US20150122258A1 - Unit dose cartridge and dry powder inhaler - Google Patents
Unit dose cartridge and dry powder inhaler Download PDFInfo
- Publication number
- US20150122258A1 US20150122258A1 US14/592,790 US201514592790A US2015122258A1 US 20150122258 A1 US20150122258 A1 US 20150122258A1 US 201514592790 A US201514592790 A US 201514592790A US 2015122258 A1 US2015122258 A1 US 2015122258A1
- Authority
- US
- United States
- Prior art keywords
- inhaler
- mouthpiece
- cartridge
- medicament
- airflow
- 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.)
- Abandoned
Links
Images
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
-
- 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
- A61M15/0013—Details of inhalators; Constructional features thereof with inhalation check valves
- A61M15/0015—Details of inhalators; Constructional features thereof with inhalation check valves located upstream of the dispenser, i.e. not traversed by the product
-
- 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
- A61M15/002—Details of inhalators; Constructional features thereof with air flow regulating means
-
- 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
- A61M15/0021—Mouthpieces therefor
- A61M15/0023—Mouthpieces therefor retractable
-
- 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
- A61M15/0021—Mouthpieces therefor
- A61M15/0025—Mouthpieces therefor with caps
-
- 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
- A61M15/00—Inhalators
- A61M15/0086—Inhalation chambers
-
- 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
- A61M15/06—Inhaling appliances shaped like cigars, cigarettes or pipes
-
- 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
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/04—Tracheal tubes
- A61M16/0488—Mouthpieces; Means for guiding, securing or introducing the tubes
- A61M16/049—Mouthpieces
- A61M16/0495—Mouthpieces with tongue depressors
-
- 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
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
- A61M16/0816—Joints or connectors
- A61M16/0825—Joints or connectors with ball-sockets
-
- 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
- A61M2205/43—General characteristics of the apparatus making noise when used correctly
Definitions
- the present invention is in the field of drug administration inhalers having improved control over system volumetric airflow rate, medicament particle transport, particle dispersion, particle metered dosimetry and patient compliance.
- Inhaler devices typically deliver medicine in a liquid droplet mist or as a dry powder aerosol. Deposition of particulate matter within the human lungs is a very complex and not fully understood phenomenon. People breathe over a relatively broad tidal volume. It is known that lower transport velocities of gas-entrained particles entering the mouth avoid impaction better within the oropharyngeal cavity. This is particularly true of particles greater than one to two microns in diameter.
- a related object is to provide an inhaler which creates a high-shear airflow field and controlled circulating gas action to break up particle agglomeration during proper inhaler usage.
- a more specific object is to provide an inhaler mouthpiece which is sized and shaped to develop an airflow which will air stream entrained medicament particles through the oropharyngeal cavity.
- Another specific object is to provide a medicament-containing inhaler cartridge which will supply medicament for complete air entrainment and proper dispersion into the air stream.
- Yet another object is to provide an inhaler airflow-controlling check valve which will straighten the airflow and limit the airflow volume and velocity to values between pre-determined maxima and minima so as to properly entrain, de-agglomerate and deliver medicament particles to the inhaler user.
- a dry powder inhaler includes an air intake and check valve section; a mixing and cartridge section; and a mouthpiece all designed to control the volume and velocity of the inhaled air and aerosolized drug.
- This inhaler can be operated over a very broad inhalation tidal volume range of human breath.
- Several features of the inhaler provide advantageous properties, most significantly with respect to using carefully designated aerodynamic forces to dilute and de-agglomerate the medicament particles, rather than using broad high pressure forces that would contribute to relatively great particle losses in the oropharyngeal region.
- the inhaler intake chamber mounts a check valve bulb having a tapered bulb, bulb travel rod and biasing spring, and one or more perimeter chutes or venturis on the bulb to modulate and control the flow of air through the device.
- the intake further optionally includes a feedback module (not shown) to generate a tone indicating to the user when the adequate inhalation airflow rate has been achieved.
- the inhaler mixing section holds a cartridge containing a dry powder medicament.
- the cartridge has two telescopically assembled halves, and each half has an air inlet hole or orifice-port and an air outlet hole or orifice-port.
- the air stream from the check valve enters the cartridge and then picks up, fluidizes and de-agglomerates the medicament powder in the cartridge.
- the airflow entraining the particles then exits the cartridge and flows through the mouthpiece to the inhaler user.
- the cover on the mixing section can open only when the mouthpiece is at an appropriate pre-determined angle to the intake conduit.
- the mixing section helps to impart a cyclonic flow to air passing through the mixing chamber and cartridge.
- the mouthpiece is integrated to the swivel joint of the mixing section, and can be rotated back into the inhaler intake section and then enclosed by a cover for storage.
- a mouthpiece transport conduit has the ability to expand the cross-section of the airflow, which in turn reduces the velocity of approach of the drug powder into the oral cavity.
- the mouthpiece is offset with respect to the centerline of the mixing cavity and mounted cartridge, and the airflow inlet from the check valve mechanism into the mixing chamber and cartridge is also offset. These tangential offsets encourage a helical airflow around the cartridge, as explained in further detail below.
- the tangential mouthpiece exit tube increases the velocity of the transport gas, which in turn inducts the discharged particles into the exit tube.
- the mouthpiece exit tube then expands in one dimension and the transport gas slows while the particle concentration per unit volume becomes more dilute.
- Flow is expanded to create a secondary shear flow, which helps to further de-agglomerate particles. This also creates a horizontal aspect ratio and therefore aerosol discharge path that is more effective in negotiating and streaming the aerosol through the convoluted pathway of the oral pharynx.
- the mouthpiece expansion wall divergence angle is important for stable particle transport conditions to exist.
- An optimum divergence angle is between 14 and 16 degrees. However, a slightly larger 17 degree divergence angle can be used to achieve a horizontal aerosol discharge path with a 3:1 aspect ratio closely approximating the aspect ratio at the rear of the human throat.
- the continuing slot discharge tube maintains the proper collimation of the particles for controlled particle injection speed and direction of the path of the particles into the oral cavity.
- the mouthpiece includes a tongue depressor, and a tactile protrusion to contact the lips of the user to tell the user that the Dry Powder Inhaler (DPI) is in the correct position.
- DPI Dry Powder Inhaler
- the cartridge halves can be twisted into and out of positions in which the air inlet holes and the air outlet holes are respectively aligned.
- the cartridge can only be inserted into the mixing chamber when a cartridge alignment boss is aligned with a receiving recess at the bottom of the mixing chamber, and a cartridge collar and engages a mating mixing chamber collar ( FIG. 2 ).
- Each cartridge has a unique key on each half that fits only with a particular part of the inhaler, thereby insuring that the proper cartridge containing the proper medicament is preselected, and further insuring that the cartridge is installed properly in the inhaler.
- FIG. 1 is an isometric view of the inhaler embodying the invention.
- FIG. 2 is an exploded view of the inhaler shown in FIG. 1 .
- FIG. 3 is a front isometric view of the medicament containing cartridge used with the inhaler, showing cartridge outlet hole or orifice port alignments.
- FIG. 4 is a rear isometric view of the medicament-containing cartridge used with the inhaler shown in FIG. 3 , showing inlet hole or orifice port alignments.
- FIG. 5 is a front elevational view of the cartridge shown in FIGS. 3 and 4 .
- FIG. 6 is a rear elevational view of the cartridge shown in FIGS. 3 , 4 and 5 .
- FIG. 7 is a sectional view taken substantially in the plane of line 7 - 7 in FIG. 5 .
- FIG. 8 is a sectional view taken substantially in the plane of line 8 - 8 in FIG. 7 .
- FIG. 9 is a sectional view taken substantially in the plane of line 9 - 9 in FIG. 7 .
- FIG. 10 is a top plan view of the inhaler shown in FIGS. 1 and 2 .
- FIG. 11 is a sectional view taken substantially in the plane of line 11 - 11 in FIG. 10 .
- FIG. 12 is a sectional view taken substantially in the plane of line 12 - 12 in FIG. 10 .
- FIG. 13 is an isometric view of the inhaler shown in FIGS. 1 and 2 but configured for the insertion or removal of a medicament-containing cartridge.
- FIG. 14 is an isometric view similar to FIG. 13 but configured as it appears when a medicament-containing cartridge has been inserted in the inhaler.
- FIG. 15 is a sectional view taken substantially in the plane of line 15 - 15 in FIG. 13 .
- FIG. 16 is a sectional view taken substantially in the plane of line 16 - 16 in FIG. 14 .
- FIGS. 16 a , 16 b and 16 c are fragmentary sectional views taken substantially in the plain of line 16 a - 16 c in FIG. 16 .
- FIG. 17 is an isometric view showing the inhaler of FIGS. 1 and 2 , parts being broken away to permit the diagramming of airflow through the inhaler.
- FIG. 18 is an isometric view similar to FIG. 17 diagramming airflow through and around the inhaler check valve, mixing section, cartridge and mouthpiece.
- FIG. 19 is an isometric view similar to FIG. 18 diagramming airflow through and around the inhaler check valve, inside the cartridge, and through the mouthpiece.
- FIG. 20 is an isometric view similar to FIGS. 1 , 2 , 17 , 18 and 19 showing the inhaler, the inhaler flow-control/check-valve, and the flow-control/check-valve sub-housing.
- FIG. 21 is a top plan view of the inhaler shown in FIG. 20 .
- FIG. 22 is a sectional view taken substantially in the plane of line 22 - 22 in FIG. 21 .
- FIG. 23 is a top plan view substantially similar to FIG. 21 .
- FIG. 24 is a sectional view taken substantially in the plane of line 24 - 24 in FIG. 23 .
- FIG. 25 is an isometric view of the flow-control/check-valve and sub-housing shown on FIGS. 17 , 18 , 19 , 20 , 22 and 24 .
- Medicament particles can be delivered/administered over a broad range of inhalation velocity and tidal volume of human breath.
- An inhaler mouthpiece exit tube dilutes, expands, and collimates the particle dispersoid so that the particles do not re-agglomerate during delivery.
- This inhaler provides the means to effect a process whereby particles are fluidized, suspended, then scavenged from the walls by re-circulating scrubbing air, as well as higher speed-flow-through air, followed by a high-shear flow field discharge into an expanded, slower-moving mass of air that disperses and meters the particle concentration expelled from the unit dose cartridge upper outlet port.
- FIG. 1 shows an embodiment of a dry powder inhaler 10 described and claimed herein.
- an inhaler housing 15 includes an intake section 20 , a mixing section 30 and a mouthpiece 40 .
- this inhaler housing 15 is approximately 93 mm long, 38 mm high, and 22 mm thick.
- the other parts illustrated and described here are of proportionate size.
- the mouthpiece 40 can be swiveled from a stored position within the housing 15 to a cartridge installation position in which the mouthpiece 40 is oriented at 90 degrees to the long dimension of the housing. When a cap 352 is closed, the mouthpiece can then be further rotated into an operating position in which the mouthpiece is located at a 180 degree position to the long dimension of the housing.
- a sliding dirt shield cover 16 slidably mounted stored on the housing can be slid upwardly to protect the mouthpiece 40 and the air intake conduit entrance of the inhaler.
- the housing 15 can be formed of a gamma radiation-proof polycarbonate plastic for the rapid sterilization of the inhaler in mass production, as well as in clinical-hospital use.
- An air passage 50 extends through the intake section 20 , the mixing section 30 and the mouthpiece 40 .
- a swivel joint 80 ( FIGS. 2 and 17 ) connects the mouthpiece 40 to the mixing section 30 .
- the mouthpiece and mixing section are one unit, and are connected by a swivel joint to the main housing.
- the cap 352 is pivotally attached to the mixing section 30 , and an interlock mechanism 355 prevents the mouthpiece 40 from being swung into an operating position unless the cartridge 301 is properly seated and installed.
- a cartridge 301 shown in FIGS. 3 , 4 and 5 contains a medicament powder, and it can be installed in and removed from the mixing chamber 30 .
- Aerosolized powder is drawn from the cartridge 301 and mixing section 30 through the mouthpiece 40 to the users' oropharangeal cavity via the mouthpiece 40 .
- the velocity of the travel slows, thus preparing the powder for effective delivery to the inhaler user's broncheal tract and lungs.
- the mixing section 30 has a cap 352 which may be configured as a transparent magnifying lens.
- An arrow 460 ( FIG. 17 ) shows the direction of aerosolized medicament powder discharge from the cartridge and through the mouthpiece.
- Air is caused to enter the inhaler by an inhalation effort which the inhaler user exerts on and in the mouthpiece 40 .
- ambient air enters the air control system 171 through air intake ports 172 and is directed to an airflow-control/check-valve 180 .
- this check valve system 180 includes a conical head 181 mounted upon a bulb rod 182 .
- a bulb 184 is slidably mounted upon the rod 182 for reciprocation between a stagnant airflow position and a dynamic airflow-inhibiting position.
- the bulb 184 is drawn into a normal relatively downstream airflow position, by the force of airflow acting to overcome the bulb reactive force of a conical tension spring 185 as suggested particularly in FIG. 19 .
- This spring is preferably formed of medical grade stainless steel.
- Chute-like recesses 186 in the surface 187 of the bulb 184 control and direct the flow of air over the bulb 184 .
