JP2017047130A - Medicine inhaler - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a medicine inhaler allowing a particulate medicine to reach a target organ without generating disturbance of an airflow conveying the particulate medicine in a patient's body.SOLUTION: In a medicine inhaler 1 for administering a particulate medicine to a respiratory system of a patient, a control part 9 operates a selector valve 4, switches a flow path of a first conduit 8 interposed between a compressor 7 and a first nozzle 2 from a closed state to an open state, and operates a cylinder 3 to supply the medicine to the flow path after a lapse of a predetermined time. The first nozzle 2 jets compressed air containing the medicine into an oral cavity and makes the medicine reach the respiratory system by a transport flow containing the medicine.SELECTED DRAWING: Figure 1

Description

  The present invention relates to a drug inhalation device for administering a liquid drug or a powder drug to a patient with a respiratory disease.

  In the treatment of respiratory diseases such as cold syndrome, bronchitis, and pneumonia, liquid drugs or powder drugs that have anti-inflammatory and bronchodilating effects are often administered to patients. Is also used. Devices for inhaling medicine include a steam inhaler and a nebulizer. A steam inhaler mainly sprays a liquid medicine in the form of a mist, and sends a fine liquid medicine to the trachea, bronchi and lungs. Nebulizers mainly deliver powdered drugs to the trachea, bronchi, and lungs with airflow generated by inhalation and jet airflow generated by a compressor. Hereinafter, the microdroplet drug and the powder drug are collectively referred to as a particulate drug.

  When the target organ that transports the particulate medicine is, for example, the lung, the particulate medicine reaches the lung from the oral cavity through the pharynx, larynx, trachea, bronchus, and the like. At this time, it is inevitable that a part of the medicine put into the oral cavity adheres to the inner wall of the oral cavity or pharynx before reaching the lungs, and only the remaining part that does not adhere Reach the target lung.

  Since the dose of the drug, that is, the amount of the drug that should reach the lungs, is determined in advance, considering that only a part of the injected drug reaches the lungs, the dose of the drug should be larger than the dose of the drug to be administered. It is put in the oral cavity.

  In addition, particulate drugs adhering to the inner wall of the oral cavity and pharynx are also absorbed into the body, so a larger amount of drug than the dose is absorbed into the body, and there is a high risk of side effects due to excessive drugs. There is a problem of becoming.

  In the actuator for an inhaler described in Patent Document 1, a plurality of through holes are provided in a peripheral wall of an outlet that is inhaled by a user, and an annular air flow is formed on the inner peripheral surface of the outlet during inhalation. The formed annular air flow becomes an air flow covering the aerosolized drug, and the jet flow of the drug can be favorably guided.

JP 2010-501225 A

  The actuator for an inhaler described in Patent Document 1 is said to form an annular air flow and to guide the medicine jet flow well, but after being discharged from the outlet, the central medicine jet flow and its surroundings It is difficult to reach the patient's body, for example, the trachea, while the annular airflow is maintained. This is because the central drug jet flow diffuses outward and disturbs the surrounding annular air flow, or the surrounding annular air flow hits the inner wall such as the pharynx and heads inward, and the central drug jet flow Because it disturbs.

  The objective of this invention is providing the chemical | medical agent inhalation apparatus which can make a particulate medicine reach | attain the target organ, without disturbing the airflow which conveys a particulate medicine within a patient's body.

The present invention relates to a drug inhalation device for administering a particulate drug to a respiratory organ of a patient.
A compressed air generating section for generating compressed air;
A first nozzle through which the compressed air generated by the compressed air generation unit is guided, and is inserted between an upper dentition and a lower dentition and injects the compressed air into the oral cavity; the pharynx and the larynx from the oral cavity; A first nozzle for generating an air flow up to at least one of the trachea and bronchi;
A conduit interposed between the compressed air generating unit and the first nozzle, and a flow path for allowing the compressed air generated by the compressed air generating unit to flow from the compressed air generating unit to the first nozzle. A conduit including a switching valve for switching the flow path between an open state and a closed state;
When compressed air is flowing through the flow path, a drug supply unit that supplies particulate drug to the flow path;
A control unit that controls the operation of the medicine supply unit and the switching valve, and when the switching valve is switched from a closed state to an open state and a predetermined time elapses, the medicine supply unit is operated to supply the medicine A control unit for supplying to the flow path,
The first nozzle is a drug inhaler characterized by injecting compressed air containing a drug into the oral cavity and causing the drug to reach a respiratory organ by an air flow containing the drug.

  In the invention, it is preferable that the first nozzle has a circular nozzle hole having a hole diameter of 2.5 mm to 15 mm.

Further, the present invention is inserted between the maxillary dentition and the mandibular dentition, is located on the maxillary dentition side with respect to the first nozzle in the oral cavity, and has air in the same direction as the injection direction of the first nozzle. A second nozzle that generates a flat air flow that spreads to the left and right;
An air feeding unit for feeding air to the second nozzle,
The control unit controls the operation of the air supply unit, operates the air supply unit in advance before switching the switching valve from the closed state to the open state, and discharges air from the second nozzle. Features.

