WO2013027249A1 - エアロゾル吸引器 - Google Patents
エアロゾル吸引器 Download PDFInfo
- Publication number
- WO2013027249A1 WO2013027249A1 PCT/JP2011/068783 JP2011068783W WO2013027249A1 WO 2013027249 A1 WO2013027249 A1 WO 2013027249A1 JP 2011068783 W JP2011068783 W JP 2011068783W WO 2013027249 A1 WO2013027249 A1 WO 2013027249A1
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- Prior art keywords
- solution
- heater
- aerosol inhaler
- discharge end
- aerosol
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- A—HUMAN NECESSITIES
- A24—TOBACCO; CIGARS; CIGARETTES; SIMULATED SMOKING DEVICES; SMOKERS' REQUISITES
- A24F—SMOKERS' REQUISITES; MATCH BOXES; SIMULATED SMOKING DEVICES
- A24F40/00—Electrically operated smoking devices; Component parts thereof; Manufacture thereof; Maintenance or testing thereof; Charging means specially adapted therefor
- A24F40/40—Constructional details, e.g. connection of cartridges and battery parts
- A24F40/46—Shape or structure of electric heating means
-
- A—HUMAN NECESSITIES
- A24—TOBACCO; CIGARS; CIGARETTES; SIMULATED SMOKING DEVICES; SMOKERS' REQUISITES
- A24F—SMOKERS' REQUISITES; MATCH BOXES; SIMULATED SMOKING DEVICES
- A24F40/00—Electrically operated smoking devices; Component parts thereof; Manufacture thereof; Maintenance or testing thereof; Charging means specially adapted therefor
- A24F40/40—Constructional details, e.g. connection of cartridges and battery parts
- A24F40/48—Fluid transfer means, e.g. pumps
- A24F40/485—Valves; Apertures
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M11/00—Sprayers or atomisers specially adapted for therapeutic purposes
- A61M11/04—Sprayers or atomisers specially adapted for therapeutic purposes operated by the vapour pressure of the liquid to be sprayed or atomised
- A61M11/041—Sprayers or atomisers specially adapted for therapeutic purposes operated by the vapour pressure of the liquid to be sprayed or atomised using heaters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M11/00—Sprayers or atomisers specially adapted for therapeutic purposes
- A61M11/04—Sprayers or atomisers specially adapted for therapeutic purposes operated by the vapour pressure of the liquid to be sprayed or atomised
- A61M11/041—Sprayers or atomisers specially adapted for therapeutic purposes operated by the vapour pressure of the liquid to be sprayed or atomised using heaters
- A61M11/042—Sprayers or atomisers specially adapted for therapeutic purposes operated by the vapour pressure of the liquid to be sprayed or atomised using heaters electrical
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M15/00—Inhalators
- A61M15/06—Inhaling appliances shaped like cigars, cigarettes or pipes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/10—Preparation of respiratory gases or vapours
- A61M16/1075—Preparation of respiratory gases or vapours by influencing the temperature
-
- A—HUMAN NECESSITIES
- A24—TOBACCO; CIGARS; CIGARETTES; SIMULATED SMOKING DEVICES; SMOKERS' REQUISITES
- A24F—SMOKERS' REQUISITES; MATCH BOXES; SIMULATED SMOKING DEVICES
- A24F40/00—Electrically operated smoking devices; Component parts thereof; Manufacture thereof; Maintenance or testing thereof; Charging means specially adapted therefor
- A24F40/10—Devices using liquid inhalable precursors
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M15/00—Inhalators
- A61M15/0001—Details of inhalators; Constructional features thereof
- A61M15/0013—Details of inhalators; Constructional features thereof with inhalation check valves
- A61M15/0015—Details of inhalators; Constructional features thereof with inhalation check valves located upstream of the dispenser, i.e. not traversed by the product
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M15/00—Inhalators
- A61M15/0001—Details of inhalators; Constructional features thereof
- A61M15/0013—Details of inhalators; Constructional features thereof with inhalation check valves
- A61M15/0016—Details of inhalators; Constructional features thereof with inhalation check valves located downstream of the dispenser, i.e. traversed by the product
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3368—Temperature
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/36—General characteristics of the apparatus related to heating or cooling
- A61M2205/3653—General characteristics of the apparatus related to heating or cooling by Joule effect, i.e. electric resistance
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/82—Internal energy supply devices
- A61M2205/8206—Internal energy supply devices battery-operated
Definitions
- the present invention relates to an aerosol inhaler that generates an aerosol in accordance with a user's suction operation and provides the aerosol to the user.
