</td><td></td>

<td>1: 1 Eudragit-L / S solution 12.5%</td><td> 1200</td>

<td>talcum</td><td> 140</td>

<td>Magnesium stearate</td><td> 40</td>

<td>Titan dioxide</td><td> 50</td>

<td>Pigment</td><td> 50</td>

<td>The water</td><td> 40</td>

<td>Isopropyl alcohol / acetone</td><td>Up to 3000</td>

Example 25. This example illustrates a composition and preparation of a pH-Coated Acrylic Barrier Coated Tablet with Barrier Coating.

Azithromycin tablets are manufactured according to Example 22. The tablets are spray-coated with a solution of hydroxypropyl methylcellulose (HPMC) (Colorcon, Inc.) in water, using a HCT-60 Hi-Coater device. In this way, the tablets are coated with 5% by weight barrier coating with HPMC, compared to the initial weight of the tablet. The tablets are then spray coated with an acrylic resin in a HCT-60 Hi-Coater spray coating device.R (Freund Industries Corp., Tokyo). The resin consists of a 1: 1 (w / w) mixture of Eudragit-LR and Eudragit-SR, which are methacrylic acid / methyl methacrylate copolymers provided by RohmPharma Corporation (Darmstad, Germany), the formula for spray coating solution is given in Table 33-1. Hi-Coater device, followed by spray coating with Coating Layer formulation. The total weight of acrylic resin polymer applied is 15% of the weight of the uncoated tablet bed. The lower HPMC coating serves as the barrier between azithromycin and the pH sensitive acrylic resin coating. This barrier coating prevents premature degradation (or weakening) of the acrylic resin coating, for example, in the low pH environment of the stomach, potentially caused by a high local pH inside the tablet due to the presence of azithromycin.

Example 26. This example illustrates a composition and preparation of Azithromycin Tablets with a Delayed Double Release Coating.

Azithromycin tablets are manufactured according to Example 22. The tablets are

EN 114740 Bl spray-coated with an aqueous mixture of ethylcellulose (EC) (Surelease; 2640 Colorcon Inc.) and hydroxypropylmethylcellulose (HPMC) (Opadry; Colorcon Inc.]. In a 70/30 EC / HPMC ratio, using an HCT device -60 HI-CoaterR. In this way, the tablets are covered by 5% by weight EC / HPMC, compared to the initial weight of the tablet. The tablets are then spray coated with an acrylic resin in a HCT-60 Hi-Coater spray coating device.R (Freund Industries Corp., Tokyo). Resin 2645 consists of a 1: 1 (w / w) mixture of Eudragit-LR and Eudragit-SR, which are methacrylic acid / methyl methacrylate copolymers, provided by RohmPharma Corporation (Darmstad, Germany). The formula for spray coating is given in Table 33-1. The coating formulation with Primary Layer from Eudragit-L / S is sprayed on tablets in the Hi-Coater device, followed by the spray coating with the 2650 Coating Layer formulation. The total weight of acrylic resin polymer applied is 10% by weight of the uncoated tablet paste.

Example 27. This example illustrates a composition and preparation of pH-dependent coated granules.

The azithromycin granules are prepared as follows: azithromycin, 2655 microcrystalline cellulose and water (according to the formula in table 36-1) are mixed in a Hobart mixer to form a paste. The paste is extruded as streams and is spheronized, using an extruder (Fuji-Paudal spheronizer, forming small granules (about 1 mm in diameter), which are then dried. The granules are then spray coated with an acrylic resin in a Glatt GPCG-2660 Fluid Bed Processor

1. The resin consists of a 1: 1 (w / w) mixture of Eudragit-LR and Eudragit-SR, which are methacrylic acid / methyl methacrylate copolymers, provided by RohmPharma Corporation (Darmstad, Germany). The formula for spray coating is given in Table 33-1. The coating formulation with Eudragit-L / S Primary Layer is sprayed on granules in the fluidized bed processor, followed by spray coating with 2665 Coating Layer formulation. The total weight of the applied polymer is 25% by weight of the uncoated granule paste.

Table 36-1

2670

Formula for azithromycin granules of Example 36

** Avicel PH101 # Volatile, substantially removed from the final dosage form

2680

Example 28. This example illustrates a composition and preparation of pH-dependent coated granules with a Barrier Coating with HPMC.

The azithromycin / microcrystalline cellulose granules are prepared as in Example 27. In a GPCG-1 Fluid Glatt Bed Processor, these granules are coated with an HPMC solution (OpadryR, Colorcon, Inc.). The final barrier coating 2685 dried by HPMC comprises 5% by weight of uncoated granules. Granules of

The HPMC-coated azithromycin Bls are then coated with 25% by weight acrylic resin coating as described in Example 27. The lower HPMC coating serves as a barrier between azithromycin and the pH sensitive acrylic resin coating. This barrier coating prevents premature disintegration (or weakening) of the acrylic resin coating, for example in the low pH environment of the stomach, potentially caused by high local pH inside the tablet due to the presence of azithromycin.

