Patent ID: 12186480

In the description, the terms “top”, “bottom”, “upwards”, and “downwards” refer to the position of the device as shown in particular inFIGS.1to9and13to15. The terms “axial” and “radial”, unless specified otherwise, are relative to the vertical central axis of the valve. The terms “proximal” and “distal” are relative to the mouthpiece.

The invention applies more particularly to inhaler devices of the aerosol-valve type for oral dispensing, as described in greater detail below, but it could also apply to other types of inhaler device, e.g. of the nasal type.

The figures show various advantageous embodiments of the invention, but it is understood that one or more of the component parts described below could be made in some other way, while providing functions that are similar or identical.

With reference to the drawings, the device comprises a body10provided with a mouthpiece400.

The body10may be made as a single piece or out of a plurality of parts that are assembled together.FIG.12shows an example in which the body10is formed of two half-shells, but other embodiments are possible. In the description below, the body is designated, in overall manner, by the numerical reference10.

The mouthpiece400defines a dispensing orifice through which the user inhales while the device is being used. The mouthpiece400may be made integrally with the body10. In the embodiments shown in the drawings, it is assembled on the bottom portion of the body10.

A removable protective cap1is provided to cover said mouthpiece400, in particular while it is being stored. This cap1is movable, preferably by being mounted to pivot on the body10, between a closed position, shown inFIGS.1,8,9, and13, and an open position, shown inFIGS.2to7,14, and15.

The body10contains a reservoir100that contains the product to be dispensed and a propellant gas, such as a gas of the hydrofluoroalkane (HFA) type, a metering valve200being mounted on said reservoir100for selectively dispensing the product. The metering valve200comprises a valve body and a valve member210that, during actuation, is axially movable relative to said valve body, and thus relative to said reservoir100between a rest position, and an actuation position. This metering valve200can be of any appropriate type. It is fixed to the reservoir100via an appropriate fixing element, preferably a crimped capsule, preferably with a neck gasket interposed therebetween.

Advantageously, during actuation, the valve member210is stationary relative to the body10, and it is the reservoir100that is moved axially relative to the body10between a distal position, which is the rest position, and a proximal position, which is the actuation position.

The outlet orifice of the valve member210of said metering valve200is connected via a channel to said mouthpiece400through which the user inhales the product to be dispensed. In a known manner, said valve member210is received in a valve well700that at least partially defines said channel.

An actuating member800is advantageously assembled around the reservoir100. This actuating member800comprises a hollow sleeve disposed in the body10around the reservoir100. A push member810is mounted on the distal axial edge of said actuating member800, said push member810being received in a cover element11fixed to the upper axial edge of said body10. A spring850is disposed between a bottom of said cover element11and said push member810. In the rest position, and until inhalation, the spring850is prestressed, and therefore exerts an axial force F on the push member810which transmits this force to the actuating member800. The actuating member800is axially movable, in particular slidingly, relative to said body10between a rest position and an actuation position. A lower edge802of the actuating member800cooperates with the cap1such that, in the closed position of the cap1, said actuating member800is blocked in the rest position, the lower edge802being in abutment against a portion3of said cap1. Furthermore, said cap1comprises a cam4which cooperates with said lower edge802when the cap1is returned from its open position to its closed position, so as to return said actuating member800from its actuation position to its rest position. When the actuating member800returns towards its rest position, it also returns the push member810, which causes the compression of the spring850. The spring850is therefore reloaded after each actuation when the user closes the cap1.

The device comprises a blocking element500that is movable and/or deformable between a blocking position in which said metering valve200cannot be actuated, and an actuation position in which said metering valve200can be actuated.

The blocking element500is advantageously mounted to pivot on the body10about an axis B (which can be seen better inFIGS.16to18) between the blocking position and the actuation position.

Before inhalation, said blocking element500is in the blocking position, and it is the user inhaling through the mouthpiece400that moves and/or deforms said blocking element500towards its actuation position. In other words, so long as the user does not inhale, it is impossible to actuate the metering valve200, and it is only when the user inhales that said metering valve200can be actuated, by moving the reservoir100axially in the body10.

As described in greater detail below, the blocking element500, in its blocking position, prevents the axial movement of the actuating member800in the body10. During inhaling, this blocking element500is moved and/or deformed such that it no longer blocks the axial movement of the actuating member800in the body10. Thus, after inhaling, such an axial movement of the actuating member800causes the axial movement of the reservoir100and therefore the actuation of the metering valve200and the dispensing of a dose of product, synchronously with this inhaling.