- An aerosol inhaler disclosed in Patent Document 1 includes a suction pipe provided with a mouthpiece, a solution supply source built in the suction pipe and storing a solution to be aerosolized, and a distribution in the suction pipe from the solution supply source It includes a dispensing device capable of dispensing the solution at a certain amount to the position, and an electric heater that generates aerosol in the suction pipe by atomizing the solution dispensed to the dispensing position by heating.
- the aerosol inhaler disclosed in Patent Document 2 includes an electric heater and a high-frequency generator in order to aerosolize the liquid supplied by the pump.
- the aerosol inhaler disclosed in Patent Document 3 includes an inkjet unit for aerosolizing a liquid.
- the aerosol inhaler disclosed in Patent Document 4 includes a liquid supply path using capillary action and an electric heater disposed at the outlet of the liquid supply path.
- the aerosol inhaler of Patent Document 1 requires a manual operation of the distribution device before the user performs an aspiration operation through the mouthpiece, or requests an automatic operation of the distribution device simultaneously with the aspiration operation.
- the presence of the dispensing device is not only a major factor that leads to an increase in the size of the aerosol inhaler, but also the manual operation of the dispensing device hinders easy aspiration of the aerosol by the user.
- the automatic operation of the dispensing device provides the user with simple aspiration of the aerosol.
- the dispensing device not only complicates its structure, but also consumes electrical energy for automatic operation.
- a large-capacity power source is indispensable for the distribution device and the electric heater, and the size of the aerosol inhaler is further increased.
- the aerosol inhalers of Patent Documents 2 and 3 are difficult to miniaturize due to their complicated structure, similar to the aerosol inhaler of Patent Document 1.
- the aerosol inhaler of Patent Document 4 has a simpler structure than the aerosol inhalers of Patent Documents 1 to 3, but like the aerosol inhaler of Patent Documents 1 to 3, the liquid is directly applied to the electric heater. Since it does not collide to achieve aerosolization of the liquid, reliable aerosolization is not guaranteed.
- An object of the present invention is to provide a small-sized aerosol inhaler that allows a user to easily inhale an aerosol and reliably ensure that the liquid is aerosolized.
- an aerosol inhaler which comprises: A suction path that connects the air opening and the mouthpiece, and allows a flow of air from the air opening to the mouthpiece; A solution supply device for supplying a solution for generating an aerosol, the solution supply source storing the solution; While connected to this solution supply source, it has a discharge end that opens toward the mouthpiece in the suction path, guides the solution from the solution supply source to the discharge end, and enters the suction path A solution supply device including a capillary tube for discharging the solution from the discharge end when the air flow is generated; A heater device that receives the discharged solution from the discharge end and atomizes the received discharged solution by heating, Power supply, When the voltage of the power source is applied just downstream of the discharge end and arranged to face the discharge end with a predetermined distance between the discharge end while allowing the air flow And a heater device including an electric heater that generates heat.
- the solution is discharged from the discharge end of the capillary tube when the user performs a suction operation through the mouthpiece.
- This discharged solution is received on the outer surface of the heater and at the same time receives all the heat from the heater to be atomized, and aerosol is generated in the suction path. Therefore, the user can inhale the aerosol through the mouthpiece.
- the heater extends in a direction perpendicular to the suction path axis and across the suction path.
- the capillary tube extends on the axis of the suction path.
- the aerosol inhaler of the present invention discharges the solution from the discharge end of the capillary tube in conjunction with the user's suction operation, and at the same time, can receive the discharged solution on the outer surface of the heater. Atomized on the outer surface of the gas to generate aerosol in the suction path. Therefore, the user can inhale the aerosol easily and effectively. Details and other advantages of the aerosol inhaler of the present invention will become apparent from the accompanying drawings and the following description.
- FIG. 1 is a longitudinal sectional view schematically showing an aerosol inhaler according to an embodiment of the present invention. It is the figure which showed the specific example of the liquid tank of FIG. It is the cross-sectional view which expanded and showed the heater of FIG. It is the figure which showed the heater of FIG. 1 with the electric power feeding circuit. It is the schematic which showed a part of aerosol inhaler before aerosol generation. It is the schematic which showed a part of aerosol suction device of the state which aerosol generate
- an aerosol inhaler 10 of one embodiment includes a cylindrical outer tube 12 having both ends opened, and a mouthpiece 14 detachably connected to the base end of the outer tube 12.
- the outer tube 12 and the mouthpiece 14 are each formed from a heat-resistant synthetic resin.
- the outer tube 12 includes a lid 16 at the tip, and the lid 16 can be detached from the outer tube 12.