74 members in 42 offices

This recordMember, by publication datePriority claim32 more offices are in the list below

Priority claims8

Priority claims
Document	Office	Kind	Date
23909494	United States of America	A	1994-05-06
23909494	United States of America	A	1994-05-06
9500264	International Bureau of the World Intellectual Property Organization (WIPO)	W	1995-04-13
9500264	International Bureau of the World Intellectual Property Organization (WIPO)	W	1995-04-13
239094	–	–	–
9500264	–	–	–
US19940239094	–	–	–
WO1995IB00264	–	–	–

Members74

Family members, oldest first
Document	Office	Kind
AP9500735A0	African Regional Intellectual Property Organization (ARIPO)	A0	1995-04-30
IL113516A0	Israel	A0	1995-07-31
IL113516D0	Israel	D0	1995-07-31
UY23958A1	Uruguay	A1	1995-10-31
IS4282A	Iceland	A	1995-11-07
CA2189658A1	Canada	A1	1995-11-16
WO9530422A1	World Intellectual Property Organization (WIPO)	A1	1995-11-16
AU2113195A	Australia	A	1995-11-29
MA23537A1	Morocco	A1	1995-12-31
TNSN95051A1	Tunisia	A1	1996-02-06
BR9501929A	Brazil	A	1996-03-05
PE4796A1	Peru	A1	1996-03-09
CO4290346A1	Colombia	A1	1996-04-17
AP548A	African Regional Intellectual Property Organization (ARIPO)	A	1996-10-30
FI964452A	Finland	A	1996-11-05
FI964452A0	Finland	A0	1996-11-05
FI964452A7	Finland	A7	1996-11-05
FI964452L	Finland	L	1996-11-05
NO964678D0	Norway	D0	1996-11-05
ZA953627B	South Africa	B	1996-11-05
NO964678L	Norway	L	1997-01-06
HU9603076D0	Hungary	D0	1997-01-28
EP0758244A1	European Patent Office (EPO)	A1	1997-02-19
PL317106A1	Poland	A1	1997-03-17
LV11729A	Latvia	A	1997-04-20
CN1149831A	China	A	1997-05-14
JPH09505609A	Japan	A	1997-06-03
KR970702727A	Republic of Korea	A	1997-06-10
AU680356B2	Australia	B2	1997-07-24
LV11729B	Latvia	B	1997-08-20
BG100960A	Bulgaria	A	1997-08-29
OA10320A	African Intellectual Property Organization (OAPI)	A	1997-10-07
HRP950277A2	Croatia	A2	1997-10-31
MX9605419A	Mexico	A	1997-12-31
SI9520049A	Slovenia	A	1997-12-31
CZ324296A3	Czechia	A3	1998-04-15
HUT77530A	Hungary	A	1998-05-28
SK143296A3	Slovakia	A3	1998-07-08
NZ283160A	New Zealand	A	1998-07-28
RU2130311C1	Russian Federation	C1	1999-05-20
RO114740B1This record	Romania	B1	1999-07-30
JP2977907B2	Japan	B2	1999-11-15
KR100232297B1	Republic of Korea	B1	1999-12-01
US6068859A	United States of America	A	2000-05-30
CA2189658C	Canada	C	2000-10-31
PL179910B1	Poland	B1	2000-11-30
IL131308A0	Israel	A0	2001-01-28
IL131308D0	Israel	D0	2001-01-28
TW420616B	Taiwan Province of China	B	2001-02-01
IL113516A	Israel	A	2001-04-30
BG63152B1	Bulgaria	B1	2001-05-31
IL131308A	Israel	A	2001-07-24
UA41995C2	Ukraine	C2	2001-10-15
EP0758244B1	European Patent Office (EPO)	B1	2001-11-28
MY113059A	Malaysia	A	2001-11-30
AT209497T	Austria	T	2001-12-15
ATE209497T1	Austria	T1	2001-12-15
DE69524214D1	Germany	D1	2002-01-10
ES2163504T3	Spain	T3	2002-02-01
DK0758244T3	Denmark	T3	2002-02-11
DZ1880A1	Algeria	A1	2002-02-17
US2002044965A1	United States of America	A1	2002-04-18
PT758244E	Portugal	E	2002-04-29
DE69524214T2	Germany	T2	2002-05-23
HRP950277B1	Croatia	B1	2002-06-30
SK282854B6	Slovakia	B6	2002-12-03
CN1096862C	China	C	2002-12-25
NO315453B1	Norway	B1	2003-09-08
CZ292360B6	Czechia	B6	2003-09-17
US7108865B2	United States of America	B2	2006-09-19
EP0758244B2	European Patent Office (EPO)	B2	2008-02-13
DE69524214T3	Germany	T3	2008-05-15
ES2163504T5	Spain	T5	2008-05-16
DK0758244T4	Denmark	T4	2008-06-16

Controlled release composition, process for preparing the same and method of treatment

Abstract

Term

1OOO

Priority claims8

Members74

Numbers

Titles2

Classification