Patent Application
20120282189
The present invention relates to medicinal aerosol formulations for use with pressurised metered dose inhalers (abbreviated pMDI or MDI), and especially improved medicinal aerosol formulations suitable for aerosol administration.
Drugs for the treatment of respiratory diseases and disorders, such as β2-agonists and anti-cholinergics, corticosteroids, anti-allergies, and others, are frequently administered directly to the lungs via inhalation. Administration via inhalation can increase the therapeutic index and reduce side effects of the drugs compared to administration by other routes, such as orally or intravenously. Administration by inhalation can be in the form of either dry powders or aerosol formulations which are inhaled by the patient either through use of an inhalation device or as a spray.
MDIs are known devices for the administration of aerosol medicinal formulations to the respiratory tract through inhalation by the patient. The term MDI is used to describe a metered dose inhaler, of which a standard unit comprises a canister filled with the medicinal formulation, a drug metering valve and a mouthpiece. The MDI may be selectively activated by the user to deliver successive individual doses of drug by actuation of the metering valve, such that an accurately metered dose of the formulation is expelled via the actuator mouthpiece for delivery into the patient's respiratory tract.
MDI formulations are an advantageous delivery method for many reasons, including that they deliver the drug instantaneously and do not rely on the inhalation capacity of the user. This is particularly important when considering the type of condition to be treated with the drug, such as an asthma attack. Since MDI devices usually contain a sufficient amount of the medicinal formulation for multiple unit doses, it is important that the formulation is such that it may be successfully and repeatedly used with a MDI device. The formulation must be delivered in a reliable manner and in the correctly calculated dose. The formulation must also comply with the requirements for pharmaceutical quality, stability and robustness set out by regulatory bodies.
MDIs typically use a propellant to expel droplets or particles of the formulation as an aerosol, containing the drug, to the respiratory tract.
For a long time the propellant gases used were fluorochlorohydrocarbons which are commonly called Freons or CFCs, such as CCl3F (Freon 11 or CFC-11), CCl2F2 (Freon 12 of CFC-12), and CCClF2-CClF2 (Freon 114 of CFC-114). However it has been discovered that these CFC propellants are particularly harmful to the environment and their production and, at the time of writing, their use in medicinal formulations is being phased out. An alternative propellant was therefore sought which was safe to use with inhalation drugs.
Hydrofluoroalkanes (HFAs), also known as hydro-fluorocarbons (HFCs), have been proposed as alternative propellant gases, because they contain no chlorine and are considered to be less destructive to the atmosphere. In particular 1,1,1,2-tetrafluoroethane (HFA 134a) and 1,1,1,2,3,3,3-heptafluoropropane (HFA 227) have been found to be good replacement propellants for the CFC propellants and a number of medicinal aerosol formulations using these propellants have been proposed.
Formulations administered via MDIs can be in the form of solutions or suspensions. In suspension formulations the drug is manufactured as a fine particle powder which is then suspended in a liquefied propellant or propellant blend. The suspension formulation can be stored in a sealed canister with sufficient pressure to maintain the propellant in liquid form. For example, the vapour pressure for a HFA227 formulation may typically be around 1.96 bar at 0° C., 3.90 bar at 20° C. and 7.03 bar at 40° C. In solution formulations the drug is solubilised in the liquefied propellant phase. When the metering valve is actuated, a dose is delivered in rapidly deployed fine droplets.
Suspension formulations are usually preferred because of generally improved chemical stability of the suspended particles in comparison to solubilised drugs. Stability problems associated with the chemical degradation of solubilised drug compounds are known in the art.
In order that a medicinal formulation is suitable for use with an MDI device, the particle size of the deployed aerosol must be small enough that it can be inhaled into the lungs of the users, be that a grown adult, child or elderly/infirm person. Therefore, the particles of the suspension formulation need to be microfine with a mean aerodynamic particle diameter (measured as Mass Median Aerodynamic Diameter (MMAD)) of about 1 to 10 μm, and preferably 1 to 6 μm. Micronised particles of this size can be obtained by various methods known in the art, for example mechanical grinding or spray drying.