Thus, in the absence of inhaling, there is no risk of a dose of active product being lost by accidental or incomplete actuation in which the user does not inhale.

In the closed position of the cap1, a blocking part2of the cap1cooperates with a projecting part503of the blocking member500in order to block the latter in the blocking position, as can be seen in particular inFIG.1. This blocking is eliminated when the cap1is opened.

Opening the cap1therefore releases two blockages provided by the cap in the closed position: firstly, the blockage of the actuating member800in axial movement and secondly, the blockage the blocking member500in pivoting.

The device comprises a trigger system that is controlled by the user inhaling, and that is intended for moving and/or deforming said blocking element500from its blocking position towards its actuation position, when the user inhales through the mouthpiece400.

This trigger system comprises an inhalation-sensitive member60that is deformable and/or movable under the effect of inhaling, this inhalation-sensitive member60being adapted, when it is deformed and/or moved, to make it possible to move and/or deform said blocking element500from its blocking position towards its actuation position.

As described in greater detail below, the inhalation-sensitive member may be made in the form of a deformable air chamber60, e.g. a bellows or a deformable pouch.

The inhalation-controlled trigger system is thereby not located in the user's suction flow but is formed by a specific chamber, namely the air chamber60. This differs from systems that operate by means of a flap that moves/deforms in the suction flow, systems in which, after triggering, the user sucks in the air that exists on each side of the flap. In this case, the system operates under reduced pressure and the user sucks in only the small volume of air that was inside the air chamber60before it deformed. The system according to the invention is thus much more stable and effective.

The blocking element500comprises at least one, preferably two, blocking extensions501, each of which cooperates in the blocking position with an axial projection801of said actuating member800.FIG.29is a perspective view of this blocking element500.

When the blocking element500moves towards its actuation position, in particular by pivoting about the axis B, each blocking extension501moves out of contact with the respective axial projection801. In particular, adjacent to each blocking extension501, said blocking element500comprises an axial recess502which can be seen inFIG.18, in which the respective axial projection801can slide axially, to thus enable an axial sliding of said actuating member800in said body10, causing the reservoir100to move axially and the valve200to be actuated with the dispensing of a dose of fluid product.

The blocking element500is held in the blocking position by a trigger element600.FIG.28is a perspective view of this trigger element600. This trigger element600is advantageously mounted to pivot on the body10about an axis C (which can be seen inFIGS.16and18), between a locking position in which it blocks said blocking element500in its blocking position, and a release position in which it no longer blocks said blocking element500.

Advantageously, the axes B and C are parallel.

The blocking element500and the trigger element600together define a latch. In particular, said trigger element600comprises a locking shoulder610that, in the locking position, cooperates with a locking projection510of the blocking element500, preventing said blocking element500from pivoting out of its blocking position. Thus, when said trigger element600is in the locking position, it prevents the blocking element500from moving towards its actuation position, which blocks the reservoir100from moving axially and the metering valve200from therefore being actuated.

The blocking system of the present invention therefore comprises two stages: a first stage formed by the latch between the blocking element500and the trigger element600, and a second stage formed by the blocking between the blocking element500and the actuating member800.

This blocking system makes it possible to unlock a large force (typically about 40N to 45N) by means of a small force generated by inhaling. The blocking element500stops the actuating member800from moving in translation when it is subjected to a force F (e.g. of 45N) by the spring850pressing on the actuating member800via the push member810. This blocking element500interacts with the trigger element600, and it is both blocked and released by said trigger element. The movement of said trigger element600is controlled by inhaling.

The shape of the blocking system enables very large amplification (unlocked force/unlocking force), typically of about 100.

The blocking element500and the trigger element600preferably have two contact points that are spaced apart:a first contact point, formed by the latch defined between the locking shoulder610and the projection510, located advantageously close to the pivot axis C of the trigger element600; —a second contact point spaced apart from the first contact point, formed by the cooperation between a lateral projection520of the blocking element500and a bearing surface620of the trigger element600; advantageously, in the locking position, this second contact point is at a distance from the axis C of the trigger element600that is greater than the distance between said axis C and the first contact point; —advantageously, this second contact point is the first contact that is broken while actuating the device, when the user begins to inhale.

