Aerosol deliver apparatus IV
A multipurpose aerosol medication delivery apparatus that includes a collapsible/expandable, or a fixed volume, or a combination of partially fixed volume and partially collapsible/expandable holding chamber for use with a metered dosed inhaler (MDI) and/or any standard small volume nebulizer. The holding chamber is designed to deliver-aerosol medication particles generated by an MDI; aerosol medication particles generated by a nebulizer; a single gas or a mixture of gases; a single gas or a mixture of gases that can yield a gas density that will enhance aerosol delivery of medication with both MDI and nebulizer; a single gas or a mixture of gases that will yield and deliver an oxygen concentration to a patient ranging from room air concentration to 100%. The device includes a reservoir that stores nebulized aerosol generated during exhalation to be inhaled during the next breath. The device also included a one way valve to prevent carbon dioxide generated during exhalation from rebreathing by not allowing the exhaled air from entering the holding chamber. The device includes an exit port with a second one way valve that allows the exhaled air to exit the device but closes during inhalation to prevent any entrainment of room air gas. The exit port may instead have a filter with one-way valve to trap the exhaled aerosol particles while allowing the exhaled gases to escape. The filter valve will similarly close during inhalation to prevent entrainment of room air gas. The holding chamber will allow a uniform mixture of aerosol medication and gases to flow together during inhalation to the patient via a mouthpiece or a facemask. The holding chamber is connected to a nebulizer chamber with a single or multiple connecting tubes that allow gas mixtures with varying density, viscosity, humidity and concentration of oxygen to flow into the holding chamber from the nebulizer chamber. The pattern of flow of the gas(es) does not disturb the flow of the nebulized medication from the nebulizer chamber to the holding chamber or interfere with the plume generated by an MDI. The device also serves as a facemask for delivering precise concentrations of oxygen or as a 100% non-rebreather mask. The device also serves to deliver precise concentrations of different density gases i.e. nitrogen, helium, oxygen, etc. This will allow varying fractions of inspired oxygen to deliver aerosol medication via MDI or a nebulizer. Thus, the device has the ability to deliver aerosol medication with an MDI or a nebulizer while retaining the ability to simultaneously deliver different density gas mixtures and varying fraction of inspired oxygen without interrupting one for the other.
This invention relates to an improved aerosol inhalation device and particularly to an aerosol enhancement device which:
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- can be used as a facemask to deliver precise fraction of inspired oxygen
- can be used as a 100% oxygen non-rebreather mask
- can deliver a single gas or a mixture of gases to yield varying gas densities that can enhance aerosol delivery
- can deliver an individual gas like nitrogen, oxygen, room air, helium, etc. or a single premixed gas or a mixture of individual gases to yield a final mixture which can deliver 100% oxygen or precise fraction of inspired oxygen or attain a mixture with a desired gas density and a desired concentration of oxygen that is physiologically compatible with life
- can deliver aerosol medication with a metered dose inhaler
- can deliver aerosol medication with standard small volume nebulizer
- can deliver aerosol medication with an MDI and/or a standard small volume nebulizer simultaneously
- can deliver aerosol medication with an MDI and/or a small volume nebulizer and simultaneously deliver a desired gas density to enhance aerosol delivery
- can deliver aerosol medication with an MDI and/or a small volume nebulizer; can deliver a desired gas density to enhance aerosol delivery; and deliver a desired fraction of inspired oxygen to a hypoxemic patient
- includes a reservoir in the form of a bag or an expandable/collapsible corrugated tubing for storage of aerosol generated by a nebulizer during exhalation.
- includes a valve system to prevent waste of medication generated by a nebulizer chamber during exhalation and to prevent rebreathing of exhaled carbon dioxide
- includes a valve system to prevent entrainment of room air during inhalation and for exit of carbon dioxide during exhalation
- can be used with a Continuous Positive Airway Pressure (CPAP) or a Bi-level Positive Airway Pressure (BIPAP) system
- can be introduced in a ventilatory circuit with the ability to deliver aerosol medication with a metered dose inhaler and/or a nebulizer
- includes a filter system to trap exhaled aerosol particles while allowing the exhaled gas (es) to escape into room air
- includes a filter system with a valve to prevent entrainment of room air during inhalation and to trap the exhaled aerosol particles while allowing exhaled gas (es) to escape into room air
- includes a collapsible/expandable spacer device that can be fully collapsed and made compact when not in use for delivery of aerosol medications and be partially or fully expandable when in use for aerosol medication delivery via an MDI or a nebulizer
- can serve as an ambu-bag for resuscitation
- can be used to deliver anesthetic gas (es)
MDI drug canisters are typically sold by manufacturers with a boot that includes a nozzle, an actuator, and a mouthpiece. Patients can self-administer the MDI medication using the boot alone but the majority of patients have difficulty in synchronizing the actuation of the MDI canister and inhalation of the medication. Spacers or valved chambers have been used with MDI boot to obviate the problem associated with patient coordination by helping to synchronize the actuation of MDI canister and patient inhalation and improve the delivery of medication by decreasing oropharyngeal deposition of aerosol drug. Many valved chambers of this type are commercially available. Examples of such spacers are—AeroChamber, U.S. Pat. Nos. 4,470,412 and 5,012,803; Optichamber, U.S. Pat. No. 5,385,140; Collapsible Chamber, U.S. Pat. Nos. 4,637,528 and 4,641,644; Disposable Chamber U.S. Pat. No. 4,953,545; or Collapsible and Disposable Chamber U.S. Pat Application No. 20020129814. These devices are expensive and may be alright for chronic conditions that require frequent use of MDI inhalers provided the cost and labor involved in frequent delivery of medication is acceptable to the patient. However, under acute symptoms, such devices may fail to serve the purpose and lead to an inadequate delivery of medication.
Aerosol delivery devices that use standard small volume nebulizers are commonly used in acute conditions as they are cheap and overcome the inhalation difficulties associated with actuation of MDI and synchronization of inhalation by the patient. Nebulizers are fraught with numerous problems as well. The medication dose used is about 10 times of that used with an MDI and hence the increased cost without any added proven clinical benefit. Secondly, the majority of the nebulized medication is wasted during exhalation. Thirdly, the time taken to deliver the medication is several times that of an MDI and the labor cost of respiratory therapist may outweigh the benefits of nebulizers compared with MDIs. Breath actuated nebulizer (s) with reservoir have been designed to overcome the medication waste. Example of one such device is U.S. Pat. No. 5,752,502. However, these devices are expensive and still have all the other problems associated with nebulizer use alone. Other examples of aerosol inhalation devices would be U.S. Pat. No. 4,210,155, in which there is a fixed volume mist accumulation chamber for use in combination with a nebulizer and a TEE connection. Problems with prior art devices such as described are a significant waste of medication, a non-uniform concentration of delivered medication, expensive, and difficult to use. Many such devices are commercially available in which the nebulizer is directly attached to a TEE connector without any mixing chamber. All the afore mentioned devices can be used with either an MDI or a nebulizer but not both, and hence, face the difficultly associated with either system alone. Other devices have tried to overcome the above problems by incorporating a mixing chamber in the device with adaptability to be used with an MDI or standard nebulizer. U.S. Pat. Application No. 20020121275 is an example of one such device. However, the device is plagued with problems typical of such devices. Just like other prior art devices, this device as well fails to incorporate some of the key the features necessary for enhanced aerosol delivery. A list of problems associated with this device and other similar devices are outlined below:
- (1) The entrained airflow in this device interferes with the MDI plume as well as the plume generated by a nebulizer resulting in increased impaction losses of aerosol generated by either an MDI or nebulizer.
- (2) The device does not have the ability to deliver a desired precise fraction of inspired oxygen to a hypoxic patient and simultaneously deliver aerosol medication with either a metered dose inhaler or a nebulizer.
- (3) The device cannot deliver a gas with a desired density to improve aerosol delivery and a desired fraction of inspired oxygen to a hypoxemic patient
- (4) The device does not have the ability to deliver different density gases with a desired fraction of inspired oxygen simultaneously while retaining the ability to deliver aerosol medication at the same time with either an MDI or a nebulizer
- (5) the device does not have the ability to deliver a mixture of multiple gases to a patient and simultaneously maintain a desired fraction of inspired oxygen
- (6) the device does not serve as a facemask for delivering varying concentrations of inspired oxygen from room air to 100% but serves solely as an aerosol delivery device
- (7) the device does not have a reservoir chamber-either as a bag or as a large volume tubing t store nebulized medication that is otherwise wasted during exhalation. The holding chamber of this device varies from 90 cc to 140 cc and is not enough to serve as a reservoir for the volume of nebulized medication generated during exhalation and hence in a normal sized adult most of the medication generated during exhalation is wasted
- (8) there is no mechanism in the device to prevent entrainment of room air which forms the bulk of volume during inhalation. The fraction of inspired oxygen and the density of gas mixture inhaled by the patient may vary with every breath with this device depending on the volume of entrained room air which may vary with each breath
- (9) the device does not have any valve system to prevent exhaled carbon dioxide from entering the holding chamber. Rebreathing of carbon dioxide from the holding chamber on subsequent inhalation can be extremely detrimental to a patient and extremely dangerous under certain clinical conditions
- (10) the device does not have the capability of delivering medication with an MDI and a nebulizer simultaneously
- (11) the device has a fixed volume-holding chamber, which makes the device extremely large and cumbersome to deliver medication.
Our device overcomes all the difficulties and problems associated with this and all the prior art devices. Our device incorporates all the desired features to make it a compact, user friendly economical, and multipurpose aerosol device for both acute and chronic use with either an MDI or a nebulizer or with both MDI and nebulizer simultaneously as warranted by the patient's clinical circumstances. Our device also retains the ability to deliver a desired fraction of inspired oxygen and deliver a desired gas density to decrease the work of breathing and simultaneously deliver and enhance aerosol medication delivery.
SUMMARY OF THE INVENTIONThe present invention provides an aerosol medication delivery apparatus, which incorporates the aforementioned advantages. The inventive device includes a fixed volume or a collapsible/expandable MDI holding chamber, a fixed volume or a collapsible/expandable nebulizer chamber, a system of connecting the two chambers with 2 or more hollow collapsible/expandable or fixed volume cylindrical connecting tubes. The MDI holding chamber maybe a fixed volume chamber or a collapsible/expandable chamber or a combination of the two i.e., partly fixed and partly collapsible/expandable chamber. The collapsible feature of the device makes it compact when solely in use for delivery of single gas or different gas mixtures while the expandable feature can be utilized when delivering aerosol medication with an MDI and/or a nebulizer.
The collapsible/expandable MDI chamber has a hollow cylindrical rigid inlet port at one end and a similar outlet port at the other end. When fully collapsed the outlet and the inlet port may be fused to each other to form a continuous hollow rigid cylindrical tube. When the holding chamber is fully expanded the outlet and inlet tubes stay disconnected. The holding chamber may be kept patent by internal support with a coiled metal or plastic wire. The rings of the coiled wire come together when the chamber is collapsed and stay separated when it is expanded. Alternatively, the MDI chamber may be constructed with a collapsible/expandable corrugated plastic tubing, which does not require any coiled metal or plastic wire support for maintaining patency of the chamber. The volume of the chamber may vary form 0.10 liters to 2.0 liters to accommodate both pediatric and adult patients. When partially or fully expanded, the chamber may also serve as a reservoir to prevent aerosol generated during exhalation from being wasted.