- Airflow straightening vanes 189 mounted on the conical head 181 engage a confronting conical venturi formation or seat 191 ( FIG. 22 ). Air flowing between the head 181 and seat 191 is accelerated and the airflow straightened, in accordance with known characteristics of gaseous airflow.
- This bulb and spring mechanism allow the inhaler user to generate a slight partial vacuum in his lungs before the bulb is drawn away from the seating arrangement.
- a slight velocity increase of airflow through the inhaler assists in drawing the medicament from the cartridge (FIGS. 1 and 17 - 19 ), through the inhaler and into the bronchial region and lungs of the user.
- the check valve arrangement 180 can be mounted in a sub-housing 200 of intake section 20 , and both components 20 and 180 can be removed from the inhaler housing 50 for cleaning, repair or replacement.
- a lock device 196 of known design can be used to secure the sub-housing 200 of intake section 20 and contained components within the inhaler housing 15 .
- a clicking sound is produced.
- this clicking sound indicates to the inhaler user that he or she is drawing properly upon the mouthpiece and operating the inhaler correctly.
- a vibratory mechanical reed (not shown) can be mounted in the airflow path to produce an audible signal to the user.
- an electronic flow or pressure sensor can trigger an audible or visual signal indicator to tell the user that proper airflow has been established.
- This airflow-control/check-valve system 180 serves to deliver air at a predetermined volume and velocity to downstream inhaler parts.
- the airflow acts to pick-up, fluidize, de-agglomerate and deliver entrained medicament particles to the inhaler user in a dispersed form and at a proper location to enter the user's bronchial system.
- this mixing section 30 here comprises a fixed support 31 upon which is journaled a cup 32 .
- the mouthpiece 40 is attached to the swivel cup 32 and can thus act as a handle for pivoting the cup member 32 and mouthpiece to the configurations shown in FIGS. 1 , 14 and elsewhere and as more fully described below.
- the mixing section 30 is provided with shapes on its interior surface to encourage airflow acceleration so as to suspend medicament particles in the airflow and to de-agglomerate them.
- a medicament-containing cartridge 301 can be mounted within the cup 32 .
- the cartridge 301 is provided with air inlet and outlet holes ( FIGS. 5-9 ), the cup 32 is sized and shaped so as to direct air into the cartridge through the lower inlet hole. The air then generally flows up through the cartridge in an upward direction while producing a dual counter-rotating helical motion, and out of the cartridge and down the mouthpiece as particularly suggested in FIG. 19 .
- FIG. 5-9 air inlet and outlet holes
- excess volume of air can flow around the outside of the cartridge but within the mixing chamber to again mate with the emerging medicament-laden air discharged from the cartridge and flowing into the mouthpiece.
- air flowing into the mixing chamber feeds the cartridge inlet holes, helps to extract air flowing out from the cartridge discharge holes, dilutes the medicament-laden airflow, and provides controlled, even concentrations of medicament particles into the mouthpiece airflow.
- the particle entrainment and dilution in the mouthpiece are provided primarily by the cartridge bypass air.
- the mixing chamber inlet port 33 provides vortex shedding which, aided by the top and bottom internal mixing chamber internal swirl toroids 34 and 35 , fluidizes, suspends and scrubs the powder in the cartridge.
- the upper semi-toroid shape 35 changes airflow direction from dispersion chamber to mouthpiece, thus aiding further de-agglomeration of the medicament particles in the entrained powder stream.
- a modest gas expansion velocity with subsequent air shearing forces (and flow resistance) act to support a fully dispersed flow through the mouthpiece 40 .
- a chamber which includes internal protrusions or spiral shapes can be provided.
- the interior surfaces of the mixing chamber can be shaped to provide one or more helical flows of air around and within the cartridge, if desired.
- the cartridge 301 is shown in further detail in FIGS. 3-9 .
- the cartridge 301 comprises an upper half 302 and a lower half 303 , each preferably formed of transparent plastic material.
- the preferable plastic material is provided with ultra smooth surfaces, is capable of being molded into the cartridge components which have and which maintain great dimensional accuracy, does not absorb or otherwise interact with water or moisture, and has electrostatically neutral characteristics such that the medicament powder in the cartridge 301 is not retained by cartridge static charge, and does not adhere to the cartridge halves 302 , 303 .
- One such material which can be used for the lower half 303 is the Topaz brand of cyclicolephin co-polymer plastic offered by Ticonia Corporation.
- the upper cartridge half 302 defines an air inlet hole 306 and an outlet hole 307
- the cartridge lower half defines a corresponding air inlet hole 308 and an air outlet hole 309 .
- This upper half can be made of a clear very low water absorbent nylon.
- the halves 302 and 303 interengage through a telescopic fit.
- a circumferential ring and groove arrangement 310 retain the halves 302 and 303 in their assembled configuration.
- the inlet holes 306 and 308 formed at the lower portion of the cartridge are beveled, and the outlet holes 307 , 309 are likewise beveled at an angle of substantially 60 degrees so as to encourage air ingress and egress but to discourage electrostatic adhesion and agglomerate deposition of 10 or larger micron-sized medicament particles on the plastic defining the hole edges.
- the inlet holes 306 and 308 are arranged to overlap or register with one another when the cartridge halves are twisted (as suggested by the arrow A in FIG. 4 c ) into the appropriate cartridge open position, and the holes 306 , 308 are elongated in a vertical direction.
- outlet holes 307 , 309 are arranged to overlap and provide free air egress when the cartridge halves are appropriately aligned, and the holes are elongated in a horizontal direction so as to orient the air outflow for delivery to the horizontally elongated channel in the mouthpiece 40 .
- This cartridge 301 is approximately one-quarter inch in diameter and its body is approximately 1 inch in axial length, and so to facilitate easy installation and extraction from the inhaler 10 , a handle or manipulator structure 314 is provided atop the cartridge 301 .
- the handle structure 314 comprises four web extensions 315 which extend from the cartridge body to a finger disk 316 which may have a coined or serrated periphery.
- a pointer or dial indicator 317 is formed atop the disk 316 and is further discussed below.
- a cartridge installation check boss 319 is formed at the bottom of the cartridge 301 .
- this check boss can have a unique, non-circular shape of any desired form such as those shown in FIGS. 16 a , 16 b and 16 c .
- These unique embossments are designed to fit within a closely mating relief 39 formed in the fixed support 31 of the mixing section. These unique embossed shapes will be uniquely associated with particular medicaments, so that a cartridge containing an incorrect medicament cannot be installed in a particular patient's inhaler.
- a mounting mechanism 350 is provided as especially shown in FIGS. 1 , 2 , 13 - 16 and 17 .
- This mounting mechanism 350 takes the form of a cap 352 formed of clear plastic, pivotally mounted so as to cover the mixing section cup 32 . See especially FIG. 16 .
- a pivot pin 353 interconnects the cap 352 with an extension 354 of the mount 31 .
- the top of this cap 352 is curved so as to act as a magnifying lens. This dome shape also provides strength to the cover structure.
- the cartridge can be installed and the cap 352 secured in place when the mouthpiece 40 and cartridge are pivoted into their operating positions.
- a radially outwardly biased lock pin 356 ( FIG. 2 ) depending from the cap mount 331 pushes the cap 352 upwardly and into an open position when the mouthpiece 40 and cap mount 331 are swiveled into a position so that the mouthpiece is located at approximately 90 degrees to the long or greater dimension of the inhaler body 15 .
- the lock pin 356 is pushed radially outwardly and the cap 352 is rotated upwardly when the lock pin 356 is pushed into a relief defined in a skirt 360 of the cover 358 ( FIG. 2 ).
- This arrangement acts as a safety and user prompting feature.
- the mouthpiece 40 can be pivoted out of its cartridge installation and cap release position as shown in FIGS. 13-16 and into the user medication inhalation configuration shown in FIGS. 1 , 17 and 20 - 24 .
- This mouthpiece pivoting motion can occur only when the cap skirt 360 is pushed down into its closed position and the lock pin 356 is radially depressed so as to permit mouthpiece 40 swiveling action.
- the cap springs open as shown in FIGS. 13 and 15 , and thereby indicates to the inhaler user that he or she should inspect and, if necessary, replace or insert a new cartridge 301 .
- the mouthpiece 40 discharges particle-laden air to the oropharyngeal cavity of the user.
- the mouthpiece diverges the air and particle stream to slow down the particles, and then converges the particle stream to collimate and aim the particles at the rear of the user's mouth.
- the mouthpiece is long enough so that it extends approximately midway into most users' mouths.
- the inhaler mouthpiece is oriented so as to extend diagonally upwardly at approximately a 3 degree angle X as suggested in FIGS. 22 and 24 .
- the horizontally spaced walls of the mouthpiece diverge at an angle Y of approximately 5 to 8 degrees.
- the ratio of the height H of the mouthpiece air passage page to the width W of the air passage is approximately 3:1.
- a tooth and lip placement embossment 411 can be provided to depend from the distal end 412 of the mouthpiece 40 .
- the mouthpiece is preferably made of Delrin or Celcon co-polymer acetyl plastic so as to provide proper strength, swivel bearing self-lubricity, and smooth internal and external finish.
- the inhaler employs a regulated flow of air to fluidize and aerosolize medicament particles and transport them to the desired rear region of the orophalangeal cavity.
- air is first drawn into the interior of the inhaler housing 15 and through the intake ports 172 as suggested in FIGS. 17 and 18 , to a predetermined volumetric airflow which is controlled by the flow-control/check-valve mechanism 180 .
- the airstream then enters into the cartridge interior through the vertically elongated and aligned inlet ports 306 .
- the air entering the cartridge interior immediately impinges upon the opposite cylindrical cartridge wall.
- the impacted air jet then redistributes itself into several portions.
- One of the portions flows downwardly into the medicament powder bed, and strips the powder from the cartridge surface and begins to fluidize it into an airborne dust cloud.
- Another portion of the impingement jet is directed laterally in both directions, which creates dual counter-rotating vertical spinning helical columns. The majority of the fluidized medicament powder is retained in these two columns, where the first deagglomeration action is achieved.
- Yet another portion of the impingement jet is directed vertically, which creates a vertical high-speed air jet along the cartridge wall into the cartridge discharge port or holes 306 , 309 . Particles in the helical aerosolized columns are scavenged into the jetstream and then discharged from the cartridge.
- This scavenging effect results in particles being metered out or discharged from the cartridge at a relatively steady particle distribution rate. Particle agglomerations are further broken down by the discharge process. Large agglomerates impinge upon the opposing mixing chamber wall, and are further reduced into smaller agglomerates. Single particles and smaller agglomerates are carried forward through the mixing chamber and into the mouthpiece discharge tube. The remaining agglomerates are pulled apart in the high-shear and shock flow field produced by the mouthpiece tangential entry port. Thus a steady flow of a individual medicament particles emerge from the mouthpiece and into the users oropharyngeal airway. These airstream flows and the sub-stream flows thus result in complete air entrainment of all medicament particles in the cartridge, and delivery of a complete, closely metered medicament dose to the patient.
Landscapes
- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Pulmonology (AREA)
- General Health & Medical Sciences (AREA)
- Veterinary Medicine (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Hematology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- Anesthesiology (AREA)
- Public Health (AREA)
- Bioinformatics & Cheminformatics (AREA)
- Emergency Medicine (AREA)
- Otolaryngology (AREA)
- Medicinal Preparation (AREA)
- Infusion, Injection, And Reservoir Apparatuses (AREA)
- Medical Preparation Storing Or Oral Administration Devices (AREA)
- Pharmaceuticals Containing Other Organic And Inorganic Compounds (AREA)
- Medicines Containing Antibodies Or Antigens For Use As Internal Diagnostic Agents (AREA)
Abstract
A dry powder inhaler having improved aerodynamic properties for diluting, dispersing, and metering drug particles for increasing the efficiency of pulmonary drug delivery to a patient is described. The inhaler comprises, in general, a housing having an air intake, an airflow-control/check-valve, a mixing section and a mouthpiece. A cartridge loaded with a single dose of medicament can be installed in the mixing section.
Description
- This application is a continuation of co-pending U.S. utility patent application Ser. No. 13/490,292, filed Jun. 6, 2012, which is a continuation of U.S. Ser. No. 12/102,625, filed Apr. 14, 2008, now U.S. Pat. No. 8,215,300, which is a continuation of U.S. Ser. No. 10/655,153 filed Sep. 4, 2003, now U.S. Pat. No. 7,464,706, which is a continuation-in-part of U.S. Ser. No. 09/621,092, filed Jul. 21, 2000, now U.S. Pat. No. 7,305,986, which claims priority from U.S. provisional application Ser. No. 60/145,464 filed Jul. 23, 1999, and No. 60/206,123 filed May 22, 2000, all of which are incorporated herein by reference in their entirety.
- The present invention is in the field of drug administration inhalers having improved control over system volumetric airflow rate, medicament particle transport, particle dispersion, particle metered dosimetry and patient compliance.
- In the early 1970's it was found that certain medicines could be administered in dry-powder form directly to the lungs by inhalation through the mouth or inspiration through the nose. This process allows the medicine to bypass the digestive system, and may, in certain cases, allow smaller dosages to be used to achieve the same results as orally ingested or injected medicines. In some cases, it provides a delivery technique that reduces side effects for medicines and interactions with other prescribed medicines, as well as providing a more rapid drug medication uptake.
