EP1458352A1 - Micro implant a dose solide - Google Patents

Micro implant a dose solide

Info

Publication number
EP1458352A1
EP1458352A1 EP02787456A EP02787456A EP1458352A1 EP 1458352 A1 EP1458352 A1 EP 1458352A1 EP 02787456 A EP02787456 A EP 02787456A EP 02787456 A EP02787456 A EP 02787456A EP 1458352 A1 EP1458352 A1 EP 1458352A1
Authority
EP
European Patent Office
Prior art keywords
composition according
hours
poly
composition
therapeutic agent
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP02787456A
Other languages
German (de)
English (en)
Inventor
Henrik Egesborg Hansen
Mads Christian Sabra
Thomas Buch Rasmussen
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Novo Nordisk AS
Original Assignee
Novo Nordisk AS
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Novo Nordisk AS filed Critical Novo Nordisk AS
Publication of EP1458352A1 publication Critical patent/EP1458352A1/fr
Withdrawn legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/0087—Galenical forms not covered by A61K9/02 - A61K9/7023
    • A61K9/0092—Hollow drug-filled fibres, tubes of the core-shell type, coated fibres, coated rods, microtubules or nanotubes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/0012—Galenical forms characterised by the site of application
    • A61K9/0019—Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
    • A61K9/0024—Solid, semi-solid or solidifying implants, which are implanted or injected in body tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P3/00—Drugs for disorders of the metabolism
    • A61P3/08—Drugs for disorders of the metabolism for glucose homeostasis
    • A61P3/10—Drugs for disorders of the metabolism for glucose homeostasis for hyperglycaemia, e.g. antidiabetics
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P5/00—Drugs for disorders of the endocrine system
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P7/00—Drugs for disorders of the blood or the extracellular fluid

Definitions

  • the invention relates to a solid phamaceutical composition comprising at least one pharmaceutical agent, to the use of the pharmaceutical composition and to methods for producing pharmaceutical compositions according to the invention.
  • aqueous solutions By far the most widely used method for parenteral injection of drugs is by injection of an aqueous solution using a hypodermic syringe.
  • aqueous solutions In order to inject a given volume of drug, a much larger volume of water and different additives also have to be injected. Weight ratios of drug to solvent may be in the range of 1 :100 to 1 :1 ,000.
  • Weight ratios of drug to solvent may be in the range of 1 :100 to 1 :1 ,000.
  • the pain associated with injection is primarily caused by the volume injected, not by the penetration of the skin. Any reduction in volume would thus lead to a reduction in pain for the patient.
  • an aqueous solution of any given drug is chemically less stable than a dry formulation of the same drug. Furthermore, an aqueous solution is prone to microbial contamination and needs to be sterilised by use of heat, radiation, filtration or chemical means. To increase the shelf life of aqueous drug formulations preservatives, stabilisers, anti-oxidants, biocides etc are often added. These additives may also add to the toxicity of the formulation. Alternatively or additionally, the aqueous solutions may require special storage conditions at low temperature to avoid chemical or microbial break down of the active ingredients and to avoid microbial growth.
  • US 5,851 ,547 relates to a solid dose drug formulation with an inner non- disintegrating matrix comprising a therapeutic agent and an outer layer being made from a hydrophobic polymer.
  • the outer layer can be made from biodegradable materials such as PLGA or from non-biodegradable material such as EVA or Silastic Medical Grade ETR Elastomer. It is emphasised that the inner layer must be made from a non-disintegrating material.
  • the preferred material is silicone.
  • US 6,126,956 discloses another coated solid dose drug formulation, wherein the inner matrix comprises ethylen vinyl acetat co-polymer, which is non-biodegradable.
  • the solid dose is coated with e.g. polymethylmethacrylat (PMMA) to slow down the rate of release of the drug. Release takes place through a hole in the coat to give an approximately constant rate of release.
  • PMMA polymethylmethacrylat
  • the disclosed release profiles show that approximately sustained release can take place for periods up to 90 days.
  • the reference discloses no details about the rate of release during the first hours after the solid dose drug formulation has been inserted into the body.
  • the solid dose drug formulation being made from materials that are non-biodegradable has to be removed surgically from the body after the drug has been released.
  • US 5,153,002 discloses a cylindrical solid dose drug formulation being coated on the curved sides, and one of the ends.
  • solid particles of a therapeutic agent are embedded, the amount of therapeutic agent being highest in the end furthest away from the open end of the formulation. According to the reference this provides a constant release. It is emphasised that the inner matrix must not dissolve or disintegrate before the therapeutic agent has been released. This means that the body of the inner matrix remains in the tissue for a substantial time after release of the therapeutic agent causing local irritation to the tissue.
  • PCT/DK00/00184 discloses a solid pharmaceutical composition for parenteral injection comprising a binder and at least one therapeutic agent, said binder constituting at least 0.5% by weight of the composition and said binder comprising at least one binding agent being a carbohydrate, and optionally at least one non-crystallisation agent, whereby said binder forms an amorphous matrix, and the amount of said therapeutic agent consisting at least one dosage.
  • the pharmaceutical composition has the strength to be injected directly without the need for cannulas, trocars or the like.
  • the therapeutic agent may be any pharmaceutical suitable for injection, such as subcutaneous or intramuscular injection.
  • Pharmaceutical compositions according to this disclosure are easy to manufacture store, and administer. However, the binder, being based on carbohydrates dissolves very rapidly after injection releasing a boost of the therapeutic agent shortly after injection.
  • the invention relates to a solid pharmaceutical composition for parenteral administration comprising an inner matrix comprising at least one therapeutic agent, and a biodegradable, and water-impermeable coating covering part of the surface of said composition, wherein said inner matrix disintegrates upon contact with animal tissue or tissue fluids.
