EP0194257A1 - Dispositif de production d'aerosol - Google Patents

Dispositif de production d'aerosol

Info

Publication number
EP0194257A1
EP0194257A1 EP84903729A EP84903729A EP0194257A1 EP 0194257 A1 EP0194257 A1 EP 0194257A1 EP 84903729 A EP84903729 A EP 84903729A EP 84903729 A EP84903729 A EP 84903729A EP 0194257 A1 EP0194257 A1 EP 0194257A1
Authority
EP
European Patent Office
Prior art keywords
transducer
vortex
aperture
inlet
propellant
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP84903729A
Other languages
German (de)
English (en)
Inventor
Nathaniel Hughes
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
VORTRAN CORP
Original Assignee
VORTRAN CORP
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by VORTRAN CORP filed Critical VORTRAN CORP
Publication of EP0194257A1 publication Critical patent/EP0194257A1/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M11/00—Sprayers or atomisers specially adapted for therapeutic purposes
    • A61M11/06—Sprayers or atomisers specially adapted for therapeutic purposes of the injector type
    • 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
    • A61M15/009—Inhalators using medicine packages with incorporated spraying means, e.g. aerosol cans
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B05—SPRAYING OR ATOMISING IN GENERAL; APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
    • B05B—SPRAYING APPARATUS; ATOMISING APPARATUS; NOZZLES
    • B05B7/00—Spraying apparatus for discharge of liquids or other fluent materials from two or more sources, e.g. of liquid and air, of powder and gas
    • B05B7/02—Spray pistols; Apparatus for discharge
    • B05B7/10—Spray pistols; Apparatus for discharge producing a swirling discharge
    • 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
    • A61M2202/00—Special media to be introduced, removed or treated
    • A61M2202/06—Solids
    • A61M2202/064—Powder

