Patent Application
20240269397
This disclosure relates to droplet delivery devices with ejector mechanisms and more specifically to droplet delivery devices for the delivery of fluids that are inhaled into mouth, throat nose, and/or lungs.
The use of droplet generating devices for the delivery of substances to the respiratory system is an area of large interest. A major challenge is providing a device that delivers an accurate, consistent, and verifiable amount of substance, with a droplet size that is suitable for successful delivery of substance to the targeted area of the respiratory system.
Currently most inhaler type systems, such as metered dose inhalers (MDI), pressurized metered dose inhalers (p-MDI), or pneumatic and ultrasonic-driven devices, generally produce droplets with high velocities and a wide range of droplet sizes including large droplets that have high momentum and kinetic energy. Droplet plumes with large size distributions and high momentum do not reach a targeted area in the respiratory system, but rather are deposited throughout the pulmonary passageways, mouth, and throat. Such non-targeted deposition may be undesirable for many reasons, including improper dosing and unwanted side effects.
Droplet plumes generated from current droplet delivery systems, as a result of their high ejection velocities and the rapid expansion of the substance carrying propellant, may also lead to localized cooling and subsequent condensation, deposition and crystallization of substance onto device surfaces. Blockage of device surfaces by deposited substance residue is also problematic.
Further, conventional droplet delivery devices for delivery of nicotine, including vape pens and the like, typically require fluids that are inhaled to be heated to temperatures that negatively affect the liquid being aerosolized. Specifically, such levels of heating can produce undesirable and toxic byproducts as has been documented in the news and literature.
Accordingly, there is a need for an improved droplet delivery device that delivers droplets of a suitable size range, avoids surface fluid deposition and blockage of apertures, avoids producing undesired chemical byproducts through heating, and in an amount that is consistent and reproducible.
In one embodiment of the push mode invention, a “push mode” droplet delivery device does not include a heating requirement that could result in undesirable byproducts and comprises: a container assembly with an mouthpiece port; a reservoir disposed within or in fluid communication with the container assembly to supply a volume of fluid, an ejector bracket in fluid communication with the reservoir, the ejector bracket including a mesh with a membrane operably coupled to an electronic transducer with the membrane between the transducer and the mesh, wherein the mesh includes a plurality of openings formed through the mesh's thickness, and wherein the transducer is coupled to a power source and is operable to oscillate the membrane and generate an ejected stream of droplets through the mesh, and an ejection channel within the container assembly configured to direct the ejected stream of droplets from the mesh to the outlet. The vibrating membrane “pushing” liquid through the mesh is referred to herein as “push mode” ejection and devices in embodiments of the push mode invention may be referred to as push mode devices.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes an ultrasonic transducer as an electronic transducer, and preferably an ultrasonic transducer that includes piezoelectric material.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes the container assembly having a fluid reservoir.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes an ejector bracket configured for releasably coupling to the container assembly and the ejector bracket further configured for releasable coupling to an enclosure system including an electronic transducer and a power source.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes magnets configured to releasably couple the ejector bracket and enclosure system.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a snap mechanism and/or magnets configured to releasably couple the ejector bracket and the container assembly.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a fluid reservoir with a self-sealing mating mechanism configured to couple to a fluid release mating mechanism of the ejector bracket.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a fluid release mating mechanism that has a fluid conduit configured for insertion into the self-sealing mating mechanism. In a preferred embodiment, a fluid release mating mechanism includes a spike-shaped structure with a hollow interior configured to provide fluid communication between the reservoir and the membrane.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh is configured so that the membrane does not contact the mesh and pushes fluid to be ejected as droplets from the droplet delivery device through openings in the mesh.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes the membrane having a slanted upper surface configured to contact fluid supplied from the reservoir.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a vibrating member having a slanted tip contacting an opposite underlying surface of a slanted upper surface of the membrane.
In further embodiments of the push mode invention, an electronic transducer includes piezoelectric material that is coupled to a vibrating member with a ring-shaped beveled tip, rod-shaped beveled tip, rod-shaped tip, or a ring-shaped non-beveled tip.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a mesh with a bottom surface in a parallel configuration with an upper surface of the membrane.
