EP1957138A2 - Dispositif d'administration pour aerosol de poudre - Google Patents

Dispositif d'administration pour aerosol de poudre

Info

Publication number
EP1957138A2
EP1957138A2 EP06839996A EP06839996A EP1957138A2 EP 1957138 A2 EP1957138 A2 EP 1957138A2 EP 06839996 A EP06839996 A EP 06839996A EP 06839996 A EP06839996 A EP 06839996A EP 1957138 A2 EP1957138 A2 EP 1957138A2
Authority
EP
European Patent Office
Prior art keywords
medicament
outlet
receptacle
inlet
path
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP06839996A
Other languages
German (de)
English (en)
Inventor
Robert Price
John Nicholas Staniforth
Derek Alan Woodcock
Paul Michael Young
James A. Byrnes
J. Nita Cogburn
Douglas R. Dockhorn
Robert J. Dockhorn
Edgar W. Mitchell
Susan J. Prather
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Airpharma LLC
Original Assignee
Airpharma LLC
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US11/296,637 external-priority patent/US20060213514A1/en
Application filed by Airpharma LLC filed Critical Airpharma LLC
Publication of EP1957138A2 publication Critical patent/EP1957138A2/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0028—Inhalators using prepacked dosages, one for each application, e.g. capsules to be perforated or broken-up
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M11/00—Sprayers or atomisers specially adapted for therapeutic purposes
    • A61M11/001—Particle size control
    • A61M11/002—Particle size control by flow deviation causing inertial separation of transported particles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0001—Details of inhalators; Constructional features thereof
    • A61M15/0005—Details of inhalators; Constructional features thereof with means for agitating the medicament
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0028—Inhalators using prepacked dosages, one for each application, e.g. capsules to be perforated or broken-up
    • A61M15/003—Inhalators using prepacked dosages, one for each application, e.g. capsules to be perforated or broken-up using capsules, e.g. to be perforated or broken-up
    • A61M15/0043—Non-destructive separation of the package, e.g. peeling
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0065—Inhalators with dosage or measuring devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2202/00—Special media to be introduced, removed or treated
    • A61M2202/06—Solids
    • A61M2202/064—Powder
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/82—Internal energy supply devices
    • A61M2205/8218—Gas operated
    • A61M2205/8225—Gas operated using incorporated gas cartridges for the driving gas
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2206/00—Characteristics of a physical parameter; associated device therefor
    • A61M2206/10—Flow characteristics
    • A61M2206/14—Static flow deviators in tubes disturbing laminar flow in tubes, e.g. archimedes screws
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2209/00—Ancillary equipment
    • A61M2209/06—Packaging for specific medical equipment