Definitions

  • This invention relates to devices for producing an aerosol and more specifically to transducers for creating an aerosol.
  • Aerosol dispensers are generally well known in the art. These devices utilize transducers which generally create a spray of an active ingredient using a propellant. The resulting spray includes oversized liquid particles with a significant forward velocity which impact the surface or element being sprayed. The spray is non- uniform and results in a non-uniform deposition of active ingredient and consequent ineffective use of the active ingredient. There is no device which could deliver an aerosol having particles of a relatively small, uniformly consistent size.
  • One type of aerosol dispenser presently in use is anti-asthmatic medication inhalers. In one such
  • U. S. Patent No. 4,241,877 to Hughes shows a vortex generating device in FIGS. 5A, 5B, and 6, wherein a gas and a liquid pass into a flow passage together from an inlet.
  • the mixture flows about a rod and forms vortices thereabout and enters a bore along a portion of the rod after which the mixture exits the device through a con ⁇ stricted bore to a semispherical diverging outlet.
  • the liquid is partially atomized as it leaves the bore in the inlet and becomes fully atomized as it leaves the semi ⁇ spherical diverging outlet in a vortical gas stream.
  • a device is also shown where a gas and liquid under pressure are supplied together through an inlet member to a trans ⁇ versely extending rod for formation of vortices.
  • the vor- tices flow in a direction coaxial with the rod to a con ⁇ stricted outlet bore and to a semispherical diverging outlet.
  • the vortices also flow along auxiliary passages toward the constricted bore portion to combine with the previously-mentioned coaxial flowing vortices.
  • the Hughes '877 device is suitable for relatively high mass flow rates, but would not be suitable for use with propellant-charged canisters containing a rela ⁇ tively low propellant-to-active-ingredient ratio.
  • the present invention overcomes these deficiencies in the prior devices.
  • the device provides an aerosol having particles which are uniform in size regardless of the variation in range of pressure provided through the propellant in the canister. This result inheres even with low propellant-to-active-ingredient ratios and low mass flow rates.
  • the present invention is useful in a number of appli ⁇ cations where a relatively small concentration of propel ⁇ lant and active ingredient is used in applying the active ingredient.
  • the invention may be utilized in aerosol medication inhalers, paint sprayers, topical medication applications, hairspray, deodorant, lubricants and other aerosol applications.
  • the present invention due to its unique operation on miniscule amounts of gas or liquified propellant permits a unique capability when used in conjunction with the apparatus disclosed in the copending applications CP&H Docket No. 16030 and No. 15828 as a nebulizer permits operation at extremely low flow of oxygen or propellant namely from 0-5 liters per minute. This capability is of extreme importance in hospital and home therapy. Oxygen is toxic at high levels in 100% by volume concentration. Oxygen is also costly and at high levels makes for difficult patient ingestion of drugs.
  • a transducer for creating an aerosol having an inlet and an outlet portions includes a propellant inlet and a chamber defined by at least one chamber v/all confluent with the propellant inlet. Means are provided for creating at least one vortex in the chamber when the propellant enters the propellant inlet in a supersonic flow condition. Means spaced apart from the vortex creating means and separated therefrom by the chamber wall is provided for creating an exiting vortex.
  • FIG. 1 is a side-sectional view of a metered-dose inhaler using a single-inlet transducer assembly for creating an aerosol according to the present invention?
  • FIG. 2 is a schematic and side-sectional view of the transducer assembly shown in FIG. 1;
  • FIG. 3 is a front elevation view of the transducer assembly of FIG. 2;
  • FIG. 4 is a side section of a lens element for use in the transducer assembly of FIG. 3 taken along lines 4-4 of FIG. 3;
  • FIG. 5 is a side-sectional view of a portion of the inhaler of FIG. 1 showing two expansion chambers;
  • FIG. 6 shows an alternative embodiment of the device of FIG. 1 with an additional screen
  • FIG. 7 shows a schematic of a transverse cross sec ⁇ tion of the transducer assembly of FIG. 2 showing shock- waves and vortices;
  • FIG. 8 shows a resonant screen for use in the inhaler of FIG. 1;
  • FIG. 9 shows a front elevation view of a body portion of the inhaler
  • FIG. 10 shows an alternative embodiment of the trans ⁇ ducer assembly of FIG. 2;
  • FIGS. 11 and 12 show adapters for the output por ⁇ tions of the inhaler.
  • FIGS. 13, 14 and 15 show alternative embodiments of the transducer assembly of FIG. 10.
  • the description herein of the apparatus and its use includes a description of the method for producing an aerosol.
  • the description of the transducer is provided in relation to its use in conjunc ⁇ tion with a medication inhaler.
  • the application of the transducer is not to be limited to its use with a medication inhaler but is useful for producing aerosols for other applications.
  • FIG. 1 shows a transducer assembly 22 being used in conjunction with a medication inhaler 20.
  • the transducer assembly 22 includes a propellant inlet 96 and a chamber defined by at least one chamber wall 128 and confluent with the propellant inlet 96.
  • Means in the form of bluff body 112 is provided for creating at least one vortex 152 in the chamber when the propellant enters the propellant inlet in a supersonic flow condition.
  • Means in the form of an orifice defined by a groove 118 and surface 146 is provided spaced apart from the vortexcreating means and separated therefrom by the chamber wall 128 for creating an exiting vortex, indicated generally at 154.
  • the inhaler 20 of FIG. 1 includes a first body portion 38 for accepting and retaining the container 24 and for partially enclosing the transducer assembly 22.
  • the container 24 has a structure and function similar to metered dose containers generally known in the art.
  • the first body portion 38 is generally shaped in the form of an elbow having a hollow, cylindrical, generally upwardly extending vertical arm 40 and a hollow, cylindrical, generally forwardly extending (with respect to the remain ⁇ der of the inhaler 20) horizontal arm 42.
  • the direc ⁇ tional terms used herein, such as horizontal, vertical and upward are intended to be used for reference to the drawings only and are not to be construed as a limitation on the structure or function of the device.
  • the vertical ar 40 extends along a verticle axis 44.
  • the front half 46 of the verticle arm 40 extends vertically substantially all the way to the horizontal arm 42, except for a slot, rectangular in frontal view, for allowing insertion of the transducer (described below).
  • the rear half 48 of the vertical arm 40 extends vertically downward to a bend 50 forming the back half and the bottom portion of horizontal arm 42.