In the blocking position, after opening the cap1and before inhaling, the axial force F generated by the spring550on the actuating member800is applied by the axial projections801of the actuating member800to the blocking element500at the extensions501, having the effect of urging said blocking element500in rotation in a first direction S1, which can be seen inFIG.16, that reinforces the closed position of the latch and makes it stable.

The unlocking force generated by inhaling is applied to the trigger element600by the inhalation-sensitive member60, preferably at a point630spaced apart from from the pivot axis C. This unlocking force seeks to pivot said trigger element600in the direction S2opposite to the direction S1, as shown inFIG.17.

The torque to which the blocking element500is subjected is controlled by the distance between the force axis along which the force F is applied to the blocking extensions501of the blocking element, and the pivot axis B of said blocking element500. It is desirable for the distance d to be as small as possible, in order for the torque to be as small as possible. This distance d, shown inFIG.16, is non-zero, and is less than 2 mm, advantageously less than 1 mm.

The torque to which the trigger element600is subjected is controlled by the distance d′ between the force axis conveying the force F′ to which the trigger element600is subjected by the blocking element500, and the pivot axis C of said trigger element600. Once again, it is desirable for the distance d′ to be as small as possible, in order for the torque to be as small as possible. This distance d′, shown inFIG.16, is non-zero, and is less than 2 mm, advantageously less than 1 mm.

By means of this force system of the latch, the force necessary to cause the trigger element600to pivot is very small and may be generated by the inhalation-sensitive member60that makes it possible to transform the reduced pressure generated by inhaling into unlocking force.

Advantageously, as shown in the variant ofFIGS.4and5, the mouthpiece400comprises one or more opening(s)410that are connected to the inside of the body10. This at least one opening410is closed at rest and at the start of inhaling by a check valve420, such that the inhalation flow is initially mainly transmitted to the trigger system by inhaling, in this example, the deformable air chamber60. This makes it possible to optimise this triggering by inhaling. When the blocking element500moves towards its actuation position under the effect of inhaling, and therefore the reservoir100moves axially relative to the body10so as to actuate the metering valve200in order to dispense a dose of fluid product, said actuating member800, or alternatively said reservoir100, moves said check valve420towards an open position. When said at least one opening410is thus opened, during actuation, air is drawn in, thereby making it possible to increase the inhalation flow. This optimises synchronization between the user inhaling and dispensing the dose, and also promotes good dispensing of the dose into the user's lungs.

Advantageously, the trigger element600may be accessible from the outside of the body10. This makes it possible, if necessary, to move the trigger element600manually, so as to be able to actuate the metering valve200even without inhaling, e.g. if the person that needs to receive the dose of fluid is incapable of inhaling sufficiently. This is therefore a safety measure. This also makes it possible to prime the valve, if the latter is a conventional valve requiring such priming.

In the embodiments shown in the figures, the inhalation-sensitive member60is made in the form of a deformable air chamber. Advantageously, this air chamber comprises a deformable membrane that is connected firstly to said body10and secondly to said trigger element600. Advantageously, as can be seen in the figures, the membrane is in the form of a bellows and forms a substantially sealed chamber. Other forms are possible, in particular a mere pouch or diaphragm. A stud may fix said membrane to an orifice or edge630of said trigger element600.

During inhaling, the deformable membrane deforms and/or contracts under the effect of the suction generated by inhaling, causing the trigger element600to move from its locking position towards its release position. This makes it possible to open the latch defined between the blocking element500and the trigger element600, and therefore to move said blocking element500from its blocking position towards its actuation position.

The valve200is therefore actuated only at the moment of inhaling, such that the dose of fluid product is expelled out of the dispensing orifice simultaneously with inhaling.

In the rest position, with the cap1closed, the push member810is not in contact with the reservoir100, as can be seen inFIG.1. Thus, in this position, the force of the spring850is applied by the push member810to the actuating member800, which transmits it to the cap1. Thus, during storage of the device, no stress is applied to the valve200, which limits or even eliminates the risks of leakage and/or malfunction of said valve.