Definitions

  • the present invention relates to a hand-held delivery device for a medicament in the form of a powder, typically as an aerosol of powder particles.
  • the delivery device may be used for delivery of a medicament without a carrier into the airways/lungs.
  • MDI propellant-driven metered dose inhaler
  • DPI dry powder inhaler
  • the medicament is suspended or dissolved in a propellant.
  • the propellant is provided in a pressurized canister having a metered valve which, upon activation, produces a single dose of the medicament in the form of a gas stream.
  • the device may include a tapered discharge nozzle baffle or a venturi to accelerate particles through a discharge nozzle, and to remove oversized particles.
  • Suitable halocarbons used in an MDI include hydrofluorocarbons, hydrofluorochlorocarbons and fluorochlorocarbons having a low boiling point, such as those marketed under the trade mark "Freon".
  • the problem with the MDI device is that when it is used to deliver a medicament to a patient's lungs, only a small percentage of the medicament is delivered in a respirable form (approximately 8 weight % fine particle fraction). This is because the high linear speed at which the dosage leaves the device combined with incomplete evaporation of the propellant causes much of the medicament to impact and stick to the back of the throat, causing localized problems in the impact area. This medicament is generally later swallowed by the patient which, for some medicaments such as bronchodilators, can lead to unwanted systemic side effects.
  • a further problem is that MDIs require coordination between activation and inhalation. Many patients are incapable of this, especially infants, small children and the elderly.
  • MDIs have been used with a "spacer" which provides an additional volume in which the propellant may evaporate. It has been found that the fine particle fraction is deposited within the spacer instead of the back of the patient's throat.
  • a DPI device no propellant is used but instead the device relies upon a burst of inspired air drawn through the unit by the patient. These devices suffer from the problem that the force of inspiration varies considerably from person to person. Some patients, particular those with lung problems whom such devices are designed to treat, are unable to generate sufficient air in-flow to activate the device. DPIs have many of the disadvantages of MDIs because of incomplete particle dispersion and the impact at the back of the throat.
  • the medicament for use in such devices has been formulated in a particular way to aid de-agglomeration.
  • the medicament is generally provided with a carrier or is processed in such a way that weakly bound agglomerations of the medicament are produced which the device may more easily break up. Therefore DPIs are unsuitable for use with medicaments which, due to their high dosage rate, cannot be administered with a carrier or which cannot be further processed in this way.
  • Formulated DPIs where the medicament is administered with a carrier have a problem that the amount of administered medicament in a respirable form is low because the medicament remains adhered to the carrier.
  • pumactant which is a blend of dipalmitoylphosphatidylcholine (DPPC) and phosphatidylglycerol (PG) (DPPC:PG 7:3), which is very cohesive due to its low particle size, high moisture affinity and predominantly amorphous structure.
  • DPPC dipalmitoylphosphatidylcholine
  • PG phosphatidylglycerol
  • the present invention provides a delivery device for a powdered medicament comprising: a housing, a receptacle holding a medicament in the form of a powder, and a source of propellant, wherein the housing has an inlet for the receptacle in fluid communication with the source of propellant and an outlet for the medicament, wherein the inlet is directed against the medicament and the outlet is spaced from the medicament to allow aerosolization of the medicament.
  • a surprising advantage of the device according to the present invention is that it has much greater efficiency than known inhaler devices. It has been found that the device efficiency is about 70.1 weight % in terms of the weight of the delivered dose compared to the weight of the dose loaded in the device (as measured using a Marple Miller impactor; the data is shown in Example 2 below). In particular, the delivered fine particle fraction is at least 20 weight % of the amount of medicament originally loaded in the receptacle. Where the device has been optimized, a delivered fine particle fraction of 40 weight % has been achieved.
  • the advantages of the spaced arrangement of the outlet include that it overcomes the problems of incomplete evaporation of the propellant (where the propellant is liquefied gas) and patient coordination.
  • the problem with patient coordination is improved because there is a slight delay between activation of the device and delivery of the aerosolized medicament from the outlet for the device according to the invention particularly compared to a standard MDI. This is because the aerosol is first generated in the receptacle and then has to pass through the outlet before reaching a patient. This is advantageous because a patient normally finds it difficult to simultaneously activate an inhaler and inhale; it is easier to activate the inhaler and then inhale which the device according to the present invention would allow.
  • the inlet is generally in fluid communication with the source of propellant such that there is a propellant pathway from the source to the inlet.
  • the propellant pathway is preferably provided with at least one choke to decelerate the propellant.
  • the propellant pathway choke may be in the form of a constriction or a baffle; preferably it is in the form of a constriction.
  • a propellant pathway choke is useful where the medicament is at least partially amorphous such that it is vulnerable to becoming waxy or being compressed when the propellant is directed against it. This would clearly be disadvantageous because an aerosol of the medicament would be generated less efficiently, if at all.
  • the propellant pathway generally passes from the source of propellant through the housing and then through the header unit to the inlet. It is optionally either formed by the housing or is in the form of tubing, especially medical grade tubing.
  • the inlet is preferably in the form of an inlet tube.
  • the inlet tube is in fluid communication with the propellant pathway and leads from the housing and is directed against the medicament.
  • the inlet preferably has an end which is directed against the medicament.
  • the end of the inlet is preferably in the form of a flared tube or of a "shower-head" such as a flared and perforated end.
  • the inlet tube preferably extends into the receptacle.
  • the inlet is preferably provided with one or more perforations.
  • a perforation is useful as an alternative to a propellant pathway choke as it would decelerate the propellant exiting the inlet before it is directed against the medicament.
  • a perforation in the inlet may also be useful in assisting in the formation of the aerosol of medicament.
  • the spaced arrangement of the outlet and/or the propellant pathway choke are preferably arranged such that on activation of the device, a stable aerosol of the medicament is formed in the spaced arrangement.
  • a stable aerosol of the medicament will be referred to herein as a standing cloud of medicament.
  • a device arranged to produce a standing cloud of medicament is particularly advantageous because it makes the medicament easier to administer.
  • a device preferably has a normally sealed outlet.
  • the outlet has an outlet pathway which connects to the exterior of the device (the outlet is in fluid communication with the outlet pathway); more preferably the outlet pathway ends in an exterior outlet; most preferably, the exterior outlet is normally sealed.
  • the normally sealed outlet especially the normally sealed exterior outlet
  • the receptacle generally has a bottom containing the medicament and a top which connects to the housing.
  • the outlet is preferably arranged to open into the receptacle at the top of the receptacle.
  • the outlet is formed as a hole in the housing which is in fluid communication with an outlet pathway to the exterior of the housing.
  • the source of propellant may optionally be provided by a canister of gas (e.g., compressed gas or liquefied gas) or by a supply of compressed gas such as a supply line of compressed gas such as that typically provided in a hospital room.
  • a canister of gas e.g., compressed gas or liquefied gas
  • a supply of compressed gas such as a supply line of compressed gas such as that typically provided in a hospital room.
  • the device of the invention is preferably a handheld device using a canister of a pressurized gas as the source of propellant.
  • the device according to the invention is optionally provided with a mouthpiece attached to the outlet to aid self-administration of the medicament by a patient.
  • a mouthpiece attached to the outlet to aid self-administration of the medicament by a patient. Any known mouthpiece may be used in association with the device according to the invention.
  • the outlet may be provided with a tube for engaging with a breathing tube for a patient using a respirator to enable a third party, e.g., a healthcare professional such as a doctor or nurse to administer a medicament to the patient.
  • a third party e.g., a healthcare professional such as a doctor or nurse to administer a medicament to the patient.
  • the device has been shown (in Examples 1 and 2) to be highly effective for aerosolizing even highly cohesive powders, such as pumactant.
  • the device also provides a high respirable fraction in the delivered powder and a high delivered dose relative to the loaded dose. Accordingly it provides a vehicle for dispensing powders that hitherto have required formulation with large quantities of excipients, such as lactose, for aerosolization. This causes problems of bulk when high doses of active are needed.
