Patent Application
20050019411
The present invention concerns drug formulae in powder form for nasal administration, insufflators filled with said formulae, and a method for obtaining them. Moreover, the present invention concerns primary particles for the formation of agglomerates contained in the drug formulae for nasal administration.
The present invention concerns the nasal administration of drugs.
A pharmaceutical product for nasal topical administration, for example a drug intended to “clear” the nose when affected by a cold, is commonly composed of the formula containing the drug and of the insufflator, which deposits the drug in the nasal cavity. The insufflating device and the formula (in liquid or solid form) are therefore both optimised for reciprocal use and each formula must be suitable for the insufflator used.
A characteristic required in particular from powders for nasal topical administration is that these should be at the same time fine and coarse: fine to favour their deposition in the nose, coarse to favour their introduction and dosage inside the insufflating device. This paradox is typical of all powders for inhaling, whether they be intended for inhaling through the nose or the lungs.
Despite the difficulties as described above, the need to have new ways of administering drugs in order to obtain an rapid effect without having to resort to injection has encouraged researchers to further explore the possibility of using inhalation not only for topical, but also for systemic administration. In fact, in recent years scientific literature has seen a growing interest in administration by inhalation, through nose or lungs, for drugs with a systemic action. This way in fact allows the absorption even of substances with a high molecular weight, when rapid action is desired. The respiratory epithelium is relatively extensive and the connective tissue below is characterised by a thick capillary network. For this reason the respiratory region of the nose is considered a useful site for an absorption which gives rise to a pronounced systemic effect.
As is known, the nose is often used for the abuse of psychoactive substances, but officially the administration of drugs through the nasal mucosa to obtain a systemic action is little used. Most of the nasal preparations in fact contain drugs used for a local (topical) effect on the mucosae. Instead, in order to obtain a systemic effect, the nasal means of administration could allow rapid action to be obtained for drugs that are usually administered by mouth. In fact, thanks to the high vascularisation of the nasal mucosa, the plasmatic peak time of the drug is shortened. Moreover the venous blood from the nasal cavities flows directly into the systemic circle, avoiding a possible effect of a first passage through the liver. Although nasal administration also has its limits, these limits are widely known and can be easily respected or overcome. In practice, the only limitations that must be considered require mostly that the administered dose of drug should not be too high and that the therapy should not be chronic.
While in theory all drugs with a systemic effect could be contemplated for nasal administration, in the light of the above considerations, there are nevertheless certain categories of drugs that are more suitable than others for nasal administration. Potential candidates preferred for nasal formulae are analgesic drugs for the treatment of non chronic pain (piroxicam, morphine, dextropropoxyphene, endorphin), tranquillising or sleep-inducing drugs for the treatment of stress pathologies (Diazepam, Lorazepam), antinausea or antiemetic drugs (metoclopramide), antikinetosis drugs (dimenidrinate), vitamin B12, calcitonin, nicotine, myorelaxing agents (thiocolchicoside), antimigraine agents, in any case, though without excluding many others.
As explained above it is of particular importance for the studies concerning the development of inhaling products that the nasal product should be composed of the formula and of the insufflator or dosing device that allows administration of the formula. According to the directives expressed in the Pharmacopeiae of various countries, the insufflating device and the formula are usually inseparable, in particular in the case of solid formula (powders) and to such an extent that the replacement of the insufflator with another believed similar may (but not necessarily) lead to a variation of bio-availability. This concept is linked to the fact that the nasal absorption of the drug must be preceded by the depositing of the preparation in the nasal cavity. The means of depositing inside the nose depends on the formula, on the insufflator, and in particular on the fluid-dynamic characteristics of the latter, which determine the suspension of the pharmaceutical formula in the flow of conveying gas to produce a cloud of solids. It is clear that, in the absence of a suspension of the formula in the flow of gas, and consequently in the absence of deposition of the formula on the mucosa, there will be no absorption of the substance.
Anyway, the deposition by insufflation of a drug in the nasal cavity also depends a great deal on its formula. The aerodynamic diameter of the supplied particles is the most important characteristic for the bio-availability of the drug insufflated into the nose. According to a method described in the world's major Pharmacopeiae (see for example the “Glas Impinger test” (Apparatus A) listed in Farmacopea Europea, III Edition 1997, paragraph 2.9.18., page 143), it has been established that particles with a diameter smaller than 6.4 μm, by insufflation, are certainly deposited in the lungs, whereas those with a larger diameter do not reach the lungs, but are deposited along the airways. Consequently, particles with a diameter smaller than 6.4 micron (μm) are generally classified as “breathable”. To ensure deposition in the nose instead of in the lungs, the dimensional distribution of substance supplied is therefore a critical factor.
Generally, the use of formulae in powder form, rather than liquids, allows a more controlled dimensional interval of the insufflated substance. With respect to a solution, the stability is increased and the bio-availability of the drug could be favoured. After the powder has been deposited on the nasal mucosa it dissolves locally, giving rise to a saturated solution of the drug at the level of the site of absorption, which determines transport through the mucosa at the same rate as the limit flow of the drug. Moreover, to facilitate absorption it is possible to use bioadhesive materials which allow the time of contact of the powder with the mucosa to be extended.