  • Horizontal arm 42 extends from the bend 50 substanti ⁇ ally horizontally, as shown in FIG. 1, about a horizontal axis 56.
  • the vertical axis 44 is normal to a plane con ⁇ taining the horizontal axis 56.
  • the horizontal arm 42 is substantially right circular cylindrical in vertical transverse cross section, as shown in FIG. 9.
  • the horizon- tal arm 42 extends forward about and past the transducer assembly 22 (in assembled form) to the end 58 of the first body portion 38.
  • the outer surface of the horizon ⁇ tal arm 42 terminates flush with the outer surface of second body portion 60.
  • the interior surface of horizontal arm 42 is also substantially right circular cylindrical in vertical transverse cross section and includes an end plate 60a at the left end, as seen in FIG. 1, of the horizontal arm 42.
  • a key-way 60b (FIG. 9) is cut in the top surface of the cylindrical portion of horizontal arm 42 for guiding and retaining the inlet of the " transducer assembly, to be described more fully below, as the assembly is placed
  • the first body portion 38 is formed generally such that it is compact and partly provides protection to the transducer assembly 22 and to the container 24.
  • the external dimensions of the first body portion 38, along with second body portion 60 are such that the inhaler 20 is compact and easily fits in the hand and may fit into a pocket.
  • the first body portion 38 along with the second body portion 60 are preferably made of polypropylene but may be made of other medical grade organic polymers providing structural support and desirable surface qualities after molding.
  • the second body portion 60 is for retaining and positioning the transducer assembly 22 and for changing the flow conditions of the aerosol subsequent to aerosol production in the transducer assembly.
  • the latter func ⁇ tion depends on the interior design of the second body portion 60.
  • the second body portion 60 has a rear portion whose outside and inside diameters are approximately one-half the outside and inside diameters, respectively, of the immediately adjacent forward portion.
  • the rear portion extends within and mates with the interior surface of horizontal arm 42.
  • the upper surface has a horizontally extending "U"-shaped cut (as viewed from above) made from the edge of a rear portion therein for accommodating the vertical inlet (to be described below) of the trans ⁇ ducer assembly 22.
  • the remainder of the rear portion is substantially cylindrical in vertical transverse cross section and extends from the rear portion of transducer assembly 22 to the remainder of second body portion 60.
  • a perimetrical flanged surface 61 for mating with the end 58 of the horizontal arm.
  • a rectangular key 61a extends generally horizon- tally rearward from the flanged surface 61 to mate with the key-way 60b (FIG. 9) in the top of the horizontal arm.
  • the second body portion extends from the rear end 62 having a preferred inside diameter indicated generally at 64 of approximately 0.467 inch to
  • the end 66 of the first expansion chamber wherein the in ⁇ side diameter, indicated generally at 68 is preferably 0.480 inch.
  • the inside dimensions of the second body portion 60 increase to form a diverging conical portion 72 wherein the inside diameter 74 of the second body portion is increased to preferably 0.940 inch.
  • the angle 76 of the diverging conical portion 72, from the horizontal is approximately 60°.
  • the diverging conical portion 72 and the remainder of the second body portion 60 form a second expansion chamber 78.
  • the outside dimensions of the second body portion 60 are gen ⁇ erally designed for structural integrity and compactness secondarily to the inside dimensions discussed above.
  • the inside length of the first expansion chamber 32 is prefer ⁇ ably 1.230 inch, and the inside length of the second expansion chamber from the end of the first is 1.273 inch.
  • the first and second body por- tions 38 and 60 are joined to form the ex ⁇ terior housing defining the inhaler 20.
  • the key 61a coup ⁇ ling the first and second body portions at the top of the horizontal arm 42 generally prevents rotation of the first body portion with respect to the second body portion.
  • the mutually adjacent surfaces of the first and second body portions may be bonded by ultrasonic or sonic welding to provide an airtight seal for preventing entrainment of air and preventing rotation of the two portions with re ⁇ spect to each other.
  • a vapor screen net or resonant screen 80 (FIG. 8) is positioned adjacent the outside horizontal rim 82 of the second body portion 60 forming the second expansion chamber 78.
  • the resonant screen 80 is positioned adjacent the outside horizontal rim 82 of the second body portion 60 forming the second expansion chamber 78. The resonant screen 80
  • the rim cap 84 is preferably ultra ⁇ sonically welded to the second body portion 60 to prevent removal of the cap and resonant screen 80.
  • the screen is preferably formed of a nylon lattice having an extreme diameter of 0.980 inch and a square lattice opening dimension of 0.060 inch x 0.060 inch. Each lattice member is preferably 0.012 inch across the face and 0.024 inch deep from one face of the screen to the other.
  • the outside diameter of the horizontal rim or lip of the second body portion is also preferably 1.020 inch for retaining the resonant screen in conjunction with the rim cap 84.
  • the resonant screen 80 may have a diameter of 0.910 inch and bonded to a frame 85 having an outside diameter of 1.010 inch.
  • the bonded screen is then placed on the inside of the second expansion chamber and bonded thereto.
  • the resonant screen and frame are positioned in the end of the second expansion chamber such that the outside surface of the resonant screen is flush with the rim of the second expansion chamber.
  • a cap 86 may be provided anchored around part of the second body portion 60 for capping the end of the inhaler at the second body portion 60 for protecting the resonant screen 80 and for preventing entry of foreign matter.
  • the cap 86 may be made of nylon.
  • transducer assembly 22 will now be described.
  • the outside dimensions of transducer assembly 22 to be used with the inhaler are chosen so that the assembly is retained in and held by the interior walls of the second body portion 60 at the rear portion thereof.
  • the joinder of the two is preferably a snap-in or snug fit.
  • the inlet 96 of transducer assembly 22 is placed in the
  • the transducer assembly 22 is substantially right circular cylindrical in external dimension and includes a vertically oriented inlet 96 5 previously mentioned.
  • the inlet 96 is a single fluid inlet oriented about the vertical axis 44 for accepting the nozzle 26, the medicated mixture from the nozzle 26 after actuation and for introducing the fluid to the remainder of the transducer assembly 22.
  • the rear surface 0 of the inlet 96 extends vertically downward to the upper surface 100 of the transducer body 102.
  • the flat rear surface 98 is substantially circular and closes the rear portion of the transducer body 102.
  • the front portion of the inlet 96 extends vertically 5 downward to the upper surface 100 of the transducer body
  • the transducer body 102 extends along the horizontal axis 58.
