Drug aerosol delivery device for respiratory systems

Abstract

The present invention relates to a drug aerosol supply device for a respiratory system, and an object of the present invention is to prevent secondary respiratory infection caused by condensation water. The drug aerosol supply device according to the present invention includes a T-tube, a drug fine particle generating unit, and a heater. The T-tube includes a straight tube having a first end to which air supplied from the respiratory system is supplied and a second end to be connected to a mask or a mouthpiece, and a branch tube attached to the straight tube so as to be in communication with the straight tube. The drug fine particle generating unit is installed in the branch tube and sprays a fine particle drug. The heater heats the T-tube.

Description

[Technical field]

[0001] The present invention relates to a medicinal aerosol delivery device for the respiratory tract, and more particularly to a medicinal aerosol delivery device capable of preventing secondary respiratory tract infection caused by condensed water. [Background technology]

[0002] The air generated by the respirator is typically heated to 39°C in a humidifier and humidified to 99% before entering the drug aerosol delivery device. The air heated and humidified by the humidifier is atomized with finely divided drug solution and then delivered to a user wearing a mask or mouthpiece. The drug aerosol delivery device includes a T-tube that connects the humidifier and the mask (or mouthpiece) to the nebulizer.

[0003] Because the internal temperature of the T-tube of a conventional pharmaceutical aerosol delivery device is relatively low compared to the air heated in the humidifier, moisture condenses and forms droplets on its inner surface. This condensed moisture accumulates in the T-tube over a long period of time and eventually enters the patient's airway, causing secondary bronchial infection. This situation is further exacerbated when the pharmaceutical aerosol delivery device nebulizes the pharmaceutical liquid into fine particles. Summary of the Invention [Problem to be solved by the invention]

[0004] SUMMARY OF THE PRESENT EMBODIMENT It is therefore an object of the present invention to prevent condensation of moisture inside a pharmaceutical aerosol delivery device.

[0005] Yet another object of the present invention is to prevent moisture condensed within the drug aerosol delivery device from entering the patient's airways and causing secondary bronchial infection. [Means for solving the problem]

[0006] One aspect of the present invention for achieving the above-mentioned object is a drug aerosol supply device for a respiratory system, the device comprising: a T-tube including a straight tube having a first end to which air supplied from the respiratory system is supplied and having a second end connected to a mask or mouthpiece, and a branch tube attached to the straight tube so as to be in communication with the straight tube; a drug microparticle generation unit installed in the branch tube for spraying drug in the form of fine particles; and a heater for heating the T-tube.

[0007] Preferably, the heater comprises a film including a heating wire and is attached to the T-tube. The heater also includes a temperature sensor for measuring the temperature of the T-tube. The heater is integrally formed with a first local heater for heating the straight tube and a second local heater for heating the branched portion. A heating wire terminal for connecting the heating wire to an external power source is disposed at the second end.

[0008] Preferably, the pharmaceutical aerosol supplying device further includes a socket portion including a heating wire connection terminal electrically connected to the heating wire terminal and a power connection terminal electrically connected to an external power source. The power connection terminal is disposed opposite to a first end of the straight tube. The socket portion is disposed on the straight tube such that the power connection terminal is inclined downward relative to the straight tube. The socket portion also has a sensor escape groove for allowing the temperature sensor to escape. The heating wire connection terminal is connected to the power connection terminal via an elastic body. Effect of the Invention

[0009] The present invention can suppress condensation of moisture inside the drug aerosol supplying device, and can prevent moisture condensed inside the drug aerosol supplying device from entering the patient's airway and causing secondary bronchial infection. [Brief description of the drawings]