  Further, the present invention is characterized in that an air flow velocity ejected from the first nozzle is higher than an air flow velocity ejected from the second nozzle.

  In the invention, it is preferable that the second nozzle has a plurality of circular nozzle holes arranged in the left-right direction.

The present invention is also a mouthpiece,
A first holding unit for holding the first nozzle;
A second holding part for holding the second nozzle;
The first holding portion and the second holding portion so that the second holding portion is positioned on the upper dentition side with respect to the first holding portion in a state of being sandwiched between the upper jaw row and the lower jaw row. And a main body provided with an opening for taking in external air into the oral cavity.

  According to the present invention, in the drug inhaler for administering the particulate drug to the respiratory organs of the patient, the control unit operates the switching valve, and the conduit interposed between the compressed air generation unit and the first nozzle. When a predetermined time elapses after the channel is switched from the closed state to the open state, the drug supply unit is operated to supply the drug to the channel. When the compressed air containing the medicine is injected into the oral cavity by the first nozzle, a transport flow containing the medicine is generated, and thereby the medicine reaches the respiratory system organ.

  Thereby, the particulate medicine can reach the target respiratory system organ in the patient's body without disturbing the airflow that transports the particulate medicine.

  According to the invention, it is preferable that the first nozzle has a circular nozzle hole having a hole diameter of 2.5 mm to 15 mm.

  Further, according to the present invention, the control unit operates the air supply unit in advance before switching the switching valve from the closed state to the open state, and is positioned closer to the maxillary dentition side than the first nozzle in the oral cavity. Air is discharged from the second nozzle.

  The air discharged from the second nozzle becomes a guide flow, and it is possible to suppress the turbulence of the transport flow particularly at the bent portion from the oral cavity to the pharynx.

  Further, according to the present invention, it is preferable that the flow velocity of air injected from the first nozzle is higher than the flow velocity of air discharged from the second nozzle.

  According to the present invention, the second nozzle can generate a flat guide flow by a plurality of circular nozzle holes arranged in the left-right direction.

  According to the invention, the mouthpiece includes a mouthpiece having a first holding portion that holds the first nozzle, a second holding portion that holds the second nozzle, and a main body portion. Thereby, the patient who uses the device can appropriately inject the first nozzle and the second nozzle in the oral cavity just by biting the mouthpiece, and can easily and reliably inhale the medicine. It can be performed.

BRIEF DESCRIPTION OF THE DRAWINGS It is the schematic which shows the structure of the chemical | medical agent inhalation apparatus 1 which is 1st Embodiment of this invention, and the schematic of a human respiratory system. It is the schematic which shows the structure of 1 A of chemical | medical agent inhalation devices which are 2nd Embodiment, and the schematic of a human respiratory system. It is a schematic diagram which shows the relationship between the air flow of a guide flow and a conveyance flow. 2 is a diagram illustrating a configuration of a mouthpiece 20. FIG. It is the figure which visualized the air flow generated with the conventional double tube structure nozzle. It is the figure which visualized the air flow generated by the single nozzle. It is the figure which image | photographed the powder when the compressed air containing the powder imitating a particulate medicine is injected from the single 1st nozzle. It is the schematic which shows the structure of the test apparatus 101 using the simulation flow path. It is the figure which visualized the air flow in the bending part of a flow path. It is the figure which visualized the air flow by the test apparatus 101 using the simulation flow path 113. FIG. It is a figure which shows the time-dependent change of the visualized air flow in the bending part of the simulation flow path. In the test apparatus 101, it is the figure which image | photographed the powder in the bending part when conveying the powder imitating a particulate medicine.

  FIG. 1 is a schematic diagram showing a configuration of a drug inhaler 1 according to a first embodiment of the present invention and a schematic diagram of a human respiratory system.

  The medicine inhaler 1 includes a first nozzle 2, a cylinder 3, a switching valve 4, a pressure gauge 5, a compression tank 6, a compressor 7, a first conduit 8, and a control unit 9.

  The drug inhaler 1 is an apparatus for administering a particulate drug including a liquid drug in the form of a fine droplet and a solid drug in the form of a fine powder to a patient with a respiratory disease by inhalation.

  The first nozzle 2 is an injection nozzle that injects compressed air, and injects air into the oral cavity to generate an air flow from the oral cavity to at least one of the pharynx, larynx, trachea, and bronchus. Although the air flow generated by the air ejected from the first nozzle 2 will be described in detail later, this air flow becomes a transport flow for transporting the particulate medicine, and for example, adheres to the inner wall of the oral cavity, pharynx, etc. The drug reaches the bronchi instead.

  The compressed air to be injected from the first nozzle 2 may be, for example, a pressure of 50 kPa to 200 kPa and a flow rate of 1 m / s to 10 m / s.

