Patent Application
20160058959
The present invention relates to an inhaler. In particular, the invention relates to a novel design of outlet configuration designed to produce a particular particle size distribution from a reservoir of pressurised composition.
The invention has primarily been designed as a development to a simulated cigarette such as that disclosed in WO 2011/015825. However, it has broad applications in other types of inhaler such as a metered dose inhaler (MDI) of the type commonly used in asthma inhalers.
Aerosols are an attractive means of delivering drugs to patients when the site of action is the lungs themselves or for quick delivery of drugs to the brain. The particle size of aerosols is an important parameter to control when delivering an inhaled composition since the depth of penetration into the lungs increases with reducing particle size. It plays a significant role in determining the deposition profile of the aerosol in the respiratory system. It is known that larger particles (>10 μm) are deposited in the mouth and upper thoracic region, whilst smaller particles (<10 μm) have deposition distributions that are from the upper thoracic through to the alveolar region. Fine droplets (0.1 μm<Dm<1 μm) have good alveolar deposition at between 1-5 um. Ultra-fine droplets (<0.1 um) are optimal for alveolar deposition from where drug molecules can be efficiently absorbed into the circulatory system, but are currently not feasibly produced in a portable device. This deposition distribution can be exploited to allow for effective delivery of pharmaceuticals, proteins, vaccines or, nicotine in the case of a simulated cigarette device. It is known that the D50 (mass-median-diameter, or average particle size by mass) of cigarette smoke is between 0.3-0.5 μm for most main stream cigarettes. To be successful as a cigarette replacement, ideally a simulated cigarette would be able to reproduce this particle size.
WO 2004/022242 discloses an aerosol generating device wherein the generated droplet size lies between 0.5 and 2.5 μm. The droplet size is controlled by preferably increasing the exit velocity of a vapour that is generated by heating the formulation liquid source while it passes through a capillary sized flow pathway. The vapour, after exiting, is mixed with air to produce an aerosol.
U.S. Pat. No. 5,957,124 discloses devices, packaging and methodology for creating aerosols with particle size ranging from 0.5 to 12 μm. The device comprises of collapsible containers containing the drug formulations, which when actuated, forces the formulation through a membrane having pores of 0.25 to 6 μm diameters. This membrane is aligned such that the formulation is forced from the containers into a channel through which the patient inhales air. Sufficient energy from the air (which may or may not be heated) is imparted to the formulation to induce particle size reduction. It incorporates a microprocessor into the device to obtain real-time measurements of inspiratory volume and flow rate for determination of a beginning point to force formulation through the pores.
WO 2008/151796 teaches an inhaler that produces an aerosol which has a mean particle size of 2-5 μm. Also, the primary aim is to devise an inhaler that has a flow resistance of at least 60000 Pa1/2s/m3, which translates to a much higher draw resistance when compared to existing devices of a similar type.
U.S. Pat. No. 7,293,559 discloses a device for creating an aerosol through the use of a focusing funnel to focus the liquid stream using a second fluid stream, leading to a mean particle size of 2 μm upon exit of the device.
WO 2011/015825, our own earlier application, discloses an inhaler composed of a non-metered breath activated valve comprising a flow path in the form of a deformable tube extending from a reservoir (containing the formulation) to an outlet end. It discloses a clamping member which pinches the deformable tube when no suction is applied resulting in obstruction of flow. It releases the pinch to form an opening when suction is applied to provide uninterrupted flow from the reservoir to the outlet. However, the disclosure concerns flow control and makes the reference to the particle size generated using this design.
According to the present invention there is provided an inhaler comprising a reservoir of inhalable composition, an outlet valve to control the flow of composition from the reservoir, the valve outlet orifice having a maximum dimension h, measured in the direction of opening when fully opened; an expansion chamber downstream of the valve having a length L and diameter D measured half way along the expansion chamber; and an exit orifice at the downstream end of the expansion chamber, the orifice having a length l and a diameter d; wherein:
0.1<h/d<1.0
0.05<h/D<0.25
l<D/d<10
5<L/D<15
0.1<l/d<5.