[0010] [Figure 1] FIG. 1 is a diagram showing the configuration of a respiratory apparatus to which a pharmaceutical aerosol supply device according to an embodiment of the present invention is applied. [Diagram 2] FIG. 2 is a cross-sectional view showing the function of the pharmaceutical aerosol supplying device shown in FIG. [Diagram 3] 1 is a diagram showing a configuration of a pharmaceutical aerosol supplying device to which an embodiment of the present invention is applied. [Figure 4] 4 is a diagram showing the configuration of a T-tube, a heater, and a socket portion shown in FIG. 3. [Diagram 5] 4 is a diagram showing an assembly process of the T-tube, the heater, and the socket portion shown in FIG. 3. [Figure 6a] 4 is a diagram showing a configuration for assembling a socket portion to the T-tube to which the heater shown in FIG. 3 is attached. FIG. [Figure 6b] FIG. [Figure 7] FIG. 4 is a diagram showing a state in which a power cable is connected to the pharmaceutical aerosol supplying device shown in FIG. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0011] Hereinafter, the embodiments of the present invention will be described in detail with reference to the accompanying drawings. Terms used in this specification should not be interpreted as being limited to their conventional or dictionary meanings. Therefore, the embodiment described in this specification and the configuration shown in the drawings are merely one of the most preferred embodiments of the present invention, and do not represent all of the technical ideas of the present invention, and therefore, it should be understood that there may be various equivalents and modifications that can replace them at the time of this application. In the entire drawings, the same reference numbers are used for parts having the same functions, and detailed descriptions are omitted.

[0012] It should be noted that terms such as "first" and "second" may be used to describe various components, and these terms are used only to distinguish any component from other components.

[0013] 1 is a diagram showing the configuration of a respirator 100 to which a pharmaceutical aerosol supplying device 200 according to an embodiment of the present invention is applied. As shown in FIG. 1, the respirator 100 includes an air purifier 1, an inhalation breath detector 10, a T-tube 20, a cover 40, and a packing closure part 50.

[0014] The air purifier 1 discharges the first air, the oxygen concentration, the oxygen pressure, and the oxygen speed of which are each set to a predetermined value. The oxygen concentration may be set according to the lung function capacity of the patient. For example, when the lung function is half the level of a healthy person, the oxygen concentration may be set to about 40%. The inhalation breath detector 10 may be connected to the air purifier 1. The inhalation breath detector 10 may detect the first air and generate a detection signal when the first air is discharged from the inhalation breath detector 10. The first tube 2 may be connected to the inhalation breath detector 10 and may flow the first air. The humidifier 3 is connected to the first tube 2 and controls the temperature and humidity of the first air to generate the second air, which is then discharged. The second tube 4 may be connected to the humidifier 3 and may flow the second air.

[0015] The T-tube 20 has a branch tube 24 formed on one side of the straight tube 22. The second tube 4 is connected to one end of the straight tube 22 so that the second air can pass through the straight tube 22. The drug microparticle generating unit 30 is installed in the branch tube 24, and operates to spray microparticle drug into the second air only when a detection signal is input.

[0016] The Y tube 5 may be connected at one end to the T tube 20 and at the other end to a mask or mouthpiece. The return tube 6 may be connected at one end to the Y tube 5 and at the other end to the air purifier 1 to carry exhaled air.

[0017] FIG. 2 is a cross-sectional view showing the function of the pharmaceutical aerosol delivery device 200 shown in FIG.

[0018] In the drug aerosol supplying device 200, the drug microparticle generating unit 30 is disposed at the inlet of the Y tube 5. The drug microparticle generating unit 30 changes the drug into microparticles by ultrasonic vibration. This makes it possible to shorten the distance from the location where the aerosol drug is generated to the mask (or mouthpiece) as much as possible. In other words, the path along which the microparticle drug travels is extremely short. Therefore, even if a small amount of drug is changed into microparticles, a good drug effect can be expected.

[0019] The drug aerosol supplying device 200 does not introduce additional outside air. This allows the oxygen concentration, oxygen pressure, and oxygen rate of the first air processed by the air purifier 1 and the second air processed by the humidifier 3 to be maintained, allowing the patient to breathe naturally. In addition, the drug aerosol supplying device 200 operates the drug fine particle generating unit 30 in response to a detection signal generated from the inhalation breath detector 10 so that the drug can be sprayed accurately when the drug is consumed. As a result, the drug aerosol supplying device 200 can significantly reduce the waste of the drug.

