AP86A

AP86A - Implant

Info

Publication number: AP86A
Application number: APAP/P/1989/000117A
Authority: AP
Inventors: Ettience Honore Schacht
Original assignee: Schering Ag
Priority date: 1988-03-05
Filing date: 1989-03-03
Publication date: 1990-05-28
Also published as: GB8904597D0; GB8805286D0; OA09237A; GB2216411A; AP8900117A0

Abstract

A trypanocide drug

Description

This invention relates to controlled release deliverysystems containing a trypanocids.

Trypanocida1ly active phenanthr id i ne compounds, such as homidium bromide or chloride, are widely used against animal trypanosomiasis such as that spread by tsetse fly in Africa. The present formulations are water soluble and as a result the drug is only bioavailable for a short period of time and usually no more than about 60 days. Since the tsetse fly challenge extends for a much longer period, it is highly desirable that the drug can be made available for as long a period as possible. The present invention relates to a system of such drugs whereby the drug is slowly released into the bloodstream over a period of time thus maintaining therapeutic levels over a long period.

In various articles, reviews and books e.g. in Controlled Drug Delivery by S Bruck (CRC Press, Boca Raton 1983) and Sustained and Controlled Release Drug Delivery Systems, 2nd edition. by J Robinson and V Lee (Marcel Dekker 1985) a variety of drug delivery systems proposed for the administration cf various drugs have been described. Until now no drug delivery system based on biodegradable polymers, has been reported for the delivery of trypanocides in animals.

DeLoach reported on a delivery system for trypanocidal drugs, e.g. horaidium bromide that was based on an inclusion of the active agent in erythrocytes (Res Exp Med., 53 5 , 1-9 . 1985 ). D Fluck (I . 5 . C . R . T. C . report 520, 1985) described the use of lipsomes as drug dosage forms for iometamidium. Finally D James (Trans Roy Soc Trop Med Hyg 72, 471-476, 1987) attempted to enhance the duration of activity of isometamidium chloride by preparing ionic complexes with dextran sulphate. A distinct disadvantage of the erythrocyte and lipsome systems is the risk of

BAD ORIGINAL early leakage of the enclose! drugs. In the case of the dextran sulphate complex the pharmacokinetic properties are significantly changed which results in a loss of the prophylactic action of the complexed isometamidium (D Schilinger et al, Abstracts of the 18th Meeting

I.S.C.T.R.C. Harare, Zimbabwe, 4-8 March. 1985).

The present invention overcomes these disadvantages.

According to the invention there is provided a trypanocide drug delivery system which comprises a trypanocide dispersed in least one biodegradable polymer.

The invention is especially applicable to formulations of salts of homidium (3,8-diamino-5-ethyl-6-phenylphenanthridium), eg the chloride and especially the bromide. This latter salt is also sold as Ethidium. Other phenanthradine compounds include that sold under the trade name Samorin (3-amino-8-(2-amino-6-methylpyrimidin-4-ylamino-5-ethyl-6-phenylJphenanthridinium chloride hydrochloride; common name, isometamidium). Other trypanocides include quinpyramine sulphate (4-amino20 6-(2-amino-6-methylpyrimidin-4-ylamino)-2-methyl1,1'-dimetho(methyl sulphate)) and salts of diminazine (p,p'-diamidinodiazoaminobenzene). eg the aceturate, which is sold under the trade name Berenil, pyrethidium bromide, ronidazol, MF-nitroimidazol and α-D.L-difluoromethyl ornithine.

The system preferably also comprises other additives such as a) substances to facilitate the fabrication of the device, b) substances to increase the stability of the devices and/or c) substances to adjust the release characteristics of the drug.

The device can contain two or more bioactive agents. The drug content in the delivery systems can vary between over a wide range, e.g. from 5¾ and 60%, preferably 20-35%, by weight.

The polymer can be a homopolymer or a copolymer. If

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BAD ORIGINAL desired a mixture of two or more biodegradable polymers cat be used The biodegradable polymers are those which upon administration to the body degrade to harmless products. Examples of suitble polymers include:

polyglyco1ide. poly (L-1 actide), poly(D.L-lactide), polycaprolaclone, poly(β-hydroxybutyrate). poly(β-hydroxyvalerate) and poly(α-aminoacids), in addition to copolymers composed of two or more of the following structural units: glycolide, L-lactide,

D,L-lactide, D-lactide, caprolactone or valerolactone.

This also include stereocopolymers of L-lactide and D,L-lactide. A system based on polycaprolactone is especially preferred.

The delivery systems are preferably fabricated in the shape of cylinders, as tablets or spherical particles. The devices prepared according to this invention can be administered to animals by intramuscular or subcutaneous injection or by surgical implantation. Cylinders are especially preferred as these can be most satisfactorally implanted into an animal. The diameter of such cylindershaped devices can vary between e.g. 1 mm and 7 mm and the length can range from e.g. 1 to 7 cm. The diameter of spheres can vary between 20 microns and 1 mm. The cylindrical devices can be prepared by extrusion or injection moulding of the the appropriate mixture of biodegradable polmer(s), drug(s) and possible adcitive(s). The tablets can be prepared by compression of the appropriate mixture. The spherical devices can be prepared e.g. by a solvent-evaporation technique, eg as described by M. Morishita et al. U.S, Patent 3,560,757. The devices, prepared in the various geometrical forms described before, can. if necessary, be subsequently coated with a biodegradable polymer belonging to the class of polymers cited before as candidate carrier materials. Coating can be achieved eg by dip coating or spraying techniques. In

BAD ORIGINAL ft coated devices the surrounding polymer membrane can act as a barrier controlling the release of the drug enclosed in the device. The drug delivery systems loaded with trypanocidal drug(s) and prepared according to this invention will, after subcutaneous or intra-muscular administration, release the drug over a period varying from one week to over one year. The duration of the release and the release rate can be controlled and varied over a broad range and depends on the chemical composition of the polymer substrate, the nature of the drug retained within the device, the drug loading, the additives, the shape of the device, and the presence of a coating membrane. The release of the drug retained within the device occurs by diffusion and or erosion of the polmer material used as a constructive part of the device.