In another embodiment of the push mode invention, a droplet delivery device having membrane that cooperates with a mesh further includes the mesh including a bottom surface in a non-parallel, i.e., slanted at an angle, configuration with an upper surface of the membrane.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a central axis of the droplet delivery device passing through the ejection channel and the membrane, and wherein the transducer is coupled to a vibrating member that is coupled to the membrane at a position offset from the central axis.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a fluid in the reservoir including at least one of a non-therapeutic substance, nicotine, or cannabinoid.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a fluid in the reservoir including a therapeutic substance that treats or prevents a disease or injury condition.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a laminar flow element positioned in an ejection channel of a container assembly before a mouthpiece port of the delivery device. In preferable embodiments, the laminar flow element includes a plurality of cellular apertures. In some embodiments, a laminar flow element includes blade-shaped walls defining the plurality of cellular apertures. In further embodiments, one or more of the plurality of cellular apertures include a triangular prismatic shape, quadrangular prismatic shape, pentagonal prismatic shape, hexagonal prismatic shape, heptagonal prismatic shape, or octagonal prismatic shape.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a breath-actuated sensor, such as a pressure sensor, operatively coupled to the power source, wherein the breath-actuated senor is configured to activate the electronic transducer upon sensing a predetermined pressure change within the ejection channel or within a passageway of the droplet delivery device in fluid communication with the ejection channel.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes the mesh made of a material of at least one of palladium nickel, polytetrafluoroethylene, and polyimide.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes the mesh made of a material of at least one of poly ether ketone, polyetherimide, polyvinylidine fluoride, ultra-high molecular weight polyethylene, Ni, NiCo, Pd, Pt, NiPd, and metal alloys.
In other embodiments a mesh may be made of single crystalline or poly crystalline materials such as silicon, silicon carbide, aluminum nitride or germanium with hole structures formed using semiconductor processes such as photo lithography and isotropic and anisotropic etching. With photolithography and isotropic and/or anisotropic etches different hole shapes can be formed in a single crystalline wafer with very high precision. Using sputtering, films can be deposited on the surface with different contact angles. Thin layers formed or deposited on the surface will have, in certain embodiments, much better adherence than film deposited on metal mesh formed by galvanic deposition or polymer mesh formed by laser ablation. This better adherence is because the surfaces on the single crystalline wafers “slices” are atomically smooth and can be etched to produce exact surface roughness to facilitate mechanical bonding with glue or other materials. Silicon carbide would be a preferable material because of its high strength and toughness. An important advantage of using semiconductor processes to fabricate hole structures from a single crystalline wafer “slice” in a mesh of embodiment of the push mode invention is that the holes and surface contact angles will be exact without the variation we see in conventional ejector plates using mesh made from galvanic deposition or laser ablation.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes the membrane made a of material of at least one of polyethylene naphthalate, polyethylenimine and poly ether ketone.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes the membrane made a of material of at least one of metal membranes, metalized polymers, threaded polymers, threaded nylon, threaded polymers that are coated with polymers or metal, threaded nylon coated with polymers or metal. threaded metals, threaded SiC, threaded graphite composites, metalized graphite composites, graphite composites coated with polymers, polymer sheets filled with carbon fibers, poly ether ketone filled with carbon fibers, polymer sheets filled with SiC fibers, polymer sheets filled with ceramic or metal fibers, ULPA filter media, NITTO DENKO™ Temic Grade filter media, NITTO DENKO™ polymer sheets, threaded polymers bonded to a polymer sheet, nylon weave bonded to poly ether ketone or polyimide, graphite composites bonded to polymer sheets, polymer fiber weave with metalized coating, and nylon with sputtered on Al or vapor deposited Al.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a PZT-based ultrasonic transducer coupled to a vibrating member having a tip portion made of at least one of Grade 5 titanium alloy, Grade 23 titanium alloy, and about 99% or higher purity titanium. In certain embodiments, the vibrating member's tip includes a sputtered on outer layer of and about 99% or higher purity titanium providing a smooth tip surface configured to contact an underlying bottom surface of the membrane that is opposite an exterior top surface of the membrane positioned nearest the mesh so as to help reduce wear of the membrane and increase the longevity and operation consistency of the membrane (and also possibly vibrating member's tip portion).
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes an exterior surface of the membrane, opposite an underlying surface of the membrane contacting the vibrating member, having a hydrophobic coating.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes an exterior surface of the membrane, opposite an underlying surface of the membrane contacting the vibrating member, having a hydrophilic coating.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a hydrophilic coating on one or more surfaces of the mesh.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a mesh including a hydrophobic coating on one or more surfaces of the mesh.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a hydrophobic coating on a first surface of the mesh and a hydrophilic coating on a second surface of the mesh.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes the membrane having an operable lifespan of over 55,000 aerosol-creating activations by the transducer.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes at least one superhydrophobic vent in fluid communication with the reservoir that is covered with a removable aluminized polymer tab during storage.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh further includes a removable aluminized polymer tab coupled to an exterior surface of the membrane adjacent the mesh during storage.