  The shape and diameter of the nozzle hole of the first nozzle 2 are the controlling factors of the shape and size of the generated transport flow. Although the transport flow to be generated varies depending on the organ to which the drug reaches, for example, when trying to reach the bronchus, the nozzle hole having a circular channel cross section with a hole diameter of 2.5 mm to 15 mm It is preferable to do.

  The cylinder 3 is a drug supply unit that supplies particulate drug to an air flow in which the compressed air discharged from the compression tank 6 flows through the first conduit 8. The cylinder 3 includes a tubular member that is interposed in the flow path of the first conduit 8 and constitutes a part of the flow path, and a tubular cartridge 3a that stores a medicine, and is configured to be able to switch between them. Yes. When the medicine is not supplied, the tubular member is interposed in the flow path so that the air flow is simply passed, and the tubular member is switched to the cartridge 3a at the timing of supplying the medicine. Since the medicine is stored in the cartridge 3a, when the cartridge 3a is switched, the stored medicine is contained in the air flow through which the medicine flows, and the medicine is conveyed toward the first nozzle 2 together with the air flow. .

  The switching mechanism between the tubular member and the cartridge 3a may be any type, for example, a slide type or a rotary type. It is preferable that the operation of the switching mechanism in the cylinder 3 is electrically controlled by the control unit 9, but this is not restrictive, and a lever or the like can be provided so that a patient, a doctor, a nurse, or the like can be switched manually. In such a configuration, it is not necessary to secure a power source for control.

  The switching valve 4 switches the flow path in the first conduit 8 between an open state and a closed state. When the flow path is closed by the switching valve 4, air is not injected from the first nozzle 2. When the flow path is opened by the switching valve 4, air is injected from the first nozzle 2 to generate an air flow. The switching valve 4 is, for example, an electromagnetic pressure control valve, and the opening / closing operation of the valve body is electrically controlled by the control unit 9. Moreover, it is preferable that the switching valve 4 is configured not only to switch the open / close state but also to change the opening when it is in the open state. By making it possible to change the opening, it is possible to adjust the flow rate of the air flowing through the first conduit 8 as appropriate, and the flow passage cross section of the first conduit 8 and the opening cross section of the switching valve 4 can be adjusted. This is preferable because it can be matched quickly. Note that the switching valve 4 can be opened and closed and the opening thereof can be changed by providing a lever or the like as in the cylinder 3 so that it can be switched manually. It is not necessary to secure a power source for

  The pressure gauge 5 measures the pressure (static pressure) in the compression tank 6, and the measured value is used to keep the pressure in the compression tank 6 constant. Note that the pressure gauge 5 is not an essential component, and a pressure in the compression tank 6 may be kept constant by providing a relief valve or the like. Further, if the compressed air is generated manually by air cocking or the like, a desired pressure can be easily obtained by the number of operations.

  The compression tank 6 is a pressure vessel that temporarily stores the compressed air generated by the compressor 7. The compression tank 6 can store about 0.05 L to 0.2 L (liter) of compressed air having a pressure of 50 kPa to 200 kPa.

  The compressor 7 is a gas transporter and is a compressed air generating unit that generates compressed air. The compressor 7 only needs to be able to generate compressed air so that the pressure and flow velocity of the compressed air to be injected are within the above-described predetermined range, and various types such as a reciprocating type using a piston and a centrifugal type using an impeller. It is possible to use a compressor of the compression method.

  The first conduit 8 is an air transport pipe having a flow path that guides the compressed air generated by the compressor 7 to the first nozzle 2. The first conduit 8 only needs to be capable of transporting air, and can be any of a metal tube such as a steel tube and an aluminum tube, a non-metal tube such as a glass tube, a rubber tube, a vinyl chloride tube, and a polyurethane tube. A polyurethane tube is preferred.

  The control unit 9 is realized by a microcomputer or the like, and electrically controls at least the operations of the cylinder 3 and the switching valve 4. The switching valve 4 is normally closed, and compressed air is not injected from the first nozzle 2. When the patient tries to inhale the medicine and operates the medicine inhaler 1, the control unit 9 switches the switching valve 4 to the open state and injects compressed air from the first nozzle 2 to generate an air flow in the oral cavity. generate. When the operation of the cylinder 3 is started, the tubular member is set in the flow path, and when a predetermined time elapses after the switching valve 4 is switched to the open state, the control unit 9 operates the cylinder 3 to switch the tubular member. And the cartridge 3a is set in the flow path. At the start of operation, only compressed air flows through the first conduit 8, only air is injected from the first nozzle 2 into the patient's oral cavity, and the drug is supplied after the air flow is generated. Included compressed air is jetted from the first nozzle 2. At this time, a stable air flow has reached the bronchi by the compressed air previously injected, and the medicine is transported by the transport flow, which is this air flow, and reaches the bronchus. Since the medicine once included in the carrier flow is not released from the carrier flow, the medicine contained in the carrier flow does not adhere to the inner wall of the oral cavity or the pharynx and can reach the bronchus. If the cylinder 3 and the switching valve 4 are configured so as to be manually operable as described above, the control unit 9 is unnecessary, and the configuration of the apparatus is simplified by providing air cocking instead of the compressor 7. In addition, it is not necessary to secure a power source, and the device can be used even in the event of a power failure such as a disaster.