- Inhaler devices typically deliver medicine in a liquid droplet mist or as a dry powder aerosol. Deposition of particulate matter within the human lungs is a very complex and not fully understood phenomenon. People breathe over a relatively broad tidal volume. It is known that lower transport velocities of gas-entrained particles entering the mouth avoid impaction better within the oropharyngeal cavity. This is particularly true of particles greater than one to two microns in diameter.
- In order for particles to remain suspended in a gas stream, their superficial transport velocity must be greater than their gravity settling velocity. For example, a 100 micron particle must have a transport gas velocity of approximately 7 ft/sec or greater for the 100 micron particle to remain in a particle/gas entrainment state. The required transport velocity for smaller particles is much less High speed particles have a greater propensity to impact and deposit on the tissue lining of the oropharyngeal cavity, as noted above. Thus, a significant number of particles are lost and will not enter the lungs, if those particles are not transported at the correct velocity.
- Another common problem with inhalers is that the particles agglomerate, causing clumping of particles that then adhere to the inhaler or the oral cavity, rather than entering the lungs. Most approaches to this problem have been to include a surfactant in, on or with the particles to decrease the adhesion between particles.
- Importantly, it should not be difficult for a patient to load the inhaler with medicine, and to easily and properly use the inhaler so that the correct dosage is actually administered. Many current dry particle inhalers fail in one or more of these important criteria.
- It is therefore an object of the present invention to provide inhalers which are easy to properly use, and which deliver drug powders so that the powder enters the lungs instead of adhering to the back of the throat.
- It is an object of the invention to provide an inhaler which will operate effectively with dry powder medicaments having particles ranging in size from about 0.5 to about 10 microns, and preferably from about 1 to about 5 microns in size.
- It is a further object of the present invention to provide an inhaler that can operate effectively over a broad inhalation tidal volume range of human breath.
- It is a still further object of the present invention to provide an inhaler which controls the volume and velocity of airflow so as to provide effective and desirable colimation, de-agglomeration and entrainment of the inhaled drug.
- A related object is to provide an inhaler which creates a high-shear airflow field and controlled circulating gas action to break up particle agglomeration during proper inhaler usage.
- A more specific object is to provide an inhaler mouthpiece which is sized and shaped to develop an airflow which will air stream entrained medicament particles through the oropharyngeal cavity.
- Another specific object is to provide a medicament-containing inhaler cartridge which will supply medicament for complete air entrainment and proper dispersion into the air stream.
- Yet another object is to provide an inhaler airflow-controlling check valve which will straighten the airflow and limit the airflow volume and velocity to values between pre-determined maxima and minima so as to properly entrain, de-agglomerate and deliver medicament particles to the inhaler user.
- Other objects and advantages of the invention will become apparent upon reading the following detailed description and upon reference to the drawings. Throughout the drawings, like reference numerals refer to like parts.
- A dry powder inhaler (DPI) includes an air intake and check valve section; a mixing and cartridge section; and a mouthpiece all designed to control the volume and velocity of the inhaled air and aerosolized drug. This inhaler can be operated over a very broad inhalation tidal volume range of human breath. Several features of the inhaler provide advantageous properties, most significantly with respect to using carefully designated aerodynamic forces to dilute and de-agglomerate the medicament particles, rather than using broad high pressure forces that would contribute to relatively great particle losses in the oropharyngeal region.
- The inhaler intake chamber mounts a check valve bulb having a tapered bulb, bulb travel rod and biasing spring, and one or more perimeter chutes or venturis on the bulb to modulate and control the flow of air through the device. The intake further optionally includes a feedback module (not shown) to generate a tone indicating to the user when the adequate inhalation airflow rate has been achieved.
- The inhaler mixing section holds a cartridge containing a dry powder medicament. The cartridge has two telescopically assembled halves, and each half has an air inlet hole or orifice-port and an air outlet hole or orifice-port. When the halves are twisted so as to align the air holes, the air stream from the check valve enters the cartridge and then picks up, fluidizes and de-agglomerates the medicament powder in the cartridge. The airflow entraining the particles then exits the cartridge and flows through the mouthpiece to the inhaler user. The cover on the mixing section can open only when the mouthpiece is at an appropriate pre-determined angle to the intake conduit. The mixing section helps to impart a cyclonic flow to air passing through the mixing chamber and cartridge.
- An important feature of the inhaler is the mouthpiece. The mouthpiece is integrated to the swivel joint of the mixing section, and can be rotated back into the inhaler intake section and then enclosed by a cover for storage. A mouthpiece transport conduit has the ability to expand the cross-section of the airflow, which in turn reduces the velocity of approach of the drug powder into the oral cavity. As shown in
FIGS. 10 , 18, 19, 21 and 23, the mouthpiece is offset with respect to the centerline of the mixing cavity and mounted cartridge, and the airflow inlet from the check valve mechanism into the mixing chamber and cartridge is also offset. These tangential offsets encourage a helical airflow around the cartridge, as explained in further detail below. Initially, the tangential mouthpiece exit tube increases the velocity of the transport gas, which in turn inducts the discharged particles into the exit tube. The mouthpiece exit tube then expands in one dimension and the transport gas slows while the particle concentration per unit volume becomes more dilute. Flow is expanded to create a secondary shear flow, which helps to further de-agglomerate particles. This also creates a horizontal aspect ratio and therefore aerosol discharge path that is more effective in negotiating and streaming the aerosol through the convoluted pathway of the oral pharynx. - The mouthpiece expansion wall divergence angle is important for stable particle transport conditions to exist. An optimum divergence angle is between 14 and 16 degrees. However, a slightly larger 17 degree divergence angle can be used to achieve a horizontal aerosol discharge path with a 3:1 aspect ratio closely approximating the aspect ratio at the rear of the human throat. Once the expansion divergence has reached a specified limit, the continuing slot discharge tube maintains the proper collimation of the particles for controlled particle injection speed and direction of the path of the particles into the oral cavity. The mouthpiece includes a tongue depressor, and a tactile protrusion to contact the lips of the user to tell the user that the Dry Powder Inhaler (DPI) is in the correct position.
- The cartridge halves can be twisted into and out of positions in which the air inlet holes and the air outlet holes are respectively aligned. The cartridge can only be inserted into the mixing chamber when a cartridge alignment boss is aligned with a receiving recess at the bottom of the mixing chamber, and a cartridge collar and engages a mating mixing chamber collar (
FIG. 2 ). Each cartridge has a unique key on each half that fits only with a particular part of the inhaler, thereby insuring that the proper cartridge containing the proper medicament is preselected, and further insuring that the cartridge is installed properly in the inhaler. -
FIG. 1 is an isometric view of the inhaler embodying the invention. -
FIG. 2 is an exploded view of the inhaler shown inFIG. 1 . -
FIG. 3 , includingFIGS. 3 a, 3 b and 3 c, is a front isometric view of the medicament containing cartridge used with the inhaler, showing cartridge outlet hole or orifice port alignments. -
FIG. 4 , includingFIGS. 4 a, 4 b and 4 c, is a rear isometric view of the medicament-containing cartridge used with the inhaler shown inFIG. 3 , showing inlet hole or orifice port alignments. -
FIG. 5 is a front elevational view of the cartridge shown inFIGS. 3 and 4 . -
FIG. 6 is a rear elevational view of the cartridge shown inFIGS. 3 , 4 and 5. -
FIG. 7 is a sectional view taken substantially in the plane of line 7-7 inFIG. 5 . -
FIG. 8 is a sectional view taken substantially in the plane of line 8-8 inFIG. 7 . -
FIG. 9 is a sectional view taken substantially in the plane of line 9-9 inFIG. 7 . -
FIG. 10 is a top plan view of the inhaler shown inFIGS. 1 and 2 . -
FIG. 11 is a sectional view taken substantially in the plane of line 11-11 inFIG. 10 . -
FIG. 12 is a sectional view taken substantially in the plane of line 12-12 inFIG. 10 . -
FIG. 13 is an isometric view of the inhaler shown inFIGS. 1 and 2 but configured for the insertion or removal of a medicament-containing cartridge. -
FIG. 14 is an isometric view similar toFIG. 13 but configured as it appears when a medicament-containing cartridge has been inserted in the inhaler. -
FIG. 15 is a sectional view taken substantially in the plane of line 15-15 inFIG. 13 . -
FIG. 16 is a sectional view taken substantially in the plane of line 16-16 inFIG. 14 . -
FIGS. 16 a, 16 b and 16 c are fragmentary sectional views taken substantially in the plain ofline 16 a-16 c inFIG. 16 . -
FIG. 17 is an isometric view showing the inhaler ofFIGS. 1 and 2 , parts being broken away to permit the diagramming of airflow through the inhaler. -
FIG. 18 is an isometric view similar toFIG. 17 diagramming airflow through and around the inhaler check valve, mixing section, cartridge and mouthpiece. -
FIG. 19 is an isometric view similar toFIG. 18 diagramming airflow through and around the inhaler check valve, inside the cartridge, and through the mouthpiece. -
FIG. 20 is an isometric view similar toFIGS. 1 , 2, 17, 18 and 19 showing the inhaler, the inhaler flow-control/check-valve, and the flow-control/check-valve sub-housing. -
FIG. 21 is a top plan view of the inhaler shown inFIG. 20 . -
FIG. 22 is a sectional view taken substantially in the plane of line 22-22 inFIG. 21 . -
FIG. 23 is a top plan view substantially similar toFIG. 21 . -
FIG. 24 is a sectional view taken substantially in the plane of line 24-24 inFIG. 23 . -
FIG. 25 is an isometric view of the flow-control/check-valve and sub-housing shown onFIGS. 17 , 18, 19, 20, 22 and 24. - While the invention will be described in connection with several preferred embodiments and procedures, it will be understood that it is not intended to limit the invention to these embodiments and procedures. On the contrary, it is intended to cover all alternatives, modifications and equivalents as may be included within the spirit and scope of the invention as defined by the appended claims.
- An improved inhaler has been developed which has several novel features optimizing performance. Medicament particles can be delivered/administered over a broad range of inhalation velocity and tidal volume of human breath. An inhaler mouthpiece exit tube dilutes, expands, and collimates the particle dispersoid so that the particles do not re-agglomerate during delivery. This inhaler provides the means to effect a process whereby particles are fluidized, suspended, then scavenged from the walls by re-circulating scrubbing air, as well as higher speed-flow-through air, followed by a high-shear flow field discharge into an expanded, slower-moving mass of air that disperses and meters the particle concentration expelled from the unit dose cartridge upper outlet port.
- Inhaler Overview
-
FIG. 1 shows an embodiment of adry powder inhaler 10 described and claimed herein. In broad conceptual terms, aninhaler housing 15 includes anintake section 20, amixing section 30 and amouthpiece 40. In the preferred embodiment, thisinhaler housing 15 is approximately 93 mm long, 38 mm high, and 22 mm thick. The other parts illustrated and described here are of proportionate size. Themouthpiece 40 can be swiveled from a stored position within thehousing 15 to a cartridge installation position in which themouthpiece 40 is oriented at 90 degrees to the long dimension of the housing. When acap 352 is closed, the mouthpiece can then be further rotated into an operating position in which the mouthpiece is located at a 180 degree position to the long dimension of the housing. When themouthpiece 40 is stored within theinhaler 15, a sliding dirt shield cover 16 slidably mounted stored on the housing can be slid upwardly to protect themouthpiece 40 and the air intake conduit entrance of the inhaler. Thehousing 15 can be formed of a gamma radiation-proof polycarbonate plastic for the rapid sterilization of the inhaler in mass production, as well as in clinical-hospital use. - An air passage 50 (
FIG. 17 ) extends through theintake section 20, the mixingsection 30 and themouthpiece 40. A swivel joint 80 (FIGS. 2 and 17 ) connects themouthpiece 40 to themixing section 30. In the preferred embodiment, the mouthpiece and mixing section are one unit, and are connected by a swivel joint to the main housing. Thecap 352 is pivotally attached to themixing section 30, and an interlock mechanism 355 prevents themouthpiece 40 from being swung into an operating position unless thecartridge 301 is properly seated and installed. Acartridge 301 shown inFIGS. 3 , 4 and 5 contains a medicament powder, and it can be installed in and removed from the mixingchamber 30. - Aerosolized powder is drawn from the
cartridge 301 and mixingsection 30 through themouthpiece 40 to the users' oropharangeal cavity via themouthpiece 40. As air and powder travel through the mouthpiece, the velocity of the travel slows, thus preparing the powder for effective delivery to the inhaler user's broncheal tract and lungs. - So that writing or identifying indicia on medicament-containing
cartridge 301 can be read easily, the mixingsection 30 has acap 352 which may be configured as a transparent magnifying lens. An arrow 460 (FIG. 17 ) shows the direction of aerosolized medicament powder discharge from the cartridge and through the mouthpiece. - Air is caused to enter the inhaler by an inhalation effort which the inhaler user exerts on and in the
mouthpiece 40. As shown particularly inFIG. 17 and as suggested by theairflow arrows 460 inFIGS. 17 and 18 , ambient air enters theair control system 171 throughair intake ports 172 and is directed to an airflow-control/check-valve 180. As shown inFIGS. 17 , 18, and 25, thischeck valve system 180 includes aconical head 181 mounted upon abulb rod 182. Abulb 184 is slidably mounted upon therod 182 for reciprocation between a stagnant airflow position and a dynamic airflow-inhibiting position. Thebulb 184 is drawn into a normal relatively downstream airflow position, by the force of airflow acting to overcome the bulb reactive force of aconical tension spring 185 as suggested particularly inFIG. 19 . This spring is preferably formed of medical grade stainless steel. Chute-like recesses 186 in thesurface 187 of thebulb 184 control and direct the flow of air over thebulb 184.Airflow straightening vanes 189 mounted on theconical head 181 engage a confronting conical venturi formation or seat 191 (FIG. 22 ). Air flowing between thehead 181 andseat 191 is accelerated and the airflow straightened, in accordance with known characteristics of gaseous airflow. - When the inhaler user draws air through the
mouthpiece 40, air flows to and around thebulb 184, and the imbalance of air pressure forces acting upon thereciprocating bulb 184 pushes the bulb in a downstream direction along therod 182 into positions which inhibits airflow. Because thebulb 184 is mounted to thetension spring 185, increasing amounts of force are required to draw thebulb 184 into increasingly airflow-restricting positions. Additional bulb movement control can be provided, if desired, by an opposing second spring (not shown) forming a high-sensitivity push-pull system. - This bulb and spring mechanism allow the inhaler user to generate a slight partial vacuum in his lungs before the bulb is drawn away from the seating arrangement. Thus, by the time significant vacuum is generated, a slight velocity increase of airflow through the inhaler assists in drawing the medicament from the cartridge (FIGS. 1 and 17-19), through the inhaler and into the bronchial region and lungs of the user.