In another embodiment of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh includes a pre-assembly step of removing a sealed packaging including aluminum and/or aluminum coating that contains the reservoir with a fluid, preferably wherein the reservoir is included in the container assembly that is also packaged for storage in the sealed packaging. In some embodiments, sealed packaging may include dry nitrogen, argon or other gas that does not contain oxygen.
In various embodiments of the push mode invention, a droplet delivery device having a membrane that cooperates with a mesh may be used for mouth inhalation or nasal inhalation. The mouthpiece port may be sized, shaped and include materials that are better suited for that particular mouth or nasal inhalation use and purpose.
The push mode invention will be more clearly understood from the following description given by way of example, in which:
Push mode has been developed as a reduced-risk product to deliver (i) nicotine, cannabinoids, and other non-therapeutic substances (devices described herein as “BlueSky” are preferable for use with such substances), as well as (ii) therapeutic and prescriptive drug products (devices described herein as “Norway” are preferable for use with such products). The push mode device is designed to deliver the user a safe and controlled dose. The push mode droplet delivery device 10 is capable of delivering aqueous and nonaqueous solutions and suspensions at room temperature. Large molecule formulations, whether water soluble or not, can also be delivered with this technology. Harmful chemical by-products commonly found with heated nicotine, and other substances, are eliminated in the push mode device making it a safer option for aerosol delivery.
Push mode utilizes a vibrating member 1708 and transducer 26 that work in conjunction with a membrane 25 and mesh 2 to aerosolize fluid 901, which is held in a reservoir 1200 and supplied to the mesh 22 using various methods (e.g., wick material, hydrophilic coatings, capillary action, etc.). Preferably the vibrating member is coupled to the transducer, such as by bonding (e.g. adhesives and the like), welding, gluing, physical connections (e.g. brackets and other mechanical connectors), and the like. The transducer and vibrating member interact with the membrane to push fluid through the mesh. As illustrated and described in various embodiments, the membrane may in some cases contact the mesh while also “pushing” fluid through holes in the mesh, and may in other cases be separated without contacting the mesh to push liquid through holes in the mesh. The transducer may comprise one or more of a variety of materials (e.g., PZT, etc.). In certain embodiments the transducer is made of lead-free piezoelectric materials to avoid creation of unwanted or toxic materials in a droplet delivery device intended for human inhalation. The vibrating member may be made of one or more of a variety of different materials (e.g., titanium, etc.). The mesh may be one or more of a variety of materials (e.g., palladium nickel, polyimide, etc.). After the fluid is pushed through the mesh, a droplet spray is formed and ejected through a mouthpiece port, carried by entrained air.
The device is tunable and precise. The device can be optimized for individual user preferences or needs. The aerosol mass ejection and mass median aerodynamic diameter (MMAD) can be tuned to desired parameters via the mesh hole size, mesh treatment, membrane design, vibrating member design, airflow, manipulation of power to the transducer, etc. The design produces an aerosol comprised of droplets with a high respirable fraction, such that the lungs can absorb the aerosol most efficiently.
The vibrating member and transducer are both separate from the cartridge, isolated by the membrane. Not only does this create a safer product, but it eases manufacturability. The vibrating member and transducer are both typically expensive components. Keeping these components in the enclosure system rather than the cartridge reduces the cost of goods sold (COGS).
Substance, feature, and part numbers are provided for convenient reference with respect to the descriptions and figures provided herein in Table 1:
Referring to
The push mode I and II embodiments have a transducer consisting of a lead zirconate titanate (PZT) disc bonded to the bottom of a vibrating member made of titanium alloy. The vibrating member and transducer are encased by a plastic cover in an enclosure system 17. A membrane made of polyethylene naphthalate (PEN) in the ejector bracket 15 isolates the transducer and vibrating member from the fluid that is supplied from a reservoir in the container assembly 12. The membrane can be thermoformed to the shape of the vibrating member tip. The embedded system on the device consists of the transducer, pressure sensor, and lithium-ion battery all connected on a single board microcontroller. The aluminum enclosure that houses the embedded system contains a button that can double as a fingerprint sensor for use with controlled substances. The device is charged through a USB-C charging port. Magnets are used to hold the cartridge in the enclosure.
Embodiments use a two-component cartridge system to keep the fluid from contacting the mesh in storage. This design involves two spikes, one of which contains wicking material, on one part of the cartridge, the ejector bracket. The other part of the cartridge, the container, houses a fluid reservoir and two septa. The user pushes the ejector bracket and container together, and the spikes puncture the septa, creating a path for fluid to flow to the mesh. The wicking material in one spike aids in the supply of fluid to the mesh. The other spike, which does not include wicking material, allows air to enter the container for pressure equalization. Vents covered with vent material are located at the top of each side of the fluid reservoir and are connected to the open atmosphere via airflow outlets, allowing for equalization of pressure.
