KR101466616B1 - Dry Powder Inhaler Device - Google Patents

Abstract

/L/min 내지 0.030

/L/min이 되도록 형성되는 공기 유입부;를 포함하는 것을 특징으로 한다.There is little change in the value of the dynamic particle size distribution due to the change of the flow rate of the pharmacologically active ingredient, and the drug delivery to the deep lung is good, thereby providing a dry powder inhaler excellent in targeting.
The dry powder inhaler of the present invention comprises: a main body in which a capsule accommodating portion in which a capsule-like composition is mounted is formed; And a suction port communicating with the main body and adapted to discharge the composition of the capsule by suctioning by the patient, the main body being formed so that external air can flow in, a flow velocity resistance value of 0.02

/ L / min to 0.030

/ L / min. ≪ / RTI >

Description

[0001] Dry powder inhaler device [0002]

The present invention relates to a dry powder inhaler for delivering particles of a dry powder inhaler to the lungs.

For the treatment of respiratory diseases, such as asthma and chronic obstructive pulmonary disease (COPD), various drugs have been used in the form of inhalants. While inhalants have the advantage of achieving the desired therapeutic effect with a small amount of the pharmacologically active ingredient, only a part of the pharmacologically active ingredient to be administered reaches the target site and the pharmacologically active ingredient reaches the other organs that do not require treatment Which causes side effects.

Therefore, research is continuing to maximize the drug efficacy by allowing the pharmacologically active ingredient to be reproducibly targeted to the target site, and to prevent the pharmacologically active ingredient from reaching organs not requiring treatment.

For effective administration of such an inhalant, an inhaler for inhalation of the drug with air and administration to the airways is widely used for the treatment of respiratory diseases. Since the introduction of the Metered Dose Inhaler (MDI) for the first time in 1956, it has been widely used to dominate 80% of the inhaler market, but due to environmental problems such as ozone depletion and global warming In recent years, research into the dry powder inhaler (DPI) has begun in earnest. Currently, DPI formulations are at the stage of complementing the shortcomings of MDI formulations. MDI has the disadvantage that since the solvent and the pharmacologically active ingredient which can be used as the propellant are compressed, the stability is lowered and the pharmacologically active ingredient is delivered to the throat very quickly because of the high rate of spraying, DPI is easy to use, (See Martin J Telko and Anthony J Hickey, Dry Powder Inhaler Formulation, Respiratory Care, September 2005, Vol. 50, No. 9).

However, in the case of DPI, it was observed during the invention that the effective amount and the effective amount pattern vary depending on the suction device used for inhalation. This is because the flow rate in the inhalation device is different due to the different breathing rate for each patient using the DPI, and since the model of the inhalation device commercialized by each maker is different, the pressure drop in the inhalation device and the shape of the gas flow are different This is because it shows the aspect. Therefore, it is not only convenient to use in accordance with the change in the volume of air, but also develops a suction device that can transfer to the lungs well and does not change the effective amount.

 Dry Powder Inhaler Formulation, Respiratory Care, (2005), Vol. 9 (Patent Document 1) US 2003-0000523 (Patent Document 2) EP1270034

Accordingly, an object of the present invention is to provide a dry powder inhaler which is not only easy to use but also has a small change in dynamic particle distribution according to a change in flow rate, and is well-conveyed to a deep place in the lungs and excellent in targeting.

/L/min 내지 0.03

/L/min이 되도록 형성되는 공기 유입부;를 포함하는 것을 특징으로 하는 건조분말 흡입장치를 제공할 수 있다.According to the above object, a dry powder inhaler of the present invention comprises: a main body in which a capsule accommodating portion in which a capsule-like composition is mounted is formed; And a suction portion communicated with the main body and configured to discharge the composition of the capsule as the user sucks the main body. The main body is formed to allow external air to flow therein, and has a flow velocity resistance of 0.02

/ L / min to 0.03

/ L / min. ≪ / RTI > According to another aspect of the present invention, there is provided a dry powder inhaler comprising:

In addition, the air inlet may be formed so that the capsule containing portion of the main body is communicated with the outside.

The present invention also provides a dry powder inhaler comprising a push button assembly protruding from the main body and movable in an inner or outer direction of the main body.

The push button assembly may further include: a needle for forming a hole in the capsule; A pushbutton provided with the needle and moving to the inside or outside of the main body; And an elastic member elastically supporting the push button between the main body and the push button.