[0020] In addition, the detection signal for operating the drug fine particle generating unit 30 in the drug aerosol supplying device 200 may be diversified as follows, in addition to detecting the first air discharged from the air purifier 1. 1) The detection signal may be generated by a chest sensor that is placed on the patient's chest and detects when the patient's chest expands. When the patient breathes, the chest repeatedly goes up and down. Such a movement can be detected and used as the detection signal. 2) The detection signal may be a specific brain wave signal generated when the patient breathes. When the lung organs operate, specific brain waves are generated in the brain, and these brain waves can be detected and used as the detection signal. 3) The detection signal may be generated by placing a sensor on a mask or mouthpiece to detect the air flow during inhalation. There is a difference in the direction of the air flow between inhalation and exhalation, and the difference may be detected and used as the detection signal. 4) The detection signal may be generated by placing a sensor on a mask or mouthpiece to detect the air pressure during inhalation. There is a difference between the pressure during inhalation and the pressure during exhalation. Such a difference may be detected and used as the detection signal. 5) The detection signal may be generated by placing a sensor on a mask or mouthpiece to detect the air temperature during inhalation. There is a difference between the temperature during inhalation and the temperature during exhalation. Such a difference may be detected and used as the detection signal. That is, the pharmaceutical aerosol supplying device 200 according to another embodiment of the present invention may replace the detection signal generated by the inhalation breath detector 10 with at least one of the various examples described above. Also, by applying all of the various examples described above, the pharmaceutical fine particle generating unit 30 can be operated when any of the detection signals is generated.

[0021] As shown in FIG. 2, the drug microparticle generating unit 30 may include an intubation tube 32, a microparticle generating element 34, a drug container 36, a cover 40, and a packing closure 50. The intubation tube 32 is assembled to the branch tube 24. The microparticle generating element 34 may be disposed on the upper part of the intubation tube 32. The microparticle generating element 34 can change the drug into microparticles using, for example, ultrasonic vibration. This technology is well known, so further detailed description is omitted. The drug container 36 is disposed above the microparticle generating element 34 and contains the drug. The cover 40 is disposed on the drug container 36, thereby preventing the drug contained in the drug container 36 from being exposed to the outside.

[0022] The packing closure part 50 may be installed in the cover 40. The packing closure part 50 includes an upper case 51a, a lower case 51b, a packing 52, and a discharge part 53. The inner diameter of the upper case 51a is smaller than the inner diameter of the lower case 51b. The upper case 51a has an opening 54 formed in the upper part, and a syringe or the like can be inserted into the opening 54. The lower part of the upper case 51a is connected to the upper part of the lower case 51b. The lower part of the lower case 51b is connected to the discharge part 53. The packing 52 is made of an elastic material such as soft rubber, and is disposed inside both the upper case 51a and the lower case 51b. The packing 52 has an incision 55 in the upper part or side and a passage 56 formed therein. The passage 56 connects the incision 55 and the discharge part 53. The packing 52 has an outer shape that seals the inner wall of the upper case 51a, and has a small gap 57 between it and the inner wall of the lower case 51b. The lower case 51b has a threshold 58 at its bottom, and the threshold 58 supports the bottom of the packing 52.

[0023] The packing 52 normally seals the packing closure part 50 (particularly the inner wall of the upper case 51a). However, for example, when a needleless syringe (not shown) is inserted through the opening 54, the threshold 58 supports the packing 52 to move backward, and the gap 57 allows the packing 52 to be deformed, so that the upper part of the packing 52 is pushed back and the incision 55 is opened. In this state, when the syringe injects a drug, the drug is filled into the drug container 36 through the incision 55, the passage 56, and the discharge part 53. When the syringe is separated from the packing closure part 50, the packing closure part 50 is immediately sealed due to the elasticity of the packing 52. This can fundamentally prevent the inside of the drug container 36 from being exposed to the outside, so that contamination of the drug container 36 can be prevented. Therefore, the patient can be treated in a strictly clean environment. Furthermore, by preventing the inside of the drug container 36 from being exposed, it is possible to strictly prevent the inside of the entire section of the respiratory system, in particular the entire section of the tube connected from the air purifier 1 to the mask (or mouthpiece), from being exposed to the outside.

