WO2006082941A1

WO2006082941A1 - Inhaler

Info

Publication number: WO2006082941A1
Application number: PCT/JP2006/301906
Authority: WO
Inventors: Toshiyuki Nobutani
Original assignee: Canon Kabushiki Kaisha
Priority date: 2005-02-01
Filing date: 2006-01-30
Publication date: 2006-08-10
Also published as: JP2006212088A

Abstract

There is provided an inhaler which includes a detection means for detecting or measuring inclination of a housing and when used for inhalation of a drug, reduces mental and physical labors of a patient and enables efficient inhalation of the drug by a simple operation of the patient. The inhaler is for a user to inhale a liquid formulation from an inbreathing port. The inhaler has a detection means for detecting or measuring the inclination of the housing with respect to the inclination reference. The inhaler may further include a noticing means connected to the detection means, for serving notice to the user in accordance with an information from the detection means, a control means for controlling ejection of the liquid formulation in accordance with an information from the detection means, the both means, or a storage means for storing an information from the detection means.

Description

DESCRIPTION INHALER

TECHNICAL FIELD The present invention relates to an inhaler, particularly to an inhaler . for ej ecting a liquid formulation of a drug, an aroma, a favorite food such as nicotine or the like as fine droplets to make a user inhale it .

BACKGROUND ART

In recent years, the average life expectancy has been increasing to thereby increase the elderly population because of the advances in medicine and science . However, new illness and infectious diseases due to change in dietary habits or living environments , environmental pollution, viruses or fungi have appeared, so that anxiety to the health of the people ' has been increasing. Particularly, in the so-called advanced nations , the increase of patients of life-style related diseases such as diabetes mellitus , hypertension or the like has become a problem.

For example, diabetes mellitus patients need to be administered with insulin, and the administration has generally been performed by inj ection before meals . However, administration using an injection syringe will cause considerable pain to a patient . To solve this problem, administration of a drug through respiratory system has been considered . This generally includes three methods , specifically one using a metered dose inhaler, one using a dry powder inhaler, and one using an atomizer .

The metered dose inhaler (MDI ) is widely used for treatment of asthma . The MDI has a valve for discharging a metered dose of aerosol upon operation and is convenient for its portability because of size reducibility of its body. However, the discharge amount will vary over a considerably wide range . Moreover, to use the MDI , some degree of synchronization between manual valve operation and inhalation is required, so that many users feel this synchronization difficult .

When using the dry powder inhaler (DPI ) , a large amount of air must be inhaled in order to provide a powder with flowability to thereby administer an effective amount of the powder to the inside of a bronchial system. This seems to obviate the problem of synchronization between manual valve operation and inhalation . However, inhaling a large amount of air forces a user to spend a considerable labor . Moreover, for a patient who is sensitive to humidity and also to inhaled powder, the DPI may cause a seizure of asthma . Therefore, the DPI cannot be used for such patient . Furthermore, because the inhalation force differs in individuals, the amount of administration will vary- depending on individuals . The atomizer atomizes a liquid of a carrier gas flow to generate aerosol and requires a continuously- operating gas compressor or a large amount of compressed gas . In general, the size of a fine droplet of aerosol is a function of carrier gas pressure and velocity, so that it is not easy to independently change the concentration of a drug in a gas flow . < Moreover, because inhalation decreases the pressure inside a nozzle of the atomizer, the atomized amount and particle size are influenced by the period and strength of breathing . As described above, the above-mentioned inhaling devices generally have a problem in the accuracy of administering a drug having a proper particle size to an applied portion in. a proper amount, so that their use is limited only to a drug having a wide allowance for dose . In any device, it is a current situation that administration to an intended proper portion depends on the technique of a user .

On the other hand, there is a need for an improved administration system for optimizing the . medical treatment of nose and lungs diseases by use of a locally-acting drug . Moreover, as a result of the advances in medicine, it is shown that administration of a drug such .as protein, peptide and analgesic to lungs is considerably advantageous compared to conventional means such as oral or injection administration . However, the hitherto proposed inhalers have a large fluctuation in particle size and administration amount and cannot be used for the above-mentioned cases .

