US20210046258A1 - Method and apparatus for producing fine concentrated aerosol - Google Patents
Method and apparatus for producing fine concentrated aerosol Download PDFInfo
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- US20210046258A1 US20210046258A1 US17/089,184 US202017089184A US2021046258A1 US 20210046258 A1 US20210046258 A1 US 20210046258A1 US 202017089184 A US202017089184 A US 202017089184A US 2021046258 A1 US2021046258 A1 US 2021046258A1
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- nebulizer
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- 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
- A61M11/02—Sprayers or atomisers specially adapted for therapeutic purposes operated by air or other gas pressure applied to the liquid or other product to be sprayed or atomised
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M11/00—Sprayers or atomisers specially adapted for therapeutic purposes
- A61M11/001—Particle size control
- A61M11/003—Particle size control by passing the aerosol trough sieves or filters
-
- 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
-
- 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
- A61M15/0086—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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/07—General characteristics of the apparatus having air pumping means
- A61M2205/071—General characteristics of the apparatus having air pumping means hand operated
- A61M2205/073—Syringe, piston type
Definitions
- partially absorbed refers to a porous medium wherein at least 0.5% of the surface and sub-surface pores contain liquid. In some embodiments, partially absorbed refers to at least 1% liquid contents within the surface and sub-surface pores. In some embodiments, partially absorbed refers to at least 10% liquid contents within the surface and sub-surface pores. In some embodiments, partially absorbed refers to at least 20% liquid contents within the surface and sub-surface pores. In some embodiments, partially absorbed refers to at least 30% liquid contents within the surface and sub-surface pores. In some embodiments, partially absorbed refers to at least 40% liquid contents within the surface and sub-surface pores. In some embodiments, partially absorbed refers to at least 50% liquid contents within the surface and sub-surface pores. In some embodiments, partially absorbed refers to at least 60% liquid contents within the surface and sub-surface pores.
- the porous medium has a modulus of rigidity of at least 10 GPa (10 9 pascal) at 25° C. In some embodiments, the porous medium has a modulus of rigidity of at least 15 GPa at 25° C. In some embodiments, the porous medium has a modulus of rigidity of at least 20 GPa at 25° C. In some embodiments, the porous medium is substantially devoid of materials having modulus of rigidity lower than 10 GPa at 25° C.
- a polymer used for forming the porous medium is typically a rigid polymer, such as, a polymer having a Tg (glass transition temperature) in the range of 100 or above 100.
- the porous medium is in a shape of a disc.
- Concentrated aerosol refers to the number of droplets per volume unit. Concentrated aerosols include more than 10 8 droplets per cm 3 . Highly concentrated aerosol includes more than 10 9 droplets per cm 3 .
- FIGS. 2 a -2 b illustrate nebulizer 100 comprising porous medium 102 prior to aerosol production, in a first optional compressed position and a second optional compressed position, respectively;
- FIG. 2 c illustrates nebulizer 100 comprising porous medium 102 when nebulizer 100 is in aerosol production position, due to the pressure drop generated between upper flat side 102 b and lower flat side 102 a of the porous medium 102 ;
- FIG. 2 d describes nebulizer 100 comprising porous medium 102 in a position that enables aerosol inhalation.
- Nebulizer 100 being under a pressure drop across porous medium 102 is illustrated in FIG. 2 c .
- atomization occurs as a result of the pressure difference across the two sides of porous medium 102 , according to some embodiments.
- the pressure difference causes the medium to act as a pneumatic multi-nozzle, where the nozzles are defined by pores 2 of porous medium 102 , according to some embodiments.
- porous medium 102 is configured for multiple uses. According to some embodiments, porous medium 102 is configured for discharge of, and replenishment with, liquid 3 .
Abstract
The present disclosure generally relates to the field of nebulizers for aerosol generation and methods of using same for treating diseases and disorders.
Description
- This application is a Continuation of U.S. patent application Ser. No. 15/467,527, filed on Mar. 23, 2017, which is a Continuation-in-Part of U.S. patent application Ser. No. 13/521,718, filed on Jul. 11, 2012 (published as US 20120318259), which is the U.S. National Stage of International Patent Application No. PCT/IL2011/000038, filed on Jan. 12, 2011, which claims the benefit of U.S. Provisional Patent Application No. 61/294,161, filed on Jan. 12, 2010, the contents of each of which are incorporated herein by reference in their entireties.
- The present invention relates to a method and apparatus enabling production of ultra-fine and concentrated aerosol from liquids, for various applications, by using rigid porous material, enabling storage and easy streaming of the aerosol (e.g. for inhalation), fast replacement of liquid carrier device and accuracy of output sprayed dose.
- Nebulizers are commonly used for delivering aerosol medication to patients via the respiratory system. Desirably, for efficient delivery of medication, the droplet diameter of the aerosol should be sufficiently small so as to reach the lungs of the patient without being obstructed by objects or organs (such as, the inner surface of the nozzle in the nebulizer and the mouth cavity perimeters) and large enough so as to remain in the lungs during exhalation.
- The main techniques for producing aerosol in nebulizers include vibrating Mesh technology, jet nebulizers and ultrasonic wave nebulizers. Common to these techniques is the challenge to deliver large volume of medication to the patient while keeping the diameter of the droplets within desired limits.
- U.S. Pat. No. 2,284,591 discloses a liquid nebulizer device adapted to provide oily compositions specifically to the nose and throat, through preventing their entrance and congestion in the lungs.
- U.S. Pat. No. 3,812,854 discloses an ultrasonic nebulizer for atomizing a liquid medicament comprising a porous solid body having a defined intercommunicating pore structure where the diameters of at least 75% of the pore openings is in the range of 0.5 to 5 microns.
- U.S. Pat. No. 4,907,581 discloses a disposable radioactive aerosol inhalation apparatus including a lung aerosol unit, which both generates and traps sub-micron particles, on the order of 0.3 micron, for use in diagnostic pulmonary ventilation studies.
- U.S. Pat. No. 5,603,314 discloses a filtration device suitable for reducing exhaled particles released by a patient during aerosol inhalation therapy.
- U.S. Pat. Nos. 5,755,221 and 7,246,617 disclose inhaling devices.
- U.S. Pat. No. 6,070,575 discloses a nozzle for aerosolizing a drug formulation, the nozzle includes a flexible membrane material having a plurality of pores, the pores have an exit aperture diameter in the range of about 0.5 to about 50 microns.
- US 2002/0073991 discloses a method of monitoring aerosol delivery efficacy.
- US 2007/0175476 discloses an aerosol powder delivery device.
- The following embodiments and aspects thereof are described and illustrated in conjunction with systems, tools and methods which are meant to be exemplary and illustrative, not limiting in scope. In various embodiments, one or more of the above-described problems have been reduced or eliminated, while other embodiments are directed to other advantages or improvements.
- In some embodiments, there is provided a nebulizer for producing aerosol, comprising a porous medium, wherein the porous medium is rigid, has two flat sides and further comprises: a plurality of pores; a liquid partially adsorbed in the porous medium; and gas, wherein the gas is caged in pores that are vacant of said liquid, wherein the porous medium is configured to act as a pneumatic multi-nozzle atomizing system.
- In some embodiments, the nebulizer further comprising a mouthpiece configured to deliver the aerosol to the lungs of a subject by inhalation.
- In some embodiments, the aerosol comprises droplets of the liquid, the droplets having an MMAD within the range of 0.3 to 7 microns. In some embodiments, the diameter of said droplets is in the range 0.3 to 1.1 micrometer. In some embodiments, the droplets are having a Geometric Standard Diameter (GSD) within the range of about 2-5 micrometer
- In some embodiments, the diameter of the pores in the porous medium is below 1 micrometer.
- In some embodiments, the porous medium contains at least 10% liquid contents.
- In some embodiments, the porous medium has a modulus of rigidity of at least 10 GPa at 25° C.
- In some embodiments, the porous medium comprises a metal.
- In some embodiments, the nebulizer further comprises a chamber and a path, wherein the path is configured to receive the aerosol from the porous medium and transfer said aerosol to the chamber.
- In some embodiments, the nebulizer further comprises means configured for creating a pressure drop between the two flat sides of the porous medium, said means are selected from a piston and a spring, and a vacuum pump. In some embodiments, the means for creating the pressure drop include a piston and a spring connected to the piston, and wherein said means are configured to generate at least two different magnitudes of said pressure drop.
- In some embodiments, the nebulizer further comprises a fixture, the fixture comprises a fixture notch, wherein the piston comprises a plurality of piston slots, wherein the fixture notch is configured to adapt to any one of the plurality of piston slots, thereby compressing the spring at a plurality of heights.
- In some embodiments, the liquid comprises a pharmaceutical composition.
- In some embodiments, the porous medium is disposable.
- In some embodiments, the pressure drop is within the range of 600 to 900 mbar.
- In some embodiments, the aerosol is ultra-fine highly concentrated aerosol comprising at least 109-1011 droplets per cm3.
- In some embodiments, there is provided a method for treating a disease or disorder related to the respiratory system in a subject in need thereof, comprising, administering to the subject a pharmaceutical composition for treatment of said disease or disorder by inhalation, using the nebulizer disclosed herein.
- In some embodiments, the diameter of the pores of the porous medium is below 1 micrometer.
- In some embodiments, there is provided a method for producing aerosol, comprising the steps of
- providing the nebulizer disclosed herein; and
- generating a pressure drop across the porous medium, thereby obtaining aerosol.
- In some embodiments, the nebulizer further comprises a mouthpiece.