  A feature of the present invention is that a compressed air not containing a medicine is jetted from a single first nozzle 2 to generate a stable transport flow that does not contact the inner wall in the respiratory system, and the medicine is supplied to this stable transport flow. By including, it is in the point which can convey a chemical | medical agent to the target organ, without making a chemical | medical agent adhere to an inner wall.

  Since the present invention can reach the deep main bronchus or bronchiole without adhering to the inner wall in the respiratory system, of course, trachea and larynx, pharynx as the target organ of transport, It is possible to reach each organ without adhering to the inner wall on the way.

  FIG. 2 is a schematic diagram showing a configuration of a drug inhaler 1A according to the second embodiment and a schematic diagram of a human respiratory system.

  The medicine inhaler 1A includes a first nozzle 2, a cylinder 3, a switching valve 4, a pressure gauge 5, a compression tank 6, a compressor 7, a first conduit 8, a control unit 9A, a second nozzle 10, an air pump 11, and a second conduit. 12 is provided.

  In the present embodiment, a second nozzle 10, an air pump 11, and a second conduit 12 are further added to the medicine inhaler 1 of the first embodiment. About the site | part which performs the same operation | movement with the same structure as 1st Embodiment, the same referential mark is attached | subjected and detailed description is abbreviate | omitted. Below, each structure of the 2nd nozzle 10, the air pump 11, and the 2nd conduit | pipe 12 added by this embodiment is demonstrated.

  Similar to the first nozzle 2, the second nozzle 10 is used to generate an air flow in the oral cavity, and is inserted between the upper and lower jaw dentitions. The air is discharged toward the back side of the oral cavity which is located on the upper dentition side and is the same direction as the injection direction of the first nozzle 2, thereby generating a flat air flow spreading left and right. Here, the same direction means that the injection direction of the first nozzle 2 and the injection direction of the second nozzle 10 are parallel, or the intersecting angle is less than 90 °, and in the case of intersecting, the angle is preferably 45 ° or less. .

  The air pump 11 is the same gas transport machine as the compressor 7, but the discharge pressure (wind pressure) is lower than that of the compressor 7, and the air flow velocity ejected from the first nozzle 2 is the air ejected from the second nozzle 10. It is higher than the flow rate.

  The air sent out from the air pump 11 reaches the second nozzle 10 through the flow path in the second conduit 12 and is discharged from the second nozzle 10. The air pump 11 and the second conduit 12 constitute an air supply unit that supplies air to the second nozzle 10.

  The second conduit 12 is an air transport pipe having a flow path that guides the air sent from the air pump 11 to the second nozzle 10. Similar to the first conduit 8, the second conduit 12 only needs to be able to transport air, and is a metal tube such as a steel tube or an aluminum tube, a non-metal tube such as a glass tube, a rubber tube, a vinyl chloride tube, or a polyurethane tube. Any of these can be used, but a polyurethane tube is preferred.

  The air flow generated by the air discharged from the second nozzle 10 is flat as described above. By flowing such an air flow from the maxillary dentition side of the first nozzle 2, a flat air flow flows from the inner wall of the upper jaw along the inner wall of the pharynx, the larynx and the back side of the trachea. The width of the flat air flow is about the length of a semicircular circumference when the cross-sectional shapes of the pharynx, larynx and trachea are circular.

  Even in the first embodiment, the transport flow generated by the injection from the first nozzle 2 flows from the oral cavity to the bronchus, but in particular, the portion from the oral cavity to the pharynx is bent at approximately 90 ° and goes straight in the oral cavity. The transporting flow is easily disturbed at the bent portion of the pharynx. Since the flat air flow generated by the discharge from the second nozzle 10 does not include a medicine, it may contact the inner wall and can flow along the inner wall as described above. When compressed air is jetted from the first nozzle 2 in a state where such an air flow is flowing in advance, the generated transport flow is guided by a wide air flow flowing along the inner wall in advance. Thereby, it can flow stably to the larynx, trachea, and bronchus without disturbing the transport flow at the bent portion of the pharynx.

  Thus, the flat air flow generated by the air discharged from the second nozzle 10 functions as a guide flow for guiding the transport flow. Here, the air flow velocity discharged from the second nozzle 10 is set lower than the air flow velocity ejected from the first nozzle 2 so that the guide flow does not disturb the transport flow.

  FIG. 3 is a schematic diagram showing the relationship between the guide flow and the carrier flow air flow. FIG. 3A is a longitudinal sectional view, and FIG. 3B is a transverse sectional view taken along the cutting plane line AA. FIG. 3 is a schematic diagram when the cross section of the flow path is rectangular, and the air discharged from the second nozzle 10 is 1/3 to 1/2 the thickness of the flow path at the top of the flow path. It flows along the upper inner wall of the flow path as a flat guide flow 15 that extends over the entire width of the flow path. The air injected from the first nozzle 2 is in the vicinity of the center of the flow path and flows along the guide flow 15 as a carrier flow 16 having a circular cross section under the guide flow 15. Due to the presence of the guide flow 15, the carrier flow 16 can flow in the vicinity of the center of the channel without contacting the inner wall of the channel even if it is a bent channel corresponding to the pharynx from the oral cavity.