- As suggested particularly in
FIG. 20 , thecheck valve arrangement 180 can be mounted in asub-housing 200 ofintake section 20, and bothcomponents inhaler housing 50 for cleaning, repair or replacement. Alock device 196 of known design can be used to secure thesub-housing 200 ofintake section 20 and contained components within theinhaler housing 15. - When air is being drawn through the
inhaler 10 and thebulb 184 is drawn along therod 182 so as to impact theconical head 181, a clicking sound is produced. In accordance with one aspect of the invention, this clicking sound indicates to the inhaler user that he or she is drawing properly upon the mouthpiece and operating the inhaler correctly. If desired, a vibratory mechanical reed (not shown) can be mounted in the airflow path to produce an audible signal to the user. Alternatively, an electronic flow or pressure sensor can trigger an audible or visual signal indicator to tell the user that proper airflow has been established. - This airflow-control/check-
valve system 180 serves to deliver air at a predetermined volume and velocity to downstream inhaler parts. The airflow, at this predetermined volume and velocity, acts to pick-up, fluidize, de-agglomerate and deliver entrained medicament particles to the inhaler user in a dispersed form and at a proper location to enter the user's bronchial system. - Venturi and Mixing Section
- As suggested particularly in
FIGS. 12 , 17 and 18, the airflow is then drawn through aventuri passage 201 of restricted size, thus increasing the velocity of that airflow, and into theinhaler mixing section 30. As shown inFIGS. 10-17 , this mixingsection 30 here comprises a fixedsupport 31 upon which is journaled acup 32. It will be noted that themouthpiece 40 is attached to theswivel cup 32 and can thus act as a handle for pivoting thecup member 32 and mouthpiece to the configurations shown inFIGS. 1 , 14 and elsewhere and as more fully described below. - In general, the mixing
section 30 is provided with shapes on its interior surface to encourage airflow acceleration so as to suspend medicament particles in the airflow and to de-agglomerate them. Within the cup 32 a medicament-containingcartridge 301 can be mounted. As more fully described below, thecartridge 301 is provided with air inlet and outlet holes (FIGS. 5-9 ), thecup 32 is sized and shaped so as to direct air into the cartridge through the lower inlet hole. The air then generally flows up through the cartridge in an upward direction while producing a dual counter-rotating helical motion, and out of the cartridge and down the mouthpiece as particularly suggested inFIG. 19 . As suggested inFIG. 18 , excess volume of air can flow around the outside of the cartridge but within the mixing chamber to again mate with the emerging medicament-laden air discharged from the cartridge and flowing into the mouthpiece. Thus, air flowing into the mixing chamber feeds the cartridge inlet holes, helps to extract air flowing out from the cartridge discharge holes, dilutes the medicament-laden airflow, and provides controlled, even concentrations of medicament particles into the mouthpiece airflow. The particle entrainment and dilution in the mouthpiece are provided primarily by the cartridge bypass air. - As suggested in
FIGS. 11 , 12, 15 and 16, the mixingchamber inlet port 33 provides vortex shedding which, aided by the top and bottom internal mixing chamberinternal swirl toroids semi-toroid shape 35 changes airflow direction from dispersion chamber to mouthpiece, thus aiding further de-agglomeration of the medicament particles in the entrained powder stream. To reduce powder cohesion, a modest gas expansion velocity with subsequent air shearing forces (and flow resistance) act to support a fully dispersed flow through themouthpiece 40. - Alternatively, a chamber which includes internal protrusions or spiral shapes can be provided. The interior surfaces of the mixing chamber can be shaped to provide one or more helical flows of air around and within the cartridge, if desired.
- Cartridge
- The
cartridge 301 is shown in further detail inFIGS. 3-9 . In the illustrated embodiment, thecartridge 301 comprises anupper half 302 and alower half 303, each preferably formed of transparent plastic material. To encourage medicament particle dispersion, the preferable plastic material is provided with ultra smooth surfaces, is capable of being molded into the cartridge components which have and which maintain great dimensional accuracy, does not absorb or otherwise interact with water or moisture, and has electrostatically neutral characteristics such that the medicament powder in thecartridge 301 is not retained by cartridge static charge, and does not adhere to the cartridge halves 302, 303. One such material which can be used for thelower half 303 is the Topaz brand of cyclicolephin co-polymer plastic offered by Ticonia Corporation. - The
upper cartridge half 302 defines anair inlet hole 306 and anoutlet hole 307, and the cartridge lower half defines a correspondingair inlet hole 308 and anair outlet hole 309. This upper half can be made of a clear very low water absorbent nylon. As shown particularly inFIG. 7 , and as suggested inFIG. 3 a, thehalves groove arrangement 310 retain thehalves - As suggested particularly in
FIGS. 5 , 6, 8, and 9, the inlet holes 306 and 308 formed at the lower portion of the cartridge are beveled, and the outlet holes 307, 309 are likewise beveled at an angle of substantially 60 degrees so as to encourage air ingress and egress but to discourage electrostatic adhesion and agglomerate deposition of 10 or larger micron-sized medicament particles on the plastic defining the hole edges. To enable airflow and particle pickup action, the inlet holes 306 and 308 are arranged to overlap or register with one another when the cartridge halves are twisted (as suggested by the arrow A inFIG. 4 c) into the appropriate cartridge open position, and theholes mouthpiece 40. - This
cartridge 301 is approximately one-quarter inch in diameter and its body is approximately 1 inch in axial length, and so to facilitate easy installation and extraction from theinhaler 10, a handle ormanipulator structure 314 is provided atop thecartridge 301. Here, thehandle structure 314 comprises fourweb extensions 315 which extend from the cartridge body to afinger disk 316 which may have a coined or serrated periphery. A pointer ordial indicator 317 is formed atop thedisk 316 and is further discussed below. - At the bottom of the
cartridge 301, a cartridgeinstallation check boss 319 is formed. In accordance with another aspect of the invention, this check boss can have a unique, non-circular shape of any desired form such as those shown inFIGS. 16 a, 16 b and 16 c. These unique embossments are designed to fit within a closelymating relief 39 formed in the fixedsupport 31 of the mixing section. These unique embossed shapes will be uniquely associated with particular medicaments, so that a cartridge containing an incorrect medicament cannot be installed in a particular patient's inhaler. - Cartridge Mounting Mechanism
- To properly mount the
cartridge 301 in theinhaler 10, a mounting mechanism 350 is provided as especially shown inFIGS. 1 , 2, 13-16 and 17. This mounting mechanism 350 takes the form of acap 352 formed of clear plastic, pivotally mounted so as to cover themixing section cup 32. See especiallyFIG. 16 . Apivot pin 353 interconnects thecap 352 with anextension 354 of themount 31. To facilitate reading indicia marked upon the top of thecartridge pointer 317, the top of thiscap 352 is curved so as to act as a magnifying lens. This dome shape also provides strength to the cover structure. - The cartridge can be installed and the
cap 352 secured in place when themouthpiece 40 and cartridge are pivoted into their operating positions. To this end, a radially outwardly biased lock pin 356 (FIG. 2 ) depending from thecap mount 331 pushes thecap 352 upwardly and into an open position when themouthpiece 40 andcap mount 331 are swiveled into a position so that the mouthpiece is located at approximately 90 degrees to the long or greater dimension of theinhaler body 15. In this configuration, thelock pin 356 is pushed radially outwardly and thecap 352 is rotated upwardly when thelock pin 356 is pushed into a relief defined in askirt 360 of the cover 358 (FIG. 2 ). This arrangement acts as a safety and user prompting feature. - After the cartridge is inserted into the inhaler and the cap is closed, the
mouthpiece 40 can be pivoted out of its cartridge installation and cap release position as shown inFIGS. 13-16 and into the user medication inhalation configuration shown inFIGS. 1 , 17 and 20-24. This mouthpiece pivoting motion can occur only when thecap skirt 360 is pushed down into its closed position and thelock pin 356 is radially depressed so as to permitmouthpiece 40 swiveling action. Thus, when the inhaler user moves the mouthpiece from its stored position within thehousing 15 to the cap unlocked position, the cap springs open as shown inFIGS. 13 and 15 , and thereby indicates to the inhaler user that he or she should inspect and, if necessary, replace or insert anew cartridge 301. - Mouthpiece
- As suggested above, the
mouthpiece 40 discharges particle-laden air to the oropharyngeal cavity of the user. In addition, the mouthpiece diverges the air and particle stream to slow down the particles, and then converges the particle stream to collimate and aim the particles at the rear of the user's mouth. The mouthpiece is long enough so that it extends approximately midway into most users' mouths. To encourage correct inhaler and mouthpiece usage, the inhaler mouthpiece is oriented so as to extend diagonally upwardly at approximately a 3 degree angle X as suggested inFIGS. 22 and 24 . As suggested inFIGS. 21 and 23 , the horizontally spaced walls of the mouthpiece diverge at an angle Y of approximately 5 to 8 degrees. As suggested by a comparison ofFIGS. 21 and 22 , the ratio of the height H of the mouthpiece air passage page to the width W of the air passage is approximately 3:1. If desired, a tooth and lip placement embossment 411 can be provided to depend from thedistal end 412 of themouthpiece 40. The mouthpiece is preferably made of Delrin or Celcon co-polymer acetyl plastic so as to provide proper strength, swivel bearing self-lubricity, and smooth internal and external finish. - In use, the inhaler employs a regulated flow of air to fluidize and aerosolize medicament particles and transport them to the desired rear region of the orophalangeal cavity. To accomplish this, air is first drawn into the interior of the
inhaler housing 15 and through theintake ports 172 as suggested inFIGS. 17 and 18 , to a predetermined volumetric airflow which is controlled by the flow-control/check-valve mechanism 180. The airstream then enters into the cartridge interior through the vertically elongated and alignedinlet ports 306. The air entering the cartridge interior immediately impinges upon the opposite cylindrical cartridge wall. The impacted air jet then redistributes itself into several portions. One of the portions flows downwardly into the medicament powder bed, and strips the powder from the cartridge surface and begins to fluidize it into an airborne dust cloud. Another portion of the impingement jet is directed laterally in both directions, which creates dual counter-rotating vertical spinning helical columns. The majority of the fluidized medicament powder is retained in these two columns, where the first deagglomeration action is achieved. Yet another portion of the impingement jet is directed vertically, which creates a vertical high-speed air jet along the cartridge wall into the cartridge discharge port or holes 306, 309. Particles in the helical aerosolized columns are scavenged into the jetstream and then discharged from the cartridge. This scavenging effect results in particles being metered out or discharged from the cartridge at a relatively steady particle distribution rate. Particle agglomerations are further broken down by the discharge process. Large agglomerates impinge upon the opposing mixing chamber wall, and are further reduced into smaller agglomerates. Single particles and smaller agglomerates are carried forward through the mixing chamber and into the mouthpiece discharge tube. The remaining agglomerates are pulled apart in the high-shear and shock flow field produced by the mouthpiece tangential entry port. Thus a steady flow of a individual medicament particles emerge from the mouthpiece and into the users oropharyngeal airway. These airstream flows and the sub-stream flows thus result in complete air entrainment of all medicament particles in the cartridge, and delivery of a complete, closely metered medicament dose to the patient.
Claims (20)
1. An inhaler comprising:
a mixing cavity adapted to mount a medicament-containing cartridge, wherein airflow exiting the medicament-containing cartridge during an inhalation is configured to meet a shearing flow.
2. The inhaler of claim 1 , wherein the medicament-containing cartridge includes a drug powder.
3. The inhaler of claim 1 , wherein the shearing flow is from airflow that does not flow through the medicament-containing cartridge.
4. The inhaler of claim 1 , wherein the shearing flow is from cartridge bypass airflow.
5. The inhaler of claim 1 , further comprising a mouthpiece.
6. The inhaler of claim 5 , wherein the mouthpiece includes a transport conduit with an expansion wall having a divergence angle configured to create a horizontal discharge path.
7. The inhaler of claim 6 , wherein the horizontal discharge path has a 3:1 aspect ratio.
8. The inhaler of claim 6 , wherein the divergence angle is about 3 degrees.
9. The inhaler of claim 5 , wherein the mouthpiece is configured to diverge an air stream of particles when the inhaler is in use.