- In some embodiments, the nebulizer further comprises a chamber and a path, and the method further comprising the steps of
- transferring the aerosol from the porous medium and to the chamber through the path; and
- storing the aerosol in the chamber.
- In some embodiments, the method further comprises the step of positioning the mouthpiece in a position that exposes the aerosol in the chamber to the outer environment.
- In some embodiments, there is provided a method for producing aerosol, comprising the steps of
- providing the nebulizer as disclosed herein, the nebulizer comprise means for creating the pressure drop include a piston and a spring connected to the piston, and wherein said means are configured to generate at least two different magnitudes of said pressure drop, and further comprises a fixture, the fixture comprises a fixture notch, wherein the piston comprises a plurality of piston slots, wherein the fixture notch is configured to adapt to any one of the plurality of piston slots, thereby compressing the spring at a plurality of heights;
- electing a piston slot from the plurality of piston slots;
- engaging the fixture notch with the elected piston slot, thereby compressing the spring to a height corresponding to said piston slot, generating a pressure drop across the porous medium (by releasing the fixture notch from the piston slot) and producing aerosol, wherein the pressure drop being proportional to the height of the elected piston slot.
- Certain embodiments of the present disclosure may include some, all, or none of the above advantages. One or more technical advantages may be readily apparent to those skilled in the art from the figures, descriptions and claims included herein. Moreover, while specific advantages have been enumerated above, various embodiments may include all, some or none of the enumerated advantages.
- In addition to the exemplary aspects and embodiments described above, further aspects and embodiments will become apparent by reference to the figures and by study of the following detailed descriptions.
- Examples illustrative of embodiments are described below with reference to figures attached hereto. In the figures, identical structures, elements or parts that appear in more than one figure are generally labeled with a same numeral in all the figures in which they appear. Alternatively, elements or parts that appear in more than one figure may be labeled with different numerals in the different figures in which they appear. Dimensions of components and features shown in the figures are generally chosen for convenience and clarity of presentation and are not necessarily shown in scale. The figures are listed below.
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FIG. 1 schematically illustrates a cross section of a porous medium, in accordance with some embodiments; -
FIG. 2a schematically illustrates a cross-section of a nebulizer with a porous medium, in accordance with some embodiments; -
FIG. 2b schematically illustrates a cross-section of a nebulizer with a porous medium, in accordance with some embodiments; -
FIG. 2c schematically illustrates a cross-section of a nebulizer with a porous medium, in accordance with some embodiments; -
FIG. 2d schematically illustrates a cross-section of a nebulizer with a porous medium, in accordance with some embodiments; -
FIG. 3 schematically illustrates a cross-section of a nebulizer with a porous medium, in accordance with some embodiments. - In the following description, various aspects of the disclosure will be described. For the purpose of explanation, specific configurations and details are set forth in order to provide a thorough understanding of the different aspects of the disclosure. However, it will also be apparent to one skilled in the art that the disclosure may be practiced without specific details being presented herein. Furthermore, well-known features may be omitted or simplified in order not to obscure the disclosure.
- The proposed technology is intended for creating ultra-fine aerosol, which is specifically beneficial for delivering pharmaceutically active ingredients to the lungs, including the alveoli, of a subject in need of a treatment to their respiratory system, through inhalation. Generally, the formation of ultra-fine aerosol (typically, 0.3 to 1.1 micrometer of droplet size of the aerosol) is achieved by using rigid porous material into which a liquid comprising the pharmaceutically active ingredients, is partially adsorbed. The porous medium acts as a pneumatic multi-nozzle atomizing system.
- In some embodiments, there is provided a nebulizer for producing aerosol, comprising a porous medium, wherein the porous medium is rigid, has two flat sides and further comprises: a plurality of pores; a liquid partially adsorbed in the porous medium; and gas, wherein the gas is caged in pores that are vacant of said liquid, and wherein the porous medium is configured to act as a pneumatic multi-nozzle atomizing system.
- The nebulizer disclosed herein may function as an inhaler under some circumstances. Thus, the terms ‘nebulizer’ and ‘inhaler’ as used herein may be interchangeable.
- Advantageously, the nebulizer disclosed herein prevents accumulation or formation “dead” volume of atomized liquid, during aerosol generation, which cannot be sprayed as aerosol.
- An additional benefit of the nebulizer disclosed herein is that it may be used (held) in any orientation, during its operation. The formation of aerosol in the required dosage is not affected by the position or orientation of the nebulizer, during usage.
- Furthermore, unlike use of a mask, tent or any disperser, use of the nebulizer disclosed herein does not involve medicine leakage. Thus, use of the nebulizers disclosed herein is safer and effective to the patients and the environment.
- Another advantage conferred by use of the nebulizer is that no heating nor ultrasonic energy is required for its operation. Thus, the nebulizer is safe and effective for any pharmaceuticals, including heat/radiation sensitive pharmaceutical compositions.
- In some embodiments, the nebulizer is configured to deliver the aerosol to the lungs by inhalation. In some embodiments, the nebulizer is configured to deliver the aerosol to a subject's lungs by inhalation. In some embodiments, the nebulizer is configured to prevent substantially the delivery of the aerosol to subject's nose and/or throat.
- The correlation between droplet size and deposition thereof in the respiratory system has been established. It is generally known in the art that large droplets which are intended for delivery of therapeutics to the nose and throat, and not to the lungs, should be in the size of above 5 micrometers in diameter (see, for example, Natural Ventilation for Infection Control in Health-Care Settings, Atkinson et al. World Health Organization 2009, p. 103 lines 15-18). Droplets around 10 micron in diameter are suitable for deposition in the oropharynx and the nasal area; while droplets around 2-4 micron in diameter are suitable for deposition in the central airways, including the lungs, alveoli, bronchi and alveolar ducts. As a result, a nebulizer configured for producing aerosol having a diameter lower than 5 micrometer may enhance lung congestion at the expense of delivery to the nose and/or throat.
- As used herein, the term “respiratory system” refers to the system of organs in the body responsible for the intake of oxygen and the expiration of carbon dioxide. The system generally includes all the air passages from the nose to the pulmonary alveoli. In mammals it is generally considered to include the lungs, bronchi, bronchioles, trachea, nasal passages, and diaphragm.
- In some embodiments, the aerosol comprises droplets. In some embodiments, the aerosol comprises droplets of the liquid. In some embodiments, the nebulizer produces the aerosol from the liquid.
- It was found that nebulization of liquids using nebulizers as disclosed herein, results in droplets having a mass median aerodynamic diameter (MMAD) sufficiently small so as to reach the lungs, rather than precipitate on their way thereto. The small droplets reaching the lungs enable efficient respiratory delivery of therapeutic agents in the aerosolized liquid. This is an overall advantage as maximizing the delivery of therapeutic agents to the lungs, while minimizing their deposition in the mouth and throat are important in treating diseases or disorders related to the respiratory system.
- The terms ‘droplet size’ and ‘mass median aerodynamic diameter’, also known as MMAD, as used herein are interchangeable. MMAD is commonly considered as the median particle diameter by mass. MMAD may be evaluated by plotting droplet size vs. the cumulative mass fraction (%) in the aerosol. MMAD may then be determined according to the interpolated droplet size corresponding to the point, where the cumulative mass fraction is 50%. This point represents the estimated values of particle sizes, above which the droplets are responsible to half to masses and below, which the droplets are responsible to the other halves, in each solution.
- In some embodiments, the MMAD is within the range of 2 to 10 microns. In some embodiments, the aerosol comprises droplets having an MMAD of less than 10 microns. In some embodiments, the aerosol comprises droplets having an MMAD within the range of 0.3 to 7 microns. In some embodiments, the MMAD is less than 5 microns.
- In some embodiments, the diameter of the droplets is in the range 0.1 to 2.5 micrometer. In some embodiments, the diameter of the droplets is in the range 0.1 to 1.5 micrometer. In some embodiments, the diameter of the droplets is in the range 0.3 to 1.1 micrometer. In some embodiments, the diameter of the droplets is in the range 0.5 to 1.0 micrometer.
- In some embodiments, the aerosol comprises droplets having a Geometric Standard Diameter (GSD) within the range of about 0.4-7 micrometer. In some embodiments, the aerosol comprises droplets having a GSD within the range of about 2-5 micrometer.
- In some embodiments, the diameter of the pores in the porous medium is below 2 micrometer. In some embodiments, the diameter of the pores in the porous medium is below 1 micrometer. In some embodiments, the diameter of the pores in the porous medium is below 0.75 micrometer. In some embodiments, the diameter of the pores in the porous medium is below 0.5 micrometer. In some embodiments, the diameter of the pores in the porous medium is below 0.25 micrometer. In some embodiments, the diameter of the pores in the porous medium is below 0.1 micrometer.
- The term “partially absorbed” as used herein refers to the percentage of liquid absorbed in the pores of the porous medium, wherein 0% refers to a porous medium where all of its pores are vacant of liquid. Thus, the term “partially absorbed” may refer to a porous medium wherein at least 0.005% of the pores contain liquid, or wherein the overall contents of the vacant space within the porous medium occupied with liquid is 0.005%. In some embodiments, partially absorbed refers to at least 0.001% liquid contents within the porous medium. In some embodiments, partially absorbed refers to at least 0.05% liquid contents within the porous medium. In some embodiments, partially absorbed refers to at least 0.01% liquid contents within the porous medium. In some embodiments, partially absorbed refers to at least 0.5% liquid contents within the porous medium. In some embodiments, partially absorbed therein refers to at least 0.1% liquid contents within the porous medium. In some embodiments, partially absorbed refers to at least 1% liquid contents within the porous medium. In some embodiments, partially absorbed refers to at least 5% liquid contents within the porous medium. In some embodiments, partially absorbed refers to at least 10% liquid contents within the porous medium. In some embodiments, partially absorbed refers to at least 20% liquid contents within the porous medium. In some embodiments, partially absorbed refers to at least 30% liquid contents within the porous medium. In some embodiments, partially absorbed refers to at least 40% liquid contents within the porous medium. In some embodiments, partially absorbed refers to at least 50% liquid contents within the porous medium.