Description will be made below with reference to a specific example . Of the diabetes mellitus patients who are increasing at present, the so-called •insulin-dependent type (type I ) diabetes mellitus patients have no secretion of insulin from their pancreas and need to be regularly admin-istered with insulin . Because insulin is administered by subcutaneous injection at present, the physical and mental labor of patients is large . In order to reduce the labor of such patients, a pen-shaped inj ection syringe has been developed which has a thin needle and gives less pain to a patient . However, because most of the I-type diabetes mellitus patients work as with an able-bodied person except for requiring regular administration of insulin and have mental resistance to inj ection in public even with a pen-shaped inj ection syringe, it is difficult to administer insulin at a proper time .

For such a case, in order to ease the administration by a patient himself, there is a continuing need for a simple method for ej ecting a drug as droplets, not by inj ection, and making the droplets securely reach lungs with indrawn breath to administer the drug via the lungs .

Therefore, there has recently be proposed a method in which an ejection energy is given to a liquid containing a drug by a heater element or piezoelectric element provided in an ejection head portion (ej ection portion) to ej ect a physiologically effective drug from an ej ection orifice to air flow inhaled through a mouthpiece or the like as a predetermined number of proper droplets (see International Publication Nos . WO1995/001137 and WO2002/004043) .

DISCLOSURE OF THE INVENTION

However, the above-mentioned conventional examples include methods of a system in which the particle diameter or ej ection amount of the ej ected liquid droplets, is changed depending on the orientation of an inhaler . The change in the particle diameter of a liquid droplet influences the probability of reaching lungs and the change in the ej ection amount influences administration of a proper amount, each of which may become a factor of failure to inhale a drug in a proper dose prescribed by a doctor .

In view of the above-mentioned problems , the present invention provides an inhaler for a user to inhale a liquid formulation from an inbreathing port, which comprises a detection means for detecting or measuring inclination of a housing with respect to an inclination reference .

In the present invention, it is preferable that the inhaler further comprises a noticing means (e . g . , ^■ vibration motor described later) connected to the detection means, for serving notice to the user in accordance with an information from the detection means .

Further, it is preferable that the inhaler further comprises a control means (e . g . , control circuit described later) for controlling ejection of the liquid formulation in accordance with an information from the detection means .

Moreover, it is preferable that the inhaler further comprises the both means .

Furthermore, it is preferable that the inhaler further comprises a storage means (e . g . , memory described later) for storing an information from the detection means . As the detection means , it is possible to use an acceleration sensor . To use the acceleration sensor as the means for detecting inclination is effective because the direction of gravity G in an environment in which the inhaler is used is a vertical direction .

The inhaler according to the present invention includes a detection means for detecting or measuring inclination of a housing with respect to an inclination reference . Thereby, when using the present inhaler as an inhaler of a drug, it is possible to reduce the mental and physical labors of a patient and enables efficient inhalation of the drug only by a simple operation by the patient . That is , the ejection driving parameters (voltage applied to ej ection head portion, pulse width, particle diameter, ejection amount, ej ection time, and the like ) are changed depending on how a patient holds the inhaler . Alternatively, a notice is given to the patient . Thus , there is attained the advantage that more drug is delivered to lungs to improve the inhalation efficiency, thereby efficiently administering the drug . Moreover, the result of inclination detection can be used for various purposes .

Other features and advantages of the present invention will be apparent from the following description taken in conj unction with the accompanying drawings , in which like reference characters designate the same or similar parts throughout the figures thereof .

BRIEF DESCRIPTION OF THE DRAWINGS

FIG . 1 is a schematic perspective view showing an example of the inhaler according to the present invention; •

FIG . 2 is a schematic perspective view showing the inhaler of FIG . 1 when an access cover is opened;

FIG . 3 is a schematic perspective view showing an example of a cartridge (CRG) unit;

FIG. 4 is a vertical sectional view of an example of a mouthpiece;

FIG. 5 is a horizontal sectional view of the mouthpiece shown in FIG . 4 ; FIG . 6 is a vertical sectional view showing the dispositional relationship between the mouthpiece shown in FIG.. 4 , a negative pressure sensor, and an ej ection head of a cartridge unit;

FIG . 7 is an entire sectional view of the inhaler shown in FIG. 1;

FIG. 8 is a graphical representation for explaining an example of the inhalation operation of the inhaler shown in FIG . 1 ;

FIG . 9 is a sectional view of a mouthpiece of a parallel-flow-path type and the vicinity thereof;

FIG . 10 is a block diagram of an example of the inhaler according to the present invention; FIG. 11 is a schematic view illustrating the vibration patterns of a vibration motor of an example of the inhaler according to the present invention; and FIG. 12 is a block diagram of a head driver of an example of the inhaler according to the present invention .

