LIQUID DISPENSERS FOR NASAL APPLICATIONS AND PUMPING DEVICES

Description

[0001] The invention relates to a nasal dispenser for the nasal application of atomized liquids and to a pumping device particularly suitable for such a nasal dispenser.

[0002] Nasal dispensers are used to administer atomized liquid nasally through a patient's nostrils, particularly pharmaceutical liquids used to relieve respiratory symptoms associated with colds. The application of the atomized liquid in the form of a conical spray promotes the desired distribution of the liquid throughout the respiratory tract.

[0003] A spray of atomized liquid can be produced in various ways with nasal dispensers, for example, through a nozzle plate with numerous nozzle openings or by means of a swirl chamber in which the liquid is rapidly swirled before being dispensed. A dispensing opening is provided at the front of the swirl chamber, and the swirling liquid is broken up into fine droplets upon dispensing. The use of nasal dispensers that dispense liquid in atomized form is particularly common among adults. However, nasal drops are often perceived as easier to use for children, partly because children sometimes find the spray of atomized liquid unpleasant.EP3412325 A1 relates to a dispensing head for the nasal application of pharmaceutical liquid from a pressure accumulator, which has an outlet valve with a valve nozzle that can be acted upon against a spring force to open the outlet valve. TASK AND SOLUTION

[0004] The object of the invention is to provide a nasal dispenser for the nasal application of liquid in atomized form, the dispensing of which is perceived by children as less unpleasant.

[0005] To solve this problem, a nasal dispenser for the nasal application of liquids is proposed, particularly for use in children. It comprises, in the generic manner, a liquid reservoir for holding liquid prior to dispensing, as well as a slim nasal applicator for insertion into the nose and for dispensing the liquid in a dispensing direction. The nasal applicator is preferably part of a dispensing unit that is linearly displaceable relative to the liquid reservoir in an actuating direction, particularly parallel to the dispensing direction. When pressed down, a pumping device is actuated or a valve device is opened against the force of a return spring.

[0006] The nasal applicator comprises an outer component and an inner component. The outer component forms an outer surface visible to the user. The outer component comprises a slender applicator tip with a distal end wall, through which a discharge opening is formed, which is designed to deliver a spray jet in the discharge direction. The discharge direction preferably corresponds to the main extension direction of the slender applicator tip.

[0007] The slim applicator tip is preferably rotationally symmetrical, with this referring to the basic shape. A design in which a thread or other secondary holding structures for attaching a cap are provided on the outside, but which otherwise have a rotationally symmetrical shape, are also to be understood as rotationally symmetrical within the meaning of the invention. The slim shape is expressed in the fact that its length from a root area to the distal end is preferably twice, in particular at least 2.5 times as large as the outer diameter in the root area. The root area is formed by the point that is no longer inserted when inserted into the nostril. The length of the applicator tip from the root area to the distal end is preferably at least 15 mm.It is therefore particularly preferred that the applicator tip has a diameter of maximum 7.5 mm, preferably maximum 6 mm, at a distance of 15 mm from the distal end.

[0008] The inner component is inserted into the outer component. Together with the outer component, it defines a fluid path leading to the discharge opening, in particular a vortex chamber provided in this fluid path upstream of the discharge opening. Preferably, the vortex chamber is formed at least partially, and in particular predominantly, by a recess in the inner component. The inner component can additionally form a discharge channel connecting the vortex chamber to a pumping device. In other designs, the discharge channel is arranged between the inner component and the outer component.

[0009] At least one swirl-generating inlet channel opens into the vortex chamber, with preferably at least two such inlet channels being provided, which are opposite one another, or more than two inlet channels that open into the preferably rotationally symmetrical vortex chamber at a circumferentially distributed angle. The inlet channels are angled relative to a radial direction to allow the liquid to flow into the vortex chamber in such a way that it enters a rotating vortex motion.

[0010] The inlet channel(s) are preferably formed by recesses in the inner component or by openings in an inwardly facing web of the outer component. In the case of inlet channels formed by recesses in the inner component, it is preferred if these recesses have a shallower depth than the adjacent vortex chamber, which is also formed by a recess, in order to cause a flow separation when the liquid flows into the vortex chamber through the step created by the difference in depth.

[0011] To achieve a spray jet that is not perceived as unpleasant by children, it has proven advantageous to reduce the liquid flow, i.e., to reduce the amount of liquid dispensed through the dispensing opening per unit of time. The nasal dispenser is preferably designed such that, during normal operation, a liquid flow of less than 0.7 ml / second is achieved, preferably less than 0.6 ml / second. In contrast, conventional nasal dispensers for adults typically have a liquid flow of 1.0 ml / second or even 1.5 ml / second. Despite the reduced liquid flow, the components of the nasal dispenser must be designed to ensure the desired atomization.

[0012] A mere reduction of the liquid flow, for example by a throttle in the discharge channel upstream of the vortex chamber and the inlet channels, has proven to be not ideal, since the reduced pressure downstream of the throttle makes it difficult for the vortex chamber to form a fine atomization.