Such an arrangement is capable of delivering particles size distribution with a D50 of 0.5 μm and can therefore produce the type of small particle size distributions that are to be found in cigarette smoke. However, the present invention achieves this simply by careful selection of the geometry of existing components. It does not, as with the prior art, require any additional features such as baffles or heat input. The avoidance of heating the composition is beneficial as it avoids degradation and problems associated with the risk of fumes.
A combination of the various parameters quoted above is one which has been arrived at after numerous tests required to identify the key geometrical relationships for producing the optimum particle size. All five of the parameters are inter-related. However, broadly speaking, the effect of the parameters is as follows.
The ratio h/d is important in promoting turbulent flow. Having an exit orifice, the diameter of which is equal to or greater than the valve outlet height ensures a homogenous pattern of bubbles dispersion which is favourable for droplet size reduction and the formation of a spray instead of a jet.
Preferably h/d is between 0.2 and 0.9 and more preferably substantially 0.5.
The ratio h/D is important in ensuring that there is sufficient volume for expansion of the formulation as it passes through the valve outlet orifice. If the diameter of the expansion chamber is too large, flow will be laminar thus preventing effective particle break up. Preferably h/D is between 0.05 and 0.25 and more preferably between 0.10 and 0.15.
The ratio D/d has an important role in maintaining a small droplet size exiting the device as ensuring that there is still sufficient volume for mixing whilst avoiding significant dead zones. Preferably, D/d is between 2 and 7 and more preferably between 3 and 5.
The ratio L/D effects the flow regime inside the expansion chamber. Sufficient volume is provided within the claimed range for the formulation to evaporate, re-circulate and form sufficiently sized bubbles to provide droplets of a small, uniform size upon exit of the outlet orifice. Preferably, the ratio L/D is between 6 and 13 and more preferably between 7 and 10.
The diameter D is specified as being measured at the mid point of the expansion chamber. This is because preferably, the expansion chamber tapers from the valve outlet orifice to the exit orifice at an included angle of between 0 and 30°, preferably between 9 and 10° and most preferably substantially 2°. This tapering prevents dead zones from forming in the expansion chamber and promotes a well-mixed system which is useful in maintaining a uniform aerosol.
The ratio l/d is important in the formulation of a turbulent exit aerosol. By optimising its ratio, the droplet size can be decreased or increased. Preferably, l/d is between 1 and 4 and more preferably between 2 and 3.
Preferably, 0.05<h<1 mm and more preferably 0.05<h<0.6 mm. Preferably, 0.15<d<0.25 mm. Preferably 0.6<D<0.12 mm. Preferably, 7.0<L<7.8 mm. Preferably, 0.40<l<0.5 mm.
The outlet valve may, for example, be a sliding gate valve member which opens to the required extend. However, preferably, the outlet valve is a pinch valve in which a valve element pinches a deformable tube with the outlet orifice dimension representing the maximum opening height at the pinch point. It is preferably a breath operated valve.
The deformable tube preferably also provides the expansion chamber and the exit orifice. This allows the profile of the droplet size of the emitted aerosol to be defined entirely by the dimensions of a single component. This is extremely useful in tuning the inhaler to the required particle size and also in producing inhalers offering a range of particle profiles whilst only having to change a single component in order to achieve these different sizes.
Preferably, the inhaler is configured so that the Reynolds number of the aerosol at the exit is between 1000 and 4000 and preferably between 1500 and 3000.
The inhaler may be an MDI, but is preferably a simulated cigarette. Preferably, the inhalable composition comprises nicotine and a propellant.
In order to minimise impact between the composition and the inhaler downstream of the outlet orifice, the outlet orifice is preferably close to an outlet end of the inhaler, (preferably within 10 mm, more preferably within 5 mm and most preferably within 3 mm). For the same reason, there is preferably a flared flow path with an angle of at least 10° from the valve outlet orifice to the outlet end.