In addition, it is possible to provide a dry powder inhaler, wherein a grid is provided between the main body and the suction portion.

In addition, the suction unit may include a suction duct formed to communicate with the capsule containing unit;

And a flange extending from the suction duct to be coupled to the main body.

The dry powder inhaler according to the present invention is not only easy to use but also has a merit that the pharmacologically active ingredient hardly changes in the value of the dynamic particle size distribution due to the change of the flow rate, .

1 is an exploded perspective view of a dry powder inhaler according to an embodiment of the present invention,
FIG. 2 is an exploded perspective view of the main body and the suction unit of the dry powder inhaler according to the embodiment of the present invention,
3 is a perspective view of a dry powder inhaler according to an embodiment of the present invention,
4 is a sectional view of a dry powder inhaler according to an embodiment of the present invention,
5 is a top view of a dry powder inhaler according to an embodiment of the present invention,
6 is a bottom view of the dry powder inhaler according to the embodiment of the present invention,
7 is a sectional view showing the operation of the dry powder inhaler according to the embodiment of the present invention,
8 is a comparative view showing the air inlet width of the dry powder inhaler according to the embodiment of the present invention,
9 is a graph showing the results of the Salmeterol dynamic particle distribution test of Test Example 1,
10 is a graph showing the result of the Fluticasone dynamic particle distribution test of Test Example 1,
11 is a graph showing the results of the Salmeterol dynamic particle distribution test of Test Example 2,
12 is a graph showing the results of Fluticasone dynamic particle distribution test of Test Example 2. Fig.

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings.

In the following description of the present invention, detailed description of known functions and configurations incorporated herein will be omitted when it may make the subject matter of the present invention rather unclear.

In order for the pharmacologically active ingredients to be effectively transferred to the lungs to exhibit pharmacological activity, the particles of each active ingredient must be micronized. In general, the optimum particle size for inhalation into the bronchial system is more than 0.1 μm to 10 μm, preferably more than 0.1 μm to 5 μm. If the particle size is too small, less than 0.1 μm, it may not be deposited on the bronchus when inhaled, but rather may be drained back out of the body. According to USP 34, Aerosol, Nasal spray, Metered-dose inhaler, and Dry powder inhaler, a variety of apparatuses (Apparatus 1 to 6) were used for MDI and DPI formulations, As shown in Fig. For example, using Apparatus 3 (Anderson Cascade Impactor) of USP 34 < 601 >, it can be judged that the main component gathered on Stages 1 to 5 has a dynamic particle size distribution of approximately 0.1 to 5 [mu] When quantifying the amount, an effective amount of pharmacological activity can be inferred into the lungs when the inhalant is used. Generally, the particle distribution ratio corresponding to this region is preferably 10% to 30% of the active ingredient content to be inhaled.

In addition, in the inhalation formulation, selection of the inhalation device is important not only for determining the delivery efficiency of the pharmacologically active ingredient but also for ensuring patient safety and convenience of medication. Many types of inhalation devices for inhalation of dry powder are already on the market, but it is necessary to develop satisfactory products in terms of delivery efficiency and ease of use of pharmacologically active substances.

FIG. 1 is an exploded perspective view of a dry powder inhaler according to an embodiment of the present invention, FIG. 2 is an exploded perspective view of a body and a nose piece of a dry powder inhaler according to an embodiment of the present invention, FIG. 4 is a cross-sectional view of a dry powder inhaler according to an embodiment of the present invention, FIG. 5 is a top view of a dry powder inhaler according to an embodiment of the present invention, and FIG. 6 Is a bottom view of a dry powder inhaler according to an embodiment of the present invention.

1 to 6, a dry powder inhaler 1 according to an embodiment of the present invention includes a capsule body 10 having a capsule receiving portion 11 formed therein to receive a capsule 60 having a composition therein A suction unit 20 coupled to the main body 10 and a push button assembly 30 mounted on the main body 10 and movably coupled to the inside and outside of the main body 10.

The capsule 60 is converted into a through type so that the contents of the medicine contained therein can be easily used, which is generally known technology.

The main body 10 is formed to have an outer shape, and a capsule receiving portion 11 having an upwardly open shape is formed to accommodate the capsule 60 therein.

A mounting hole 15 is formed in the side surface of the main body 10 to provide a push button assembly 30 movably coupled to the inside and outside of the main body 10.

The mounting holes 15 may be formed to be opposed to each other on one side and the other side of the main body 10.