  • the present invention thus allows active materials that require high doses to be delivered in respirable "drug only" form, i.e., without a carrier.
  • the outlet of the header unit is generally in fluid communication with the exterior of the housing and may be in the form of a passage formed in the header unit or in the form of tubing, especially medical grade tubing.
  • the outlet is preferably provided with one or more chokes for decelerating the aerosol of the medicament where the device is not a device arranged to produce a standing cloud of medicament. Having one or more outlet chokes is useful because it increases the delay between activation of the device and delivery of the medicament, aiding patient compliance. It is also useful because it reduces the problems of reduction in delivered respirable dose because of impact at the back of a patient's throat.
  • the one or more outlet chokes are preferably one or more constrictions and/or one or more baffles in the outlet.
  • a constriction for use as a choke in the present invention is preferably a reduction in the cross-section of the propellant pathway and/or of the outlet. The reduction in cross-section is optionally either temporary such that after the choke, the propellant pathway and/or outlet revert to their previous cross-section or it is permanent.
  • a baffle for use as a choke in the present invention is preferably provided as an abrupt change in direction of the propellant pathway and/or of the outlet such as a change of direction of from 45 to 135 degrees (measured as the angle between the outlet or propellant pathway before and after the baffle), especially a change of direction of about 90 degrees.
  • the present invention provides a method of dispensing a medicament as an aerosol to a patient in need of such treatment which method comprises the steps of: providing a receptacle having an opening which receptacle contains the medicament in powder form; discharging a pressurized propellant from a canister or cartridge through a delivery tube extending into the receptacle and directed at the medicament so as to fluidize it; forming an aerosol by transfer of energy from the propellant to the powder; and discharging the aerosol through an outlet passage provided at the opening of the receptacle.
  • the device may be provided in the form of a first kit according to the invention which kit comprises a gas canister, a receptacle containing a medicament in powder form and a first delivery device housing including the header unit.
  • a first delivery device housing suitable for use in a first kit according to the invention having a first and a second open-ended compartment wherein the first compartment is adapted to receive a source of propellant and the second compartment is adapted to receive a receptacle containing a medicament in powder form wherein the second compartment provides an inlet for propellant in fluid communication with the first compartment and an outlet wherein the outlet, in use, is spaced from the medicament to allow aerosolization of the medicament.
  • the first kit optionally further comprises a closure (such as an end cap) for sealing the receptacle in the second compartment.
  • a closure such as an end cap
  • the receptacle may be provided in association with the header unit such that a second kit according to the invention comprises a source of propellant, a dispensing receptacle according to the invention and a second delivery device housing according to the invention.
  • the dispensing receptacle comprises a receptacle containing a medicament unit in fluid tight engagement with a header unit wherein the header unit provides the receptacle with an inlet for propellant and an outlet wherein the outlet is spaced from the medicament to allow aerosolization of the medicament in use and wherein the header unit has a propellant entry connector in fluid communication with the inlet for propellant.
  • the second delivery device housing according to the invention has a first open- ended compartment which is adapted to receive a source of propellant and a clip which is adapted to receive a dispensing receptacle according to the invention wherein the clip has a propellant connector associated with it which exit connector is arranged to engage with the entry connector of the dispensing receptacle.
  • a first Mt according to the invention preferably comprises a plurality of receptacles.
  • the receptacle and source of propellant may be provided in the form of combined supply for the first delivery device housing such that the receptacle and source of propellant are linked for combined insertion into the housing.
  • the receptacle containing the medicament can be any suitable packaging container, for example, a glass or plastic vial or a blister pack.
  • a suitable packaging container for example, a glass or plastic vial or a blister pack.
  • the opening of the receptacle is sealed to preserve sterility of the powder and avoid water adsorption.
  • the receptacle may then inserted into the device according to the invention such that the opening of the receptacle is brought into a fluid-tight engagement with the housing, preferably via a gasket or sealing ring.
  • the receptacle may be held in engagement with the housing by a screw or twist connection.
  • the receptacle may contain a single dose of powder for onetime use, or sufficient powder for several doses.
  • the medicament is preferably in the form of a respirable powder. More preferably the medicament is in the form of a powder having a mass median aerodynamic diameter (MMAD) measured by laser diffraction of less than 20 ⁇ m, preferably less than lO ⁇ m, more preferably less than 5 ⁇ m, most preferably from l ⁇ m to 5 ⁇ m.
  • MMAD mass median aerodynamic diameter
  • the spaced arrangement of the outlet is provided by the vial. This is because there is typically empty space between the contents of the vial and its opening. For a 10ml vial, the volume of the contents is usually from 0.5 to 2ml, leaving an empty volume of 8 to 9.5 ml. If the outlet of the device of the invention is formed in the header unit, this empty volume has been found to be sufficient to provide the spaced arrangement between the medicament and the outlet for certain medicaments, particularly pumactant.
  • the device preferably comprises an open-ended compartment for receiving the blister pack.
  • the volume of the open-ended compartment preferably provides the spaced arrangement for the outlet. This is because in a blister pack there is usually insufficient volume between the opening of the blister pack and the medicament for this volume to be used as the volume for the spaced arrangement of the outlet.
  • This volume of the spaced arrangement of the outlet is preferably chosen according to the amount of medicament to be aerosolized and its degree of cohesion. It is preferably not so small that the medicament cannot be aerosolized. Also it is preferably not so large that the aerosol of the medicament is dissipated and destabilizes.
  • the source of propellant is generally arranged in fluid-tight engagement with the propellant pathway by a screw, twist or push connection.
  • the source of propellant is a gas canister, it is preferably a replaceable canister with a metering valve having an extended valve stem which is pressed to discharge gas.
  • the device is preferably arranged such that in use the valve is above the canister.
  • the device of the invention can be used to administer any medicament suitable for administration by inhalation such as a SAPL (surface active phospholipid) composition, such as pumactant, a bronchodilator or a steroid.
  • a SAPL surface active phospholipid
  • the propellant used in the present invention is preferably carbon dioxide, nitrogen, air, or a halocarbon (e.g., a fluorocarbon such as HFA-134a or HFC-227).
  • a halocarbon e.g., a fluorocarbon such as HFA-134a or HFC-227.
  • Figure 1 is a cross-sectional view of a first embodiment of a device according to the invention.
  • Figure Ia is a plan view of the device shown in Figure 1;
  • Figure Ib is a perspective view of a part of the device shown in Figure 1;
  • Figure 2 is a cross-sectional view of a second embodiment of a device according to the invention.
  • Figure 3 is a cross-sectional view of a third embodiment of a device according to the invention.
  • Figure 4 is a cross-sectional view of a first embodiment of a kit according to the invention.
  • Figure 5 is a cross-sectional view of a second embodiment of a kit according to the invention.
  • Figure 6 shows a graph illustrating the data obtained from an in-vitro assessment of
  • Figure 7 shows the relationship between loaded dose and delivered dose in the procedure of Example 2.
  • Figure 8 charts fine particle fractions as a function of canister pressure in the procedure of Example 2.
  • Figure 9 is a side view of a fourth embodiment of a device according to the invention.
  • Figure 10 is a front view of the fourth embodiment of a device according to the invention.
  • Figure 11a is a top view of a fourth embodiment of a device according to the invention.
  • Figure lib is a bottom view of a fourth embodiment of a device according to the invention.
  • Figure 12 is a cross-sectional view of a fourth embodiment of a device according to the invention.
  • Figure 13 is a further cross-sectional view of a fourth embodiment of a device according to the invention.
  • Figure 14 is a front view focusing on the mouthpiece of a fourth embodiment of a device according to the invention.
  • Figure 15 is a view of a bulkhead of a fourth embodiment of a device according to the invention.
  • Figure 16 shows the delivery characteristic of aerosols from a fourth embodiment of a device according to the invention.
  • Figure 17 shows the delivered dose uniformity following repeated actuations from a fourth embodiment of a device according to the invention.
  • Figure 18 shows the fine particle dose uniformity following repeated actuations from a fourth embodiment of a device according to the invention.
  • Figures 19(a)-(c) show views of a fifth embodiment of a device according to the invention.
  • Figures 20(a)-(c) show views of a vial according to the invention.