- a power unit 18 as a power source, a liquid tank 20 as a solution supply source, and an inner tube 22 are accommodated.
- the power supply unit 18, the liquid tank 20, and the inner tube 22 are sequentially arranged on the axis of the outer tube 12 from the lid 16 side.
- the inner tube 22 communicates with the mouthpiece 14.
- the power supply unit 18 and the liquid tank 20 can be replaced, and the replacement of the power supply unit 18 and the liquid tank 20 is performed by removing the lid 16 from the outer tube 12.
- the power supply unit 18 includes a battery holder 24 and one commercially available battery held by the battery holder 24, for example, an AA battery 26. This battery 26 has a nominal voltage of 1.5 V and is arranged on the axis of the outer tube 12.
- the liquid tank 20 is shown more specifically in FIG.
- the liquid tank 20 includes a cylindrical tank casing 28.
- a plurality of ribs are formed on the outer peripheral surface of the tank casing 28. These ribs are arranged at intervals in the circumferential direction of the tank casing 28, and extend in the axial direction of the tank casing 28 except for the end of the tank casing 28 on the battery unit 18 side.
- the ribs described above form a plurality of axial passages 27 (see FIG. 1) between the outer surface of the tank casing 28 and the inner surface of the outer tube 12, while the end of the tank casing 28 and the inner surface of the outer tube 12 are connected to each other.
- An annular chamber 29 (see FIG. 1) is secured in between. The annular chamber 29 is connected to the axial passage 27.
- a tube coil 30 is accommodated in the tank casing 28.
- the tube coil 30 extends in the axial direction of the outer tube 12 and has both ends opened.
- An introduction conduit 32 extends from one end of the tube coil 30 to the outer surface of the tank casing 28, and the introduction conduit 32 opens at the outer surface of the outer casing 28 and is connected to the annular chamber 29 described above.
- a check valve 34 is disposed in the introduction pipe line 32, and the check valve 34 opens only toward one end of the tube coil 30.
- a delivery line 36 extends from the other end of the tube coil 30, and this delivery line 36 is connected to a capillary tube 40 via a joint 38.
- the capillary tube 40 projects from the tank casing 28 into the inner tube 22 described above, and is positioned on the axis of the inner tube 22.
- the protruding end of the capillary tube 40 forms a discharge end 42, and the discharge end 42 opens toward the mouthpiece 14.
- a check valve 44 is also arranged in the delivery line 36, and the check valve 44 opens only toward the capillary tube 40.
- the interior flow path (introduction conduit 32, tube coil 30 and delivery conduit 36) of the liquid tank 22 and the capillary tube 40 are filled with the solution to be aerosolized, and the solution reaches the discharge end 42 of the capillary tube 40.
- the solution can contain, for example, propylene glycol, glycerin and the like.
- the inner tube 22 extends from the liquid tank 20 toward the mouthpiece 14 and is connected to the absorption sleeve 48.
- the absorption sleeve 48 is positioned coaxially with the inner tube 22 and has the same inner diameter as the content of the inner tube 22.
- the thickness of the outer tube 12 surrounding the inner tube 22 and the absorption sleeve 48 is thicker than the thickness of the outer tube 12 surrounding the power supply unit 18 and the liquid tank 20.
- the inner tube 22 is made of, for example, stainless steel or ceramic.
- the absorption sleeve 48 is formed by, for example, a paper tube or a hollow cylindrical paper filter capable of absorbing the solution described above. Such an absorption sleeve 48 has a volume sufficient to cover the required amount of solution absorption.
- a plurality of atmospheric ports 50 are formed in the outer tube 12. These atmospheric ports 50 are, for example, adjacent to the liquid tank 20 and are arranged at intervals in the circumferential direction of the outer tube 12.
- the atmospheric port 50 extends from the outer peripheral surface of the outer tube 12 through the inner tube 22.
- the atmospheric port 50 provides an atmospheric opening 52 opened on the outer peripheral surface of the outer tube 12, and is connected to the annular chamber 29 via the axial passage 27 described above.
- the atmosphere port 50 and the inner tube 22 form a suction path that connects the atmosphere opening 52 and the mouthpiece 14. Further, the atmospheric port 50 maintains the inside of the annular chamber 29 at atmospheric pressure, and as a result, the solution in the liquid tank 20 is always in the state of receiving atmospheric pressure through the opening end of the introduction pipe line 32.
- the negative pressure in the inner tube 22 is caused to discharge a solution from the discharge end 42 of the capillary tube 40 into the suction path, that is, the inner tube 22, and the discharge amount of the solution here is determined by the strength of the negative pressure.