The central rigid inlet port is connected to a universal boot adapter panel with an opening to accommodate the boot of any commercially available MDI such that medication can be delivered to the MDI chamber on actuation of the MDI canister. For aerosol delivery with nebuliser, the universal boot adapter is disconnected from the inlet port, which now fuses with the outlet port of the nebulizer chamber. The inlet of the MDI chamber is connected to the outlet to the nebulizer chamber with two additional peripheral hollow cylindrical connecting tubes; the two tubes have two outlet ports at 3 and 9 o'clock positions in the nebulizer chamber and two inlet ports in similar locations in the MDI chamber. The distance between the connecting tubes and the length of the connecting tubes allows for any commercially available MDI boot to be accommodated easily between the MDI and the nebulizer chambers. At the inlet end of the MDI chamber, the peripheral hollow cylindrical connecting tubes split into multiple micrometric openings that are distributed at intervals along the entire circumference of the MDI chamber's inlet. This allows the flow of gas(es) from the two openings in the nebulizer chambers outlet to the multiple openings distributed all along the circumference of the MDI chamber's inlet. The pattern of flow of the gas(es) through multiple openings that are distributed along the circumference of the MDI chamber's inlet is such that it does not interfere with the plume of the MDI when it is actuated. Also this arrangement allows different desired density gas(es) with a desired fraction of inspired oxygen to flow into the MDI chamber to enhance aerosol delivery from MDI and to deliver oxygen to a patient if necessary. The flow pattern of the gas(es) in addition minimizes the impaction losses of aerosol generated by an MDI.
The outlet rigid tube of the MDI chamber has an inhalation flap valve and a flap seat. The flap valve moves away from the flap valve seat on inhalation to allow the flow of medication from the MDI chamber to the patient. On exhalation the flap valve presses against the flap valve seat which prevents carbon dioxide exhaled during exhalation from entering into the MDI chamber. The outlet tube has an exhalation flap valve assembly with an exhalation flap valve and a valve seat on the superior or inferior surface. The flap valve moves away from the flap valve seat on exhalation to allow the exhaled gases to exit the outlet tube and presses against the valve seat on inhalation to prevent any entrainment of any room air gases on inhalation. The provision of a filter at this opening may be optional depending on the conditions under which aerosol is being delivered. The filter can trap all exhaled aerosol particles while allowing the gases to exit from this port. A flap valve may again be provided at the end of the filter to prevent entrainment of room air gas during inhalation and to allow exit of all exhaled gas(es).
The nebulizer chamber has an inlet port with a central cylindrical hollow rigid tube for entry of one or more gases into the nebulizer chamber; an outlet port, a port for a nebulizer, and a port for a reservoir (a bag reservoir or a collapsible/expandable corrugated plastic tubing reservoir), the reservoir bag has one or more inlet ports for inflow of desired gases. There are two additional openings at 3 and 9 o'clock positions for connection of peripheral tubes that connect the MDI chamber and the nebulizer chamber. The outlet of the nebulizer chamber has a rigid hollow cylindrical tube similar to that seen in the MDI chamber's inlet. The port of the nebulizer chamber remains plugged with a cap when MDI is in use. The cap is unplugged and the outlet port of the nebulizer fuses with the inlet port of the MDI chamber when nebulizer is to be used. When aerosol delivery is desired with a nebulizer, the nebulizer is connected to the nebulizer port, the nebulized medication flows through the peripheral connecting tubes between the MDI chamber and the nebulizer chamber through multiple openings distributed along the circumference of the MDI chamber's inlet. The universal boot adapter assembly may be disconnected from the central rigid tube of MDI the chamber, which could now be plugged with a cap. Alternatively, the central inlet tube of the MDI chamber and the central outlet tube of the nebulizer chamber can both uncapped and the two tubes fused to each other by moving the MDI chamber closer to the nebulizer chamber by collapsing the peripheral connecting tubes. The aerosol generated by the nebulizer can now flow from the nebulizer chamber to the MDI chamber via the central connection between the MDI chamber and the nebulizer chamber, as well as via the peripheral connections between the two chambers via the peripheral connecting tubes at 3 and 9 o'clock positions. The connecting tubes between the MDI and nebulizer chambers are made collapsible/expandable in a manner identical to the principles of the expandable/collapsible MDI chamber itself. This will allow the MDI and the nebulizer chambers to be moved closer to each other to be fused during nebulizer operation or to be disconnected and moved apart to accommodate MDI in the space between the MDI and the nebulizer chambers during MDI operation.
The aerosol reservoir may comprise of a collapsible/expandable bag made of plastic or neoprene, a fixed chamber, or a collapsible/expandable corrugated plastic tubing. The volume of the reservoir could vary from 0.1 liter to 2.0 liters to meet the needs of both pediatric and adult patients. The reservoir could be attached to a reservoir port in the nebulizer chamber or alternatively it could be attached to the inlet port of the nebulizer chamber to store the aerosol generated during exhalation which would otherwise, have been wasted as is the case with most TEE nebulizers. During the subsequent inhalation the aerosol stored in the reservoir bag during exhalation would flow from the nebulizer chamber into the MDI chamber via central and/or peripheral connections and then through the mouthpiece or facemask to the patient.
Additional inlet ports may be available directly on the nebulizer chamber or on the reservoir bag or on the corrugated plastic tubing reservoir which will allow one of more, unmixed or premixed gases to flow into the nebulizer chamber and/or the reservoir at different flow rates to achieve a desired density, viscosity, humidity and fraction of inspired oxygen to simultaneously enhance medication delivery and deliver oxygen to a hypoxemic patient. The gases used may be oxygen, nitrogen, helium, heliox (premixed), room air, various anesthesia gases, various diagnostic gases, i.e. xenon, krypton etc. When not in use for aerosol delivery either via MDI or nebulizer the device could be used solely to deliver desired oxygen concentration or other aforementioned gases via a facemask which can be connected to outlet of the MDI chamber. The equipment in this case will be made extremely compact by fully collapsing the MDI chamber, fully collapsing the peripheral connecting tubes, and fully collapsing the corrugated plastic reservoir tubing connected to the nebulizer chamber. The nebulizer outlet port in the nebulizer chamber may be plugged with a cap when only delivering a gas without aerosolized medication or the inlet port of MDI chamber and the outlet port of the nebulizer chamber may be fused. The desired gas(es) can now flow to the patient from the reservoir bag/tubing to the MDI chamber via the central and/or peripheral connections between the two chambers and to the patient via a facemask.
The device can also be incorporated into the inspiratory limb of the ventilatory circuit by making connections at two sites—between the inspiratory tubing and the outlet port of the MDI chamber at one end and between the inlet port of the nebulizer chamber and the inspiratory tubing at the other end. The device can now deliver aerosol medication with MDI or nebulizer to the patient on mechanical ventilation. This arrangement will have the distinct advantage of delivering the precise dose via MDI (ex-actuator) as specified by the manufacturer. This arrangement allows the MDI canister to be actuated using the MDI boot and actuator as specified by the manufacturers as opposed to commercially available custom designed universal actuators that are currently available to fit nozzles of various MDIs. Hence, this mode of delivery is different from all the prior art devices which have used custom designed universal actuators in ventilatory circuit to deliver aerosol by MDI as those devices fail to meet the ex-actuator delivery of dose as specified by the manufacturer. Hence, the ex-actuator dose output for each MDI will be different from that specified by the manufacturer. Our device obviates that problem.
Alternatively, our device, like numerous prior art devices, can incorporate a custom designed universal actuator on the inlet port of the MDI chamber to accommodate the nozzles of all commercially available MDI canisters to deliver aerosol via MDI, as opposed to a universal MDI boot assembly to accommodate the boot of all commercially available MDIs. In this case all other features of the device would remain the same except that the MDI chamber and the nebulizer chamber may be fused at the center without any connecting tubes at the 3 and 9 o'clock positions. Alternatively, the nebulizer and MDI chambers maybe connected only at peripheral 3 and 9 o'clock positions with collapsible connecting tubes or fixed rigid tubes without intervening space between the MDI and the nebulizer chambers for MDI boot assembly which will no longer be required. Alternatively, nebulizer and MDI chambers maybe connected or fused at both central and peripheral locations.
Alternatively, the collapsible/expandable MDI chamber and the collapsible/expandable MDI chamber may be fused to form a single chamber and the MDI boot assembly instead of now being fitted at the inlet of the MDI chamber fits at the inlet of the nebulizer chamber where an MDI boot can be attached to deliver aerosol medication via MDI. The boot assembly may also be designed to accommodate a nebulizer Tee piece which may generate aerosol particles via a nebulizer to deliver it into the collapsible/expandable MDI and nebulizer chambers. The Tee piece in this case will have one end of the horizontal limb completely closed so that no aerosol particles will escape out of the holding chamber during exhalation phase and there may be no need for a reservoir bag as the collapsible/expandable tubing of the MDI and nebulizer chambers when expanded will create a volume that will serve as a reservoir for storage of aerosol medication generated during the exhalation phase. Alternatively, the Tee piece may be open at both ends, one open end of which may be connected to the inlet of the nebulizer chamber and the other free end of which may be connected to a second Tee piece. The vertical limb of the second Tee piece may now serve as the inlet for the reservoir bag or the corrugated reservoir tubing and one end of the horizontal limb of the second Tee piece remaining closed.
BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWINGFurther features of the present invention will become apparent in the accompanied drawings as well as the detailed description of the preferred embodiments.
The present invention will now be described in detail by reference to the drawing figures, where as like parts as indicated by like reference numerals.
The inlet end 8a of the central tube 7a is attached to the outlet end 27a of the boot 25a of a metered dose inhaler 24a. The inhaler 24a has a boot 25a with an inlet end 26a and an outlet end 27a. A canister 28a is introduced into the boot 25a through the inlet end 26a and the nozzle 29a of the MDI 24a is attached to an actuator 30a. The actuator 30a has an opening or an aperture 31a. On actuation of the MDI canister 28a, the medication aerosol particles are generated through the opening 31a of the actuator 30a, and enter into the chamber 1a through the outlet end 9a of the central tube 7a.
The outlet tube 16a of the MDI chamber 1a has two valve assemblies disposed between the inlet end 17a and the outlet end 18a—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 32a that has a circular opening 33a and a flap valve 34a as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 35a that has a circular opening 36a and a flap valve 37a as demonstrated by the dotted line. On inhalation, the inhalation flap valve 34a moves away from the valve seat 32a for the aerosol particles to move from the MDI chamber 1a to the patient through the opening 33a in the valve seat 32a of the tube 16a. On exhalation, the flap valve 34a moves towards the flap valve seat 32a and closes the opening 33a to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 1a thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 32a prevents any protrusion of the flap valve 34a through the opening 33a. The exhalation flap valve assembly has a flap valve 37a that presses against the flap valve seat 35a on inhalation and completely occludes the opening 36a to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 16a on inhalation. On exhalation the flap valve 37a moves away from the flap valve seat 35a for the air exhaled by the patient to escape into the atmosphere from tube 16a through the opening 36a.