  The compressed air to be injected from the second nozzle 10 is preferably injected so as to flow in the oral cavity at a constant flow rate. For example, the flow rate may be 0.2 L / min to 1.0 L / min.

  The shape and size of the nozzle hole of the second nozzle 10 are the controlling factors of the shape and size of the guide flow to be generated. For example, it is preferable to arrange the nozzle holes having a circular channel cross section with a hole diameter of 2 mm to 5 mm in the left-right direction.

  9 A of control parts control the operation | movement of the cylinder 3 and the switching valve 4 which are the same as the control part 9 of 1st Embodiment, and also control the operation | movement of the air pump 11. FIG. As described above, since the guide flow needs to flow in advance before the carrier flow occurs, control is performed so that the operation of the air pump 11 is started before the switching valve 4 is switched to the open state. .

  The guide flow only needs to flow before the carrier flow containing the medicine starts to flow, so even after the switching valve 4 is switched to the open state, before the cylinder 3 is operated. You may control so that operation | movement of the air pump 11 may be started.

  In the present embodiment, it is preferable to further include a mouthpiece. In the first embodiment, since only the first nozzle 2 is inserted into the patient's oral cavity, for example, the patient holds the first nozzle 2 with one hand and inserts it into the oral cavity. It is also possible to operate the device by hand.

  In the second embodiment, since the second nozzle 10 is also used, it is difficult for the patient to operate the apparatus with two nozzles. Further, if the first nozzle 2 and the second nozzle 10 are not inserted and used in the correct direction in the oral cavity, the transport flow may not reach the target organ.

  FIG. 4 is a diagram showing the configuration of the mouthpiece 20. 4A is a view showing a state in which the patient is barking, FIG. 4B is a plan view, FIG. 4C is a front view, and FIG. 4D is a bottom view. is there. The mouthpiece 20 is a state in which the first holding unit 21 that holds the first nozzle 2, the second holding unit 22 that holds the second nozzle 10, and the first holding unit 21 and the second holding unit 22 are stacked. And the second nozzle 10 is closer to the upper dentition side than the first nozzle 2 in a state in which the patient is sandwiched between the upper dentition and the lower dentition. 2nd holding | maintenance part 22 is connected with the upper dentition side rather than 1st holding | maintenance part 21 so that it may be located. Furthermore, the first nozzle 2 and the second nozzle 10 are in a state where the patient holds the mouthpiece 20 and the guide flow from the second nozzle 10 is at an injection angle that is transmitted through the upper wall of the oral cavity (maxillary side), and The first holding portion 21 and the second holding portion are set so that the air flow from the first nozzle 2 is sufficiently below (mandible side), and is set to an injection angle that avoids direct contact with the protruding tongue and uvula. 22 respectively. A groove 24 corresponding to the maxillary dentition is provided on the upper surface of the main body 23, and a groove 25 corresponding to the mandibular dentition is provided on the lower surface of the main body 23. By biting so as to match the tooth rows, the injection angles of the first nozzle 2 and the second nozzle 10 can be easily positioned.

  When the mouthpiece 20 is used, the oral cavity may be sealed by the first holding part 21, the second holding part 22, and the main body part 23. When sealed, external air can no longer be taken into the oral cavity, so the body portion is provided with an opening 23a for taking external air into the oral cavity.

  First, as in the prior art, a configuration in which a transport flow for transporting a medicine to the center portion is generated and an annular air flow is generated around the transport flow was examined.

  A double-tube nozzle 50 having an inner diameter of 8 mm and an outer diameter of 13 mm is prepared, and high-pressure air stored in a compression tank having a pressure of 150 kPa and a volume of 0.2 L is injected, and the channel cross section is a square having a side of 35 mm and a length The air flow generated in the straight flow path of 600 mm was observed.

  As a method for observing the air flow, an existing visualization method used in the particle image velocimetry (PIV) was used. In the PIV method, tracer particles are mixed in a flow of air, the tracer particles are irradiated with laser light from a laser sheet light source, and the movement of the tracer particles is measured by photographing the position of the tracer particles with a high-speed camera. be able to.

  FIG. 5 is a diagram visualizing the air flow generated by the conventional double tube structure nozzle 50. FIG. 5A shows a state immediately after the air is injected from the nozzle, FIG. 5B shows a state after 0.3 seconds from the injection, and FIG. 5C shows a state after 0.7 seconds from the injection. Was taken. As can be seen from FIG. 5, in the double pipe structure nozzle 50, vortex flows 51, 52, 53 are generated around the nozzle immediately after injection, at a position away from the nozzle after injection, and the like, thereby generating a stable conveying flow. I can't.