[0013] Two alternatives are proposed to achieve a child-friendly reduced liquid flow while maintaining good atomization.

[0014] A first alternative concerns a nasal applicator whose inner and outer components are arranged in a fixed position relative to each other, for example, by being firmly locked together by a snap connection. Together, they define the vortex chamber and circumferentially delimit the inlet channels into the vortex chamber.

[0015] In such a configuration, the invention proposes that the inlet channels, or at least one inlet channel, be designed to be particularly narrow. The cross-sectional area of ​​the inlet channel, oriented transversely to the flow direction, at its narrowest point, or in the case of a plurality of inlet channels, the sum of the cross-sectional areas of the inlet channels at their respective narrowest points, is only 0.05 mm², preferably even less, namely 0.04 mm² or less.

[0016] It has been found that such a constriction alone leads to a suitable reduction in the discharged liquid flow and to an acceleration of the liquid, resulting in strong atomization. The very fine inlet channels thus allow for reliable atomization with a reduced liquid flow. Furthermore, the inlet channels are particularly suitable as the narrowest point of a discharge channel, as they can be easily and precisely shaped to the desired cross-section by appropriately shaping the inner and outer components.

[0017] The at least one inlet channel preferably has a cross-section that tapers in the flow direction, so that the narrowest point, with a maximum clear cross-section of 0.05 mm2 according to the invention, is provided at an inlet into the vortex chamber. The velocity of the liquid therefore increases continuously as it flows in the flow direction toward the vortex chamber.

[0018] The size of the discharge opening is not crucial in the described design with very fine inlet channels, since in this case the inlet velocity of the liquid into the vortex chamber is primarily responsible for good atomization. It is therefore proposed to design the discharge opening relatively large. In the interests of easier production, the discharge opening should have a cross-sectional area at its narrowest point that is larger than the cross-sectional area of ​​the inlet channel or than the sum of the cross-sectional areas of the inlet channels. In particular, the discharge opening preferably has a cross-sectional area of ​​at least 0.06 mm², in particular of at least 0.08 mm², at its narrowest point.

[0019] In this first alternative, the inlet channels are formed circumferentially jointly by the outer component and the inner component. They are formed, so to speak, by a remaining gap that remains between an end face of the inner component and the inner side of the end wall of the outer component. In particular, recesses that form the inlet channels can be provided in an upper end face of the inner component, which rests against the inner end wall of the outer component. The inlet channels are formed by opposing channel walls of both components, the outer component and the inner component. The distance between these channel walls defines the channel height. The channel height is preferably less than 0.15 mm, more preferably less than 0.12 mm. This narrow gap can be created reliably and with little manufacturing effort by providing the aforementioned recesses of appropriate depth on the end face of the inner component.

[0020] The inlet channels are preferably provided with a greater width than height. In particular, the channel width, i.e., the extent of the cross-sectional area of ​​the respective inlet channel at its narrowest point transverse to the flow direction and transverse to the channel height, is preferably twice as large as the channel height. The channel width is preferably at least 0.15 mm, particularly preferably 0.18 mm or more.

[0021] The second alternative proposed here relates to a nasal applicator in which the inner component is movably arranged within the outer component. In particular, the inner component is arranged within the outer component so that it can be moved linearly, and is pushed away from the discharge opening, particularly by increasing the fluid pressure, against the force of a return spring.

[0022] In such a design with a movable inner component, it is difficult to design the inlet channels in such a way that they produce a reproducible throttling effect and thereby a reduced liquid flow and reliably atomize it, because in such a design the inner component and the outer component together limit the at least one inlet channel and the minimum cross section of the at least one inlet channel is variable due to the mobility.

[0023] For such a case with a movable internal component, the invention proposes designing the discharge opening in a special shape to exert a throttling effect while simultaneously achieving sufficient atomization. For this purpose, the discharge opening is designed with a particularly small cross-section, namely with a clear cross-sectional area at its narrowest point of a maximum of 0.05 mm², preferably a maximum of 0.04 mm². The discharge opening can, in particular, have a rotationally symmetrical shape.

[0024] It is therefore intended that atomization is not primarily influenced by influencing the velocity of the liquid as it flows into the vortex chamber, but rather by a particularly small discharge opening. This has been shown to also enable atomization and the generation of a conical spray jet at low liquid flow rates. This can be achieved, in particular, if the average diameter of the discharge opening is in a ratio of 1:3 to 1:5 to the maximum diameter of the pumping chamber.

[0025] The inlet channels can be provided, in particular, in a web surrounding the discharge opening on the inside. Depending on the relative position of the inner component, this can partially close the inlet channels in the manner of an internal aperture, thus creating the aforementioned variable cross-section.