The nebulizer chamber 4a has a hollow cylindrical inlet tube 38a with an inlet end 39a and an outlet end 40a. The inlet and 39a can be attached to a single or multiple gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. The nebulizer chamber 4a has a hollow cylindrical outlet tube 41a that has an inlet end 42a and an outlet end 43a. The outlet end 43a may remain plugged with a cap when the device is in use with a metered dose inhaler. The nebulizer chamber also has two hollow cylindrical tubes, 44a and 47a, at three o'clock and nine o'clock positions. Tube 44a has an inlet end 45a and an outlet end 46a, whereas the tube 47a has an inlet end 48a and an outlet end 49a. The inlet end 1a of the tube 10a the inlet end 5a of the MDI chamber 1a is connected to the outlet end 46a of the tube 44a at the outlet end 6a of the nebulizer chamber 4a with a collapsible/expandable stiff corrugated plastic tubing 50a and similarly the inlet end 14a of tube 13a is connected to the outlet end 49a of tube 47a with a collapsible/expandable corrugated plastic tubing 51a. The collapsible/expandable tubings 50a and 51a are demonstrated to be fully expanded in
The nebulizer chamber has an inlet port 52a for connection with a standard small volume nebulizer 53a. Chamber 4a also has another inlet 54a for connection to a reservoir bag 55a. The reservoir bag 55a serves to store the aerosol particles generated by the nebulizer 53a during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The bag 55a has two small inlets 56a and 57a to be connected to one or more gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The inlet end 8b of the tube 7b is attached to the outlet end 27b of the boot 25b of a metered dose inhaler 24b. The inhaler 24b has a boot 25b with an inlet end 26b and an outlet end 27b. A canister 28b is introduced into the boot 25b through the inlet end 26b and the nozzle 29b of the MDI 24b is attached to an actuator 30b. The actuator 30b has an opening or an aperture 31b. On actuation of the MDI canister 28b, the medication aerosol particles are generated through the opening 31b of the actuator 30b, and enter into the chamber 1b through the outlet end 9b of the tube 7b.
The outlet tube 16b of the MDI chamber 1b has two valve assemblies disposed between the inlet end 17b and the outlet end 18b—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 32b that has a circular opening 33b and a flap valve 34b as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 35b that has a circular opening 36b and a flap valve 37b as demonstrated by the dotted line. On inhalation, the inhalation flap valve 34a moves away from the valve seat 32b for the aerosol particles to move from the MDI chamber 1b to the patient through the opening 33b in the valve seat 32b of the tube 16b. On exhalation, the flap valve 34b moves towards the flap valve seat 32b and closes the opening 33b to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 1a thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 32b prevents any protrusion of the flap valve 34b through the opening 33b. The exhalation flap valve assembly has a flap valve 37b that presses against the flap valve seat 35b on inhalation and completely occludes the opening 36b to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 16b on inhalation. On exhalation the flap valve 37b moves away from the flap valve seat 35b for the air exhaled by the patient to escape into the atmosphere from tube 16b through the opening 36b.
The nebulizer chamber 4b has a hollow cylindrical inlet tube 38b with an inlet end 39b and an outlet end 40b. The inlet and 39b can be attached to a single or multiple gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. The nebulizer chamber 4b has a hollow cylindrical outlet tube 41b that has an inlet end 42b and an outlet end 43b. The outlet end 43b may remain plugged with a cap when the device is in use with a metered dose inhaler. The nebulizer chamber also has two hollow cylindrical tubes, 44b and 47b, at three o'clock and nine o'clock positions. Tube 44b has an inlet end 45b and an outlet end 46b, whereas the tube 47b has an inlet end 48b and an outlet end 49b. The inlet end 11b of the tube 10b is connected to the outlet end 46b of the tube 44b with a collapsible/expandable stiff corrugated plastic tubing 50b and similarly the inlet end 14b of tube 13b is connected to the outlet end 49b of tube 47b with a collapsible/expandable corrugated plastic tubing 51b. The collapsible/expandable tubings 50b and 51b are demonstrated to be fully expanded in
The nebulizer chamber has an inlet port 52b for connection with a standard small volume nebulizer 53b. Chamber 4b also has another inlet 54b for connection to a reservoir bag 55b. The reservoir bag 55b serves to store the aerosol particles generated by the nebulizer 53b during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The bag 55b has two small inlets 56b and 57b to be connected to one or more gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The outlet tube 16c of the MDI chamber 1c has two valve assemblies disposed between the inlet end 17c and the outlet end 18c—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 32c that has a circular opening 33c and a flap valve 34c as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 35c that has a circular opening 36c and a flap valve 37c as demonstrated by the dotted line. On inhalation, the inhalation flap valve 34c moves away from the valve seat 32c for the aerosol particles to move from the MDI chamber 1c to the patient through the opening 33c in the valve seat 32c of the tube 16c. On exhalation, the flap valve 34c moves towards the flap valve seat 32c and closes the opening 33c to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 1c thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 32c prevents any protrusion of the flap valve 34c through the opening 33c. The exhalation flap valve assembly has a flap valve 37c that presses against the flap valve seat 35c on inhalation and completely occludes the opening 36c to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 16c on inhalation. On exhalation the flap valve 37c moves away from the flap valve seat 35c for the air exhaled by the patient to escape into the atmosphere from tube 16c through the opening 36c.
The nebulizer chamber 4c has a hollow cylindrical inlet tube 38c with an inlet end 39c and an outlet end 40c. The inlet and 39c can be attached to a single or multiple gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. The nebulizer chamber 4c has a hollow cylindrical outlet tube 41c that has an inlet end 42c and an outlet end 43c. The nebulizer chamber also has two hollow cylindrical tubes, 44c and 47c, at three o'clock and nine o'clock positions. Tube 44c has an inlet end 45c and an outlet end 46c, whereas the tube 47a has an inlet end 48c and an outlet end 49c. The inlet end 11c of the tube 10c is connected to the outlet end 46c of the tube 4c with a collapsible/expandable stiff corrugated plastic tubing 50c and similarly the inlet end 14c of tube 13c is connected to the outlet end 49c of tube 47c with a collapsible/expandable corrugated plastic tubing 51c. Quite unlike
The nebulizer chamber has an inlet port 52c for connection with a standard small volume nebulizer 53c. The aerosol medication generated with the nebulizer 53c can enter the MDI chamber via a central connection between the tubes 7c and 41c or through the peripheral connections between the tubes 10c and 44c, and 13c and 47c. Chamber 4c also has another inlet 54c for connection to a reservoir bag 55c. The reservoir bag 55c serves to store the aerosol particles generated by the nebulizer 53c during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The bag 55c has two small inlets 56c and 57c to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. The MDI 24c can be connected to the inlet 40c and on actuation the aerosol particles generated by the MDI will be transferred from the nebulizer chamber 4c to the MDI chamber 1c via the central and two peripheral connections between the two chambers as described before.
The outlet tube 16d of the MDI chamber 1d has two valve assemblies disposed between the inlet end 17d and the outlet end 18d—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 32d that has a circular opening 33d and a flap valve 34d as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 35d that has a circular opening 36d and a flap valve 37d as demonstrated by the dotted line. On inhalation, the inhalation flap valve 34d moves away from the valve seat 32d for the aerosol particles to move from the MDI chamber 1d to the patient through the opening 33d in the valve seat 32d of the tube 16d. On exhalation, the flap valve 34d moves towards the flap valve seat 32d and closes the opening 33d to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 1d thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 32d prevents any protrusion of the flap valve 34d through the opening 33d. The exhalation flap valve assembly has a flap valve 37d that presses against the flap valve seat 35d on inhalation and completely occludes the opening 36d to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 16d on inhalation. On exhalation the flap valve 37d moves away from the flap valve seat 35d for the air exhaled by the patient to escape into the atmosphere from tube 16d through the opening 36d.
The nebulizer chamber 4d has a hollow cylindrical inlet tube 38d with an inlet end 39d and an outlet end 40d. The inlet and 39d can be attached to a single or multiple gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. The nebulizer chamber 4d has a hollow cylindrical outlet tube 41d that has an inlet end 42d and an outlet end 43d. The nebulizer chamber also has two hollow cylindrical tubes, 44d and 47d, at three o'clock and nine o'clock positions. Tube 44d has an inlet end 45d and an outlet end 46d, whereas the tube 47d has an inlet end 48d and an outlet end 49d. The inlet end 1d of the tube 10d is connected to the outlet end 46d of the tube 44d with a collapsible/expandable stiff corrugated plastic tubing 50d and similarly the inlet end 14d of tube 13d is connected to the outlet end 49d of tube 47d with a collapsible/expandable corrugated plastic tubing 51d. Quite unlike
The nebulizer chamber has an inlet port 52d for connection with a standard small volume nebulizer 53d. The aerosol medication generated with the nebulizer 53d can enter the MDI chamber via a central connection between the tubes 7d and 41d or through the peripheral connections between the tubes 10d and 44d, and 13d and 47d. Chamber 4d also has another inlet 54d for connection to a reservoir bag 55d. The reservoir bag 55d serves to store the aerosol particles generated by the nebulizer 53d during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The bag 55d has two small inlets 56d and 57d to be connected to one or more gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The outlet tube 16e of the MDI chamber 1e has two valve assemblies disposed between the inlet end 17e and the outlet end 18e—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 32e that has a circular opening 33e and a flap valve 34e as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 35e that has a circular opening 36e and a flap valve 37e as demonstrated by the dotted line. On inhalation, the inhalation flap valve 34e moves away from the valve seat 32e for the aerosol particles to move from the MDI chamber 1e to the patient through the opening 33e in the valve seat 32e of the tube 16e. On exhalation, the flap valve 34e moves towards the flap valve seat 32e and closes the opening 33e to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 1e thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 32e prevents any protrusion of the flap valve 34e through the opening 33e. The exhalation flap valve assembly has a flap valve 37e that presses against the flap valve seat 35e on inhalation and completely occludes the opening 36e to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 16e on inhalation. On exhalation the flap valve 37e moves away from the flap valve seat 35e for the air exhaled by the patient to escape into the atmosphere from tube 16e through the opening 36e.
The nebulizer chamber 4e has a hollow cylindrical inlet tube 38e with an inlet end 39e and an outlet end 40e. The inlet and 39e can be attached to a single or multiple gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles and/or to deliver a fixed concentration of oxygen to a hypoxemic patient. The inlet end 39e may have a boot adapter assembly to accommodate the boot of any commercially available MDI and the MDI 24e maybe alternatively be connected to the inlet end 39e of the tube and on actuation the aerosol particles generated by the MDI will be transferred from the nebulizer chamber 4e to the MDI chamber. The inhaler 24e has a boot 25e with an inlet end 26e and an outlet end 27e. A canister 28e is introduced into the boot 25e through the inlet end 26e and the nozzle 29e of the MDI 24e is attached to an actuator 30e. The actuator 30e has an opening or an aperture 31e. On actuation of the MDI canister 28e, the medication aerosol particles are generated through the opening 31e of the actuator 30e.