- the solution is supplied from the liquid tank 20 to the capillary tube 40 by the amount of the discharged solution.
- the solution in the liquid tank 20 constantly receives atmospheric pressure, the solution in the internal flow path of the liquid tank 20 moves toward the capillary tube 40 as the solution is replenished.
- a cylindrical heater 56 is disposed in the inner tube 22, and this heater 56 is positioned immediately downstream of the discharge end 42 of the capillary tube 40 in view of the flow of air generated in the suction path.
- the outer diameter D O of the heater 56 is smaller than the inner diameter D IT of the inner tube 22 and The inner diameter DCT or the diameter of the capillary tube 40 is larger.
- the outer diameter D O satisfies the following relationship.
- the heater 56 penetrates the inner tube 22 in the diameter direction, and has an axis perpendicular to the axis of the inner tube 22. Both ends of the heater 56 are supported by the outer tube 12.
- the discharge end 42 of the capillary tube 40 is the heater.
- the cross section of the discharge end 42 can be completely projected onto the outer surface of the heater 56.
- the maximum diameter of the droplets is determined by the inner diameter D CT of the capillary tube 40
- D MAX the maximum droplet diameter
- D CT the distance Z between the discharge end 42 and the heater 56 has the following relationship.
- Table 1 shows that when the solution is propylene glycol (PG: density 1.036 g / mm 2 ), the inner diameter D CT of the capillary tube 42 and the suction amount of the air generated in the inner tube 22 The relationship between discharge amount, discharge volume, and diameter is shown.
- PG propylene glycol
- the liquid tank 20 of FIG. 3 has a structure that is different from the structure of the liquid tank already described. Specifically, the liquid tank 20 of FIG. 3 has an internal flow path 30 a that extends in a zigzag shape instead of the coil tube 30. This means that the coil tube 30 is not essential for the liquid tank 20.
- the heater 56 includes, for example, a nichrome wire 58 as a resistance heating element, and a cylindrical sheath element 60 covering the nichrome wire 58.
- the nichrome wire 58 penetrates the sheath element 60 three times in the axial direction of the sheath element 60 and has two ends protruding from both ends of the sheath element 60.
- the nichrome wire 58 is connected in series to the battery 26 described above via a power supply circuit 63, and the power supply circuit 63 has a switch 64.
- the power feeding circuit 63 and the switch 64 are not shown in FIG. 1, the power feeding circuit 63 and the switch 64 are disposed on the inner surface of the outer tube 12, and the outer tube 12 is a push button (not illustrated) that operates the switch 64 on the outer surface. Not).
- the sheath element 60 is made of ceramic such as alumina or silicon nitride, and provides the outer surface of the heater 56. Further, as apparent from FIG. 4, for example, an annular groove 62 is formed on a part of the outer surface of the sheath element 60, and a ring-shaped heat-resistant net 64 as a wetness increasing element is held in the annular groove 62. Is preferred.
- the net 64 faces the discharge end 42 of the capillary tube 40, and the interval Z described above is defined between the discharge end 42 and the net 64.
- the sheath element 60 described above not only protects the nichrome wire 58 but also thermally connects the nichrome wire 58 and the net 64. Specifically, when the battery 26 is in a usable state and a voltage of 1 to 1.5 V is applied to the nichrome wire 58, the sheath element 60 quickly transfers the heat generated by the nichrome wire 58 to the outer surface of the heater 56. And has a function of maintaining the heating temperature of the outer surface of the heater 56 within a temperature range required for atomization of the solution. That is, the nichrome 58 and the sheath element 60 provide an internal structure that maintains the heating temperature of the outer surface of the heater 56 within the temperature range, and thus the sheath element 60 has a predetermined thickness and volume.
- FIG. 5 shows a state where the above-described switch 64 of the power feeding circuit 63 is turned on and the aerosol inhaler can be used.
- the heating temperature of the outer surface of the heater 56 is quickly maintained within the required temperature range, and the relationship in the above equation (2) is satisfied, so that the solution in the capillary tube 40 is It does not atomize in response to the radiant heat from the heater 56. That is, no aerosol is generated.
- the aerosol inhaler when the aerosol inhaler is sucked through the mouthpiece 14 by the user from the state shown in FIG. 5, the solution is discharged from the discharge end 42 of the capillary tube 40 as described above.
- the discharge solution L is supplied to the heater 56 as shown in FIGS.
- the outer surface is securely received.
- the above-described net 64 is provided on the outer surface of the heater 56, the discharged solution is received by the net 64 and extends and spreads on the net 64.