[0024] 3 is a diagram showing the configuration of a drug aerosol supplying device 200 to which an embodiment of the present invention is applied. As shown in the figure, the drug aerosol supplying device 200 includes a T-tube 20, a drug fine particle generating section 30, and a heater 102.

[0025] The T-tube 20 includes a straight tube 22 and a branch tube 24. Air supplied from the humidifier 3 is supplied to a first end 22a of the straight tube 22 through a tube 4, and a second end 22b is connected to a mask or a mouthpiece through a Y-tube 5. The branch tube 24 is attached to the straight tube 22 and communicates with the straight tube 22. The drug microparticle generating unit 30 is installed in the branch tube 24 and sprays the drug in the form of microparticles. The heater 102 heats the T-tube 20.

[0026] The heater 102 is attached to the outer surface of the T tube 20 by a method such as adhesion, and heats the T tube 20 so that the temperature of the inner surface of the T tube 20 becomes similar to the temperature of the second air discharged from the humidifier 3. When the second air passes through the T tube 20 heated by the heater 102, the moisture evaporated in the second air does not condense. Therefore, secondary respiratory infection due to condensed water can be prevented.

[0027] FIG. 4a shows the configuration of the T-tube 20 before assembly, FIG. 4b shows the configuration of the heater 102, and FIG. 4c shows the configuration of the socket portion.

[0028] It is preferable to see inside the T-tube 20 to check whether spray and condensation are generated from the drug microparticle generating section 30. For this purpose, the T-tube 20 and the film 402 are made of a transparent or translucent material.

[0029] The heater 102 includes a film 402 including a heating wire 404, and is attached to the outer surface of the T-tube 20. The heater 102 includes a first local heater 406 for heating the straight tube 22 and a second local heater 408 for heating the branch tube 24. The heater 102 includes a temperature sensor 410 for measuring the temperature of the T-tube 20. The temperature sensor 410 is for monitoring and controlling the temperature of the T-tube 20, and is disposed approximately in the center of the heater 102.

[0030] The heater 102 has a heating wire terminal 412 for connecting the heating wire 404 to an external power source and a sensor terminal 414 for connecting the temperature sensor 410 to an external control device. The heating wire terminal 412 and the sensor terminal 414 are attached to the second end 22b. The heater 102 also has a hook hole 416 and a boss hole 418 for connecting the T-tube 20 and the socket portion 104.

[0031] The socket portion 104 includes a heating wire connection terminal 420 electrically connected to the heating wire terminal 412, and a sensor connection terminal 422 electrically connected to the sensor terminal 414. The socket portion 104 has a sensor escape groove 424, a hook connection groove 426, and a boss connection groove 428 formed on its upper surface which is attached to the T-tube 20. The socket portion 104 also has a locking jaw portion 430 on its front portion.

[0032] Figures 5a to 5c show the assembly of the T tube 20, heater 102, and socket portion 104 shown in Figure 3. First, as shown in Figure 5a, the heater 102 is attached to the lower surface of the straight tube 22 of the T tube 20, and as shown in Figure 5b, the heater 102 is attached to the branch tube 24. Next, as shown in Figure 5c, the socket portion 104 is assembled to the straight tube 22 of the T tube 20.

[0033] Fig. 6a shows a configuration for assembling the socket part 104 to the T-tube 20 to which the heater 102 shown in Fig. 3 is attached, and Fig. 6b shows the completed state of assembling. Fig. 7 is a diagram for explaining the state in which a power cable is connected to the medicine aerosol supplying device 200 shown in Fig. 3.

[0034] Because the power cable 108 and the heater 102 cannot be directly connected, they are electrically connected via the socket portion 104. The power cable 108 may include an anti-reverse assembly structure to prevent reverse assembly when connected to the cable socket 612.