  • the rate of release of the drug can be controlled.
  • the specific rate of release can be controlled by carefully designing the part of the surface which is not covered. All compositions according to the invention have a release profile with a smaller peak and longer duration compared to non-coated compositions.
  • the amount of injected therapeutic agent can be diminished and/or the interval between administration be increased. By having a more constant release rate of the therapeutic agent, less unwanted side effects are observed.
  • compositions according to the present invention is that the whole composition is broken down completely in the tissue within relatively short time in comparison to the time required for release of the therapeutic agent.
  • the inner matrix is either soluble or degradable and the coating, which is relatively thin, is biodegradable, preferably within a short time after the inner matrix has been completely dissolved or degraded.
  • compositions are especially adapted for administration of therapeutic agents which have to be administered regularly, such as insulin, growth hormone etc.
  • the invention relates to use of a solid pharmaceutical composition according to the invention for parenteral injection in an animal.
  • the compositions may be injected with or without the use of a trocar or syringe, depending on the strength of the inner matrix.
  • the invention relates to a method for manufacturing the composition according to the invention.
  • the method may comprise injection moulding, extrusion, or compression followed by coating either through immersion, vapour deposition, or co-extrusion of coat and inner matrix.
  • Figure 1 shows the development of the composition in time when no coating is present.
  • Figure 2 shows the development of the composition in time when half the surface is coated.
  • Figure 3 shows the development of the composition in time when only a small part of the composition is left open.
  • Figure 4 shows a graph of the release of material from the composition as a function of time for each of the cases shown in figures 1 , 2 and 3.
  • A corresponds to the composition of Fig 1.
  • B corresponds to the composition of Fig 2.
  • C corresponds to the composition of Fig. 3.
  • Figure 5 shows the erosion of the elongated composition in time when the composition is uncoated.
  • Figure 6 shows the erosion when only the ends are uncoated.
  • Figure 7 shows the erosion of the composition in time when the composition is uncoated.
  • Figure 8 shows the erosion when only the ends are uncoated.
  • Figure 9 shows a graph of the release of material from the composition as a function of time.
  • E corresponds to the composition of Fig. 5.
  • F corresponds to the composition of Fig. 6.
  • G corresponds to the composition of Fig. 7.
  • H corresponds to the composition of Fig. 8.
  • Biodegradable As used herein a material is biodegradable if it hydrolyses and/or is absorbed into animal tissues such as human tissue when in contact with tissue and/or tissue fluids in an animal.
  • Inner matrix As used herein the inner matrix is the core of the composition.
  • Zero order release the rate of release of the pharmaceutical agent from the composition is substantially constant over time.
  • First order release the rate of release of the pharmaceutical agent from the composition increases/decreases substantially linearly with time.
  • the role of the biodegradable water-impermeable coating is to reduce the rate of release of the therapeutic agent from the solid composition.
  • the coating will have this effect even if it is partly broken down before the therapeutic agent has been released.
  • the coating is water-impermeable at least for a substantial time after the composition has been injected.
  • the coating remains water-impermeable until essentially the whole inner matrix has been dissolved. This ensures that the coating exerts the same or substantially the same effect during the whole period of dissolution and/or disintegration of the inner matrix.
  • the coating may remain water-impermeable until most of the therapeutic agent has been dissolved. This likewise ensures that the coating exerts the same or substantially the same effect during the whole period of release of therapeutic agent.
  • the materials that can be used for manufacturing the coat are any materials that fulfil the requirements of biodegradability and water-impremeability, the latter for at least a period.
  • Suitable examples of coating materials comprise materials selected from the group consisting of polyesters such as polyglycolides, polylactides and polylactic polyglycolic acid copolymers (PLGA); polyglycolide; polylactide; polyethers such as polycaprolactone (PCL); Glycolide, Poly(dl-lactic acid) - MW 20,000 - 30,000; Poly(dl-lactic acid) - MW 330,000 - 600,000; Poly(dl-lactic acid) - MW 6,000 -
  • polyesters such as polyglycolides, polylactides and polylactic polyglycolic acid copolymers (PLGA); polyglycolide; polylactide; polyethers such as polycaprolactone (PCL); Glycolide, Poly(dl-lactic acid) - MW 20,000 - 30,000; Poly(dl-lactic acid) - MW 330,000 - 600,000; Poly(dl-lactic acid) - MW 6,000 -
  • Preferred materials used for the coat comprise materials selected from the group consisting of polylactic polyglycolic acid copolymer, polyglycolides, and polylactides such as Poly(dl-lactic acid) - MW 20,000 - 30,000; Poly(dl-lactic acid) - MW 330,000 - 600,000; Poly(dl-lactic acid) - MW 6,000 - 16,000; Poly(dl-lactide/glycolide) [50:50 ]; Poly(dl-lactide/glycolide) [70:30]; Poly(dl-lactide/glycolide) [75:25]; Poly(dl- lactide/glycolide) [80:20]; Poly(dl-lactide/glycolide) [85:15]; Poly(dl-lactide/glycolide) [90:10]; Poly(glycolic acid) [i.v.
  • the coating is made essentially from polylactic polyglycolic acid copolymer such as Poly(dl- lactide/glycolide) [50:50 ]; Poly(dl-lactide/glycolide) [70:30]; or Poly(dl- lactide/glycolide) [75:25]; Poly(dl-lactide/glycolide) [80:20]; Poly(dl-lactide/glycolide) [85:15]; Poly(dl-lactide/glycolide) [90:10]; Poly(l-lactide/glycolide) [70:30]; Poly(l- lactide/glycolide) [70:30].