BEST MODE FOR CARRYING OUT THE INVENTION Preferred embodiments of the present invention will now be described in detail with reference to the accompanying drawings .

Specific examples are described below by referring to FIGS . 1 to 12 in order to clarify the embodiments of the present invention . [Examples] (Example 1)

FIG . 1 is a schematic perspective view showing the appearance of an example of the inhaler (hereinafter sometimes referred to as "the device") according to the present invention . In the figure, reference numeral 1 denotes an inhaler body; reference numeral 2 denotes an access cover; reference numeral 3 denotes a front cover; and a housing is formed by these components-. Reference numeral 5 denotes a lock lever which is formed such that a claw-shaped portion formed at the front edge of the lock lever 5 urged by a spring engages with a protrusion 2a formed at the front edge of the access cover 2 in order that the access cover 2 does not open when used. When sliding the lock lever 5 downwardly, the access cover 2 opens with a hinge axis (not shown) being used as a rotation center by the force of an access-cover-returning spring urging the access cover 2. Moreover, reference numeral 120 denotes a power supply switch and reference numeral¹ 104 denotes a display LED which displays that an ej ection head cartridge (CRG) unit or mouthpiece described later is not mounted or that no liquid formulation remains in the tank of the cartridge unit . The display LED 104 will be further described later , FIG. 2 illustrates a state when the access cover 2 opens . When the access cover 2 is opened, a cartridge unit 6 and a mouthpiece 4 mounted in the housing along a cartridge guide 20 can be seen . The mouthpiece 4 is present under the cartridge unit 6 and. these members are mounted so as to intersect with each other . FIG . 3 shows the entirety of the cartridge unit 6. The cartridge unit 6 has a tank 7 for containing a liquid formulation and a head portion (ejection portion) 8 for ej ecting the liquid formulation . Moreover, the cartridge unit further has a portion (electric connection portion) 9 having an electric connection face for supplying a power for providing a heat energy to generate bubbles by a heater provided in the head portion 8 from a battery 10 ( see FIG . 7 ) . Incidentally, the configuration of the head portion is not limited to the above, and there may be adopted a configuration in which a piezoelectric device is provided instead of the heater or a configuration for forming liquid droplets by applying a vibration energy to a mesh structure film having a number of holes provided therethrough . The battery 10 can be recharged as a secondary battery holding the power for applying the energy to the heater in the inhaler . The front face portion of the cartridge unit 6 is formed so as to be opened around a hinge portion 24 thereby making it possible to access the tank 7. On the rear surface of the front face portion a protrusion or the like is formed, so that when closing the front face portion, the protrusion simultaneously enters the tank 7 to slightly pressurize the liquid formulation in the tank 7 to refresh the ej ection port of the head portion 8.

FIGS . 4 and 5 show sectional views of the mouthpiece 4. The mouthpiece 4 forms an air flow path by only the mouthpiece 4 itself and a window (liquid formulation intake port) 12 for intaking a liquid formulation into the mouthpiece 4 from an ej ection port provided in the head portion 8 of the cartridge unit 6 is opened at a portion close to the air intake port 11. In the middle of the mouthpiece 4A a drawn portion 4a is formed which has a shape gradually changing in the direction in which the sectional area decreases . As shown in FIG : 6 in detail, at a portion where the sectional area reduced at the drawn portion is increased again, a hole 13 is provided which communicates with a measuring hole of a negative pressure sensor 19 for sensing a negative pressure to detect an inhalation speed or a flow rate as an integrated value of the speed. The negative pressure sensor 19 is disposed on a control board 21 (see FIGS . 6 and 7 ) . In the middle of a flow path communicating with the negative pressure sensor 19 from ^' the air hole 13, an expanded space 22 is provided. This is formed as a collection place for dust, dirt, water drops, liquid formulation, and . the like and prevents these from intruding from the air hole 13 and attaching to the surface of the negative pressure sensor 19 to cause a malfunction .