When the user wishes to use the device, the user opens the cap1. In doing so, it prevents the actuating member800from being blocked axially by the cap1as well as the blocking element500from being blocked in terms of pivoting by the cap1. In this position, the actuating member800is blocked and prevented from sliding axially in the body10by the blocking extensions501of the blocking element500that axially block the axial projections801of the actuating member800. As can be seen inFIG.2, in this armed position (cap open, before inhalation), the push member810is still not in contact with the reservoir100. Thus, also in this position, the force of the spring850is applied by the push member810to the actuating member800, which transmits it to the blocking element500, which transmits it to the trigger element600. Thus, before inhalation, no stress is applied to the valve200, which limits or even eliminates the risks of leakage and/or malfunction of said valve.

When the user inhales through the mouthpiece400, the deformable membrane of the inhalation-sensitive member60deforms, and this causes the trigger element600that is fixed to said deformable membrane to pivot. This movement of the trigger element600releases the latch formed between the locking shoulder610of the trigger element600and the projection510of the blocking element500. Under the effect of the axial force F transmitted by the actuating member800, the blocking element500pivots, enabling said actuating member800to slide axially. Consequently, the push member810, integral with said actuating member800, comes into contact with the reservoir100, thus causing said reservoir100to move axially in the body10towards its dispensing position, and the valve200therefore to be actuated.

At the same time, in the variant ofFIGS.4and5, the actuating member800(or alternatively the reservoir100) will open the valve420.

At the end of inhalation, the device advantageously comprises signalling means for signalling to the user that he/she must close the cap1. These signalling means may comprise a visual indicator, as shown inFIGS.6and7. In this example, a window15is formed in the body10, through which a coloured portion of the actuating member800is visible from the outside, forming indicating means. Thus, in the rest position or in the armed position, with the cap1open but before inhalation, the window15can indicate a light colour, for example green, whereas after inhalation, it is a dark colour, for example red, which can be displayed in the window15. Naturally, any other similar embodiment is possible.

In a variant, it is possible to have several windows15. The window(s)15may be positioned differently on the device, for example in the upper part of the body10or on the cover11. The indication means which are displayed in the window15may, as a variant, comprise symbols, figures, letters or any other indication which is useful for alerting the user. These indicating means may be formed, for example formed by pad printing, directly on the actuating member800, or may be formed on a part fixed thereto. The indicating means may be made on any other moving part during actuation, for example the push member810, the blocking element500, the trigger element600, the inhalation-sensitive member60.

In another variant, the signalling means may comprise an audible indicator, such as a loudspeaker, which emits a sound audible by the user to indicate to him/her that the cap1must be closed.

When the user closes the cap1, the actuating member800is axially repelled by said cap1towards its rest position, such that said reservoir100can axially rise in the body10in the direction of its rest position under the effect of the return spring of the valve200, and the valve member210of the metering valve simultaneously returns to its rest position, once again filling the valve chamber with a new dose of fluid product. The trigger element600is returned into its initial position, in particular by the springiness of the membrane. The blocking element500returns into its blocking position.

The device is thus ready for another use.

In an advantageous variant embodiment, shown inFIGS.8to11, the final assembly of the device is simplified for the pharmaceutical laboratory which markets the device. In fact, in most existing devices, the reservoir filled with active principle is inserted into the body and then it is necessary to position several parts above the reservoir, which does not facilitate the production rates and the simplicity of assembly. To eliminate this drawback, the present invention advantageously provides for pre-assembling the subassembly formed by the push member810, the spring850and the cover11. This subassembly is prestressed during the assembly of these three parts, for example by coming with a hot tool O to thermally deform the lower axial edge111of a central axial sleeve110of the cover11, around which the push member810and the spring850are assembled. Said lower axial edge111is thus deformed to produce a retention collar which retains the push member810and the spring850in the cover11. This subassembly thus formed can then be assembled on the body10in a single assembly operation, for example by screwing or by snap-fitting. This then results in only two operations on the assembly line of the pharmaceutical laboratory: inserting the reservoir100in the body10(FIG.8) and assembling said subassembly on said body10(FIG.9). During this assembly, the actuating member800disposed in the body10will cooperate with the push member810, so as to push it axially into the cover11and thus load the spring850. In a screw-on version, this system can also make it possible to change the reservoir. Indeed, the device could be reusable and refillable for ecological reasons, in particular to avoid throwing away too many plastic components and/or too many electronic components.

In an advantageous embodiment, shown inFIGS.12to15and19to22, the device comprises an automatic valve release system, which automatically returns the valve member210of the valve200towards its rest position after actuation of the valve, independently of the position of the cap1and of the position of the actuating member800. Thus, in this variant, there is no risk of malfunction, such as an underdose of the next dose, even if the user delays closing the cap.