The nebulizer chamber has an inlet port 52e for connection with a standard small volume nebulizer 53e. The aerosol medication generated with the nebulizer 53e can enter the MDI chamber via a central connection between the MDI chamber and the nebulizer chamber 2e6e. Chamber 4e also has another inlet 54e for connection to a reservoir bag 55e. The reservoir bag 55e serves to store the aerosol particles generated by the nebulizer 53e during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The bag 55e has two small inlets 56e and 57e to be connected to one or more gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The outlet tube 16f of the MDI chamber 1f has two valve assemblies disposed between the inlet end 17f and the outlet end 18f—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 32f that has a circular opening 33f and a flap valve 34f as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 35f that has a circular opening 36f and a flap valve 37f as demonstrated by the dotted line. On inhalation, the inhalation flap valve 34f moves away from the valve seat 32f for the aerosol particles to move from the MDI chamber 1f to the patient through the opening 33f in the valve seat 32f of the tube 16f. On exhalation, the flap valve 34f moves towards the flap valve seat 32f and closes the opening 33f to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 1f thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 32f prevents any protrusion of the flap valve 34f through the opening 33f. The exhalation flap valve assembly has a flap valve 37f that presses against the flap valve seat 35f on inhalation and completely occludes the opening 36f to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 16f on inhalation. On exhalation the flap valve 37f moves away from the flap valve seat 35f for the air exhaled by the patient to escape into the atmosphere from tube 16f through the opening 36f.
The nebulizer chamber 4f has a hollow cylindrical inlet tube 38f with an inlet end 39f and an outlet end 40f. The inlet and 39f can be attached to a single or multiple gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles and/or to deliver a fixed concentration of oxygen to a hypoxemic patient. The inlet end 39f may have a boot adapter assembly to accommodate the boot of any commercially available MDI and the MDI 24f maybe alternatively be connected to the inlet end 39f of the tube and on actuation the aerosol particles generated by the MDI will be transferred from the nebulizer chamber 4f to the MDI chamber. The inhaler 24f has a boot 25f with an inlet end 26f and an outlet end 27f. A canister 28f is introduced into the boot 25f through the inlet end 26f and the nozzle 29f of the MDI 24f is attached to an actuator 30f. The actuator 30f has an opening or an aperture 31f. On actuation of the MDI canister 28f, the medication aerosol particles are generated through the opening 31f of the actuator 30f.
The nebulizer chamber has an inlet port 52f for connection with a standard small volume nebulizer 53f. The aerosol medication generated with the nebulizer 53f can enter the MDI chamber via a central connection between the MDI chamber and the nebulizer chamber 2f6f. Chamber 4f also has another inlet 54f for connection a reservoir bag 55f. The reservoir bag 55f serves to store the aerosol particles generated by the nebulizer 53f during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The bag 55f has two small inlets 56f and 57f to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The outlet tube 73a of the MDI chamber 58a has two valve assemblies disposed between the inlet end 74a and the outlet end 75a—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 89a that has a circular opening 90a and a flap valve 91a as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 92a that has a circular opening 93a and a flap valve 94a as demonstrated by the dotted line. On inhalation, the inhalation flap valve 91a moves away from the valve seat 89a for the aerosol particles to move from the MDI chamber 58a to the patient through the opening 90a in the valve seat 89a of the tube 73a. On exhalation, the flap valve 91a moves towards the flap valve seat 89a and closes the opening 90a to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 58a thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 89a prevents any protrusion of the flap valve 91a through the opening 90a. The exhalation flap valve assembly has a flap valve 94a that presses against the flap valve seat 92a on inhalation and completely occludes the opening 93a to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 73a on inhalation. On exhalation the flap valve 94a moves away from the flap valve seat 92a for the air exhaled by the patient to escape into the atmosphere from tube 73a through the opening 93a.
The nebulizer chamber 61a has a hollow cylindrical outlet tube 98a that has an inlet end 99a and an outlet end 100a. The outlet end 100a may remain plugged with a cap when the device is in use with a metered dose inhaler. The nebulizer chamber also has two hollow cylindrical tubes, 101a and 104a, at three o'clock and nine o'clock positions. Tube 101a has an inlet end 102a and an outlet end 103a, whereas the tube 104a has an inlet end 105a and an outlet end 106a. The inlet end 68a of the tube 67a is connected to the outlet end 103a of the tube 101a with a collapsible/expandable stiff corrugated plastic tubing 107a and similarly the inlet end 71a of tube 70a is connected to the outlet end 106a of tube 104a with a collapsible/expandable corrugated plastic tubing 108a. The collapsible/expandable tubings 107a and 108a are demonstrated to be fully expanded in
Nebulizer chamber 61a may have another inlet 11a for connection to a reservoir bag 112a. The bag 112a may have two small inlets 113a and 114a to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. Alternatively, the reservoir bag 112a may be replaced by a corrugated plastic reservoir tubing or chamber 115a that may be connected to inlet 111a or to the inlet end 62a of the nebulizer chamber 61a. The reservoir tubing/chamber 115a may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 116a and grooves 117a. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 118a of the coil are demonstrated in the figure as dotted lines. The distance 119a and 120a between the two adjacent ridges, rings of the coil, or grooves may be equal. The reservoir bag 112a or reservoir tubing 115a serves to store the aerosol particles generated by the nebulizer 110a during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The reservoir tubing has an inlet end 121a that may have a hollow cylindrical inlet tube 95a with an inlet end 96a and an outlet end 97a. The inlet and 96a can be attached to a single or multiple gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The outlet tube 73b of the MDI chamber 58b has two valve assemblies disposed between the inlet end 74b and the outlet end 75b—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 89b that has a circular opening 90b and a flap valve 91b as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 92b that has a circular opening 93b and a flap valve 94b as demonstrated by the dotted line. On inhalation, the inhalation flap valve 91b moves away from the valve seat 89b for the aerosol particles to move from the MDI chamber 58b to the patient through the opening 90b in the valve seat 89b of the tube 73b. On exhalation, the flap valve 91b moves towards the flap valve seat 89b and closes the opening 90b to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 58b thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 89b prevents any protrusion of the flap valve 91b through the opening 90b. The exhalation flap valve assembly has a flap valve 94b that presses against the flap valve seat 92b on inhalation and completely occludes the opening 93b to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 73b on inhalation. On exhalation the flap valve 94b moves away from the flap valve seat 92b for the air exhaled by the patient to escape into the atmosphere from tube 73b through the opening 93b. The nebulizer chamber 61b has a hollow cylindrical inlet tube 95b with an inlet end 96b and an outlet end 97b. The inlet and 96b can be attached to a single or multiple gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The nebulizer chamber 61b has a hollow cylindrical outlet tube 98b that has an inlet end 99b and an outlet end 100b. The outlet end 100b may remain plugged with a cap when the device is in use with a metered dose inhaler. The nebulizer chamber also has two hollow cylindrical tubes, 101b and 104b, at three o'clock and nine o'clock positions. Tube 101b has an inlet end 102b and an outlet end 103b, whereas the tube 104b has an inlet end 105b and an outlet end 106b. The inlet end 68b of the tube 67b is connected to the outlet end 103b of the tube 101b with a collapsible/expandable stiff corrugated plastic tubing 107b and similarly the inlet end 71b of tube 70b is connected to the outlet end 106b of tube 104b with a collapsible/expandable corrugated plastic tubing 108b. The collapsible/expandable tubings 107b and 108b are demonstrated to be fully expanded in
Nebulizer chamber 61b may have another inlet 111b for connection to a reservoir bag 112b. The bag 112b may have two small inlets 113b and 114b to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. Alternatively, the reservoir bag 112b may be replaced by a corrugated plastic reservoir tubing/chamber 115b that may be connected to inlet 111b or to the inlet end 62b of the nebulizer chamber 61b. The reservoir tubing/chamber 115b may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 116b and grooves 117b. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 118b of the coil are demonstrated in the figure as dotted lines. The distance 119b and 120b between the two adjacent ridges, rings of the coil, or grooves may be equal. The reservoir bag 112b or reservoir tubing 115b serves to store the aerosol particles generated by the nebulizer 110b during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The reservoir tubing has an inlet end 121b that may have a hollow cylindrical inlet tube 95b with an inlet end 96b and an outlet end 97b. The inlet and 96b can be attached to a single or multiple gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The outlet tube 73c of the MDI chamber 58a has two valve assemblies disposed between the inlet end 74c and the outlet end 75c—the inhalation valve assembly and an exhalation valve assembly The inhalation flap valve assembly has a circular flap valve seat 89c that has a circular opening 90c and a flap valve 91c as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 92c that has a circular opening 93c and a flap valve 94c as demonstrated by the dotted line. On inhalation, the inhalation flap valve 91c moves away from the valve seat 89c for the aerosol particles to move from the MDI chamber 58c to the patient through the opening 90c in the valve seat 89c of the tube 73c. On exhalation, the flap valve 91c moves towards the flap valve seat 89c and closes the opening 90c to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 58c thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 89c prevents any protrusion of the flap valve 91c through the opening 90c. The exhalation flap valve assembly has a flap valve 94c that presses against the flap valve seat 92c on inhalation and completely occludes the opening 93c to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 73c on inhalation. On exhalation the flap valve 94c moves away from the flap valve seat 92c for the air exhaled by the patient to escape into the atmosphere from tube 73c through the opening 93c. The nebulizer chamber 61c has a hollow cylindrical inlet tube 95c with an inlet end 96c and an outlet end 97c. The inlet and 96c can be attached to a single or multiple gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The nebulizer chamber 61c has a hollow cylindrical outlet tube 98c that has an inlet end 99c and an outlet end 100c. The nebulizer chamber also has two hollow cylindrical tubes, 101c and 104c, at three o'clock and nine o'clock positions. Tube 101c has an inlet end 102c and an outlet end 103c, whereas the tube 104c has an inlet end 105c and an outlet end 106c. The inlet end 68c of the tube 67c is connected to the outlet end 103c of the tube 101c with a collapsible/expandable stiff corrugated plastic tubing 107c and similarly the inlet end 71c of tube 70c is connected to the outlet end 106c of tube 104c with a collapsible/expandable corrugated plastic tubing 108c. Quite unlike
Nebulizer chamber 61c may have another inlet 111c for connection to a reservoir bag 112c. The bag 112c may have two small inlets 113c and 114c to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. Alternatively, the reservoir bag 112c may be replaced by a corrugated plastic reservoir tubing/chmaber 115c that may be connected to inlet 111c or to the inlet end 62c of the nebulizer chamber 61c. The reservoir tubing/chamber 115c may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 116c and grooves 117c. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 118c of the coil are demonstrated in the figure as dotted lines. The distance 119c and 120c between the two adjacent ridges, rings of the coil, or grooves may be equal. The reservoir bag 112c or reservoir tubing 115c serves to store the aerosol particles generated by the nebulizer 110c during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The reservoir tubing has an inlet end 121c that may have a hollow cylindrical inlet tube 95c with an inlet end 96c and an outlet end 97c. The inlet end 96c can be attached to a single or multiple gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the The MDI 81c can be connected to the inlet 97c and on actuation the aerosol particles generated by the MDI will be transferred from the nebulizer chamber 61c to the MDI chamber 58c via the central and two peripheral connections between the two chambers as described before. On actuation of the MDI canister 85c, the medication aerosol particles are generated through the opening 88c of the actuator 87c, and enter into the chamber 58 through the outlet end 66c of the tube 64c.