- In some embodiments, the term “partially absorbed” may refer to the content of liquid within the volume of pores located on the surface and in the immediate vicinity of the surface (sub surface) of a porous medium. In some embodiments, the volume of the sub-surface may extend from the surface to a depth of about 50 micron from the surface.
- In some embodiments, partially absorbed refers to a porous medium wherein at least 0.5% of the surface and sub-surface pores contain liquid. In some embodiments, partially absorbed refers to at least 1% liquid contents within the surface and sub-surface pores. In some embodiments, partially absorbed refers to at least 10% liquid contents within the surface and sub-surface pores. In some embodiments, partially absorbed refers to at least 20% liquid contents within the surface and sub-surface pores. In some embodiments, partially absorbed refers to at least 30% liquid contents within the surface and sub-surface pores. In some embodiments, partially absorbed refers to at least 40% liquid contents within the surface and sub-surface pores. In some embodiments, partially absorbed refers to at least 50% liquid contents within the surface and sub-surface pores. In some embodiments, partially absorbed refers to at least 60% liquid contents within the surface and sub-surface pores.
- In some embodiments, the porous medium is rigid when liquid is partially adsorbed therein.
- The term “rigid” as used herein characterizes materials that are generally non-flexible, and do not undergo deformation in response to an applied force. Specifically, a porous medium that is rigid, does not bend or otherwise deforms upon ejection of liquid droplets therethrough. Rigidity is typically measured in pressure units, through parameters such as Modulus of Rigidity (G; Shear Modulus) or Young's modulus. Rigidity of materials may be dependent on environments features. For example, cellulose may exhibit a rigid structure in a dry form, however, when adsorbed in liquid cellulose cannot maintain a dry rigid structure, but rather becomes flexible. Glass and most metals are rigid in a wide range of temperature, including at room temperature, but become flexible in extremely high temperatures.
- In some embodiments, the rigid porous medium does not substantially change its rigidity upon adsorption of liquids therein. In some embodiments, the rigidity of the rigid porous medium is not substantially effected upon being in contact with liquids.
- In some embodiments, porous medium is made of a rigid material, wherein the rigidity of the rigid material is not substantially effected by contact with liquids.
- In some embodiments, the porous medium has a modulus of rigidity of at least 10 GPa (109 pascal) at 25° C. In some embodiments, the porous medium has a modulus of rigidity of at least 15 GPa at 25° C. In some embodiments, the porous medium has a modulus of rigidity of at least 20 GPa at 25° C. In some embodiments, the porous medium is substantially devoid of materials having modulus of rigidity lower than 10 GPa at 25° C.
- As used herein, the terms “substantially effected” and “substantially change”, when referring to the rigidity of materials, are intended to include changes of more than 10% in the modulus of rigidity of the material. For example, for a dry porous medium having a modulus of rigidity of 50 GPa, the phrase “the rigidity of the porous medium is not substantially effected by contact with liquids” means that upon contact with liquids, the modulus of rigidity of the material will remain in the range of 45 GPa to 55 GPa.
- In some embodiments, the porous medium is made of a material selected from the group consisting of metals and metal alloys. In some embodiments, the porous medium comprises a metal. In some embodiments, the porous medium is made of metal. In some embodiments, the porous medium comprises polymers.
- It is to be understood that a polymer used for forming the porous medium is typically a rigid polymer, such as, a polymer having a Tg (glass transition temperature) in the range of 100 or above 100.
- In some embodiments, the porous medium comprises materials selected from the group consisting of aluminum, cobalt, copper, iron, magnesium, nickel, silicon, steel, titanium, polymers, including alloys and combinations thereof.
- In some embodiments, the porous medium is rigid and has two flat sides. It is to be understood that, due to the rigidity of the porous medium, it remains flat throughout the operation of the nebulizer. As defined above, a rigid medium is resistant to deformation upon application of external force. Therefore, the medium does not curve into a concave or convex shape, rather it remains flat during operation of the nebulizer, and specifically, during formation of aerosol.
- In some embodiments, the nebulizer further comprises a chamber and a path, wherein the path is configured to receive the aerosol from the porous medium and transfer said aerosol to the chamber.
- In some embodiments, the nebulizer further comprises an outlet, also referred to as exit hole. In some embodiments, the outlet is configured to release said aerosol by inhalation. In some embodiments, the outlet is configured to deliver said aerosol to the lungs by inhalation.
- In some embodiments, the nebulizer further comprises a cover configured to fix the porous medium to the body of the nebulizer.
- In some embodiments, the cover further comprises a duct extended between the cover and the external environment.
- In some embodiments, the duct is open, such that the internal environment of the nebulizer is exposed to the atmospheric pressure. Without being bound by any theory or mechanism, by maintaining the duct open, the internal pressure within the nebulizer reaches a steady state of atmospheric pressure.
- In some embodiments, the nebulizer further comprises means for creating a pressure drop between the two flat sides of the porous medium. In some embodiments, the nebulizer further comprises an element configured for creating a pressure drop between the two flat sides of the porous medium. In some embodiments, the element comprises a piston and a spring. In some embodiments, the element further comprises a vacuum pump. In some embodiments, the element further comprises a piston, a spring and vacuum pump.
- In some embodiments, creating a pressure drop between the two flat sides of the porous medium is achieved by introducing pressurized air to one flat side of the porous medium. In some embodiments, creating a pressure drop between the two flat sides of the porous medium comprises introducing vacuum or sub-atmospheric pressure near one flat side of the porous medium. In some embodiments, creating a pressure drop between (or across) the two flat sides of the porous medium comprises generating or having a pressure difference between the two flat sides (or flat surfaces) of the rigid porous medium. In some embodiments, the pressure difference is in the range of 600 mbar to 900 mbar.
- In some embodiments, prior to the pressure drop, the pressure across the porous medium is an atmospheric pressure. In some embodiments, the pressure drop across the porous medium is within the range of 500 to 990 mbar. In some embodiments, the pressure drop is within the range of 600 to 900 mbar. In some embodiments, the pressure drop is within the range of 650 to 850 mbar.
- In some embodiments, the porous medium is in a shape of a disc.
- In some embodiments, the porous medium is in a shape of a pill.
- In some embodiments, the porous medium is in a shape of a coin.
- In some embodiments, the porous medium is in a shape of a cylinder.
- In some embodiments, the nebulizer further comprises a tube connecting the chamber to said duct and configured to increase the pressure drop between the two flat sides of the porous medium.
- In some embodiments, the nebulizer further comprises a fixture and a piston connected to a spring, the fixture comprising a fixture notch, and the piston comprising at least two piston slots located at different levels along the piston. In some embodiments, the fixture is connected to the peripheral surface of the outer structure, optionally through a joint, wherein the joint serves as a rotation axis and one end of the fixture is further attached to the peripheral surface of the outer structure in order to force the other end of the fixture, comprising the fixture notch, to be engaged with any one of the piston slots. In some embodiments, applying pressure to the fixture at the region of the fixture spring causes the fixture to rotate against the joint, thereby releasing (displacing) the fixture notch from any one of the piston slots. In some embodiments, the displacement of the fixture notch releases the spring along a given height, depending on the piston slot from which the fixture notch has been released. Thus, displacement of the fixture notch can release the spring along various heights, thereby generating different magnitudes of pressure drop across the porous medium for, depending on the position (level or height relative to the dimension of the nebulizer) of the piston slot. The terms “height” and “heights” as used herein generally refer to the distance between the bottom of the nebulizer's body (also termed
outer structure 101 inFIGS. 2a-2d ) and the piston. - In some embodiments, the liquid comprises water. In some embodiments, the liquid comprises an aqueous pharmaceutically suitable carrier and at least one pharmaceutical active ingredient. In some embodiments, the liquid comprises an aqueous dispersion. In some embodiments, the liquid comprises any one of an aqueous solution, an aqueous emulsion, an aqueous suspension and an aqueous colloidal suspension.
- In some embodiments, the liquid comprises a pharmaceutical composition.
- As used herein, the term “pharmaceutical composition” is interchangeable with any of the terms “medication”, “drug” and the like, refers to a preparation of a composition comprising one or more pharmaceutically active agents, suitable for administration to a patient via the respiratory system.
- In some embodiments, the liquid comprises a therapeutically effective amount of a pharmaceutical composition. In some embodiments, the liquid comprises a pharmaceutical composition for treatment or prevention of a disease or disorder of the respiratory system.
- In some embodiments, the aerosol comprises a pharmaceutical composition. In some embodiments, the aerosol comprises a therapeutically effective amount of the pharmaceutical composition. In some embodiments, the aerosol comprises a pharmaceutical composition for treatment or prevention of a disease or disorder of the respiratory system.
- As used herein, the term “therapeutically effective amount” refers to a pharmaceutically acceptable amount of the pharmaceutical composition, or the pharmaceutical active ingredient(s), which prevents or ameliorates, at least partially, the symptoms signs of a particular pulmonary or respiratory disease or disorder, in a living organism to whom it is administered over some period of time.