The amount of active drug deployed in fine, inhalable particles is called the fine particle dose (FPD) or the fine particle fraction (FPF), which is defined as the percentage of the fine particle dose relative to the total amount of released active compound. Both are determined by the measurement of the aerodynamic particle size distribution with a cascade impactor or liquid impingers. These are routine tests for which the methods and apparatus are described in the pharmacopoeias. For example, formulations of the present invention meet the requirement set out in Chapter <601> of the United States Pharmacopoeia (USP) 32 or in the inhalants monograph 2.9.18 of the European Pharmacopoeia (Ph. Eur.), 6th edition 2009.
Microfine particles for use in suspension formulations do, however, have some associated drawbacks. They have a large surface area and therefore an unfavourable ratio of surface area to volume or mass. This ratio results in strong interaction forces between the particles and undesirable powder cohesion and adhesion tendencies. This in turn can lead to difficult handling due to poor flow rate of the powdered drug during manufacture and poor suspension properties of the MDI formulation. Such powders are therefore difficult to formulate for use with a MDI device, difficult to handle and are strongly influenced by electrostatic charge, processing methods, humidity, etc.
Formoterol fumarate dihydrate (hereafter called formoterol) is a long acting β2-agonist bronchodilator (β-sympathomimetic) commonly used for the relief of asthma symptoms. Fluticasone propionate (hereafter called fluticasone) is a potent synthetic corticosteroid which is also often prescribed as a treatment for asthma, chronic obstructive pulmonary disease and allergic rhinitis. Both are examples of drugs which can be individually delivered via a MDI product.
Formoterol and fluticasone (but in particular formoterol) are each notoriously difficult compounds to be formulated for use with MDIs. One reason for this is because the potency of these drugs means that only a very small dose should be delivered in each case and the concentration of the drug within the HFA formulation is therefore very low. This exacerbates the problems highlighted above with regard to the manufacture of the aerosol formulation and the pharmaceutical quality, stability and robustness of the aerosol formulation, as required by the regulatory authorities, can therefore be compromised. Robustness of the formulation may be determined when handled by the patient, under different conditions of use, upon prolonged storage or upon storage under stress conditions (e.g. freeze-thaw cycles). Due to the low concentration of drug present within the formulation, fluctuations in the local homogeneity of the drug suspended in the propellant (i.e., in a volume range of about 50 μL) can result in deviation in the delivered dose.
It has also been shown that MDI formulations comprising hydrofluoroalkanes (HFAs) as propellants are difficult to formulate because there are only a limited number of currently known suspension aids that are regarded as safe for inhalation, which can be employed to reduce undesirable particle cohesion and adhesion tendencies and to improve the physical stability of the suspension formulation using such HFA propellants.
Furthermore, chemical stability of the HFA formulations is particularly a problem when bronchodilator β2-agonists, such as formoterol, are used owing to their susceptibility to oxidative and hydrolytic conditions. Hydrolysis is one of the major identified factors affecting degradation of formoterol under stress conditions (e.g. 40° C./75% relative humidity) because such formulations are usually sensitive to moisture and are susceptible to the ingress of moisture from the surrounding air.
Slight concentration changes or changes in the physical stability of the MDI suspension which may occur during storage due to temperature changes and/or moisture ingression may lead to significant differences in the metered and delivered doses (e.g. dose uniformity failures). These differences may also be seen as a reduction in the inhalable proportion of the released dose, which is determined in vitro as the FDP or FPF.
This reduction may be caused by strong adsorption of drug particles to internal surfaces of the container closure system (canister and metering valve) and by agglomeration of microfine particles as a result of imperfect suspension stability. It is found that water molecules, which may accumulate in the MDI formulation during long term storage and use, are particularly detrimental to the suspension since they interact with the polar drug particles and result in a stronger binding between the particles.
In view of the above described problems, it is generally thought to be key to prevent ingression of water to reduce hydrolysis of formoterol formulations.
Cromolyn sodium (DSCG) is an excellent internal moisture scavenger and a suspension enabler. It has been used for administration via the inhalation route and has been demonstrated to be clinically safe. However, it has been shown that cromolyn sodium itself has a biological pharmacological effect and so its use in the HFA formulations described above has previously been avoided so that an effect over and above that of the fluticasone and formoterol is not seen.