  • polylactic polyglycolic acid copolymer such as Poly(dl- lactide/glycolide) [50:50 ]; Poly(dl-lactide/glycolide) [70:30]; or Poly(dl- lactide/glycolide) [75
  • the thickness of the coating is such that it remains water impermeable until essentially all therapeutic agent has been absorbed.
  • Suitable examples of average thickness are at least 0.5 ⁇ m, such as at least 0.75 ⁇ m, for example at least 1 ⁇ m, such as at least 1.5 ⁇ m, for example at least 2 ⁇ m, such as at least 2.5 ⁇ m, for example at least 5 ⁇ m, such as at least 10 ⁇ m, for example at least 15 ⁇ m, such as at least 20 ⁇ m, for example at least 25 ⁇ m, such as at least 30 ⁇ m, for example at least 40 ⁇ m, such as at least 50 ⁇ m, for example at least 60 ⁇ m, such as at least 70 ⁇ m, for example at least 75 ⁇ m, such as at least 80 ⁇ m, for example at least 90 ⁇ m, such as at least 100 ⁇ m, for example at least 125 ⁇ m, such as at least 150 ⁇ m, for example at least 200 ⁇ m.
  • the thickness of the coating depends to a large extent on the method used for coating the composition. Thus by co-extrusion of the inner matrix and the coat, a coating thickness from 50 to 200 ⁇ m can be obtained. By dipping or spray-coating or vapour deposition a coating thickness of approximately 1 ⁇ m can be obtained.
  • the coating is completely broken down in an animal tissue or tissue fluid more slowly than the time it takes to liberate the therapeutic agent. This is to ensure that the effect of the coating is maintained for longer time than it takes to liberate the therapeutic agent.
  • the coating may be broken down within ten times the time it takes to liberate the therapeutic agent, more preferably within five times the liberation time, more preferably within 4 times the liberation time, more preferably within 3 times the liberation time, more preferably within 2.5 times the liberation time, more preferably within 2 times the liberation time, such as within 1.5 times the liberation time.
  • the coating is broken down as soon as possible after the therapeutic agent has been released from the coat.
  • the coating may cover any percentage of the surface of the composition and the covering of any part - however small - will reduce the rate of liberation of therapeutic agent from the composition. Accordingly, the coating may cover at least 5% of the surface of the composition, such as at least 10 %, for example at least 15%, such as at least 20%, for example at least 25%, such as at least 30%, for example at least 35%, such as at least 40%, for example at least 45%, such as at least 50%, for example at least 55%, such as at least 60%.
  • the coating covers at least 67%, such as at least 70%, more preferably at least 75 %, more preferably at least 80 %, more preferably at least 85 %, more preferably at least 90 %, for example at least 91 %, such as at least 92 %, for example at least 93 %, such as at least 94 %, such as at least 95 %, for example at least 96 %, such as at least 97 %, for example at least 98 %, such as at least 99 %, for example at least 99.5 %.
  • the effect of the coating is increased.
  • the non-coated part of the surface is one, two or a few contiguous area(s). This may be part of the surface located on an end surface of the composition or both end surfaces may be non-coated. Production of the composition is facilitated when the non-coated areas are the end surfaces of the composition. The composition may then be extruded or moulded, be coated and subsequently cut into pieces of the desired length.
  • the non-coated part of the surface of the composition is coated by a coat functioning as a membrane.
  • the permeable coat must be permeable to both water and the therapeutic agent as well as to the constituents of the inner matrix.
  • the permeable coat is made such that diffusion across said permeable membrane is the rate limiting step in liberation of the therapeutic agent.
  • the inner matrix may be soluble in water.
  • examples of this are matrices based on a carbohydrate binder or matrices consisting essentially of the therapeutic agent in the form of a water soluble protein.
  • the inner matrix may also be degradable in water.
  • the example of this is an inner matrix based on a polymer, which can be broken down by enzymes in the tissue.
  • the inner matrix may comprise crystalline material, such as crystalline carbohydrates and/or crystalline therapeutic agent. Such material may advantageously be adapted for extrusion.
  • the inner matrix may contain at least 50 % (v/v) therapeutic agent, such as at least 60 %, for example at least 70 %, such as at least 75%, for example at least 80%, such as at least 85%, for example at least 90%, such as at least 95%, for example at least 97%, such as at least 99%, for example essentially 100%.
  • the remaining parts of the inner matrix may comprise binders and/or additives. Any suitable binder may be used, provided that it is acceptable for parenteral use, such as binders mentioned in the European Pharmacopoeia, the Japanese Pharmacopoeia and/or the US
  • binders include but are not limited to: carboxymethylcellulose (CMC), fructose, glucose, sucrose, sorbitol, maltose, maltitol, xylito, hydroxypropyl-cellulose, lactose, D-mannitol, MCC, HPC (hydroxypropylcellulose), Na-phosphates, K-phosphates, Ca-phosphates, Na- carbonates and/or Ca-carbonates.
  • CMC carboxymethylcellulose
  • fructose glucose
  • sucrose sucrose
  • sorbitol maltose
  • maltitol maltitol
  • xylito hydroxypropyl-cellulose
  • lactose lactose
  • D-mannitol lactose
  • MCC hydroxypropylcellulose
  • HPC hydroxypropylcellulose
  • the composition may comprise additives, which could be selected from but is not restricted to the group of preservatives, stabilisers, adjuvants, lubricants, and disintegraters.
  • additives which could be selected from but is not restricted to the group of preservatives, stabilisers, adjuvants, lubricants, and disintegraters.