10. The inhaler of claim 5 , wherein the mouthpiece is configured to converge an air stream of particles when the inhaler is in use.
11. The inhaler of claim 5 , wherein the mouthpiece is configured to converge an air stream of particles to aim the particles when the inhaler is in use.
12. The inhaler of claim 5 , wherein the mouthpiece is connected to the mixing cavity by a joint.
13. An inhaler comprising:
an air pathway configured to generate a shearing flow, wherein the shearing flow is directed to meet airflow exiting a medicament-containing cartridge during an inhalation.
14. The inhaler of claim 13 , wherein the medicament-containing cartridge includes a drug powder.
15. The inhaler of claim 13 , wherein the shearing flow is from airflow that does not flow through the medicament-containing cartridge.
16. The inhaler of claim 13 , wherein the shearing flow is from cartridge bypass airflow.
17. The inhaler of claim 13 , further comprising a mouthpiece connected to a mixing section by a joint.
18. The inhaler of claim 17 , wherein the mouthpiece is configured to diverge an air stream of particles when the inhaler is in use.
19. The inhaler of claim 17 , wherein the mouthpiece is configured to converge an air stream of particles when the inhaler is in use.
20. The inhaler of claim 13 , wherein the inhaler is a dry powder inhaler.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US14/592,790 US20150122258A1 (en) | 1999-07-23 | 2015-01-08 | Unit dose cartridge and dry powder inhaler |
Applications Claiming Priority (7)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US14546499P | 1999-07-23 | 1999-07-23 | |
US20612300P | 2000-05-22 | 2000-05-22 | |
US09/621,092 US7305986B1 (en) | 1999-07-23 | 2000-07-21 | Unit dose capsules for use in a dry powder inhaler |
US10/655,153 US7464706B2 (en) | 1999-07-23 | 2003-09-04 | Unit dose cartridge and dry powder inhaler |
US12/102,625 US8215300B2 (en) | 1999-07-23 | 2008-04-14 | Unit dose cartridge and dry powder inhaler |
US13/490,292 US8950397B2 (en) | 1999-07-23 | 2012-06-06 | Unit dose cartridge and dry powder inhaler |
US14/592,790 US20150122258A1 (en) | 1999-07-23 | 2015-01-08 | Unit dose cartridge and dry powder inhaler |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US13/490,292 Continuation US8950397B2 (en) | 1999-07-23 | 2012-06-06 | Unit dose cartridge and dry powder inhaler |
Publications (1)
Publication Number | Publication Date |
---|---|
US20150122258A1 true US20150122258A1 (en) | 2015-05-07 |
Family
ID=34273452
Family Applications (4)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/655,153 Expired - Lifetime US7464706B2 (en) | 1999-07-23 | 2003-09-04 | Unit dose cartridge and dry powder inhaler |
US12/102,625 Expired - Fee Related US8215300B2 (en) | 1999-07-23 | 2008-04-14 | Unit dose cartridge and dry powder inhaler |
US13/490,292 Expired - Fee Related US8950397B2 (en) | 1999-07-23 | 2012-06-06 | Unit dose cartridge and dry powder inhaler |
US14/592,790 Abandoned US20150122258A1 (en) | 1999-07-23 | 2015-01-08 | Unit dose cartridge and dry powder inhaler |
Family Applications Before (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/655,153 Expired - Lifetime US7464706B2 (en) | 1999-07-23 | 2003-09-04 | Unit dose cartridge and dry powder inhaler |
US12/102,625 Expired - Fee Related US8215300B2 (en) | 1999-07-23 | 2008-04-14 | Unit dose cartridge and dry powder inhaler |
US13/490,292 Expired - Fee Related US8950397B2 (en) | 1999-07-23 | 2012-06-06 | Unit dose cartridge and dry powder inhaler |
Country Status (14)
Country | Link |
---|---|
US (4) | US7464706B2 (en) |
EP (1) | EP1670532B1 (en) |
JP (2) | JP4456116B2 (en) |
KR (3) | KR20090074284A (en) |
CN (2) | CN1859938B (en) |
AU (3) | AU2004270204B2 (en) |
BR (1) | BRPI0414085A (en) |
CA (2) | CA2635665C (en) |
DK (1) | DK1670532T3 (en) |
ES (1) | ES2638279T3 (en) |
IL (1) | IL174041A (en) |
MX (1) | MXPA06002544A (en) |
NZ (2) | NZ577038A (en) |
WO (1) | WO2005023348A2 (en) |
Cited By (25)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9339615B2 (en) | 2008-06-13 | 2016-05-17 | Mannkind Corporation | Dry powder inhaler and system for drug delivery |
US9346766B2 (en) | 2004-08-20 | 2016-05-24 | Mannkind Corporation | Catalysis of diketopiperazine synthesis |
US9364436B2 (en) | 2011-06-17 | 2016-06-14 | Mannkind Corporation | High capacity diketopiperazine microparticles and methods |
US9446001B2 (en) | 2005-09-14 | 2016-09-20 | Mannkind Corporation | Increasing drug affinity for crystalline microparticle surfaces |
US9610351B2 (en) | 2011-10-24 | 2017-04-04 | Mannkind Corporation | Methods and compositions for treating pain |
US9630930B2 (en) | 2009-06-12 | 2017-04-25 | Mannkind Corporation | Diketopiperazine microparticles with defined specific surface areas |
US9655850B2 (en) | 2008-12-29 | 2017-05-23 | Mannkind Corporation | Substituted diketopiperazine analogs for use as drug delivery agents |
US9662461B2 (en) | 2008-06-13 | 2017-05-30 | Mannkind Corporation | Dry powder drug delivery system and methods |
US9675674B2 (en) | 2004-08-23 | 2017-06-13 | Mannkind Corporation | Diketopiperazine salts for drug delivery and related methods |
US9700690B2 (en) | 2002-03-20 | 2017-07-11 | Mannkind Corporation | Inhalation apparatus |
US9706944B2 (en) | 2009-11-03 | 2017-07-18 | Mannkind Corporation | Apparatus and method for simulating inhalation efforts |
US9801925B2 (en) | 1999-06-29 | 2017-10-31 | Mannkind Corporation | Potentiation of glucose elimination |
US9802012B2 (en) | 2012-07-12 | 2017-10-31 | Mannkind Corporation | Dry powder drug delivery system and methods |
US9925144B2 (en) | 2013-07-18 | 2018-03-27 | Mannkind Corporation | Heat-stable dry powder pharmaceutical compositions and methods |
US9943571B2 (en) | 2008-08-11 | 2018-04-17 | Mannkind Corporation | Use of ultrarapid acting insulin |
US9983108B2 (en) | 2009-03-11 | 2018-05-29 | Mannkind Corporation | Apparatus, system and method for measuring resistance of an inhaler |
US10130581B2 (en) | 2006-02-22 | 2018-11-20 | Mannkind Corporation | Method for improving the pharmaceutic properties of microparticles comprising diketopiperazine and an active agent |
US10159644B2 (en) | 2012-10-26 | 2018-12-25 | Mannkind Corporation | Inhalable vaccine compositions and methods |
US10307464B2 (en) | 2014-03-28 | 2019-06-04 | Mannkind Corporation | Use of ultrarapid acting insulin |
US10342938B2 (en) | 2008-06-13 | 2019-07-09 | Mannkind Corporation | Dry powder drug delivery system |
US10421729B2 (en) | 2013-03-15 | 2019-09-24 | Mannkind Corporation | Microcrystalline diketopiperazine compositions and methods |
US10561806B2 (en) | 2014-10-02 | 2020-02-18 | Mannkind Corporation | Mouthpiece cover for an inhaler |
US10625034B2 (en) | 2011-04-01 | 2020-04-21 | Mannkind Corporation | Blister package for pharmaceutical cartridges |
US10675421B2 (en) | 2008-06-20 | 2020-06-09 | Mannkind Corporation | Interactive apparatus and method for real-time profiling of inhalation efforts |
US11446127B2 (en) | 2013-08-05 | 2022-09-20 | Mannkind Corporation | Insufflation apparatus and methods |
Families Citing this family (113)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6428771B1 (en) * | 1995-05-15 | 2002-08-06 | Pharmaceutical Discovery Corporation | Method for drug delivery to the pulmonary system |
PT1808438E (en) * | 1999-06-29 | 2015-01-14 | Mannkind Corp | Purification and stabilization of peptide and proteins in pharmaceutical agents |
US7464706B2 (en) | 1999-07-23 | 2008-12-16 | Mannkind Corporation | Unit dose cartridge and dry powder inhaler |
US7305986B1 (en) | 1999-07-23 | 2007-12-11 | Mannkind Corporation | Unit dose capsules for use in a dry powder inhaler |
GB0025749D0 (en) * | 2000-10-20 | 2000-12-06 | Glaxo Group Ltd | Inhaler |
US6994083B2 (en) | 2001-12-21 | 2006-02-07 | Trudell Medical International | Nebulizer apparatus and method |
US20080260838A1 (en) * | 2003-08-01 | 2008-10-23 | Mannkind Corporation | Glucagon-like peptide 1 (glp-1) pharmaceutical formulations |
US8377869B2 (en) | 2007-10-24 | 2013-02-19 | Mannkind Corporation | Method of preventing adverse effects by GLP-1 |
US9078866B2 (en) | 2003-08-01 | 2015-07-14 | Mannkind Corporation | Method for treating hyperglycemia with GLP-1 |
DE10345950A1 (en) * | 2003-10-02 | 2005-05-19 | Pari GmbH Spezialisten für effektive Inhalation | Inhalation therapy device with valve |
US20070027063A1 (en) * | 2004-01-12 | 2007-02-01 | Mannkind Corporation | Method of preserving the function of insulin-producing cells |
KR100985126B1 (en) * | 2004-01-12 | 2010-10-05 | 맨카인드 코포레이션 | A method of reducing serum proinsulin levels in type 2 diabetics |
JP4618545B2 (en) * | 2004-02-19 | 2011-01-26 | 昭彦 宮本 | Fine powdered therapeutic drug inhaler aid with lead |
US20080085298A1 (en) * | 2004-03-12 | 2008-04-10 | Biodel, Inc. | Rapid Mucosal Gel or Film Insulin Compositions |
US20080248999A1 (en) * | 2007-04-04 | 2008-10-09 | Biodel Inc. | Amylin formulations |
US20080090753A1 (en) | 2004-03-12 | 2008-04-17 | Biodel, Inc. | Rapid Acting Injectable Insulin Compositions |
US20080096800A1 (en) * | 2004-03-12 | 2008-04-24 | Biodel, Inc. | Rapid mucosal gel or film insulin compositions |
US20050263153A1 (en) * | 2004-05-28 | 2005-12-01 | Quadrant Technologies Limited | Unit dose dry powder inhaler |
US20080206342A1 (en) * | 2005-01-10 | 2008-08-28 | Rosemary Kovelesky | Compositions and Methods For Increasing the Bioavailability of Pulmonarily Administered Insulin |
CN100431634C (en) * | 2005-04-04 | 2008-11-12 | 陈庆堂 | Dry powder aerosolizing inhalator |
WO2007002393A2 (en) * | 2005-06-23 | 2007-01-04 | Patricia Bohman | Spirometer toy |
US20090159062A1 (en) * | 2005-06-23 | 2009-06-25 | Patricia Bohman | Spirometer Toy |
WO2007007110A1 (en) * | 2005-07-13 | 2007-01-18 | Cipla Limited | Inhaler device |
US8763605B2 (en) | 2005-07-20 | 2014-07-01 | Manta Devices, Llc | Inhalation device |
US7713929B2 (en) * | 2006-04-12 | 2010-05-11 | Biodel Inc. | Rapid acting and long acting insulin combination formulations |
US8084420B2 (en) * | 2005-09-29 | 2011-12-27 | Biodel Inc. | Rapid acting and long acting insulin combination formulations |
WO2007041481A1 (en) * | 2005-09-29 | 2007-04-12 | Biodel, Inc. | Rapid acting and prolonged acting insulin preparations |
DE602006013865D1 (en) | 2005-11-21 | 2010-06-02 | Mannkind Corp | Apparatus and method for powder dispensing and measurement |
EP1986722B1 (en) | 2006-01-31 | 2018-10-24 | Oriel Therapeutics, Inc. | Dry powder inhalers having spiral travel paths for microcartridges with dry powder |