The type of propellant used also has an effect on the actuation of the metered dose inhaler. The use of HFA propellants instead of CFC propellants has led to a further problem with the fine particles of suspended drug. This is because the HFA propellants have a higher polarity than the CFC propellants previously used, which causes the HFA suspension formulations to be comparatively more susceptible to physical stability problems. When active agents are used that have a density lower than that of the liquid in which they are placed then they have a tendency to float and cream which can lead to an irregularity in the dosage delivered. The drugs also frequently adhere to the inside surface of the device and the dosage mechanism.
This deposition on the walls of the metering valve has been found to be significantly increased compared to the CFC propellant. This deposition can lead to a reduction in the actual dose dispensed. This adherence can also lead to the device failing owing to a clogging of the internal mechanisms of the canister or blockage of the metering valve.
Previously proposed devices have used a container in which the interior surfaces are coated with fluorocarbon polymer plastics; see WO-A-96/32150 and U.S. Pat. No. 6,596,260. However, the problems with such systems include that the fluorocarbon polymers, and their constituents, can be soluble in the propellants used in the aerosol formulations. Also such coatings themselves need to undergo safety tests and product formulation development in order to give a safe and stable product. These tests further add to the production cost which adds to the overall cost of the product.
Coating the internal surfaces of the containers to prevent adsorption also causes problems with regard to the use of certain metals for the canister. The most commonly used metals for the canister are aluminum alloys. The plastics coating must undergo heat treatment in order to be cured which results in the strength of the container being compromised because the metal canister layer becomes softer and malleable from the heat.
The plastics coating material itself can also lead to contamination of the medicinal formulation because there is the potential for leachable compounds to find their way into the formulation contained within the canister. Such leachable compounds can lead to degradation of the drug compound within the medicinal formulation and a less effective and less robust product. The shelf-life of the product may also be compromised with degradation of the active ingredients upon storage.
There are, therefore, a number of important parameters that need to be considered when producing a medicinal aerosol formulation for use with a MDI.
Some of the difficulties in formulating fluticasone propionate and formoterol fumarate within a single formulation have been addressed in WO 2005/034911 by the introduction of a drying step to dry the formoterol fumarate prior to mixing it together with the other ingredients. However, the problems associated with long term storage of such formulations have not been addressed.
The present application seeks to alleviate at east some of the aforementioned problems with the prior art.
Accordingly, a first aspect of the present invention is directed to a medicinal aerosol suspension formulation for MDI administration, comprising (a) a micronised β2-agonist, (b) a micronised corticosteroid, (c) a sub-therapeutic quantity of a moisture-scavenger excipient, and (d) a HFA propellant wherein (a), (b) and (c) and their respective relative amounts are selected such that they associate to form floccules having a density substantially the same as that of the HFA propellant.
It has been found that the constituents of the present formulation tend to associate in such a way as to form floccules (also known as flocs, flocculi or flocculates). Floccules comprise a loosely held mass or aggregation of discrete fine particles held together in a network-like fragile structure, suspended in solution. The aggregates formed by the floccules tend to break up easily under the application of small amounts of sheer stress, such as gentle agitation of the canister, and reform an extended network of particles after the force is removed. Flocculation, therefore, imparts a structure to the suspension with virtually no increase in viscosity. In contrast to deflocculated systems, the floccules will settle rapidly, usually to a high sediment volume and may be easily re-suspended even after standing for prolonged periods of storage, for example after 3, 6, 9 or 12, 18 months or longer.
It has been found that, once associated, the floccules of the present formulation have a density to match that of the density of the propellant in which they are placed. This gives the floccules the ability to remain in suspension without the tendency to cream, float or sink. The suspension formulation of the present invention may therefore remain in a viable formulation for an extended period of time and results in a robust product with an extended shelf life and improved reliability of the end product.
Furthermore, the tendency to faun these floccules may provide enhanced uniformity in the suspension and less fluctuation in the local homogeneity which then results in a product which may have reduced deviation in the delivered dose.
In addition to the above, the floccules afford an increased stability to the suspension formulation. This increased stability of the suspension means that the ingredients associate together in preference to associating with the internal surfaces of the canister or metering valve of the inhaler. Therefore there is a reduced tendency to adhere to the inside of the container or the metering valve of the canister through which the suspension formulation must pass. This may lead to an increase in the reliability of the delivered dose. In addition there are fewer tendencies to block the actuation mechanism and the metering valve, which in turn provides for a formulation which can be reliably and repeatedly dispensed at the correct amount.