  • Some therapeutic agents may need to be preserved or stabilised through the use of a preservative or stabiliser, although this is likely to be necessary only in a few cases, owing to the almost anhydrous conditions in the drug formulation. In the cases where the therapeutic agent is for immunisation, it may be preferential to add an adjuvant to increase the immunogenic response.
  • composition may comprise stabilisers, such as alanine, histidine and glycine.
  • compositions comprising crystalline inner matrix and an optional binder may be manufactured according to methods described in e.g. WO 01/26602 (Novo Nordisk A/S).
  • the inner matrix may comprise amorphous material, such as for instance a glass, such as described in WO 00/62759 (Novo Nordisk).
  • the therapeutic agent may be dispersed as crystalline particles.
  • compositions made according to this embodiment of the invention are particularly adapted for solid-dose parenteral injection through the cutis and/or mucosa, because they have sufficient mechanical strength to be injected without the used of a syringe or trocar.
  • the glassy inner matrix may for instance comprise a binder and at least one therapeutic agent, said binder constituting at least 0.5% by weight of the composition and said binder comprising at least one binding agent being a carbohydrate, and optionally at least one non-crystallisation agent, whereby said binder forms an amorphous matrix.
  • the binder may constitute from 5-60% by weight of the inner matrix, the remaining part of the inner matrix being essentially therapeutic agent.
  • the binder essentially remains an amorphous matrix for at least 6 months at ambient temperature. This is achieved by carefully selecting the binding agent and the optional non-crystallisation agent so that the binding agent does not crystallise during storage. If the binding agent starts crystallising the composition will lose its mechanical strength, or if the crystallisation only takes place at the surface, the geometry of the composition will change and the friction upon injection may increase undesirably.
  • At least 95 % of the strength of the composition may be maintained after 6 months, preferably after 12 months, at ambient temperature. It is important that these compositions are long term stable not only with respect to the biological activity and the structure of the composition, but also that the strength is essentially unaffected by storage.
  • Some binding agents have a propensity to slowly crystallise after the amorphous glass matrix has been formed. Such binding agents are unsuitable for the present embodiment.
  • the at least one binding agent which together with the optional at least one non- crystallisation agent comprises the binder may comprise from 50 to 97 % by weight of the binder. The preferred amount of binding agent is determined by numerous factors, primarily the actual compound chosen. Some binding agents may form the amorphous glassy matrix of the binder in a pure state and others will need to be mixed with the non-crystallisation agent in various amounts.
  • the at least one non-crystallisation agent may comprise at least 1 % by weight of the binder. In some cases very limited amount such as down to 1 % of non-crystallisation agent needs to be present to prevent crystallisation of the binding agent. The amount of non-crystallisation agent is determined largely by the propensity of the binding agent to crystallise.
  • Tg glass transition temperature of the compound
  • Glasses can also be formed by dissolution and subsequent removal of the solvent, whereby the Tg is raised to above the storage and usage temperature.
  • most compounds have a propensity to crystallise by themselves. Whereas an amorphous glass matrix often has a high compressive strength and a smooth surface, the same compound in a crystalline state has very limited compressive strength and a rough surface.
  • the present inventors have determined that compositions can be made from pure maltose or from pure sorbitol.
  • the compositions are not necessarily completely water free.
  • the water content of the binder is less than 20 % (w/w), preferably less than 10 %, more preferably less than 5 %, such as from 0.1 to 5 %, preferably from 1 to 5%. It has been determined that by having a water content between 0.1 and 5 %, the composition is not sticky. By lowering the water content even further, the rate of dissolution upon contact with the body fluids may be reduced causing the therapeutic agent to be released very slowly. Furthermore, many therapeutic agents such as proteins, peptides and polypeptides are more stable at a low water content than when completely dry. The advantage of having a low water content is that the therapeutic agent becomes biologically very stable and does not require special storage conditions such as refrigeration to maintain the biological activity.
  • a third advantage is that the composition becomes essentially resistant to microbial attack, since microbes require a certain water content in order to establish a colony.
  • the requirement for handling the compositions become less rigid since the presence of a few microbes on the composition will not result in microbic proliferation and thereby not cause contamination.
  • the presence of excess water in the composition may result in water vapour during processing, which may give rise to air entrapment in the composition during subsequent cooling.
  • the at least one binding agent is a mono-, di-, or oligosaccharide or a corresponding sugar alcohol or a derivative thereof.
  • the at least one binding agent is a mono-, di-, or oligosaccharide or a corresponding sugar alcohol or a derivative thereof.
  • Many of these compounds are frequently used for drug formulation, are contained in the pharmacopoeia and can therefore readily be approved by the authorities. Furthermore, these compounds make an amorphous glassy matrix readily.
  • the at least one binding agent may be a carbohydrate-derivative.
  • carbohydrates make amorphous glassy matrices readily.
  • the at least one binding agent is selected from maltose, sucrose, lactose, cellobiose, trehalose, maltulose, iso-maltulose, maltitol, sorbitol, mannitol, glucose, fructose, raffinose, melezitose, dextran, mannose, sorbose, melibiose, sophrose, turanose, lactulose, stachyose, and xylitol.
  • This group of carbohydrates has excellent amorphous glass matrix making abilities. Furthermore, the carbohydrates are well known and can be purchased at reasonable price and in well characterised grades.
  • the optional at least one non-crystallisation agent may preferentially also be a carbohydrate, said carbohydrate being different from the binding agent.
  • the non-crystallisation agent may be a mono-, di-, or oligosaccharide, a corresponding sugar alcohol, or a derivative.
  • the at least one non-crystallisation agent is selected from maltose, sucrose, lactose, cellobiose, trehalose, maltulose, iso-maltulose, maltitol, sorbitol, mannitol, glucose, fructose, raffinose, melezitose, dextran, mannose, sorbose, melibiose, sophrose, turanose, lactulose, stachyose, and xylitol.