However, as mentioned above, powders for nasal administration must possess particular dimensional characteristics: they should be fine so that they can be efficiently conveyed by the flow of gas and so that they can be correctly deposited in the nose, but at the same time they should be coarse to facilitate the introduction of the dose in the insufflating device. Moreover, in cases where the insufflator is not loaded with individual pre-established doses of powder, but where an internal mechanism takes the required quantity for each dose one by one from a silo containing the insufflator itself, the powder must also be sufficiently coarse to make dosing efficient and precise at the time of being taken. So, while the powder for producing an aerosol (a cloud of solids dispersed in a flow of gas) must be fine, on the other hand the powder to be dosed in the containers of an insufflator must be fluid, and fluidity is a typical property of coarse powders.
This paradox is typical of all powders for inhaling, whether they be intended for inhaling through the nose or the lungs. A solution to this paradox, described in patent literature (see for example EP 1 036 562) and applied up till now exclusively for powder for inhaling in the lungs, particularly those with a topical effect, has been the construction of aggregates of particles, held together by weak forces of attraction. These aggregates, called “soft pellets”, are prepared from micronised particles having a mean diameter smaller than 10 micron, obtained with a powder grinding (micronising) procedure. Soft pellets have dimensions of a few hundred microns and a roundish shape. For these reasons they are perfectly fluid and suitable for the operations of filling the containers with the dose. Soft pellets are then demolished into the particles making them up through the turbulence in the conveying air flow generated by the aerosol device, substantially restoring the dimensional distribution of the original micronised powder. The fact that the dimensional distribution of the original micronised powder is obtained is critical for the aerosol's ability to be breathed into the lungs, since only particles with an aerodynamic diameter smaller than 6.4 microns can penetrate the lungs. Substantially, as appears in EP 1 036 562, it may be concluded that the objective of the “soft pellets” technology is to make available formulae for pulmonary administration of active principles with a prevalently topical action.
However, there are some cases, especially when a systemic effect is required, in which nasal administration, if feasible, would be preferable by far to pulmonary administration. In fact there are some drugs which can demonstrate perturbing collateral effects in that they irritate the pulmonary airways and thus produce bronchial spasm, a problem which becomes even more accentuated when patients have to be treated who also suffer from attacks of asthma. Instead, as the nasal mucosae are by nature more exposed to exogenous substances of every type, they are far less sensitive and therefore tend less to become sites of perturbing or even painful conditions for the patient.
Unfortunately, however, the soft pellets technique is not applicable in the specific field of nasal powders. The main reason is that there is an essential difference between nasal and pulmonary inhalation, consisting of the different required dimension of the particles of product supplied to obtain nasal deposition, in comparison with the pulmonary method. In fact, the dimension of the powder entering the respiratory apparatus to be deposited in the nose must be at least another of magnitude larger than that intended for the pulmonary route. So for deposition in the nose, the particles must have a diameter at least an order of magnitude larger than 6.4 microns (preferably larger than 10 microns), to avoid their being breathed inadvertently.
Besides, a technical solution based simply on the preparation of larger particles could compromise the release of the drug, once the powder has been deposited on the nasal mucosa. It is known that the speed of dissolving of a drug in powder form depends on the dimensions of the particles: the smaller the particles, the faster they dissolve. While a decrease of the dissolving speed and also the consequent effect of a delayed and maybe prolonged availability may be acceptable or even desirable in the context of the administration of certain highly soluble drugs with a topical effect, this certainly does not apply to drugs with a topical effect that are not very soluble, and even less in cases where a systemic effect is to be obtained.
Clearly, for systemic nasal administration carried out to obtain rapid action, it would not be logical to propose the administration of particles with large dimensions, as they would lead to a decrease of the dissolving speed and therefore a slow action. So the particles must absolutely be kept within the range of small dimensions, without at the same time causing them to be breathed into the pulmonary tract. Therefore the paradox of powders for inhalation, in the case of nasal powders, is even more complex, since the particles would have to be small in order to dissolve quickly, but not so fine as to risk being breathed. Moreover they must be sufficiently large to be able to be handled during the preparation and dosing of the pharmaceutical product.
The aim of the present invention is therefore to overcome the problems described above and therefore to provide formulae of drugs in powder form for nasal, preferably systemic, administration.
A further aim of the present invention is to provide formulae of drugs in powder form for nasal, preferably systemic, administration which are adaptable to the insufflating devices currently available.
A further aim of the present invention is to provide procedures for obtaining formulae of drugs in powder form for nasal, preferably systemic, administration.
A further aim of the present invention is to provide insufflators loaded with formulae of drugs in powder form for nasal, preferably systemic, administration.