Referring to
Referring to
Referring to
In the push mode II embodiment, a stainless-steel annulus carrier 1518 is bonded to the mesh 22. A gasket 1513 is placed above the mesh and mesh carrier between the upper 1502 and lower 1504 ejector brackets.
Two vents are located on the wide sides of the lower ejector bracket 1504 as shown in
As in push mode I, the container, which houses the fluid reservoir, includes three COC pieces. The lower container for the push mode II embodiment extends further than in push mode I, with the tubular portion extending into the upper ejector bracket.
Push mode has multiple vibrating member and membrane designs. Table 2 and Table 3 contain descriptions of the vibrating member and membrane designs, respectively, that have been prototyped and tested. Referring to
The transducer requires a large amount of power during the actuation of the device. As the power usage increases, the heat generated by the printed circuit board assembly (PCBA) increases. The effect from the heat is mitigated through several design features in the PCBA. A four-layer PCBA increases anti-interference and heat dissipation capabilities. The PCBA also contains a large amount of copper foil, making it conducive to heat dissipation. The MOSFET driving the transducer adopts a high-current package to avoid damage caused by heating in long-term continuous operation. The automatic transformer, to increase the voltage output, it is suspended to insulate it from the rest of PCBA. These features allow the device to operate for days without concern of overheating or being subjected to electrical noise.
The prototype BlueSky push mode embodiments, I and II, have gone through life testing. The life test consisted of repeated three-second dosing with one-second resting intervals over the course of several days. Mass ejection was done before and after the life test. Mass ejection is defined as the mass the device aerosolizes over one three-second dose. Mass ejection data before the life test is listed in Table 3 and the data for after life testing is listed in Table 4. The mass ejection of one embodiment remained consistent before and after 55,000 doses and can likely go beyond. This embodiment, II push mode with H4 and M11, has a stainless-steel mesh carrier. There is a second embodiment, I push mode, which has a COC plastic mesh carrier. Due to heat from the extreme dosing cycling, the plastic mesh carrier warped during testing. This led to a decrease in mass ejection after the life test. However, the stainless-steel carrier in II push mode did not warp from the heat, which allowed it to remain consistent after testing. In both I and II, thermal management is improved through a four-layer PCBA, a larger than standard amount of copper foil, and a high current MOSFET driver. The conditions of the testing are not representative of normal consumer use. During normal daily use, where extreme heating does not occur, both embodiments, I and II, show consistent mass ejection. Tables 2 and 3 provide details of the referenced Vibrating Member and Membrane, respectively.
As set forth in Example 1 described subsequently, prototypes of BlueSky I and II push mode were tested and compared to prior technology, referred to as BlueSky ring mode (such as described and shown with respective test data for that technology in WO 2020/264501), is provided as follows:
Ejectors with a hole size of 2.0 μm were tested in each device. Half of the ejectors tested had a hydrophilic entrance and hydrophobic exit (R). The other half had a hydrophobic entrance and exit (W). The testing was performed with a TSI Mini-MOUDI Model 135 and a THERMO FISHER™ Vanquish UHPLC. Eight different design combinations (vibrating members, membranes, ejector treatments) were tested with BlueSky I and II. Based on the results of the testing, push mode I appears to be the preferred embodiment for push mode. The push mode I design resulted in more consistent mass ejection and MMAD values versus II. Seven of the eight design combinations resulted in comparable mass ejections and MMADs. One outlier, H5 with M12 and R-treated ejector, had a significantly higher mass ejection than the others. Upon comparison of I push mode to BlueSky ring mode, I delivered higher and more consistent mass ejection and lower MMADs. Table 6, Table 7 and Table 8 provide the data obtained from ring mode, I push mode, and II push mode, respectively. The data in the tables include micrograms of nicotine ejected, MMAD, geometric standard deviation (GSD), and the percentage of ejected solution in stage 1 and stage 2 of the mini-MOUDI. All the vibrating member and membrane combinations tested with I push mode, found in Table 7, performed well with both ejector treatments. As seen in Table 8, the best performing combinations with II push mode were H4 with M11 and H5 with M12, both using W-treated ejectors.
The results obtained from Push Mode I device are shown in Table 7. Tables 2 and 3 provide details of the referenced Vibrating Member and Membrane, respectively.
The results obtained from Push Mode II device are shown in Table 8. Tables 2 and 3 provide details of the referenced Vibrating Member and Membrane, respectively.
Based on the results of the testing, I push mode is the preferred embodiment when compared to II.
Another embodiment of push mode incorporates the two-part cartridge system into a singular component. Having the cartridge in one piece simplifies setup for the user and increases manufacturability while reducing cost.
In another embodiment, there is a short vibrating member with the fluid reservoir above the mesh (see
The vibrating member and transducer work in conjunction with a membrane and mesh, as previously described embodiments of BlueSky push mode. The membrane also serves to isolate the vibrating member and transducer from the fluid. A mesh carrier is used in both designs. Magnets on the bottom of the containers hold the cartridge in the enclosure.
Further embodiments, shown in
The low COGS designs shown in
Another embodiment of push mode, Norway, is similar to its BlueSky counterpart in most aspects, except that is tailored for prescriptive and medical use. Much like BlueSky, Norway features a releasable cartridge which contains a fluid reservoir and ejector bracket. The device can also be used to assess lung health using spirometry.
Patients diagnosed with lung diseases can use the Norway device to track their medication dosages and take lung function tests so their treatment progression can be assessed. The patient can perform lung function tests and view dosage history via a phone app which pairs to the Norway device with Bluetooth. The device saves pressure sensor measurements from each dosage of medication. Inspiratory flow measurements can be derived from the pressure sensor measurements to ensure the user is inhaling their medication at a flow rate which delivers the solution most efficiently. The device can also perform lung function tests to measure a patient's forced expiratory volume over 1 second, forced vital capacity, peak expiratory flow, and other spirometry measurements. The data from dosage tracking and lung function tests are uploaded to the cloud so that the patient and doctor may view the patient's progression.
The ejector bracket has been designed to accept many different sizes of containers, where the fluid reservoir volume changes. This makes the device capable of being used with biologics, or one time use ejections. Possible fluid reservoir volumes range from 1 μL to 20 mL.
The mouthpiece for the Norway embodiment has a preferred length of 15 mm. There are two slits on the sides of the mouthpiece with a dimension of 9 mm by 3 mm for an area of 27 mm2. The length of the mouthpiece could be anywhere from 5 mm to 30 mm. The area for the mouthpiece could be from 1 mm2 to 100 mm2. The mouthpiece opening has dimensions of 14 mm×24 mm for an area of 336 mm2. The area of the mouthpiece opening could be anywhere from 10 mm2 to 500 mm2.
The cartridge can be inserted into the main body of the device. The front of the cartridge can be sealed by an O-Ring attached to the cap that presses around the mesh on a stainless-steel annulus when closed to prevent any evaporation through the mesh, this is the face seal. The device features voice coaching and LED lights to guide the user through the ejection inhalation. There is an LCD screen to display dose count, and other necessary information.
Referring to
The cartridge spacer can be removed so the container can be pushed down onto the ejector bracket such that the spikes pierce the septa making the cartridge one piece. Then, the cartridge can be pushed into the main body of the device to complete the device. This process is illustrated in
The cap of the Norway embodiment is designed to create a firm seal around the cartridge after each use. An O-Ring is seated on a spring-loaded plastic piece which lightly compresses onto the cartridge assembly when the cap is closed, generating a seal between the cartridge and open atmosphere. The components of the cap are shown isolated in as illustrated in
The critical components to generate precise aerosol of the ejector bracket include the mesh, gasket, membrane, vent material, and mouthpiece. The membrane is positioned such that the membrane face is held parallel to the mesh face, or at a small precise angle. The ejector bracket also has two spikes protruding out of the top that pierce the container. One is for fluid supply, and the other provides a ventilation path for air generated by ejection. On the side of the ejector bracket with the air ventilation spike there is an opening covered by vent material to help relieve pressure and build-up of air. The mouthpiece is positioned following the face of the mesh.
The critical components of the container to maintain consistent aerosol are vent material, a spiral, septa, and septa caps. The vent material is positioned between the fluid and the spiral. The spiral is created by the upper container and vent spacer which minimizes evaporation of the fluid through the vent material. The vent spacer is bonded onto the top of the upper container to create the sealed spiral with an opening to the push mode Inside of the container assembly and another opening to atmosphere. The septa are at the bottom of the container. The septa are placed into a cavity in the lower container and held in place with septa caps that are bonded onto the lower container. The critical components of both the ejector bracket and container can be seen in
The main body of the Norway contains the vibrating member and transducer assembly. In one embodiment, as shown in
Additional embodiments of Norway push mode include different suspension systems to hold the mesh in the cartridge, similar to those in BlueSky push mode. With the suspension systems seen in
An additional embodiment of the Norway push mode device includes a heating element that increases the push mode Inhaled air temperature to roughly 50° C. to make the dose more comfortable. As with the BlueSky designs that include heating elements, the heated air temperature is kept below thermal degradation levels, so the push mode Integrity of the formulation is maintained, and no harmful by-products are produced. This can be accomplished because, as with BlueSky, the device does not depend on heat to aerosolize.
In the push mode design, the vibrating member and transducer are completely isolated from the push mode Inhaled solution by a membrane. The transducer, which typically contains heavy metals, is located behind a vibrating member, such that it is completely removed from the ejection area and fluid reservoir. The membrane separates the fluid reservoir from the vibrating member, presenting a chemically inert barrier that permits little or no diffusion, and subsequent evaporation. In one embodiment, a palladium nickel alloy mesh is used to atomize the fluid. A polyimide mesh has also been tested and was shown to be a viable option. Using a polymer mesh would significantly reduce manufacturing cost and potentially improve the extractable/leachable profile of the device. The non-metallic components in prototyped embodiments are primarily comprised of cyclic olefin copolymer (COC) and silicone, both widely accepted materials used in the medical device industry.
The heating element is breath actuated such that the element only heats air as the user inhales. This allows the battery to have a much longer life. It also creates a much safer device in that the heating element is not always on. This can be accomplished due to the push mode Incorporation of small gauge wire. This wire heats up very quickly, so the heating element responds as soon as the user inhales.
In the embodiment shown in
Referring to
In the embodiments shown in
Another embodiment features external heating elements seated on the outside of the enclosure (
In another embodiment of a heated air push mode device, closed loop control is used to regulate the power delivered to the heating element. The power is adjusted to keep the airstream temperature constant and at safe levels. Referring to
In another embodiment of the heated air push mode device, open loop control is used to regulate the power delivered to the heating element. The power is adjusted to keep the airstream temperature constant. The pressure drop from inhalation is sensed. The amount of power needed to supply the heating element to keep the air stream temperature constant due to changes in pressure drop is known. A look-up table is created to determine the amount of power needed to supply the heating element to keep the air stream temperature constant based upon the pressure sensor value.
In another embodiment of the heated air push mode device, one or more of the push mode Internal device components that are in contact with heated air is preferably made of metal (i.e., aluminum, Inconel, etc.). This will insulate the heating element and enhance biocompatibility of the device.
In another embodiment of the heated air push mode device, any component that could be compromised by the heated air is preferably made of metal (i.e., titanium, aluminum, Inconel, etc.). These components include, but are not limited to the mouthpiece, the heating chamber, and like components that heated air could negatively affect.
In one embodiment of the heated air push mode device, the metal components that are in contact with the heated air are preferably made of a material with a low thermal conductivity, such as Inconel.
In one embodiment of the heated air push mode device, ceramic is used to insulate the heating element.
Another embodiment of push mode incorporates a mechanism to adjust the size of the airflow inlets. The airflow inlets can be opened and closed using a sleeve or an adjustable aperture. In this way, the resistance experienced by the user can be adjusted to individual preferences.
BlueSky push mode has also been adapted for nasal inhalation.
Another embodiment of push mode incorporates a tube with a hydrophilic interior that supplies fluid from the fluid reservoir to the mesh. A hydrophilic tube eliminates the need for wicking material and allows for a wider variety of suspensions and solutions to be delivered from the device. An example of one of these tubes is the spike on BlueSky I and II.
Another embodiment of push mode incorporates a tube with a hydrophilic interior that supplies fluid from the fluid reservoir to the mesh without a wick material, allowing for a wider variety of suspensions and solutions to be delivered from the device; and an opposite hydrophobic tube that encourages gas migration from the fluid supply area between the membrane and mesh.
In another embodiment, as shown in
Another embodiment of push mode uses a tidal breathing system that can be used for pediatric therapy. The push mode technology supplies aerosol a mask similar to the AERO CHAMBER PLUS™ Z-Stat Pediatric Mask (Monaghan Medical). This allows for long use therapy. When a user inhales, the device will start ejection and when the user exhales the device will stop ejection. Due to the robustness of push mode, this can be a very effective device for extended therapies.
In another embodiment, two parallel plates 1528 surround the fluid next to the mesh and membrane area. These two parallel plates will measure the capacitance of the fluid. The capacitance of the supplied fluid is known. If the capacitance measured is different than the known capacitance, the device will not work. This will prevent tampering of the cartridge, and it will prevent unauthorized fluids to be inserted into the cartridge. One of the parallel plates is shown in
Another embodiment of push mode utilizes vibrating member and membrane geometries at their coupled interface to act as both an atomizer and microfluidic pump in applications where wicking materials are not incorporated into the preferred embodiment for certain suspensions, solutions, and other medical, therapeutic, and consumer applications. The tip of the vibrating member is coupled to a membrane matching the desired geometry allowing fluid to enter between the mesh and membrane while also encouraging any gas to exit freely. These membranes may be treated by technologies mentioned previously to be hydrophilic or hydrophobic.