  • Each combination of binding agent and non-crystallisation agent gives a unique amorphous glass matrix with a unique glass transition temperature, unique solubility, and unique strength.
  • the composition has been found to perform excellently when the binding agent is selected from maltitol, sucrose, sorbitol, and mannitol and the non-crystallisation agent is selected from sorbitol, maltitol, and mannitol. These compounds are often used for pharmaceutical compositions, they all have the advantage of being edible and without any side effects upon administration.
  • the binding agent is maltitol and the non-crystallisation agent is sorbitol and/or hydrogenated oligosaccharides.
  • maltitol can be obtained in quantities and in a very suitable grade.
  • Commercial maltitol is made by enzymatically degrading starch whereby a mixture of glucose, maltose, maltotriose and higher saccharides are formed. These are hydrogenated to form their corresponding sugar alcohols sorbitol, maltitol and hydrogenated oligosaccharides.
  • the product contains primarily maltitol and sufficient amounts of the other sugar alcohols to prevent the crystallisation.
  • Maltitol is tissue compatible, it is a well tested compound and has been used for years in the production of so-called sugarfree candies.
  • the binder comprising the at least carbohydrate and the optional at least one non- crystallisation agent should not reduce the stability of the therapeutic agent. This could for instance take place via chemical reactions between the therapeutic agent and the components of the binder, either during processing or during storage.
  • the at least one carbohydrate and the at least one non-crystallisation agent are preferentially chosen from the group of non-reducing sugars.
  • the Tg of the binder in the final composition should preferably be at least 30°C.
  • the Tg of the binder should be above ambient temperature, preferably 5 to 10°C above ambient temperature, or the composition will gradually melt during storage.
  • Tg e.g. 50°C.
  • the invention is not limited by an upper Tg of the binder. Binders having a Tg from 40 to 120°C are preferred. Depending on the therapeutic agent, it is preferred that the Tg of the binder is less than 90°C, more preferably less than 80°C. A majority of therapeutic agent are heat labile and although many proteins or peptides can tolerate exposure to elevated temperatures in a dry state a loss of activity may nevertheless be encountered during processing. To reduce exposure of the therapeutic agent to elevated temperatures it is therefore preferable to select binders with a low Tg with due respect to the lower limits mentioned above.
  • the viscosity of the composition is less than 50,000 Pa*s, preferably less than 40,000 Pa * s, more preferably from 1 ,000 to 30,000 Pa * s, in a sub-range of the temperature interval between 60 and 140°C. In this temperature interval the composition is in the state of a melt, which can be shaped.
  • most glasses encompassed by the present embodiment have a suitable viscosity for bringing into the desired geometry at 20 to 30°C or even approximately 40 C C above Tg of the binder.
  • the viscosity of the composition is very important during injection of the melt into the mould and furthermore in the embodiments where the therapeutic agent is mixed with the melted binder.
  • the composition may also be injection mouldable in a sub-range of the same temperature interval.
  • a preferred method for manufacturing the composition is by injection moulding. This means that the composition should possess a certain viscosity e.g. 1 ,000 to 30,000 Pa * s in at least a sub-range of the temperature interval 60 to 140°C.
  • the composition may be designed to have almost any release profile, which is longer and/or more constant than the release profile of a non-coated composition.
  • at most 70% of the therapeutic agent is released from the composition within 50 % of the total release time after administration. This compares with the non-coated counterpart in which the release is much more rapid, so that 80-90 % of the therapeutic agent is released within 50% of the total release time after administration.
  • compositions comprising therapeutic agents, which are to be released within hours or days or up to a week. Accordingly, at least 95% of the therapeutic agent may be released within one week, such as within 6 days, for example within 5 days, such as within 4 days, for example within 48 hours, such as within 47 hours, for example within 46 hours, such as 45 hours, for example 44 hours, such as 43 hours, for example 42 hours, such as 41 hours, for example 40 hours, such as 39 hours, for example 38 hours, such as 37 hours, for example 36 hours, such as 35 hours, for example 34 hours, such as 33 hours, for example 32 hours, such as 31 hours, for example 30 hours, such as 29 hours, for example 29 hours, such as 28 hours, for example 27 hours, such as 26 hours, for example 26 hours, such as 25 hours, for example 24 hours, such as 23 hours, for example 22 hours, such as 21 hours, for example 20 hours, such as 19 hours, for example 18 hours, such as 17 hours
  • the therapeutic agent is released as a pseudo 0-order release.
  • This can for instance be obtained through a composition, from which release takes place through an opening (non- coated part of the surface) having a constant area.
  • this is one example of a composition having approximate zero-order release.
  • the therapeutic agent may be released as a first order release. This could be obtained by giving the composition the shape of a cone, which is non-coated on the planar surface. Thus during release, the area from which therapeutic agent is released decreases at an approximately constant rate, and the rate of release of the therapeutic agent decreases at an approximately constant rate.
  • the composition may comprise any therapeutic agent, such as an agent is selected from analgesics, antianxiety drugs, antiarthiritic drugs, antibiotic agents, anticholinergics, antidepressants, antidiabetics, antiemetics, antihistaminics, antihypertensive agents, antiinflammatory drugs, antimigraine agents, antiparkinsonism agents, antipasmodesics, antipsychotics, antithrombotic agents, antiviral agents, appetite suppressants, blood factors, cardiovascular drugs, cerebral vasodilators, chemotherapeutic drugs, cholinergic agonists, contraceptives, coronary agents, diuretics, hormonal agents, immunosuppressive agents, growth factors, narcotic antagonists, opiods, peripheral asodilators, tranquilizers, vaccines, immunogenic agents, and immunising agents.