MX2008013165A (en) * | 2006-04-12 | 2009-01-29 | Biodel Inc | Rapid acting and long acting insulin combination formulations. |
EP1844806A1 (en) * | 2006-04-13 | 2007-10-17 | Boehringer Ingelheim Pharma GmbH | Device for delivery of medicaments, magazine for medicaments, and method for withdrawing medicaments from a medicament chamber |
GB0623732D0 (en) * | 2006-11-28 | 2007-01-10 | Optinose As | Powder delivery devices |
US11224704B2 (en) * | 2007-07-06 | 2022-01-18 | Manta Devices, Llc | Dose delivery device for inhalation |
EP2898914B1 (en) * | 2007-07-06 | 2018-06-20 | Manta Devices, LLC | Inhalation devices for storing and delivering medicament |
GB0719299D0 (en) | 2007-10-03 | 2007-11-14 | Optinose As | Nasal delivery devices |
US8785396B2 (en) | 2007-10-24 | 2014-07-22 | Mannkind Corporation | Method and composition for treating migraines |
CN101969928B (en) * | 2007-10-24 | 2014-05-07 | 曼金德公司 | Delivery of active agents |
CA2709071C (en) | 2007-12-14 | 2016-11-15 | Labogroup S.A.S. | Delivering aerosolizable food products |
GB0802028D0 (en) * | 2008-02-05 | 2008-03-12 | Dunne Stephen T | Powder inhaler flow regulator |
BRPI0910875B8 (en) * | 2008-03-27 | 2021-06-22 | Mannkind Corp | dry powder inhalation system |
AU2015201158B2 (en) * | 2008-03-27 | 2017-04-13 | Mannkind Corporation | A dry powder inhalation system |
JP5553520B2 (en) * | 2008-03-31 | 2014-07-16 | キヤノン株式会社 | Inhaler |
US20190262557A1 (en) * | 2010-03-04 | 2019-08-29 | Mannkind Corporation | Dry powder drug delivery system |
AU2014200952B2 (en) * | 2008-06-13 | 2014-12-11 | Mannkind Corporation | A dry powder inhaler and system for drug delivery |
AU2015275293B2 (en) * | 2008-06-13 | 2018-06-07 | Mannkind Corporation | A dry powder inhaler and system for drug delivery |
JP5339797B2 (en) * | 2008-07-08 | 2013-11-13 | キヤノン株式会社 | Inhaler |
MX2011001421A (en) | 2008-08-05 | 2011-04-04 | Mannkind Corp | Improved powder dispenser modules and powder dispenser assemblies. |
EP2345893B1 (en) | 2008-11-04 | 2016-05-04 | Panasonic Healthcare Holdings Co., Ltd. | Measurement device, measurement method, and program |
JP5513519B2 (en) * | 2008-12-23 | 2014-06-04 | コーニンクレッカ フィリップス エヌ ヴェ | Method for aerosol drug delivery and device comprising a mouthpiece having a step structure |
PT2379511E (en) | 2008-12-29 | 2015-02-27 | Mannkind Corp | Substituted diketopiperazine analogs for use as drug delivery agents |
WO2010083042A1 (en) | 2009-01-15 | 2010-07-22 | Manta Devices, Llc | Delivery device |
US9060927B2 (en) | 2009-03-03 | 2015-06-23 | Biodel Inc. | Insulin formulations for rapid uptake |
CN102438602B (en) * | 2009-03-04 | 2016-04-13 | 曼金德公司 | The dried powder delivery system improved |
CA2755514C (en) | 2009-03-18 | 2018-03-13 | Mannkind Corporation | Inhaler adaptor for a laser diffraction apparatus and method for measuring particle size distribution |
JP5548769B2 (en) * | 2009-05-11 | 2014-07-16 | コーニンクレッカ フィリップス エヌ ヴェ | Aerosol chemical supply device and kit including aerosol chemical supply device |
GB0910537D0 (en) * | 2009-06-18 | 2009-07-29 | Ivax Pharmaceuticals Ireland | Inhaler |
EP2440186B1 (en) | 2009-06-12 | 2019-08-07 | MannKind Corporation | Diketopiperazine microparticles with defined isomer contents |
US9345848B2 (en) | 2009-10-20 | 2016-05-24 | Sima Patent Ve Lisanslama Hizmetleri Ltd. Sti. | Dry powder inhaler |
GB0919465D0 (en) * | 2009-11-06 | 2009-12-23 | Norton Healthcare Ltd | Airflow adaptor for a breath-actuated dry powder inhaler |
EP2506905B1 (en) * | 2009-12-04 | 2017-07-05 | Koninklijke Philips N.V. | Apparatus comprising adjustable stepped mouthpiece for aerosol drug delivery |
WO2011116293A2 (en) | 2010-03-19 | 2011-09-22 | Manta Devices, Llc | Delivery device and related methods |
CN107854454A (en) | 2010-11-09 | 2018-03-30 | 曼金德公司 | For treating the composition comprising serotonin receptor agonist and diketopiperazine of antimigraine |
JP5897026B2 (en) * | 2010-11-29 | 2016-03-30 | サノフィ−アベンティス・ドイチュラント・ゲゼルシャフト・ミット・ベシュレンクテル・ハフツング | Medicinal module for inhaler |
USD742503S1 (en) * | 2011-01-12 | 2015-11-03 | Vectura Gmbh | Mobile inhaler device |
DE202011101012U1 (en) * | 2011-05-20 | 2012-05-21 | Hans Haindl | inhaler |
US11103659B2 (en) | 2011-07-06 | 2021-08-31 | Manta Devices, Llc | Delivery device and related methods |
US9849255B2 (en) * | 2011-11-25 | 2017-12-26 | Mahmut Bilgic | Inhalation device |
DK2790758T3 (en) | 2011-12-16 | 2017-11-20 | Indosys Ltd | Cartridge for a drug dose and delivery device |
US9603907B2 (en) | 2012-02-01 | 2017-03-28 | Protalix Ltd. | Dry powder formulations of dNase I |
US9649454B2 (en) | 2012-05-03 | 2017-05-16 | Manta Devices, Llc | Delivery device and related methods |
EP2858701A2 (en) * | 2012-06-06 | 2015-04-15 | AeroDesigns, Inc | Aerosol dispenser with replaceable cartridge |
US20150367366A1 (en) * | 2012-12-06 | 2015-12-24 | Aerodesigns, Inc. | Aerosol dispenser with edible cartridge |
WO2014150826A1 (en) * | 2013-03-15 | 2014-09-25 | Aerodesigns, Inc. | Aerosol dispenser with edible cartridge |
CN103285485B (en) * | 2013-06-25 | 2015-07-15 | 夏云 | Drug feeding device |
EP3110484A4 (en) | 2014-02-21 | 2018-02-14 | Respira Therapeutics, Inc. | Powder inhaler, system and methods |
USD773034S1 (en) * | 2014-02-25 | 2016-11-29 | PHARI Pharma GmbH, Inc. | Inhalation device head |
USD773033S1 (en) * | 2014-02-25 | 2016-11-29 | Pari Pharma Gmbh, Inc. | Inhalation device |
US11147936B2 (en) | 2014-05-02 | 2021-10-19 | Manta Devices, Llc | Dose delivery device with cover connected to dose chamber seal |
CN104223362B (en) * | 2014-08-20 | 2017-02-01 | 深圳麦克韦尔股份有限公司 | Inhalator |
CN104223363B (en) * | 2014-08-20 | 2017-02-15 | 深圳麦克韦尔股份有限公司 | Inhalator |
WO2016057693A1 (en) | 2014-10-10 | 2016-04-14 | Alnylam Pharmaceuticals, Inc. | Methods and compositions for inhalation delivery of conjugated oligonucleotide |
CA2972826C (en) * | 2015-01-14 | 2023-09-12 | Respira Therapeutics, Inc. | Powder dispersion methods and devices |
BR112017022201A2 (en) | 2015-04-15 | 2018-07-03 | Sansa Corporation (Barbados) Inc. | device for adding an aroma component or cough suppressant to an inhaler, dry powder inhaler, and method for inhaling dry powder |
AU2016247911B2 (en) * | 2015-04-15 | 2020-06-11 | Philip Morris Products S.A. | Dual resistance dry powder inhaler |
AU2016261113A1 (en) * | 2015-05-12 | 2018-01-04 | Cipla Europe Nv | Inhaler device |
SE539111C2 (en) * | 2015-06-03 | 2017-04-11 | Iconovo Ab | Single dose dry powder inhaler |
US9877520B2 (en) * | 2015-07-29 | 2018-01-30 | Nitesh Rastogi | Hinged vaping system |
RU2610779C1 (en) * | 2015-09-28 | 2017-02-15 | Евгений Константинович Агантаев | Single dose dry powder inhaler |
USD824015S1 (en) * | 2016-01-29 | 2018-07-24 | Mannkind Corporation | Inhaler |
USD824510S1 (en) * | 2016-01-29 | 2018-07-31 | Mannkind Corporation | Inhaler |
USD841798S1 (en) * | 2016-01-29 | 2019-02-26 | Mannkind Corporation | Inhaler |
USD824016S1 (en) * | 2016-01-29 | 2018-07-24 | Mannkind Corporation | Inhaler |
IL311489A (en) | 2016-01-29 | 2024-05-01 | Mannkind Corp | Dry powder inhaler |
CN109475711B (en) | 2016-05-19 | 2022-04-15 | 曼金德公司 | Device, system and method for detecting and monitoring inhalation |
WO2018097758A1 (en) * | 2016-11-25 | 2018-05-31 | Айна Владимировна ИСАКОВА | Multi-cartridge multi-dose inhalator |
RU168963U1 (en) * | 2016-11-25 | 2017-02-28 | Максим Александрович Котс | MULTI-CARTRIDGE MULTI-DOSE INHALATOR |
USD834178S1 (en) * | 2017-05-19 | 2018-11-20 | Mannkind Corporation | Inhaler |
UA126152C2 (en) | 2017-05-31 | 2022-08-25 | Філіп Морріс Продактс С.А. | Inhaler article with occluded airflow element |
US11864587B2 (en) * | 2018-06-15 | 2024-01-09 | Valley Product Concepts, LLC | Capsules for use in personal vaporizers |
WO2020072449A1 (en) * | 2018-10-02 | 2020-04-09 | Boston Scientific Scimed, Inc. | Devices for fluidization and delivering a powdered agent |
CN113164722B (en) * | 2018-10-02 | 2023-04-11 | 波士顿科学国际有限公司 | Device for fluidizing and transporting powder agent |
KR20210088599A (en) * | 2018-10-28 | 2021-07-14 | 사이키 메디컬 엘티디. | cartridge unit coupler |
USD898187S1 (en) * | 2019-05-21 | 2020-10-06 | Receptor Holdings, Inc. | Inhaler device |
US10729860B1 (en) * | 2019-05-22 | 2020-08-04 | Berkshire Biomedical, LLC | Computerized oral prescription administration for securely dispensing a medication and associated systems and methods |
CN112274737B (en) * | 2019-07-12 | 2023-05-05 | 深圳市卓力能技术有限公司 | Medical nasal inhalation device |
US20210085896A1 (en) * | 2019-07-24 | 2021-03-25 | Spencer Boatman | Mouthpiece for use with nebulizer and similar devices |
US11090668B2 (en) * | 2020-01-09 | 2021-08-17 | L'oreal | Selective sealing cartridge |
GB202012180D0 (en) * | 2020-08-05 | 2020-09-16 | Nicoventures Trading Ltd | Aerosol provision device |
IL305510A (en) | 2021-03-03 | 2023-10-01 | United Therapeutics Corp | A dry powder composition of treprostinil and its prodrug thereof and further comprising (e)-3,6-bis[4-(n-carbonyl-2-propenyl)amidobutyl]-2,5-diketopiperazine (fdkp) |
EP4387694A1 (en) * | 2021-08-17 | 2024-06-26 | SHL Medical AG | Medicament delivery device |
AU2023219692A1 (en) | 2022-02-08 | 2024-08-01 | United Therapeutics Corporation | Treprostinil iloprost combination therapy |
CN115089825A (en) * | 2022-07-06 | 2022-09-23 | 苏州易合医药有限公司 | Lung drug delivery device |
WO2024059819A2 (en) | 2022-09-15 | 2024-03-21 | Tff Pharmaceuticals, Inc. | Compositions of cannabinoids for delivery by inhalation |
Family Cites Families (138)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2549303A (en) * | 1949-04-20 | 1951-04-17 | Bristol Lab Inc | Inhaler for crystalline pencilllin or the like |
BE509861A (en) | 1952-03-13 | |||
US3337740A (en) | 1962-02-13 | 1967-08-22 | Deering Milliken Res Corp | Process for separating acrylic acid from impurities |
US3669113A (en) | 1966-03-07 | 1972-06-13 | Fisons Ltd | Inhalation device |
US3518340A (en) | 1968-04-15 | 1970-06-30 | Dow Corning | Method of forming silicone rubber drug carriers |
US3622053A (en) | 1969-12-10 | 1971-11-23 | Schering Corp | Aerosol inhaler with flip-up nozzle |
BE794951A (en) * | 1972-02-03 | 1973-05-29 | Parke Davis & Co | WATER SOLUBLE PACKAGING |
US3823843A (en) * | 1972-10-26 | 1974-07-16 | Lilly Co Eli | Locking capsule |
US3856142A (en) | 1973-01-24 | 1974-12-24 | Mine Safety Appliances Co | Inhalant package |
FR2224175B1 (en) * | 1973-04-04 | 1978-04-14 | Isf Spa | |
GB1479283A (en) * | 1973-07-23 | 1977-07-13 | Bespak Industries Ltd | Inhaler for powdered medicament |
DE2502251A1 (en) * | 1975-01-17 | 1976-07-22 | Schering Ag | DEVICE FOR INHALATION OF POWDERED SOLIDS |