The outlet tube 73d of the MDI chamber 58d has two valve assemblies disposed between the inlet end 74d and the outlet end 75d—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 89d that has a circular opening 90d and a flap valve 91d as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 92d that has a circular opening 93d and a flap valve 94d as demonstrated by the dotted line. On inhalation, the inhalation flap valve 91d moves away from the valve seat 89d for the aerosol particles to move from the MDI chamber 58d to the patient through the opening 90d in the valve seat 89d of the tube 73d. On exhalation, the flap valve 91d moves towards the flap valve seat 89d and closes the opening 90d to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 58d thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 89d prevents any protrusion of the flap valve 91d through the opening 90d. The exhalation flap valve assembly has a flap valve 94d that presses against the flap valve seat 92d on inhalation and completely occludes the opening 93d to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 73d on inhalation. On exhalation the flap valve 94d moves away from the flap valve seat 92d for the air exhaled by the patient to escape into the atmosphere from tube 73d through the opening 93d.
The nebulizer chamber 61d has a hollow cylindrical inlet tube 95d with an inlet end 96d and an outlet end 97d. The inlet and 96d can be attached to a single or multiple gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. The nebulizer chamber 61d has a hollow cylindrical outlet tube 98d that has an inlet end 99d and an outlet end 100d. The nebulizer chamber also has two hollow cylindrical tubes, 101d and 104d, at three o'clock and nine o'clock positions. Tube 101d has an inlet end 102d and an outlet end 103d, whereas the tube 104d has an inlet end 105d and an outlet end 106d. The inlet end 68d of the tube 67d is connected to the outlet end 103d of the tube 101d with a collapsible/expandable stiff corrugated plastic tubing 107d and similarly the inlet end 71d of tube 70d is connected to the outlet end 106d of tube 104d with a collapsible/expandable corrugated plastic tubing 108d. Quite unlike
Nebulizer chamber 61d may have another inlet 111d for connection to a reservoir bag 112d. The bag 112d may have two small inlets 113d and 114d to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. Alternatively, the reservoir bag 112d may be replaced by a corrugated plastic reservoir tubing/chamber 115d that may be connected to inlet 111d or to the inlet end 62d of the nebulizer chamber 61d. The reservoir tubing/chamber 115d may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 116d and grooves 117d. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 118d of the coil are demonstrated in the figure as dotted lines. The distance 119d and 120d between the two adjacent ridges, rings of the coil, or grooves may be equal. The reservoir bag 112d or reservoir tubing 115d serves to store the aerosol particles generated by the nebulizer 110d during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The reservoir tubing has an inlet end 121d that may have a hollow cylindrical inlet tube 95d with an inlet end 96d and an outlet end 97d. The inlet and 96d can be attached to a single or multiple gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the The MDI 81d can be connected to the inlet 97d and on actuation the aerosol particles generated by the MDI will be transferred from the nebulizer chamber 61d to the MDI chamber 58d via the central and two peripheral connections between the two chambers as described before. On actuation of the MDI canister 85d, the medication aerosol particles are generated through the opening 88d of the actuator 87d, and enter into the chamber 58 through the outlet end 66d of the tube 64d.
The outlet tube 73e of the MDI chamber 58e has two valve assemblies disposed between the inlet end 74e and the outlet end 75e—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 89e that has a circular opening 90e and a flap valve 91e as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 92e that has a circular opening 93e and a flap valve 94e as demonstrated by the dotted line. On inhalation, the inhalation flap valve 91e moves away from the valve seat 89e for the aerosol particles to move from the MDI chamber 58e to the patient through the opening 90e in the valve seat 89e of the tube 73e. On exhalation, the flap valve 91e moves towards the flap valve seat 89e and closes the opening 90e to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 58e thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 89e prevents any protrusion of the flap valve 91e through the opening 90e. The exhalation flap valve assembly has a flap valve 94e that presses against the flap valve seat 92e on inhalation and completely occludes the opening 93e to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 73e on inhalation. On exhalation the flap valve 94e moves away from the flap valve seat 92e for the air exhaled by the patient to escape into the atmosphere from tube 73e through the opening 93e.
The nebulizer chamber 61e has a hollow cylindrical inlet tube 95e with an inlet end 96e and an outlet end 97a. The inlet and 96e can be attached to a single or multiple gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles and/or to deliver a fixed concentration of oxygen to a hypoxemic patient. The inlet end 96e may have a boot adapter assembly to accommodate the boot of any commercially available MDI and the MDI 81e maybe alternatively be connected to the inlet end 96e of the tube and on actuation the aerosol particles generated by the MDI will be transferred from the nebulizer chamber 61e to the MDI chamber. The inhaler 81e has a boot 82e with an inlet end 83e and an outlet end 84e. A canister 85e is introduced into the boot 82e through the inlet end 83e and the nozzle 86e of the MDI 81a is attached to an actuator 87e. The actuator 87e has an opening or an aperture 88e. On actuation of the MDI canister 85e, the medication aerosol particles are generated through the opening 88e of the actuator 87e.
The nebulizer chamber has an inlet port 109e for connection with a standard small volume nebulizer 110e. The aerosol medication generated with the nebulizer 110e can enter the MDI chamber via a central connection between the MDI chamber and the nebulizer chamber 59e63e. Nebulizer chamber 61e may have another inlet 111e for connection to a reservoir bag 112e. The bag 112e may have two small inlets 113e and 114e to be connected to one or more gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. Alternatively, the reservoir bag 112e may be replaced by a corrugated plastic reservoir tubing/chamber 115e that may be connected to inlet 111e or to the inlet end 62e of the nebulizer chamber 61e. The reservoir tubing/chamber 115e may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 116e and grooves 117e. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 118e of the coil are demonstrated in the figure as dotted lines. The distance 119e and 120e between the two adjacent ridges, rings of the coil, or grooves may be equal. The reservoir bag 112e or reservoir tubing 115e serves to store the aerosol particles generated by the nebulizer 110e during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The reservoir tubing has an inlet end 121e that may have a hollow cylindrical inlet tube 95e with an inlet end 96a and an outlet end 97e. The inlet end 96e can be attached to a single or multiple gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. The MDI 81e can be connected to the inlet 97e and on actuation the aerosol particles generated by the MDI will be transferred from the nebulizer chamber 61e to the MDI chamber 58e via the central and two peripheral connections between the two chambers as described before. On actuation of the MDI canister 85e, the medication aerosol particles are generated through the opening 88e of the actuator 87e, and enter into the chamber 58e through the outlet end 66e of the tube 64e.
The outlet tube 73f of the MDI chamber 58f has two valve assemblies disposed between the inlet end 74f and the outlet end 75f—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 89f that has a circular opening 90f and a flap valve 91f as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 92f that has a circular opening 93f and a flap valve 94f as demonstrated by the dotted line. On inhalation, the inhalation flap valve 91f moves away from the valve seat 89f for the aerosol particles to move from the MDI chamber 58f to the patient through the opening 90f in the valve seat 89f of the tube 73f. On exhalation, the flap valve 91f moves towards the flap valve seat 89f and closes the opening 90f to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 58f thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 89f prevents any protrusion of the flap valve 91f through the opening 90f. The exhalation flap valve assembly has a flap valve 94f that presses against the flap valve seat 92f on inhalation and completely occludes the opening 93f to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 73f on inhalation. On exhalation the flap valve 94f moves away from the flap valve seat 92f for the air exhaled by the patient to escape into the atmosphere from tube 73f through the opening 93f.
The nebulizer chamber 61f has a hollow cylindrical inlet tube 95f with an inlet end 96f and an outlet end 97f. The inlet and 96f can be attached to a single or multiple gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles and/or to deliver a fixed concentration of oxygen to a hypoxemic patient. The inlet end 96f may have a boot adapter assembly to accommodate the boot of any commercially available MDI and the MDI 81f maybe alternatively be connected to the inlet end 96f of the tube and on actuation the aerosol particles generated by the MDI will be transferred from the nebulizer chamber 61f to the MDI chamber. The inhaler 81f has a boot 82f with an inlet end 83f and an outlet end 84f. A canister 85f is introduced into the boot 82f through the inlet end 83f and the nozzle 86f of the MDI 81f is attached to an actuator 87f. The actuator 87f has an opening or an aperture 88f. On actuation of the MDI canister 85f, the medication aerosol particles are generated through the opening 88f of the actuator 87f.
The nebulizer chamber has an inlet port 109f for connection with a standard small volume nebulizer 110f. The aerosol medication generated with the nebulizer 110f can enter the MDI chamber via a central connection between the MDI chamber and the nebulizer chamber 59f63f. Nebulizer chamber 61f may have another inlet 111f for connection to a reservoir bag 112f. The bag 112f may have two small inlets 113f and 114f to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. Alternatively, the reservoir bag 112f may be replaced by a corrugated plastic reservoir tubing/chamber 115f that may be connected to inlet 111f or to the inlet end 62f of the nebulizer chamber 61f. The reservoir tubing/chamber 115f may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 116f and grooves 117f. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 118f of the coil are demonstrated in the figure as dotted lines. The distance 119f and 120f between the two adjacent ridges, rings of the coil, or grooves may be equal. The reservoir bag 112f or reservoir tubing 115f serves to store the aerosol particles generated by the nebulizer 110f during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The reservoir tubing has an inlet end 121f that may have a hollow cylindrical inlet tube 95f with an inlet end 96f and an outlet end 97f. The inlet and 96f can be attached to a single or multiple gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. The MDI 81f can be connected to the inlet 97f and on actuation the aerosol particles generated by the MDI will be transferred from the nebulizer chamber 61f to the MDI chamber 58f via the central and two peripheral connections between the two chambers as described before. On actuation of the MDI canister 85f, the medication aerosol particles are generated through the opening 88f of the actuator 87f, and enter into the chamber 58 through the outlet end 66f of the tube 64f.
FIGS. 3A,3B,3C,3D,3E, and 3F are the plan views of the MDI chamber 1a as described in
FIGS. 4A,4B,4C,4D,4E, and 4F are expanded plan views of the collapsible/expandable tubings 50a and 51a as described in
The inlet end has been illustrated in this figure as 148a (corresponds to 2a of
The MDI chamber 178a has an outlet end 180a. The nebulizer chamber 181a has an inlet end 182a. The inlet end of the MDI chamber and the outlet end of the nebulizer chamber are fused together, the fused ends are labeled as 1792a183a. The outlet end 180a of the MDI chamber 178a has a hollow cylindrical tube 193a with an inlet end 194a and an outlet end 195a. The MDI chamber 178a may be made of plastic, paper, or metal. The chamber 178a may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 196a and grooves 197a. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 198a of the coil are demonstrated in the figure as dotted lines. The distance 199a and 200a between the two adjacent ridges, rings of the coil, or grooves may be equal. The outlet tube 193a of the MDI chamber 178a has two valve assemblies disposed between the inlet end 194a and the outlet end 195a—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 209a that has a circular opening 210a and a flap valve 211a as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 212a that has a circular opening 213a and a flap valve 214a as demonstrated by the dotted line. On inhalation, the inhalation flap valve 211a moves away from the valve seat 209a for the aerosol particles to move from the MDI chamber 178a to the patient through the opening 210a in the valve seat 209a of the tube 193a. On exhalation, the flap valve 211a moves towards the flap valve seat 209a and closes the opening 210a to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 178a thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 209a prevents any protrusion of the flap valve 211a through the opening 210a. The exhalation flap valve assembly has a flap valve 214a that presses against the flap valve seat 212a on inhalation and completely occludes the opening 213a to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 193a on inhalation. On exhalation the flap valve 214a moves away from the flap valve seat 212a for the air exhaled by the patient to escape into the atmosphere from tube 193a through the opening 213a. The nebulizer chamber 181a has a hollow cylindrical inlet tube 215a with an inlet end 216a and an outlet end 217a. The inlet and 216a can be attached to a single or multiple gas sources to obtain a mixture of gases with a desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles and/or to deliver a fixed concentration of oxygen to a hypoxemic patient. Alternatively, a universal actuator 207a may be disposed between the inlet end 216e and the outlet end 217a of the tube 215a. The nozzle 206a of a canister 205a of any commercially available MDI may be attached to an actuator 207a. The actuator 207a has an opening or an aperture 208a. On actuation of the MDI canister 205a, the medication aerosol particles are generated through the opening 208a of the actuator 207a.