The examples described hereafter illustrate the preparation of devices containing homidium bromide and the in vitro and in vivo evaluation of these devices.

Homopolymers and copolymers of c-caprolactone as well as copolymers with L,L- and D.L-dilactides were prepared by ring opening polymerisation of the purified monomers, using 1000 ppm stannous bis(2~ethylenehexenoate) in toluene as catalyst, at a temperature of 130°C. Polymerisations were carried out in bulk, in silanised glass tubes under vacuum and after several freeze-thaw cycles for degassing. After sealing, the tubes were immersed and rotated in a silicone oil bath at 130°C for 7 days to give polymers with molecular weights in the range 40,000 to 90,000. Polymers were collected by cooling to room temperature, dissolving in chloroform, precipitating with hexane and dried in vacuo.

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Example 1

Small scale preparation of cylindrical devices composed of a po’.:aorolactor.e matrix loaded with homidium bromide.

2.5 g Polycaprolactone (MW ca.: 56,000) is dissolved in 25 ml dichloromethane and 750 mg homidium bromide is added. From this mixture a film is cast. After drying, the film is cut in small pieces which are transferred into a melt index apparatus, provided with a 1.2 mm nozzle and heated at 120°C. A pressure of about 300 KPa is applied to force the mixture of drug and polymer through the nozzle. The extruded fibres are cut in pieces of ca. 1 cm. The diameter of the fibres ranges from 1.5 to 1.7 mm depending on the speed of the extrusion process.

The cylindrical pieces are sterilized by ethylene oxide vapor treatment and stored in vacuum-sealed polyethylene bags.

Example 2

r. Larger scale preparation of cylindrical devices composed of a pclycaprolactone matrix loaded with homidium bromide

500 g Polycaprolactone (MW ca.: 56,000) is mixed for min with 150 g homidium using a Erabender mixer, heated at 60°C. The mixture is transferred to a lab-scale extruder, provided with a 1.2 mm nozzle and is extruded at 100-150°C. The extruded fibres are cut in pieces of ca.

1 cm. The diameter of the fibres ranges from 1.5 to 1.7 mm depending on the speed of the extrusion process.

Example 3

Preparation of cylindrical devices loaded with homidium bromide coated with a biodegradable membrane

Poly(caprolactone-co-D,L-lactide) cylindrical devices loaded with homidium bromide are coated by dipping the devices in a 10¾ (by weight) solution of polycaprolactone in chloroform (MW ca 60.000). The dipcoating-drying cycle is repeated to obtain the desired coating thickness. A typical coating thickness is 50-100 microns.

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Example 4

In vitro evaluation of devices loaded with trypanocidal drugs, e.g. polycsprolactone cylinders loaded with homidium bromide.

Medium used for in vitro release: phosphate buffer pH 7.4; 30.4 ml 0.5 NaOH + 40.3 mo 0.5 M KH₂PC>₄ adjusted to 1 1 with distilled water. 250 ml Buffer is transferred to a silanized glass-stoppered Erlenmeyer flask, maintained at 37°C. One or more devices (e.g. cylinders of

1-2 mm diameter and 0.5-2 cm length) are transferred to that solution. At regular time intervals, samples are withdrawn for analysis of the amount of drug released. Analysis of the homidium bromide content was carried out by HPLC using the method of Perschke and Vollmert (Acta tropica 42. 209-216, 1985).

Example 5

In a similar manner to the previous Examples various other cylinders are prepared and evaluated. The release rates and details of all such devices are shown in Figures

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Example 6

In vivo evaluation of poly(e-caprolactoneco-L,L-lactide) (75/25) cylindrical devices loaded with

25% homidium bromide, using rabbits as test animals.

Cylinders of 1 cm length each were subcutaneously administered to rabbits infected with different strains of T. congolense. At regular intervals blood samples were taken and analysed for homidium bromide by HPLC. For comparison, in a separate experiment rabbits were given homidium bromide intra-muscularly at a 1 mg/kg dose. Blood samples were taken regularly and assayed for homidium bromide. The results of these experiments are summarized in figure 7, expressing the plasma concentration in ng/ml (average value for 5 rabbits) as a function of time after subcutaneous implantation. AP 0 0 0 0 8 6

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Example 7

Evaluation of the therapeutic effectiveness of the delivery system aga ir.s t pre-established T. congolense infection.

The method described in Example 6 is used. At days 28, and 150 the rabbits were reinfected with different strains of T. congolense. No positive parasitemia was observed over the total duration of the experiment in rabbits treated with the device prepared according to this invention and specified in Example 6. Rabbits treated with an intra-muscular dose of homidium bromide gave a positive result when reinfected 23 days after the start of the treatment. Upon removal of the subcutaneous implant, at day 120 after implantation and reinfection with

T. congolense. positive parasitemia was observed, thus P proving that the observed prophylactic effect is not an ^Λ immunological phenomenon but solely caused by the implant of the invention.

Claims

1, A trypanocide drug delivery system which comprises a trypanocide dispersed in least one biodegradable polymer .

2. A system according to claim 1 in which the trypanocide is a salt of homidium.