[0026] The inner component and the outer component preferably jointly form a discharge valve. The inner component preferably has a closing piston which, in the end position, covers the at least one inlet channel in the web on the inside, thereby completely preventing any inflow of fluid from the inlet channel into the swirl chamber in an end position. Alternatively or additionally, it can be provided that the inner component and the outer component axially seal each other in an end position by having an end face of the inner component bear against the inside of the end wall of the outer component.

[0027] The manufacture of a small discharge opening proposed according to the invention, which penetrates a comparatively large external component, can be facilitated by the discharge opening having a cross-section that is non-uniform across the thickness of the end wall, i.e., not having the aforementioned small cross-section across the entire thickness of the end wall. Preferably, the discharge opening has a particularly conical or cylindrical recess on the inside or outside of the end wall, i.e., on the inlet or outlet side, which recess is, as it were, part of the discharge opening or represents a taper of the end wall. This recess makes it easier to achieve the desired precision of the discharge opening in an external component produced by plastic injection molding.

[0028] A nasal dispenser according to the invention dispenses pressurized liquid. One possible design provides for the liquid to be stored in a fluid reservoir designed as a pressure accumulator and released via a manually operated valve. However, it is preferred that the liquid be stored in the fluid reservoir without pressure and be pumped to the discharge opening by means of a pumping device.

[0029] In particular, a pumping device is preferably provided, which is connected to the liquid reservoir at an inlet side and to the discharge opening via a discharge channel. To actuate the pumping device, an actuating handle is provided, which can be moved between an unactuated end position and an actuated end position. This actuating handle is preferably fixed to the applicator tip and is pressed down together with the applicator tip relative to the liquid reservoir to convey liquid from a pumping chamber of the pumping device to the discharge opening.

[0030] The pumping device is preferably a piston pump with a cylinder wall and a piston sealing thereto, by means of which a pumping chamber volume can be varied. The pumping device has an inlet valve and an outlet valve on the inlet and outlet sides.

[0031] The outlet valve is preferably designed as a pressure-dependent outlet valve that opens when there is excess pressure in the pump chamber. In a design in which the inner component and the outer component are movable relative to each other and together form a discharge valve, this discharge valve can simultaneously serve as the outlet valve of the pumping device or be provided as an additional valve in addition to a separate outlet valve of the pumping device.

[0032] The inlet valve can also be a pressure-dependent valve, which opens when there is negative pressure in the pump chamber and thereby draws fluid from the fluid reservoir, particularly through a riser pipe. However, a travel-dependent inlet valve is preferred over a pressure-dependent inlet valve. This will be described below.

[0033] The pumping device is preferably designed to deliver a comparatively small amount of fluid per actuation, so that the dispensing is not unpleasant for a child. It is preferable that the nasal dispenser be used several times in succession for application into the same nostril of the child, rather than dispensing the desired amount of fluid completely with one actuation.

[0034] In particular, the pumping device can be designed to convey a quantity of liquid of less than 70 µl to the discharge opening when the actuating handle is moved from the unactuated end position to the actuated end position, in particular preferably less than 50 µl or even less than 30 µl.

[0035] It is particularly preferred, although not mandatory, that this small amount of fluid be delivered during an actuation from the unactuated end position to the actuated end position of at least 4 mm, in particular of at least 6 mm, whereby the actual delivery process only needs to take place during part of this actuation. The comparatively large actuation length facilitates operation and reduces the required actuation force.

[0036] As already explained at the beginning, it is preferred if the nasal dispenser is designed for a comparatively low liquid flow, i.e. in particular to achieve a dispensing rate with an average liquid flow of less than 0.7 ml / second. In a design with a pumping device, the pumping device and a discharge channel adjoining it up to the discharge opening are therefore preferably designed such that when actuated with a reference force of 25 Newtons, actuation from the unactuated end position to the actuated end position results in an average liquid flow of less than 0.7 ml / second, preferably to a liquid flow of less than 0.5 ml / second or less than 0.3 ml / second. This only takes into account the period in which dispensing takes place, i.e. when the outlet valve of the pumping device is open.

[0037] In addition to the nasal dispenser described, the invention also relates to a pumping device for a liquid dispenser, in particular a pumping device for use in a nasal dispenser of the type described above. Particularly preferred for a nasal dispenser of the type described is a pumping device that is suitable for dispensing a small and precisely metered amount of liquid.

[0038] To achieve this, the pumping device according to the invention comprises a pumping chamber formed by two pumping components that can move relative to one another, in particular a first pumping component that is part of the discharge unit, and a second pumping component that is part of a base that is fixed to the liquid reservoir. A displacement of the pumping components leads to a change in the volume of the pumping chamber.

[0039] The pumping device has an inlet valve and an outlet valve, which connect the pumping device to a liquid reservoir and a discharge opening, respectively. The outlet valve is preferably designed as a pressure-dependent outlet valve and can be identical to a discharge valve of the dispenser, which can be formed by the described internal component and the described external component.

[0040] The inlet valve of a pump device according to the invention, on the other hand, is designed as a path-dependent opening inlet valve. This means that the inlet valve is opened and closed in at least one defined relative position of the pump components. For this purpose, the inlet valve has a valve piston on the first pump component and a metering channel on the second pump component. When actuated from the starting position to the end position, the valve piston moves into the metering channel to close the inlet valve and thus effect discharge. The valve piston therefore lies in sealing contact with the inside of the metering channel. The valve piston and the metering channel are preferably dimensioned such that the valve piston can disengage from the metering channel again with its sealing surface at the opposite end, thus achieving a sudden end to discharge towards the end of the actuation.

[0041] Inlet valves that open depending on the travel are generally already known, but known valves of this type are designed for larger fluid flows. In order to design a pump device according to the invention of the type described with a metering channel and valve piston with a low delivery volume, it is considered preferred according to the invention if the pump device has a cylindrical pump chamber wall on the first pump component and a piston surface on the second pump component that rests on the inside against the cylindrical pump chamber wall, wherein this is structurally solved in such a way that a sleeve is provided on the second pump component that forms both the metering channel and the piston surface. The sleeve points into an inner region of the cylindrical pump chamber wall. The inside of the sleeve forms the metering channel.The piston surface is provided on the outside of the sleeve and / or at the distal end of the sleeve and is permanently in contact with the cylindrical pump chamber wall during operation.

[0042] This design allows the pump chamber to be designed with a very small cross-section, as the sleeve described above performs a dual function. Because it directly supports the piston surface, the cylindrical pump chamber wall can be designed with a cross-section only slightly larger than the metering channel. Accordingly, the delivery volume relative to the actuation distance is comparatively small.

[0043] In particular, it can be provided that the cross-sectional area of ​​the cylindrical pump chamber wall is between 10 mm 2< and 20 mm 2<, preferably between 10 mm 2< and 17 mm 2< . The cross-sectional area of ​​the dosing channel is preferably between 2 mm 2< and 5 mm 2<, in particular between 3 mm 2< and 4 mm 2<. The piston area of ​​the pump chamber effective for liquid delivery is preferably between 6 mm 2< and 15 mm 2<. In the case of an effective piston area of, for example, 10 mm 2<, a liquid quantity of 50 µl is discharged over a dosing distance of 5 mm.

[0044] The invention relates to a nasal dispenser of the type described, both in the unfilled state before filling and in the finished state for the end customer with filled liquid reservoir.

[0045] When filled, the liquid reservoir is preferably filled with a total liquid quantity of less than 50 ml, preferably less than 30 ml.

[0046] When filled, the dispenser contains a pharmaceutical liquid, which includes, in particular, saline aqueous solutions. In particular, the pharmaceutical liquid can also be a liquid with a decongestant effect, especially a liquid containing an imidazoline component, such as oxymetazoline. BRIEF DESCRIPTION OF THE DRAWINGS

[0047] Further advantages and aspects of the invention emerge from the claims and from the following description of preferred embodiments of the invention, which are explained below with reference to the figures. Fig. 1 and 2 show a first embodiment of a nasal dispenser according to the invention in uncut and cut representation. Fig. 3 to 5 show the discharge opening and the vortex chamber upstream of the discharge opening of the nasal dispenser of the Fig. 1 and 2 . Figs. 6 and 7show a second embodiment of a nasal dispenser according to the invention in uncut and cut representation. Fig. 8 to 10 show the discharge opening and the vortex chamber upstream of the discharge opening of the nasal dispenser of the Figs. 6 and 7 . DETAILED DESCRIPTION OF THE EMBODIMENTS

[0048] Fig. 1 to 5 illustrate a first embodiment of a nasal dispenser 10 according to the invention. Fig. 6 to 10 illustrate a second embodiment of a nasal dispenser 10 according to the invention.

[0049] Both nasal dispensers 10 have a liquid reservoir 12 to which a dispensing head 14 is attached. This dispensing head 14 has a base 16, which is connected to the liquid reservoir, for example, by means of a threaded or snap connection. The dispensing head 14 further has a dispensing unit 18, which is movably attached to the base 16 and can be pressed down toward the base 16 in an actuation direction 6. The dispensing unit 18 has a slender nasal applicator 40 in the form of an applicator tip 42 tapering toward a distal end, which is intended to be inserted into a nostril of a user. Furthermore, the dispensing unit has an actuation handle 44 in the form of a circumferential finger rest.

[0050] At the distal end of the applicator tip 42, a discharge opening 54 is provided, upstream of which is a vortex chamber 98. The discharge opening 54 is formed as a frontal opening of an outer component 50. The vortex chamber 98 is delimited by the inner side of an end wall 52 of this outer component and by an inner component 60.

[0051] The nasal dispensers each have a pumping device 70, which can be activated by depressing the discharge unit 18 relative to the liquid reservoir 12 and the base 16. The pumping device conveys liquid from the liquid reservoir 12 to the discharge opening 54, which flows through inlet channels 96 into the swirl chamber 98. By orienting the inlet channels 96 at an angle relative to a radial direction, the liquid is imparted a swirl as it enters the swirl chamber 98. The liquid entering the swirl chamber 98 therefore rotates at high speed in a clockwise or counterclockwise direction.

[0052] The rotating liquid reaches the end wall 52 and the discharge opening 54 provided therein. The swirl of the liquid causes the liquid emerging through the discharge opening 54 to be torn into a conical spray jet of fine individual droplets at a sufficiently high speed.

[0053] The Fig. 1 to 5 The nasal dispensers 10 shown in Figures 6 to 10 represent two designs of nasal dispensers 10 that differ in essential details and are intended especially for use with children. What these nasal dispensers 10 have in common is that they are specifically designed to generate a discharged liquid flow of only approximately 0.7 ml / second. This low liquid flow, together with a fine atomization, ensures that the discharge is not perceived as particularly unpleasant by children. Depending on how much the liquid flow is reduced, it can even be achieved that the discharge is barely noticeable to children.

[0054] In the case of the design of the Fig. 1 to 5It is provided that the discharge unit 18 and the nasal applicator 40 provided thereon are essentially formed by two components, namely the outer component 50 and the inner component 60. The liquid is conveyed to the discharge opening 54 by a pump device 70. The pump device 70 has an inlet valve 76 and an outlet valve 86. Beyond the outlet valve 86, the liquid flows towards the discharge opening 54 through a channel 87, which is partially surrounded by the inner component 60. At the end of this channel 87, the liquid enters through radial openings into an end-side channel section 88, which is jointly delimited by the inner component 60 and the outer component 50. The liquid flows through this channel section 88 to two inlet channels 96.

[0055] The inlet channels 96 are, as in particular the Fig. 3 can be seen, is limited by opposing channel walls 96A, 96B, wherein the Fig. 3 shown upper channel wall 96A is formed by the inside of the end wall 52 of the outer component 50 and wherein the Fig. 3 shown lower channel wall 96B is formed by the end face 64 of the inner component 60.

[0056] The end face 64 of the inner component 60 is in particular the Fig. 5 The end face is formed with a central recess with a depth of, for example, 0.2 mm, which, together with the end wall 52, forms the vortex chamber 98. The inlet channels 96 are primarily formed by two further recesses that have a smaller depth of, for example, 0.1 mm, so that fluid flowing through them flows over a step into the vortex chamber 98, thereby causing a clean flow separation.

[0057] The inlet channels are tapered relative to a flow direction 4. They have their narrowest cross-section immediately before the junction with the vortex chamber 98. There, the width of the inlet channels transverse to the flow direction 4 is 0.2 mm. The total cross-section of each of the two inlet channels is therefore 0.02 mm 2< , in total as 0.04 mm 2< , as can be seen from the Fig. 5 shown enlarged area can be seen

[0058] The discharge opening 54 is larger than the sum of the cross-sections of the inlet channels, so that the inlet channels represent the narrowest point between the pumping device 70 and the liquid outlet. The discharge opening is preferably rotationally symmetrical and has a diameter of at least 0.25 mm and preferably at least 0.3 mm at its narrowest point, i.e., a smallest clear cross-section of at least approximately 0.05 mm 2 and preferably at least approximately 0.1 mm 2 .

[0059] The very narrow inlet channels 96, in combination with the step at the transition between the inlet channels 96 and the vortex chamber 98, cause the liquid to flow in at high speed with little disruption. At the same time, the narrow inlet channels 96 reduce the liquid flow achieved at normal actuation speed, preferably to approximately 0.3 ml / second. Despite this reduced liquid flow, the high velocity of the liquid as it flows into the vortex chamber 98 results in very good atomization. The diameter of the discharge opening 54 is therefore hardly important. In the embodiment shown here, the diameter of the discharge opening 54 is approximately 0.3 mm. However, larger diameters would also be possible, since the advantageous atomization in this design is primarily ensured by the inlet channels 96.

[0060] In the case of the design of the Fig. 6 to 10It is provided that the outer component 50 and the inner component 60 are movable relative to each other and together form a discharge valve 90. As can be seen from the Fig. 8 to 10 and in particular based on Fig. 9As can be seen, a circumferential web 56 is provided on the inside of the end wall 52, which is interrupted by slots which, together with the inner component 60, form the inlet channels 96. The inner component 60 forms, with its distal end, a closing piston 62 which is movable relative to the web 56. If no liquid pressure is applied, the discharge valve 90 is closed. In this state, the closing piston is engaged so far into the web 56 that the slots there are completely covered and thus no liquid can flow into the swirl chamber 98 delimited by the web and the closing piston. If liquid is pressurized by means of the pump device 70 of the nasal dispenser 10, the liquid pressure pushes the inner component 60 away from the discharge opening 54 against the force of a valve spring 92, so that the swirl chamber 98 is enlarged and access for the liquid is opened through the inlet channels 96.

[0061] Since the opening of the inlet channels is not well suited as a constriction to achieve a reproducible throttling effect due to the pressure dependence of the opening, the design of the Fig. 6 to 10 In contrast, the discharge opening 54 is designed to be very small. It has been shown that this also allows for a low liquid flow and the desired atomization.

[0062] The discharge opening 54 therefore has a cross-sectional area of ​​0.04 mm 2 or less at its narrowest point. Particularly preferably, the discharge opening is rotationally symmetrical and configured with a smallest diameter of 0.2 mm and, accordingly, a cross-sectional area of ​​less than 0.035 mm 2 .

[0063] To facilitate the production of a discharge opening that is so fine at its narrowest point, it is provided that the end wall 52 has depressions 58 on the inside and / or outside in the region of the discharge opening. The maximum thickness of the end wall of approximately 0.5 mm to 0.8 mm is thus reduced in the region of the discharge opening by the depressions 58, preferably to a thickness of between 0.2 mm and 0.4 mm. This thickness of preferably between 0.2 mm and 0.4 mm is further preferably penetrated by a cylindrical section of the discharge opening 54, which section consistently has the aforementioned small cross-sectional area of ​​less than 0.04 mm 2<, preferably less than 0.035 mm 2<.

[0064] The vortex chamber 98 preferably has a maximum diameter that is approximately four to eight times the diameter of the discharge opening 54 and is therefore particularly preferably between 0.8 mm and 2.0 mm, in particular between 0.8 mm and 1.2 mm. The vortex chamber 98 preferably merges into the cylindrical section of the discharge opening 54 via a conically narrowed region, in particular formed by the aforementioned inner recess.

[0065] When the nasal dispenser 10 is activated by pushing down the discharge unit 18, the Fig. 10 The inlet channels 96 are pressure-dependent, as the closing piston 62 is spaced apart from the discharge opening. The liquid flows into the swirl chamber 98 and is discharged through the very narrow discharge opening 54. Although the inlet channels are significantly larger than in the design of the Fig. 1 to 5Due to the narrow discharge opening 54, a considerable actuation resistance and the desired atomization are achieved with a low liquid flow of less than 0.3 ml / second.

[0066] In addition to the design of the nasal dispenser 10 of the Fig. 6 to 10 With regard to the vortex chamber 8 and the discharge opening 54, the pumping device 70 is designed in a special way. The pumping device has an inlet valve 76 and an outlet valve 90. The outlet valve 90 is identical to the previously mentioned discharge valve 90. However, designs with two independent valves downstream of the pumping chamber 72 of the pumping device 70 are also possible.

[0067] The inlet valve 76 differs from the design of the Fig. 1 bis5 no pressure-dependent opening inlet valve, but a path-dependent opening one.

[0068] It comprises a first pump component 74A, which is part of the displaceable discharge unit 18 and is firmly connected to the outer component 50, including the inner component 60. This first pump component 74A has a central valve piston 77 and a circumferential web surrounding this valve piston 77, the inside of which forms a pump chamber wall 80.

[0069] A second pump component 74B is part of the base 16. This second pump component 74B has a central sleeve 84 that performs the following functions: The sleeve 84 is penetrated by an inlet channel 85, wherein a section of the inlet channel 85 with a small cross-section forms a metering channel 78. This metering channel is designed such that the valve piston 77 of the first pump chamber component, when arranged in the metering channel, thereby closes the inlet channel 85 and interrupts the communicating connection between the pump chamber 72 and the liquid reservoir 12.

[0070] The sleeve 84 also supports a piston surface 82, which is provided at the distal end of the sleeve and defines the maximum sleeve diameter. The piston surface 82 rests against the pump chamber wall 80.

[0071] If the discharge unit 18 is now depressed, the liquid is initially forced from the pump chamber 72 through the still open inlet channel 85 back into the liquid reservoir 20 until the valve piston 77 enters the metering channel 78. The backflow is now interrupted, and continued depression of the discharge unit 18 causes an increase in pressure in the pump chamber 72 and, accordingly, an opening of the outlet and discharge valve 90. This discharge takes place over an actuation distance of 5 mm, which is determined by the length of the metering channel 78. As soon as the valve piston 77 emerges from the metering channel 78 at the lower end, the communicating connection between the pump chamber 72 and the liquid reservoir 12 is re-established. The excess pressure in the pump chamber is discharged into the liquid reservoir 12, and the discharge and outlet valve 90 closes.

[0072] During discharge, i.e. during the period between the closing of the inlet valve 76 and the opening of the inlet valve 76, the liquid is pumped from the pump chamber 72 in the direction of the discharge opening 54.

[0073] Because the sleeve 84 performs a dual function and itself supports the piston surface 82, a pump chamber with a very small diameter is achievable. In this case, the diameter of the cylindrical pump chamber wall is 4 mm, and the cross-sectional area is thus approximately 12.5 mm 2 . The effective piston area, taking into account the valve piston 77, is even somewhat smaller and is approximately 7 mm 2 to 10 mm 2 , in this case 8 mm 2 . Accordingly, 40 µl of liquid are pumped and discharged over the 5 mm dosing distance.