- In some embodiments, the pharmaceutical composition is for the treatment of a respiratory disease or disorder. In some embodiments, the disease or disorder is selected from the group consisting of asthma, bronchitis, emphysema, lung infection, cystic fibrosis, AAT deficiency, COPD, ARDS, IRDS, BPD, and MAS. Each possibility is a separate embodiment of the invention.
- In some embodiments, the disease or disorder is affecting the airways, the alveoli or the interstitium, such as, asthma, chronic obstructive pulmonary disease, chronic bronchitis, emphysema, acute bronchitis, cystic fibrosis, pneumonia, tuberculosis, fragile connections between alveoli, pulmonary edema, lung cancer in its many forms, acute respiratory distress syndrome, pneumoconiosis, mouth and pharynx cancer, tracheal tumors and interstitial lung disease among others.
- As used herein the term “aerosol” or “aerosolized agent” refers to a suspension of solid or liquid particles of the agent in a gas. As used herein “aerosol” or “aerosolized agent” may be used generally to refer to an agent, including, a pharmaceutically active agent, that has been vaporized, nebulized, or otherwise converted from a solid or liquid form to an inhalable form including suspended solid or liquid drug particles.
- In some embodiments, the liquid further comprises at least one pharmaceutical acceptable carrier. In some embodiments, the liquid may further comprise one or more stabilizers.
- In some embodiments, the liquid further comprises a sweetener. In some embodiments, the sweetener is selected from the group of artificial sweeteners including saccharine, aspartame, dextrose and fructose.
- In some embodiments, the liquid further comprises at least one anti-coughing agent.
- The term “anti-coughing agent” as used herein refers to an active agent used for the suppression, alleviation or prevention of coughing and irritations and other inconveniencies in the large breathing passages that can, or may, generate coughing. Anti-coughing agent include, but are not limited to antitussives, which are used for which suppress coughing, and expectorants, which alleviate coughing, while enhancing the production of mucus and phlegm. Anti-coughing agents may ease the administration of inhaled aerosols.
- In some embodiments, the at least one anti-coughing agent is selected from expectorants, antitussives or both. In some embodiments, the at least one anti-coughing agent is selected from the group consisting of menthol, dextromethorphan, dextromethorphan hydrobromide, hydrocodone, caramiphen, dextrorphan, 3-methoxymorphinan or morphinan-3-ol, carbetapentane, codeine, acetylcysteine and combinations thereof.
- In some embodiments, the liquid further comprises at least one preservative. In some embodiments, the preservative is selected from the group consisting of benzyl alcohol, propylparaben, methylparaben, benzalkonium chloride, phenyl ethyl alcohol, chlorobutanol, potassium sorbate, phenol, m-cresol, o-cresol, p-cresol, chlorocresol and combinations thereof.
- In some embodiments, the porous medium is disposable.
- In some embodiment, the porous medium is configured to multiple uses. It is to be understood, that multiple use may require washing the porous medium between uses.
- In some embodiments, the nebulizer is mobile. In some embodiments, the nebulizer is portable. In some embodiments, the nebulizer is handheld. In some embodiments, the nebulizer is powered by a mobile power source.
- In some embodiments, the nebulizer is configured to communicate with servers, databases, personal devices (computers, mobile phones) among others.
- In some embodiments, the nebulizer is configured to communicate wirelessly with servers, databases, personal devices (computers, mobile phones) among others.
- In some embodiments, the nebulizer further comprises at least one tubular opening, also termed herein “mouthpiece” configured to deliver the aerosols to a respiratory system of a subject, and an outer structure opening configured to expose the contents of the chamber to the mouthpiece. In some embodiments, the mouthpiece extends outwardly from the lower peripheral surface of the outer structure towards the environment outside the nebulizer, or towards the user. In some embodiments, the mouthpieces is, configured to rotate around said peripheral surface from a first opening position to a second opening position. In first opening position the mouthpiece is positioned against a wall of the outer structure, where in second opening position the mouthpiece is positioned against the outer structure opening. In first opening position, both the mouthpiece and the outer structure opening are blocked, such that the mouthpiece is exposed to the outer environment but blocked by the wall of the outer structure to the contents of the chamber. Similarly, the outer structure opening is blocked from the outer environment. Blocking of the outer structure can be, for example by means of a ring. In some embodiments, the ring is connected to the mouthpiece and is configured to rotate around the periphery of the outer structure, the ring being open only at the region of connection with the mouthpiece. In the second opening position, the aerosol contained within the chamber is exposed, through the outer structure opening, followed by the mouthpiece, to the outer environment.
- In some embodiments there is provided a method of delivering a pharmaceutical composition to a subject by inhalation, the method comprising administering the pharmaceutical composition to the subject using the nebulizer disclosed herein.
- In some embodiments there is provided a method of delivering a pharmaceutical composition to a subject in need thereof by inhalation, the method comprising administering the pharmaceutical composition to the subject using the nebulizer disclosed herein.
- In some embodiments, administering the pharmaceutical composition to the subject comprises delivering the pharmaceutical composition in the form of aerosols to the respiratory system of the subject.
- In some embodiments, the subject in need thereof is a subject afflicted with respiratory disease or disorder.
- In some embodiments there is provided a porous medium configured to act as a pneumatic multi-nozzle atomizing system, wherein the porous medium is rigid, has two flat sides and further comprises a plurality of pores; a liquid partially adsorbed in the porous medium; and gas, wherein the gas is caged in pores that are vacant of said liquid.
- In some embodiments, the porous medium is configured to release an aerosol. In some embodiments, the aerosol comprises droplets. In some embodiments, the aerosol comprises droplets of the liquid.
- In some embodiments, the MMAD is within the range of 2 to 10 microns. In some embodiments, the aerosol comprises droplets having an MMAD of less than 10 microns. In some embodiments, the aerosol comprises droplets having an MMAD within the range of 0.3 to 7 microns. In some embodiments, the MMAD is less than 5 microns. In some embodiments, the diameter of the droplets is in the range 0.1 to 2.5 micrometer. In some embodiments, the diameter of the droplets is in the range 0.1 to 1.5 micrometer. In some embodiments, the diameter of the droplets is in the range 0.3 to 1.1 micrometer. In some embodiments, the diameter of the droplets is in the range 0.5 to 1.0 micrometer. In some embodiments, the aerosol comprises droplets having a Geometric Standard Diameter (GSD) within the range of about 0.4-7 micrometer. In some embodiments, the aerosol comprises droplets having a GSD within the range of about 2-5 (two to five) micrometer.
- In some embodiments, the porous medium is in a flat shape selected from the group consisting of: cylinder, ring, disc and coin.
- In some embodiments, the liquid comprises a pharmaceutical composition. In some embodiments, the aerosol comprises a pharmaceutical composition for treatment of a disease or disorder of the respiratory system. In some embodiments, the pharmaceutical composition is intended for delivery to the lungs.
- In some embodiments, there is provided a method for producing ultra-fine highly concentrated aerosol, comprising providing the nebulizer disclosed herein and inducing a pressure drop between the two flat sides of the porous medium, thereby producing aerosol.
- In some embodiments, inducing a pressure drop between the two flat sides of the porous medium comprises introducing pressurized air to one flat side of the porous medium.
- In some embodiments, inducing a pressure drop between the two flat sides of the porous medium comprises introducing vacuum or sub-atmospheric pressure near one flat side of the porous medium.
- In some embodiments, inducing a pressure drop between the two flat sides of the porous medium comprises connecting the nebulizer to a pump.
- In some embodiments, inducing a pressure drop between the two flat sides of the porous medium comprises displacing the piston. In some embodiments, inducing a pressure drop between the two flat sides of the porous medium comprises manually displacing the piston. In some embodiments, the outer structure includes an elongated slot through which an extension arm, connected to the piston, protrudes outwardly. In some embodiments the extension arm is displaced in the elongated direction along the outer structure, such that manual displacement of said extension arm, for example by the user's hand, in the upward or downward direction, displaces the piston located in the chamber of the outer structure in the same direction. In that manner, after the release of the piston and its movement downward by the force exerted by the spring, as described hereinabove, the user is able to manually push the extension arm upwards while compressing the fixture spring, releasing the fixture when the fixture notch is placed against the desired height level of the piston slot, rendering the nebulizer ready for reuse.
- The term “concentrated aerosol” as used herein refers to the number of droplets per volume unit. Concentrated aerosols include more than 108 droplets per cm3. Highly concentrated aerosol includes more than 109 droplets per cm3.
- In some embodiments, the aerosol includes more than 109 droplets per cm3. In some embodiments, the aerosol includes more than 109-1011 droplets per cm3.
- In some embodiments, inducing the pressure drop is achieved by inducing a pressure drop on one side of said two flat sides of the porous medium.
- In some embodiments, inducing the pressure drop is achieved by vacuum generating means comprising a piston.
- In some embodiments, pressure drop across the porous medium is within the range of 500 to 990 mbar; 600 to 900 mbar; or 650 to 850 mbar.
- In some embodiments, the method further comprises storing the aerosol in the chamber.
- In some embodiments, the method further comprises storing the aerosol in the chamber under vacuum.
- In some embodiments, the aerosol is transferred under vacuum in the chamber for storage.