The suction portion 20 includes a suction duct 22 formed to communicate with the capsule accommodation portion 11 of the main body 10 and a flange 21 extending from the suction duct 22.

 The suction portion 20 is provided on the upper portion of the main body 10 and includes a peg 24 protruding from a lower portion of a flange 21 provided to be engaged with the main body 10, The protruding cross-tooth 23 is formed.

The main body 10 is formed with a fastening hole 12 having a shape corresponding to that of the peg 24 and the cross tooth 23 of the suction portion 20. [

Although not shown in the fastening hole 12, a longitudinal slot having a shape corresponding to the crossover 23 can be formed so as to be coupled with the crossover 23.

Therefore, when the peg 24 coupled to the fastening hole 12 reaches the bottom of the fastening hole 12, the peg 24 is rotated in the fastening hole 12 to move the suction part 20 relative to the body 10, So that it can be fastened.

As shown in Figs. 2 to 3, the main body 10 and the suction unit 20 are coupled to each other by a ridge 14 protruding into the latching recess 13 formed in the main body 10, And can be locked in a closed state by a hook formed on the flange 21 of the part 20.

At this time, the locking structure of the main body 10 and the suction unit 20 is the ridge 14 and the hook in this embodiment, but the spirit of the present invention is not limited to this. For example, a spring-type locking means.

The push button assembly 30 installed in the installation hole 15 of the main body 10 is provided with a needle 33 for forming a hole in the capsule 60 and a needle 33, And an elastic member 32 for elastically supporting the body 10 between the push button 31 and the push button 31. [

Although the elastic member 32 is a coil spring in the embodiment of the present invention, the spirit of the present invention is not limited to this.

The needle 33, the push button 31, and the elastic member 32 are disposed on the same axis line so as to be horizontally movable. The needle 33 is installed to be fixed to the inside of the push button 31.

A guide 16 having a guide hole 16a formed therein for guiding the movement of the needle 33 is formed in the mounting hole 15 of the main body 10. [

The needle 33 can be stably moved along the guide hole 16a of the guide 16 of the main body 10 when the push button 31 is moved.

Needle 33 is similar to subcutaneous needle, and a beveled tip may be formed to facilitate penetration of the coating and the composition of capsule 60.

Since the hypodermic needle has a small resistance to penetration and allows very accurate operation, it is possible to use a needle having a relatively large diameter without damaging the capsule 60, thereby providing a very simple penetration. With a small number of needles, for example two needles, the cross-sectional area can be the same and the contact surface between the needle and the capsule can be reduced, thereby reducing friction and problems affecting the previous inhaler.

The push button assemblies 30 are disposed to face the opposite sides of the main body 10 and may be formed as a pair.

In addition, the main body 10 is formed with an air inflow portion 40 for allowing external air to flow into the main body 10.

The air inlet portion 40 is formed to communicate with the outside of the capsule receiving portion 11 of the main body 10.

Therefore, when suction is performed by the suction unit 20, external air flows from the air inflow unit 40 to generate an air flow, and air flows into the capsule accommodation unit 11, So that the patient is able to suck the product through the suction duct 22 of the suction unit 20.

At this time, the suction unit 20 is provided with a grid 50 for filtering foreign substances.

The grid 50 is disposed between the main body 10 and the suction unit 20 and can be disposed at the end of the suction duct 22. [

7 is a sectional view showing the operation of the dry powder inhaler according to the embodiment of the present invention.

As shown in FIG. 7, the operation of the above-configured dry powder inhaler will be described.

The capsule 60 is inserted into the capsule accommodation portion 11 of the main body 10 while the suction portion 20 is opened from the main body 10 and the suction portion 20 is rotated to be coupled to the main body 10 do.

When the push button 31 of the main body 10 is pushed, the push button 31 moves in the direction of the center of the inside of the main body 10 (the direction of the arrow in Fig. 7), the needle 33 fixed to the push button 31, Passes through the capsule 60 so that the composition inside the capsule 60, that is, the dry powder of the present invention, is accommodated in the capsule accommodation portion 11.

When the patient is sucked through the suction unit 20, external air is introduced into the main body 10 through the air inlet 40 of the main body 10.

The incoming air generates an air flow inside the main body 10 which mixes the composition of the capsule accommodating portion 11 (dry powder) and sucked into the patient through the grid 50 and the suction duct 22 .