The valve release system comprises the following additional parts:two levers901,902,a push element910,a lever spring920.

The push element910is intended to come into contact with the reservoir100, and is connected to the push member810, with the interposition of the lever spring920. Advantageously, before inhalation, the push element910is very slightly offset axially from the reservoir100, such that in this position, it transmits no stress to said reservoir100or to the valve200. It is only when the user inhales, and releases the actuating member800from moving axially, that the push element910comes into contact with the reservoir100.

Each lever901,902is assembled via studs905so as to pivot in a cam815of the push member810and cooperates with said push element910.

When the user inhales, the actuating member800and therefore the push member810move axially downwards under the effect of the spring850. This force is transmitted by the levers901,902to the push element910, which transmits it to the reservoir100, thus causing the axial movement of said reservoir100and the valve200to be actuated.

The aim of the valve release system is therefore to release the transmission of the force from the spring850to the reservoir100after inhalation, so as to enable said reservoir100to return towards its rest position independently of the actuating member800. This makes it possible to load the next dose into the valve200immediately after inhalation, when the device is still in the appropriate position for this loading, without risk of incorrect dosing, for example in the case of forgetting to close the cap1.

The valve release system operates as follows:

In the locked position, before inhalation, shown inFIG.19, the levers901and902bear on a shoulder911of the push element910. On the opposite side, the levers are in contact with locking fingers115formed in the cover11and which extend axially downwards from the bottom of said cover. These locking fingers115prevent the levers901,902from pivoting out of contact with the shoulder911of the push element. In this position, the force of the spring850is therefore transmitted by the levers901,902to the push element910and therefore to the reservoir100.

When the actuating member800arrives in the actuation position, with the valve200which has been actuated to dispense a dose, the push member810, the push element910and the levers901,902have slid axially downwards relative to the cover11, as can be seen inFIG.20. In this position, the levers901,902no longer cooperate with the locking fingers115of the cover11. They can then pivot in the push member810until they are no longer in contact with the shoulder911of the push element. Advantageously, the release of the push element910occurs after the dose has been expelled by the valve, but before the end of the actuation stroke of the latter.

When the levers901,902are no longer in contact with the shoulder911of the push element, each of them faces an opening912in said push element910, such that the reservoir100can rise again towards its rest position under the effect of the return spring of the valve200, with the levers901,902passing through said holes912, as can be seen inFIG.21. During this return of the reservoir100towards its rest position, the push element910slides axially upwards together with the reservoir100, with respect to the push member810and to the levers901,902. During this movement, the lever spring920, the stiffness of which must be less than that of the spring of the valve200, compresses.

When the device shown inFIG.22is reset, when the user closes the cap1, the actuating member800and the push member810return to their rest positions, compressing the spring850. During this movement, the levers901,902undergo a force exerted by the lever spring920, which urge them in rotation, as indicated by the arrow F1. As long as the levers901,902are in the holes912of the push element910, they cannot pivot and they move axially with the push member810, as indicated by the arrow F2. When they come into contact with the locking fingers115of the cover11, the studs905are forced to move radially outwards into the cams815, as indicated by arrow F3, which allows the levers901,902to return around said locking fingers115of the cover11. When the actuating member800and the push member810reach their rest positions, the levers901,902have emerged from the holes912in the push element, and the lever spring920returns said levers to bear on the shoulder911.

To ensure reliable operation of the device, the valve release system must be actuated only after a sufficient stroke to ensure that dose dispensing occurs. Because of the manufacturing tolerances of the parts, it may be advantageous to provide a buffer element between the push element910and the reservoir100. This buffer element, which must slow down or offset the actuation of the valve release system, may be an elastic element, such as a spring or a compressible part, for example made of elastomer. Its resistance must be, on the one hand, greater than the force of the spring of the valve200in the actuation position of the valve210, such that it is first of all the valve200which is actuated before the buffer element deforms, and, on the other hand, less than the force of the spring850in the actuation position of the actuating member800, in order to guarantee that the buffer element will compress at the end of the actuating stroke. In a variant, it is also possible to use a buffer element formed by an actuator or by a variable-volume chamber, filled with air or a fluid, and provided with a leakage orifice.