  Next, a configuration in which a transport flow is generated by a single nozzle (first nozzle 2) as in the first embodiment of the present invention was studied.

  A nozzle having a circular nozzle hole with a hole diameter of 3 mm is prepared as the first nozzle 2, and compressed air accumulated at a pressure of 150 kPa is injected into a 0.2 L compression tank, and the flow path cross-section is a rectangle of 35 mm × 45 mm. The air flow generated in the straight channel 54 having a length of 500 mm was observed.

  FIG. 6 is a diagram visualizing the air flow generated by a single nozzle. Immediately after the compressed air is jetted from the first nozzle 2, a vortex or the like is generated as in the double pipe structure nozzle 50, but after 3 seconds from the jet, a straight and stable airflow is generated in the straight flow path 54. It was confirmed that it occurred.

  Immediately after the compressed air is injected from the first nozzle 2, the injected air collides with the air existing in the straight flow path 54, and the air flow is disturbed. Further, when the injection continues, the air present in the flow path is pushed out to the downstream side by the injected air (right part in the photograph in FIG. 6), and thereafter continues from the tip of the first nozzle 2. Thus, a straight and stable air flow A1 is generated (the left part of the photograph in FIG. 6).

  Furthermore, instead of the tracer particles, a powder imitating a particulate drug was conveyed by an air flow, and the movement of the powder at that time was observed. FIG. 7 is a photograph of the powder in the straight flow path 54 when compressed air containing the powder 55 imitating a particulate medicine is ejected from the single first nozzle 2. FIG. 7A is a photograph of the entire straight channel 54 (channel length 500 mm) having a rectangular channel cross section of 35 mm × 45 mm, and FIG. 7B is an enlarged view of the vicinity of the nozzle tip. It is a photograph.

  As can be seen from FIG. 7A, the powder 55 is conveyed in a straight line by the conveying flow through the central portion of the flow path over the entire straight flow path 54. Further, as can be seen from the enlarged photograph of FIG. 7B, the powder 55 exists only in the transport flow in the central portion, and no powder exists outside the transport flow.

From the above examination, it became clear that
(1) The conventional double-pipe structure nozzle cannot stably generate a transport flow for transporting a medicine (2) It is necessary to inject compressed air from a single nozzle (3 However, immediately after the injection, the air flow is disturbed by the collision with the air existing in the flow path, and a stable air flow is generated in the flow path after a predetermined time has elapsed since the injection.

  Even if a single nozzle is used, if compressed air is allowed to flow through the flow path in the state where the particulate medicine is placed in the flow path of the compressed air in the apparatus as in a conventional inhaler, the jet from the nozzle The drug is already contained in the compressed air at the start, and in the oral cavity, the air existing in the oral cavity collides with the compressed air containing the drug, and a turbulent air flow is generated. . If it does so, the chemical | medical agent contained in the turbulent air flow will adhere to the inner wall of the oral cavity, the inner wall of the pharynx and the larynx downstream from the oral cavity.

  Therefore, in the present invention, as described above, first, the switching valve 4 is switched from the closed state to the open state with the tubular member set in the cylinder 3, and the compressed air containing no medicine is injected from the first nozzle 2. The compressed air containing no medicine pushes the air present in the oral cavity downstream and generates a stable air flow. After a predetermined time (for example, 2 to 3 seconds) has elapsed after switching the switching valve 4, that is, after the air flow has started to flow stably, the cartridge 3a is set in the cylinder 3 and the first conduit 8 The particulate drug is supplied to the flow path. Since the medicine supplied by the cylinder 3 is contained in the already generated stable air flow, the air flow is carried through the patient's respiratory system organ without adhering to the inner wall.

  In the above examination, compressed air is injected into a simple straight flow path in order to confirm the generation of a stable air flow. However, the human respiratory flow path is bent approximately 90 ° between the oral cavity and the pharynx, so that the particulate drug can reach the larynx, trachea, and bronchi further downstream from the pharynx. It is necessary to generate a stable air flow along the flow path without being disturbed even if the flow path is bent.

  Therefore, the inventors of the present invention produced a simulated flow path bent at the pharyngeal part imitating the human respiratory system, and observed the air flow generated in the simulated flow path.

  The simulated channel was modeled on respiratory organs from the oral cavity to the main bronchus based on anatomical knowledge. Furthermore, in order to reproduce inhalation by breathing, a negative pressure fan is provided at the most downstream side of the simulated flow path to generate an air flow toward the outside of the flow path.

  FIG. 8 is a schematic diagram showing the configuration of the test apparatus 101 using a simulated flow path. The test apparatus 101 includes a first nozzle 102, a tracer tank 103, a switching valve 104, a pressure gauge 105, a compression tank 106, a compressor 107, a first conduit 108, a second nozzle 110, an air pump 111, a second conduit 112, a simulated flow. A path 113, a laser device 114, and a negative pressure fan 115 are provided.

  The test apparatus 101 has a configuration similar to that of the second embodiment, and parts having the same configuration as that of the second embodiment, such as the first nozzle 2 and the first nozzle 102, are denoted by reference numerals 100 in the second embodiment. A number added with is added as a reference sign.