  • the exterior portion of the transducer body 102 terminates at a forward circumferential rim 106.
  • the outside dimensions of the transducer body 102 are formed so as to provide an airtight fit with the inside surfaces of the second body portion 60 which will enclose the transducer body. This prevents rotation of the transducer assembly with respect to the second body portion 60 and prevents entrainment of air during operation of the inhaler.
  • the transducer assembly including the lens portion to be described below, is preferably formed from polypropylene.
  • the inlet 96 includes a bore 107 adjacent the interior of the transducer body 102 and a counterbore 107a having an inside diameter 108 for accepting the nozzle of the canister.
  • the inside diameter of the bore 107 and the length of bore 107 are dimensioned such that the fluid ejected from the nozzle of the canister is optimized for adequate fluid expansion and flow to the interior of the transducer body.
  • the inside diameter of bore 107 is preferably 0.075 inch, and the length is preferably 0.0825 inch
  • the inside diameter 108 is dimensioned for the appro ⁇ priate size of the nozzle 26.
  • the inlet terminates in an aperture 109 opening into the interior of the transducer body 102.
  • the transducer body is formed in part by the rear inside surface 109a forming a substantially circular face at the extreme up ⁇ stream end of the transducer body 102 and by the circumfer- ential surface 110, which surface is oriented equidistant about the horizontal axis 58.
  • Concentric with the circum ⁇ ferential surface 110 and coaxial with the horizontal axis 58 is a bluff body 112 formed substantially from a right circular cylinder whose axis is the horizontal axis 58 and against which the mixture is impacted for creating vorti ⁇ ces in the transducer body.
  • the upstream portion of bluff body 112 is formed from, or molded with, the center of the rear inside surface 109a of the transducer body 102.
  • the surface of the junction of the two is curved and has a radius of curvature.
  • the inside diameter of the circumferential surface 110 is preferably 0.312 inch.
  • the circumferential surface 110 terminates opposite the rear inside surface 109a in a second circumferential surface 114 for surrounding and holding the lens.
  • OMft_ ⁇ inside diameter of the second circumferential surface 114 is preferably 0.375 inch.
  • the second inside circumferen ⁇ tial surface 114 extends from the termination of the circumferential surface 110 to the transducer body rim 106.
  • the distance from the termination of the circum ⁇ ferential surface 110 to the body rim is preferably 0.176 inch.
  • a substantially hemi-cylindrical woodruff key 116 for orienting and retaining the lens within the trans ⁇ ducer body 22.
  • the key preferably has a radius of 0.025 inch and extends substantially the length of the second circumferential surface 114.
  • the bluff body 112 extends beyond the termination of the circumferential surface 110 almost to a point in a plane defined by rim 106, preferably to within 0.013 inch of the plane of rim 106.
  • the length of the bluff body 112 extends from the rear inside surface 109a a distance of preferably 0.366 inch.
  • a groove 118 is pro ⁇ vided for forming an orifice for creating supersonic vor ⁇ tex flow from the transducer assembly.
  • the groove prefer ⁇ ably extends 0.040 inch to the end of the bluff body and has a radius of curvature of 0.012 inch.
  • a cylindrical lens portion 120 is seated in the vol ⁇ ume defined by the second circumferential surface 114 and mounted on the portion of bluff body 112 surrounded by the second circumferential surface 114.
  • the cylindrical lens portion 120 is for focusing and condensing vortically flowing fluid developed by the bluff body 112.
  • the lens has an outside circumferential face 122 dimensioned to correspond in part with the second circumferential surface 114 of the transducer body 102.
  • the face 122 is dimensioned to form a tapered surface at the upstream end thereof to facilitate an easy but tight, snap-in fit with the transducer body.
  • the cylindrical lens portion 120 is provided with a groove 124 in its outside circumferential face correspond ⁇ ing to the woodruff key 116 of the transducer body 102.
  • the diameter of the groove is preferably 0.056 inch.
  • the outside circumferential face 122 is preferably dimen ⁇ sioned such that when placed within the second circum ⁇ ferential surface 114, the cylindrical lens portion 120 is retained by the tight fit of the transducer body 102 and the lens portion 120. If desired, an airtight fit may be provided by ultrasonic or sonic welding.
  • the cylindrical lens portion 120 is provided with an aperture 126 having an inside diameter corresponding to the outside diameter of the bluff body 112.
  • the outside diameter of the bluff body 112 is pre ⁇ ferably 0.072 inch, and the inside diameter of the lens aperture is 0.072 inch.
  • Aperture 126 is formed symmetri- cally about horizontal axis 58.
  • a first conically shaped depression 128 is formed in the upstream surface of cylindrical lens portion 120, con ⁇ verging inward toward the aperture 126 and serves to focus the vortices.
  • the maximum diameter of the depression 128 at the upstream edge 130 is preferably 0.322 inch and sub ⁇ stantially equivalent to the inside diameter of the cir ⁇ cumferential surface 110.
  • the surface of the cone forms an angle of about 57° with the horizontal axis 58.
  • the depression terminates at the aperture 126 having a diame- ter of 0.072 inch.
  • the height of the conical depression from the upstream edge 130 to the upstream edge of aperture 126 is preferably 0.081 inch.
  • a second conically-shaped depression 132 extends from the downstream edge of aperture 126 along horizontal axis 58 to the downstream edge 134 of the lens portion 120.
  • the second depression 132 diverges such that the conical surface preferably forms a 45° angle with the horizontal axis 58 for enhancing formation of a large vortex having supersonic flow and a subatm ⁇ spheric pressure region.
  • the maximum diameter of the depression is preferably 0.133 inch.
  • the aperture 126 preferably extends 0.084 inch along the cylindrical lens portion 120 such that there is a cylindrical volume 136 beyond bluff body 112 before the second conically depression 132 begins for focusing the vortices.
  • the length of the cylindrical volume is 0.004 inch.
  • the inside diameter is the same as that of the aperture 126.
  • a second cylindrical aperture 138 is formed in the cylindrical lens portion 120 having an axis 140 extending horizontally-and parallel to horizontal axis 58 and is radially offset from aperture 126.
  • the second aperture is provided for concentrating vortices developed at bluff body 112, and the conically-shaped depression 128, and for transporting the flow to the orifice formed by groove 118.
  • the second cylindrical aperture 138 is preferably formed on the side of the bluff body opposite the inlet 96 and on the same side as groove 118.
  • the aperture 138 is formed in the lens portion 120 180° from the woodruff key groove 124.
  • the axis 140 is positioned 0.122 inch from the horizontal axis 58. As a result, the upstream rim of the second aperture is positioned entirely along the surface of the first conically-shaped depression 128.