At an end opposite to the air intake port 11 of the mouthpiece 4 , there is formed a mouthpiece 4 exit (inbreathing port) 15 having such a shape that a person can put it in his mouth . The cross section of the mouthpiece exit 15 is formed in an elliptical shape according to the shape of the mouth of a person and a flow path exit 14 serving as a route of the liquid formulation is provided at an inner side of a duplex structure . The flow path exit 14 has a shape in which the sectional area gradually increases in order to prevent that a mixed fluid of air and the liquid formulation abruptly expands at the exit and attaches to teeth of the mouth of a person having the mouthpiece exit 15 in this mouth . Therefore, when a user has the mouthpiece exit 15 in his mouth, it is preferred that the end of the flow path exit 14 enters the mouth through the upper and lower teeth to some degree . To easily perform the entering, it is also preferred that the end of the flow path exit 14 is formed so ^' as to protrude slightly outside the end of the mouthpiece exit 15. Moreover, as shown in FIGS . 1 and 2 , the cross section of the air flow path of the mouthpiece 4 has a square shape so that when mounting the mouthpiece 4 in the housing, the mouthpiece 4 is surely mounted- in a state in which the air intake port 11 faces upwardly. FIG. 7 is an entire longitudinal sectional view of the inhaler of this example . The control board 21 for controlling the inhaler is disposed under a battery 10. Moreover, a probe board 16 connected to the control board 21 by a cable or connector ( connector 25 being used in FIG . 7 ) is disposed under the cartridge unit 6. Furthermore, a contact probe 17 for performing energization for heat generation to the head portion- 8 of the cartridge unit 6 is provided for connection from the probe board 16 to the electric connection portion 9 of the cartridge unit 6. A vibration motor 18 is disposed in a space between the battery 10 and the mouthpiece 4 so as to be in contact with the control board 21.

The inhalation operation of this example having the above configuration is described with reference to FIG . 8. FIG . 8 shows a relation between an inhaling curve in breathing and a period for ej ection . When inhalation by a user starts and a negative pressure (relating to inhaling speed and flow rate) detected by the negative pressure sensor 19 reaches a region in which ej ection can be performed, the liquid formulation starts to be ej ected from the head portion 8 of the cartridge unit 6 under the control of the control board 21. At the same time, the vibration of the vibration motor 18 also starts to serve notice to the user that liquid formulation ej ection has started. After liquid formulation ej ection of a scheduled amount from the head portion 8 is completed, in order that the last ejected liquid formulation reaches lungs, the vibration motor 18 vibrates for an additional inhaling time after the completed of ej ection so as to attain inhalation in an additional inhaling amount on the basis of the inhaling speed and inhalation duration computed from the negative pressure value measured -by the negative pressure sensor 19. Thereby, the user is urged to perform inhalation so that the ej ected liquid formulation completely reaches lungs . When the vibration of the vibration motor 18 is completed, the user or patient stops inhalation . Thereby, the liquid formulation ej ection and the inhalation are brought into association with each other, so that it becomes possible to securely deliver the liquid formulation to lungs and there is no fail such as insufficient inhalation .

Thus , air enters the mouthpiece 4 from the air intake port 11 by the inhalation operation of the user and forms a mixed fluid with the liquid formulation ej ected from the ej ection port provided in the head portion 8 of the cartridge unit 6 and the mixed fluid moves to the mouthpiece exit 15 having such a shape that a person can put it in his mouth . The mouthpiece exit 15 prevents the leakage of the mixed fluid from the lateral sides of the mouth to reduce the waste of inhalation and suppresses easy collision of the mixed fluid against an obstacle such as teeth in the mouth, whereby the liquid formulation is efficiently inhaled into the body of the user . In this example, by considering that a patient or user generally dislikes that his inhalation becomes known by those around him or bothers those around him and prefers vibration using a vibration ^• motor 18 rather than an auditory notice, the vibration motor 18 is used . Thereby, inhalation can be easily made at any place . (Example 2 )

FIG. 9 shows a modified example in which only the configuration of the flow path up to the pressure detection portion (hole 13 for communication with negative pressure sensor 19) is different from Example 1. In the this modified example, the communication hole 13 is provided at the outside of the flow path exit 14 of the mouthpiece exit 15 present at the front end of the mouthpiece 4 , whereby the negative pressure detection flow path leading to the negative pressure sensor 19- is completely separated from the ^' air flow path of the mouthpiece 4 and disposed parallel thereto . In a case where a mounting method is adopted in which the mouthpiece 4 is mounted by inserting from the upper/front side of the inhaler, the mounting direction is a direction in which the communication hole 13 comes into contact with the negative pressure detection flow path leading to the negative pressure sensor 19, which is advantageous to prevent air leakage . Therefore, negative pressure detection is securely performed . Moreover, because the negative pressure detection flow path leading to the negative pressure sensor 19 and the flow path for .the liquid formulation are completely separated from each other, the contamination of the negative pressure detection flow path with the liquid formulation or the like is reduced and accurate detection is secured .