  • FIG. 1 A first embodiment of a dispenser device 10 of this invention is shown in Figures 1, Ia and Ib of the accompanying drawings.
  • This embodiment has a housing 50 in the form of two open-ended cylinders 51, 52 mounted side by side and forming respective chambers to hold a canister of pressurized propellant 53 (shown in part) and a receptacle 54 of medicament in powder form.
  • the upper surface 95 of the housing 50 is moulded to provide a ridge surface to aid a patient's grip on the device.
  • a propellant pathway 57 is provided through the housing 50.
  • the propellant pathway 57 links a propellant inlet fitting 58 for propellant formed at the top end of cylinder 51 and an aperture 59 formed in the end portion 56.
  • Aperture 59 has a smaller cross-section than that of the propellant pathway 57 such that it provides a propellant pathway choke to decelerate fluid flow through the propellant pathway 57.
  • the propellant pathway choke is in the form of a baffle.
  • the aperture 59 is adjacent to a screw-in header unit 60 seen in more detail in Fig Ib.
  • the header unit 60 has a circumferential groove 68.
  • the housing 50 and header unit 60 are arranged such that the passageway 57 meets the circumferential groove 68.
  • the groove 68 provides a further propellant pathway choke which is in the form of a baffle.
  • the header unit 60 has an inlet pathway 61 which exits the base of the header unit 60.
  • the direction of the inlet pathway 61 is at an angle of approximately 90 degrees to the propellant pathway 57.
  • a further propellant pathway choke is provided in the form of a baffle.
  • the header unit 60 is integrally moulded with the housing 50 such that the features of the header unit 60 are provided by the housing itself.
  • An inlet tube 63 is inserted into the pathway 61 in the base of the header unit 60 and extends into the interior of the cylinder 52. Thus the inlet tube 63 extends into the receptacle 54.
  • An outlet 55 is also formed as a hole in the base of the header unit 60. Outlet 55 does not extend into the receptacle 54. Outlet 55 is spaced from the opening 65 of the receptacle 54 by a gasket 66 which seals the receptacle. In an alternative embodiment, outlet 55 is substantially flush with the opening 65 of receptacle 54. Outlet 55 is in fluid communication with outlet pathway 56 which extends to an outlet port 64 on the outer surface of the header unit 60.
  • Outlet pathway 56 is provided with a constriction 62a where the cross-section of outlet pathway 56 is reduced. Outlet pathway 56 is also provided with a baffle 62b. Constriction 62a and baffle 62b are arranged to decelerate fluid flow through outlet pathway 56.
  • the base of the header unit 60 is provided with a gasket 66 which provides a fluid-tight seal between the header unit 60 and receptacle 54.
  • the receptacle 54 is held tightly against gasket 66 because the open-end of cylinder 52 is sealed by screw-threaded end cap 67.
  • the propellant canister 53 is provided as a replaceable unit, and most suitably contains a compressed gas as propellant, such as carbon dioxide, nitrogen or air.
  • a compressed gas as propellant such as carbon dioxide, nitrogen or air.
  • propellants such as a low boiling liquid, preferably a fluorocarbon such as HFA-134a or HFC-227, under sufficient pressure to maintain the propellant liquid at normal room temperature, may also be used.
  • the propellant canister 53 is a conventional unit which has a metering valve with a protruding valve stem, which when depressed releases propellant through a passage way in the valve stem.
  • the canister 53 is inserted into the cylinder 51 so that the valve stem is located in gas inlet fitting 58.
  • the fitting 58 is dimensioned so that the valve stem is a press fit in the fitting 58 and so holds the canister 53 in the interior of the cylinder 51.
  • the receptacle 54 containing medicament is typically supplied as a sealed unit.
  • Receptacle 54 has an opening 65 which before use is sealed to protect the powder contents.
  • the receptacle 54 is introduced into the interior of the cylinder 52, so that the opening 65 is forced against a resilient gasket 66 and the delivery tube 63 enters into the receptacle 54.
  • the open end of the cylinder 52 is closed with an end cap 61 which engages with the cylinder 52 by a mutual screw-thread 90.
  • the end cap 61 provides the means by which the receptacle 54 is maintained in position with the opening 65 sealingly engaged with the gasket 66.
  • FIG. 3 An alternative arrangement to Figure 1 is shown in Figure 3.
  • This device 210 is the third embodiment of the device according to the invention.
  • Like reference numerals are used to represent like features of the first embodiment.
  • receptacle 54a is smaller than the receptacle 54 shown in Figure 1.
  • This receptacle 54a is in the form of a blister pack.
  • a gasket 66a is provided adjacent to screw-thread 90.
  • a blister pack 54a can be placed into end cap 67 which is then used to close cylinder 52.
  • the mouth 65 of blister pack 54a then engages with gasket 66a which holds the blister pack in place.
  • the outlet tip is directed against the medicament in the blister pack 54a.
  • the device 210 works in the same way as the device 10 according to the first embodiment of the invention.
  • the user pushes the end of the gas canister 53 into the interior of the cylinder 51.
  • the valve stem of the canister remains secured in the passage 58, the inward movement of the canister effectively depresses the valve stem, and releases propellant through the valve stem into the passageway 57.
  • the propellant proceeds through aperture 59, circumferential groove 68, inlet passage 61 and into the receptacle 54 via delivery tube 63.
  • the delivery tube 63 is dimensioned so that its outlet tip 70 is directed at or dipping into the powder contents of the receptacle 54, so that the propellant is directed against the powder.
  • the tube 63 is dimensioned so that the tip 70 lies within the cylinder 52.
  • the propellant fluidizes the powder and forms a respirable aerosol in the volume 82 between the level of the medicament 80 and the outlet 55.
  • the aerosol exits the receptacle 54 via the outlet 55 and the outlet passage 56. On its way through the outlet passage, the aerosol is decelerated by constriction 62a and baffle 62b.
  • the outlet port 64 may be formed as, or exit into, a mouthpiece 165 or a shaped end piece which is a comfortable shape to place in the mouth, nose or other body orifice of a patient.
  • the mouthpiece 165 shown has a baffle 85.
  • the outlet 64 may be extended to form, or connect to, a respiration tube, e.g., a tracheal tube (not shown).
  • a second embodiment of a dispenser device 110 according to the invention is shown in Figure 2. Like reference numerals are used to represent like features of the first embodiment.
  • the device 110 differs from device 10 in that outlet pathway 56a lacks the constriction 62a and baffle 62b of the first embodiment.
  • the device 110 also differs in that outlet port is sealed with removable seal 64a.
  • the device 110 works in the same way as device 10 except that it is suitable for optimization to generate a stable aerosol or standing cloud on activation.
  • FIG. 4 A first embodiment of a kit 310 according to the invention is shown in Figure 4.
  • Kit 310 has a device housing 150, an end cap 67, a source of propellant 53 and a receptacle
  • kit 410 A second embodiment of a kit 410 according to the invention is shown in
  • Kit 410 has a device housing 250, a source of propellant 53 and a dispensing receptacle 154. Like reference numerals are used to represent like features of the first embodiment.
  • Device housing 250 has a propellant exit connector 159 which is provided with a constriction to act as a propellant pathway choke.
  • Device housing 250 also has a clip (not shown) for engaging dispensing receptacle 154.
  • Dispensing receptacle 154 has a receptacle connector 160, header unit 60 and receptacle 54.
  • Receptacle connector 160 joins header unit 60 to receptacle 54.
  • Receptacle connector 160 has a propellant entry connector 175 which is in fluid communication with a propellant pathway
  • the dispensing receptacle 154 is clipped onto the device housing 250 such that the propellant exit connector 159 of the device housing 250 engages with the propellant entry connector 175 of the receptacle connector 160.
  • the assembled kit then functions in the same way as the device 10 according to the first embodiment of the invention.
  • a device according to the invention has been successfully used in experimental veterinary treatment of respiratory disorders in horses using pumactant, as detailed below.
  • Horses are susceptible to a plethora of respiratory complaints. Heaves is the equine equivalent of asthma and both diseases share similar etiology and pathology. The disease, in the equid, has been shown to proceed via a Th2 cytokine driven mechanism (Lavoie, J-P., Maghni, K., Desnoyers, M., Taha, R., Martin, J.G., and Hamid Q.A. (2001) Neutrophilic airway inflammation in horses with heaves is characterized by a Th2 cytokine profile. AmJ.Respir.Crit.Care.Med 164 1410-1413). They, like their human counterparts, have poor compliance and a massive lung surface area estimated to be in the region of 1000m 2 .
  • the aim of the study was to investigate the use and approach to delivery of a thermally labile, hygroscopic and dry surfactant, ensuring an acceptable physicochemical character.
  • the surfactant used was pumactant, (formerly known as ALEC), which is a mixture of two phospholipids: DPPC and PG in a ratio of 7 parts : 3 parts DPPC:PG.
  • ALEC pumactant
  • This specific ratio of phospholipids has a low phase transition temperature (approximately 32 0 C) which it is believed facilitates rapid spreading at body temperature when in contact with an air/water interface. It is also highly rich in DPPC which mimics the high percentage of endogenous DPPC in vivo.
  • Pumactant is physically unstable even at conditions of low relative humidity (approximately 30%), and it can undergo morphological changes, which may affect particle size. Careful attention must therefore be applied to storage and delivery of the surfactant.