  • a third cylindrical aperture 142 is formed in the lens portion 120 extending from the outside circumferential face 122 of the lens portion 120 radially inward to the aperture 126.
  • the third cylindrical aperture 142 is ori ⁇ ented about a second vertical axis 144 which preferably intersects and is at right angles with the horizontal axis 58. Additionally, the horizontal axis 140 preferably intersects and is perpendicular to the second vertical axis 144.
  • the third cylindrical aperture enhances the vortical flow of the mixture due to its 90° configuration with respect to the second aperture 138 and further focuses the flow of the mixture and transports it to the orifice.
  • the second vertical axis 144 is preferably 0.122 inch from the upstream edge 130 of the lens portion 120.
  • the diameter of the third cylindrical aperture 142 ° is preferably 0.060 inch. As a result, only a portion of the third cylindrical aperture 142 opens into a portion of the groove 118. The remainder of groove 118, specif ⁇ ically between 0.0065 and 0.0125 inch of groove 118, is enclosed within the aperture 126. A nozzle or orifice is 5 thereby formed in the final portion of groove 118 as a result of the intersection of the grooved cylinder with the circular aperture. Due to the circular nature of the third cylindrical aperture 142 as it intersects groove 118, the bottom surface 146 formed by the intersection of 0 the groove 118 and the third cylindrical aperture 142 appears as indicated in FIGS. 2 and 3.
  • the vertical sectional view of the orifice formed by the intersection of the groove 118 with the lens portion 120 is as shown in FIG. 3 comprising two arcs having different radii of curvature. Tests have been conducted wherein the radius of the groove 118 is varied between 0.010 and 0.014 inch, and it has been determined that with the other dimensions described, the optimum radius is 0.012.
  • the nozzle formed by the intersection of the groove 118 and the third cylindrical aperture 142 is for focusing the fluid obtained from the second cylindrical aperture 138 and third cylindrical aperture 142 for ejection into the cylindrical volume 136 and expansion into the second .
  • the nozzle forms a single, large vortex having supersonic flow and a sub- atmospheric region. As described below, the nozzle produces the vortex and assists in centralizing the vortex.
  • the downstream edge 134 is at the extreme downstream portion of the lens 120.
  • the remainder of the downstream portion of lens 120 extends outwardly and rearwardly, preferably at a 10° angle from the plane defined by the downstream edge 134, to the outside circumferential face 122 of lens 120.
  • the outside face 122 then extends rearwardly to the forward circumferential rim 106 of transducer body 102.
  • the horizontal distance from the downstream edge 134 to the outside circumf rential face 122 is preferably 0 021 inch.
  • the output of the transducer assembly can be varied by varying the diameters of the various apertures and of the groove.
  • addi ⁇ tional apertures may be provided for providing a flow path to the groove 113.
  • the configuration of FIG. 1 is preferred.
  • FIG. 6 shows a schematic of an alternative embodiment of the inhaler 20, including a second resonant screen 148 for performing substantially the same function of the first resonant screen 80 in substantially the same way.
  • Resonant screens 80 and 148 may be used together or alone to achieve the desired flow characteristics.
  • the inhaler 20 is assembled as would be apparent to one skilled in the art.
  • the pa ⁇ tient then places a container 24 having a mixture of pro ⁇ pellant, active medication, and solvent in an inverted fashion into the first body portion 38.
  • the outlet port of nozzle 26 then is confluent with aperture 92 (FIG. 3).
  • the staging chamber of container 24 is filled with the appropriately metered dose of the mixer of propellant and the medication.
  • the patient then depresses the con ⁇ tainer relative to the first body portion 38 so that the nozzle 26 is forced further into the mouth of container 24.
  • the interior port to container 24 is thereby sealed and the mixture contained in the staging chamber is ejected under a pressure of between 30 and 50 pounds per square inch, depending upon the particular container be ⁇
  • the volume of the staging chamber may be ap ⁇ proximately 0.05 cubic centimeters so that the total volume of the mixture of propellant and medication is approximately 0.05 cubic centimeters.
  • the phenomenon of ⁇ "*5 "cold boiling” and/or the resultant atomization of the liquid in the propellant-solvent mixture may occur when the injected mixture is pressurized and then released into the inlet 96.
  • the ratio of the gas pressure to the ambient pressure is greater than the
  • the * pressure of the mixture in the canister 24 may be approximately 50 pounds per square inch, gage (psig).
  • the propellant to liquid ratio may be typically 30:1 and the volume of output per shot may be 0.05 cubic centimeters.
  • the presence of bluff body 112 in front of the supersonic gas gives rise 35 to a standing shock wave indicated at 150 in FIGS. 2 and 7 and generation of a very large number of vortices indicated at 152.
  • the potential energy, i.e., static pressure, of the gas supplied to the inlet is, in effect, partly converted to kinetic energy—first as an increase in linear gas velocity, then as shock waves, and finally as vortices in the flow passage.
  • the vortices are formed having axes generally parallel to the bluff body 112.
  • the vortices formed at the periphery of the bluff body rotate en masse about axis 58. It is estimated that the pressure at the bluff body 112 in the transducer body 102 is approximately 20-30 psig.
  • the tiny vortices are formed at a rate of approximately 40,000-50,000 vortices per second, according to present estimates. This is due to the high velocity of the flow and to the less viscous flow of the propellant-liquid mixture. Formation of a maximum number of vortices per unit time is preferred. The number of vortices is proportional to the velocity and the area across which the gas flows having a coef ⁇ ficient of drag.
  • the cylindrical apertures contribute to the for-"" mation of the aerosol from the outlet of the orifice for creating the exiting vortex. These result in superior atomization and/or higher sonic energy genera ⁇ tion.
  • the vortex activity from the bluff body 112 to the final large vortex 154 produces atomization of the liquid fraction in the liquid-propellant mixture so that the medication contained in the liquid fraction is atomized into a mist substantially containing one to three micron- 5 sized particles for entering the first expansion chamber 30. It was found that one massive vortex was formed by impinging the vortices on a rod and letting them escape through an annular chamber. It is believed that once the large number of tiny vortices are created from the bluff 0 body, the vortices can then be manipulated as desired to produce a given result such as the single, large vortex 154.
  • the single large exiting vortex 154 is comprised of fluid flowing at supersonic velocity due to the compres- 5 sion of the vortices flowing through the orifice and due