An example of an inhaler in accordance with the present invention will now be described with reference to the accompanying drawings, in which:
The present invention is primarily intended as a modification of an existing breath operated valve used in our simulated cigarette. The basic design of the simulated cigarette is shown in
The device has a housing 1 made up of a main chassis 2 and a closure element 3 as shown in
The breath-activated valve 7 is positioned between an outlet end 8 and the reservoir 5. The breath-activated valve is arranged so that, when a user sucks on the outlet end 8, the breath-activated valve 7 opens to allow the inhalable composition from the reservoir 5 to be inhaled.
The housing at the outlet end has two orifices. The first of these is the suction orifice 9 which communicates with a chamber 10 as will be described in greater detail below and the second is an outlet orifice 11 from which the inhalable composition dispensed is also described in more detail below.
An outlet path 13 is defined between the reservoir 5 and outlet orifice 11.
A portion of the outlet path 13 is provided by deformable tubular element 14. This tubular element is moved between the closed position shown in
This mechanism comprises a pivotally mounted vane 15 and a membrane 16. The pivotally mounted vane has a pivot 17 at the end closest to the outlet end 8 and a central reinforcing rib 18 running along its length and tapering away from the outlet end. At around the midpoint, the vane 15 is provided with a recess 19 for receiving a spring 20 which biases it into the closed position shown in
The underside 24 of the membrane 16 is open to atmospheric pressure as a leakage path exists through the housing 1 which is not shown in the drawings as it extends around the outlet path 1 and is therefore not shown in the plane of
When a user sucks on the outlet end 8 with the device in the configuration shown in
In a later example in WO 2011/015825, the outlet orifice 11 is provided in the same deformable tube component as is used for the deformable tubular element 14. A further example of such an element is disclosed in our later WO 2011/107737.
A further modification to the breath activated valve is disclosed in pending UK application 1215278.1. In this modification, there are no orifices 25 such that the chamber 10 is a blind chamber. Orifices are provided in the lower part of the cigarette to provide an air flow path over the underside of the membrane 4 which has an outlet at the outlet end 8. When a user sucks on this cigarette, there is a decrease in the pressure in the upper chamber and an increase in the pressure in the air flow path on the underside of the chamber to open the valve.
The present invention concerns an improvement in the valve geometry. As such, it is applicable to either of the above described flow paths. It is applicable to both arrangement shown in
Further, although the invention is motivated an improvement to a simulated cigarette, it can be more broadly applied to other types of inhaler such as a metered dose inhaler. Also, whilst the size of the valve outlet orifice is an important parameter of the present invention, the valve may be operated by any known mechanism. It may therefore be operated by hand or by an automated mechanism, rather than being breath operated. Further, the pinch valve may be replaced, for example, by a sliding gate valve arrangement.
The present invention is described with reference to
Between the valve outlet orifice 32 and the exit orifice 31 is expansion chamber 33. This has an axial length L and an internal diameter D which is measured halfway along the expansion chamber. The exit orifice 31 has a length l and a diameter d.
The closure of the tube is shown schematically in
The axial distance x between the end of the exit orifice 31 and the outlet end 8 is 1.4 mm. Between the exit orifice 31 and the outlet end 8 is a flared flow path 37 which is flared with an angle θ of 51.1°. This short distance and wide angle of flow path prevents as far as possible any impingement of the composition leaving the outlet orifice 31 on the body of the inhaler.
The inhaler has a reservoir volume of approximately 1 ml maintained at a pressure of 600 kPa. The opening height (h) is 0.1 mm in the fully opened position. The length (L) is 7.4 mm and the diameter (D) is 0.94 mm. The exit orifice has a length (l) of 0.5 mm and an internal diameter (d) of 0.2 mm.
| Number | Date | Country | Kind |
|---|---|---|---|
| 1305496.0 | Mar 2013 | GB | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/GB2014/050937 | 3/25/2014 | WO | 00 |