  The tracer tank 103 stores the tracer particles, and causes the compressed air injected from the first nozzle to contain the tracer particles in the first conduit 108. The simulated flow path 113 is a flow path that imitates the human respiratory system as described above. The simulated flow path 113 is open to both the oral cavity side and the main bronchus side, and the first nozzle 102 and the second nozzle 110 are fixed to the oral cavity side opening. is set up. The laser device 114 is a laser sheet light source used in the PIV method, and irradiates the simulated flow path 113 with a sheet laser 114a spreading in a planar shape. Images were taken by a high speed camera (not shown) from a direction perpendicular to the sheet laser 114a. The negative pressure fan 115 is realized by a suction fan, an attraction fan, or the like, and forcibly generates a flow from the simulated flow path 113 to the external space. By operating the negative pressure fan 115, Reproduce the intake state.

  FIG. 9 is a diagram visualizing the air flow in the bent portion 56 of the flow path. FIG. 9A shows that the high pressure air of 150 kPa is accumulated from the first nozzle 102 into the compression tank having a volume of 0.2 L, the switching valve is switched from the closed state to the open state, and the compressed air is injected at once, and the second nozzle 110 Shows the air flow in the flow path when air is discharged at a flow rate of 0.8 L / min. FIG. 9B further shows the air flow in the flow path when the negative pressure fan 115 is operated. In FIG. 7, not the simulated flow path 113 but a flow path that is simply bent at 90 ° is used as the flow path.

  As shown in FIG. 9A, the transport flow generated by the injection from the first nozzle 102 is bent downward along the curved portion by the guide flow generated by the discharge from the second nozzle 110. The air flow was slightly disturbed immediately after the curved portion, and a stable air flow was generated only for a short time.

  As shown in FIG. 9B, it was found that by further operating the negative pressure fan 115, the air flow is stabilized for a long time without disturbing the flow path after the curved portion.

  FIG. 10 is a diagram visualizing the air flow by the test apparatus 101 using the simulated flow path 113. FIG. 11 is a diagram showing a change with time of the visualized air flow in the bent portion 113a of the simulated flow path 113. FIG. 10 and 11, the air flow A2 when the negative pressure fan 115 is operated is shown as in FIG. 9B.

  As shown in FIG. 10, it can be seen that a stable air flow is generated over the entire flow path of the simulated flow path 113. FIG. 11A shows a state immediately after injection, and the time has passed in the order of FIGS. 11B, 11C, and 11D. As shown in FIG. 11 (a), immediately after the injection, the air flow injected from the first nozzle 102 flows so as to contact the inner wall on the back side of the oral cavity in the bent portion 113a, but time elapses. It can be seen that the air flow moves toward the center of the flow path and flows stably without contacting the inner wall.

  Furthermore, similarly to FIG. 7, instead of the tracer particles, a powder imitating a particulate medicine was conveyed by an air flow, and the movement of the powder at that time was observed.

  FIG. 12 is a photograph of the powder in the bent portion 113a when the test apparatus 101 transports the powder 55 imitating a particulate medicine.

  The time elapses in the order of FIG. 12A to FIG. 12B, FIG. 12C, and FIG. It can be seen that the powder 55 passing through the bent portion 113a passes through the center of the flow path without adhering to the inner wall.

  As described above, according to the present invention, the particulate medicine can reach the target organ without attaching the medicine to the inner wall even if there is a bent portion like a human respiratory organ. .

  As can be seen from the above examination, the air flow is further stabilized when the negative pressure fan 115 in the test apparatus 101 is operated. The negative pressure fan 115 is operated when the patient using the drug inhaler 1, 1A inhales. Therefore, when using the drug inhaler 1, 1A, the patient sucks air. Preferably it is done.

  The medicine inhaler 1, 1 </ b> A includes an operation switch and a power switch that are operated when starting inhalation of medicine. When the patient operates the power switch by himself / herself, the doctor or nurse may operate it. However, in any case, when the operated switch is turned on, the switching valve 4 is closed and the cylinder 3 is tubular. In addition to setting the members, the compressor 7 starts to compress the air to enter a standby state.

  The operation switch may be operated by a doctor or a nurse when the patient operates by himself / herself. In any case, when the operation switch is operated in the standby state, the control unit 9 or 9A detects this. Then, the air pump 11 is operated to discharge air from the second nozzle 10 to generate a guide flow in the oral cavity. When a predetermined time (1 to 2 seconds) elapses, the control units 9 and 9A operate the switching valve 4 to switch the flow path from the closed state to the open state, inject compressed air from the first nozzle 2, and A conveying flow is generated inside. When a predetermined time (2 to 5 seconds) elapses after the switching valve 4 is switched to the open state, the control units 9 and 9A operate the cylinder 3 and set the cartridge containing the particulate medicine in the flow path. To do. From the first nozzle 2, compressed air containing the medicine is jetted, and the medicine is already transported by the transport flow that has already flowed stably in the oral cavity. The drug reaches, for example, the main bronchi of respiratory organs. At this time, the drug does not adhere to the inner wall of each organ passing through the oral cavity.