Another embodiment utilizes a separate microfluidic pump to direct the proper amount of fluid and pressure between the mesh and membrane when powered on, at breath actuation, at set intervals, etc. to ensure proper dosing.
Vibrating members of the embodiments are to be made of materials featuring proper acoustical and mechanical properties. Thin film sputtering of various nonreactive metals such as titanium, palladium, gold, silver, etc. can be performed on the vibrating member tip section to further enhance biocompatibility. According to industry leaders, titanium has the best acoustical properties of the high strength alloys, has a high fatigue strength enabling it to withstand high cycle rates at high amplitudes, and has a higher hardness than aluminum, making it more robust. Correct material must be selected, vibrating members must be balanced, designed for the required amplitude, and be accurately tuned to a specific frequency. One aspect of tuning is making the vibrating member have the correct elongated length. Another aspect of tuning is matching the vibrating member to the mesh and having the correct gain ratio. Incorrectly tuned vibrating members may cause damage to the power supply and won't be resonating at the device's optimized frequency, decreasing mass ejection and longevity. (see also Ultrasonic Vibrating member catalog—Emerson. Catalog—Ultrasonic Vibrating member (2014). Available at: www.emerson.com/documents/automation/catalog-ultrasonic-vibrating member-branson-en-us-160126.pdf. (Accessed: 2 Nov. 2021)—incorporated herein by reference.)
For example, Titanium 7-4 material has far more uniform wave propagation in one direction (axial) than Titanium 6-4.
Embodiments must have vibrating members with proper moduli of elasticity, acoustical properties, sound speeds, mechanical properties, molecular structure, etc. such as Ti Grade 23, Ti Grade 5, Ti Pure >99.9%, TIMETAL® 7-4, 302 Stainless Steel, 303 Stainless Steel, 304 Stainless Steel, 304L Stainless Steel, 316 Stainless Steel, 347 Stainless Steel, Al 6061, Al 6063, Al 3003, etc.
Other embodiments have crystalline vibrating members with proper moduli of elasticity, acoustic properties, sound speeds, mechanical properties, molecular structure, etc. such as: Sapphire (Al2O3Aluminum oxide), monocrystalline silicon, etc.
In one embodiment, vibrating member design is based on industrial ultrasonic vibrating member design such as disclosed by the push mode Indicated reference subsequently noted, but optimized to be used for the purposes of aerosol generation in the delivery of fluids to the lungs, nose, ear, eye, etc.
Referring to
Referring to
In other embodiments, shown in
Referring to
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With further reference to
In other embodiments, the vibrating member 1708 may include other shapes and the membrane 25 may also include alternative shapes. For example,
In another embodiment,
In further embodiment shown in
The membranes 25 of the embodiments are made of materials featuring robust and proper acoustical and mechanical properties such as polyethylene naphthalate, polyethylenimine, poly ether ketone, polyamide, poly-methyl methacrylate, polyetherimide, polyvinylidene fluoride, ultra-high molecular weight polyethylene, and the like.
The membranes of the embodiments may have a hydrophobic coating, hydrophobic etching, hydrophilic etching, hydrophilic coating, roughening etch, etc.
In some embodiments, such as shown in
Meshes 22 of the embodiments are to be made of materials featuring robust and proper acoustical and mechanical properties such as poly-methyl methacrylate, poly ether ketone, polyetherimide, polyvinylidene fluoride, ultra-high molecular weight polyethylene, polytetrafluoroethylene (PTFE), Ni, NiCo, Pd, Pt, NiPd, and metal alloys.
In one embodiment, the mesh is made from single crystalline or poly crystalline materials such as silicon, silicon carbide, aluminum nitride, boron nitride, silicon nitride, or aluminum oxide. Different hole shapes can be formed in a single crystalline wafer via high precision photolithography with and without using greyscale masks, and isotropic and/or anisotropic etches. Sputtered films can be deposited on the mesh to modify the wettability of the surface. Thin layers formed or deposited on the surface will have, in certain embodiments, much better adherence than films deposited on metal mesh formed by galvanic deposition or polymer mesh formed by laser ablation. The surfaces on the single crystalline wafers “slices” are atomically smooth and can be etched to produce exact surface roughnesses. Exact surface roughnesses can be used for better adherence of mechanical bonding with glue or other materials. Silicon carbide would be a preferable material because of its high strength and toughness. An important advantage of using semiconductor processes to fabricate hole structures from a single crystalline wafer “slice” in a mesh of embodiment of the push mode invention is that the holes and surface contact angles will be exact without the variation seen in conventional ejector plates using mesh made from galvanic deposition or laser ablation. This mesh, as noted in Table 9 may be fixed as in II, or suspended as in I, and the membrane is coupled with an optimized vibrating member with a thin film sputtering of nonreactive metals such as palladium or gold member tip section to further enhance biocompatibility.
The hole structures of other embodiments are formed using semiconductor processes such as photo lithography and isotropic and anisotropic etching, laser ablation, femtosecond laser ablation, electron beam drilling, EDM (Electrical discharge machining) drilling, diamond slurry grinding, etc. See also
The meshes of the embodiments may have a hydrophobic coating, hydrophobic etching, hydrophilic etching, hydrophilic coating, roughening etch, etc. or a combination thereof.
In other embodiments,
In embodiments of the push mode invention, a laminar flow element 1600, such as shown in
Referring to
In another embodiment of the push mode invention, a droplet delivery device 10 having a membrane 25 that cooperates with a mesh 22 includes a pre-assembly step of removing a sealed packaging including aluminum and/or aluminum coating that contains the reservoir with a fluid, preferably wherein the reservoir is included in the container assembly that is also packaged for storage in the sealed packaging.
In embodiments of the push mode invention, it is desirable to decrease large droplet formation and encourage smaller droplet sizes to be delivered out of the droplet delivery device and in the aerosol stream.
In one embodiment, a hydrophilic wicking material may be provided to line the mouthpiece of the droplet delivery device. Droplets formed on the outer perimeter of a mesh exit are absorbed by the hydrophilic wicking material and decrease the likelihood of large droplets propelling off the surface of the mesh exit. This wicking material absorption of large droplets increases MMAD repeatability and prevents pooling.
In another embodiment, a one-dimensional hydrophilic lattice (see laminar flow element 1600 but taking such as a cross section), or a series of one dimensional hydrophilic lattices, may be used to absorb large droplets that might “pop” off the mesh due to pooling.
It has been noticed in tests of push mode droplet production that a fog of aerosol may remain within the mouthpiece tube after inhalation. This fog could lead to pulling on the mesh and along the outer perimeter. This pulling happens due to no entrained air pulling the tail end of the aerosol ejection out. Via electronic programming and monitoring through a microcontroller or microchip integrated or coupled in the droplet delivery device, the droplet device can be programmably controlled to start spraying when the air flow rate reaches a threshold and then the droplet delivery device detection controller records your maximum air intake every 2 ms. The droplet delivery device is programmed to stop spraying when the flow rate recedes to a percentage of the maximum flow rate achieved during inhalation. In embodiments, a parameter labeled “pressure cutoff” can be added to a graphical user interface (GUI) for control/programming of the droplet delivery device so that a manufacturer or other device operator and alter the stop condition parameter for the spray.
Referring to
As described, it is important to get all the small droplets out of the mouthpiece. The small droplets have a very small stopping distance; therefore, the airflow must be close enough to the ejector plate to carry the small droplets. One design was tested wherein airflow directors were used to point the airflow towards the end of the mouthpiece and away from the mesh. As shown in
While the push mode invention has been described with reference to exemplary embodiments, it will be understood by those skilled in the art that various changes may be made and equivalents may be substituted for elements thereof without departing from the scope of the push mode invention. In addition, many modifications may be made to adapt a particular situation or material to the teachings without departing from the essential scope thereof. Therefore, it is intended that the push mode invention not be limited to the particular embodiment disclosed as the best mode contemplated for carrying out this invention, but that the push mode invention will include all embodiments falling within the scope of the appended claims.
The present application is a continuation of U.S. patent application Ser. No. 17/846,902 filed Jun. 22, 2022, which claims the benefit of priority of U.S. Provisional Patent Application No. 63/280,643 filed Nov. 18, 2021, U.S. Provisional Patent Application No. 63/256,546 filed Oct. 16, 2021, Provisional Patent Application No. 63/256,245 filed Oct. 15, 2021, and Provisional Patent Application No. 63/213,634 filed Jun. 22, 2021, all of which are incorporated herein by reference in their entirety.
| Number | Date | Country | |
|---|---|---|---|
| 63280643 | Nov 2021 | US | |
| 63256546 | Oct 2021 | US | |
| 63213634 | Jun 2021 | US | |
| 63256245 | Oct 2021 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 17846902 | Jun 2022 | US |
| Child | 18382637 | US |