Thus, the propellant that sucks the pharmacologically active ingredient from the capsule 60 in the air in the dry powder inhaler 1 is the suction force of the patient. All dry powder inhalers have a pressure drop value due to the movement of air when the patient is inhaled. The value of the pressure drop due to the flow of air is a function of the dynamic particle size distribution and unit dose amount uniformity It can serve as an important parameter in the test. Actually, the flow resistance value (AR, airflow resistance, KPa / Lmin) varies depending on the apparatus. Therefore, in the US, the suction flow rate can be adjusted from 0 L to 100 L per minute and the pressure drop value is maintained at 4 kPa (Q _out ) and T (sec) = 240 / Q _out The value of T obtained from the equation is used as the inhalation time to evaluate the product test for the inhalation formulation.

Therefore, in order to exhibit a similar pharmacological activity effect for each patient, it is preferable that the change of the dynamic particle size distribution value according to the change of the flow velocity is small.

/L/min 내지 0.030

/L/min인 유속저항값을 가짐으로써 약리활성성분이 유속의 변화에 의한 동적입자크기분포값에 변화가 거의 없을 뿐 아니라, 폐 깊숙한 곳으로의 전달율이 다른 건조분말 흡입장치에 비해 우수한 효과가 있다.The dry powder inhaler 1 according to the embodiment of the present invention has 0.02

/ L / min to 0.030

/ L / min, the pharmacologically active ingredient hardly changes the dynamic particle size distribution value due to the change of the flow rate, and the delivery rate to the deep lung is superior to that of other dry powder inhalers have.

In the dry powder inhaler 1, the flow resistance value is proportional to the square root of the pressure drop (P, kPa) and inversely proportional to the flow rate (Φ, L / min) (JP de Koning et al, airflow on the inspiratory flow curve, International Journal of Pharmaceutics 234 (2002) 257-266).

Therefore, it is possible to measure the inherent flow resistance value of the suction device by measuring the pressure drop value according to the change in flow rate of each suction device by using the Delivered-Dose Uniformity (DUSA) method per unit dose of the US Pharmacopoeia.

/L/min 내지 0.030

/L/min인 건조분말 흡입장치(1)를 사용하면, USP 34 <601>의 Apparatus 3(Anderson Cascade Impactor)의 Stage 3 내지 7영역에 약리학적활성성분의 전달이 잘 이루어져 폐의 깊은 곳인 기관지 및 폐포로의 약리학적활성물질의 전달이 우수한 것을 확인할 수 있다.When the flow velocity resistance value according to the embodiment of the present invention is 0.02

/ L / min to 0.030

/ L / min, the pharmacologically active ingredient was delivered to Stage 3 to 7 of Apparatus 3 (USP 34 < 601 &gt;) (Anderson Cascade Impactor) And the delivery of pharmacologically active substance to alveoli is excellent.

/L/min 내지 0.030

/L/min 영역에 해당할 경우, 건조분말 흡입장치(1)는 적절한 공기저항을 가지게 되어 건조분말 흡입장치(1)를 사용하는 환자가 깊은 흡입을 통한 폐의 완벽한 팽창을 통해 약리활성물질이 입이나 기관지상부영역에 침착하지 않고 폐 깊숙한 곳으로 전달될 수 있다.Therefore, when the flow velocity resistance value of the dry powder inhaler 1 is 0.02

/ L / min to 0.030

/ L / min, the dry powder inhaler 1 has an appropriate air resistance, so that the patient using the dry powder inhaler 1 is able to fully inflate the lungs through deep inhalation, It can be delivered deep into the lungs without sedimentation in the mouth or bronchial area.

The width w of the air inlet 40 of the main body 10 can be adjusted to change the flow resistance value of the dry powder inhaler 1 as in the embodiment of the present invention.

/L/min 내지 0.030

/L/min에 들어오게 되며, 이때의 동적입자크기분포값은 폐로의 전달효율이 최대화 될 수 있다.When the width (w) of the air inflow portion 40 of the main body 10 is adjusted to 1.5 mm to 3.5 mm, preferably 1.5 mm to 3 mm, the flow velocity resistance value is 0.02

/ L / min to 0.030

/ L / min, and the dynamic particle size distribution value at this time can maximize the transfer efficiency of the closed loop.

Therefore, when the dry powder inhaler 1 according to the embodiment of the present invention is used, the pharmacologically active ingredient in the inhalation formulation can sufficiently reach the bronchial or alveoli capable of exhibiting activity, and the dynamic particle size distribution The patient will be able to use the inhalation formulation safely.