  • the device according to the present invention was used for delivery of pumactant because it has the following advantageous delivery characteristics:
  • the pumactant was administered by utilizing an endotracheal tube, bypassing the nasal anatomy, delivering the material to each bronchus; this arrangement, obviously, would also omit patient compliance issues.
  • This Example shows the use of the device according to the invention in administering phospholipids in the treatment of equine respiratory disorders: Heaves in this instance.
  • the treatment is hypothesized to 'work above the line': to form a barrier over the epithelial surface it contacts with.
  • the results from Table 2 indicate a reduction in epithelial shedding.
  • the epithelium is denuded or missing, the tissues below are exposed to insult, allowing the cascade of subsequent inflammatory mechanisms to proceed.
  • micronized pumactant Prior to in vitro testing, the micronized pumactant was first characterized for particle morphology, size distribution, moisture sorption and crystal structure.
  • micronized pumactant was investigated using scanning electron microscopy (SEM) (Jeol 6310: Jeol, Japan). Samples were mounted on carbon sticky tabs prior to analysis and gold coated (Edwards Sputter Coater, UK). Analysis of the data suggests discrete particulates with diameters less than 5 ⁇ m. Furthermore, the micronized particles appeared heavily agglomerated.
  • SEM scanning electron microscopy
  • micronized pumactant The particle-size distribution of the micronized pumactant was determined by laser light scattering (Mastersizer X, Malvern, UK), using a 100 mm lens and small volume stirring circulation cell. The micronized powder was dispersed in cyclohexane and ultras onicated for 5 minutes prior to analysis (determined sufficient to fully de-aggregate the powder).
  • the median volumetric diameter (d ⁇ .5) for micronized pumactant was 1.49 ⁇ m ⁇
  • Moisture sorption profiles of the micronized Pumactant was conducted using dynamic vapour sorption (DVS) (DVS-I Surface Measurement Systems, London, UK).
  • Diffraction patterns for the micronized pumactant were obtained using X-ray powder diffraction (XElPD) using components and methods described elsewhere [Tobyn,
  • Delivered dose was calculated by mass difference.
  • the device and actuator were cleaned using methanol and air-dried.
  • AU experiments were conducted at 45% RH and 25 0 C, and were randomized for loaded dose.
  • the Marple Miller impactor has five collection stages (in the form of sample cups), which at 60 L.min "1 produce 5 effective aerodynamic cut-off diameters; lO ⁇ m, 5 ⁇ m, 2.5 ⁇ m, 1.5 ⁇ m and 0.625 ⁇ m. In addition, a throat and after filter provide collection of particles >10 ⁇ m and ⁇ 0.625 ⁇ m.
  • a rotary vein pump (Gast, Buckinghamshire, UK) generated a flow rate of ⁇ OL.min "1 through the impactor, which was calibrated using a flow meter.
  • micronized pumactant The efficiency of the device in delivering micronized pumactant was investigated. Initially the relationship between loaded dose and delivered dose (0-250 mg) was studied (12 bar canister pressure). Secondly, the aerosolization efficiency of the micronized pumactant (i.e., particles that would potentially be respirable ( ⁇ 5 ⁇ m)) was investigated as a function of canister pressure (6-14 bar). In this case a 120 mg loaded dose was chosen for similarity to clinical trial doses reported previously.
  • delivered dose is a good estimation of the powder bed fluidization efficiency, it is not indicative of the aerosolization efficiency of the system (that is to say, the efficiency of the system in de-agglomerating the micronized powder agglomerates).
  • the fine particle dose therefore is used to describe the potential dose that would be received in the lower respiratory tract (lower bronchiole) [Pritchard supra].
  • FIG. 9-15 show a fourth embodiment of a device 300 according to the invention.
  • the device 300 delivers a medicament in a dry powder form in larger doses than prior devices can achieve. Many prior devices cannot deliver dry powder or can only effectively deliver dry powder in a minimal amount.
  • the device 300 provides a delivered dose of a dry powder medicament of up to approximately 40% to approximately 50% by weight of a loaded dose.
  • higher percentages of the delivered dose such as 55%, 65%, 75%, or 85%
  • lower percentages of the delivered dose such as 10%, 20%, or 30%, may be achieved depending upon the pressure of the propellant gas, the amount of loaded dose, etc.
  • the device 300 is capable of delivering an aerosol of respirable (having a mass median aerodynamic diameter of less than 5 microns) medicament particles.
  • the respirable particles may have a mass median aerodynamic diameter of less than 5 microns, less than 4 microns, less than 3 microns, less than 2 microns, or less than 1 micron.
  • Other larger medicament particles may be delivered by the device 300, such as those having a mass median aerodynamic diameter of less than 20 microns or less than 10 microns.
  • the device 300 positions a power source 305 and the receptacle 54 in the same axis.
  • the power source 305 provides the propellant gas for aerosolizing the medicament.
  • the power source 305 may be a canister, cylinder, container or other source of the propellant gas.
  • the power source 305 may be connected to or inserted into the device 300.
  • the specific propellant gas may be carbon dioxide, nitrogen, argon, helium, air, fluorocarbons such as HFA-134a, or other compressed gases which can be delivered to the body.
  • a canister of nitrogen gas at a pressure of approximately 6 bar to approximately 20 bar is a preferred power source 305.
  • canisters of nitrogen gas at, for example, 8 bar, 10 bar, 12 bar, 14 bar, 16 bar, 18 bar, etc. may be used.
  • the device 300 includes a main body 310, which may be constructed from a pharmaceutical grade molded plastic.
  • the main body 310 provides a housing for the device 300.
  • the main body 310 receives the power source 305 through a top opening 315 of the main body 310.
  • the main body receives the receptacle 54 opposite of the power source 305, i.e., on the bottom of the main body 310 shown as a bulkhead 350.
  • This arrangement provides a direct, non-turning path for the propellant gas to enter the main body 310 and pass through the main body 310 to the receptacle 54.
  • the direct, non-turning path includes a venturi, but the general direction of the propellant gas is not changed as it passes through the main body 310.
  • the bulkhead 350 acts as an interface for the receptacle 54.
  • the terms “top” and “bottom” are used for reference purposes only, as the invention may be practiced in other orientations, such as in a horizontal fashion.
  • This embodiment of the invention functions with or without the inlet tube 63 described in other embodiments of the invention.
  • the device 300 includes an ergonomic design, well suited for the user to self- administer the aerosol.
  • a user applies a direct force to the power source 305 and the main body 310 to deliver the aerosol.
  • a mouthpiece 320 generally protrudes from the main body 310. In the embodiment shown in Figures 9-15, the mouthpiece 320 protrudes in a generally perpendicular manner, although other embodiments of the invention may include a mouthpiece protruding at other angles.
  • the mouthpiece 320 forms a mouthpiece opening 325.
  • the mouthpiece 320 is integral with main body 310.
  • the mouthpiece 320 defines an open passage to deliver the aerosol from the main body 310 to the user.
  • the mouthpiece 320 delivers the medicament in the form of the aerosol to the user.
  • a dust cap 330 may be used to cover the mouthpiece opening 325.
  • the bulkhead 350 receives the receptacle cover 360.
  • the receptacle cover 360 contains the receptacle 54, and the receptacle cover 360 is threadably received by the bulkhead 350.
  • securing the receptacle cover 360 to the bulkhead 350 connects the receptacle 54 to the bulkhead 350.
  • the bulkhead 350 is shown in Figure 15 with the receptacle 54 and the receptacle cover 360 removed.
  • a gasket 365 is positioned between the receptacle cover 360 and the bulkhead 350. As the bulkhead 350 threadably receives the receptacle cover 360, the gasket 365 is compressed between the receptacle cover 360 and the bulkhead 350, thus sealing the receptacle 54 against the bulkhead 350.
  • the gasket 365 and the receptacle 54 may be replaced with a screw top vial that is threadably received by the bulkhead 350. This arrangement eliminates the need for the gasket 365, which may make the device 300 more desirable to users.
  • the bulkhead 350 includes an outlet 370 and an inlet 380.
  • the outlet 370 is in open communication with the mouthpiece opening 325 and the receptacle 54 containing the medicament.
  • the inlet 380 is in open communication with the power source 305 and the receptacle 54 containing the medicament.
  • the receptacle 54 contains the medicament in a powder form.
  • the propellant gas from the power source 305 enters the receptacle 54 via the inlet 380.
  • the propellant gas then aerosolizes the medicament contained in the receptacle 54 forming an aerosol of medicament in the receptacle 54 that is propelled into the mouthpiece 320 via the outlet 370 for inhalation by the user.
  • the receptacle 54 may contain approximately 20 mg to approximately 250 mg of medicament.
  • One of ordinary skill in the art will recognize that the receptacle 54 may contain, for example, 40 mg, 80 mg, 120 mg, 160 mg, 200 mg, etc. of medicament.
  • the receptacle 54 may have a total volume of approximately 1 ml to approximately 10 ml.
  • the receptacle 54 may have a total volume of, for example, 2 ml, 4 ml, 6 ml, 8 ml, etc.
  • the receptacle 54 may be a glass, plastic, or other container suitable to hold a dry powder pharmaceutical.
  • the receptacle 54 may also be replaced with a blister pak having a total volume of 1 ml or less.
  • the diameter of the outlet 370 may range from approximately 0.5 mm to approximately 2.5 mm.
  • the diameter of the outlet 370 may be, for example, 0.8 mm, 1.1 mm, 1.7 mm, 2.0 mm, etc.
  • a preferred diameter for the outlet 370 is approximately 1.4 mm.