- Reference is now made to
FIG. 1 , which schematically illustrates a cross section ofporous medium 102.Porous medium 102 comprises rigid porous material 1, pores 2,liquid 3 and gas 4, according to some embodiments. -
Liquid 3 is contained within some of pores 2 ofporous medium 102, according to some embodiments. It is intended for spraying from a nebulizer, such asnebulizer 100 ofFIGS. 2a-2d , which includesporous medium 102, according to some embodiments.Liquid 3 is partially absorbed in porous material 1, according to some embodiments.Liquid 3 includes an aqueous pharmaceutical composition, comprising medication for the treatment of a pulmonary disease, and is intended for spraying through a nebulizer into the lungs, according to some embodiments. - Pores 2 are being cavities within rigid porous material 1, according to some embodiments. Pores 2 are of sub-micron size, i.e. their median diameter is below 1 micrometer, according to some embodiments. Pores 2 are partially adsorbed by
liquid 3 and partially filled with gas 4, according to some embodiments. Pores 2 are acting as nozzles, according to some embodiments. - Gas 4 is caged in some of pores 2, which are vacant of
liquid 3, according to some embodiments. - Porous material 1 form the body of
porous medium 102, according to some embodiments. It is a rigid metallic material, which is shaped as a coin, according to some embodiments. Porous material 1 has structure and dimensions, which are determined according to the required aerosol characteristics for each required application, according to some embodiments. For example, the dispersing area of porous material 1 (i.e. the surface area, or one side, of porous material 1) determines the quantity of achieved aerosol. The greater the surface area, the more aerosol is produced, per use. Reference is now made toFIGS. 2a-2d , which schematically illustrate cross-sectional views of anebulizer 100 comprisingporous medium 102, according to some embodiments. Specifically,FIGS. 2a-c illustratenebulizer 100 comprisingporous medium 102, in different stages:FIGS. 2a-2b illustratenebulizer 100 comprisingporous medium 102 prior to aerosol production, in a first optional compressed position and a second optional compressed position, respectively;FIG. 2c illustratesnebulizer 100 comprisingporous medium 102 whennebulizer 100 is in aerosol production position, due to the pressure drop generated between upperflat side 102 b and lowerflat side 102 a of theporous medium 102; andFIG. 2d describesnebulizer 100 comprisingporous medium 102 in a position that enables aerosol inhalation. -
Nebulizer 100 is configured to transform liquid 3 to an aerosol, according to some embodiments. The aerosol spraying is performed by instantaneously inducing pressure drop across the thickness ofporous medium 102, according to some embodiments. Sinceporous medium 102 is has a thickness and two flat sides, the differential pressure occurs between the two flat sides ofporous medium 102, according to some embodiments. Whenporous medium 102 is in atmospheric pressure, a pressure drop is induced acrossporous medium 102, creating a low pressure at one side ofporous medium 102, compared to the atmospheric pressure on the other side ofporous medium 102, according to some embodiments. According to some embodiments, the size of the pressure drop may be in the range of 600 to 900 mbar.Nebulizer 100 being under a pressure drop acrossporous medium 102 is illustrated inFIG. 2c . At this stage, atomization occurs as a result of the pressure difference across the two sides ofporous medium 102, according to some embodiments. The pressure difference causes the medium to act as a pneumatic multi-nozzle, where the nozzles are defined by pores 2 ofporous medium 102, according to some embodiments. - Without wishing to be bound by any theory or mechanism of action, the effect of pneumatic multi-nozzle atomization is the result of gas 4, which is caged in the internal volume of
porous medium 102, being released in the direction of vacuum or low pressure. Gas 4 release causes pores 2 to act as nozzles andspray liquid 3 outsideporous medium 102. The aerosol is then achieved on the side of the lower pressure—bottomflat side 102 a, as illustrated inFIG. 2a . This mechanism of nebulizing action does not require an external gas supply in order to achieve aerosol formation. - The pressure drop is the result of the difference between an atmospheric pressure above
porous medium 102 and the lower pressure generated in the chamber belowporous medium 102, also referred to as aerosol accumulator, orvacuum accumulator 101 a.Vacuum accumulator 101 a is also used for storing the aerosol, after being produced, until the aerosol is required for use (i.e. inhalation), according to some embodiments. - According to some embodiments, the low pressure generated in the aerosol accumulator (
vacuum accumulator 101 a) is sub-atmospheric pressure. - According to some embodiments, the low pressure generated in aerosol accumulator (
vacuum accumulator 101 a) is vacuum or negative pressure. -
Vacuum accumulator 101 a may also be used as a drying chamber depending on the relation between the volume ofaccumulator 101 a and the quantity of the droplets, and further depending on the overall parameters of the environment insidevacuum accumulator 101 a, according to some embodiments. Such parameters include temperature and pressure. Upon usingchamber 101 a for drying, dry aerosol is obtained bynebulizer 100, according to some embodiments. - In addition, drying process can take place by the act of inhalation itself, when the inhaled air acts as drying agent, according to some embodiments.
- Nebulizers comprising
porous medium 102, such asnebulizer 100, operate in many different environments and any positions, such as, in an upright and horizontal position, according to some embodiments. - According to some embodiments,
nebulizer 100 may be self-sustained, i.e. the pressure drop is created inherently and not by connectingnebulizer 100 to a pump. - Porous medium 102 may also be used as a storage container for
liquid 3 prior to the conversion ofliquid 3 to aerosol, according to some embodiments. Porous medium 102 as a storage container may include porous medium 102 soaked with a pre-determined quantity ofliquid 3, according to some embodiments. - According to some embodiments,
porous medium 102 is soaked with a pre-determined quantity ofliquid 3, forming a ready for use “pill”. According to some embodiments, the pill is hermetically and sterilely sealed and packed. - According to some embodiments,
porous medium 102 is packed together with acontainer containing liquid 3, where in between porous medium 102 and the container, there is a buffer layer impermeable to liquids. This packing forms a “sandwich” like device. Upon removal of the buffer layer,porous medium 102 absorbs liquid 3. According to some embodiments, removal of the buffer layer from the sandwich pack is performed prior to use ofnebulizer 100 orporous medium 102, i.e. before the atomizing effect takes place in order to perform aerosol. - According to some embodiments, the sandwich is sealed and packed. In some embodiments, the sandwich is disinfected and sterilized prior to being sealed and packed.
- According to some embodiments,
porous medium 102 is designed to be used with specific nebulizer devices, and may be adapted to use with any nebulizer, if required. - According to some embodiments,
porous medium 102 is disposable. - According to some embodiments,
porous medium 102 is configured for multiple uses. According to some embodiments,porous medium 102 is configured for discharge of, and replenishment with,liquid 3. - According to some embodiments,
nebulizer 100 further comprises anouter structure 101.Outer structure 101 encompassesvacuum accumulator 101 a. The dimensions ofvacuum accumulator 101 a are determined according to the volume of aerosol required for each application. According to some embodiments, to produce 30 mg of medical aerosol for local delivery to the lung or systematic delivery through the lung, a volume of at least 30 cc is required.Vacuum accumulator 101 a has apath 101 b through which the aerosol received fromporous medium 102 entersvacuum accumulator 101 a. -
Nebulizer 100 further comprise a mouth-piece, also termed opening orexit hole 103, astructure opening 101 d,cylinder piston 104,spring 105,cover 106 andduct 106 b, according to some embodiments.Exit hole 103 is utilized for aerosol inhalation by a user when it is positioned against thestructure opening 101 d (seeFIG. 2d ).Exit hole 103 is blocked when it is positioned against an external wall of the outer structure 101 (seeFIGS. 2a-2c ). According to some embodiments, a vacuum or a low-pressure effect can be generated externally by a vacuum pump (e.g., for stationary use) or by an internal device included in the nebulizer itself. According to some embodiments,cylinder piston 104 is attached tospring 105, thereby displaced from one position whereinspring 105 is compressed (seeFIGS. 2a-2b ) to other positions, towards the bottom ofouter structure 101, whenspring 105 is released (seeFIG. 2c ). This movement ofcylinder piston 104 results in a desired pressure drop, due to the vacuum or sub-atmospheric pressure generated invacuum accumulator 101 a, needed for aerosol production, according to some embodiments. The upper side ofnebulizer 100 comprises a grove (not numbered) configured for placement ofporous medium 102, according to some embodiments.Porous medium 102 is fixed or sealed to the device bycover 106, designed for fast opening/closing, according to some embodiments. Cover 106 hasduct 106 b extended betweencover 106 and the external environment, according to some embodiments. - According to some embodiments,
porous medium 102 may be located in any position withinnebulizer 100. According to some embodiments,porous medium 102 is located at the upper side of nebulizer 100 (as shown inFIGS. 2a-2c ) but can also be located on the opposite (bottom side) or in any side ofnebulizer 100. -
FIG. 2a showsnebulizer 100 prepared for generation of aerosol, in accordance with some embodiments.Fixture 108 includes notch 108 a. The formation ofnotch 108 a enablesfixture 108 to be engaged withpiston slot 104 a in such a manner thatpiston 104 is maintained in a first optional compressed position. In this first optional position,spring 105 is compressed such that the distance between the lower edge ofpiston 104 and the bottom ofvacuum accumulator 101 a is H1.Porous medium 102 is fixed tonebulizer 100 bycover 106; andexit hole 103 is blocked byouter structure 101. -
FIG. 2b showsnebulizer 100 prepared for generation of aerosol, in accordance with some embodiments.Notch 108 a is engaged withpiston slot 104 b in such a manner thatpiston 104 is maintained in a second optional compressed position. In this second optional position,spring 105 is compressed such that the distance between the lower edge ofpiston 104 and the bottom of thevacuum accumulator 101 a is H2. - It will be understood that
piston 104 ofnebulizer 100, prepared for generating aerosol, can be maintained either in first optional compressed position (seeFIG. 2a ) or in a second optional compressed position (seeFIG. 2b ), prior to the release of thespring 105. - In accordance with some embodiments, H1 and H2 are not equal. In accordance with some embodiments, H2 is longer than H1.