The nebulizer chamber has an inlet port 229a for connection with a standard small volume nebulizer 230a. The aerosol medication generated with the nebulizer 230a can enter the MDI chamber via a central connection between the MDI chamber and the nebulizer chamber 179a183a. Chamber 181a also has another inlet 231a for connection a reservoir bag 232a. The reservoir bag 232a serves to store the aerosol particles generated by the nebulizer 230a during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The bag 232a has two small inlets 233a and 234a to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The MDI chamber 178b has an outlet end 180b. The nebulizer chamber 181b has an inlet end 182b which may be a single opening or it may have multiple micrometric openings. The inlet end of the MDI chamber and the outlet end of the nebulizer chamber are fused together, the fused ends are labeled as 179b183b. The outlet end 180b of the MDI chamber 178b has a hollow cylindrical tube 193b with an inlet end 194b and an outlet end 195b. The MDI chamber 178b may be made of plastic, paper, or metal. The chamber 178b may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 196b and grooves 197b. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 198b of the coil are demonstrated in the figure as dotted lines. The distance 199b and 200b between the two adjacent ridges, rings of the coil, or grooves may be equal. The outlet tube 193b of the MDI chamber 178b has two valve assemblies disposed between the inlet end 194b and the outlet end 195b—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 209b that has a circular opening 210b and a flap valve 211b as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 212b that has a circular opening 213b and a flap valve 214b as demonstrated by the dotted line. On inhalation, the inhalation flap valve 211b moves away from the valve seat 209b for the aerosol particles to move from the MDI chamber 178b to the patient through the opening 210b in the valve seat 209b of the tube 193b. On exhalation, the flap valve 211b moves towards the flap valve seat 209b and closes the opening 210b to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 178b thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 209b prevents any protrusion of the flap valve 211b through the opening 210b. The exhalation flap valve assembly has a flap valve 214b that presses against the flap valve seat 212b on inhalation and completely occludes the opening 213b to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 193b on inhalation. On exhalation the flap valve 214b moves away from the flap valve seat 212b for the air exhaled by the patient to escape into the atmosphere from tube 193b through the opening 213b.
The nebulizer chamber 181b is connected to two hollow cylindrical concentric tubes—a hollow cylindrical inner inlet tube 215b with an inlet end 216b and an outlet end 217b. The inlet end 216b of the inner concentric hollow tube is closed and the outlet end 217b is open and in communication with the nebulizer chamber 181b. A universal actuator 207b may be disposed between the inlet end 216b and the outlet end 217b of the tube 215b. The nozzle 206b of a canister 205b of any commercially available MDI may be attached to an actuator 207b. The actuator 207b has an opening or an aperture 208b. On actuation of the MDI canister 205a, the medication aerosol particles are generated through the opening 208b of the actuator 207b and the medication delivered into the nebulizer chamber 181b through outlet end 217b of the tube 215b. The outlet concentric tube 235b is fused with the inlet end 182b of the nebulizer chamber 181b at one end and has an opening 236a at the opposite end. Hence the gas(es) from the atmosphere or another outside gas source can flow into the nebulizer chamber 181b from the inlet opening 236b of the outer concentric tube 235b through the connection between the outer concentric tube and the inlet end 182b of the nebulizer chamber 181b. The flow is only peripheral and there is no central flow as the inlet end 216b of the inner concentric tube 215b is closed. The open end 236b of the outer concentric tube 235a can be attached to one or more gas sources to yield a mixture of gas(es) with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The nebulizer chamber has an inlet port 229b for connection with a standard small volume nebulizer 230b. The aerosol medication generated with the nebulizer 230b can enter the MDI chamber via a central connection between the MDI chamber and the nebulizer chamber 179e183e. Chamber 181b also has another inlet 231b for connection a reservoir bag 232b. The reservoir bag 232b serves to store the aerosol particles generated by the nebulizer 230b during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The bag 232b has two small inlets 233b and 234b to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The MDI chamber 178c has an outlet end 180c. The nebulizer chamber 181c has an inlet end 182c which may be a single opening or it may have multiple micrometric openings. The inlet end of the MDI chamber and the outlet end of the nebulizer chamber are fused together, the fused ends are labeled as 179c183c. The outlet end 180c of the MDI chamber 178c has a hollow cylindrical tube 193c with an inlet end 194c and an outlet end 195c. The MDI chamber 178c may be made of plastic, paper, or metal. The chamber 178c may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 196c and grooves 197c. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 198c of the coil are demonstrated in the figure as dotted lines. The distance 199c and 200c between the two adjacent ridges, rings of the coil, or grooves may be equal. The outlet tube 193c of the MDI chamber 178c has two valve assemblies disposed between the inlet end 194c and the outlet end 195c—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 209c that has a circular opening 210c and a flap valve 211c as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 212c that has a circular opening 213c and a flap valve 214c as demonstrated by the dotted line. On inhalation, the inhalation flap valve 211c moves away from the valve seat 209c for the aerosol particles to move from the MDI chamber 178c to the patient through the opening 210c in the valve seat 209c of the tube 193c. On exhalation, the flap valve 211c moves towards the flap valve seat 209c and closes the opening 210c to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 178c thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 209c prevents any protrusion of the flap valve 211c through the opening 210c. The exhalation flap valve assembly has a flap valve 214c that presses against the flap valve seat 212c on inhalation and completely occludes the opening 213c to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 193c on inhalation. On exhalation the flap valve 214c moves away from the flap valve seat 212c for the air exhaled by the patient to escape into the atmosphere from tube 193c through the opening 213c.
The nebulizer chamber 181c is connected to two hollow cylindrical concentric tubes—a hollow cylindrical inner inlet tube 215c with an inlet end 216c and an outlet end 217c. The inlet end 216c of the inner concentric hollow tube is open and the outlet end 217c is in communication with the nebulizer chamber 181c. A universal actuator 207c may be disposed between the inlet end 216c and the outlet end 217c of the tube 215c. The nozzle 206c of a canister 205c of any commercially available MDI may be attached to an actuator 207c. The actuator 207c has an opening or an aperture 208c. On actuation of the MDI canister 205c, the medication aerosol particles are generated through the opening 208c of the actuator 207c and the medication delivered into the nebulizer chamber 181c through outlet end 217c of the tube 215c. The outlet concentric tube 235c is fused with the inlet end 182c of the nebulizer chamber 181c at one end and has an opening 236c at the opposite end. Hence the gas(es) from the atmosphere or another outside gas source can flow into the nebulizer chamber 181c from the inlet openings 236c of the outer concentric tube 235c and the inlet opening 216c of the inner concentric tube 235c through the connections between the outer concentric tube 235c and the nebulizer chamber 181c and the inner concentric tube 215c and the inlet end 182c of the nebulizer chamber 181c. The flow is now both central and peripheral from the outside source to the nebulizer chamber. The open end 236c of the outer concentric tube 235c and the open end 216c of the inner tube 215c can be attached to one or more gas sources to yield a mixture of gas(es) with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The nebulizer chamber has an inlet port 229c for connection with a standard small volume nebulizer 230c. The aerosol medication generated with the nebulizer 230c can enter the MDI chamber via a central connection between the MDI chamber and the nebulizer chamber 179c183c. Chamber 181c also has another inlet 231c for connection a reservoir bag 232c. The reservoir bag 232c serves to store the aerosol particles generated by the nebulizer 230c during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The bag 232c has two small inlets 233c and 234c to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
The MDI chamber 178d has an outlet end 180d. The nebulizer chamber 181d has an inlet end 182d. The inlet end of the MDI chamber land the outlet end of the nebulizer chamber are fused together, the fused ends are labeled as 179d183d. The outlet end 180d of the MDI chamber 178d has a hollow cylindrical tube 193d with an inlet end 194d and an outlet end 195d. The MDI chamber 178d may be made of plastic, paper, or metal. The chamber 178d may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 196d and grooves 197d. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 198a of the coil are demonstrated in the figure as dotted lines. The distance 199d and 200d between the two adjacent ridges, rings of the coil, or grooves may be equal.
The outlet tube 193d of the MDI chamber 178d has two valve assemblies disposed between the inlet end 194d and the outlet end 195d—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 209d that has a circular opening 210d and a flap valve 211d as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 212d that has a circular opening 213d and a flap valve 214d as demonstrated by the dotted line. On inhalation, the inhalation flap valve 211d moves away from the valve seat 209d for the aerosol particles to move from the MDI chamber 178d to the patient through the opening 210d in the valve seat 209d of the tube 193d. On exhalation, the flap valve 211d moves towards the flap valve seat 209d and closes the opening 210d to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 178d thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 209d prevents any protrusion of the flap valve 211d through the opening 210d. The exhalation flap valve assembly has a flap valve 214d that presses against the flap valve seat 212d on inhalation and completely occludes the opening 213d to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 193d on inhalation. On exhalation the flap valve 214d moves away from the flap valve seat 212d for the air exhaled by the patient to escape into the atmosphere from tube 193d through the opening 213d.
The nebulizer chamber 181d has an hollow cylindrical inlet tube 215d at it's inlet end 182d. The inlet tube 215d has an inlet end 216d and an outlet end 217d. The inlet end 182d of the nebulizer chamber 181d may be closed at it's periphery 246d shown as the shaded area in the figure and open in the center 247d where it fuses with the tube 215d and the two openings 217d and 247d fuse with each other. A universal actuator 207d may be disposed between the inlet end 216d and the outlet end 217d of the tube 215d. The nozzle 206d of a canister 205d of any commercially available MDI may be attached to an actuator 207d. The actuator 207d has an opening or an aperture 208d. On actuation of the MDI canister 205d, the medication aerosol particles are generated through the opening 208d of the actuator 207d. The flow of the gas(es) from the nebulizer chamber 181d to the MDI chamber is central through the opening 216d of the tube 215d as the peripheral part of the MDI chambers inlet 182d is closed.