Typically, suspension formulations, especially MDI suspension formulations using HFA propellants are inherently physically unstable. The formulations form two phases, a liquid propellant phase and a suspended particulate phase, which segregate as a result of gravitational force. Within the canister, areas having different concentrations of suspended particles may also exist as a result of small temperature fluctuations inside the canister which leads to thermal motion of particles. However, the tendency of formulations according to the present invention to associate to form floccules results in all the active ingredients remaining associated right up until the moment they are dispensed from the MDI and enter the patient's respiratory system. This provides for a formulation with an improved quality and improved ability to adhere to a calculated dose.
Preferably the HFA propellant is HFA 227. HFA 227 is an inert propellant with low toxicity and is suitable for use in metered-dose inhalers. HFA 227 propellant, when combined with a small amount of ethanol to form the liquid propellant phase has a calculated density, over a range of temperatures, as follows:
The above numbers were calculated using thermodynamic laws on ideal mixtures. However, in practice the liquid mixtures are likely to behave as non-ideal mixtures and the “true” densities may be slightly different to the calculated values.
It is therefore advantageous to have a formulation wherein the average density of the floccules (comprising the micronised β2-agonist, micronised corticosteroid and moisture-scavenger excipient) is substantially the same as the density of the propellant ±0.2 g/cm3, preferably ±0.1 gcm3, more preferably ±0.05 g/cm3 of the propellant.
The average density of the floccules may be calculated using any standard technique, for example by determining the true particle density of each solid component by helium pycnometry. The density of the floccules may therefore substantially match that of the density of the propellant over a range of temperatures of 10° C. to 30° C. under which a MDI would usually be operated by a user.
Preferably the corticosteroid is fluticasone propionate or a pharmaceutically acceptable salt thereof. The corticosteroid is advantageously present in an amount of 0.01-0.6% by weight; preferably between 0.02-0.5% by weight; and more preferably 0.03-0.4% by weight, based on the total weight of the formulation. This is the advantageous amount in order to be effective in use and also to form the correct density of floccules for suspension in the propellant.
The corticosteroid preferably has a defined particle size of less than 10 μm for 100%, less than 6 μm for 90%, less than 3 μm for 50%, and less than 2 μm for 10% of the particles.
Preferably the β2-agonist is formoterol fumarate dihydrate or a pharmaceutically acceptable salt or derivative thereof. The β2-agonist is preferably present in an amount of 0.003-0.04% by weight; preferably 0.004-0.03% by weight; and more preferably 0.005-0.02% by weight, based on the total weight of the formulation. In a preferred embodiment, formoterol fumarate dihydrate may be employed in an amount of 0.003-0.008% by weight, based on the total weight of the formulation. In an alternative preferred embodiment, formoterol fumarate dihydrate may be employed in an amount of 0.01-0.04% by weight, based on the total weight of the formulation. As with the corticosteroid, this is the advantageous amount of β2-agonist in order to be able to be effective in use and also to form the correct density of floccules for suspension in the propellant.
The β2-agonist preferably has a defined particle size of less than 10 μm for 100%, less than 6 μm for 90%, less than 3 μm for 50%, and less than 2 μm for 10% of the particles.
Preferably, the moisture scavenger excipient is sodium cromolyn (DSCG) and is advantageously present at sub-therapeutic levels such that it does not exert a biological effect itself and is pharmaceutically inactive. The moisture scavenger is therefore suitably present in an amount of 0.01-0.1% by weight; preferably 0.016-0.09% by weight; more preferably 0.02-0.08% by weight; more preferably 0.025-0.07% by weight; more preferably 0.03-0.05% by weight; more preferably 0.03-0.04% by weight, based on the total weight of the formulation.
The moisture scavenger preferably has a defined particle size of less than 10 μm for 100%, less than 6 μm for 90%, less than 3 μm for 50%, and less than 2 μm for 10% of the particles.
It has been found that DSCG is an excellent suspension enabling agent when used in formulations including a HFA propellant. DSCG itself consists of particles which encourage and allow the formation of heterogeneous floccules with the active agents.