-
FIG. 2c showsnebulizer 100 in the instant right after the release of thefixture 108, also referred to as the stage of aerosol generation.Fixture 108 is designed as a lever, according to some embodiments, thereby configured to release notch 108 a from eitherpiston slot 104 a orpiston slot 104 b, when pressure is applied to the bottom portion offixture 108, i.e. the portion offixture 108 opposite to the location ofnotch 108 a. The displacement ofnotch 108 areleases piston 104, thereby releasingspring 105 from its compressed state, either at first optional compressed position or at second optional compressed position, to a released position. In the released position,spring 105 displacespiston 104 towards the bottom ofouter structure 101, thereby creating vacuum or sub-atmospheric pressure, invacuum accumulator 101 a. The pressure drop created acrossporous medium 102 generates aerosol withinvacuum accumulator 101 a. - While
fixture 108 illustrated inFIGS. 2a-2d is designed as a lever, it will be understood thatfixture 108 may be formed to accommodate other methods known in the art for release ofnotch 108 a by a user. - Without wishing to be bound by any theory or mechanism of action, the magnitude of pressure drop across
porous medium 102 is proportional to the initial distance between the lower edge of thepiston 104 and the bottom of thevacuum accumulator 101 a, such that if distance H2 is longer than H1, the pressure inaerosol accumulator 101 a at the instant afterspring 105 is released is lower in the case thatpiston 104 was positioned in the second optional compressed position, at height H2, compared to the case whereinpiston 104 was positioned in the first optional compressed position, at height H1. Therefore, the former results in a higher pressure drop than the later. Thus, as there are more than one optional position forpiston 104 prior to the release of spring 105 a range of different pressure drops can be generated. Thus, user ofnebulizer 100 can choose pressure drops, based on the desired parameters of the resulting aerosol, such as, but not limited to: MMAD, GSD or aerosol concentration. - While
FIGS. 2b-2c illustrate twopiston slots piston 104 may include any number of piston slots, thereby having any corresponding number of optional compressed positions, allowing an operator to choose between such positions in order to regulate the magnitude of the pressure drop acrossporous medium 102.FIG. 2d showsnebulizer 100 prepared for aerosol inhalation by a user:exit hole 103 is displaced to a position in front of structure opening 101 d, thereby exposing the contents ofaerosol accumulator 101 a to the outside environment, allowing the aerosol to be nebulized by the user. - According to some embodiments, the aerosol within aerosol accumulator (or chamber, or
vacuum accumulator 102 a) is stored in low pressure or in vacuum, whereinpositioning outlet 103 in front of structure opening 101 d (seeFIG. 2d ), exposesvacuum accumulator 101 a to the atmospheric pressure, rendering an equilibrium such that the pressure withinvacuum accumulator 101 a is atmospheric as well, prior to inhalation by the user. - According to some embodiments,
duct 106 b is kept open to the atmosphere. When low pressure is generated inaerosol accumulator 101 a at the first instant after the release of spring 105 (which is allowing generation of aerosol) air entersnebulizer 100 throughduct 106 b, creating a new equilibrium of steady state in which the pressure withinvacuum accumulator 101 a is atmospheric pressure. - Reference is now made to
FIG. 3 , which schematically illustratesnebulizer 200 comprisingporous medium 102.Nebulizer 200 is similar in function and structure tonebulizer 100, and further comprisestube 109.Tube 109 is used for supply of air during the aerosol generation stage.Tube 109 extends fromvacuum accumulator 101 a toduct 106 b, and delivers gas in that direction to increase aerosol capacity by increasing dispersing gas. - Without being bound by any theory or mechanism, introducing additional dispersing gas increases the magnitude of the pressure drop across
porous medium 102.
Claims (20)
1. A nebulizer for producing aerosol, comprising a porous medium, wherein the porous medium is rigid, has two flat sides and further comprises: a plurality of pores; a liquid partially absorbed in the porous medium; and gas, wherein the gas is caged in pores that are vacant of said liquid, wherein the porous medium is configured to act as a pneumatic multi-nozzle atomizing system.
2. The nebulizer of claim 1 , further comprising a mouthpiece configured to deliver the aerosol to the lungs of a subject by inhalation.
3. The nebulizer of claim 1 , wherein the aerosol comprises droplets of the liquid, the droplets having a mass median aerodynamic diameter (MMAD) within the range of 0.3 to 7 microns.
4. The nebulizer of claim 3 , wherein the diameter of said droplets is in a range of 0.3 to 1.1 micrometer.
5. The nebulizer of claim 1 , wherein the diameter of the pores in the porous medium is below 1 micrometer.
6. The nebulizer of claim 1 , wherein the overall contents of vacant space within the porous medium occupied with liquid is at least 10% liquid contents.
7. The nebulizer of claim 1 , wherein the porous medium has a modulus of rigidity of at least 10 GPa at 25° C.
8. The nebulizer of claim 1 , wherein the porous medium comprises a metal.
9. The nebulizer of claim 1 , further comprising a chamber and a path, wherein the path is configured to receive the aerosol from the porous medium and transfer said aerosol to the chamber.
10. The nebulizer of claim 1 , further comprising means configured for creating a pressure drop between the two flat sides of the porous medium, said means are selected from a piston and a spring, and a vacuum pump.
11. The nebulizer of claim 11 , wherein the means for creating the pressure drop include a piston and a spring connected to the piston, and wherein said means are configured to generate at least two different magnitudes of said pressure drop.
12. The nebulizer of claim 1 , wherein the liquid comprises a pharmaceutical composition.
13. The nebulizer of claim 1 , wherein the porous medium is disposable.
14. The nebulizer of claim 11 , wherein the pressure drop is within the range of 600 to 900 mbar.
15. The nebulizer of claim 1 , wherein the aerosol is ultra-fine highly concentrated aerosol comprising at least 109-1011 droplets per cm3.
16. The nebulizer of claim 1 , wherein the rigidity of the rigid porous medium is not substantially effected upon being in contact with liquids.
17. The nebulizer of claim 1 , further comprising an outer structure blocking the mouthpiece, the outer structure having a structure opening, wherein in the first position, the mouthpiece is positioned against a wall of the outer structure, and in the second opening the mouthpiece is displaced to a position in front of the structure allowing the aerosol to be nebulized and administered to the subject.
18. A method for treating a disease or disorder related to the respiratory system in a subject in need thereof, comprising, administering to the subject a pharmaceutical composition for treatment of said disease or disorder by inhalation, using the nebulizer of claim 1 .
19. The method of claim 18 , wherein the diameter of the pores of the porous medium is below 1 micrometer.
20. A method for producing aerosol, comprising the steps of
a. providing the nebulizer of claim 1 ; and
b. generating a pressure drop across the porous medium, thereby obtaining aerosol.