[0035] The heater 102 is attached to the outer surface of the T-tube 20, and the temperature sensor 410 provided on the heater 102 is located within the sensor recess 424. As a result, the temperature sensor 410 is sealed by the T-tube 20 and the socket portion 104, and is therefore protected from external impacts.

[0036] The socket portion 104 includes a power connection terminal 610 that is electrically connected to an external power source. The power connection terminal 610 is exposed to a cable socket 612. When a patient wears the mask or mouthpiece, the power cable 108 should not be directed toward the patient. Therefore, the cable socket 612 is disposed on the opposite side of the T tube 20 from the Y tube 5. As a result, when the socket portion 104 is assembled to the T tube 20, the power connection terminal 610 is disposed opposite the first end 22a of the straight tube 22.

[0037] To facilitate fastening of the power cable 108, the socket portion 104 is configured so that the power connection terminal 610 is angled downwardly, for example, at approximately 12.5 degrees relative to the straight tube 22.

[0038] The power connection terminal 610 and the heating wire connection terminal 420 may be ends of a pogo pin 614. The pogo pin 614 has an internal spring and supports the heating wire connection terminal 420. Therefore, in the process of fastening the socket part 104 to the T-tube 20, the fastening can be smoothly performed, and after fastening, the electrical connection between the heating wire connection terminal 420 and the heating wire terminal 412 can be firmly maintained.

[0039] The T-tube 20 has a socket locking protrusion 602, a hook 604, and a boss fitting portion 606 on the lower surface to which the socket portion 104 is fastened. The socket locking protrusion 602 is formed on the second end 22b of the straight tube 22 and fastened to the locking jaw portion 430 of the socket portion 104. The socket locking protrusion 602 and the locking jaw portion 430 can connect the heating wire connection terminal 420 of the pogo pin 614 to the heating wire terminal 412 and the sensor connection terminal 422 to the sensor terminal 414. The hook 604 is fastened to the hook connection groove 426 through the hook hole 416. The hook 604 is fastened to the hook connection groove 426 to prevent the socket portion 104 from being separated from the T-tube 20 and to prevent the socket portion 104 from being pushed in the opposite direction by the elasticity of the pogo pin 614 and moving. Furthermore, the boss fitting portion 606 is fastened to the boss connection groove 428 via the boss hole 418. The boss fitting portion 606, together with the hook 604, prevents the socket portion 104 from being pushed in the opposite direction by the elasticity of the pogo pin 614 and moving.

[0040] In this embodiment, the heater 102 has a film including a heating wire 404, and is attached to the T-tube 20 by an attachment method. In addition, since no screws are used when assembling the socket portion 104 to the T-tube 20, the assembly procedure can be minimized.

[0041] Although the preferred embodiments of the present invention have been described in detail above, the scope of the present invention is not limited thereto, and various modifications and improvements made by those skilled in the art using the basic concept of the present invention defined in the appended claims are also included in the scope of the present invention.

Claims

1. 1. A pharmaceutical aerosol delivery device for a respiratory tract, said device comprising: a T-tube including a straight tube having a first end to which air supplied from a respirator is supplied and a second end to be connected to a mask or mouthpiece, and a branch tube attached to the straight tube so as to be in communication with the straight tube; A drug fine particle generating unit that is installed in the branch tube and sprays the drug in fine particles; a heater for heating the T-tube; A pharmaceutical aerosol delivery device comprising:

2. 2. The pharmaceutical aerosol delivery device of claim 1, wherein the heater comprises a film containing a heating wire and is attached to the T-tube.

3. 3. The pharmaceutical aerosol delivery device of claim 2, wherein the heater comprises a temperature sensor that measures the temperature of the T-tube.

4. 4. The pharmaceutical aerosol delivery device of claim 3, wherein the heater comprises a first local heater for heating the straight tube and a second local heater for heating the branched tube, the first local heater and the second local heater being integrally formed.

5. 5. The pharmaceutical aerosol delivery device of claim 4, wherein the heater further comprises a heating wire terminal disposed at the second end for connecting the heating wire to an external power source.

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