  • an agent is selected from analgesics, antianxiety drugs, antiarthiritic drugs, antibiotic agents, anticholinergics, antidepressants, antidiabetics
  • the therapeutic agent may be selected from hormones, lipids, nucleic acids, nucleotides, oligonucleotides, oligosaccharides, organics, peptide mimetics, antibodies, peptides, polysaccharides, and proteins.
  • the therapeutic agent is selected from proteins, peptides, and polypeptides, said protein, peptide, or polypeptide being amorphous or crystalline.
  • composition according to the invention is particularly suitable for administering therapeutic agents selected from hormones, antidiabetic drugs, growth factors, and blood factors, preferably being a protein selected from insulin, glucagon, growth hormone, coagulation factors such as FVII and FVIII, GLP-1 , EPO, TPO, interferon or derivatives of these proteins. Due to the possibility for approximate zero order release the composition is especially adapted for administration of therapeutic agents, which have to be present in a certain amount in the tissue and/or tissue fluids.
  • the therapeutic agent is insulin or a derivative thereof such as: an insulin hexamer, crystals of insulin, insulin cross-linked to protamin (for example marketed as Protafan® by Novo Nordisk), insulin cross-linked to zinc, acidic crystals of insulin, insulin precipitated with block-copolymers.
  • an insulin hexamer crystals of insulin
  • insulin cross-linked to protamin for example marketed as Protafan® by Novo Nordisk
  • insulin cross-linked to zinc for example marketed as Protafan® by Novo Nordisk
  • acidic crystals of insulin insulin precipitated with block-copolymers.
  • the amount of therapeutic agent in the composition should be as high as possible in order to keep the total volume of the composition low. It is thus anticipated that the therapeutic agent comprises at least 25 % by weight of the composition, preferably more than 30 %, more preferably more than 40 %, such as more than 50%, for example more than 60 %, such as more than 70%, for example more than 75%, such as more than 80%, for example more than 90%, such as more than 95 %.
  • composition is especially adapted for regular administration so that one composition contains one dose of the therapeutic agent.
  • the composition may also contain fractions of a dose, such that one dose corresponds to 2, 3, 4, 5, 6 or up to 10 compositions that can be administered at the same time.
  • the optional other components of the inner matrix should not reduce the stability of the therapeutic agent.
  • the solubility of of the optional other components of the inner matrix can be either higher or lower than the solubility of the therapeutic agent.
  • Examples of other components include but are not limited to preservatives, adjuvants, stabilisers.
  • the composition should be essentially free from entrapped air. It is very important for the strength of the composition that no air is trapped inside the composition during processing in order to prevent air in the composition after cooling. Apart from reducing the strength, entrapped air also takes up unnecessary space and thereby reduces the amount of therapeutic agent contained in the composition.
  • the composition preferentially has the shape of a pellet wherein the cross section of the pellet is substantially circular, triangular, square, or polygonal. According to an especially preferred embodiment, the composition has the shape of a rod essentially cylindrical and pointed at one end.
  • compositions according to the present invention are in the shape of microbeads, which are coated on part of their surface. Compared to non-coated microbeads these give a more constant rate of release because the initial peak observed with non-coated microbeads is reduced.
  • the top radius of the tip is preferably below half of the diameter of the composition as such, more preferably below a fourth of the diameter of the composition as such.
  • the composition acts like a needle and can penetrate the cutis or mucosa of the patient in the same way as a hypodermic needle to enter the subcutis or submucosa. Thereby less force is required to force the composition through the cutis or mucosa.
  • the composition has the shape of a needle it is especially important the composition remains stable and the tip does not deteriorate.
  • porcine abdomen skin has been used in penetration tests.
  • Graphite rods with differently shaped pointed ends are pressed into porcine skin with a Lloyd Instrument LR5K, UK.
  • the pressure force is measured in Newton as a function of the distance.
  • Using a graphite rod with a cone shaped point (90° top angle) is sufficient to penetrate the skin.
  • a top angle of 60° significantly improves the penetration of the skin.
  • the rod is preferably as pointed as possible, however, points with an angle below 10° are very thin and thereby fragile.
  • the top angle of the pointed end should preferably be between 10 and 110°, preferably between 20 and 90°, more preferably between 30 and 70°, if the composition is going to be injected without the use of a trocar or syringe.
  • compositions for parenteral injection must be able to withstand such pressure force.
  • the strength can be tested in a force gauge tester such as an Advanced Force Gauge AFG-250N from Mecmesin, UK. Tests are carried out by formulating the composition as a rod and applying a pressure force to the rod. The pressure force is increased until the rod breaks. The instrument records the pressure force necessary to break the rod. This parameter is termed the compressive strength and should be understood as the breaking strength under compression.
  • a rod-shaped composition is able to withstand a pressure force of at least 10 Newton.
  • a rod made from the composition is able to withstand a pressure force of at least 5 Newton.
  • the composition has a well-defined compressive strength, which is furthermore sufficient to endure the force required to penetrate the epidermis.
  • the compositions are injected with the use of a trocar. Such compositions do not need such a strength.
  • the composition is preferably in the form of a pellet.
  • the cross section of the pellet may be substantially cylindrical, triangular, square or polygonal.
  • the composition has the shape of a rod being essentially cylindrical.
  • the composition may have a constant cross section in the longitudinal direction which facilitates production and in combination with one or two non-coated ends ensures an approximate zero-order release.
  • the composition may also have a variable cross section in the longitudinal direction. This could potentially give a variable release rate according to the variation in the cross section.
  • shapes of the composition include the shape of a bead, a sphere, a hemisphere, a cube, a cone, a prism, and an irregular shape.