The nebulizer chamber has an inlet port 229d for connection with a standard small volume nebulizer 230d. The aerosol medication generated with the nebulizer 230d can enter the MDI chamber via a central connection between the MDI chamber and the nebulizer chamber 179e183e. Chamber 181d also has another inlet 231d for connection a reservoir bag 232d. The reservoir bag 232d serves to store the aerosol particles generated by the nebulizer 230d during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The bag 232d has two small inlets 233d and 234d to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient. Alternatively, the reservoir bag 232d may be replaced by a corrugated plastic reservoir tubing 237d that may be connected to inlet end 216d of the nebulizer chamber 181d. The reservoir tubing 237d may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 238d and grooves 239d. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 240d of the coil are demonstrated in the figure as dotted lines. The distance 241d and 242d between the two adjacent ridges, rings of the coil, or grooves may be equal. The reservoir bag 232d or reservoir tubing 237d serves to store the aerosol particles generated by the nebulizer 230d during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The reservoir tubing has an inlet end 238d that may have a hollow cylindrical inlet tube 243d with an inlet end 244d and an outlet end 245d. The inlet end 244d can be attached to a single or multiple gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the The MDI 205d can be connected to the inlet end 244d of the inlet tube 243d and on actuation the aerosol particles generated by the MDI will be transferred from the reservoir tubing 232d to the nebulizer chamber 181d and then to the MDI chamber 178d.
The MDI chamber 178e has an outlet end 180e. The nebulizer chamber 181e has an inlet end 182e. The inlet end of the MDI chamber and the outlet end of the nebulizer chamber are fused together, the fused ends are labeled as 179183e. The outlet end 180e of the MDI chamber 178e has a hollow cylindrical tube 193e with an inlet end 194e and an outlet end 195e. The MDI chamber 178e may be made of plastic, paper, or metal. The chamber 178e may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 196e and grooves 197e. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 198e of the coil are demonstrated in the figure as dotted lines. The distance 199e and 200e between the two adjacent ridges, rings of the coil, or grooves may be equal.
The outlet tube 193e of the MDI chamber 178e has two valve assemblies disposed between the inlet end 194e and the outlet end 195e—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 209e that has a circular opening 210e and a flap valve 211e as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 212e that has a circular opening 213e and a flap valve 214e as demonstrated by the dotted line. On inhalation, the inhalation flap valve 211e moves away from the valve seat 209e for the aerosol particles to move from the MDI chamber 178e to the patient through the opening 210e in the valve seat 209e of the tube 193e. On exhalation, the flap valve 211e moves towards the flap valve seat 209e and closes the opening 210e to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 178e thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 209e prevents any protrusion of the flap valve 211e through the opening 210e. The exhalation flap valve assembly has a flap valve 214e that presses against the flap valve seat 212e on inhalation and completely occludes the opening 213e to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 193e on inhalation. On exhalation the flap valve 214e moves away from the flap valve seat 212e for the air exhaled by the patient to escape into the atmosphere from tube 193e through the opening 213e.
The nebulizer chamber 181e has an hollow cylindrical inlet tube 215e at it's inlet end 182e. The inlet tube 215e has an inlet end 216e and an outlet end 217e. The inlet end 182e of the neulizer chamber 181e is open quite unlike the closed periphery 246e shown as the shaded area in
The nebulizer chamber has an inlet port 229e for connection with a standard small volume nebulizer 230e. The aerosol medication generated with the nebulizer 230e can enter the MDI chamber via a central connection between the MDI chamber and the nebulizer chamber 179e183e. Chamber 181e also has another inlet 231e for connection a reservoir bag 232e. The reservoir bag 232e serves to store the aerosol particles generated by the nebulizer 230e during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The bag 232e has two small inlets 233e and 234e to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
Alternatively, the reservoir bag 232e may be replaced by a corrugated plastic reservoir tubing 237e that may be connected to inlet end 216e of the nebulizer chamber 181e. The reservoir tubing 237e may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 238e and grooves 239e. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 240e of the coil are demonstrated in the figure as dotted lines. The distance 241e and 242e between the two adjacent ridges, rings of the coil, or grooves may be equal. The reservoir bag 232e or reservoir tubing 237e serves to store the aerosol particles generated by the nebulizer 230e during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The reservoir tubing has an inlet end 238e that may have a hollow cylindrical inlet tube 243e with an inlet end 244e and an outlet end 245e. The inlet end 244e can be attached to a single or multiple gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the The MDI 205e can be connected to the inlet end 244e of the inlet tube 243e and on actuation the aerosol particles generated by the MDI will be transferred from the reservoir tubing 232e to the nebulizer chamber 181e and then to the MDI chamber 178e.
The MDI chamber 178f has an outlet end 180f. The nebulizer chamber 181f has an inlet end 182f. The inlet end of the MDI chamber and the outlet end of the nebulizer chamber are fused together, the fused ends are labeled as 179f183f. The outlet end 180f of the MDI chamber 178f has a hollow cylindrical tube 193f with an inlet end 194f and an outlet end 195f. The MDI chamber 178f may be made of plastic, paper, or metal. The chamber 178f may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 196f and grooves 197f. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 198f of the coil are demonstrated in the figure as dotted lines. The distance 199f and 200f between the two adjacent ridges, rings of the coil, or grooves may be equal.
The outlet tube 193f of the MDI chamber 178f has two valve assemblies disposed between the inlet end 194f and the outlet end 195f—the inhalation valve assembly and an exhalation valve assembly. The inhalation flap valve assembly has a circular flap valve seat 209f that has a circular opening 210f and a flap valve 211f as demonstrated by the dotted line. The exhalation valve assembly has a circular flap valve seat 212f that has a circular opening 213f and a flap valve 214f as demonstrated by the dotted line. On inhalation, the inhalation flap valve 211f moves away from the valve seat 209f for the aerosol particles to move from the MDI chamber 178f to the patient through the opening 210f in the valve seat 209f of the tube 193f. On exhalation, the flap valve 211f moves towards the flap valve seat 209f and closes the opening 210f to prevent any flow of gas exhaled by the patient from entering into the MDI chamber 178f thus avoiding re-breathing of carbon dioxide on the next inhalation. The flap valve seat 209f prevents any protrusion of the flap valve 211f through the opening 210f. The exhalation flap valve assembly has a flap valve 214f that presses against the flap valve seat 212f on inhalation and completely occludes the opening 213f to prevent any room air entrainment i.e. not allowing the air from the atmosphere to enter into the tube 193f on inhalation. On exhalation the flap valve 214f moves away from the flap valve seat 212f for the air exhaled by the patient to escape into the atmosphere from tube 193f through the opening 213f.
The nebulizer chamber 181f has an hollow cylindrical inlet tube 215f at it's inlet end 182f. The inlet tube 215f has an inlet end 216f and an outlet end 217f. The inlet end 182f of the neulizer chamber 181f is open quite like the opening in
The nebulizer chamber has an inlet port 229f for connection with a standard small volume nebulizer 230f. The aerosol medication generated with the nebulizer 230f can enter the MDI chamber via a central connection between the MDI chamber and the nebulizer chamber 179f183f. Chamber 181f also has another inlet 231f for connection a reservoir bag 232f. The reservoir bag 232f serves to store the aerosol particles generated by the nebulizer 230f during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The bag 232f has two small inlets 233f and 234f to be connected to one or more gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the delivery of aerosol particles as well as deliver a fixed concentration of oxygen to a hypoxemic patient.
Alternatively, the reservoir bag 232f may be replaced by a corrugated plastic reservoir tubing 237f that may be connected to inlet end 216f of the nebulizer chamber 181f. The reservoir tubing 237f may be a fixed volume chamber or a collapsible/expandable chamber. The chamber may be cylindrical with smooth edges or cylindrical with multiple ridges 238f and grooves 239f. The chamber may be made of stiff corrugated plastic that may not require any additional support to maintain patency of the chamber. Alternatively the chamber may be supported with a metal or plastic coil with multiple rings. The multiple rings 240f of the coil are demonstrated in the figure as dotted lines. The distance 241f and 242f between the two adjacent ridges, rings of the coil, or grooves may be equal. The reservoir bag 232f or reservoir tubing 237f serves to store the aerosol particles generated by the nebulizer 230f during the exhalation phase to be inhaled on the next breath thus improving aerosol medication delivery. The reservoir bag may be made of plastic, neoprene, paper, or metal. The reservoir tubing has an inlet end 238f that may have a hollow cylindrical inlet tube 243f with an inlet end 244f and an outlet end 245f. The inlet end 244f can be attached to a single or multiple gas sources to obtain a mixture of gases with desired density, oxygen concentration, viscosity, and humidity to improve the The MDI 205f can be connected to the inlet end 244f of the inlet tube 243f and on actuation the aerosol particles generated by the MDI will be transferred from the reservoir tubing 232f to the nebulizer chamber 181f and then to the MDI chamber 178f.
It is noted that the illustration (drawings) and description of the preferred embodiments have been provided merely for the purpose of explanation and although the invention has been described herein with reference to particular means, materials and embodiments, the invention is not intended to be limited to the particulars disclosed herein; rather the invention intents to all functionally equivalent structures, methods and uses such as are within the scope of the appended claims.
Claims
1) An aerosol inhalation apparatus, comprising:
- collapsible/expandable first housing or a fixed first housing or a partially fixed and a partially collapsible/expandable first housing with a configuration of a cylinder, a bell, a pear, a cone, or any three dimensional polygon;
- a first housing that is fully collapsible into a substantially compact minimum volume, fully expandable to a maximum volume and partially expandable to different volumes;
- a collapsible/expandable second housing or a fixed second housing or a partially fixed and partially collapsible/expandable second housing;
- the first housing that is connected to the second housing through one of more peripheral and/or central hollow connecting tubes;
- the first housing with an inhalation/exhalation outlet tube at an inhalation/exhalation end of the first housing;
- the inhalation/exhalation outlet tube with an inhalation/exhalation outlet port at the end of the inhalation/exhalation outlet tube;
- a mouthpiece or a facemask connected to the inhalation/exhalation port of the inhalation/exhalation outlet tube;
- the first housing with an inlet tube at a diametrically opposite end of the inhalation/exhalation outlet tube;
- the inlet tube with an inlet port at an end of the inlet tube;
- a boot adapter panel that may be connected to the inlet port of the inlet tube of the first housing;
- the boot adapter panel with an opening for receiving a boot of an MDI inhaler;
- a one way inhalation flap valve assembly that comprises of an inhalation flap valve and a valve seat for the inhalation flap valve that is disposed in the outlet port of the outlet tubing of the first housing;
- the one way inhalation valve assembly whereby inhalation by a patient through the inhalation/exhalation outlet port will cause the inhalation flap valve to move away from the inhalation flap valve seat to allow one way flow of gas(es) from the first housing to a mouth piece or a face mask and exhalation by a patient through the inhalation/exhalation outlet port of the first housing presses the inhalation flap against the inhalation flap valve seat to prevent the flow of exhaled gas into the first housing;
- a one way exhalation flap valve assembly with an exhalation flap valve with and exhalation flap valve seat for the exhalation flap valve that is disposed in a wall of the outlet port of the first housing;
- the one way exhalation flap valve assembly whereby exhalation by a patient through the inhalation/exhalation outlet port will cause the exhalation flap valve to move away from the exhalation flap valve seat to allow one way flow of gas exhaled from the outlet tube to outside atmosphere;
- the one way exhalation flap valve assembly whereby exhalation by a patient through the inhalation/exhalation outlet port will cause exhalation flap valve to move away from the exhalation flap valve seat to allow one way flow of gas from the mouthpiece or the face mask to outside atmosphere and inhalation by a patient through the inhalation/exhalation outlet port will press the exhalation flap valve against the exhalation flap valve seat to prevent the flow of gas from atmosphere to the mouthpiece or facemask or the first housing and hence a patient;
- said one way exhalation flap valve assembly further comprising an exhalation filter in said valve assembly to trap all exhaled aerosol medication but allowing all exhaled gas(es) to escape to atmosphere.
2) The aerosol inhalation apparatus of claim one, comprising:
- a collapsible/expandable first and/or second housing composed of a single piece of material that may be plastic, paper, or metal or a housing that may be composed of a combination of different such materials;
- said housing that may be composed of a stiff corrugated plastic material with multiple ridges and grooves or pleats like an accordion that may be collapsible/expandable
- said housing that does not require any support with a metal or plastic wire for patency;
- said housing that is expandable to a maximum volume by fully stretching all the pleats of the housing and fully collapsible by pulling all the pleats of the housing together and partially expandable/collapsible to any volume between maximum and minimum volumes by pulling the pleats together or stretching them apart;
- said housing with an inlet and an outlet end;
- said housing that may be supported by a metal or plastic wire with 2 free ends;
- the wire, one free end of which terminates at or near the inlet end of the housing and other free end of which terminates at the outlet end of housing;
- said wire that has a configuration of a coil and is arranged in spirals or multiple concentric rings;
- said coil is expandable when the rings are pulled apart;
- said coil is collapsible when the rings are pulled together;
- said housing is expandable when the coil rings are pulled apart and collapsible when the rings are pulled together;
- said housing is fully expandable to bound a fully expanded maximum volume when each ring is pulled apart from an adjoining ring and fully collapsible to minimum volume when each ring is pulled together to an adjoining ring;
- said housing is expandable to bound a first volume when a first coil ring is fully pulled apart from a second coil ring, and all remaining coil rings are pulled together;
- said first volume is expandable to bound a second volume of said housing when a third coil ring is fully pulled apart from the second spiral ring, and all or remaining coil rings pulled together;
- said second volume of housing is expandable to bound a third volume of housing when a fourth spiral ring is fully pulled apart from the third spiral ring, and all remaining coils pulled together;
- a partially expandable/collapsible volume of said housing between a maximum and a minimum volume that is further expandable to any volume less than the maximum volume by pulling apart a ring from an adjoining ring and collapsible tube any volume greater than the minimum volume by pulling together a ring to an adjoining ring;
- said first volume of the housing may be equal to the difference between the second and the first volume, which may be equal to the difference between the third and the second volume, such that each intervening volume obtained by expanding any two adjoining rings may be equal;
- said first volume housing that may be different from the difference between the second and the first volume, such that each intervening volume obtained by expanding any two adjacent rings may be unequal;
- minimum fully collapsible volume wherein the inlet tube of said housing may be fused with the outlet tube of said housing;
- any partially expandable volume of the first housing other than minimum collapsible volume wherein inlet tube of said housing is detached from the outlet tube of said housing;
3) The aerosol inhalation apparatus of claim one, comprising:
- a fixed volume second housing or collapsible/expandable second housing or a partially fixed and a partially expandable/collapsible second housing;
- a housing composed of a corrugated plastic material with multiple ridges/grooves or pleats like an accordion;
- a collapsible/expandable housing composed of a single piece of material;
- said housing with an inlet end and an outlet end;
- said housing with an inhalation/exhalation outlet tube at the outlet end;
- said housing with one or more inlet tubes at the inlet end;
- said inlet tube which may be connected to one or more sources of gas(es) to receive one or more gas(es) into said housing;
- said inlet tube that may be connected to expandable/collapsible corrugated tubing;
- said corrugated tubing that may connected to one or more gas sources;
- said housing with two ports disposed in the wall of the housing between the inlet and outlet end—a port for a nebulizer, and a port for a reservoir;
- said outlet end, which is plugged with a cap when using an MDI and said outlet tube of the second housing is fused with the inlet tube of the first housing when using a nebulizer;
- said reservoir which may be an expandable/collapsible corrugated tubing as described in claim 2 and/or a collapsible/expandable bag made of plastic or neoprene;
- said second housing is connected to the first housing with two peripheral collapsible/expandable connecting tubes;
- the two peripheral connecting tubes that are fully or partially expandable during MDI use to allow a central disconnection between the inlet tubing of the first housing and the outlet tubing of the second housing and to create a room to accommodate the MDI boot between the first and the second housing;
- the two peripheral connecting tubes that are fully collapsible to a minimum volume during nebulizer use to allow a central connection between the inlet tube of the first and the outlet tube of the second housing;
- said second housing wherein a nebulizer is connected to the nebulizer port of the housing to generate aerosol medication that is transferred to the first housing via two peripheral connecting tubes and a central connection between two housings via the outlet tube of the second housing and the inlet tube of the first housing;
- said second housing wherein during MDI use, the outlet tube remains plugged with a cap and the MDI is attached to the inlet tube of the first housing via a universal boot adapter assembly and a gas(es) is transferred from the second housing to the first housing via the two peripheral connecting tubes;
- a reservoir which stores aerosol medication generated by the nebulizer during an exhalation phase of the nebuliser to be used in a subsequent inhalation phase of a respiratory cycle;
- a reservoir that may have one or more inlet ports for one or more gas(es) to enter the reservoir for uniform mixing with the aerosol particles before entering the second housing and prior to inhalation by a patient.
4) An aerosol inhalation apparatus of claim one, comprising:
- two or more peripheral connecting tubes between the first housing and the second housing to allow a passage of aerosol medications and/or one or more gases from the first housing to the second housing;
- said connecting tubes that are cylindrical and are collapsible/expandable;
- said tubes that are collapsible to allow a central fusion of the first housing and the second housing;
- said tubes that could be expanded to make room for accommodating MDI between the first and the second housing;
- said tubes wherein each tube is connected to first and second housing via a single port or opening;
- said tubes wherein each tube after connection with the first housing splits into multiple micrometric openings;
- said multiple micrometric openings that are distributed along the circumference in the inlet of the first housing;
- said openings wherein air entrained into the first housing from the second housing does not interrupt or interfere with a plume generated by an MDI;
- said openings wherein aerosol generated by a nebulizer in the second housing enters the first housing via multiple micrometric openings distributed along entire circumference of the inlet of the first housing.
5) An aerosol inhalation apparatus of claim one, comprising:
- a universal MDI adapter that may be located at the inlet end of the central inlet tube of the first housing;
- the MDI adapter that may be used for delivering aerosol medication by actuation of MDI into the first housing;
- a nebulizer that may generate aerosol medication in the second housing;
- the first housing and the second housing that are connected at a central location by fusion of the outlet tube of the second housing to the inlet tube of the first housing, such as to form a passage to allow the aerosol medication to move between the two housings;
- the first housing and the second housing that may also be connected at peripheral locations by peripheral connecting tubes that are partially or fully collapsible/expandable such as to form a passage to allow the aerosol medication to move between the two housings.
6) The aerosol inhalation apparatus of claim 1:
- useable with a facemask to deliver a desired mixture of gas(es) with a desired density, viscosity, humidity, and fraction of inspired oxygen;
- useable with a facemask to deliver aerosol medication via an MDI and/or a nebulizer with a desired mixture of gas(es) with a desired density, viscosity, humidity, and fraction of inspired oxygen;
- useable in a ventilatory circuit by connecting the outlet tube at the outlet end of the first housing at one end of the ventilatory circuit and the inlet tube at the inlet end of the second housing at other end of the ventilatory circuit;
7) Aerosol inhalation apparatus of claims 2,3,4,5 and 6 comprising:
- a collapsible/expandable or fixed volume first housing;
- a fixed volume, or collapsible/expandable second housing;
- a central connection between the first and the second housing during nebulizer use and during delivery of a desired mixture of gases with or without aerosol medication delivery;
- one or more peripheral connections between the first and the second housing that are collapsible during nebulizer use and expandable during MDI use;
- the peripheral connections that permit delivery of a desired mixture of gas (es) with or without aerosol medication from the second housing to the first housing and hence to a patient;
- the peripheral connections between the first and the second housings that allow a desired mixture gas (es) to be delivered from the second housing to the first housing that is distributed in a pattern that does not interfere with a plume generated by the MDI or the nebulizer;
- first housing, second housing and/or reservoir that are all collapsible/expandable and could be used for pediatric and/or adult patients by expanding and/or collapsing the housings and/or reservoir to a precise desired volume;
- second housing that has a collapsible/expandable reservoir which may be a bag or a corrugated plastic tubing to store aerosol generated during exhalation, and to allow uniform mixing of one or more gases with aerosol medication to be delivered during inhalation to a patient;
- a second housing with one or more inlets for one or more gases to yield and deliver a gas mixture with a desired humidity, density, viscosity, and fraction of inspired oxygen to a patient;
- a closed circuit that serve as 100% non rebreather system with an inhalation valve assembly to prevent any air to be entrained from atmosphere into a circuit during inhalation and an exhalation valve assembly to allow exhaled air to exit a circuit into atmosphere and not allowing rebreathing of the exhaled air;
- a filter that is incorporated into the exhalation valve assembly to trap exhaled aerosol medication, allowing the exhaled gases to escape from the closed circuit to atmosphere and not permit entrainment of gases from atmosphere into the closed circuit;
- an enhanced aerosol delivery via MDI or nebulizer separately or simultaneously via MDI and nebulizer with delivery of a gas mixture of a desired density, viscosity, humidity, and fraction of inspired oxygen during aerosol delivery without disconnecting a patient from a desired gas source during aerosol delivery;
- a reservoir which may be moveable or could be repositioned in the apparatus such that it may be in front of the nebulizer, behind the nebulizer, connected to the nebuliser with a Y or Tee connector may be located in the second housing or be placed in the first housing before the inhalation valve assembly
- The collapsible/expandable first housing that may serve as a reservoir in a closed circuit to store aerosol medication during exhalation if expanded to a certain minimum volume to meet a patient's ventilatory requirement such that no additional reservoir bag or collapsible/expandable corrugated tube may be requited as a reservoir in the second housing;
8) An aerosol inhalation apparatus of claims 1 and 7 comprising:
- a single fixed collapsible/expandable or partially fixed and partially collapsible/expandable first housing;
- the housing has an outlet port for connection to a facemask or a mouthpiece;
- the outlet has two flap valve assemblies—an inhalation and an exhalation valve assembly;
- the housing that has an inlet port for connection with a boot adapter panel;
- the housing that has a port for a nebulizer and a reservoir that is disposed in a wall of the housing between the inlet and outlet ports;
- an inhalation valve assembly in the outlet tube of the first housing which may be a ball valve assembly and not a flap valve assembly such that inhalation by a patient triggers a ball to rise to a higher level and drop to it's original position during exhalation to allow one way flow of aerosol medication and/or gases to a patient and not allow any re-breathing of carbon dioxide exhaled by a patient.
Type: Application
Filed: Mar 30, 2004
Publication Date: Oct 6, 2005
Inventors: Sunil Dhuper (Old Westbury, NY), Sarita Dhuper (Old Westbury, NY)
Application Number: 10/812,618