- the discharge solution L is immediately atomized by being heated by the heater 56, and thereby the aerosol is injected into the inner tube 22. X is generated. Therefore, the user can suck the aerosol X through the mouthpiece 14.
- the heater 56 has the net 64
- the net 64 increases the wettability of the heater 56 with respect to the discharge solution L. Therefore, the discharge solution L is atomized in a wide area, and rapid aerosol is generated. To achieve. Further, when the user stops the suction operation, the solution discharge from the discharge end 42 of the capillary tube 40 is immediately stopped. Since wider than the interval Z is at least capillary tube 40 the inner diameter D CT between the outer surface of the discharge end 42 as is apparent from the foregoing description heater 56, keeping the heating temperature of the outer surface of the heater 56 is in the temperature range described above As long as this is done, the solution in the discharge end 42 is not atomized by receiving radiant heat from the heater 56.
- the generation of aerosol is stopped simultaneously with the stop of the user's suction operation, and the solution in the capillary tube 40 is not wasted.
- the user can reliably suck the aerosol every time the suction operation is performed, and the amount of the aerosol sucked by the user is determined by the strength of the user's suction operation and the period of the suction operation.
- the relationship of the above equation (2) is not satisfied, and the interval Z is larger than the maximum diameter D MAX of the solution droplets. If there is, the discharge solution L is not received by the outer surface of the heater 56 and falls to the inner surface of the inner tube 22 as shown in FIG. In this case, the discharge solution L is not atomized and the user cannot aspirate the aerosol.
- the relationship of the expressions (1) and (2) is satisfied, and the heating temperature of the outer surface of the heater 56 is not maintained in an appropriate temperature range.
- the atomization of the discharge solution L that is, the generation of aerosol cannot be performed or the waste of the solution cannot be avoided.
- the heating temperature of the outer surface of the heater 56 is required to be within a temperature range of 180 to 280 ° C. Is done.
- the aerosol inhaler does not include a control circuit that controls the heat generation of the nichrome wire 58. Therefore, in order to maintain the heating temperature of the outer surface of the heater 56 in the above-described temperature range, the thickness (volume) of the sheath element 60 must be set appropriately.
- the moving speed of heat reaching the outer surface of the heater 56 from the nichrome wire 58 through the sheath element 60 is delayed, while the area of the outer surface of the sheath element 60 is increased. Increases the amount of heat radiation from the sheath element 60. That is, it is considered that the heating temperature of the outer surface of the heater 56 decreases as the thickness of the sheath element 60 increases.
- the present inventors prepared heaters 56 A to 56 G that differ only in the thickness of the sheath element 60.
- the thickness of the sheath element 60 in the heater 56 A ⁇ 56 G is increased by a predetermined increment in the order of the heaters 56 A ⁇ 56 G.
- FIG. 10 shows a heating test apparatus for the heater 56 X (X represents any of A to G).
- the heating test apparatus includes a power supply circuit 66 that applies a voltage to the heater 56 X.
- the power supply circuit 66 includes a DC power supply 68 that can change the applied voltage, a shunt resistor 70 (1 m ⁇ ), and a voltmeter 72. X is connected in series with the shut resistor 70.
- the heating test apparatus includes a temperature sensor 74 that can measure the temperature of the outer surface of the heater 56 X , ie, its sheath element 60.
- the temperature sensor 74 includes a K thermocouple.
- nichrome wire 58 When the heater 56 X is connected to the power supply circuit 66 as shown in FIG. 10, a voltage is applied from the DC power supply 68 to the nichrome wire 58 of the heater 56 X, nichrome wire 58 generates heat. The heat generated by the nichrome wire 58 moves in the sheath element 60 and raises the temperature of the sheath element 60 while being released from the outer surface of the sheath element 60 to the surroundings.
- the heating temperature of the outer surface of the sheath element 60 is determined by the difference between the amount of heat generated by the nichrome wire 58 and the amount of heat released from the sheath element 60, and the rate of temperature rise of the outer surface of the sheath element 60 is determined by the sheath element 60. It is determined by the moving speed of the heat transferred in 60.
- the DC power source 68 applies a voltage to the nichrome wire 56 while sequentially changing the applied voltage to the nichrome wire 58 within the range of 0.8V to 1.6V.
- the temperature sensor 74 measures the heating temperature of the outer surface of the sheath element 60 for each applied voltage of the nichrome wire 58. The measurement results are shown in FIG.
- the heater 56 X heats the outer surface of the sheath element 60 to a higher temperature as the applied voltage to the nichrome wire 58 becomes higher.
- the heating temperature of the outer surface of only the heater 56 F sheath element 60 can be maintained in the above-mentioned temperature range (180 to 280 ° C.).