US4040536A (en) * | 1975-05-05 | 1977-08-09 | R. P. Scherer Corporation | Locking hard gelatin capsule |
US3998226A (en) * | 1975-09-22 | 1976-12-21 | Edward G. Gomez | Inhalation device for encapsulated concentrates |
GB1598081A (en) | 1977-02-10 | 1981-09-16 | Allen & Hanburys Ltd | Inhaler device for dispensing medicaments |
IE46865B1 (en) | 1977-04-29 | 1983-10-19 | Allen & Hanburys Ltd | Device for dispensing medicaments |
US4148308A (en) * | 1977-05-31 | 1979-04-10 | Sayer William J | Mouthpiece with a tongue retractor |
US4268460A (en) * | 1977-12-12 | 1981-05-19 | Warner-Lambert Company | Nebulizer |
CA1113044A (en) * | 1977-12-16 | 1981-11-24 | J. Paul Leblond | Personal repellant device |
DE2849493C2 (en) | 1978-11-15 | 1982-01-14 | Carl Heyer Gmbh, Inhalationstechnik, 5427 Bad Ems | Hand-held aerosol dispenser |
US4407525A (en) * | 1979-10-04 | 1983-10-04 | Gao Gesellschaft Fur Automation Und Organisation Mbh | Identification card with hallmark for authentication by incident and transmitted light |
GB2072536B (en) | 1980-03-25 | 1983-12-07 | Malem H | Nebuliser |
DE3167658D1 (en) | 1980-12-12 | 1985-01-17 | Combi Co | Inhaler |
SE438261B (en) * | 1981-07-08 | 1985-04-15 | Draco Ab | USE IN A DOSHALATOR OF A PERFORED MEMBRANE |
EP0069715B1 (en) * | 1981-07-08 | 1986-11-05 | Aktiebolaget Draco | Powder inhalator |
US4487327A (en) * | 1982-12-21 | 1984-12-11 | Grayson Robert E | Locking capsule |
GB8325529D0 (en) | 1983-09-23 | 1983-10-26 | Lilly Industries Ltd | Medicinal forms |
CH661878A5 (en) | 1983-11-04 | 1987-08-31 | Warner Lambert Co | CAPSULE DOSING FORMS. |
IE58468B1 (en) | 1984-10-25 | 1993-09-22 | Warner Lambert Co | Method for sealing capsules and capsule |
US4592348A (en) * | 1984-12-17 | 1986-06-03 | Waters Iv William C | Aerosol inhaler |
AT384552B (en) * | 1985-08-01 | 1987-12-10 | Hurka Wilhelm | INHALATION DEVICE FOR DOSING AND DISTRIBUTING SOLID BODIES INTO THE BREATHING AIR |
SE453566B (en) * | 1986-03-07 | 1988-02-15 | Draco Ab | POWDER INHALATOR DEVICE |
US4926852B1 (en) * | 1986-06-23 | 1995-05-23 | Univ Johns Hopkins | Medication delivery system phase one |
DE3639836A1 (en) | 1986-11-21 | 1988-06-01 | Sigrid Bechter | Mouthpiece for an inhaler |
KR890003520Y1 (en) * | 1986-12-20 | 1989-05-27 | 주식회사 서흥캅셀 | Medicinal capsule |
DE3727894A1 (en) | 1987-08-21 | 1989-03-02 | Stephan Dieter | CAPSULE FOR PHARMACEUTICAL ACTIVE INGREDIENTS OF A DRUG |
ATE104867T1 (en) * | 1988-10-04 | 1994-05-15 | Univ Johns Hopkins | INHALATION DEVICE FOR AEROSOLS. |
IT1228459B (en) | 1989-02-23 | 1991-06-19 | Phidea S R L | INHALER WITH REGULAR AND COMPLETE EMPTYING OF THE CAPSULE. |
IT1228460B (en) * | 1989-02-23 | 1991-06-19 | Phidea S R L | DISPOSABLE INHALER WITH PRE-PERFORATED CAPSULE |
US5067500A (en) * | 1989-04-24 | 1991-11-26 | Philip Morris Incorporated | Container for additive materials for smoking articles |
US4991605A (en) * | 1989-04-24 | 1991-02-12 | Philip Morris Incorporated | Container for additive materials for smoking articles |
EP0705614B1 (en) * | 1989-04-28 | 2002-09-25 | Riker Laboratories, Inc. | Dry powder inhalation device |
DK544589D0 (en) * | 1989-11-01 | 1989-11-01 | Novo Nordisk As | MANUALLY OPERATED DEVICE FOR DISPENSING A PRESCRIBED QUANTITY OF A POWDER-SHAPED SUBSTANCE |
US5328464A (en) * | 1990-04-24 | 1994-07-12 | Science Incorporated | Closed drug delivery system |
IL98441A (en) * | 1990-06-14 | 1995-12-31 | Rhone Poulenc Rorer Ltd | Powder inhalers |
EP0503031B1 (en) | 1990-09-26 | 1998-04-01 | Pharmachemie B.V. | Inhaler devices provided with a reservoir for several doses of medium for inhaling, transporting device, whirl chamber |
US5170801A (en) * | 1990-10-02 | 1992-12-15 | Glaxo Inc. | Medical capsule device actuated by radio-frequency (rf) signal |
FR2667509B1 (en) | 1990-10-04 | 1995-08-25 | Valois | POWDER INHALER, DEVICE FOR PACKAGING POWDER MICRODOSES IN THE FORM OF BANDS SUITABLE FOR USE IN A POWDER INHALER, AND METHOD FOR MANUFACTURING SUCH BANDS. |
GB9024760D0 (en) | 1990-11-14 | 1991-01-02 | Riker Laboratories Inc | Inhalation device and medicament carrier |
GB9027234D0 (en) | 1990-12-15 | 1991-02-06 | Harris Pharma Ltd | An inhalation device |
DE69127826T2 (en) | 1990-12-17 | 1998-04-09 | Minnesota Mining & Mfg | INHALATION DEVICE |
GB2253200A (en) | 1991-02-01 | 1992-09-02 | Harris Pharma Ltd | Inhalation apparatus and fracturable capsule for use therewith |
AU6130394A (en) | 1991-03-05 | 1994-08-15 | Miris Medical Corporation | Apparatus for providing a timed release of an amount of aerosol medication |
US5404871A (en) * | 1991-03-05 | 1995-04-11 | Aradigm | Delivery of aerosol medications for inspiration |
US5797391A (en) | 1991-03-28 | 1998-08-25 | Rhone-Poulenc Rorer Limited | Inhaler |
US5327883A (en) * | 1991-05-20 | 1994-07-12 | Dura Pharmaceuticals, Inc. | Apparatus for aerosolizing powdered medicine and process and using |
US5492112A (en) * | 1991-05-20 | 1996-02-20 | Dura Pharmaceuticals, Inc. | Dry powder inhaler |
US6055980A (en) * | 1991-05-20 | 2000-05-02 | Dura Pharmaceuticals, Inc. | Dry powder inhaler |
FR2676929B1 (en) * | 1991-05-30 | 1994-02-11 | Aerosols Bouchage Ste Fse | POWDER INHALER. |
US6681767B1 (en) * | 1991-07-02 | 2004-01-27 | Nektar Therapeutics | Method and device for delivering aerosolized medicaments |
ATE189124T1 (en) * | 1991-07-02 | 2000-02-15 | Inhale Inc | METHOD AND DEVICE FOR DELIVERING MEDICATIONS IN AEROSOL FORM |
US5337740A (en) | 1991-08-01 | 1994-08-16 | New England Pharmaceuticals, Inc. | Inhalation devices |
DE4211475A1 (en) | 1991-12-14 | 1993-06-17 | Asta Medica Ag | POWDER INHALATOR |
GB2262452B (en) | 1991-12-19 | 1995-12-20 | Minnesota Mining & Mfg | Inhalation device |
US5476093A (en) | 1992-02-14 | 1995-12-19 | Huhtamaki Oy | Device for more effective pulverization of a powdered inhalation medicament |
US5785049A (en) | 1994-09-21 | 1998-07-28 | Inhale Therapeutic Systems | Method and apparatus for dispersion of dry powder medicaments |
GB9216038D0 (en) | 1992-07-28 | 1992-09-09 | Bespak Plc | Dispensing apparatus for powdered medicaments |
GB2270293A (en) * | 1992-09-05 | 1994-03-09 | Medix Ltd | Drug dispensing system |
EP0665759B1 (en) * | 1992-10-19 | 1998-12-23 | Dura Pharmaceuticals, Inc. | Dry powder inhaler |
MY115140A (en) | 1992-12-18 | 2003-04-30 | Schering Corp | Inhaler for powdered medications |
US5896855A (en) | 1992-12-24 | 1999-04-27 | Rhone-Poulenc Rorer Limited | Multi dose inhaler apparatus |
FR2700279B1 (en) | 1993-01-14 | 1995-03-17 | Valois | Portable device for projecting doses of a fluid substance using a stream of compressed air. |
US5888477A (en) * | 1993-01-29 | 1999-03-30 | Aradigm Corporation | Use of monomeric insulin as a means for improving the bioavailability of inhaled insulin |
IL108780A (en) | 1993-02-27 | 1999-06-20 | Fisons Plc | Inhalation device |
EP0714314B1 (en) | 1993-08-18 | 1998-10-14 | FISONS plc | Inhalator with breath flow regulation |
US5524613A (en) | 1993-08-25 | 1996-06-11 | Habley Medical Technology Corporation | Controlled multi-pharmaceutical inhaler |
PT101450B (en) | 1994-02-02 | 1999-11-30 | Hovione Produtos Farmaceuticos | NEW INHALATION DEVICE |
US5505194A (en) * | 1994-03-23 | 1996-04-09 | Abbott Laboratories | Aerosol inhalation device having slideably and rotatably connected elliptical cylinder portions |
US5483954A (en) * | 1994-06-10 | 1996-01-16 | Mecikalski; Mark B. | Inhaler and medicated package |
CN1318104C (en) * | 1994-09-21 | 2007-05-30 | 耐科塔医药公司 | Method for spraying dried powder medicine and its equipment |
FR2725626A1 (en) * | 1994-10-18 | 1996-04-19 | Sofab | DEVICE FOR INHALING POWDERED PRODUCTS |
SE9404439D0 (en) | 1994-12-21 | 1994-12-21 | Astra Ab | Inhalation device |
DK0805696T3 (en) | 1995-01-23 | 2000-06-05 | Direct Haler A S | inhaler |
US5901703A (en) | 1995-02-06 | 1999-05-11 | Unisia Jecs Corporation | Medicine administering device for nasal cavities |
US5645051A (en) * | 1995-04-21 | 1997-07-08 | Dura Pharmaceuticals, Inc. | Unit dose dry powder inhaler |
US5921237A (en) * | 1995-04-24 | 1999-07-13 | Dura Pharmaceuticals, Inc. | Dry powder inhaler |
US5622166A (en) * | 1995-04-24 | 1997-04-22 | Dura Pharmaceuticals, Inc. | Dry powder inhaler delivery system |
DE19519840A1 (en) | 1995-05-31 | 1996-12-05 | Kaewert Klaus | Gelatin capsule as packaging for medication and toiletries |
US5714007A (en) | 1995-06-06 | 1998-02-03 | David Sarnoff Research Center, Inc. | Apparatus for electrostatically depositing a medicament powder upon predefined regions of a substrate |
GB9513218D0 (en) | 1995-06-29 | 1995-09-06 | Fisons Plc | Inhalation device and method |
DE19523516C1 (en) * | 1995-06-30 | 1996-10-31 | Asta Medica Ag | Inhaler for administering medication from blister packs |
US5758638A (en) | 1995-07-24 | 1998-06-02 | Kreamer; Jeffry W. | Indicator for a medicament inhaler |
US6209538B1 (en) * | 1995-08-02 | 2001-04-03 | Robert A. Casper | Dry powder medicament inhalator having an inhalation-activated flow diverting means for triggering delivery of medicament |
US5746197A (en) * | 1995-08-18 | 1998-05-05 | Williams; Jeffery W. | Extension for metered dose inhaler |
KR0124764Y1 (en) | 1995-09-23 | 1998-09-15 | 양주환 | Medical capsule |
US6470884B2 (en) * | 1996-01-29 | 2002-10-29 | Aventis Pharma Limited | Capsule opening arrangement for use in a powder inhaler |
US5699789A (en) | 1996-03-11 | 1997-12-23 | Hendricks; Mark R. | Dry powder inhaler |
JP3328132B2 (en) | 1996-03-21 | 2002-09-24 | 株式会社ユニシアジェックス | Inhaler type dispenser |
WO1997040819A1 (en) * | 1996-04-29 | 1997-11-06 | Dura Pharmaceuticals, Inc. | Methods of dry powder inhalation |
US5883893A (en) * | 1996-09-10 | 1999-03-16 | Cisco Technology, Inc. | ATM voice transport protocol |
DE19647947A1 (en) | 1996-11-20 | 1998-05-28 | Pfeiffer Erich Gmbh & Co Kg | Discharge device for media |
GB9626233D0 (en) * | 1996-12-18 | 1997-02-05 | Chawla Brinda P S | Medicament packaging and deliveery device |
GB9626263D0 (en) * | 1996-12-18 | 1997-02-05 | Innovata Biomed Ltd | Powder inhaler |
EP0898978B1 (en) | 1997-01-30 | 2005-03-02 | Unisia Jecs Corporation | Suction type medicator |
JP3011898B2 (en) | 1997-02-20 | 2000-02-21 | フォルテ グロウ メディカル株式会社 | Aspirator |
SE9700935D0 (en) | 1997-03-14 | 1997-03-14 | Astra Ab | Inhalation device |
US6006747A (en) * | 1997-03-20 | 1999-12-28 | Dura Pharmaceuticals, Inc. | Dry powder inhaler |
US5904139A (en) | 1997-03-28 | 1999-05-18 | Hauser; Stephen G. | Breath coordinated inhaler |
CA2212430A1 (en) * | 1997-08-07 | 1999-02-07 | George Volgyesi | Inhalation device |
US6394085B1 (en) * | 1997-09-25 | 2002-05-28 | Norton Healthcare Ltd. | Inhaler spacer |