In an advantageous embodiment, the device may comprise a dose meter1000, shown inFIGS.1to9, which may be mechanical or electronic, advantageously assembled in the body10. Such a meter could also be associated with the embodiments inFIGS.12to22. In particular, this meter1000can detect the movements of the actuating member800or of the reservoir100. In a variant, the meter could be connected to a sensor, in particular a membrane sensor, that detects the dose of fluid product being dispensed, for example in the valve well. Such a meter could be actuated in other ways, for example by detecting the movement of the valve member210of the metering valve200relative to the valve body.

When the meter is electronic, it must be able to have enough electrical energy to operate throughout the storage period until its first use. The battery must then have a sufficient capacity, for example to communicate with the user (viewing the number of doses remaining) and/or with a third-party application, throughout its use and at least until the expiry date of the medicinal product. To avoid an excessively large battery, it is necessary to reduce the power consumption of the electronic board before first use. To do this, the electronics is advantageously put in a standby mode, which consumes little energy, until the moment of first use. To “wake up” the electronics, the user is asked to actuate the device by inhaling the first dose (if the device is provided with a valve without priming) or by priming (if the device is provided with a conventional valve). The first actuation causes the actuating member800to descend into the body10. A portion of the actuating member800will then press on a contactor1010, as shown inFIGS.2to5, thereby closing a current loop. The device then detects this change in intensity, which will wake up the electronics and put the meter in a normal operating state.

In a variant, or additionally, the device may comprise an accelerometer.

This accelerometer can have several functions:it can be used to check that the device has indeed been shaken before use; indeed, most of the medicines stored in a pressurized reservoir are more or less soluble medicines and it is therefore necessary to mix them before taking a dose; if the electrical circuit senses via the accelerometer that the device has not been shaken, the user may be informed of this, for example by an application on its smartphone or on a screen of the device;some people take the device upside down when they wish to actuate it; when the device is upside down, i.e. with the reservoir disposed below the valve, the liquid cannot enter the dosing chamber of the valve, which results in a reduced or even zero dose when loading the dose; the accelerometer can detect whether the patient is taking the device upside down and indicate to them, preferably before taking the dose, for example by a beep sound and/or an indication on the screen and/or on the smartphone, that the device is not in the correct direction;another use of the accelerometer is to use it to save battery power; when the device is in a pouch or trouser pocket or placed on a table, the device is in standby mode; during this phase, the meter screen and a large portion of the onboard electronics are in standby mode, which greatly reduces power consumption; when the user grasps the device, the accelerometer detects movement and wakes up the electronics to put the meter in the normal operating condition; this option then makes it possible to reduce the capacity of the onboard battery and therefore to have a less negative impact on the environment.

The device may also comprise signal-transmitter means for communicating, in particular communicating remotely, information relating to the actuations of the device. In particular, the body and/or the cap and/or the meter may comprise a signal-transmitter module, for communicating remotely with any remote device. Appropriate power supply means are advantageously provided.

Advantageously, the electronic module may comprise a board comprising an electrical switch that sends a pulse. The module may also comprise a display unit and/or use a Bluetooth or Wi-fi connection for sending information to an accompanying peripheral. Appropriate sensors, such as flowrate and/or pressure sensors, may be provided for detecting various parameters of the inhalation flow.

The switch can be actuated by virtue of the movement of the actuating member and/or of the blocking element and/or of the trigger element and/or of the inhalation-sensitive member.

Associated with a dose meter that counts each dose that is actually dispensed, and with the inhalation-synchronized device of the invention, these signal-transmitter means make it possible for each dose that has been dispensed to be transmitted in completely reliable manner, for example to a doctor or to any other person wishing to monitor the use of the inhaler device by the user. The inhalation-synchronized device guarantees that the user inhales each time the user actuates the device, and the meter records each dose that is dispensed, as well as with various associated parameters, such as the timestamp for each dispensing. The doctor can thus know very accurately the conditions of use of the device by the user.

The present invention applies, in particular, to treating asthma attacks or chronic obstructive pulmonary disease (COPD), by using formulations of the following types: salbutamol, aclidinium, formoterol, tiotropium, budesonide, fluticasone, indacaterol, glycopyrronium, salmeterol, umeclidinium bromide, vilanterol, olodaterol, or striverdi, or any combination of these formulations.

The present invention has been described with reference to advantageous embodiments and variants, but naturally any modification could be applied thereto by a person skilled in the art, without going beyond the scope of the present invention, as defined by the accompanying claims.