- the heater 56 F is used as the heater 56 of this embodiment, the aerosol inhalator 10 without requiring a control circuit for controlling the voltage applied to the nichrome wire 58, the heating temperature of the outer surface of the heater 56 Can be maintained in the temperature range described above.
- the control circuit is not required for the aerosol inhaler 10
- the load on the battery 26 is reduced, and the aerosol inhaler 10 can be used for a long period of time.
- the use of the battery 26 realizes miniaturization or slimming of the aerosol inhaler 10 and improves the convenience of the aerosol inhaler.
- the generated aerosol may be aggregated on the inner surface of the inner tube 22 and the solution may adhere to the inner surface of the inner tube 22. It is done. Such attached solution may move toward the mouthpiece 14 and flow into the user's oral cavity in accordance with the user's suction operation.
- the absorption sleeve 48 formed of a paper tube or a paper filter is disposed between the inner tube 22 and the mouthpiece 14, even if the adhesion solution moves toward the mouthpiece 14, the adhesion solution is absorbed. It is reliably absorbed by the sleeve 48 and does not flow into the user's mouth.
- the present invention is not limited to the aerosol inhaler 10 of the embodiment described above, and various modifications are possible.
- the resistance heating element is not limited to the nichrome wire, and the cross section of the heater 56 is not limited to a circle but may be an ellipse or a polygon.
- the sheath element 60 may be made of metal, and may have a rough outer surface 66 as shown in FIG. 12, for example, at least at the site for receiving the above-described discharge solution, instead of the above-described net 64.
- the rough outer surface 62 is formed by a large number of narrow annular grooves that are spaced apart in the axial direction of the sheath element 60, and such annular grooves are formed when the discharge solution is received on the outer surface 66 of the sheath element 60. Like 64, it functions to extend and spread the discharged solution.
- both the sheath element 60 and the inner tube 22 of the heater 56 are made of the same ceramic, it is desirable that the sheath element 60 and the inner tube 22 are formed as a single-piece product. The number of parts can be reduced.
Abstract
Description
特許文献1に開示されたエアロゾル吸引器は、マウスピースを備えた吸引パイプと、この吸引パイプに内蔵され、エアロゾル化すべき溶液を蓄えた溶液供給源と、この溶液供給源から吸引パイプ内の分配位置に溶液を定量ずつ分配可能な分配装置と、分配位置に分配された溶液を加熱によって霧化させることで、吸引パイプ内にエアロゾルを発生させる電気ヒータとを含む。
特許文献3に開示されたエアロゾル吸引器は、液体をエアロゾル化するためインクジェットユニットを含む。
特許文献4に開示されたエアロゾル吸引器は、毛細管現象を利用した液供給経路と、この液供給経路の出口に配置された電気ヒータとを含む。