  • OMPI_ to the pressure difference across the orifice being greater than the critical pressure.
  • the dose mixture went through a first supersonic flow regime, followed by expansion and creation of vortices.
  • the vortices were then forced through the second and third apertures fol ⁇ lowed by a second supersonic flow regime out of the orifice and expansion into one large vortex.
  • the pres ⁇ sure on the downstream side of the orifice is approxi ⁇ mately atmospheric.
  • the exiting vortex represents a conversion of a substantial amount of static energy to dynamic energy.
  • the vortex is spinning about an approxi ⁇ mate center along axis 58 even though the orifice is offcenter.
  • the semicircular, axially extending, wedge- shaped orifice, as seen in transverse cross section, 5 contributes to the centralizing effect on the single vortex.
  • Other configurations for an outlet orifice are contemplated, but the arcuately sectioned circle shown in FIG. 3 is preferred.
  • the design of the cylindrical lens portion 120 serves o several functions. One is to focus the vortex-containing fluid at the orifice.
  • the single cylindrical apertures 138 and 142 provide means for impinging the tightly con ⁇ figured vortices developed about bluff body 112 into focused flow and for increasing the pressure in the flow 5 channels of which the cylindrical apertures are comprised. Because the flow rate in terms of mass times velocity is so low for each dose from the canister, the flow passages must be small enough to maintain the pressure gradient to the first expansion chamber 30 and to provide forward flow velocity for the vortices.
  • the orifice comprising groove 118 and bottom surface 146 is also designed to provide these features and to provide vortex action and supersonic flow, rather than merely squirting the fluid.
  • the dimensions of the orifice are preferably such as to create supersonic flow in the fluid at the output for creating the single vortex, for providing good atomiza ⁇ tion of the liquid portion of the mixture and to provide a shock wave pattern in the single vortex which also serves to enhance the atomization of the liquid.
  • a second factor which affects the configuration of the exiting vortex is the propellant to liquid ratio. A limited amount of energy is available for atomization to take place. It is important to ration that energy while still obtaining the desired results. A minimum amount of propellant is desired for a given volume of liquid to maintain the supersonic nature of the exiting vortex, the atomization characteristics thereof and the shock wave pattern produced in the vortex during supersonic condi ⁇ tions.
  • the design of the transducer lens in the single inlet transducer 22 and the relative proportion of propellant may be adjusted as desired to maintain the desired characteristics of the exiting vortex.
  • a second design consideration is the formation of the orifice by the conjunction of groove 118 and the bot ⁇ tom surface 146 of the cylindrical lens portion 120.
  • there are various methods for formation of such an orifice including formation of a hole in a cylindrical plug using a laser process, and the formation of a hole through var ⁇ ious molding techniques.
  • the formation of the hole through molding techniques is often inaccurate and often does not provide consistently reliable results. Molding techniques are especially important where low cost, single inlet transducers of the type shown in FIG. 2 are desired.
  • the design illustrated in FIG. 2 was de- veloped.
  • the small orifice is easily formed by the conjunction of a cylindrical rod having a groove formed therein with a circular aperture extending coaxial with the cylindrical rod wherein the diameter of the aper ⁇ ture is equivalent to the diameter of the cylindrical rod except for the groove cut therein.
  • a small orifice is formed and problems of tolerances between the rod and aperture are eliminated and problems of variation in dimensions of the orifice are minimized.
  • the single inlet transducer 22 can be accommodated for higher flow rates and for larger variations in the propellant-to-liquid ratio by changing the dimensions of the interior of the transducer and the cylindrical aper ⁇ tures 138 and 142.
  • the groove and the conically shaped depressions in the lens portion 120 may be adjusted as required to produce the desired exiting vortex.
  • additional cylindrical apertures may be provided for producing a symmetrical input to the first expansion chamber with appropriate modification to the orifice.
  • a separate orifice may be provided for each radially extend ⁇ ing cylindrical aperture.
  • the single vortex includes a negative pressure zone at the center thereof due to the pressure differential across the orifice being greater or equal to the critical pressure ratio. It has been found that there is enhanced atomization with the disclosed configuration and minimiza ⁇ tion of deposition of moisture on adjacent surfaces and on a target. It is believed that the particles are
  • OMPI electrostatically charged and, therefore, inhibit deposi ⁇ tion and recombination or condensation to form larger droplets.
  • the first expansion chamber provides for expansion of the vortex, thereby reducing the velocity and, there ⁇ fore, mean free path of the individual medication parti ⁇ cles and provides an area for confining the atomized vapor.
  • the expansion and slowing of the particles inhi ⁇ bits condensation of the individual particles and depo ⁇ sition of the particles along the chamber wall.
  • the for ⁇ ward velocity of the particles is transferred to increased random motion of the individual particles. Additionally, it is believed that further atomization of the particles may occur to a limited extent.
  • the vortex continues to the second expansion cham ⁇ ber, a like process occurs whereby the forward velocity of the individual particles is further decreased and the vapor vortex is further expanded due to the increased cross sectional area of the second expansion chamber.
  • the effect of the increase in cross sectional area on the vortex is the same as that from the expansion in the first expansion chamber.
  • the second expansion chamber assists in storing the vapor in the vortex, slows the vortex in its forward movement and allows creation of greater vorticity when the fluid reaches the resonant screen, to be described more fully below.
  • the fluid in the vortex is then impacted on the reso ⁇ nant screen 80 with several resulting effects.
  • the screen resonates to set up a standing wave pattern in the expan- sion chambers to assist in uniformly dispersing particles in the vortex in the second expansion chamber. It also serves as a drag brake to break up the remaining particles in the vortex. This is enhanced by the fact that a force of drag on the fluid flow is more significant than the force due to the forward momentum of the fluid. Therefore, the effects due to the drag force predominate over the effect due to forward flow of the fluid.
  • the final result, after impingement of the fluid on the resonant screen is a soft, "warm", low-velocity mist or vapor to be inhaled by a patient.
  • the mist will have minimal if any impact on the air passageways in the pa ⁇ tient's mouth and lungs as the vapor is inhaled.