US6073629A (en) * | 1997-09-25 | 2000-06-13 | Norton Healthcare Ltd. | Inhaler spacer |
US6116238A (en) | 1997-12-02 | 2000-09-12 | Dura Pharmaceuticals, Inc. | Dry powder inhaler |
JP3530004B2 (en) * | 1998-02-06 | 2004-05-24 | 株式会社日立ユニシアオートモティブ | Inhalation type dispenser |
US6158431A (en) * | 1998-02-13 | 2000-12-12 | Tsi Incorporated | Portable systems and methods for delivery of therapeutic material to the pulmonary system |
US6113238A (en) * | 1998-02-17 | 2000-09-05 | Younger Mfg. Company | Glare demonstrator |
US6655379B2 (en) * | 1998-03-16 | 2003-12-02 | Nektar Therapeutics | Aerosolized active agent delivery |
US6578571B1 (en) * | 1998-04-20 | 2003-06-17 | Infamed Ltd. | Drug delivery device and methods therefor |
US6257233B1 (en) * | 1998-06-04 | 2001-07-10 | Inhale Therapeutic Systems | Dry powder dispersing apparatus and methods for their use |
AU755989B2 (en) * | 1999-05-20 | 2003-01-02 | Kos Life Sciences, Inc. | Low spray force, low retention atomization system |
US6644315B2 (en) | 1999-06-18 | 2003-11-11 | Saeed Ziaee | Nasal mask |
US9006175B2 (en) | 1999-06-29 | 2015-04-14 | Mannkind Corporation | Potentiation of glucose elimination |
US6606992B1 (en) * | 1999-06-30 | 2003-08-19 | Nektar Therapeutics | Systems and methods for aerosolizing pharmaceutical formulations |
US7305986B1 (en) | 1999-07-23 | 2007-12-11 | Mannkind Corporation | Unit dose capsules for use in a dry powder inhaler |
US7464706B2 (en) | 1999-07-23 | 2008-12-16 | Mannkind Corporation | Unit dose cartridge and dry powder inhaler |
DE60038511T2 (en) | 1999-07-23 | 2009-04-30 | Mannkind Corp., Valencia | Single serving capsules for a dry powder inhaler |
IT1308581B1 (en) | 1999-12-03 | 2002-01-08 | Medel Italiana Srl | APPARATUS FOR SPRAYING A LIQUID, IN PARTICULAR FOR MEDICAL USE. |
US6427688B1 (en) * | 2000-02-01 | 2002-08-06 | Dura Pharmaceuticals, Icn. | Dry powder inhaler |
US6443151B1 (en) * | 2000-03-08 | 2002-09-03 | Aradigm Corporation | Fluid velocity-sensitive trigger mechanism |
AR028746A1 (en) * | 2000-06-23 | 2003-05-21 | Norton Health Care Ltd | DOSE CARTRIDGE PREVIOUSLY MEASURES FOR DRY POWDER INHALER OPERATED BY BREATHING, INHALER AND A METHOD OF PROVISION OF DOSE PREVIOUSLY DRY POWDER MEASURES |
US6363932B1 (en) * | 2000-07-06 | 2002-04-02 | Clinical Technologies, Inc. | Aerosol enhancement device |
US6644309B2 (en) * | 2001-01-12 | 2003-11-11 | Becton, Dickinson And Company | Medicament respiratory delivery device and method |
US6614197B2 (en) | 2001-06-30 | 2003-09-02 | Motorola, Inc. | Odd harmonics reduction of phase angle controlled loads |
GB0130857D0 (en) * | 2001-12-22 | 2002-02-06 | Glaxo Group Ltd | Medicament dispenser |
DE102004006450B4 (en) | 2004-02-05 | 2012-09-27 | Ing. Erich Pfeiffer Gmbh | metering |
US7219664B2 (en) | 2005-04-28 | 2007-05-22 | Kos Life Sciences, Inc. | Breath actuated inhaler |
AR058289A1 (en) | 2005-12-12 | 2008-01-30 | Glaxo Group Ltd | COLLECTOR TO BE USED IN MEDICINAL DISPENSER |
PT103481B (en) * | 2006-05-16 | 2008-08-01 | Hovione Farmaciencia S A | INHALER OF SIMPLE USE AND INHALATION METHOD |
BRPI0910875B8 (en) | 2008-03-27 | 2021-06-22 | Mannkind Corp | dry powder inhalation system |
-
2003
- 2003-09-04 US US10/655,153 patent/US7464706B2/en not_active Expired - Lifetime
-
2004
- 2004-09-03 KR KR1020097013309A patent/KR20090074284A/en active Search and Examination
- 2004-09-03 CA CA 2635665 patent/CA2635665C/en not_active Expired - Lifetime
- 2004-09-03 WO PCT/US2004/028699 patent/WO2005023348A2/en active Application Filing
- 2004-09-03 EP EP04783061.7A patent/EP1670532B1/en not_active Expired - Lifetime
- 2004-09-03 DK DK04783061.7T patent/DK1670532T3/en active
- 2004-09-03 CN CN2004800284690A patent/CN1859938B/en not_active Expired - Fee Related
- 2004-09-03 ES ES04783061.7T patent/ES2638279T3/en not_active Expired - Lifetime
- 2004-09-03 JP JP2006525464A patent/JP4456116B2/en not_active Expired - Fee Related
- 2004-09-03 KR KR1020077029059A patent/KR20080003462A/en not_active Application Discontinuation
- 2004-09-03 NZ NZ577038A patent/NZ577038A/en not_active IP Right Cessation
- 2004-09-03 BR BRPI0414085-0A patent/BRPI0414085A/en not_active Application Discontinuation
- 2004-09-03 AU AU2004270204A patent/AU2004270204B2/en not_active Ceased
- 2004-09-03 MX MXPA06002544A patent/MXPA06002544A/en active IP Right Grant
- 2004-09-03 CN CN200910133514.3A patent/CN101554504B/en not_active Expired - Fee Related
- 2004-09-03 NZ NZ545733A patent/NZ545733A/en not_active IP Right Cessation
- 2004-09-03 CA CA002537498A patent/CA2537498C/en not_active Expired - Lifetime
-
2006
- 2006-03-01 IL IL174041A patent/IL174041A/en active IP Right Grant
- 2006-03-04 KR KR20067004578A patent/KR100906269B1/en not_active IP Right Cessation
-
2008
- 2008-04-14 US US12/102,625 patent/US8215300B2/en not_active Expired - Fee Related
-
2009
- 2009-04-22 AU AU2009201564A patent/AU2009201564B2/en not_active Expired
- 2009-08-24 JP JP2009192888A patent/JP5071991B2/en not_active Expired - Lifetime
- 2009-08-28 AU AU2009212849A patent/AU2009212849B2/en not_active Ceased
-
2012
- 2012-06-06 US US13/490,292 patent/US8950397B2/en not_active Expired - Fee Related
-
2015
- 2015-01-08 US US14/592,790 patent/US20150122258A1/en not_active Abandoned
Cited By (36)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9801925B2 (en) | 1999-06-29 | 2017-10-31 | Mannkind Corporation | Potentiation of glucose elimination |
US9700690B2 (en) | 2002-03-20 | 2017-07-11 | Mannkind Corporation | Inhalation apparatus |
US9346766B2 (en) | 2004-08-20 | 2016-05-24 | Mannkind Corporation | Catalysis of diketopiperazine synthesis |
US9796688B2 (en) | 2004-08-20 | 2017-10-24 | Mannkind Corporation | Catalysis of diketopiperazine synthesis |
US9675674B2 (en) | 2004-08-23 | 2017-06-13 | Mannkind Corporation | Diketopiperazine salts for drug delivery and related methods |
US10130685B2 (en) | 2004-08-23 | 2018-11-20 | Mannkind Corporation | Diketopiperazine salts for drug delivery and related methods |
US10143655B2 (en) | 2005-09-14 | 2018-12-04 | Mannkind Corporation | Method of drug formulation |
US9717689B2 (en) | 2005-09-14 | 2017-08-01 | Mannkind Corporation | Method of drug formulation based on increasing the affinity of crystalline microparticle surfaces for active agents |
US9446001B2 (en) | 2005-09-14 | 2016-09-20 | Mannkind Corporation | Increasing drug affinity for crystalline microparticle surfaces |
US10130581B2 (en) | 2006-02-22 | 2018-11-20 | Mannkind Corporation | Method for improving the pharmaceutic properties of microparticles comprising diketopiperazine and an active agent |
US10342938B2 (en) | 2008-06-13 | 2019-07-09 | Mannkind Corporation | Dry powder drug delivery system |
US10201672B2 (en) | 2008-06-13 | 2019-02-12 | Mannkind Corporation | Dry powder inhaler and system for drug delivery |
US9662461B2 (en) | 2008-06-13 | 2017-05-30 | Mannkind Corporation | Dry powder drug delivery system and methods |
US9511198B2 (en) | 2008-06-13 | 2016-12-06 | Mannkind Corporation | Dry powder inhaler and system for drug delivery |
US9339615B2 (en) | 2008-06-13 | 2016-05-17 | Mannkind Corporation | Dry powder inhaler and system for drug delivery |
US9446133B2 (en) | 2008-06-13 | 2016-09-20 | Mannkind Corporation | Dry powder inhaler and system for drug delivery |
US10751488B2 (en) | 2008-06-13 | 2020-08-25 | Mannkind Corporation | Dry powder inhaler and system for drug delivery |
US10675421B2 (en) | 2008-06-20 | 2020-06-09 | Mannkind Corporation | Interactive apparatus and method for real-time profiling of inhalation efforts |
US9943571B2 (en) | 2008-08-11 | 2018-04-17 | Mannkind Corporation | Use of ultrarapid acting insulin |
US10172850B2 (en) | 2008-12-29 | 2019-01-08 | Mannkind Corporation | Substituted diketopiperazine analogs for use as drug delivery agents |
US9655850B2 (en) | 2008-12-29 | 2017-05-23 | Mannkind Corporation | Substituted diketopiperazine analogs for use as drug delivery agents |
US9983108B2 (en) | 2009-03-11 | 2018-05-29 | Mannkind Corporation | Apparatus, system and method for measuring resistance of an inhaler |
US9630930B2 (en) | 2009-06-12 | 2017-04-25 | Mannkind Corporation | Diketopiperazine microparticles with defined specific surface areas |
US9706944B2 (en) | 2009-11-03 | 2017-07-18 | Mannkind Corporation | Apparatus and method for simulating inhalation efforts |
US10625034B2 (en) | 2011-04-01 | 2020-04-21 | Mannkind Corporation | Blister package for pharmaceutical cartridges |
US9364436B2 (en) | 2011-06-17 | 2016-06-14 | Mannkind Corporation | High capacity diketopiperazine microparticles and methods |
US10130709B2 (en) | 2011-06-17 | 2018-11-20 | Mannkind Corporation | High capacity diketopiperazine microparticles and methods |
US10258664B2 (en) | 2011-10-24 | 2019-04-16 | Mannkind Corporation | Methods and compositions for treating pain |
US9610351B2 (en) | 2011-10-24 | 2017-04-04 | Mannkind Corporation | Methods and compositions for treating pain |
US9802012B2 (en) | 2012-07-12 | 2017-10-31 | Mannkind Corporation | Dry powder drug delivery system and methods |
US10159644B2 (en) | 2012-10-26 | 2018-12-25 | Mannkind Corporation | Inhalable vaccine compositions and methods |
US10421729B2 (en) | 2013-03-15 | 2019-09-24 | Mannkind Corporation | Microcrystalline diketopiperazine compositions and methods |
US9925144B2 (en) | 2013-07-18 | 2018-03-27 | Mannkind Corporation | Heat-stable dry powder pharmaceutical compositions and methods |
US11446127B2 (en) | 2013-08-05 | 2022-09-20 | Mannkind Corporation | Insufflation apparatus and methods |
US10307464B2 (en) | 2014-03-28 | 2019-06-04 | Mannkind Corporation | Use of ultrarapid acting insulin |
US10561806B2 (en) | 2014-10-02 | 2020-02-18 | Mannkind Corporation | Mouthpiece cover for an inhaler |
Also Published As
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US8950397B2 (en) | Unit dose cartridge and dry powder inhaler | |
US5355872A (en) | Low flow rate nebulizer apparatus and method of nebulization | |
US6948496B2 (en) | Inhalers | |
US20150246188A1 (en) | Unit dose capsules and dry powder inhaler | |
US20080115785A1 (en) | Inhalers | |
US20070125375A1 (en) | Device and method for deagglomeration of powder for inhalation | |
WO1988003419A1 (en) | Inhalation device | |
GB2375310A (en) | Inhalers |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: MANNKIND CORPORATION, CALIFORNIA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:STEINER, SOLOMON S.;POOLE, TRENT A.;FOG, PER B.;AND OTHERS;SIGNING DATES FROM 20031201 TO 20040106;REEL/FRAME:035330/0216 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |