Improved inhalation device

Abstract

The present invention relates to the field of suction devices for liquids. In particular, the present invention relates to a liquid discharge mechanism for suction devices and a method for discharging liquid from a suction device. The suction device comprises a housing (1), a reservoir (2) for storing liquid, a pumping unit, the unit comprising a standpipe (5), a hollow cylindrical part (3) having an internal space and capable of linear movement on the standpipe (5), wherein a pump chamber is fluidically connected to the reservoir (2) and a nozzle (6), the nozzle is fluid-tightly connected to the downstream end (5B) of the standpipe (5), and wherein the linear relative movement can be achieved by relative rotation of a rotatable part (1A) relative to a mating part (1B) around a rotation axis (R), so that the relative rotation is converted into the linear relative movement by a gear mechanism, the gear mechanism comprising at least one cam surface having a first section (9A) and a second section (9B), and wherein a potential energy storage device (7) is provided. The device is characterized in that the cam surface has a third section (9C) of constant height between the first section and the second section (9A, 9B), so that when the mating part (1B) slides along the third section (9C), no linear relative movement occurs. A method for generating an aerosol comprises, when the rotatable part (1A) rotates, a first filling phase for filling a pump chamber with liquid, and a second discharge phase for discharging atomized liquid from a nozzle (6), and is characterized in that between the two phases there is a third stationary phase, during which the volume of the pump chamber remains constant despite further rotation.

Description

Technical Field

[0001] The present invention relates to the field of suction devices for liquids. In particular, the present invention relates to a liquid discharge mechanism for a suction device, and a method of discharging liquid from a suction device. Background Art

[0002] For a long time, nebulizers or other aerosol generators for liquids are well known in the art. Such devices are particularly used in medicine and treatment. They are used as inhalation devices in medicine and treatment to apply active ingredients in the form of aerosols (that is, embedded in the gas in the form of droplets). Such inhalation devices are known, for example, according to document EP 0 627 230 B1. The main components of such inhalation devices are: a reservoir, which contains liquid to be atomized; a pumping unit, which is used to generate a sufficiently high pressure for atomization; and an atomizing device in the form of a nozzle.

[0003] Improvements to such an inhalation device are disclosed in patent application PCT / EP2018 / 061056 filed by the same applicant as the present invention, the contents of which are incorporated herein in their entirety.

[0004] Typical liquid discharge mechanisms include potential energy storage devices, such as springs and gear units. Potential energy is stored in the suction device by (preferably manually) loading the spring. This energy can then be used to generate pressure in a pump chamber connected to the nozzle fluid.

[0005] Document WO 2007 / 128381 A1 discloses another atomizing device for medically active liquids, which includes a liquid discharge mechanism. The relative rotation of the two parts of the housing is converted into linear motion by the gear unit, which is then used to load the spring. This motion transmission is achieved by using at least one pair of spiral surfaces that slide against each other. After the fully loaded rotation, when there are two pairs, 180 degrees are reached, and the surfaces that initially rise axially each provide a sharp edge with (also axial) vertical descent. The length of the descent corresponds to the pumping motion of the pumping device. Therefore, when the edge attempts to further rotate the mechanism and passes each other, the axial motion is reversed, and the potential energy is released again, causing pressure to be generated.

[0006] Care must be taken to prevent a premature and undesired release of the potential energy. To this end, solutions known in the art provide a locking element that stops the rotation when the two sliding surfaces reach the edge. In other words, the locking element prevents any axial movement just when further rotation would lead to the "descent". By manually releasing the locking element (i.e. by pressing a release button), the potential energy is intentionally released and used to generate pressure.

[0007] In WO 2007 / 128381 A1, when the device is primed, a small amount of liquid is already pumped through the filling conduit (pump chamber, nozzle). By axially offsetting the locking mechanism, when reaching the end of the rotary loading movement, the edges actually pass each other, resulting in a partial movement along the aforementioned "descent" and a pre-discharge of liquid due to the initial axial movement of the pumping mechanism. After a short distance, the offset locking mechanism ends the movement. Only at the subsequent actuation by activation (release) of the locking mechanism, the full pumping movement is performed and the desired dose of liquid is atomized.

[0008] The disadvantage of the premature pumping effect is that the amount of liquid discharged before the actual administration must be discharged from the nozzle outlet before the actual atomization begins. Otherwise, the blockage of the nozzle outlet will lead to the generation of undesirable droplet formation and / or splashing. In addition, the amount of liquid required for premature pumping reduces the total number of possible administration cycles per reservoir. In addition, the above-mentioned "drop" will produce a click that can be clearly heard, which may make some users feel uncomfortable.

[0009] Another disadvantage is that the structural effort to provide a locking element of the above-mentioned type is considerable, leading to higher production and assembly costs and an increased probability of mechanical failure. Summary of the invention

[0010] In a first aspect, the present invention provides an inhalation device for generating an aerosol of a medically active liquid, comprising

[0011] - a housing, a reservoir for storing a liquid in the housing, a pumping unit, the unit comprising a standpipe, a hollow cylindrical portion having an inner space configured to receive an upstream end of the standpipe, the cylindrical portion being linearly movable on the standpipe, wherein the cylindrical portion and the standpipe form a pump chamber having a variable volume for generating a pressure in the pump chamber by a linear relative movement of the cylindrical portion with respect to the standpipe, wherein

[0012] - the pump chamber is in fluid connection with the reservoir and the nozzle, the nozzle being fluid-tightly connected to the downstream end of the standpipe, and wherein

[0013] - the linear relative movement can be achieved by relative rotation of a rotatable part relative to a counterpart part about a rotation axis, the rotatable part being part of a first part of the housing or connected to the first part, the counterpart part being part of a second part of the housing or connected to the second part, such that the relative rotation is converted into the linear relative movement by a gear mechanism, the gear mechanism comprising at least one cam surface, the cam surface comprising a first section of increased height and a second section of reduced height in an axial direction, the cam surface being able to slide along an adjacent counterpart face, wherein the cam surface is adapted to slide along the counterpart face when rotating, resulting in the conversion, and wherein

[0014] - a potential energy storage device is provided, said device being capable of storing energy by said relative rotation along said first section, and wherein said energy when released is capable of being released to said pumping device, and wherein

[0015] - the cam surface comprises a third section of constant height between the first section of increasing height and the second section of decreasing height, so that when the third section of the cam surface slides along the mating surface, the cylindrical portion does not undergo linear relative movement with respect to the riser, and wherein

[0016] A dosing cycle covering the rotation angle of said first, second and third section corresponds to a rotation of 180 degrees.

[0017] In a second aspect, the present invention provides a method for generating an aerosol by means of an inhalation device according to the aforementioned method, wherein the method comprises, as the rotatable part rotates, a first filling phase for filling the pump chamber with liquid, and a second discharge phase for discharging the atomized liquid from the nozzle, wherein between the two phases there is a third stationary phase, during which the volume of the pump chamber remains constant despite further rotation.

[0018] Purpose of the Invention

[0019] The object of the present invention is to provide a device which avoids the disadvantages of the known art.

[0020] The invention should provide the possibility to prevent premature and undesired release of liquid from the nozzle and avoid reducing the dosing cycles per reservoir.

[0021] The present invention will also provide a cost-effective and mechanically reliable solution.

[0022] Description of the invention

[0023] According to a first aspect of the invention, this object is solved by an inhalation device for generating an aerosol of a medically active liquid, the inhalation device comprising

[0024] - a housing, a reservoir for storing a liquid in the housing, a pumping unit, the unit comprising a standpipe, a hollow cylindrical portion having an inner space configured to receive an upstream end of the standpipe, the cylindrical portion being linearly movable on the standpipe, wherein the cylindrical portion and the standpipe form a pump chamber having a variable volume for generating a pressure in the pump chamber by a linear relative movement of the cylindrical portion with respect to the standpipe, wherein

[0025] - the pump chamber is in fluid connection with the reservoir and the nozzle, the nozzle being fluid-tightly connected to the downstream end of the standpipe, and wherein

[0026] - the linear relative movement can be achieved by relative rotation of a rotatable part relative to a counterpart part about a rotation axis, the rotatable part being part of a first part of the housing or connected to the first part, the counterpart part being part of a second part of the housing or connected to the second part, such that the relative rotation is converted into the linear relative movement by a gear mechanism, the gear mechanism comprising at least one cam surface, the cam surface comprising a first section of increased height and a second section of reduced height in an axial direction, the cam surface being able to slide along an adjacent counterpart face, wherein the cam surface is adapted to slide along the counterpart face when rotating, resulting in the conversion, and wherein

[0027] - a potential energy storage device is provided, said device being capable of storing energy by said relative rotation along said first section, and wherein said energy when released is capable of being released to said pumping device, and wherein

[0028] - the cam surface comprises a third section of constant height between the first section of increasing height and the second section of decreasing height, so that when the third section of the cam surface slides along the mating surface, the cylindrical portion does not undergo linear relative movement with respect to the riser, and wherein

[0029] A dosing cycle covering the rotation angle of said first, second and third section corresponds to a rotation of 180 degrees.

[0030] Furthermore, the object is solved by a method according to a second aspect of the invention. Advantageous embodiments are described in the ensuing description and in the accompanying drawings.

[0031] The inhalation device is used to generate a medical aerosol from an active liquid for inhalation therapy. In particular, the inhalation device is suitable for generating and emitting an atomized aerosol suitable for pulmonary delivery of a medical active ingredient in a dosed manner.

[0032] Typically, such an inhalation device comprises a housing, within which there is a reservoir for storing a liquid, and a pumping unit preferably based on the piston pump or plunger pump principle. More specifically, the pumping unit according to the invention comprises a hollow cylindrical part having an inner space for generating a pressure in a pump chamber. Note that the term "cylindrical part" refers to a part having a cylindrical inner surface; the outer part and the part not in contact with the riser and / or the seal does not have to be cylindrical.

[0033] The pump chamber is formed by the cylindrical part and the standpipe and has a variable volume for generating pressure in the pump chamber. The pump chamber is fluidically connected to the reservoir; optionally, via a non-return valve, which blocks in the direction of the reservoir. In order to achieve volume variability, the standpipe can accommodate at least one inner end facing the reservoir (hereinafter referred to as "upstream end") in the cylindrical part, and the cylindrical part can be linearly movable on the standpipe.

[0034] The nozzle is connected directly or indirectly in a fluid-tight manner to the downstream end of the riser.

[0035] The standpipe may be fixed relative to the housing of the device, or at least relative to a portion of the housing, to which the nozzle is also securely fixed, directly or indirectly, so that the standpipe is also fixed or immovable relative to the nozzle. In another embodiment, the standpipe is movable and the pump chamber / cylindrical portion is immovable relative to the housing. In yet another embodiment, both the cylindrical portion and the standpipe are movable.

[0036] In other words, the cylindrical portion has an interior space configured to receive the upstream end of the riser. The cylindrical portion is configured to be linearly movable along the end so that the volume inside the cylindrical portion can be changed by a linear relative movement of the riser and vice versa.

[0037] Further, the linear relative motion can be achieved by relative rotation of a rotatable part relative to a counterpart part around a rotation axis, the rotatable part being part of a first part of the housing or connected to the first part, the counterpart part being part of a second part of the housing or connected to the second part, so that the relative rotation is converted into the linear relative motion by a gear mechanism or the like. Therefore, the housing comprises two parts, one of which is capable of rotating relative to the other. The gear mechanism comprises at least one cam surface, i.e. a surface capable of sliding along an adjacent counterpart surface or another corresponding component guided by a specific shape of the cam surface. The cam surface may be in the form of a track running in a curved manner around the main axis of rotation of the device. Specifically, the cam surface may be in the form of a closed or annular track running in a circular or circumferential manner around the main axis of rotation, as described in further detail below.

[0038] The cam surface has or includes a first section with increased height and a second section with reduced height in the axial direction. Here, the axial direction is parallel to (or is equal to) the longitudinal direction of the pump chamber / cylindrical part. When the part bearing the cam surface and the part bearing the mating surface rotate relative to each other, the cam surface can slide along the mating surface, causing the conversion. During the sliding process, the cam surface and the mating surface keep axial contact. As a result, the volume of the pump chamber is changed by the relative rotation of the rotatable part relative to the mating part. The movement along the first section causes an increase in volume (therefore the pressure in the pump chamber is reduced, and the pump chamber is filled with liquid from the reservoir), and the movement along the second section causes a decrease in volume (and an increase in pressure in the pump chamber, and the discharge of liquid from the nozzle). Obviously, according to the actual construction, the opposite effect can also be obtained. However, for the sake of clarity, the influence of each part on the volume is defined as described above.

[0039] In other words, a first portion of the gear has a cam surface and is connected to a first portion of the housing; and a second portion of the gear (a mating portion) has a mating surface and is connected to a second portion of the housing; and the first portion and the second portion are rotatable relative to each other so that the cam surface and the mating surface slide on each other.

[0040] Further, a potential energy storage device is provided, which can store energy by means of said relative rotation along the first section, and said energy can be released to said pumping device when released, for example by activating a release device. Preferably, said storage device is provided by an elastic spring. By tightening said spring, potential energy is stored, and by allowing it to re-contract, energy is released. In another embodiment, the effect is the opposite (compressing the spring).

[0041] According to the invention, the cam surface has or includes a third section of constant or almost constant height between the section of increased height and the section of reduced height, so that when the mating surface slides along the third section, no or almost no linear relative movement occurs.

[0042] As a result, the rotation of the rotatable part along the third section arranged between the first and second sections will not change the relative axial position of the rotatable part and the paired part, and therefore will not change the volume in the pump chamber, and therefore will not change its internal pressure. Simultaneously, the loading state of the potential energy storage device will not change due to this rotation along the third section. At this stage, premature pumping of liquid will not occur, and therefore liquid will not be discharged before actual administration. Due to the pre-discharge of liquid, the nozzle outlet will not be blocked, and the generation of undesirable droplet formation and splashing is avoided. In addition, the total number of possible administration cycles of each reservoir is increased, and if necessary or desired, the aforementioned click can be avoided. In addition, the blocking device that may be provided to prevent the unintentional actuation of the device can be constructed in a simpler way, thereby reducing production and assembly costs and reducing the possibility of mechanical failure.

[0043] In one embodiment, the cam surface is arranged at or connected to the rotatable part and the mating part provides the mating face.

[0044] In another embodiment, the cam surface is arranged at or connected to the mating part and the rotatable part provides the mating face.

[0045] It should be noted that the term "mating surface" should be interpreted broadly so that every type of component used to provide sliding interaction with the cam surface falls under this definition.

[0046] In one embodiment, the counterface is provided by a second cam surface. Thus, there are two cam surfaces, which simultaneously serve as respective counterfaces. In other words, the counterpart (or, conversely, the rotatable part) also provides a cam surface, and in particular a surface having the inverted shape of a corresponding cam surface of the rotatable part (or, conversely, the counterpart), or one or more parts thereof. This results in maximum mechanical overlap of the two parts, reducing mechanical wear.

[0047] In another embodiment, in one part there is one cam surface, but instead of a second cam surface the second part (the rotatable part or the mating part) provides a corresponding cam.

[0048] In yet another embodiment, instead of a cam, the rotatable portion or mating portion may provide a roller or the like for physical interaction with a corresponding cam surface, providing very low friction and thereby potentially reducing the force required to load the device.

[0049] However, all of the above-described embodiments have a substantially equivalent effect of ensuring a variable relative axial position of the rotatable part and the counter part upon relative rotation of these parts.

[0050] When each portion of the cam surface is projected onto a plane perpendicular to the axis of rotation ("plane of rotation"), each portion can be assigned a respective rotation angle.

[0051] Thus, one dosing cycle covers or includes the corresponding rotation angles of the first, second and third sections and optionally other parts, such as the optional fourth section or the optional fifth section as described below, preferably with a constant height, which may follow the second section. One dosing cycle may be defined as a "sequence" of said sections.

[0052] In one embodiment of the inhalation device, about a complete cycle, a 360 degree rotation covers two complete sequences of all these parts at least once. This means that when the rotatable part is rotated 360 degrees, all corresponding sections, i.e. the first, second, third and possibly the fourth or fifth section, are passed through twice.

[0053] In other words, the sum of the various rotation angles measured in the rotation plane from the beginning to the end of the various sections around the rotation axis is equal to 360 degrees, or to an integer fraction thereof. This means that, depending on the embodiment, a full 360 degree rotation is required to pass through all sections in order to load and discharge a dose of liquid, or for example 1 / 2, 1 / 3, ... of the 360 ​​degrees, i.e. 180, 120, ... degrees.

[0054] In a preferred embodiment, the sum of the various rotation angles measured in the rotation plane about the rotation axis from the beginning to the end of the various sections is equal to 180 degrees, or to an integer fraction thereof. This means that, depending on the embodiment, a rotation of 180 degrees is required to pass through all sections in order to load and discharge a dose of liquid, or for example half or a third of said 180 degrees or another ratio, i.e. 90, 60 ... degrees or another angle, depending on the number of doses discharged per 180 degrees of rotation.

[0055] Thus, two doses are discharged over a rotation of 360 degrees, which means that one dose is loaded and discharged over half a complete rotation corresponding to 180 degrees. Other preferred integers are three and four.

[0056] If an optional fourth and / or fifth segment (e.g. another segment of constant height, or a segment intended to inhibit further rotation of the rotatable part) is additionally present between or after the aforementioned segments, in particular between the second and first segments (i.e. the first segment is preceded by said fourth segment), or between the third segment and the second segment (i.e. the fourth segment provides a differently shaped "end" of the third segment), or after the end of the second segment, e.g. in the form of another segment of constant height after the second segment, it is clear that the above is true for all four or five segments, i.e. a complete dosing cycle of 180 degrees covers all four or five segments, and so on.

[0057] The advantage of rotating through 180 degrees for one dosing cycle is that the slope of the first section can still be lower, since more (rotational) paths are provided to obtain the desired linear relative movement to generate sufficient pressure, whereas two dosing cycles can be achieved with one complete rotation. This is advantageous if the pressure must be particularly high, the dosing volume is large, or the forces available for rotation are low (e.g. when the device is operated by a child), and a full 360 degree rotation cannot be achieved, e.g. due to structural or design limitations.

[0058] In other cases, partial rotation of a dose is preferred.

[0059] As mentioned above, the sum of the rotation angles of one pumping cycle defined above is equal to 180 degrees. Rotating 180 degrees per dosing cycle has proven to be a good compromise in terms of the force required for operation and the pressure / volume achievable by the dose. Furthermore, in this case, in a particular embodiment, the rotation angle of the third segment (i.e., the segment with a constant or substantially constant height) reaches 7±6 degrees, or in other words from 1 to 13 degrees. Experiments have shown that this range is particularly useful in practice. If the angle of the third segment is too small, for example less than 1°, it becomes more difficult to stop the rotation immediately at the end of the segment. On the other hand, the larger third segment wastes valuable space that could be used for other rotation stages, in particular the first segment, which is necessary to build up pressure and therefore cannot be too short / too steep.

[0060] In another embodiment, the rotation angle of the second section, i.e. the section of reduced height, is equal to 0 degrees, resulting in an axially oriented section of the cam surface. In other words, after passing the edge of the third section, the adjacent section suddenly "drops" back to the beginning of the first section, allowing the stored energy to be released instantaneously, resulting in a sudden increase in pressure in the pump chamber. Note that the term "drop" refers only to the decrease in the axial position of the rotatable part relative to the mating part, and does not indicate a specific spatial direction. The same is true for the terms "up" and "down" when used.

[0061] However, due to the limited amount of liquid that can pass through the nozzle, the volume will decrease within a certain period of time ("injection time"). Therefore, depending on the specific construction, the various parts may not reach their initial position (almost) immediately, and a certain "undefined" intermediate state of their position may occur, in which the cam surface and the mating surface may temporarily lose contact. Therefore, in another embodiment, the rotation angle is equal to a value greater than 0 degrees, such as 1 degree, 2 degrees or 3 degrees. Therefore, the corresponding part does not "fall", but is still guided along the cam surface even in the discharge phase, which can enhance the stability of the drug delivery function.

[0062] In a specific embodiment in which a pumping cycle reaches 180 degrees as described above, the rotation angle of the first segment (the segment with increased height) can reach a value of about 170 degrees, such as a value in the range of about 150 to 170 degrees or about 155 to about 165 degrees. In addition, in these embodiments, the rotation angle of the second segment (the segment with reduced height) reaches a value in the range of about 0 to about 3 degrees or about 0 to about 2 degrees or only about 1 degree. In addition, in these embodiments, the rotation angle of the third segment (the segment with substantially constant height) reaches a value in the range of about 1 to about 13 degrees or about 3 to about 11 degrees or about 5 to about 9 degrees or about 6 to about 8 degrees. However, it should be noted that additional fourth and fifth segments can be present between the first, second and third segments or after the second segment. In a specific embodiment, the fifth segment is located after the third segment (thus before the first segment of the subsequent dosing or pumping cycle), and the fifth segment can generally cover an angle from about 5 degrees to about 15 degrees, or from about 7 degrees to about 10 degrees.

[0063] In a further specific embodiment, in which a pumping cycle as defined above reaches 180 degrees, the rotation angle of the first segment (the segment with increased height) can be selected in the range from about 165 degrees to about 170 degrees, the rotation angle of the second segment (the segment with reduced height) can be selected in the range from about 0 degrees to about 2 degrees, and the rotation angle of the third segment (the segment with essentially constant height) can be selected in the range from about 1 degree to about 13 degrees, wherein the sum of the rotation angles of these segments adds up to 180 degrees.

[0064] In yet another embodiment, the rotation angle is less than 0 degrees. This means that before starting a new cycle, there is an "undercut" into which the corresponding part will fall. This allows reverse rotation, which helps to clean up unwanted splashes or drops at the nozzle outlet, or even retract the liquid into the nozzle outlet, so that the next dosing cycle can start from a very stable predetermined state, thereby improving the quality of the device.

[0065] In another embodiment, further, there is a device for preventing the actuation of the inhalation device, the device being suitable for suppressing the change of the relative axial position of the rotatable part and the mating part corresponding to the third section. This means that the device for preventing actuation prevents the accidental release of the potential energy storage device, and therefore prevents the premature discharge of the medical liquid through the nozzle. Only the intentional deactivation of the blocking device allows the discharge.

[0066] The means may be provided by a button which allows further rotation only when pushed, or by an axial recess or projection in the third section which causes a mechanical obstacle which prevents further rotation due to a temporary increase in the necessary rotational force, or by a retractable mechanical obstacle which prevents movement along the aforementioned "descent".

[0067] Preferably, the rotational position at which the blocking means starts to work is at the extreme end of the third section, or just behind said end. Thus, when the blocking is released, the discharge phase can start automatically without further manual rotation.

[0068] In one embodiment, the device for preventing actuation is adapted to passively allow further rotation when it is deactivated, or actively further rotates the parts so that the second section of the cam surface contacts the mating face. If the blocking device starts working before the end of the third section, this embodiment is particularly advantageous. Then, further rotation is required to start dosing. Then, manually or actively provide this further rotation during the deactivation of the blocking device, the mating face is pushed over the edge of the third section into the second section.

[0069] According to another embodiment, the means for initial blocking (ie when activated, engaged) blocks any relative axial movement of the rotatable part with respect to the mating part when the mating face is in contact with the third section, i.e. before the discharge phase. When the blocking means are deactivated, it allows said axial movement and the discharge phase starts immediately.

[0070] In summary, the blocking means may temporarily prevent a rotation of the rotatable part into the third section, or prevent a linear movement along said section.

[0071] In a further embodiment, the slope of the first section is selected from constant, increasing, decreasing and combinations thereof. A constant slope results in a constant increase in the volume of the pump chamber. If the slope increases, the liquid loading rate of the pump chamber at a constant speed also increases along the angle. The result is a smooth start of the loading phase.

[0072] If there is a preload check valve between the reservoir and the pump chamber, it may be necessary to start the phase of filling the pump chamber from the reservoir faster. This can be achieved by reducing the slope, which is highest at the beginning of the phase and the rotational force is reduced during the rest of the phase.

[0073] Furthermore, depending on the specific requirements of the construction, a combination of slopes may be advantageous.

[0074] The invention also relates to a method for generating an aerosol by means of an inhalation device according to the above definition. For the sake of simplicity, please refer to the above explanation. In other words, all options and preferences described for the inhalation device itself also apply to this method.

[0075] The method comprises a first "filling phase" in which the pump chamber is filled with liquid while the rotatable part rotates, and a second "discharging phase" in which the atomized liquid is discharged from the nozzle. According to the invention, between the two phases, there is a third "stationary phase" during which the volume of the pump chamber remains constant despite further rotation. These three phases correspond to the three sections mentioned above. In particular, in the third phase, the volume of the pump chamber does not change because there is no linear relative movement of the cylindrical part.

[0076] With regard to the method of the present invention, one dosing cycle is achieved by a rotation of 180 degrees. Therefore, a rotation of more than 360 degrees comprises two dosing cycles. However, in other embodiments, other integers are also possible, such as three or four cycles in every 360 degree rotation.

[0077] In a preferred embodiment, the entire stationary phase passes through 7 ± 6 degrees of rotation, ie, from about 1 degree to about 13 degrees.

[0078] It will be apparent that the remaining angle (180 degrees) to complete one cycle may be used for the sum of the first and second stages and the various sections described above in conjunction with the first aspect of the invention.

[0079] In a specific embodiment, the term "medically active liquid" as used herein refers to a medically active liquid in the form of a pharmaceutical composition, which comprises at least one active pharmaceutical ingredient (API), more specifically at least one inhalable active pharmaceutical ingredient. More specifically, this at least one inhalable active pharmaceutical ingredient can be, for example, selected from long-acting muscarinic antagonists (LAMA), long-acting beta agonists (LABA) and inhalable glucocorticoids (ICS), as well as analgesics and antidiabetic agents alone or in combination with each other.

[0080] Examples of long-acting muscarinic antagonists (LAMA) include, but are not limited to, achlorclidinium, glycopyrrolate salts such as glycopyrrolate, refenacin, troponium bromides such as tiotropium, umeclidinium, oxitropium, flutropium, ipratropium, trospium chloride, tolterodine.

[0081] Examples of long-acting beta agonists (LABAs) include, but are not limited to, albuterol, aformoterol, bambuterol, bitolterol, brosaterol, carbuterol, clenbuterol, fenoterol, formoterol, hexadrenaline, ibuterol, indacaterol, isetaline, isoproterenol, levalbuterol, mabuterol, isobutyl acetate, metaproterenol, olodaterol, metaproterenol, pirbuterol, procaterol, reproterol, rimaterol, ritodrine, salmeterol, samethamine, sotenot, sulphonterol, tiaramde, terbutaline, terbuterol.

[0082] Examples of inhaled corticosteroids (ICS) include, but are not limited to, prednisolone, prednisone, butixocortpropionate, flunisolide, beclomethasone, triamcinolone acetonide, budesonide, fluticasone, mometasone, ciclesonide, roflenide, dexamethasone, eprednolate, deflazacort, etiprednol, loteprednol, RPR-106541, NS-126, ST-26.

[0083] Furthermore, the active pharmaceutical ingredient may be selected from analgesics, such as opioid analgesics (e.g. morphine, fentanyl) or non-opioid analgesics (e.g. salicylic acid derivatives, such as acetylsalicylic acid) or cannabinoids (e.g. tetrahydrocannabinol), antidiabetic drugs, such as insulin.

[0084] The medically active liquid or liquid pharmaceutical composition which can be nebulized or aerosolized by the present inhalation device may contain at least one pharmaceutically active ingredient as described above, but may also contain a mixture of two or more pharmaceutically active ingredients which can be administered by inhalation.

[0085] The medically active liquid or pharmaceutical composition nebulizable by the inhalation device according to the invention is preferably formulated as a composition suitable and adapted for inhalation use, in other words a composition that can be nebulized or aerosolized for inhalation and is physiologically acceptable for inhalation by a subject.

[0086] The medically active liquid or pharmaceutical composition that can be administered by the inhalation device according to this aspect of the invention or contained in the inhalation device and reservoir can be in the form of a dispersion, such as a suspension having a liquid continuous phase and a solid dispersed phase, or in the form of a solution.

[0087] In further embodiments, the medically active liquid or pharmaceutical composition as described above may optionally contain one or more physiologically acceptable excipients suitable for inhalation use. Excipients that may be characterized in the composition may include, but are not limited to, one or more buffers, salts, taste masking agents, surfactants, lipids, antioxidants, and cosolvents that regulate or control the pH value of the solution, which may be used to increase or improve solubility, such as ethanol or ethylene glycol.

[0088] In certain embodiments, the medically active liquids described above may be substantially free of propellants.

[0089] In further specific embodiments, the medically active liquid as described above can be an aqueous solution, wherein one or more active pharmaceutical ingredients as described above are dissolved and solubilized in a liquid carrier solution comprising water. This aqueous solution optionally can also include one or more excipients as described above. BRIEF DESCRIPTION OF THE DRAWINGS

[0090] FIG1 shows a schematic simplified cross-sectional view of a general inhalation device;

[0091] FIG2 shows a more detailed cross-sectional view of the inhalation device;

[0092] FIG3 shows a simplified development of a rotatable part having a cam surface with two sequences of three sections;

[0093] FIG4 shows a simplified top view of a rotatable part having two sequences of three segments;

[0094] 5 , 6 and 7 show simplified expanded schematic diagrams of mating parts with mating faces;

[0095] Figures 8, 9 and 10 show different stages of interaction between the cam surface and the mating surface;

[0096] 11 , 12 and 13 show views of a more detailed embodiment at respective stages corresponding to FIGS. 8 , 9 and 10 ;

[0097] Figures 14, 15 and 16 show an example of a fourth section which is intended to inhibit further rotation of the rotatable part.

[0098] In Figure 1 a schematic simplified cross-sectional view of a generic inhalation device is shown. Figure 1 shows the situation before first use.

[0099] The inhalation device comprises a housing 1, which is shaped and dimensioned so that it can preferably be held in one hand and can be operated with one finger, for example a thumb (not shown). A reservoir 2 for storing a medically active liquid is located inside the housing 1. The reservoir 2 shown is designed to be collapsible; this means that during emptying, the elastic walls or at least the soft walls bend so that the negative pressure required to extract a certain amount of liquid does not increase or hardly increases. A similar effect can be achieved when the rigid container has a removable bottom, by which the internal volume of the reservoir can be continuously reduced (not shown).

[0100] In addition, the inhalation device comprises a pumping device having a hollow cylindrical portion 3, which forms a variable volume pump chamber in the housing 1 for generating the desired pressure required for discharging and atomizing the liquid. The pumping device may also comprise additional components (buttons, locking devices, etc.) not shown.

[0101] The hollow cylindrical portion 3 is in fluid connection with the reservoir 2 via an optional inlet non-return valve 4. The non-return valve 4 serves to allow liquid to flow into the pump chamber and to block liquid from flowing back into the reservoir 2 when a blocking means, not shown, is released.

[0102] As the potential energy storage device 7, there is provided a compression spring, one end of which is connected (upward) to the hollow cylindrical portion 3 and is supported at the bottom (lower part in the figure) of the housing 1.

[0103] The inhalation device further comprises a standpipe 5 having at least one upstream end 5A facing the reservoir, which upstream end can be accommodated in the hollow cylindrical part 3. In other words, the standpipe 5 can be at least partially pushed into the hollow cylindrical part 3 forming the pump chamber, resulting in a reduction in the internal volume of the pump chamber. The term "internal volume" describes the volume extending from the inlet of the pump chamber facing the reservoir to the location of the inner end 5A of the standpipe 5. In the illustrated case, the standpipe 5 is almost completely withdrawn from the hollow cylindrical part 3. As a result, the internal volume of the pump chamber, which is currently located between the check valve 4 and the upstream end 5A of the standpipe 5, is the largest and is filled with liquid.

[0104] Preferably, in the section 1 for receiving the riser 5, the hollow cylindrical part 3 has at least one portion with a circular inner cross section corresponding to the (then also) circular outer cross section of the respective riser section. Of course, other cross-sectional shapes are also possible.

[0105] According to the described embodiment, the non-return valve 4 is arranged between the reservoir 2 and the inlet of the pump chamber.

[0106] In addition, the suction device comprises a nozzle 6, which is connected to the downstream end 5B of the standpipe 5 in a liquid-tight manner. The nozzle 6 can be any known nozzle suitable for atomizing liquids. The nozzle 6 described as an example uses the atomization principle by means of two colliding liquid jets. Preferably, the cross section of the liquid-containing channel is relatively small and is typically in the micrometer range.

[0107] Also shown is an optional outlet valve 8 in the standpipe 5 for preventing a backflow of liquid or air from the outside to the downstream end 5B of the standpipe 5. The outlet valve 8 is arranged in the upstream end 5A of the standpipe 5. Liquid can pass through the outlet valve 8 in the direction of the nozzle 6, but the outlet valve 8 prevents any undesired reverse backflow.

[0108] As can be seen in Figure 1, the standpipe 5 is designed to be stationary and firmly attached to the housing 1, as shown by the connection in the area of ​​the outer end 5B with the housing 1. The standpipe 5 is also firmly attached to the nozzle 6, which in turn is attached to the housing 1. In contrast, the hollow cylindrical portion 3 is designed to be movable relative to the housing 1, the standpipe 5 and the nozzle 6.

[0109] Not visible in FIG. 1 is the gear mechanism required according to the invention, thanks to which the linear relative movement of the hollow cylindrical part 3 can be achieved by a relative rotation of a rotatable part (which is part of the housing 1 or is connected to the housing 1) about an axis R relative to a second part of the housing, so that the relative rotation can be converted into the linear relative movement.

[0110] However, in Fig. 2, an embodiment of the present invention is shown, wherein these parts are visible.Some reference numerals shown in Fig. 1 and the lower part (potential energy storage device, reservoir) are omitted.The pump chamber is located in the overlapping part of the hollow cylindrical part 3 and the riser 5, and no valve is shown.In particular, it can be seen how the housing 1, the rotatable part 1A and the mating part 1B are related to each other.The mating part 1B is firmly connected to the housing 1.The rotatable part 1A partially overlaps with the mating part 1B.The rotatable part 1A can move linearly along the axis of rotation R within certain limits.However, it does not rotate with the mating part 1B.The riser 5 is connected to a part of the housing 1, the mating part 1B is also connected to the part, and is connected to the nozzle 6 (not shown), and the hollow cylindrical part 3 is connected to the rotatable part 1A.Therefore, by linearly moving the rotatable part 1A, the internal volume of the hollow cylindrical part 3 forming the pump chamber can be changed. In the present example, moving the rotatable part 1A upwards (ie downstream or towards the nozzle) reduces the volume, resulting in discharge of liquid, whereas moving downwards increases the volume, resulting in (re)filling of the pump chamber from the reservoir side.

[0111] In Fig. 3, a simplified development of a rotatable part 1A is depicted, which has a rim with two sequences of cam surface segments, each of which comprises segments 9A, 9B and 9C. The rim provides the downstream surface of the rotatable part 1A. Alternatively, the rim with the cam surface can be accommodated in the mating part 1B, or both the rotatable part 1A and the mating part 1B can have corresponding cam surfaces. Obviously, all three versions will result in the same conversion of rotation into linear motion.

[0112] As can be seen from Figure 3, the first section 9A consists of an ascending slope, while the third section 9C is provided by a "flat" slope. Subsequently, the second section 9B is shaped as a "step" or a vertical "descent". In the described example, the corresponding rotation angle of one dosing cycle, i.e. the rotation from the beginning of the first section 9A to the end of the second section 9B, amounts to 180 degrees. Therefore, a complete 360-degree relative rotation of the rotatable part 1A relative to the second part 1B will include two dosing cycles.

[0113] FIG. 4 shows the same situation in a top view, i.e. a view parallel to the axis of rotation R. Semicircle C represents the rotation angle (180 degrees) of a dosing cycle. At the beginning of the angle (the leftmost starting point), the first segment 9A starts. Arrow 10 represents the beginning of the third segment 9C. Just between the third segment 9C and the next first segment belonging to the second dosing cycle (thick black line, reference numeral omitted), is the second segment 9B. In the view of this example, the second segment 9B extends along the viewing direction (parallel to the axis of rotation R) and is therefore very short. On the contrary, the third segment 9C has a visible length, so that when the rotation is continued, the part is easy to detect manually. If the device that is expected to be loaded has not yet discharged a dose of medicine, the rotation is stopped anywhere in the third segment. When further rotating, the end of the third segment 9C is reached, and the device is actuated, while the mating part (not shown) slides over the edge of the first segment 9A and descends along the second segment 9B. Then, a new cycle can begin.

[0114] Figures 5 to 7 show a mating face which, in the embodiment shown, is a feature of the mating part 1B. Alternatively or additionally, it can also be a feature of the rotatable part 1A. In Figure 5, the mating face has the inverted shape of the cam surface shown in Figure 3, carrying all three sectors 9A, 9B, 9C.

[0115] In FIG6 , the mating surface is shortened; however, it still has a flat portion corresponding to the third section 9C, and an inclined portion corresponding to the first section 9A. On the right side of FIG6 , the area drawn with dashed lines represents a fourth section 9D, which "interrupts" or shortens the corresponding first section 9A. However, the remaining mating surface is sufficient for the desired cam interaction between the two surfaces / components 1B, 1A.

[0116] FIG. 7 shows a short cam 11 which is also sufficient to achieve the desired interaction but provides a low overlap area between the segments 9A, 9B, 9C (not shown) and their mating faces (not shown).

[0117] In Figures 8, 9 and 10, different stages of interaction between the cam surface and the mating surface are shown. In this embodiment, for each segment 9A, 9B and 9C, the two parts 1A, 1B have matching shapes or slopes of the corresponding cam surfaces; of course, one has the opposite profile of the other. Similar parts have similar reference numerals (partially omitted). The relative rotation of the actual parts 1B, 1A is described by the relative movement in the figure; the relative movement of the mating part 1B to the right corresponds to the intended direction of rotation (loading, rest, discharge).

[0118] In Fig. 8, the loading phase is shown, wherein the counterpart part 1B slides on the first section 9A of the rotatable part 1A, resulting in a linear movement of the counterpart part 1B, thereby increasing the volume of the pump chamber (not shown) and loading the potential energy storage device (not shown).

[0119] In FIG. 9 , a stationary phase is depicted, wherein, despite the possibility of further rotation, no changes in volume and loading occur, since the axial measuring distance (or axial position) of the components 1A and 1B remains constant.

[0120] In Figure 10, the distance decreases rapidly, as the counterpart part 1B "descends" along the second section 9B of the rotatable part 1 A. This figure therefore depicts the expulsion phase.

[0121] The device is then at the beginning of another dosing cycle, which will begin from the loaded condition.

[0122] The subsequent FIGS. 11 , 12 and 13 correspond to the stages schematically described previously in FIGS. 8 , 9 and 10 .

[0123] Note that in the depicted embodiment, a rotation of 180 degrees results in a complete dosing cycle, including the loading and discharge phases. Note further that in order to make the relevant areas as visible as possible, the cross-sectional views do not have identical cross-sections.

[0124] In Figure 11 the loading is in the loading phase. The counter part 1B is firmly connected to a part of the housing 1. The rotatable part 1A provides a cam surface. In the described phase the inclined section 9A is in contact with an adjacent counter face of the counter part 1B.

[0125] In Figure 12, the stationary phase is depicted. In this case, the segment 9C (flat segment) is in contact with the corresponding counter-face. Further rotation about the axis of rotation R does not (immediately) result in a change in the axial position or distance between the rotatable part 1A and the counter-part 1B.

[0126] Finally, in Figure 13, the discharge phase is shown. In this phase, the "descending" section 9B slides along the corresponding mating surface and the distance between the rotatable part 1A and the mating part 1B decreases rapidly, driven by the energy storage device (not shown), which now releases its energy to put the pump chamber (not shown) under pressure. As a result, the liquid is discharged from the nozzle (neither shown).

[0127] In Figs. 14, 15 and 16, a not-to-scale example of a fourth section 9D is shown, which is intended to inhibit a further rotation of the rotatable part.

[0128] In these embodiments, the fourth section 9D is arranged at the end of the section 9C. According to Figure 14, the fourth section 9D has a slope of increasing height. Therefore, when the mating surface represented by the cam 11 reaches the fourth section 9D during rotation, climbing the section will require further energizing the potential energy storage device (not shown). However, the user will be able to feel the sudden increase in the force required for further rotation and stop in further rotation. In addition, if there is no other external force, the rotation will not continue, ensuring that, for example, during storage, no unintentional liquid release will occur.

[0129] In Figure 15, the fourth section 9D performs the same function. In this embodiment, it has the shape of a slope that increases first and then decreases ("bump"). Only after the highest point is passed does the discharge phase begin.

[0130] In Figure 16, the fourth section 9D provides a slope ("notch") that decreases first and then increases. When the cam reaches the lowest part of the fourth section 9D, it stays in this stable position until additional force is provided to "lift" it out of the section to start discharging.

[0131] Compared with the embodiment without the fourth segment 9D, as shown in Figures 8-10, the rotation angle of the third segment 9C is the "original" full size, and the rotation angle of the fourth segment accounts for 5% to 50%, or 10% to 30%, or 15% to 25% of the "original" angle. The maximum height (or depth) of the fourth segment 9D relative to the third segment 9C is 0.05mm to 5mm, or 0.1mm to 1mm, or 0.25mm to 0.5mm.

[0132] Reference numerals list

[0133] 1 Housing

[0134] 1A Rotatable part

[0135] 1B Pairing section

[0136] 2 Storage

[0137] 3 Hollow cylindrical part

[0138] 4 Check valve

[0139] 5. Riser

[0140] 5A Upstream end

[0141] 5B Downstream end

[0142] 6 Nozzles

[0143] 7 Potential Energy Storage Devices

[0144] 8 Outlet valve

[0145] 9A Section 1

[0146] 9B Section 2

[0147] 9C Section 3

[0148] 9D Section 4

[0149] 10 Arrow

[0150] 11 Cam

[0151] R Rotation axis

[0152] C Semicircle

[0153] The following list of numbered items are embodiments encompassed by the present invention:

[0154] 1. An inhalation device for producing an aerosol of a medically active liquid (F), comprising

[0155] - a housing (1), a reservoir (2) for storing a liquid (F) in the housing (1), a pumping unit, the unit comprising a standpipe (5), a hollow cylindrical portion (3), the hollow cylindrical portion having an inner space configured to receive an upstream end (5A) of the standpipe (5), the cylindrical portion (3) being linearly movable on the standpipe (5), wherein the cylindrical portion (3) and the standpipe (5) form a pump chamber having a variable volume for generating a pressure in the pump chamber by a linear relative movement of the cylindrical portion (3) relative to the standpipe (5), wherein the pump chamber is fluidically connected to the reservoir (2) and a nozzle (6), the nozzle being fluid-tightly connected to a downstream end (5B) of the standpipe (5),

[0156] - and wherein the linear relative movement can be achieved by relative rotation of a rotatable part (1A) relative to a mating part (1B) around a rotation axis (R), the rotatable part being part of a first part of the housing (1) or connected to the first part, the mating part being part of a second part of the housing (1) or connected to the second part, so that the relative rotation is converted into the linear relative movement by a gear mechanism, the gear mechanism comprising at least one cam surface, the cam surface having a first section (9A) with increased height and a second section (9B) with reduced height in an axial direction, the cam surface being able to slide along an adjacent mating surface, wherein the cam surface is adapted to slide along the mating surface when rotating, resulting in the conversion,

[0157] - and wherein a potential energy storage device (7) is provided, said device being capable of storing energy by said relative rotation along said first section (9A), and wherein said energy, when released, is capable of being released to said pumping device,

[0158] It is characterized in that the cam surface has a third section (9C) of constant height between the first section (9A) with increased height and the second section (9B) with reduced height, so that when the third section (9C) of the cam surface slides along the mating surface, no linear relative movement occurs.

[0159] 2. The inhalation device according to claim 1, wherein

[0160] - the cam surface is arranged on or connected to the rotatable part (1A), and the mating part (1B) provides the mating surface, or

[0161] - the cam surface is arranged on or connected to the counter part (1B), and the rotatable part (1A) provides the counter surface.

[0162] 3. Inhalation device according to item 1 or 2, wherein the counterface is provided by a second cam surface, or a cam (11), or a roller.

[0163] 4. An inhalation device according to any one of items 1 to 3, wherein the dosing cycle covering the rotation angle of the first, second and third sections (9A, 9B, 9C) corresponds to a rotation of 360 degrees, or an integer fraction thereof.

[0164] 5. The inhalation device according to item 4, wherein the sum of the rotation angles as described in item 4 is equal to 180 degrees.

[0165] 6. The inhalation device according to item 5, wherein the rotation angle of the third section (9C) reaches 7±6 degrees.

[0166] 7. Inhalation device according to any of the preceding items, wherein the rotation angle of the second section (9B) is equal to 0 degrees, resulting in an axially oriented section of the cam surface.

[0167] 8. An inhalation device according to any of the preceding items, wherein there is further a device for preventing actuation of the inhalation device, the device being suitable for suppressing changes in the relative axial position of the rotatable part (1A) and the mating part (1B) corresponding to the third section (9C).

[0168] 9. An inhalation device according to item 8, wherein the means for preventing actuation is adapted to, when it is deactivated,

[0169] - passively allowing further rotation, or actively further rotating said rotatable part (1A) so that said second section (9B) of said cam surface comes into contact with said counter-face, or

[0170] - allowing a previously prevented relative axial movement of said rotatable part (1A) with respect to said counterpart part (1B) corresponding to said second section (9B).

[0171] 10. Inhalation device according to any of the preceding items, wherein the slope of the first section (9A) is selected from constant, increasing, decreasing and combinations thereof.

[0172] 11. A method for producing an aerosol by means of an inhalation device according to any of the preceding items, wherein the method comprises, as the rotatable part (1A) rotates, a first filling phase for filling the pump chamber with liquid, and a second discharge phase for discharging the atomized liquid from the nozzle (6), characterised in that between the two phases there is a third stationary phase during which the volume of the pump chamber remains constant despite further rotation.

[0173] 12. The method according to claim 11, wherein one dosing cycle is achieved by a 180 degree rotation.

[0174] 13. A method according to item 11 or 12, wherein the entire stationary phase is a rotation of 7±6 degrees.

Claims

1. An inhalation device for producing an aerosol of a medically active liquid, comprising: - a housing (1), a reservoir (2) for storing a liquid in the housing (1), a pumping unit, the unit comprising a standpipe (5), a hollow cylindrical part (3), the hollow cylindrical part having an inner space configured to receive an upstream end (5A) of the standpipe (5), the hollow cylindrical part (3) being linearly movable on the standpipe (5), wherein the hollow cylindrical part (3) and the standpipe (5) form a pump chamber, the pump chamber having a variable volume for generating a pressure in the pump chamber by a linear relative movement of the hollow cylindrical part (3) relative to the standpipe (5), wherein - the pump chamber is in fluid connection with the reservoir (2) and a nozzle (6) which is fluid-tightly connected to the downstream end (5B) of the standpipe (5), and wherein - the linear relative movement can be achieved by relative rotation of the rotatable part (1A) relative to the mating part (1B) around the rotation axis (R), the rotatable part being part of the first part of the housing (1) or connected to the first part, the mating part being part of the second part of the housing (1) or connected to the second part, so that the relative rotation is converted into the linear relative movement by a gear mechanism, the gear mechanism comprising at least one cam surface, the cam surface comprising a first section (9A) with increased height and a second section (9B) with reduced height in the axial direction, the cam surface being able to slide along an adjacent mating surface, wherein the cam surface is suitable for sliding along the mating surface when rotating, resulting in the conversion, and wherein - a potential energy storage device (7) is provided, which is capable of storing energy by said relative rotation along said first section (9A), and wherein the potential energy can be released to said pumping unit when released, and wherein said cam surface comprises a third section (9C) of constant height between said first section (9A) of increasing height and said second section (9B) of decreasing height, so that when said third section (9C) of said cam surface slides along said mating surface, said hollow cylindrical part (3) does not undergo linear relative movement with respect to said standpipe (5), and wherein - A dosing cycle covering the rotation angle of said first, second and third sections (9A, 9B, 9C) corresponds to a rotation of 180 degrees.

2. An inhalation device according to claim 1, wherein - the cam surface is arranged on or connected to the rotatable part (1A), and the mating part (1B) provides the mating surface, or - the cam surface is arranged on or connected to the counter part (1B), and the rotatable part (1A) provides the counter surface.

3. An inhalation device according to claim 1 or 2, wherein the counterface is provided by a second cam surface, or a cam (11), or a rolling element, wherein At least a portion of the second cam surface has an inverse shape of the cam surface.

4. An inhalation device according to claim 1 or 2, wherein the rotation angle of the first section (9A) reaches 170 degrees.

5. Inhalation device according to claim 1 or 2, wherein the value of the rotation angle of the first section (9A) is in the range of 150 to 170 degrees.

6. Inhalation device according to claim 1 or 2, wherein the value of the rotation angle of the first section (9A) is in the range of 155 to 165 degrees.

7. Inhalation device according to claim 1 or 2, wherein the value of the rotation angle of the second section (9B) is in the range of 0 to 3 degrees.

8. Inhalation device according to claim 1 or 2, wherein the value of the rotation angle of the second section (9B) is in the range of 0 to 2 degrees.

9. Inhalation device according to claim 1 or 2, wherein the rotation angle of the second section (9B) has a value in the range of 0 to 1 degree.

10. Inhalation device according to claim 1 or 2, wherein the rotation angle of the third section (9C) has a value in the range of 1 to 13 degrees.

11. Inhalation device according to claim 1 or 2, wherein the rotation angle of the third section (9C) has a value in the range of 3 to 11 degrees.

12. Inhalation device according to claim 1 or 2, wherein the rotation angle of the third section (9C) has a value in the range of 5 to 9 degrees.

13. Inhalation device according to claim 1 or 2, wherein the rotation angle of the third section (9C) has a value in the range of 6 to 8 degrees.

14. An inhalation device according to claim 1 or 2, wherein the rotation angle of the first section (9A) is selected in the range from 165 degrees to 170 degrees, the rotation angle of the second section (9B) is selected in the range from 0 degrees to 2 degrees, and the rotation angle of the third section (9C) is selected in the range from 1 degree to 13 degrees, wherein the sum of the rotation angles of these sections adds up to 180 degrees.

15. An inhalation device according to claim 1 or 2, wherein the cam surface comprises a fourth section (9D) and / or a fifth section.

16. The inhalation device according to claim 15, wherein the fourth section (9D) is a section whose height decreases or increases between the third section (9C) and the second section (9B).

17. Inhalation device according to claim 15, wherein the fifth section is a section of constant height following the second section (9B).

18. Inhalation device according to claim 16, wherein the fifth section is a section of constant height following the second section (9B).

19. Inhalation device according to claim 1 or 2, wherein the rotation angle of the second section (9B) is equal to 0 degrees, resulting in an axially oriented section of the cam surface.

20. An inhalation device according to claim 1 or 2, wherein there is further present means for preventing actuation of the inhalation device, the means being adapted to inhibit changes in the relative axial position of the rotatable part (1A) and the mating part (1B) corresponding to the third section (9C).

21. An inhalation device according to claim 20, wherein the means for preventing actuation of the inhalation device is adapted to, when the inhalation device is deactivated, - passively allowing further rotation, or actively further rotating said rotatable part (1A) so that said second section (9B) of said cam surface comes into contact with said counter-face, or - allowing a previously prevented relative axial movement of said rotatable part (1A) with respect to said counterpart part (1B) corresponding to said second section (9B).

22. Inhalation device according to claim 1 or 2, wherein the slope of the first section (9A) is selected from constant, increasing, decreasing and combinations thereof.

23. A method for generating an aerosol by means of an inhalation device according to any one of claims 1 to 22, wherein the method comprises, as the rotatable part (1A) rotates, a first filling phase for filling the pump chamber with liquid, and a second discharge phase for discharging the atomized liquid from the nozzle (6), wherein between the first filling phase and the second discharge phase there is a third stationary phase during which the volume of the pump chamber remains constant despite further rotation, and One dosing cycle is achieved by a 180 degree rotation.

24. The method of claim 23, wherein the entire first filling stage is through a rotation of up to 170 degrees.

25. The method of claim 23, wherein the entire first filling stage is through a rotation of 150 to 170 degrees.

26. The method of claim 23 or 25, wherein the entire first filling stage is through a rotation of 155 to 165 degrees.

27. The method of claim 23 or 24, wherein the entire second discharge stage is through a rotation of 0 to 3 degrees.

28. The method of claim 23 or 24, wherein the entire second discharge stage is through a rotation of 0 to 2 degrees.

29. The method of claim 23 or 24, wherein the entire second discharge stage is through a rotation of 0 to 1 degree.

30. The method of claim 23 or 24, wherein the entire third stationary phase is over a rotation in the range of 1 to 13 degrees.

31. The method of claim 23 or 24, wherein the entire third stationary phase is over a rotation in the range of 3 to 11 degrees.

32. The method of claim 23 or 24, wherein the entire third stationary phase is over a rotation in the range of 5 to 9 degrees.

33. The method of claim 23 or 24, wherein the entire third stationary phase is over a rotation in the range of 6 to 8 degrees.

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