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Citations (16)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2284591A (en) * | 1939-11-24 | 1942-05-26 | Stanco Inc | Nebulizer |
US3046983A (en) * | 1959-10-01 | 1962-07-31 | Grubb Thomas Christman | Variable dose inhaler |
US3610480A (en) * | 1969-07-31 | 1971-10-05 | Geigy Chem Corp | Aerosol dispensing apparatus |
US3927806A (en) * | 1972-09-07 | 1975-12-23 | Philip Meshberg | Applicator for attachment to a spray mist dispenser |
US4114811A (en) * | 1977-04-12 | 1978-09-19 | Ciba-Geigy Corporation | Spray dispenser with easily actuable mouthpiece |
GB2074454A (en) * | 1980-04-24 | 1981-11-04 | Somova Spa | Inhalation device with retractible mouthpiece |
US4969455A (en) * | 1988-11-29 | 1990-11-13 | Somova S.P.A. | Inhalator for aerosol containers |
US5755221A (en) * | 1990-09-12 | 1998-05-26 | Bisgaard; Hans | Aerosol inhaler with piston dump |
US5833057A (en) * | 1997-04-28 | 1998-11-10 | Char; Aka Loka | Apparatus for packaging and shipping biological fluid samples collected in vials |
US6354516B1 (en) * | 1999-11-02 | 2002-03-12 | Aradigm Corporation | Pore structures for reduced pressure aerosolization |
US20020073991A1 (en) * | 1998-01-22 | 2002-06-20 | Igor Gonda | Formulation and devices for monitoring the efficacy of the delivery of aerosols |
US20060231090A1 (en) * | 2005-04-13 | 2006-10-19 | Russell King | Inhalation apparatus |
US20070175476A1 (en) * | 2005-12-28 | 2007-08-02 | Philip Morris Usa Inc. | Aerosol powder delivery device |
US20080216828A1 (en) * | 2007-03-09 | 2008-09-11 | Alexza Pharmaceuticals, Inc. | Heating unit for use in a drug delivery device |
US20090192443A1 (en) * | 2008-10-06 | 2009-07-30 | Collins Jr James F | Ophthalmic fluid delivery device and method of operation |
US20120318259A1 (en) * | 2010-01-12 | 2012-12-20 | Omega Life Science Ltd. | Method and apparatus for producing fine concentrated aerosol |
Family Cites Families (113)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1023063A (en) | 1911-01-03 | 1912-04-09 | Lowell C Bassford | Window-screen. |
US1132679A (en) | 1914-10-14 | 1915-03-23 | Thomas E Murray | Method of neutralizing corrosive fumes in gases. |
FR648541A (en) | 1929-01-14 | 1928-12-11 | ||
US2276878A (en) | 1940-08-22 | 1942-03-17 | Stanco Inc | Nebulizer |
US2348420A (en) | 1942-06-10 | 1944-05-09 | William H Rose | Liquid spraying device |
US3583635A (en) | 1969-02-24 | 1971-06-08 | Jerome H Lemelson | Spraying systems |
US3570038A (en) | 1969-10-22 | 1971-03-16 | Vernon F Jones | Bottle brush structure |
US3762409A (en) | 1970-11-03 | 1973-10-02 | V Lester | Nebulizer |
US3771721A (en) | 1972-09-06 | 1973-11-13 | Respiratory Care | Nebulizer |
US3812854A (en) | 1972-10-20 | 1974-05-28 | A Michaels | Ultrasonic nebulizer |
GB8325047D0 (en) | 1983-09-19 | 1983-10-19 | Medica Aid Ltd | Nebulizers |
SE449440B (en) | 1983-12-19 | 1987-05-04 | Jr Mans Arborelius | NEBULIZER FOR SUBMICRON PREPARATION, HOMOGEN AEROSOL |
US4941618A (en) | 1986-07-07 | 1990-07-17 | Leeman Labs Inc. | Nebulizer employing a fine mesh screen |
US4743407A (en) | 1986-11-21 | 1988-05-10 | The United States Of America As Represented By The United States Department Of Energy | Externally pressurized porous cylinder for multiple surface aerosol generation and method of generation |
US4832012A (en) | 1987-07-08 | 1989-05-23 | Vortran Medical Technology, Inc. | Intermittent signal actuated nebulizer |
US4907581A (en) | 1988-06-30 | 1990-03-13 | Medi-Nuclear Corporation, Inc. | Radioactive aerosol inhalation apparatus |
US4947874A (en) | 1988-09-08 | 1990-08-14 | R. J. Reynolds Tobacco Company | Smoking articles utilizing electrical energy |
US5030390A (en) | 1989-07-20 | 1991-07-09 | University Of Delaware | Process for cooling water in an inflated fabric cooling dome |
GB8917775D0 (en) | 1989-08-03 | 1989-09-20 | Atomic Energy Authority Uk | Aerosol inhaler |
US5152456A (en) | 1989-12-12 | 1992-10-06 | Bespak, Plc | Dispensing apparatus having a perforate outlet member and a vibrating device |
GB9021433D0 (en) | 1990-10-02 | 1990-11-14 | Atomic Energy Authority Uk | Power inhaler |
US5277175A (en) | 1991-07-12 | 1994-01-11 | Riggs John H | Continuous flow nebulizer apparatus and method, having means maintaining a constant-level reservoir |
US5301664A (en) | 1992-03-06 | 1994-04-12 | Sievers Robert E | Methods and apparatus for drug delivery using supercritical solutions |
US5379760A (en) | 1992-10-26 | 1995-01-10 | Ryder; Steven L. | Position insensitive low resistance aspirator |
GB2272389B (en) | 1992-11-04 | 1996-07-24 | Bespak Plc | Dispensing apparatus |
US5743250A (en) | 1993-01-29 | 1998-04-28 | Aradigm Corporation | Insulin delivery enhanced by coached breathing |
US5915378A (en) | 1993-01-29 | 1999-06-29 | Aradigm Corporation | Creating an aerosolized formulation of insulin |
US5497763A (en) | 1993-05-21 | 1996-03-12 | Aradigm Corporation | Disposable package for intrapulmonary delivery of aerosolized formulations |
JP3493366B2 (en) | 1993-06-14 | 2004-02-03 | 日本モンサント株式会社 | Connection structure of cartridge type chemical liquid container used for chemical liquid sprayer |
DE4227899A1 (en) | 1993-09-24 | 1994-02-24 | Pfeiffer Erich Gmbh & Co Kg | Discharge mechanism for fluidic media with discharge head(s) - has distributor(s) with medium receiver(s) for distribution and stationary reception of at least one medium |
US5431345A (en) | 1993-11-12 | 1995-07-11 | The Procter & Gamble Company | Foam dispensing system for a foamable liquid |
US5570682A (en) | 1993-12-14 | 1996-11-05 | Ethex International, Inc. | Passive inspiratory nebulizer system |
US5479920A (en) | 1994-03-01 | 1996-01-02 | Vortran Medical Technology, Inc. | Breath actuated medicinal aerosol delivery apparatus |
US5810755A (en) | 1994-10-17 | 1998-09-22 | Leveen; Harry H. | Medicated wound dressing |
US5535989A (en) | 1994-12-02 | 1996-07-16 | Sen; Dipak K. | Liquid film producing process and apparatus for fluid-liquid contacting |
US5603314A (en) | 1995-03-22 | 1997-02-18 | Bono; Michael | Aerosol filtration device and inhalation apparatus containing same |
US6205999B1 (en) | 1995-04-05 | 2001-03-27 | Aerogen, Inc. | Methods and apparatus for storing chemical compounds in a portable inhaler |
US5545456A (en) | 1995-04-20 | 1996-08-13 | Suida; Teresa | Wash-cloth that cleans and massages |
KR0144599B1 (en) | 1995-07-01 | 1998-07-15 | 윤덕용 | Liquid-drop generator and device for preparing fine-partides |
US5823179A (en) | 1996-02-13 | 1998-10-20 | 1263152 Ontario Inc. | Nebulizer apparatus and method |
WO1997048293A1 (en) | 1996-06-17 | 1997-12-24 | Japan Tobacco Inc. | Flavor producing article |
US5685291A (en) | 1996-11-15 | 1997-11-11 | Marsh; Jean Ann | Nebulizer adapter system for premature babies |
DE19720701A1 (en) | 1997-05-16 | 1998-11-19 | Gsf Forschungszentrum Umwelt | Device for applying a medicament aerosol via the lungs |
US5855564A (en) | 1997-08-20 | 1999-01-05 | Aradigm Corporation | Aerosol extrusion mechanism |
JPH11316031A (en) | 1998-05-06 | 1999-11-16 | Yasumasa Akazawa | Air processing device |
US6070575A (en) | 1998-11-16 | 2000-06-06 | Aradigm Corporation | Aerosol-forming porous membrane with certain pore structure |
US6315272B1 (en) | 1999-01-06 | 2001-11-13 | Emerson Electric Co. | Humidifier with stacked reservoir |
US6196218B1 (en) | 1999-02-24 | 2001-03-06 | Ponwell Enterprises Ltd | Piezo inhaler |
AU3158600A (en) | 1999-03-06 | 2000-09-28 | Glaxo Group Limited | Medicament delivery system |
US6467477B1 (en) | 1999-03-26 | 2002-10-22 | Respironics, Inc. | Breath-based control of a therapeutic treatment |
IL129208A0 (en) | 1999-03-28 | 2000-02-17 | Liposol Ltd | A method and apparatus for nebulizing a liquid particulary useful for the aerosol delivery of biopharmaceuticals |
GB2353222B (en) | 1999-06-23 | 2001-09-19 | Cambridge Consultants | Inhalers |
SE9902627D0 (en) | 1999-07-08 | 1999-07-08 | Siemens Elema Ab | Medical nebulizer |
US6530370B1 (en) | 1999-09-16 | 2003-03-11 | Instrumentation Corp. | Nebulizer apparatus |
US8820316B2 (en) | 2000-02-11 | 2014-09-02 | Respironics Respiratory Drug Delivery (Uk) Ltd | Drug delivery apparatus |
JP4777574B2 (en) | 2000-02-11 | 2011-09-21 | レスピロニクス・レスピラトリー・ドラッグ・デリバリー・(ユーケー)・リミテッド | Drug administration device |
US6443151B1 (en) | 2000-03-08 | 2002-09-03 | Aradigm Corporation | Fluid velocity-sensitive trigger mechanism |
US20050066968A1 (en) | 2000-08-01 | 2005-03-31 | Shofner Frederick M. | Generation, delivery, measurement and control of aerosol boli for diagnostics and treatments of the respiratory/pulmonary tract of a patient |
US6527257B1 (en) | 2000-09-05 | 2003-03-04 | Rps Products, Inc. | Decorative humidifier and fountain combination |
US7077130B2 (en) | 2000-12-22 | 2006-07-18 | Chrysalis Technologies Incorporated | Disposable inhaler system |