  • the diameter of the outlet 370 may be varied to best accommodate the physical/chemical characteristics of the particular medicament to be aerosolized.
  • the diameter of the inlet 380 may range from approximately 0.6 mm to approximately 1.8 mm.
  • the diameter of the inlet 380 may be, for example, 0.8 mm, 1.0 mm, 1.4 mm, 1.6 mm, etc.
  • a preferred diameter of the inlet 380 is approximately 1.2 mm.
  • the diameter of the inlet 380 may be varied to best accommodate the physical/chemical characteristics of the particular medicament to be aerosolized.
  • the main body 310 fixedly receives a stem block 400.
  • the stem block 400 may be integral with the main body 310.
  • the stem block 400 includes an outlet path 410 that is in open communication with the mouthpiece 320 and the outlet 370.
  • the stem block 400 further includes an inlet path 450 that is in open communication with the inlet 380 and a propellant opening 455.
  • the propellant opening 455 is bored or formed in the stemblock 400 and provides an entrance for the propellant gas into the inlet path 450 of the stem block 400.
  • the propellant opening 455 receives a power source inlet 308 from the power source 305.
  • the power source inlet 308 is a tube or conduit extending from the power source 305.
  • the inlet path 450 and the outlet path 410 may be bored through the stem block 400 or may be formed during the molding of the stem block 400.
  • the stem block 400 positions the inlet path 450 and the outlet path 410 in a generally parallel arrangement.
  • the propellant opening 455 receives the power source inlet 308 from the power source 305.
  • the propellant gas next passes through an inlet venturi 460.
  • the inlet venturi 460 decelerates the flow of the propellant gas into the inlet path 450. By decelerating the propellant gas, a better aerosolization of the medicament is achieved.
  • the inlet venturi 460 may be formed or bored into the stem block 400.
  • An average diameter of the inlet venturi 460 may range from approximately 0.3 mm to approximately 0.9 mm.
  • the average diameter of the inlet venturi 460 may be, for example, 0.4 mm, 0.6 mm, 0.8 mm, etc.
  • a preferred average diameter for the inlet venturi 460 is approximately 0.7 mm.
  • the average diameter of the inlet venturi 460 may be varied to best accommodate the physical/chemical characteristics of the particular medicament to be aerosolized.
  • the inlet venturi 460 may be positioned approximately 5 mm to approximately 20 mm from the bulkhead 350.
  • the inlet venturi 460 may be positioned, for example, 8 mm, 11 mm, 14 mm, 17 mm, etc. from the bulldiead 350. This distance between the inlet venturi 460 and the bulkhead 350 also assists in decelerating the propellant gas to achieve better aerosolization of the medicament.
  • the size and positioning of the inlet venturi 460, the outlet 370, the inlet 380 are important in delivering the aerosolized medicament and the high dose of delivery of the medicament.
  • the inlet venturi 460 and the inlet 380 regulate the propellant gas entering the receptacle 54 such that the propellant gas aerosolizes the medicament.
  • the outlet 370 regulates the flow of the aerosol out of the receptacle 54.
  • the bulkhead 350 includes an outlet passage 372 and an inlet passage 382 formed or bored through the bulkhead 350 to provide for the propellant gas and the aerosol to pass through the bulkhead 350.
  • the outlet passage 372 openly connects the outlet 370 with the outlet path 410.
  • the inlet passage 382 openly connects the inlet 380 with the inlet path 450.
  • the bulkhead positions the inlet 380 to direct the incoming propellant gas toward the bottom of the receptacle 54 and the medicament therein. The medicament is then aerosolized, and exits via the outlet 370.
  • the outlet 370 is positioned away from the medicament.
  • the outlet 370 opens to the outlet passage 372 in the bulkhead 350, the outlet passage 372 opens to the outlet path 410 in the stemblock 400, and the outlet path 410 opens into the mouthpiece 320.
  • the outlet path 410 includes an opening 415 in open communication with the mouthpiece 320.
  • the flow of the aerosol through the mouthpiece 320 is generally perpendicular to the flow of the aerosol through the outlet path 410 in this embodiment.
  • the device provides for the delivery of an aerosol of a dry powder.
  • a dry powder includes a substance containing less than or equal to 25% water by weight.
  • the dry powders have less than or equal to 15% water by weight.
  • Certain dry powders have less than or equal to 1%, 2%, 3%, 4% or 5% water by weight.
  • the device 300 was studied using a dry powder medicament called ZofacTM. Notably, up to approximately 40 mg of ZofacTM was delivered in an aerosol with a single actuation from an a loaded dose of approximately 100 mg of ZofacTM.
  • ZofacTM is composed of two synthetic phospholipids, dipalmitoylphosphatidylcholine (DPPC) and unsaturated phosphatidylglycerol (PG), in a ratio of 7:3.
  • DPPC dipalmitoylphosphatidylcholine
  • PG unsaturated phosphatidylglycerol
  • ZofacTM has mass median aerodynamic diameter of the less than 5 microns.
  • ZofacTM contains not more than 4% by weight of water.
  • other dry power medicaments may be used with the device 300.
  • the characteristics of the aerosols delivered by the device 300 were evaluated by both Malvern laser diffraction and Anderson cascade impactor studies.
  • the power source 305 was a nitrogen canister at 10 bar or 14 bar.
  • the amount of ZofacTM delivered at 10 bar and at 14 bar from a 100 mg loaded dose is shown in Table 4. A higher delivered dose was observed with 14 bar compared to 10 bar pressure in the nitrogen canisters.
  • Device efficiency (% respirable dose) under these conditions was 18-22% at 10 bar and 19-31% at 14 bar when evaluated by Malvern and Anderson cascade impactor methods. Delivered dose ranged from 30-44%.
  • the measurement of the delivered dose was determined gravimetrically.
  • the weight of the device 300 and the loaded receptacle 54 was recorded before and after firing the device 300, with the difference being the delivered dose.
  • a Malvern Spraytec system was used to perform the laser diffraction to measure particle size distribution for determination of the respirable fraction ( ⁇ 5 ⁇ m).
  • the device 300 was positioned with the mouthpiece 320 being 5 cm from the laser beam, such that the plume was fired horizontally and the laser beam intersected the direction of plume travel at 90 degrees. Visually, the laser sampled the center of the plume in the vertical direction. Measurements performed were Dv(IO), Dv(50), Dv(90), % Transmittance and % Volume ⁇ 5 ⁇ m.
  • the device 300 provides for the delivery of more than 40 mg ZofacTM from a single actuation of a 100 mg dose.
  • the device 300 has an efficiency in the range of 18-31%, based on respirable fraction.
  • the device 300 provided a higher percent delivered dose with the higher pressure in the nitrogen canisters.
  • the device 300 is a useful delivery device for patients who have low inspiratory flow and for applications requiring delivery of large doses of drugs.
  • the device 300 provides for the repeated active delivery of drugs, including high dose drugs, such as those drugs with a delivered dose of greater than approximately 40 mg delivered dose to approximately 50 mg delivered dose.
  • the device 300 may be repeatedly used to deliver high dose drugs with generally consistent and uniform dosing.
  • the device 300 may be repeatedly used one to fifteen or twenty times to provide one to fifteen or twenty separate aerosols of medicament, for example, the device may be used two, four, six, eight, ten, twelve, fourteen, sixteen, eighteen, etc. times to administer these high dose drugs to provide an economical and convenient drug delivery device. For example, an entire week's worth or more of drugs at two doses per day may be administered by a single device 300.
  • the present invention is described as being usable for one to fifteen or twenty actuations, the device may be actuated additional times to deliver drugs.
  • the single device 300 may be supplied to a user with multiple receptacles 54 in the form of a vial each containing a medicament and multiple power sources 305 in the form of canisters containing the propellant gas.
  • the number of canisters and vials provided with the device 300 will often depend upon the prescription from the physician.
  • the user may then repeatedly use the single device 300 to administer the medicament from the several receptacles 54 using the single device 300.
  • the receptacle 54 and the power source 305 are replaced to assist in providing accurate and uniform dosing of the medicament.
  • the device 300 delivers aerosols with a controlled force.
  • a combination of the device 300, the pressure in the power source 305 and a valve of power source 305 contribute to delivering the aerosols with the controlled force.
  • the device 300 delivers a high dose in multiple actuations with generally consistent and accurate dosing.
  • the device 300 may deliver a dose for two, three, four or five separate actuations with minimal variation between the level of dosing per actuation.
  • the device 300 is designed to deliver a full dose in these separate or multiple actuations. The ability to re-use the device 300 for several actuations provides a product with commercial appeal.
  • the ability of the device 300 to be repeatedly used is tested using either ZofacTM or Lactohale 300 (Freisland Foods Domo, Zwolle, The Netherlands), a micronized lactose that has an average particle size (D50) of ⁇ 5 ⁇ m with no more than 10% of the particles > 10 ⁇ m.
  • D50 average particle size
  • a test configuration was designed to deliver 40 mg of ZofacTM from the mouthpiece from a loaded dose of 100 mg in the receptacle 54.
  • Nitrogen gas (stored in a canister at 14 bar) released via a continuous valve is the power source 305 used to aerosolize ZofacTM from the receptacle 54 in the form of a glass vial.
  • the delivered dose was determined gravimetrieally by measuring the difference between the weight of the device 300 and the loaded receptacle 54 before and after firing the device 300.