FIG . 10 shows an entire block diagram of the control board 21 and the- vicinity thereof of the present device .

In FIG . 10 , reference numeral 101 denotes a CPU, which is an arithmetic processing unit and including therein a flash ROM that stores a program. Reference numeral 102 denotes an SRAM which is a readable/writable memory for temporarily storing data when the program operates . Reference numeral 104 denotes the aforementioned LED which is a display unit for showing the state of the device to a μser or maintenance worker . Reference numeral 105 denotes a radio unit for performing radiocommunication for transferring the state of the device or storage content to a host computer or receiving data from the host computer, and reference numeral 106 denotes an antenna for the radio unit . Reference numeral 107 denotes a cover sensor for detecting the opening/closing state of the access cover 2. Reference numeral 108 denotes an amplifier for level converting and amplifying an output of the negative pressure sensor 19 and reference numeral 109 denotes an AD converter for converting an analog output of the amplifier 108 to a digital signal . Reference numeral 110 denotes a driver for controlling the head portion 8. Reference numeral 111 denotes an RTC (real time clock) having a calendar/clock function and reference numeral 112 denotes a backup battery for the RTC 111. Reference numeral 113 denotes a power supply for generating various voltages to be supplied to electric circuits, which includes a main battery, a charging circuit, a reset circuit, the aforementioned power supply switch 120 , and the like .

Moreover, reference numeral 114 denotes a sensor for detecting the inclination of the device which is a characteristic of the. present invention; reference numeral 115 denotes a detection circuit for processing an output of the sensor 114 ; and reference numeral 116 denotes an AD converter for converting an analog signal which is an output of the detection circuit 115 to a digital signal . The sensor 114 is attached in a proper space in the inhaler body at a predetermined orientation . Moreover, reference numeral 117 denotes a control circuit for processing output/input signals to or from various blocks, which is connected to the CPU 101 through a bus . Further, a USB port connected to the CPU 101 is also provided as an external interface .

As the sensor 114 for detecting inclination, it is possible to use one of various types of inclination sensors and acceleration sensors and a suitable one may be chosen depending on the specification of the inhaler . Examples of the acceleration sensor include an electrostatic-capacity-type acceleration sensor and a piezoelectric-type 3-axis acceleration sensor . The electrostatic-capacity-type acceleration sensor has a configuration in which there are provided a plurality pairs of electrostatic capacity elements each prepared by attaching electrodes to opposing surfaces of a fixed substrate made of glass or the like and a flexible substrate made of silicon or the like and disposing them in opposition to each other and a change in acceleration of each of X-, Y-, and Z-axis directional components is detected based on an electrostatic capacity change between the plurality pairs of electrostatic capacity elements .

Moreover, the piezoelectric-type 3-axis acceleration sensor is configured such that when an acceleration acts on a weight, a deflection is generated at a portion of a piezoelectric ceramic substrate existing around the weight . The 3-axis acceleration sensor is commercially available from various companies and examples thereof include HAAM301 (trade name) manufactured by HOKURIKU ELECTRIC INDUSTRY CO . , LTD . and ML8950 (trade name) manufactured by Oki Electric Industry Co . , Ltd.

The reference of inclination of the device when detecting the inclination includes , for example, an inclined orientation of the device when the ej ection direction of the ej ection head is a horizontal direction, an inclined orientation of the device when the .ej ection direction of the ej ection head is downward in a vertical direction, and an inclined orientation of the device when the ej ection direction of the ejection head forms a certain angle relative to a vertical direction. The reference of inclination may suitably be defined considering the characteristics and performance of the ej ection head and further the use of the result of inclination ^• detection .

With the above-described configuration, when the power supply switch 120 is turned on, the power supply 113 outputs a reset signal to the CPU 101 and the CPU 101 is initialized in accordance with the signal . Thereafter, an operation starts by the program stored in the internal flash ROM, and when any special setting is not made, the operation starts in a normal operation mode . When a user performs inhalation, the output of the negative pressure sensor 19 is changed and the change is conveyed to the CPU 101 through the amplifier 108 , AD converter 109, and control circuit 117. When the inhalation rate exceeds a predetermined threshold value, the CPU 101 applies a voltage to the vibration motor 18 to vibrate it and sends a pulse signal to the head portion 8 through the control circuit 117 and the driver 10, whereby a liquid formulation contained in the cartridge unit 6 is ej ected . After the liquid formulation has been ej ected for a specified time period, the vibration motor 18 continues vibration for another specified time period to urge the user to perform inhalation during the another specified time period .

In the series of operation, the CPU 101 sequentially monitors the information of the sensor 114 , and for example when the information to inclination exceeds a threshold value, the CPU 101 changes the control for the head portion 8 through the control circuit 117 ( for example, applied voltage or pulse width is changed) . Thereby, for example, the particle diameter of liquid droplets ejected by the head portion 8 is controlled . Moreover, for example when the inclination exceeds a second threshold val.ue, the CPU 101 changes the vibration pattern of the vibration motor 18 to instruct the user not to perform further inclination . FIG. 11 shows a vibration pattern (a) at a normal inclination and a vibration pattern (b) when the inclination exceeds the second threshold value . In the pattern (a) , vibration is continuously performed, while in the pattern (b) , vibration is intermittently performed. At this time, the control may be made such that when the state in which the inclination exceeds the second threshold value continues for a . certain period, the ej ection of liquid droplets is stopped.

As the sensor 114 , any sensor can be used as described above . In the case of using a sensor which includes a detection circuit and an AD converter, it is possible to connect the sensor 114 directly to the control circuit 117 or CPU 101 , not through the detection circuit 115 and AD converter 116.

FIG . 12 explains an example of control when the inclination exceeds a threshold value . In the normal inclination state, the driver 110 drives a head 8a for normal orientation . When the inclination exceeds the threshold value, the driver 110 drives a head 8b for inclined orientation . The head 8a for normal orientation and the head 8b for inclined orientation are constituted such that their ej ection particle diameters are different from each other (in this case, it suffices to set the both heads parallel to each other at the same orientation) . Moreover, as another example, there can be adopted a method in which the head 8a for normal orientation and the head 8b for inclined orientation have the same structure and are disposed in different inclinations . Moreover, as described above, there may be adopted the method of using a single head and changing driving pulses or the like to change the ejection particle diameter, ejection amount, and the like .

As described above, it is possible to adopt various countermeasures including change of the ej ection mode, stopping of the ej ection, notice to a user, and the like depending on the result of detection of inclination of the inhaler, and the combination thereof may suitably be designed depending on cases . Moreover, it is possible to use the detection information to the inclination of the inhaler for the following purpose instead of use for control of the ej ection head . That is, the inclination of the inhaler during its use can be stored in a memory and thereafter subj ected to examination on the record of state of use by a doctor or the like . In this case, it is possible to use the detection information as data for performing proper decision based on the record of state of use . Here, the proper decision includes instructions to a patient of how to use, estimation of physical condition of a patient, determination as to whether a patient performs inhalation in a recumbent position or in a standing position, adj ustment of the ej ection rate of an ej ection head, replacement of an ej ection head with another one, or the like .

The present invention is not limited to the above examples and various changes and modifications . can be made within the spirit and scope of the present invention . Therefore to apprise the public of the scope of the present invention, the following claims are made .

This application claims priority from Japanese Patent Application No . 2005-025425 filed on February 1, 2005, which is' hereby incorporated by reference herein .

Claims

1. An inhaler for* a user to inhale a liquid formulation from an inbreathing port, which comprises a detection means for detecting or measuring inclination of a housing with respect to an inclination reference .

2. The inhaler according to claim 1 , further comprising a noticing means connected to the detection means, for serving notice to the user in accordance with an information from the detection means .

3. The inhaler according to claim 1, further comprising a control means connected to the detection means, for controlling ej ection of the liquid formulation in accordance with an information from the detection means .

4. The inhaler according to claim 1, further comprising a noticing means connected to the detection means, for serving notice to the user in accordance with an information from the detection means and a control means connected to the detection means , for controlling ejection of the liquid formulation in accordance with an information from the detection means .

5. The inhaler according to claim 1, further comprising a storage means connected to the detection means, for storing an information from the detection means .

6. The inhaler according to any one of claims 1 .to 5, wherein the detection means comprises an acceleration sensor .