[0074] The geometry of the fluid path from the pump chamber 72 to the discharge opening 54 ensures that, with a reference actuation force of 25 Newtons, the discharge occurs over a period of approximately 0.15 seconds, i.e., with an average fluid flow of 0.27 ml / second. This results in a soft spray jet that is almost imperceptible in the nose and is not perceived as particularly unpleasant by children.

Claims

1. Nasal dispenser (10) for the nasal application of liquids in atomized form, in particular for the nasal application of liquids for children, comprising the following features: a. the nasal dispenser (10) has a liquid reservoir (12) for receiving liquid be fore it is discharged, and b. the nasal dispenser (10) has a nasal applicator (40) for discharging the liq uid, and c. an outer component (50) of the nasal applicator (40) has a slender applica tor tip (42) with a distal end wall (52), through which passes an outlet open ing (54) designed to discharge a spray jet in a discharge direction (2), and d. an inner component (60) of the nasal applicator (40) is inserted in the outer component (50), and e. the outer component (50) and the inner component (60) together delimit a vortex chamber (98) upstream of the outlet opening (54), wherein at least one swirl-imparting inlet channel (96) emerging into the vortex chamber (98) is provided, characterized by one of the following further features: f. the inner component (60) and the outer component (50) are arranged in a fixed position in relation to one another and together circumferentially de limit the at least one inlet channel (96), wherein the cross-sectional area, aligned transversely to the flow direction (4) in the inlet channel, of the inlet channel (96) at its narrowest point, or the sum of the cross-sectional areas, aligned transversely to the flow direction (4) in the inlet channels (96), of the inlet channels at their respective narrowest points, is at most 0.05 mm2, preferably at most 0.04 mm2, or g. the inner component (60) is arranged movably in the outer component (50) and the inner component (60) and the outer component (50) together de limit the at least one inlet channel (96), with the result that the cross section of the at least one inlet channel (96) can be varied by virtue of the movabil ity of the inner component (60) with respect to the outer component (50), and the outlet opening (54) at its narrowest point has a cross-sectional area of at most 0.05 mm 2, preferably at most 0.04 mm 2.

2. Nasal dispenser (10) according to Claim 1, comprising the following further features: a. the inner component (60) and the outer component (50) are arranged in a fixed position in relation to one another, and b. the outlet opening (54) at its narrowest point has a cross-sectional area which is greater than the cross-sectional area of the inlet channel (96), or than the sum of the cross-sectional areas of the inlet channels (96).

3. Nasal dispenser (10) according to Claim 2, comprising the following further features: a. the outlet opening (54) at its narrowest point has a cross-sectional area of at least 0.06 mm 2. preferably comprising the following additional feature: b. the outlet opening (54) at its narrowest point has a cross-sectional area of at least 0.08 mm 2.

4. Nasal dispenser (10) according to one of Claims 1 to 3, comprising the following further features: a. the inner component (60) and the outer component (50) are arranged in a fixed position in relation to one another, and b. the at least one inlet channel (96) at its narrowest point is configured such that two opposite channel walls (96A, 96B) of the inlet channel (96), one of which is formed by the inner component (60) and one of which is formed by the outer component (50), define a channel height of less than 0.15 mm, preferably less than 0.12 mm, preferably comprising the following additional feature: c. transversely in relation to the channel height, the at least one inlet channel (96) at the narrowest cross section has a channel width which is greater than the channel height and preferably is at least twice as wide as the channel height, the channel width being preferably at least 0.15 mm, in par ticular preferably 0.18 mm or more.

5. Nasal dispenser (10) according to one of Claims 1 to 4, comprising the following further features: a. the inner component (60) and the outer component (50) are arranged in a fixed position in relation to one another, and b. the vortex chamber (98) is formed by a depression in the inner component (60), wherein the at least one inlet channel (96) is formed by a further de pression in the inner component (60) with a smaller depth.

6. Nasal dispenser (10) according to Claim 1, comprising the following further features: a. the inner component (60) is arranged movably in the outer component (50), and b. the inner component (60) and the outer component (50) can be displaced into an end position in which an inflow into the vortex chamber (98) is pre vented, preferably comprising the following additional feature: c. the inner component (60) and the outer component (50) together form an outlet valve that can be switched by means of liquid pressure.

7. Nasal dispenser (10) according to Claim 1 or 6, comprising the following further features: a. the inner component (60) is arranged movably in the outer component (50), and b. the outer component (50) has, on the inner side of the end wall (52), a flange (56) which surrounds the outlet opening (54) and through which at least one inlet channel (96) passes, and c. the inner component (60) has a closing piston (62), which in the end posi tion covers the at least one inlet channel (96) on the inside and as a result prevents liquid from flowing from the inlet channel (96) into the vortex chamber (98) or in the end position bears against the inner side of the end wall (52) of the outer component (50) by way of an end face (64).