  • a Malvern Spraytec was used to measure the geometric particle size distribution from which was estimated the Fine Particle Fraction (% ⁇ 5 ⁇ m).
  • Andersen Cascade Impactors (ACI) USP Apparatus 1; Copley Scientific Ltd., Nottingham, UK
  • ACI Andersen Cascade Impactors
  • the stages were not coated and a pre-separator was used. Due to the active nature of the device 300, standard USP DPI procedures were not appropriate.
  • Lactose (Lacthohale 300) was tested in the device 300.
  • Table 6 shows the particle size distribution of lactose delivered by the device 300 when assessed by laser diffraction.
  • Ten devices 300 were supplied with glass vials filled with a 100 mg nominal loaded dose of lactose. The delivered dose was gravimetrically assessed as 28.2 - 57.6 mg. TABLE 6
  • the device 300 provides for administration of ZofacTM at >40 mg per actuation. With only two of 50 actuations outside the range of +/- 20% of target, the device 300 showed consistent performance in delivery of ZofacTM with up to 5 repeat actuations from the same device 300. Although the device 300 provides for active delivery of high dose drugs (greater than approximately 40 mg to approximately 50 mg delivered dose), one of ordinary skill in the art will recognize that lower dose drugs (such as less than approximately 35 mg, 25 mg, or 15 mg delivered dose) may also be delivered by the device 300. Although Example 4 describes the use of multiple receptacles and multiple power sources, the present invention is not limited to such configurations.
  • Figs. 19(a) - (c) show a fifth embodiment of a compact device 500 according to the invention.
  • the compact device 500 has a reduced size as compared to other embodiments of the invention, which benefits children and others who appreciate the ease of handling a smaller delivery device.
  • the compact device 500 may be easier for some users to manually grasp and squeeze in order to actuate the compact device 500.
  • the compact device 500 is shown in Figs. 19(a) - (c) and has an overall length of approximately 92 millimeters, which is approximately 20% to 40% shorter than some other embodiments of the invention.
  • Other versions of the compact device 500 may have an overall length of approximately 75 millimeters to approximately 115 millimeters.
  • the compact device 500 includes a main body 505 that receives the power source 305 through a top opening 315a of the main body 505.
  • the main body 505 receives a molded, plastic vial 600 opposite of the power source 305, i.e., on the bottom of the main body 505 shown as a bulkhead 350.
  • the main body 505 of the compact device 500 is smaller than the main body 320 of the device 300, as the compact device 500 may use a power source 305 with reduced dimensions and the size of the main body 505 is likewise reduced to accommodate the smaller power source 305.
  • a vial made out of glass or metal could be used instead of the molded plastic vial.
  • the compact device 500 is capable of delivering up to approximately 90% of a 100 mg loaded dose, despite its reduced size.
  • higher percentages of the delivered dose such as 92%, 94%, 96%, and lower percentages of the delivered dose, such as 85%, 75%, 65%, or 55% may be achieved depending upon the pressure of the propellant gas, the amount of loaded dose, etc.
  • the compact device 500 may be used for administration of a surfactant, and is suitable for use with other pharmaceutical agents herein described.
  • the compact device 500 includes the molded, plastic vial 600 that is threadably received by the main body 505.
  • the vial 600 is shown in Figs. 20(a) - (c).
  • the vial 600 used with this embodiment is more compact than other embodiments of the present invention, contributing to the overall reduced size of the compact device 500.
  • the compact device 500 and the plastic vial 600 may be constructed from a pharmaceutical grade molded plastic.
  • the vial may be constructed from materials other than plastic, such as glass or metal.
  • the dimensions of preferred embodiment of the vial 600 will now be described.
  • the preferred vial 600 is approximately 20 mm high and has a volume of 2.5 ml.
  • the compact device 500 is not limited to a specific shape, construction, size or volume of the vial 600, although vials with a volume of approximately 1.5 ml to approximately 3.5 ml and rounded bottom shapes are preferred. It is believed that the rounded interior bottom, the smaller volumes, and the straight sidewalk of the vials contribute to greater delivery efficiency.
  • the construction material may be plastic or glass or metal.
  • the vial 600 may have a length of approximately 10 millimeters to approximately 100 millimeters, e.g., the vial 600 may have a length of 20, 30, 40, 50, 60, 70, or 80 millimeters.
  • the vial 600 may have a volume of approximately 1.0 ml to approximately 8.0 ml, e.g., the vial 600 may have a volume of 1.5, 2.0, 3.0, 3.5, 4.0, 4.5, 5.0, 5.5, 6.0, 6.5, 7.0, or 7.5 ml.
  • the vial 600 is provided with exterior threads 610 that circumscribe the exterior surface of an upper portion 615 of the vial 600.
  • the upper portion of the vial 600 further defines a vial opening 605.
  • the vial 600 further includes generally straight sidewalk 630 that extend from the upper portion 615 and transition into a concave bottom portion 640.
  • the sidewalls 630 have a generally smooth interior surface 635 that reduces the likelihood of medicament adhering to the interior surface 635.
  • the concave bottom portion 640 generally forms a rounded bottom for the interior bottom surface of the vial 600 that promotes aerosolization of the medicament.
  • the concave bottom portion 640 may have a semi-circular cross-section as shown in Fig. 20(a).
  • the vial 600 further includes a stand member 660 on an exterior bottom 670 of the vial 600 below the concave bottom portion 640.
  • the stand member 660 provides the ability for the user to stand the vial 600 in an upright position on the stand member 660 during the loading or unloading procedure for the compact device 500.
  • the stand member 600 may also assist in the automated filling procedures that load the medicament into the vial.
  • the stand member 660 is an optional feature.
  • the power source 305 used with this embodiment is more compact than other embodiments of the present invention, contributing to the overall compact size of the compact device 500.
  • the power source 305 is preferably a canister of nitrogen gas having a volume of approximately 14 ml at a pressure of approximately 10 bar or a volume of 10 ml at a pressure of approximately 14 bar.
  • the preferred power source 305 has an overall length of approximately 58 millimeters.
  • the power source 305 utilizes a continuous valve.
  • the compact device 500 functions similarly in aerosolization as the other embodiments herein, namely it uses the stem block 400 to direct the propellant and aerosolized medicament.
  • the bulkhead 350 includes a ring 510 that extends from a bulkhead 350.
  • the ring 510 includes threads 520 on its interior surface 515 to threadably receive the exterior threads 610 of the vial 600.
  • the vial 600 is screwed into the main body 505 of the compact device 500 and securely tightened against the bulkhead 350. By tightening the vial 600 in place, the vial 600 is properly positioned to receive the inlet 380 and to communicate with the outlet 370.
  • the compact device 500 is comprised of four primary components, namely, the main body 505, the vial 600, the stemblock 400, and the power source 305, which is fewer components than previous embodiments of the present invention resulting in reduced manufacturing costs and assembly costs.
  • each embodiment of the device may be used with a dry powder for the treatment and/or relief of respiratory diseases or conditions.
  • the device may be used for the treatment or relief of all types of asthma, including allergic asthma, perennial asthma, environmental asthma, exercise-induced asthma, cold-induced asthma, chemical-induced asthma, mild asthma, mild to moderate asthma, severe asthma, as well as other diseases and conditions, such as acute respiratory distress syndrome, age-related loss of endogenous surfactant, Baker's lung, bronchiectasis, acute and chronic bronchitis, non-allergenic bronchitis, bronchospasm, allergen-induced bronchospasm, cold-induced bronchospasm, exercise-induced bronchospasm, chronic obstructive pulmonary disease (COPD), cystic fibrosis, emphysema, HTV induced pulmonary complications, idiopathic pulmonary fibrosis, nasal congestion, nasal rhinitis due to allergens or rhinoviruses
  • COPD chronic ob
  • the device may also be used for the treatment of pulmonary damage from a wide variety of causes, including but not limited to, damage from inhalation of particulates, such as silicates, asbestos, carbon and coal, or from inhalation of gases such as superheated air, smoke, hyperbaric oxygen, or toxic gases or fumes, such as hydrogen sulfide, gasoline, turpentine, chloroform, carbon tetrachloride, formaldehyde, dry cleaning solvents, paint solvents, and aldehydes.
  • particulates such as silicates, asbestos, carbon and coal
  • gases such as superheated air, smoke, hyperbaric oxygen, or toxic gases or fumes, such as hydrogen sulfide, gasoline, turpentine, chloroform, carbon tetrachloride, formaldehyde, dry cleaning solvents, paint solvents, and aldehydes.
  • the device may be useful in the delivery of therapeutic substances such as mucosally administered antigens, antibiotics, vaccines, gene therapies, recombinant DNA, proteins, peptides, and cromolyn sodium which can be administered as a dry powder alone or in combination with other dry powders that may be aerosolized by the device. It is envisioned that certain of these delivered substances will be part of the treatment or diagnosis of diseases and conditions unrelated to the pulmonary system. Further, the device may be useful in the deliver of radiolabels, luminescent and non-radiolabeled markers, vitamins, strontium, and other compounds that may act as tracers (i.e. markers that are mixed with a material to follow the material within its physical or biological matrix).

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  • Animal Behavior & Ethology (AREA)
  • Veterinary Medicine (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • General Health & Medical Sciences (AREA)
  • Bioinformatics & Cheminformatics (AREA)
  • Pulmonology (AREA)
  • Biophysics (AREA)
  • Medicinal Preparation (AREA)
  • Pharmaceuticals Containing Other Organic And Inorganic Compounds (AREA)
  • Medicines That Contain Protein Lipid Enzymes And Other Medicines (AREA)

Abstract

Dispositif 10, 110, 300, 500 d'administration pour médicament, comprenant : un boîtier 50 ou un corps principal 310, 505, un réceptacle 54, 600 contenant un médicament sous forme de poudre ; et une source 53, 305 d'agent propulseur, le boîtier 50 ou le corps principal 310, 505 comportant une entrée 63, 380 et une sortie 55, 370 pour le réceptacle 54, 600, l'entrée 63, 380 étant en communication fluidique avec la source 53, 305 d'agent propulseur et étant dirigée contre le médicament et la sortie 55, 370 étant espacée par rapport au médicament pour permettre la mise en aérosol du médicament. Ledit dispositif donne un rendement d'administration amélioré, en particulier une fraction de particules fines administrées supérieure à 20% en poids.
EP06839996A 2005-12-06 2006-11-22 Dispositif d'administration pour aerosol de poudre Withdrawn EP1957138A2 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US55937205A 2005-12-06 2005-12-06
US11/296,637 US20060213514A1 (en) 2003-06-12 2005-12-07 Delivery device for a powder aerosol
US11/408,906 US20070056586A1 (en) 2003-06-12 2006-04-21 Delivery device for a powder aerosol
PCT/US2006/061190 WO2007067855A2 (fr) 2005-12-06 2006-11-22 Dispositif d'administration pour aerosol de poudre

Publications (1)

Publication Number Publication Date
EP1957138A2 true EP1957138A2 (fr) 2008-08-20

Family

ID=39580353

Family Applications (1)

Application Number Title Priority Date Filing Date
EP06839996A Withdrawn EP1957138A2 (fr) 2005-12-06 2006-11-22 Dispositif d'administration pour aerosol de poudre

Country Status (5)

Country Link
EP (1) EP1957138A2 (fr)
JP (1) JP2009531070A (fr)
CN (1) CN101360529A (fr)
AU (1) AU2006321678A1 (fr)
WO (1) WO2007067855A2 (fr)

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2010035252A2 (fr) * 2008-09-26 2010-04-01 Stamford Devices Limited Système d’atomiseur
KR101567125B1 (ko) * 2009-05-27 2015-11-06 이노 테라퓨틱스 엘엘씨 인덱싱된 밸브와 압축 캐니스터 조립체를 칼라에 결합하고 플런저 조립체로 선형 작동시켜 약물 전달 조절용 장치와 유체 소통상태가 되게 하는 방법 및 장치
US20170367882A1 (en) * 2014-11-19 2017-12-28 Nigel Kelly Dosage Delivery in Miniature Dispensing Pumps
WO2019016105A1 (fr) * 2017-07-19 2019-01-24 Dutch Renewable Energy B.V. Système de distribution pour utilisation dans un traitement cryogénique de la peau
US20220211956A1 (en) * 2019-04-23 2022-07-07 Microbase Technology Corp. Atomization device

Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH036362Y2 (fr) * 1987-01-12 1991-02-18
JPH09276405A (ja) * 1996-04-15 1997-10-28 Unisia Jecs Corp 鼻腔用投薬器
GB0217199D0 (en) * 2002-07-25 2002-09-04 Glaxo Group Ltd Medicament dispenser
GB0313604D0 (en) * 2003-06-12 2003-07-16 Britannia Pharmaceuticals Ltd Delivery device for powdered medicament

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See references of WO2007067855A2 *

Also Published As

Publication number Publication date
WO2007067855A3 (fr) 2007-11-22
AU2006321678A1 (en) 2007-06-14
WO2007067855A2 (fr) 2007-06-14
JP2009531070A (ja) 2009-09-03
CN101360529A (zh) 2009-02-04

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