Hereinafter, the effects of the dry powder inhaler 1 of the embodiment of the present invention will be described in detail with reference to test examples.

Test Example  1: Measurement of flow resistance value ( Airflow resistance )

8, the width w of the air inlet 40 'of the RS01 Model 7 Inhaler (hereafter, the suction device D) is set to w1 = 1.3 mm, w2 = 1.8 mm, w3 = 2.6 mm, w4 = 4.0 mm, and the flow velocity resistance values were measured. The pressure drop value (P) of the suction device (D) was measured at four flow rates of 28.3 L / min, 60 L / min, 75 L / min and 90 L / min using Apparatus 1 of USP 34 <601> , kPa) were measured.

Then, the measured pressure drop value was measured according to the inlet width according to the following calculation method (J. Aerosol Med. 6 (1993) 99-100).

Flow rate (L / min) 28.3 L 28.3L 60L 75L 90L Average Air inlet width (mm) 1.3 mm
Pressure drop value
(kPa) 1.15 5.22 6.89 9.45 -

/L/minFlow resistance value
(

/ L / min 0.036 0.038 0.035 0.034 0.036 1.8mm Pressure drop value
(kPa) 0.78 3.93 4.84 6.61 - Flow resistance value
(

/ L / min 0.031 0.033 0.029 0.029 0.031 2.6mm Pressure drop value
(kPa) 0.41 2.07 3.00 4.14 - Flow resistance value
(

/ L / min 0.023 0.024 0.023 0.023 0.023 4.0mm Pressure drop value
(kPa) 0.28 1.6 1.94 2.62 - Flow resistance value
(

/ L / min 0.019 0.021 0.019 0.018 0.019

Table 1 shows the flow resistance values according to the width of the air inlet. As shown in Table 1, when the width (w1 to w4) of the air inlet is varied even if the same suction device (D) And the like.

Test Example  2 : Dynamic particle size distribution  ( Aerodynamic Size Distribution ) Measurement I

2 mg of lactose was added to the mixer and the mixture was applied. Then, according to the ratio of the composition shown in Table 2 below, salmeterol, phosphate, fluticasone propionate and 2 mg of lactose were added to the mixer, , And the remaining lactose was added to the mixer with a ball and mixed for 20 minutes. The mixture was stabilized for at least 12 hours and then filled into clear 3 capsules using a capsule filling machine.

ingredient (mg) Salmeterolinophosphate   0.0725 (0.05 as Salmeterol) Fluticasone propionate   0.2500 Lactose  20.0000 Sum  20.3225

The composition of Table 2 was applied to a USP 34 &lt; 601 &gt; Apparatus 3 (Anderson (R)) using an air inlet 40 ' Cascade Impactor) was used to test the particle size distribution under the conditions of flow rates of 28.3 L / min, 60 L / min and 75 L / min, respectively, and the phage active ingredients The contents were measured under the following analysis conditions.

The test results are shown in FIGS. 9 and 10. FIG.

- Analysis conditions of Salmeterol and Fluticasone -

Column: A column packed with octadecylsilylated silica gel for liquid chromatography with a particle diameter of 5 占 퐉 in a stainless steel tube having an inner diameter of about 4.6 mm and a length of 15 cm

A solution prepared by adding 0.6% (w / v) ammonium acetate to a mixed solution of mobile phase: methanol: acetonitrile: water (50:16:34, v / v / v)

Detector: Ultraviolet absorptiometer (measuring wavelength 228 nm)

Temperature: 40 ° C

Flow rate: 1.0 mL / min

Injection volume: 100 μL

/L/min 내지 0.030

/L/min를 벗어나는 공기 유입구(40')의 너비가 1.3mm 및 4.0mm(w1,w4) 샘플의 경우 유속변화에 의한 유효량변화값의 변화가 컸으며, 유속저항값이 0.02

/L/min 내지 0.030

/L/min이내의 흡입장치(D)에 비해 유효량값이 작게 측정된 것을 확인할 수 있었다.9 and 10, when the width of the air inlet 40 'is 1.8 mm to 2.6 mm (w2, w3), the results of the contents in the range of Stages 1 to 5 corresponding to the effective amount in the entire flow rate range are all In the case of meteorol, it was measured to be about 10ug and for fluticasone was measured to be about 60ug.

/ L / min to 0.030

(W1, w4) of the air inlet 40 'exceeding the flow rate / L / min was large, and the flow rate resistance value was 0.02

/ L / min to 0.030

It was confirmed that the effective amount value was measured to be smaller than that of the inhalation device D within / L / min.