  Furthermore, the medicine inhaler 1, 1A preferably includes a speaker. As can be seen from the above examination, the air flow is further stabilized when the negative pressure fan 115 in the test apparatus 101 is operated. The negative pressure fan 115 is operated when the patient using the drug inhaler 1, 1A inhales. Therefore, when using the drug inhaler 1, 1A, the patient sucks air. Preferably it is done. For example, it is preferable to cause the patient using the apparatus to inhale at the timing when the cylinder 3 is operated to supply the medicine. In order to inhale, it is preferable that a voice such as “Please take a deep breath” is output from the speaker at the timing when the cylinder 3 is operated to prompt the patient to inhale.

  The inhalation of the medicine is started when the control unit 9, 9A detects the operation of the operation switch, and the end of the inhalation is detected by the control unit 9, 9A when the operation switch is operated. May be configured to switch the open state to the closed state and operate the cylinder 3 to set the tubular member. In addition, the end of the inhalation may be determined by the control units 9 and 9A without depending on the operation of the operation switch. When the time (inhalation time) required to discharge all the medicine from the first nozzle 2 is measured in advance and the inhalation time has elapsed since the cylinder 3 was operated at the start of inhalation, the switching valve 4 is used as described above. And the cylinder 3 may be terminated. Since the inhalation time varies depending on the amount and type of the medicine to be administered, the inhalation time corresponding to the amount and type should be measured, and the inhalation should be terminated at the inhalation time corresponding to the type and amount of the medicine to be used. .

  Further, a sensor for detecting the medicine flowing in the flow path of the first conduit 8 between the cylinder 3 and the first nozzle 2 is provided, and when no medicine is detected in the flow path by this sensor, the switching valve 4 and the cylinder 3 may be terminated.

DESCRIPTION OF SYMBOLS 1,1A Drug inhaler 2,102 1st nozzle 3 Cylinder 3a Cartridge 4,104 Switching valve 5,105 Pressure gauge 6,106 Compression tank 7,107 Compressor 8,108 1st conduit | pipe 9,9A Control part 10,110 1st 2 nozzles 11, 111 air pumps 12, 112 2nd conduit 20 mouthpiece 21 1st holding part 22 2nd holding part 23 main body part 101 test apparatus 103 tracer tank 113 simulated flow path 113a bent part 114 laser apparatus 114a sheet laser 115 shadow Pressure fan

Claims (6)

In a drug inhalation device for administering a particulate drug to a respiratory organ of a patient,
A compressed air generating section for generating compressed air;
A first nozzle through which the compressed air generated by the compressed air generation unit is guided, and is inserted between an upper dentition and a lower dentition and injects the compressed air into the oral cavity; the pharynx and the larynx from the oral cavity; A first nozzle for generating an air flow up to at least one of the trachea and bronchi;
A conduit interposed between the compressed air generating unit and the first nozzle, and a flow path for allowing the compressed air generated by the compressed air generating unit to flow from the compressed air generating unit to the first nozzle. A conduit including a switching valve for switching the flow path between an open state and a closed state;
When compressed air is flowing through the flow path, a drug supply unit that supplies particulate drug to the flow path;
A control unit that controls the operation of the medicine supply unit and the switching valve, and when the switching valve is switched from a closed state to an open state and a predetermined time elapses, the medicine supply unit is operated to supply the medicine A control unit for supplying to the flow path,
The first nozzle jets compressed air containing a medicine into the oral cavity, and causes the medicine to reach a respiratory organ by an air flow containing the medicine.   The drug inhaler according to claim 1, wherein the first nozzle has a circular nozzle hole having a hole diameter of 2.5 mm to 15 mm. It is inserted between the maxillary dentition and the mandibular dentition, is located on the maxillary dentition side with respect to the first nozzle in the oral cavity, and discharges air in the same direction as the injection direction of the first nozzle. A second nozzle for generating a flat air flow extending in
An air feeding unit for feeding air to the second nozzle,
The control unit controls the operation of the air supply unit, operates the air supply unit in advance before switching the switching valve from the closed state to the open state, and discharges air from the second nozzle. The drug inhalation device according to claim 1 or 2, characterized in that   The medicine inhalation device according to claim 3, wherein an air flow velocity ejected from the first nozzle is higher than an air flow velocity ejected from the second nozzle.   The drug inhaler according to claim 3 or 4, wherein the second nozzle has a plurality of circular nozzle holes arranged in the left-right direction. A mouthpiece,
A first holding unit for holding the first nozzle;
A second holding part for holding the second nozzle;
The first holding portion and the second holding portion so that the second holding portion is positioned on the upper dentition side with respect to the first holding portion in a state of being sandwiched between the upper jaw row and the lower jaw row. 6. A drug inhalation device according to claim 3, further comprising a mouthpiece having a main body portion provided with an opening for connecting external air and taking in external air into the oral cavity.