DSCG acts to aid stabilisation of the formulation, particularly against hydrolysis by competitive water absorption. DSCG exists as a single crystal form that is non-stoichiometric with regard to water content and adsorbs or desorbs water rapidly in response to changes in relative humidity. DSCG crystals are universal in the extent of reversible water absorption without collapse of the crystal lattice and can absorb up to 9 molecules of water per mol, which is about 24% w/w. The crystal structure analysis by X-ray diffraction reveals the existence of channels that are capable of reversibly accommodating a variable number of water molecules (depending on the ambient relative humidity) with only small dimensional changes within the lattice. Despite its large moisture adsorption capacity DSCG is not deliquescent (like, for example, sodium sulphate) but is solid in the range of 10 to 90% r.h.
In the present invention DSCG acts to stabilize the fine particle fraction (FPF) in the formulation by competitively binding free (i.e. molecular dissolved) water present within the propellant phase. This assists in stabilising the fine particle fraction by preventing agglomeration of suspended particles (i.e. formation of liquid and/or crystal bridges) and particle growth (i.e. Ostwald ripening) on stability. This allows for a more robust product during storage and use as the formulation has improved tolerance to the presence of internal water. For example, up to 600 ppm of total internal water may be tolerated. Furthermore this allows for a much longer ‘use period’ once the product is in the patients hands. In addition, there is a reduced tendency to adhere to surfaces, which allows the medicinal formulation to be used with an uncoated canister instead of a canister which has its internal surfaces coated with a polymer.
Preferably the medicinal aerosol suspension formulation further comprises a wetting agent; more preferably the wetting agent is a dehydrated alcohol; and most preferably the wetting agent is ethanol which may be present in an amount of 0.01-3% by weight; preferably 0.05-2.5% by weight; and more preferably 1.0-2.0% by weight, based on the total weight of the formulation.
A wetting agent facilitates the wetting of the active agents within the liquefied propellant and thus the suspension manufacture such that the active agents do not become partially solubilised. The addition of such agents requires a delicate balancing act between allowing the active agents to become wetted without being partially solubilised and causing them to be partially solubilised such that Ostwald ripening, particle growth and, eventually, stability failures occur.
Ethanol can be added in small quantities as it also helps to prevent the deposition of the active agents on the walls of the canisters and mechanical parts.
In a preferred form, the formulation of the present invention therefore comprises as pharmaceutically active ingredients formoterol and fluticasone and as pharmaceutically inactive ingredients sodium cromolyn, HFA 227 and ethanol.
A further aspect of the present invention is directed to a pharmaceutical composition comprising, 0.01-0.6% by weight of micronised corticosteroid; 0.003-0.04% by weight of micronised β2-agonist; and 0.01-0.1% by weight of sodium cromolyn.
Preferably the corticosteroid is micronised fluticasone propionate.
Advantageously the β2-agonist is micronised formoterol fumarate dihydrate.
Preferably the pharmaceutical composition further comprises a wetting agent, more preferably the wetting agent is a dehydrated alcohol, most preferably ethanol. Preferably the wetting agent is present in an amount of 0.01-3% by weight; preferably 0.05-2.5% by weight; and more preferably 1.0-2.0% by weight, based on the total weight of the formulation.
A further aspect of the present invention is directed to a pharmaceutical suspension formulation comprising about 0.003-0.04% formoterol fumarate dihydrate, about 0.01-0.06% fluticasone propionate, about 0.01-0.1% suspension agent and about 0.01-3% dehydrated alcohol.
Preferably the suspension agent is sodium cromolyn (DCSG) which also allows the active agents to remain in the suspension state for a prolonged period of time. This improves the shelf-life of the product as it can be effective for a longer time after production.
Furthermore, DSCG acts as a ‘bulking agent’, since its use increases the concentration of particles suspended in the formulation, therefore minimising inherent concentration changes in the suspension without the need for the addition of other excipients. DSCG also provides the usual benefits of bulking agents, namely affording the preparation of a more homogeneous suspension, which leads to improved accuracy of the dose.
A further aspect of the present invention is directed to a product containing formoterol fumarate dihydrate, fluticasone propionate and sodium cromolyn as a combined preparation for separate, sequential or simultaneous use in the treatment of inflammation and preferably for the treatment of asthma and allergic rhinitis.