  • the apparent temperature of the aerosol is more acceptable to the patient also.
  • the majority of the liquified propellant will have expanded to a gaseous state leaving the liquid droplets of one to three micron monodispersed size at the monodispersed downstream end of the screen without requiring any further impinge ⁇ ment of the fluid to obtain the desired droplet size. It is believed that the quality and quantity of output is due in part to the combined effect of the supersonic and vortical nature of the transducer output flow and to the resonant screen function.
  • the results obtained in the single-inlet transducer combined with the expansion chambers and resonant screens are reproducible for any medication delivery canister pre ⁇ sently marketed. The same output is still effected.
  • the inhaler When the inhaler is manufactured in a plastic molding process, the inhaler may be disposable after completion of a medication regimen from one medication canister. The inhaler is easy to reliably manufacture and easily assembled with press fit parts. The inhaler is compact and convenient to hold and carry.
  • the transducer of the inhaler is inherently self-adjusting and provides the required particle size output, even with moderate changes in inlet characteristics. How ⁇ ever, a point is reached where larger flows in the inlet or other fluid changes, such as propellant-to-liquid ra ⁇ tio, result in a decrease in efficiency of the inhaler. At that point, the transducer would be changed to accommo ⁇ date the different flow characteristics.
  • FIG. 10 shows an alternative embodiment of a transducer in the form of transducer assembly 156.
  • the transducer assembly has a bore 158 in the form of a parallelopiped and a counterbore 160 in the shape of a right circular cylinder.
  • a first cylindrical aperture 166 extends along the first axis (not shown) toward a second cylindrical aperture 168 extending along a second axis (not shown) perpendicular to the first axis.
  • the second axis extends toward a third axis about which the transducer chamber 162 is oriented.
  • the second cylindrical aperture extends from the outside surface 170 of the transducer assembly radially inward slightly past the third axis.
  • a plug (not shown) is provided for sealing the second cylin ⁇ drical aperture 168 to provide a cylindrical aperture similar to the third cylindrical aperture 142 of FIG. 2.
  • An orifice 172 is formed coaxial with the third axis from the second cylindrical aperture 168 to a diverging coni ⁇ cal portion 174.
  • the diverging conical portion is ori ⁇ ented about the third axis.
  • the external dimensions of the transducer assembly 156 are configured in a manner similar to the transducer assembly of FIG. 2 for incor ⁇ poration into an inhaler.
  • the transducer assembly includes a tack-shaped bluff body 176 oriented symmetrically about the third axis.
  • the tack-shaped bluff body includes a cap portion 178 for sealing the transducer chamber 162 and a cylin ⁇ drical portion 180 tapering downward to the converging conical portion in the form of a bluff body 164.
  • the bluff body serves the same function as bluff body 112 described with respect to FIGS. 1 and 2.
  • the bluff body is preferably tapered to assist the flow of the resulting vortices in the direction of the first cylindrical aper ⁇ ture 166.
  • the transducer assembly 156 is relatively easier to manufacture and mass produce. For applications other than for medication inhalers, the preferred material may be different.
  • the operating characteristics of the transducer assembly 156 are similar to those described with respect
  • the dimensions of the transducer can be adjusted to accommodate different flow conditions for other applications.
  • the propellant- to-liquid ratio may be adjusted.
  • the dimensions of the bluff body 176 and apertures 166 and 168 may be modified to provide the desired flow charac ⁇ teristics in the output fluid.
  • I 5 characteristics may be adjusted as desired.
  • FIG. 11 shows a nasal adapter 182 in side section for placement over the resonant screen 80 in the second expansion chamber. This allows nasal intake of the vaporized medication.
  • FIG. 12 shows an oral adapter 184 to be positioned over the inhaler 20 in a manner similar to that described with respect to the nasal adapter of FIG. 11.
  • the oral adapter may be beneficial for providing medication to infants and patients who may be incapacitated.
  • FIG. 13 shows an alternative embodiment of the transducer of FIG. 10 including a propellant canister 188 having an inlet. tube 190 coupled to the inlet counterbore 160.
  • the elements in FIG. 13 common to those of FIG. 10 are identified with like reference numerals and are sub- 0 stantially the same in structure and function as those described with respect to FIG. 10.
  • a second inlet tube 192 is provided for supplying the active ingredient to the vortex created through the orifice 172.
  • tube 192 extends externally of the transducer 186 to a preferably flexible container 194 for the active ingre ⁇ washer.
  • a guide tube 196 may also be provided for channel ⁇ ing the flow of the fluid output having a function
  • transducer 186 may have an inside
  • transducer 186 up to the point of the orifice 172 is substantially the same as those described with respect to the transducers of FIGS. 2 and 10. As there is no liquid active ingredient
  • the fluid is effectively atomized by the action of the exiting vortex.
  • the atomization of the active ingredient is substantially the same due to the action of the vortex 0 as the atomization with the transducers previously described.
  • the propellant canister 188 may be a unit dose canister such as that described above with respect to FIG. 1 or may be a continuous flow canister providing 5 output whenever the inlet tube 190 is depressed with
  • OMPI respect to canister 188.
  • the exiting vortex produced by the transducer 196 draws the active ingredient from container 194 as long as propellant is produced from canister 188.
  • the active ingredient is drawn from flexible container 194 until fluid is no longer present in the container.
  • FIG. 14 shows an alternative embodiment of trans- ducer 186 and the inlet tube 192 wherein the inlet tube is placed external to the transducer 186 adjacent the outer rim of the diverging conical portion 174. Sub ⁇ stantially the same result can be obtained for atomizing the active ingredient with the inlet tube 192 located as shown in FIG. 14 as can be obtained with the arrangement provided in FIG. 13. The function and operation of the arrangement shown in FIG. 14 is otherwise the same as that described with respect to FIG. 13.
  • FIG. 15 shows an additional embodiment of trans- ducer 186 and the inlet tube 192 wherein the inlet 192 has its terminal portion flush with the surface of conical portion 174.
  • the structure and function of the trans ⁇ ducer is otherwise the same as described with respect to FIGS. 13 and 14.
  • These transducers are particularly efficient at low liter flows of oxygen and are very much suited for general hospital use at these flows with the requisite advantages for low oxygen rate therapy cited earlier. This capability makes nebulizers built with these inventions uniquely operable with oxygen concentrators.