大気開放口とマウスピースとを接続し、前記大気開放口から前記マウスピースへ向かう空気の流れを許容する吸引経路と、
エアロゾルを発生させる溶液を供給する溶液供給装置であって、前記溶液を蓄えた溶液供給源と、
この溶液供給源に接続されている一方、前記吸引経路内にて前記マウスピースに向けて開口した吐出端を有し、前記溶液供給源から前記吐出端まで前記溶液を導き且つ前記吸引経路内に前記空気の流れが生起されたときに前記吐出端から前記溶液を吐出させるキャピラリ管と
を含む溶液供給装置と、
前記吐出端からの吐出溶液を受け止め、この受け止めた吐出溶液を加熱によって霧化させるヒータ装置であって、
電源と、
吐出端の直下流にて、前記空気の流れを許容しつつ前記吐出端との間に所定の距離を存して前記吐出端と対向して配置され、前記電源の電圧が印加されているときに発熱する電気的なヒータとを含むヒータ装置と
を具備する。
本発明のエアロゾル吸引器の詳細及び他の利点は添付図面及び後述の説明から明らかとなる。
電源ユニット18は電池ホルダ24と、この電池ホルダ24に保持された1本の市販の電池、例えば単三電池26とを含む。この電池26は1.5Vの公称電圧を有し、アウタチューブ12の軸線上に配置されている。
液タンク20は円筒形状のタンクケーシング28を含む。このタンクケーシング28の外周面には複数のリブが形成されている。これらリブはタンクケーシング28の周方向に間隔を存して配置され、そして、電池ユニット18側のタンクケーシング28の端部を除きタンクケーシング28の軸方向に延びている。
図3に示されるように、インナチューブ22の内径及びキャピラリ管40の内径がそれぞれDIT,DCTで示されるとき、ヒータ56の外径DOはインナチューブ22の内径DITよりも小さく且つキャピラリ管40の内径DCT又は直径よりも大である。
DIT>DO>DCT ……(1)
ヒータ56はインナチューブ22をその直径方向に貫通し、インナチューブ22の軸線と直交する軸線を有する。ヒータ56の両端はアウタチューブ12に支持されている。
DMAX>Z>DCT ……(2)
以下の表1は、溶液がプロピレングリコール(PG:密度1.036g/mm2)である場合、キャピラリ管42の内径DCT及びインナチューブ22内に発生される空気の吸引量に対し、液滴における吐出量、吐出体積及び径の関係を示す。
ヒータ56は例えば抵抗発熱要素としてのニクロム線58と、このニクロム線58を覆う円筒形状のシース要素60とを含む。本実施例の場合、図3から明らかなようにニクロム線58はシース要素60をこのシース要素60の軸線方向に3回貫通し、シース要素60の両端からそれぞれ突出した2つの端を有する。
図5は前述した給電回路63のスイッチ64がオン操作され、エアロゾル吸引器が使用可能な状態を示す。この状態にあるとき、ヒータ56の外面の加熱温度は要求される温度範囲内に速やかに維持され、且つ、前記(2)式の関係が満たされていることで、キャピラリ管40内の溶液がヒータ56からの輻射熱を受けて霧化することはない。即ち、エアロゾルは発生されない。
更に、ユーザが吸引動作を停止すれば、キャピラリ管40の吐出端42からの溶液の吐出は直ちに停止される。前述の説明から明らかなように吐出端42とヒータ56の外面との間の間隔Zは少なくともキャピラリ管40の内径DCTよりも広いので、ヒータ56の外面の加熱温度が前述の温度範囲に維持されている限り、吐出端42内の溶液がヒータ56からの輻射熱を受けて霧化することもない。
この結果、ユーザは吸引動作を行う毎にエアロゾルを確実に吸引することができ、ユーザが吸引するエアロゾルの吸引量は、ユーザの吸引動作の強さ及び吸引動作の期間によって決定される。
この加熱試験装置はヒータ56Xに電圧を印加する給電回路66を含み、この給電回路66は、印加電圧を可変可能な直流電源68、シャント抵抗70(1mΩ)及び電圧計72を含み、ヒータ56Xはシャット抵抗70と直列に接続されている。
しかしながら、単三電池26の通常の使用状態にて、単三電池26の印加電圧が1.0V~1.5Vであることを考慮すれば、ヒータ56Fのみがシース要素60の外面の加熱温度を前述した温度範囲(180~280℃)に維持することができる。
このような付着溶液はユーザの吸引動作に伴い、マウスピース14に向けて移動し、ユーザの口腔内に流入する恐れがある。
例えば、ヒータ56に関し、抵抗発熱要素はニクロム線に限られるものではなし、ヒータ56の横断面は円形に限らず、楕円又は多角形等の形状であってもよい。
14 マウスピース
18 電源ユニット
20 液タンク
22 インナチューブ
26 電池
40 キャピラリ管
42 分配口
48 吸収スリーブ(紙管、ペーパフィルタ)
50 大気ポート
52 大気開放口
56 ヒータ
58 ニクロム線(抵抗発熱要素)
60 シース要素
64 ネット(濡れ増加要素)
Claims (12)
- 大気開放口とマウスピースとを接続し、前記大気開放口から前記マウスピースへ向かう空気の流れを許容する吸引経路と、
エアロゾルを発生させる溶液を供給する溶液供給装置であって、
前記溶液を蓄えた溶液供給源と、
前記溶液供給源に接続されている一方、前記吸引経路内にて前記マウスピースに向けて開口した吐出端を有し、前記溶液供給源から前記吐出端まで前記溶液を導き且つ前記吸引経路内に前記空気の流れが生起されたときに前記吐出端から前記溶液を吐出させるキャピラリ管と
を含む溶液供給装置と、
前記吐出端からの吐出溶液を受け止め、この受け止めた吐出溶液を加熱によって霧化させるヒータ装置であって、
電源と、
吐出端の直下流にて、前記空気の流れを許容しつつ前記吐出端との間に所定の距離を存して前記吐出端と対向して配置され、前記電源の電圧が印加されているときに発熱する電気的なヒータと
を含むヒータ装置と
を具備したことを特徴とするエアロゾル吸引器。 - 前記ヒータは前記吸引経路の軸線と直交し且つ前記吸引経路を横断する方向に延びていることを特徴する請求項1に記載のエアロゾル吸引器。
- 前記キャピラリ管は前記吸引経路の軸線上を延びていることを特徴とする請求項1に記載のエアロゾル吸引器。
- 前記距離は、前記吐出端に前記溶液の表面張力によって形成される最大の液滴の直径よりも短いことを特徴とする請求項1に記載のエアロゾル吸引器。