A further aspect of the present invention is directed to the use of sodium cromolyn in the preparation of a pharmaceutical suspension formulation in HFA propellant comprising fluticasone propionate and formoterol fumarate dihydrate microparticles for forming floccules of fluticasone propionate, formoterol fumarate dihydrate and sodium cromolyn having a density substantially the same as that of the HFA propellant.
According to a further aspect of the present invention, there is provided the use of 0.01 to 0.1% sodium cromolyn in the preparation of a pharmaceutical suspension formulation in HFA propellant comprising 0.01 to 0.6% fluticasone propionate and 0.003 to 0.04% of formoterol fumarate dihydrate microparticles for forming floccules of fluticasone propionate, formoterol fumarate dihydrate and sodium cromolyn having a density substantially the same as that of the HFA propellant.
Preferably, the average density of the floccules is substantially the same as the density of the HFA propellant ±0.2 g/cm3 preferably ±0. 1 gcm3, more preferably ±0.05 g/cm3 of the propellant.
Preferably, the pharmaceutical suspension formulation additionally comprises a wetting agent, preferably a dehydrated alcohol, preferably ethanol.
According to a further aspect of the present invention, there is provided a method of increasing the stability of a medicinal aerosol suspension formulation of a micronised β2-agonist and a micronised corticosteroid in HFA propellant over a prolonged period of storage, comprising the addition of a sub-therapeutic amount of sodium cromoglycate, wherein the respective relative amounts of the micronised β2-agonist, micronised corticosteroid and sodium cromoglycate are selected such that they associate to form floccules having a density substantially the same as that of the HFA propellant.
Preferably the prolonged storage is for 3, 6, 9, 12 or 18 months. Preferably the water content of the suspension formulation after prolonged storage is in the range of 500 ppm to 800 ppm, preferably 600 ppm to 700 ppm.
Examples of suitable dosage strengths of a pharmaceutical composition in accordance with the present invention may be found in the following table.
Following is a description by way of example only with reference to the accompanying drawings of embodiments of the present invention.
In the drawings:
FIG. 1—Aerodynamic particle size distribution for fluticasone and formoterol.
FIG. 2—Photographs of Suspension in Glass Vials at Different Time Points after Shaking.
The following compositions shown below in Table 2 were made up and the density of the floccules of fluticasone, formoterol and cromolyn sodium were calculated and compared to the calculated density of the liquid phase (comprising 1.43% w/w of anhydrous ethanol and HFA 227) over a range of temperatures.
The density of the liquid phase was determined based on the thermodynamic laws on ideal mixtures. However, in practice the liquid mixtures are likely to behave as non-ideal mixtures and the “true” densities may be slightly different to the calculated values.
The average density of the floccules was determined by measuring the true particle density of each solid component by helium pycometry.
The results of the density calculations are shown in Tables 3 and 4.
It can be seen from the above results in Tables 3 and 4 that the average density of the floccules substantially matches the calculated density of the liquid phase within ±0.2 g/ml.
The batches shown in Table 5 were made up and tested (over a range of ‘use temperatures’ from 10 to 30 degrees Celsius):
The size of each batch was 3.3 kg (approximately 300 units). Ethanol 96.5% w/w (97.75% v/v) was used to challenge the formulation with a water level which was about similar to the amount contained in the formulation at the end of the envisaged shelf-life. The water content of all raw materials except HFA 227 was determined by Karl-Fischer analysis prior to preparation of the suspension.
The appropriate amounts of the micronised active substances were weighed and transferred into the batching vessel. The appropriate amount of sodium cromolyn, (DSCG) was added and the vessel closed. The propellant mixture of HFA 227 (apaflurane) with 1.45% alcohol was made in a separate vessel and transferred into the batching vessel. The solid materials were dispersed in the liquefied propellant by use of a rotor-stator homogenizer at 2900 rpm for 30 min. The homogeneous bulk suspension was cooled to 4° C., and re-circulated between the vessel and the Pamasol aerosol filling machine P2001.
Pharmaceutical aerosol canisters with 14 ml brimful volume were crimped with 50 mcl metering valves using a Pamasol P2005 crimping machine Aliquots of 11±0.5 g suspension were filled into the crimped canisters by the P2001 filling machine The weight of each filled canister was checked; all filled canisters were subjected to a heat stress test at 56° C. and stored one month prior to assembly with the actuator for testing.
Glass vials were filled in addition to the above canisters with the fluticasone/fomoterol formulations of Batch 1 and Batch 2 HFA-MDI to assess suspension stability visually and by time lapse photography, see
The following analytical tests were formed in relation to Batch 1 and 2:
Table 7 shows the water content of the batches when ethanol 96.5% w/w was included in the formulation, thereby adding 500 ppm to the formulation in addition to the moisture typically present due to the manufacture process itself. The slightly higher value for Batch 1 may have been due to the presence of DCSG. The water level found in the two batches is that as would typically be expected after long-term storage of the product or after shorter term storage in humid conditions (e.g., 75% RH or higher). The values obtained therefore demonstrate that the formulations of Batch 1 and Batch 2 (or other equivalent batches produced in the same way using ethanol 96.5% w/w) can be used to demonstrate the effect of inclusion of DCSG within a formulation of fluticasone/formoterol on the parameters listed within Table 6, above, as would be found, for example, after long-term storage of the formulation.
It can be seen that the drug concentration for the formation with DCSG was higher than that of Batch 2 with 95.1% of target fluticasone and 95.5% of target formoterol content achieved with DCSG in comparison to 92.2% and 90.6% respectively without DCSG. This could be associated with drug losses during manufacturing due to drug absorption on the manufacturing equipment.
Table 8 shows the results of testing dose delivery from 10 inhalers for each Batch. The inclusion of DCSG within the formulation is shown to deliver a higher dose of both drugs (e.g. 92% with DCSG in comparison to 79% without for fluticasone).
The results of the dose content uniformity study during the life of the canister, as shown in Table 9, also shows that a higher dose of both drugs is delivered by Batch 1 (with DCSG) (89.6% with DCSG in comparison to 79.9% without for fluticasone).
The above table shows that nearly twice as much of both drugs was recovered from canisters and valve of Batch 2 in comparison to Batch 1 (with DCSG) (e.g. 608 μg of fluticasone recovered for Batch 1, compared with 1100 μg for Batch 2).
Batch 1 (with DSCG) exhibited large loose floccules soon after cessation of agitation (this result was different from that seen when the formulation is not challenged with water) while Batch 2 (without DSCG) remained more disperse and more homogeneous.
After a longer period of time, however, Batch 1 remained in the loosely flocculated form, resulting in a bulky but readily redispersible sediment while Batch 2 appeared to form agglomerates of different densities, some of which sedimented and others of which floated. At least part of the sedimented material present within the glass vial of Batch 2, which formed a creamed material deposited on the glass vial surface at the liquid-gas interface, was difficult to redisperse into a homogeneous suspension.
Visual examination therefore revealed that Fluticasone/formoterol formulation with DSCG (Batch 1) floccules more rapidly than the same formulation when not challenged by additional water, but remained homogeneous long enough to provide a satisfactory and consistent dose uniformity. In contrast, the formulation without DSCG prepared for comparison (Batch 2) creamed rapidly and resulted in drug deposition on the glass vial surface at the liquid-gas interface. These visual observations therefore provide evidence that the formulation of the present invention is able to tolerate high amounts of internal water.
In conclusion, the use of DSCG as an enabling excipient in Fluticasone/formoterol formulation HFA-MDI thus provided a more robust finished drug product, particularly against moisture ingress, which occurs unavoidably during storage and use.
The following batch was made up using the process described in Example 1:
The filled unpouched inhalers were put into an investigational stability program for 6 months at 40° C./75% RH and showed good product quality and robustness in the product performance tests, as shown by the results of Tables 12 and 13, below.
The following batches were made up using the process described in Example 1:
The results of the stability investigation up to 12 months demonstrated good product quality and robustness of both formulations, as shown by the results displayed in Tables 15 and 16, below.
| Number | Date | Country | Kind |
|---|---|---|---|
| 0918149.6 | Oct 2009 | GB | national |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/EP2010/065573 | 10/15/2010 | WO | 00 | 7/24/2012 |