  • the composition may have a maximum cross section of less than 2 mm, such as less than 1 mm, preferably from 0.7 to 0.3 mm, more preferably 0.6 to 0.4 mm.
  • the composition may be manufactured in any length but for most applications, the length of the rod is less than 10 mm, preferably less than 8 mm, more preferably less than 6 mm.
  • the length of the composition is determined by the dose of the therapeutic agent, the amount of binder required if any, and the selected diameter.
  • the dose of many therapeutic proteins is approximately 1 mg.
  • One mg of protein excluding binder corresponds approximately to a cylinder with a diameter of 0.5 mm and a length of 3 mm. If such a composition containing 1 mg of protein is made from
  • the composition has a length of 6 mm.
  • a dose of 1/3 mg protein in a composition with 50 % binder for the inner matrix and having a diameter of 0.5 mm has an approximate length of 2 mm.
  • the invention is not restricted to any specific volume, the volume being determined by the length and diameter of the composition. In most cases, the volume of the composition is less than 5 ⁇ l, such as less than 4 ⁇ L, for example less than 3 ⁇ L, such as less than 2 ⁇ L, for example less than 1 ⁇ l. Volumes down to 0.25 ⁇ l can be obtained for small doses of therapeutic agent.
  • the above-mentioned composition having a diameter of 0.5 mm and a length of 2 mm has a volume of
  • the composition may have sufficient strength to be able to penetrate the epidermis or mucosa of a human being with a force less than 5 Newton without the use of a trocar or syringe. This greatly facilitates administration and decreases the risk of cross contamination between and among patients and has the advantage that trocars and/or syringes are not necessary
  • composition is adapted to be injected using a trocar or a syringe, in which case strength is not an important parameter.
  • compositions according to the present invention may be manufactured in a number of different ways, primarily depending on the structure of the inner matrix.
  • the method may comprise shaping the inner matrix comprising at least one therapeutic agent into a pellet, and subsequently coating said pellet with a biodegradable polymer.
  • the coated pellet may advantageously be cut into elongated compositions. These compositions will then only be coated on the longitudinal surfaces and be non-coated on the cut end surfaces.
  • the pellet is in the shape of a rod.
  • compositions may be shaped either by extrusion, injection moulding, and/or compression. Injection moulding is especially suitable for compositions wherein the inner matrix comprises a glassy carbohydrate-based binder.
  • Coating may be performed either by dipping the pellet into a solution of the biodegradable polymer, by spraying the pellet with a formulation of the biodegradable polymer, or by vapour deposition of a formulation of the biodegradable polymer on the pellet, followed by drying. These methods will give relatively thin coatings in the vicinity of 1 ⁇ m or thicker depending on the viscosity of the solution of biodegradable polymer and/or the time used for spraying or vapour deposition.
  • Coating may also comprise co-extrusion of the inner matrix and the coat, which will generally result in a thicker coat in the size of 100 ⁇ m.
  • biodegradable polymer It is essential that only part of the surface of the finished compositions are coated with biodegradable polymer. This may be obtained by coating only part of the surface of the composition with biodegradable polymer, or by making at least one hole in the biodegradable polymer after coating.
  • the at least one hole may be made by cutting a rod as described above, but it can also be performed by using of a laser for making the at least one hole.
  • compositions with a coating are through coating a mould with a biodegradable polymer, melting and injecting an inner matrix comprising at least one therapeutic agent into the mould, and after hardening, cutting the resulting rod into elongated compositions being non-coated on the end surfaces.
  • a simple computer simulation on a model for diffusion from different geometries shows the principle of delaying the absorption by coating parts of the surface.
  • the model consists of three distinct zones:
  • Zone 1 is the drug and the binder on a solid form, for example as a glass.
  • Zone 2 that is, the material is dissolved
  • Material that enters Zone 3 in which there is free flow, is removed fast and is considered to have been absorbed.
  • Figure 1 shows the development of the composition in time when no coating is present.
  • Figure 2 shows the development of the composition in time when half the surface is coated.
  • Figure 3 shows the development of the composition in time when only a small part of the composition is left open.
  • Figure 4 shows a graph of the release of material from the composition a function of time for each of the cases A, B and C.
  • Curve A composition of Fig 1
  • Curve B composition of Fig. 2
  • Curve C composition of Fig. 3
  • Figure 5 shows the development of the elongated composition in time when the composition is uncoated.
  • Figure 6 shows the development when only the ends are uncoated.
  • Figure 7 shows the development of the composition in time when the composition is uncoated.
  • Figure 8 shows the development when only the ends are uncoated.
  • Figure 9 shows a graph of the release of material from the composition a function of time for each of the cases E (Fig. 5), F (Fig. 6), G (Fig. 7) and H (Fig. 8).
  • 1.0 g of insulin is mixed with 1.0 g of water.
  • the mixture was kneaded with a spatula in a glass bottle until homogeneity.
  • the mixture was placed in a Ray-Ran test sample moulder from Ray-Ran Engineering, UK.
  • the mixture was extruded through a 0.5 mm hole.
  • the resulting rods were dried for 24 hours.
  • the compressive strength was tested with an Advanced Force Gauge AFG-250N from Mecmesin, UK.
  • the compressive strength of the rods (diameter 0.5 mm, length 5 mm) was between 2 and 5 N and the rods were therefore not able to penetrate human skin, but had to be administered using a trocar or syringe.
  • the rods were investigated under microscope and air entrapment was observed.
  • mannitol 0.4 g was dissolved in 3.6 g water.
  • 1.6 g of insulin is mixed with the mannitol solution.
  • the mixture was kneaded with a spatula in a glass bottle until homogeneity.