8. Nasal dispenser (10) according to Claim 1, 6 or 7, comprising the following further features: a. the inner component (60) is arranged movably in the outer component (50), and b. the outlet opening (54) has a cross section which varies in the discharge direction (2) from an inner side of the end wall (52) to an outer side of the end wall (52), wherein a depression with a cross-sectional area which is greater than the narrowest point of the outlet opening (54), in particular a cylindrical and / or a conical depression (58), is formed on the inner side and / or the outer side.

9. Nasal dispenser (10) according to one of the preceding claims, comprising the following further feature: a. the applicator tip (42) has a rotationally symmetrical form and tapers to wards the distal end, its length from a root region to the distal end being at least twice the outside diameter in the root region, preferably comprising the following additional feature: b. the length of the applicator tip (42) from the root region (42A) to the distal end (42B) is at least 15 mm.

10. Nasal dispenser (10) according to one of the preceding claims, comprising the following further features: a. the nasal dispenser (10) has a pump device (70), which is connected to the liquid reservoir (12) by way of an inlet side and is connected to the outlet opening (54) via an outlet channel, and b. an actuator (44) which can be displaced between an unactuated end posi tion and an actuated end position is provided for actuating the pump device (70), and c. the pump device (70) is designed such that, when the actuator (44) is dis placed from the unactuated end position to the actuated end position, an amount of liquid of less than 70 µl is delivered to the at least one outlet opening (54). preferably comprising at least one of the following features: d. the pump device (70) is designed such that, when the actuator (44) is dis placed from the unactuated end position to the actuated end position, an amount of liquid of less than 50 µl, in particular less than 30 µl, is delivered to the at least one outlet opening (54), and / or e. the unactuated end position and the actuated end position are spaced apart from one another by at least 4 mm, preferably at least 6 mm, and / or f. the pump device (70) is in the form of a plunger pump with a pump cylinder and a pump plunger, which can be displaced therein to reduce a pump chamber volume, and / or g. the pump device (70) is designed according to either of Claims 14 and 15.

11. Nasal dispenser (10) according to Claim 10, comprising the following further feature: a. the pump device (70) and the outlet channel to the outlet opening (54) are designed such that, when an actuating force of 25 newtons is applied, the actuation from the unactuated end position to the actuated end position leads to an average flow of liquid of less than 0.7 ml / second.

12. Nasal dispenser (10) according to one of the preceding claims, comprising the following further feature: a. the nasal applicator (40) is part of a discharge unit (18) which can be dis placed with respect to the liquid reservoir (12) linearly in an actuation direc tion (6) parallel to the discharge direction (2).

13. Nasal dispenser (10) according to one of the preceding claims, comprising at least one of the following further features: a. a plurality of inlet channels (96), preferably two opposite inlet channels (96), are provided, and / or b. the vortex chamber (98) has a rotationally symmetrical inner contour, and / or c. the vortex chamber (98) is formed by a depression in the inner component (60), wherein the at least one inlet channel (96) is preferably formed by a further depression in the inner component (60) with a smaller depth, and / or d. the at least one inlet channel (96) has a cross section which tapers in the flow direction (4), with the result that the narrowest point is provided at an opening into the vortex chamber (98).

14. Pump device (70) for a liquid dispenser, in particular a liquid dispenser according to one of the preceding claims, comprising the following features: a. the pump device (70) has a pump chamber (72) formed by two pump com ponents (74A, 74B) which are movable relative to one another, and b. the pump device (70) has an inlet valve (76) and an outlet valve (90), which connect the pump device (70) to a liquid reservoir (12) and an outlet open ing (54), and c. the outlet valve (90) is in the form of a pressure-dependently opening outlet valve (90), and d. the inlet valve (76) has a valve piston (77) on the first pump component (74A) and a metering channel (78) on the second pump component (74B), which the valve piston (77) enters to close the inlet valve (76) when the pump is being actuated, characterized by the following further features: e. the pump device (70) has a cylindrical pump chamber wall (80) on the first pump component (74A), and f. the pump device (70) has a piston surface (82) which bears against the in ner side of the cylindrical pump chamber wall (80), and g. a sleeve (84), which projects into an inner region of the cylindrical pump chamber wall (80) and the inner side of which forms the metering channel (78) and on the outer side of which and / or at the distal end of which the pis ton surface (82) is provided, is provided on the second pump component (74B).

15. Pump device (70) according to Claim 14, comprising the following further feature: a. the cross-sectional area of the cylindrical pump chamber wall (80) is be tween 10 mm2 and 20 mm2, preferably between 10 mm2 and 17 mm2, preferably comprising the following additional feature: b. the cross-sectional area of the metering channel (78) is between 2 mm2 and 5 mm2, preferably between 3 mm2 and 4 mm2.