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Abstract

Procédé et dispositif d'application d'un ingrédient actif sous la forme d'un aérosol. Un transducteur (22) servant à produire un aérosol comprend un orifice d'entrée de propulseur (96) et une chambre définie par au moins une paroi de chambre (128) confluente avec l'orifice d'entrée de propulseur. Un corps renflé sert à créer au moins un tourbillon (152) dans la chambre lorsque le propulseur pénètre dans l'orifice d'entrée dans des conditions d'écoulement supersonique. Un orifice (118, 146) écarté du corps renflé et séparé de ce dernier par la paroi de chambre sert à créer un tourbillon de sortie (154).
EP84903729A 1984-09-18 1984-09-18 Dispositif de production d'aerosol Withdrawn EP0194257A1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/US1984/001517 WO1986001730A1 (fr) 1984-09-18 1984-09-18 Dispositif de production d'aerosol

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Publication Number Publication Date
EP0194257A1 true EP0194257A1 (fr) 1986-09-17

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EP84903729A Withdrawn EP0194257A1 (fr) 1984-09-18 1984-09-18 Dispositif de production d'aerosol

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EP (1) EP0194257A1 (fr)
WO (1) WO1986001730A1 (fr)

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10036574B2 (en) 2013-06-28 2018-07-31 British American Tobacco (Investments) Limited Devices comprising a heat source material and activation chambers for the same
US10542777B2 (en) 2014-06-27 2020-01-28 British American Tobacco (Investments) Limited Apparatus for heating or cooling a material contained therein
US11064725B2 (en) 2015-08-31 2021-07-20 British American Tobacco (Investments) Limited Material for use with apparatus for heating smokable material
US11241042B2 (en) 2012-09-25 2022-02-08 Nicoventures Trading Limited Heating smokeable material
US11452313B2 (en) 2015-10-30 2022-09-27 Nicoventures Trading Limited Apparatus for heating smokable material
US11659863B2 (en) 2015-08-31 2023-05-30 Nicoventures Trading Limited Article for use with apparatus for heating smokable material
US11672279B2 (en) 2011-09-06 2023-06-13 Nicoventures Trading Limited Heating smokeable material
US11825870B2 (en) 2015-10-30 2023-11-28 Nicoventures Trading Limited Article for use with apparatus for heating smokable material
US11924930B2 (en) 2015-08-31 2024-03-05 Nicoventures Trading Limited Article for use with apparatus for heating smokable material

Families Citing this family (2)

* Cited by examiner, † Cited by third party
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EP0308524B1 (fr) * 1987-09-22 1995-04-26 Vortran Medical Technology, Inc. Dispositif d'inhalation et méthode
GB2461752B (en) * 2008-07-14 2013-04-17 Neo Inhalation Products Ltd Metered dose inhaler

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US4109862A (en) * 1977-04-08 1978-08-29 Nathaniel Hughes Sonic energy transducer
US4241877A (en) * 1978-10-16 1980-12-30 Hughes Sciences Group, Inc. Stable vortex generating device

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Title
See references of WO8601730A1 *

Cited By (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11672279B2 (en) 2011-09-06 2023-06-13 Nicoventures Trading Limited Heating smokeable material
US12041968B2 (en) 2011-09-06 2024-07-23 Nicoventures Trading Limited Heating smokeable material
US11241042B2 (en) 2012-09-25 2022-02-08 Nicoventures Trading Limited Heating smokeable material
US10036574B2 (en) 2013-06-28 2018-07-31 British American Tobacco (Investments) Limited Devices comprising a heat source material and activation chambers for the same
US10542777B2 (en) 2014-06-27 2020-01-28 British American Tobacco (Investments) Limited Apparatus for heating or cooling a material contained therein
US11064725B2 (en) 2015-08-31 2021-07-20 British American Tobacco (Investments) Limited Material for use with apparatus for heating smokable material
US11659863B2 (en) 2015-08-31 2023-05-30 Nicoventures Trading Limited Article for use with apparatus for heating smokable material
US11924930B2 (en) 2015-08-31 2024-03-05 Nicoventures Trading Limited Article for use with apparatus for heating smokable material
US11452313B2 (en) 2015-10-30 2022-09-27 Nicoventures Trading Limited Apparatus for heating smokable material
US11825870B2 (en) 2015-10-30 2023-11-28 Nicoventures Trading Limited Article for use with apparatus for heating smokable material
US12016393B2 (en) 2015-10-30 2024-06-25 Nicoventures Trading Limited Apparatus for heating smokable material

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