  • the mixture was placed in a Ray-Ran test sample moulder from Ray- Ran Engineering, UK.
  • the mixture was extruded through a 0.5 mm hole.
  • the resulting rods were dried for 24 hours.
  • the compressive strength was tested with an Advanced Force Gauge AFG-250N from Mecmesin, UK.
  • the compressive strength of the rods was between 1 and 5 N and the rods were therefore not able to penetrate human skin, but could be administered using a trocar or syringe.
  • the rods were investigated under microscope and air entrapment was observed.
  • compositions do not have the physical strength to be parenterally injected.
  • One of the reasons for the lack of strength is the presence of entrapped air.
  • such compositions will need to be injected by use of a hypodermic needle, a trocar or similar means.
  • composition comprising a binder. 100% C * Maltidex H 16323 (88% maltitol)
  • compositions with a very high strength.
  • a composition was moulded from CMaltidex which contains 88% maltitol.
  • This product contains in itself sufficient "impurities”, primarily sorbitol and sugar alcohols of maltotriose and higher oligosaccharides, acting as non-crystallisation agents.
  • Composition comprising 50% binder 50% insulin.
  • the example illustrates the advantage of preparing a composition without adding water. Although the melt is prepared at 95°C, the reduction in insulin activity is negligible. This is primarily a consequence of the almost anhydrous state of the glass matrix. Many heat labile therapeutic agents, typically proteins, polypeptides and peptides, tolerate relatively high temperatures in the absence of water.
  • Example 3 dip-coating with PLGA.
  • a 10% solution of poly lactic acid-glycolic acid copolymer with a lactic acid/glycolic acid ratio in the polymer of 75/25 was perpared in methylene chloride.
  • the elongated compositions according to example two were immersed into the solution and left to dry at room temperature.
  • the coating layer had a thickness of 0.14 mm. After dipping and drying, the elongated compositions were cut thereby leaving both ends of the compositions un-coated.

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Abstract

L'invention concerne une composition pharmaceutique solide à administration parentérale. Cette composition comprend une matrice intérieure contenant au moins un agent thérapeutique, et un revêtement imperméable à l'eau et biodégradable recouvrant une partie de la surface de ladite composition, ladite matrice intérieure se désintégrant lorsqu'elle est en contact avec un tissu animal ou avec des fluides tissulaires. Ce revêtement est fabriqué à partir d'un matériau choisi dans le groupe constitué par des polyesters tels que des polyglycolides, des polylactides et des copolymères à base d'acide polylactique/polyglycolique (PLGA) etc. La matrice intérieure peut contenir un liant, du mannitol par exemple, et le principe actif peut contenir de l'insuline.
EP02787456A 2001-12-18 2002-12-17 Micro implant a dose solide Withdrawn EP1458352A1 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
DKPA200101901 2001-12-18
DK200101901 2001-12-18
PCT/DK2002/000865 WO2003051328A1 (fr) 2001-12-18 2002-12-17 Micro implant a dose solide

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EP1458352A1 true EP1458352A1 (fr) 2004-09-22

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US6375972B1 (en) 2000-04-26 2002-04-23 Control Delivery Systems, Inc. Sustained release drug delivery devices, methods of use, and methods of manufacturing thereof
US8871241B2 (en) 2002-05-07 2014-10-28 Psivida Us, Inc. Injectable sustained release delivery devices
WO2005000278A1 (fr) * 2003-06-26 2005-01-06 Mediolanum Pharmaceuticals Ltd. Implants sous-cutanes a liberation initiale de principe actif controlee, puis a liberation prolongee a variation lineaire
PL2233112T6 (pl) * 2003-11-13 2014-11-28 Psivida Inc Wstrzykiwalny implant o przedłużonym uwalnianiu mający biodegradowalną matrycę i biodegradowalną warstewkę
US8685435B2 (en) 2004-04-30 2014-04-01 Allergan, Inc. Extended release biodegradable ocular implants
EP3047860A1 (fr) 2006-07-20 2016-07-27 OrbusNeich Medical, Inc. Composition polymère bioabsorbable pour un dispositif médical
US7959942B2 (en) 2006-10-20 2011-06-14 Orbusneich Medical, Inc. Bioabsorbable medical device with coating
CN103212115B (zh) 2006-10-20 2016-09-14 奥巴斯尼茨医学公司 可生物吸收的聚合物组合物和医疗设备
EP1917971A1 (fr) * 2006-10-27 2008-05-07 Société de Conseils de Recherches et d'Applications Scientifiques ( S.C.R.A.S.) Préparations à libération prolongée comprenant des polymères à poids moléculaire très bas
AU2014253541B2 (en) * 2007-02-22 2016-07-28 Glide Pharmaceutical Technologies Limited Solid pharmaceutical and vaccine dose
GB2446780A (en) 2007-02-22 2008-08-27 Glide Pharmaceutical Technolog An elongate parenteral injection body having an injection point of angle 10 to 40 degrees.
GB2545880A (en) 2015-10-20 2017-07-05 Glide Pharmaceutical Tech Ltd Solid formulation
CN110730655B (zh) 2017-06-13 2024-03-05 视点制药公司 可生物侵蚀的药物递送装置

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SK279964B6 (sk) * 1991-12-27 1999-06-11 Merck & Co. Dávkovacia forma na riadené uvoľňovanie liečiva a
WO1993017662A1 (fr) * 1992-03-02 1993-09-16 Daratech Pty. Ltd. Implants ameliores
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JP2005517651A (ja) 2005-06-16
JP2010280709A (ja) 2010-12-16
AU2002351739A1 (en) 2003-06-30
JP4615862B2 (ja) 2011-01-19
WO2003051328A1 (fr) 2003-06-26

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