A further aim of the present invention is to provide primary particles that can be used for the formation of agglomerates usable in the formulae of drugs in powder form for nasal, preferably systemic, administration.
These and other aims that will appear more clearly below are achieved by the formulae of drugs in powder form as in claim 1. Moreover, claim 22 provides a procedure for obtaining formulae of drugs in powder form as in claim 1. Claims 18 and 21 provide, respectively, a nasal insufflator loaded with a formula as in claim 1 and primary particles for obtaining agglomerates usable in the formulae as in claim 1.
In particular,
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The present patent application aims to provide remedies to the difficulties identified above and therefore describes new preparations in powder form suitable for the nasal administration of drugs, preferably with a systemic effect, by insufflation, insufflating devices loaded with said new preparations, as well as the technique and the intermediate products necessary for their preparation.
In particular, the preparation of formulae able to overcome the paradox related to the optimum dimensions requires, for nasal application, new technological solutions based on methods and on excipients suitable for the formation of said formulae.
The present application therefore describes how to make a nasal powder able to satisfy the two different technological requirements for the preparation of the dose and the supply of the prepared substance. Claims are therefore made for nasal formulae made with a new technology with which powders may be obtained which, though composed of primary particles having dimensions of a few micron suitable for rapid dissolving on the mucosa and therefore advantageously suited for systemic administration, are presented as agglomerates of said particles, having dimensions of hundreds of microns, and are therefore suitable for dosing of the drug in the insufflator. The powder for insufflation described is able to deliver different quantities and numerous types of drugs to the nasal mucosa.
To satisfy not only the paradox of inhaling powders in general, but also and above all the paradox of nasal powders in particular, the present patent application describes the construction of agglomerates from primary particles with small dimensions, held together by weak forces of attraction. These agglomerates, on account of their specific behaviour at the time of their suspension in the conveying gas flow to form a cloud of solids dispersed in the gas flow, make up a so-called “chimerical” form of the inhaling powder. They are in fact prepared from primary particles with micronic dimensions (that is from a few μm up to a few tens of μm), in particular having a diameter-volume established by light scattering between 1 and 50 micron, preferably between 1.5 and 29 micron.
Preferably, the dimensional distribution of the primary particles (in the diameter-volume interval from 1 to 50 micron) is such as to present a median diameter-volume (D50) established by means of light scattering between 3 and 11 micron, 80% of the primary particles falling in the diameter range between 2 micron (D10) and 20 micron (D90), D10 constituting the lower diameter percentile value, that is the value not reached by 10% of the population of the primary particles, and D90 constituting the higher diameter percentile value, not reached by 90% of the population of primary particles.
More preferably, the dimensional distribution of the primary particles (in the diameter-volume interval from 1.5 to 29 micron) is such as to present a mean diameter-volume (D50) established by means of light scattering between 4 and 6 micron, 80% of the primary particles falling in the diameter range between 2 micron (D10) and 9 micron (D90), D10 constituting the lower diameter percentile value, that is the value not reached by 10% of the population of the primary particles, and D90 constituting the higher diameter percentile value, not reached by 90% of the population of primary particles.
Instead, the agglomerates are composed of primary particles as above and they exist only in the phases that precede the supply of the product. These agglomerates have dimensions of hundreds of microns. In particular, these agglomerates have a diameter of at least 106 micron, selected by screening; more preferably their diameter selected by screening is between 106 and 1000 micron, and their shape is generally spherical or roundish. For these reasons the agglomerates are fluid and suitable for the operations of filling the containers with the dose and for dosing inside the insufflator. The air turbulence produced during insufflation, that is the conveying gas flow supplied, suspending the formula to create a cloud of dispersed solids, demolishes the agglomerates at least partially to create fragments, giving origin—by reduction of the dimensional distribution of the aggregates—to a new powder (composed of agglomerates and their fragments) with a dimensional distribution having a prevailingly non breathable diameter (>6.4 μm), but suitable for nasal deposition.
In particular, the mist of solids dispersed in the gas flow at the time of supply from the insufflator contains a fraction of at least 80% in weight, preferably of at least 85% in weight, or even more preferably of 90% or even 95% in weight, of solids having a non breathable diameter (>6.4 μm). For example, cases are preferred where, in the gaseous suspension composed of agglomerates and their fragments, at least 60% of the weight of the solids has a diameter, selected by screening, larger than 53 micron.
It should be noted that the reduction of the initial dimensional distribution of the aggregates according to the present invention for disaggregating in the conveying gas flow takes place uniformly but for a relatively small factor (<8), preferably between 1.1 and 3 and even more preferably between 1.1 and 2.
In particular, according to a preferred form of the present invention, formulae of drugs in powder form are supplied for preferably systemic, nasal administration, by means of a suspension of said powder in a conveying gas flow at the moment of supply from a special insufflator, said powder being composed of agglomerates with a diameter of at least 106 micron selected by screening, composed of homogeneous primary particles comprising the drug and structuring excipients having a diameter-volume established by light scattering between 1 and 50 micron, characterised in that said agglomerates, at the moment of their suspension in the gas flow, are at least partly disaggregated so as to produce, in the cloud of solids dispersed in the gas flow, a fraction of at least 80% in weight, composed of agglomerates and of their fragments, the solids contained in said fraction having a non breathable diameter.
The present application also describes a procedure for the preparation of a formula of a drug in powder form for nasal administration, which as said above is “chimerical” in that it is presented as composed of agglomerates of small particles (that is “primary” particles), such that once insufflated it is transformed into fragments of such agglomerates, rather than into the original primary particles. The primary particles of this powder, having dimensions of a few micron, in particular between 1 and 50 micron and preferably between 1.5 and 29 micron (diameter-volume established by light scattering) are obtained with a spray drying technique, applied to a solution of auxiliary substances (structuring excipients and possible additional aids) and drug. These particles, having dimensions between 1 and 50 micron, or, preferably between 1.5 and 29 micron, are called primary particles, because after their production they are agglomerated directly to obtain soft agglomerates, with dimensions of a few hundred micron, preferably at least 106 micron, and selected by screening. This procedure, which is described in greater detail below, reduces by one step the method described in patent EP1036562 for pulmonary soft pellets.
Now, returning to the agglomerates of the present invention, these agglomerates are therefore defined “chimerical agglomerates” because their existence, in terms of dimension, is functional only for the dosing of the powder in the insufflator and limited to the production phases that precede insufflation. After insufflation with an air jet device (or, more generally, with a “conveying gas flow”, and therefore independently of the type of gas used to obtain the jet), these chimerical agglomerates are fragmented by the turbulence of the conveying gas flow.
However, due to the relatively low disaggregating factor (<8, preferably between 1.1 and 3, and more preferably between 1.1 and 2), the fragments obtained are not the primary particles, as described in patent EP 1036562, but still aggregates of the primary particles, though having dimensions smaller than the chimerical aggregates. In other words, the relatively low disaggregating factor (<8 or preferably between 1.1 and 3, and more preferably between 1.1 and 2) distinguishes the present invention and constitutes a fundamental difference with respect to the “soft pellets” technology, in which one does not seek to obtain a new powder with an intermediate dimension, but one regenerates the primary particles from the agglomerates, obtaining a cloud of particles with a prevalently breathable dimension (<6.4 micron).
The fragments of chimerical agglomerates of the present invention are particularly suitable for the nasal administration of drugs because, after being deposited on the nasal mucosa, since they are weak aggregates of fine primary particles, they do not prevent a fast dissolving of the drug. At the same time they are prevalently sufficiently coarse to prevent their being breathed.
While the disaggregating of given chimerical agglomerates of the present invention depends, to a certain extent, also on the fluid-dynamic characteristics of the insufflator used, the experiments carried out by the inventors of the present application have demonstrated that a turbulent conveying gas flow with a speed between 5 l/min and 15 l/min and with a total supplied volume between 5 ml and 80 ml is able to suspend and to disaggregate adequately, according to the present invention, a dose composed of between 0.5 mg and 40 mg of nearly all the samples chosen from a vast range of different formulae (that is comprising different combinations between mean dimensions of primary particles and of aggregates) according to the present invention. While these fluid-dynamic conditions are exemplary only for insufflators by Valois (model Monopowder P), Miat (Miat spa, Milan, Italy) and Puvlizer (Teijin Ltd. Tokyo, Japan), it was found that the disaggregating of the formulae of the present invention was still adequate even in extreme conditions, that is at gas flow rates created artificially with external sources and between 2 l/min and 60 l/min. The possibility of the operation at much slower or much faster flow rates than those prescribed further confirms the versatility of nasal powders according to the present invention. In particular, in the case of slow supply (for example with the Puvlizer insufflator), despite the need for several activations until the complete dose has been supplied, no substantial impact was found on the dimensional distribution of the supplied cloud of solids which always fell within the criteria of the present invention. Moreover, the experiments have demonstrated that even a gas flow rate much higher than the one usually generated in the insufflators currently on the market does not regenerate the primary particles, but maintains the dimensional distribution of the supplied cloud of solids within the range contemplated by the present invention Consequently, it has been demonstrated that the formulae of drugs in powder form according to the present invention are suitable for use with all the nasal insuflators currently on the market (or are easily adaptable by the expert in the field, by selecting a suited combination of the size of the primary particles and of their agglomerates).
It has thus been seen how the new technology described in the present application is able to control the dimension of an agglomerate of primary particles during supply and guarantees that an aerosol will be obtained that is suitable for depositing the drug at the level of the nasal mucosa after insufflation in the nostrils. In this way the possibility of the supplied material entering the lungs is very slight. The peculiar formula of the primary particles and the method adopted for preparing them ensure that these primary particles give rise to agglomerates which, when subjected to a turbulent jet of conveying gas, produce fragments larger than the primary particles. Moreover, these “chimerical” agglomerates and their fragments, on account of their composition, in the presence of water or of mucous are instantly decomposed or disaggregated into the primary particles, without in this way limiting the dissolving of the drug carried. Thus, the availability for rapid absorption through the nasal mucosa—which is critical, for example, for a formula with a systemic effect, but may also be contemplated for determined topical applications, when the active principle presents very poor solubility—is therefore not prevented by the agglomeration.
In particular, the primary particles according to the present invention are prepared by means of a spray drying method of a solution comprising the drug and one or more structuring excipients, together with optional adjuvant excipients, for example through the drying of an aqueous or water-alcohol solution of a drug and excipients. The structuring excipients are described in more detail below. Among adjuvant excipients, the leading ones to be mentioned are surface-active substances. Further adjuvant excipients may be chosen and incorporated in suitable quantity—where necessary—by the expert in this field, from the “usual” excipients in this field, that is from those authorised by the Pharmacopeia. A non limiting example for a class of further adjuvant excipients is represented by the various pharmaceutically acceptable preserving agents.
The method according to the present invention allows primary particles to be obtained directly in the desired dimensional interval, avoiding subsequent grinding operations.
The structuring excipients necessary for the formation and for the structuring of the primary particles may be used individually or as blends and they are chosen from the group that consists of sugars, amino acids, cellulose polymers, cyclodextrines, chitosane, solid polyethylenglycols and polyalcohols.
In particular, among the polyalcohols, mannitol, sorbitol and xylitol are to be mentioned.
In particular, among the sugars, lactose, sucrose, glucose, trehalose and fructose are to be mentioned.
In particular, among the amino acids, glycine, leucine and isoleucine are to be mentioned.
In particular, among the semi-synthetic cellulose polymers the natural or semi-synthetic celluloses are to be mentioned, for example methylcellulose or hydroxypropylmethylcellulose.
The primary particles (and also the agglomerates subsequently obtained from them) are characterised in that the active principle (that is the drugs) contained in them replaces the structuring excipient (or the blend of structuring excipients) in a percentage between 0.1 and 90% and that these drugs are for example chosen from the group that comprises analgesics; anti-cough drugs; tranquillisers; sleep-inducing drugs; drugs used in the therapy to break the habit of smoking, alcohol and opioids;
Preferably the drugs are chosen from the group that comprises piroxicam, dextropropoxyphene, endorphin, diazepam, dimenidrinate, thiocolchicoside, alnitidan, apomorphine, buprenorphine, bupropion, buserelin, butorphanol, calcitonin, codeine, desmopressin, dihydroergothamin, L-dopa, doxepin, enalaprilate, dronabinol, recombinant human erythropoietin, folic acid, G-CSF (Granulocite Colony Stimulating Factor), growth hormone secretagogues (GHRP-6), glucagon, gonadorelin, goserelin, aloperidol, heparin, hydromorphon, growth hormone, insulin, LHRH, lorazepam, lidocain, lipressin, melatonin, meperidin, methylphenidate, metoclopramide, midazolan, morphine, nafarelin, nalbufin, naltrexone, nicotine, estradiol, oxytocin, progesterone, prometazin, propanolol, parathyroid hormone, raloxifene, serotonin, sildenafil, tamoxifene, testosterone, tetracosactide, derivatives of delta-9-tetrahydrocannabinol, sumatriptan, urokinase, vitamin B12, endorphins, thiocolchicosides and caffeine.
Depending on the composition and on the presence of the structuring excipients as above, these primary particles may be grouped together to form chimerical agglomerates. The primary particles are agglomerated by making them roll in a cylindrical or kidney-shaped glass container which rotates on its own base. The inventors of the present application have found, however, that, if the rolling container is made of bakelite, the formation of the agglomerates is faster, more reproducible and quantitative, even starting from powders that do not tend to form electrostatic charges.
In particular, the procedure preferred for obtaining formulae of drugs in powder form according to the present invention comprises the following phases:
In cases where the drug and the structuring excipient (or one of the optional adjuvant excipients, in particular surface-active substances) are not soluble in the same solvent, the solution comprising the drug and the structuring excipient or the structuring excipients and the optional adjuvant excipients, in particular surface-active substances, is obtained by mixing a first solution of the drug with one or more second solutions of structuring excipients and optionally of adjuvant excipients, in particular surface-active substances. Preferably, mixing is carried out in such proportions as not to cause precipitations of the solutes. Preferably, to obtain the different solutions, solvents are used which are different but which are miscible among each other. In cases where this is not possible and there is very poor reciprocal miscibility of the various solvents used, a further (co-) solvent may be used as a miscibility mediator. Preferably, the said mixing is carried out in such proportions as not to cause precipitations of the solutes.
Moreover, the inventors of the present application have discovered that the agglomeration of the primary particles is achieved in an almost quantitative manner when a surface-active substance is included in their composition—in a percentage of weight, with reference to the quantity of the total dry formula, between 0.1% and 10%—as the preferred adjuvant excipient. Instead, in the absence of said surface-active substance, in some cases, the chimerical agglomerates are formed in a minimum quantity, or the powder tends to stick too the bottom of the rotating container due to an excess of electrostatic charges. In particular, the most suitable surface-active substances for obtaining this result have proved to be phospholipids, for example lecithin, semi-synthetic mono- or diglycerides, sorbitan esters, polyoxyethylensorbitan esters and poloxamers.
A further important innovation of this invention consists of the fact that the inventors have discovered that the presence of the surface-active substance offers the possibility of constructing primary particles and agglomerates, with any type of drug and with different quantities of the same drug, without altering the yields of the agglomeration method. In fact, the inventors have been able to find a basic composition, made up essentially of a polyalcohol and a sugar, preferably mannitol or lactose, and a small quantity of surface-active substance, preferably lecithin, able to receive different quantities of active principle or different active principles, simply by replacing in the composition itself a quantity of polyalcohol or sugar with the corresponding quantity of active principle. This basic composition, which contains a sugar (such as lactose or trehalose) or a polyalcohol (such as mannitol, xylitol, sorbitol or other), can also be transformed into primary particles by spray-drying, in the presence of other excipients or polymers such as chitosane, polyethylenglycols, semi-synthetic celluloses or cyclodextrines, which also perform a structuring activity for the primary particles and for the agglomerates prepared subsequently.
Below are listed some preparations which illustrate the composition and the creation of the primary particles and of the corresponding chimerical agglomerates. The examples listed highlight the importance of some substances for the success of the preparation for nasal application. Firstly a basic formula is described, composed of a sugar or of polyalcohol combined with a surface-active substance.
As an example, without any limiting intention, the drug caffeine has been considered for the formula of the chimerical agglomerates in nasal powder described herein, inserting the drug in the basic formula in a quantity between 10 and 70% by weight. The basic formula of nasal powder described has proved to be able to receive different quantities of active principle.
Without wishing to limit in any way the possibility of using other excipients to prepare primary particles and chimerical agglomerates from them, the components of the formula listed here as examples were mannitol between 25 and 95%, lecithin between 0 and 10%, hydroxypropylmethylcellulose (Methocel E3) between 0 and 2% and polyethylenglycol 6000 between 0 and 5%.
95 g of mannitol were dissolved in 2500 ml of distilled water, kept in agitation at 40° C. 5 g of lecithin dissolved in 400 ml of ethanol were dispersed in the solution obtained. The solution obtained was spray-dried using a spray-drying device (Mini Spray Dryer Buchi Model B-191), in the following operative conditions:
The powder obtained was composed of particles having a median diameter-volume (D50), established by means of a “light scattering” test, of 4.5 μm, with a measured yield of 70% with respect to the quantity of solid present in the sprayed solution. The dimensional distribution of the powder thus obtained was such that 80% of the powder was in the diameter range between 2.45 μm (D10) and 7.72 μm (D90), D10 being the lowest diameter percentile value, that is not reached by 10% of the population of primary particles, and D90 being the highest diameter percentile value, that is not reached by 90% of the population of primary particles.
A quantity of 1 g of powder of primary particles was put into a bakelite cylinder (diameter 5 cm; length 4.4 cm), or alternatively into a kidney-shaped glass container, which was rotated on its own base at a speed of 30 rpm for 30 minutes. During rotation the powder rolled inside the cylinder. As a result of the rolling, the primary particles tended to become electrostatically charged, giving rise to spherical aggregates which grew in diameter with the length of the rolling period. The aggregates obtained were selected by screening, separating the fraction between 106-850 μm which was considered the nasal powder in the form of chimerical agglomerates. The yield of this preparation, that is the quantity of agglomerates obtained with respect to the original powder, was 80%, both after agglomeration in a glass container and after agglomeration in a bakelite container.
10 g of caffeine and 83.3 g of mannitol were dissolved in 2500 ml of distilled water, kept in agitation at 40° C. 6.7 g of lecithin dissolved in 400 ml of ethanol were dispersed in the solution obtained. The solution obtained was spray-dried using a spray-drying device (Mini Spray Dryer Buchi Model B-191), in the following operative conditions:
The powder obtained was composed of particles having a median diameter-volume (D50), established by means of a “light scattering” test, of 4.36 μm, with a measured yield of 60% with respect to the quantity of solid present in the sprayed solution. The dimensional distribution of the powder thus obtained was such that 80% of the powder was in the diameter range between 4.06 μm (D10) and 4.93 μm (D90), D10 being the lowest diameter percentile value, that is not reached by 10% of the population of primary particles, and D90 being the highest diameter percentile value, that is not reached by 90% of the population of primary particles.
A quantity of 1 g of powder of primary particles was put into a bakelite cylinder (diameter 5 cm; length 4.4 cm), or alternatively into a kidney-shaped glass container, which was rotated on its own base at a speed of 30 rpm for 30 minutes. During rotation the powder rolled inside the cylinder. As a result of the rolling, the primary particles tended to become electrostatically charged, giving rise to spherical aggregates which grew in diameter with the length of the rolling period. The aggregates obtained were selected by screening, separating the fraction between 106-850 μm which was considered the nasal powder in the form of chimerical agglomerates. The yield of this preparation, that is the quantity of agglomerates obtained with respect to the original powder, was 89%, both after agglomeration in a glass container and after agglomeration in a bakelite container.
65.1 g of caffeine, 2 g of Methocel E3 and 27.9 g of mannitol were dissolved in 3500 ml of distilled water, kept in agitation at 40° C. 5 g of lecithin dissolved in 400 ml of ethanol were dispersed in the solution obtained. The solution obtained was spray-dried using a spray-drying device (Mini Spray Dryer Buchi Model B-191) in the following operative conditions:
The powder obtained was composed of particles having a median diameter-volume (D50), established by means of a “light scattering” test, of 10.48 μm, with a measured yield of 64% with respect to the quantity of solid present in the sprayed solution. The dimensional distribution of the powder thus obtained was such that 80% of the powder was in the diameter range between 4.46 μm (D10) and 19.6 μm (D90), D10 being the lowest diameter percentile value, that is not reached by 10% of the population of primary particles, and D90 being the highest diameter percentile value, that is not reached by 90% of the population of primary particles.
A quantity of 1 g of powder of primary particles was put into a bakelite cylinder (diameter 5 cm; length 4.4 cm), or alternatively into a kidney-shaped glass container, which was rotated on its own base at a speed of 0.30 rpm for 30 minutes. As a result of rolling, the primary particles gave rise to spherical aggregates which grew in diameter with the length of the rolling period. The aggregates obtained were selected by screening, separating the fraction between 106-850 μm, which constituted the nasal powder in the form of chimerical agglomerates. The yield of this preparation, that is the quantity of agglomerates obtained with respect to the original powder, was 92% in the glass container and 85% in the bakelite one.
61.6 g of caffeine, 2 g of Methocel E3, 5 g of polyethylenglycol 6000 and 26.4 g of mannitol were dissolved in 3500 ml of distilled water, kept in agitation at 40° C. 5 g of lecithin dissolved in 400 ml of ethanol were dispersed in the solution obtained. The solution obtained was spray-dried using a spray-drying device (Mini Spray Dryer Buchi Model B-191), in the following operative conditions:
The powder obtained was composed of particles having a median diameter-volume (D50), established by means of a “light scattering” test, of 4.78 μm, with a measured yield of 42% with respect to the quantity of solid present in the sprayed solution. The dimensional distribution of the powder thus obtained was such that 80% of the powder was in the diameter range between 2.66 μm (D10) and 7.85 μm (D90), D10 being the lowest diameter percentile value, that is not reached by 10% of the population of primary particles, and D90 being the highest diameter percentile value, that is not reached by 90% of the population of primary particles.
A quantity of 1 g of powder of primary particles was put into a bakelite cylinder (diameter 5 cm; length 4.4 cm), or alternatively into a kidney-shaped glass container, which was rotated on its own base at a speed of 30 rpm for 30 minutes. As a result of rolling, the primary particles gave rise to spherical aggregates which grew in diameter with the length of the rolling period. The aggregates obtained were selected by screening, separating the fraction between 106-850 μm, which constituted the nasal powder in the form of chimerical agglomerates. The yield of this preparation, that is the quantity of agglomerates obtained with respect to the original powder, was 80% in the glass container and 83% in the bakelite one.
65.1 g of caffeine, 2 g of Methocel E3, 5 g of polyethylenglycol 6000 and 27.9 g of mannitol were dissolved in 3500 ml of distilled water, kept in agitation at 40° C. The solution obtained was spray-dried using a spray-drying device (Mini Spray Dryer Buchi Model B-191), in the following operative conditions:
The powder obtained was composed of primary particles having a median diameter-volume (D50), established by means of a “light scattering” test, of 5.04 μm, with a measured yield of 53% with respect to the quantity of solid present in the sprayed solution. The dimensional distribution of the powder thus obtained was such that 80% of the powder was in the diameter range between 2.52 μm (D10) and 7.74 μm (D90), D10 being the lowest diameter percentile value, that is not reached by 10% of the population of primary particles, and D90 being the highest diameter percentile value, that is not reached by 90% of the population of primary particles.
A quantity of 1 g of powder of primary particles was put into a bakelite cylinder (diameter 5 cm; length 4.4 cm), or alternatively into a kidney-shaped glass container, which was rotated on its own base at a speed of 30 rpm for 30 minutes. As a result of rolling, the primary particles tended to give rise with difficulty to spherical aggregates. The aggregates obtained were selected by screening, separating the fraction between 106-850 μm, which constituted the nasal powder in the form of chimerical agglomerates. The yield of this preparation, that is the quantity of agglomerates obtained with respect to the original powder, was rather low, that is 22.4% in the glass container and 26% in the bakelite one.
66.5 g of caffeine and 28.5 g of mannitol were dissolved in 3500 ml of distilled water, kept in agitation at 40° C. 5 g of lecithin dissolved in 400 ml of ethanol were dispersed in the solution obtained. The solution obtained was spray-dried using a spray-drying device (Mini Spray Dryer Buchi Model B-191), in the following operative conditions:
The powder obtained was composed of particles having a median diameter-volume (D50), established by means of a “light scattering” test, of 5.29 μm, with a measured yield of 60% with respect to the quantity of solid present in the sprayed solution. The dimensional distribution of the powder thus obtained was such that 80% of the powder was in the diameter range between 2.87 μm (D10) and 8.55 μm (D90), D10 being the lowest diameter percentile value, that is not reached by 10% of the population of primary particles, and D90 being the highest diameter percentile value, that is not reached by 90% of the population of primary particles.
A quantity of 1 g of powder of primary particles was put into a bakelite cylinder (diameter 5 cm; length 4.4 cm), or alternatively into a kidney-shaped glass container, which was rotated on its own base at a speed of 30 rpm for 30 minutes. As a result of rolling, the primary particles gave rise to spherical aggregates which grew in diameter with the length of the rolling period. The aggregates obtained were selected by screening, separating the fraction between 106-850 μm, which constituted the nasal powder in the form of chimerical agglomerates. The yield of this preparation, that is the quantity of agglomerates obtained with respect to the original powder, was 92% in the glass container and 87% in the bakelite one.
Characterisation of Nasal Powders
Various measurements and tests were carried out on the chimerical agglomerates in order to check their quality and performance for nasal deposition. In particular, the morphology of the primary particles and of the agglomerates was determined.
On the latter, the dissolving speed of the active principle caffeine was then determined. Finally, using insufflators available on the pharmaceutical market, the supply of the agglomerates was studied, determining the quantity of powder supplied and the quality of the aerosol produced. In particular, as regards the last property, the dimensional distribution of the powder before and after supply was determined.
Morphology of the Primary Particles and of the Chimerical Agglomerates
The primary particles are generally spherical in shape, as are the chimerical agglomerates. However it is not an essential condition that the particles should be spherical in shape, as may be seen from the result of Example 6. As an example,
Supply of Nasal Powder
A certain number of chimerical agglomerates, corresponding to a dose of 20 mg, were introduced in the dose depositing container of a Valois insufflator for nasal powders (model Monopowder P), which is activated by a pump which, by causing an excess air pressure, produces the sudden emission of the dose stored in the deposit. For the purpose of comparison, the same dose was introduced in a gelatine capsule #2 which constitutes the deposit of the drug dose in a Puvlizer insufflator (Teijin ltd. Tokyo, J). This insufflator is composed of a rubber bulb which, when pressed, causes the emission of a jet of air which, passing through the perforated gelatine capsule, carries the powder that it contains towards the nasal adaptor.
The amount of powder emitted with the two insufflators was substantially different. In fact the Valois insufflator was able to emit the whole dose with a single pressure, while the Puvlizer insufflator had to be pressed several times in order to emit the whole loaded dose. For example, with the formula of Example 6 the Valois insufflator emitted 99.1% of the dose with a single pressure, while the Puvlizer insufflator emitted 91.6% of the dose after being pressed 7 times. This result shows that the chimerical agglomerates require a certain force of insufflation to be expelled in a quantitative manner from the drug dose deposit.
In any case, the principal characteristic which nasal powders should possess is to give origin to a cloud of insufflated powder which is deposited in the nasal cavity without the risk of being breathed. This objective is achieved by the formula according to the present invention, since the dimensional distribution of the nasal powder is such that at least 80% of the weight of the cloud of solids supplied by the insufflator has a non breathable diameter, that is larger than 6.4 micron. The demolition of the chimerical agglomerates according to the present invention therefore leads to the obtaining of fragments which are still composed of aggregates of primary particles, and which as such possess dimensions of some tens or hundreds of micron.
The powder of chimerical agglomerates obtained according to example 6, emitted by the Valois insufflator, was therefore collected from a series of screens, in order to determine the dimensional distribution of the cloud of powder supplied. The result of this measurement is shown in
Determination of the Dissolving Speed of Caffeine by the Chimerical Agglomerates
The presence in the supplied products of fragments of some hundreds of micron is desirable to ensure deposition in the nose, but at the same time it must no limit the dissolving of caffeine by the primary particles. To check this, 50 mg of chimerical agglomerates obtained according to example 6 were put into a container of distilled water at 37° C., kept constantly agitating. At set intervals of time, an amount of solution was analysed to determine the quantity of dissolved caffeine. The result obtained showed that the whole dose of powder was dissolved in less than one minute.
| Number | Date | Country | Kind |
|---|---|---|---|
| MI2001A002174 | Oct 2001 | IT | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/EP02/11628 | 10/17/2002 | WO |