/L/min 내지 0.030

/L/min의 경우 흡입속도의 변화에 대한 동적입자분포의 변화가 적고, 폐로 흡입되는 약리학적활성물질의 유효량도 최대화되는 것을 확인할 수 있었다.
Therefore, when the flow velocity resistance value is 0.02

/ L / min to 0.030

/ L / min, the change of the dynamic particle distribution with respect to the change of the suction speed was small, and the effective amount of the pharmacologically active substance inhaled into the lung was also maximized.

Test Example  3: Dynamic particle size distribution  ( Aerodynamic Size Distribution ) Measure II

The composition of Table 2 of Test Example 2 was applied to a suction device D having an air inlet 40 'of 2.6 mm (w 2) using a USP 34 <601> Apparatus 3 (Anderson Cascade Impactor) / min, the content of pharmacologically active ingredients in the stages 0 to 7 was measured by the analysis conditions of Test Example 2 after the particle size distribution was tested.

The test results are shown in Figs. As a comparative sample, salmeterol and fluticasone, the commercially available inhalation formulation Seretide Discus 250 (GSK), were tested identically.

/L/min 내지 0.030

/L/min인 건조분말 흡입장치(1)를 사용할 경우 4 스테이지 이후의 영역에서 기시판품인 세레타이드에 비해 동적입자분포값이 커지는 것을 확인할 수 있었다. 11 and 12, the flow velocity resistance value of the embodiment of the present invention is 0.02

/ L / min to 0.030

/ L / min, the dynamic particle distribution value was larger in the region after the 4th stage than in the commercial product, seretide.

/L/min 내지 0.030

/L/min인 건조분말 흡입장치(1)를 사용할 경우 폐 깊은곳으로 약리학적활성 성분이 더 높은 비율로 들어가 활성을 나타낼 수 있는 효과를 가질 수 있다.Therefore, the flow velocity resistance value of the embodiment of the present invention is 0.02

/ L / min to 0.030

/ L / min, the pharmacologically active ingredient may enter into the lungs at a higher rate and have an effect of exhibiting activity.

/L/min 내지 0.030

/L/min인 건조분말 흡입장치(1)를 사용할 경우 목표 부위인 폐로 약리활성성분이 충분히 도달할 수 있으며, 유속변화에 의한 동적입자크기분포의 변화가 작아 환자가 안전하게 사용할 수 있을 것이다.When the flow velocity resistance value according to the present invention is 0.02

/ L / min to 0.030

/ L / min, the pharmacologically active ingredient in the lungs, which is the target site, can be sufficiently reached, and the change in the dynamic particle size distribution due to the change in the flow rate is small, so that the patient can safely use the dry powder inhaler.

1: Dry powder inhalation device 10:
11: Capsule accommodating portion 20: Suction portion
22: suction duct 30: push button assembly
31: push button 32: elastic member
33: Needle 40: Air inlet
50: grid 60: capsule

Claims (6)

A main body having a capsule receiving portion in which a capsule containing the composition is accommodated;
An air inlet formed at one side of the main body and allowing outside air to be introduced into the main body by a suction operation of the patient; And
A suction portion communicating with the main body and guiding the outside air introduced into the main body and the composition to the patient;
Lt; / RTI &gt;
Wherein the suction portion includes a peg protruding from the body side end portion of the suction portion and a cross tooth protruding laterally from the end portion of the peg,
Wherein the main body is formed with a fastening hole having a shape corresponding to the shape of the peg and the cross-tooth,
Wherein the suction portion is rotatable with respect to the main body in a state where the peg and the crosstalk are inserted into the fastening hole so that the capsule accommodating portion of the main body can be opened and closed,
The flow velocity resistance value inside the body is 0.02

/ L / min to 0.027

/ L / min. &Lt; / RTI &gt; The method according to claim 1,
Characterized in that the composition comprises salmeterol, a phosphate and fluticasone propionate for the treatment of respiratory diseases. 3. The method of claim 2,
Wherein the composition further comprises lactose,
Wherein the salmeterol phosphate, the phosphate salt and the fluticasone propionate are contained in the capsules in a weight of 0.0725 mg and 0.250 mg, respectively. delete The method according to claim 1,
When the suction portion closes the capsule accommodating portion,
Wherein the main body and the suction portion are locked with respect to each other by fastening a ridge protruding into the latching recess formed in the main body and a hook formed on the suction portion.

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