- 前記距離は、前記キャピラリ管の内径よりも長いことを特徴とする請求項4に記載のエアロゾル吸引器。
- 前記キャピラリ管の直径は、前記ヒータの直径よりも小さいことを特徴とする請求項4に記載のエアロゾル吸引器。
- 前記吐出端は、前記吸引経路内を前記マウスピース側からみたとき、前記ヒータによって隠れるべく位置付けられていることを特徴とする請求項1に記載のエアロゾル吸引器。
- 前記ヒータはその外面の少なくとも一部に非平滑領域を有し、この非平滑領域にて前記吐出溶液を受け止めることを特徴とする請求項1に記載のエアロゾル吸引器。
- 前記ヒータは、その外面の加熱温度を前記印加電圧及び前記外面からの熱放射のみにより、前記吐出溶液の霧化に要求される所定の温度範囲に維持する内部構造を更に含むことを特徴とする請求項1に記載のエアロゾル吸引器。
- 前記ヒータは、抵抗発熱要素と、この抵抗発熱要素を囲むシース要素とを有することを特徴とする請求項1に記載のエアロゾル吸引器。
- 前記ヒータはその外面に受け止めた前記吐出溶液を前記外面に沿って延び広げる濡れ増加要素を更に有することを特徴とする請求項10に記載のエアロゾル吸引器。
- 前記電源は市販の電池を含むことを特徴とする請求項1に記載のエアロゾル吸引器。
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CN201180072944.4A CN103732280B (zh) | 2011-08-19 | 2011-08-19 | 气溶胶吸引器 |
MYPI2013702532A MY162480A (en) | 2011-08-19 | 2011-08-19 | Aerosol Inhalator |
PCT/JP2011/068783 WO2013027249A1 (ja) | 2011-08-19 | 2011-08-19 | エアロゾル吸引器 |
PL11871255T PL2719416T3 (pl) | 2011-08-19 | 2011-08-19 | Inhalator aerozolowy |
RU2014106076/14A RU2551944C1 (ru) | 2011-08-19 | 2011-08-19 | Аэрозольный ингалятор |
EP11871255.3A EP2719416B1 (en) | 2011-08-19 | 2011-08-19 | Aerosol inhaler |
CA2840870A CA2840870C (en) | 2011-08-19 | 2011-08-19 | Aerosol inhalator |
UAA201402786A UA110852C2 (uk) | 2011-08-19 | 2011-08-19 | Аерозольний інгалятор |
JP2013529790A JP5717218B2 (ja) | 2011-08-19 | 2011-08-19 | エアロゾル吸引器 |
KR1020147004185A KR101540192B1 (ko) | 2011-08-19 | 2011-08-19 | 에어로졸 흡인기 |
US14/144,694 US10004870B2 (en) | 2011-08-19 | 2013-12-31 | Aerosol inhalator |
HK14105724.6A HK1192496A1 (zh) | 2011-08-19 | 2014-06-17 | 氣溶膠吸引器 |
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EP (1) | EP2719416B1 (ja) |
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CN (1) | CN103732280B (ja) |
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HK (1) | HK1192496A1 (ja) |
MY (1) | MY162480A (ja) |
PL (1) | PL2719416T3 (ja) |
RU (1) | RU2551944C1 (ja) |
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Also Published As
Publication number | Publication date |
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PL2719416T3 (pl) | 2017-11-30 |
JPWO2013027249A1 (ja) | 2015-03-05 |
CN103732280B (zh) | 2016-01-06 |
US20140109905A1 (en) | 2014-04-24 |
CN103732280A (zh) | 2014-04-16 |
KR20140037270A (ko) | 2014-03-26 |
RU2551944C1 (ru) | 2015-06-10 |
EP2719416B1 (en) | 2017-06-14 |
CA2840870C (en) | 2016-02-09 |
MY162480A (en) | 2017-06-15 |
KR101540192B1 (ko) | 2015-07-28 |
CA2840870A1 (en) | 2013-02-28 |
US10004870B2 (en) | 2018-06-26 |
UA110852C2 (uk) | 2016-02-25 |
HK1192496A1 (zh) | 2014-08-22 |
EP2719416A1 (en) | 2014-04-16 |
EP2719416A4 (en) | 2015-03-04 |
JP5717218B2 (ja) | 2015-05-13 |
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