US6799572B2 (en) | 2000-12-22 | 2004-10-05 | Chrysalis Technologies Incorporated | Disposable aerosol generator system and methods for administering the aerosol |
ATE380578T1 (en) | 2001-01-18 | 2007-12-15 | Ultrasonic Dryer Ltd | METHOD AND DEVICE FOR GENERATING DROPS |
USD471626S1 (en) | 2001-06-14 | 2003-03-11 | Omron Corporation | Nebulizer |
US6729327B2 (en) | 2001-12-17 | 2004-05-04 | Joseph L. McFarland, Jr. | Portable, handheld, pneumatic driven medicinal nebulizer |
US20030205226A1 (en) | 2002-05-02 | 2003-11-06 | Pre Holding, Inc. | Aerosol medication inhalation system |
US20040045546A1 (en) | 2002-09-05 | 2004-03-11 | Peirce Management, Llc | Pharmaceutical delivery system for oral inhalation through nebulization consisting of inert substrate impregnated with substance (S) to be solubilized or suspended prior to use |
DE10243371B4 (en) | 2002-09-18 | 2006-06-14 | Pari GmbH Spezialisten für effektive Inhalation | Aeorosoltherapiegerät |
AU2002952683A0 (en) | 2002-11-15 | 2002-11-28 | Commonwealth Scientific And Industrial Research Organisation | Apparatus for delivering dry aerosols to the respiratory tract |
GB2395437C (en) | 2002-11-20 | 2010-10-20 | Profile Respiratory Systems Ltd | Improved inhalation method and apparatus |
GB2396825B (en) | 2002-11-20 | 2004-12-08 | Profile Respiratory Systems Lt | Improved inhalation method and apparatus |
US20040123863A1 (en) | 2002-12-27 | 2004-07-01 | Yi-Hua Wang | Method of controlling oxygen inhaling through involuntary action of human and product thereof |
GB0319119D0 (en) | 2003-08-14 | 2003-09-17 | Optinose As | Delivery devices |
WO2005102428A1 (en) | 2004-04-23 | 2005-11-03 | The Governors Of The University Of Alberta | Enhanced drug delivery for inhaled aerosols |
WO2006026026A2 (en) | 2004-07-30 | 2006-03-09 | Acrymed, Inc. | Antimicrobial silver compositions |
DE102005033398A1 (en) | 2004-11-10 | 2006-05-11 | Alfred Von Schuckmann | Inhale device |
US7900627B2 (en) | 2005-01-18 | 2011-03-08 | Respironics, Inc. | Trans-fill method and system |
US7634998B1 (en) | 2005-07-15 | 2009-12-22 | Fenley Robert C | HME shuttle system |
WO2008048234A2 (en) | 2005-08-26 | 2008-04-24 | North Carolina State University | Inhaler system for targeted maximum drug-aerosol delivery |
US20080082139A1 (en) | 2006-10-02 | 2008-04-03 | Mike John Means | Inhalation therapy using audiovisual stimuli |
US20080283049A1 (en) | 2007-02-27 | 2008-11-20 | Derek D Mahoney | High efficiency nebulizer |
US8371299B2 (en) | 2007-04-19 | 2013-02-12 | Respironics Respiratory Drug Delivery | Ventilator aerosol delivery |
US8261738B2 (en) | 2007-07-24 | 2012-09-11 | Respironics Respiratory Drug Delivery (Uk) Ltd. | Apparatus and method for maintaining consistency for aerosol drug delivery treatments |
WO2011021117A1 (en) | 2009-08-15 | 2011-02-24 | Koninklijke Philips Electronics, N.V. | System and method for enabling therapeutic delivery of aerosolized medicament to a plurality of subjects to be monitored |
US8925549B2 (en) | 2008-08-11 | 2015-01-06 | Surge Ingenuity Corporation | Flow control adapter for performing spirometry and pulmonary function testing |
US8695587B2 (en) | 2008-09-26 | 2014-04-15 | Incube Labs, Llc | Controlled inhaler for distributing inhalant according to inhalation velocity |
US20100092746A1 (en) | 2008-10-14 | 2010-04-15 | Jean-Marie Coant | Nonwoven material containing benefiting particles and method of making |
EP2376156B1 (en) | 2008-12-11 | 2014-01-08 | Koninklijke Philips N.V. | System and method for monitoring a metered dose inhaler |
US20100192321A1 (en) | 2009-01-30 | 2010-08-05 | 3M Innovative Properties Company | Hair and lint cleaning tool |
JP2010207297A (en) | 2009-03-09 | 2010-09-24 | Canon Inc | Liquid discharge device and method therefor |
US9060715B2 (en) | 2009-07-22 | 2015-06-23 | Koninklijke Philips N.V. | Nebulizer |
JP5731521B2 (en) | 2009-11-04 | 2015-06-10 | コーニンクレッカ フィリップス エヌ ヴェ | Pharmaceutical supply device including a drug metering system |
CN102695535B (en) | 2010-01-07 | 2016-03-30 | 皇家飞利浦电子股份有限公司 | Comprise the respiratory medications conveyer device of feedback and compliant device |
EP2523709B1 (en) | 2010-01-11 | 2016-06-15 | Koninklijke Philips N.V. | Magnetic coupling for aerosol generating apparatus |
AU2010340769B2 (en) * | 2010-01-11 | 2015-02-12 | Koninklijke Philips Electronics N.V. | Magnetic coupling for aerosol generating apparatus |
DE102010009852A1 (en) | 2010-03-02 | 2011-09-08 | Kalle Gmbh | Antimicrobial finished films, sponges and sponge cloths |
US8491491B2 (en) | 2010-03-02 | 2013-07-23 | Data Sciences International, Inc. | Respiration measurements and dosimetry control in inhalation testing systems |
US8944052B2 (en) | 2011-05-26 | 2015-02-03 | Ivan Osorio | Apparatus and methods for delivery of therapeutic agents to mucous or serous membrane |
US20130032153A1 (en) | 2011-08-04 | 2013-02-07 | Neely Travis Ray | Mask for an air delivery apparatus, system, and method |
EP2744599B1 (en) | 2011-09-19 | 2016-07-13 | Koninklijke Philips N.V. | Analysis and control of aerosol output |
US9572944B2 (en) | 2011-09-19 | 2017-02-21 | Koninklijke Philips N.V. | Nebulizer, a control unit for controlling the same, a nebulizing element and a method of operating a nebulizer |
US20130220314A1 (en) | 2012-02-29 | 2013-08-29 | General Electric Company | Medical vaporizer with porous vaporization element |
RU2630590C2 (en) | 2012-03-07 | 2017-09-11 | Конинклейке Филипс Н.В. | Device for application with nebuliser and method for nebuliser actuation |
GB2504075A (en) | 2012-07-16 | 2014-01-22 | Nicoventures Holdings Ltd | Electronic smoking device |
GB2504076A (en) | 2012-07-16 | 2014-01-22 | Nicoventures Holdings Ltd | Electronic smoking device |
US8807131B1 (en) | 2013-06-18 | 2014-08-19 | Isonea Limited | Compliance monitoring for asthma inhalers |
US9877509B2 (en) | 2014-03-31 | 2018-01-30 | Westfield Limited (Ltd.) | Micro-vaporizer heating element and method of vaporization |
US10201186B2 (en) | 2014-08-22 | 2019-02-12 | Fontem Holdings 4 B.V. | Method, system and device for controlling a heating element |
GB201511361D0 (en) | 2015-06-29 | 2015-08-12 | Nicoventures Holdings Ltd | Electronic vapour provision system |
GB201511349D0 (en) | 2015-06-29 | 2015-08-12 | Nicoventures Holdings Ltd | Electronic aerosol provision systems |
GB201511359D0 (en) | 2015-06-29 | 2015-08-12 | Nicoventures Holdings Ltd | Electronic vapour provision system |
CN205040652U (en) | 2015-08-11 | 2016-02-24 | 上海烟草集团有限责任公司 | Aerosol inhalation device |
US10328218B2 (en) * | 2015-10-15 | 2019-06-25 | Engineered Medical Systems, Inc. | Respiratory medicament nebulizer system |
US9993027B1 (en) | 2016-12-06 | 2018-06-12 | Funai Electric Co., Ltd. | Heater element for a vaporization device |
-
2017
- 2017-03-23 US US15/467,527 patent/US10857311B2/en active Active
-
2020
- 2020-11-04 US US17/089,184 patent/US20210046258A1/en not_active Abandoned
Patent Citations (16)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2284591A (en) * | 1939-11-24 | 1942-05-26 | Stanco Inc | Nebulizer |
US3046983A (en) * | 1959-10-01 | 1962-07-31 | Grubb Thomas Christman | Variable dose inhaler |
US3610480A (en) * | 1969-07-31 | 1971-10-05 | Geigy Chem Corp | Aerosol dispensing apparatus |
US3927806A (en) * | 1972-09-07 | 1975-12-23 | Philip Meshberg | Applicator for attachment to a spray mist dispenser |
US4114811A (en) * | 1977-04-12 | 1978-09-19 | Ciba-Geigy Corporation | Spray dispenser with easily actuable mouthpiece |
GB2074454A (en) * | 1980-04-24 | 1981-11-04 | Somova Spa | Inhalation device with retractible mouthpiece |
US4969455A (en) * | 1988-11-29 | 1990-11-13 | Somova S.P.A. | Inhalator for aerosol containers |
US5755221A (en) * | 1990-09-12 | 1998-05-26 | Bisgaard; Hans | Aerosol inhaler with piston dump |
US5833057A (en) * | 1997-04-28 | 1998-11-10 | Char; Aka Loka | Apparatus for packaging and shipping biological fluid samples collected in vials |
US20020073991A1 (en) * | 1998-01-22 | 2002-06-20 | Igor Gonda | Formulation and devices for monitoring the efficacy of the delivery of aerosols |
US6354516B1 (en) * | 1999-11-02 | 2002-03-12 | Aradigm Corporation | Pore structures for reduced pressure aerosolization |
US20060231090A1 (en) * | 2005-04-13 | 2006-10-19 | Russell King | Inhalation apparatus |
US20070175476A1 (en) * | 2005-12-28 | 2007-08-02 | Philip Morris Usa Inc. | Aerosol powder delivery device |
US20080216828A1 (en) * | 2007-03-09 | 2008-09-11 | Alexza Pharmaceuticals, Inc. | Heating unit for use in a drug delivery device |
US20090192443A1 (en) * | 2008-10-06 | 2009-07-30 | Collins Jr James F | Ophthalmic fluid delivery device and method of operation |
US20120318259A1 (en) * | 2010-01-12 | 2012-12-20 | Omega Life Science Ltd. | Method and apparatus for producing fine concentrated aerosol |
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