Patent Grant
9192734
The present invention relates to a high pressure chamber which is made up of a plurality of individual parts and is operated by liquid.
It is known that in most medical procedures in which liquids are administered to a patient's body or are conveyed inside technical medical equipment, very low pressures are used, for example when setting up infusions or in medical procedures in which blood or other physiological liquids are circulated. Conventional dispensing systems for cosmetics or medical pressurised gas atomisers also generally operate at below 7 bar of liquid pressure, very rarely up to 20 bar. High pressure pumping systems, on the other hand, are generally known from various industrial applications but are not really suitable for use in technical medical equipment as they are often made of materials that are not compatible with the particular medical active substances or may even release substances that are toxic to the patients. Often, with technical medical components, it is essential that they are sterilizable. Because of the hygiene requirements imposed, components for medical equipment are generally designed for brief periods of use or even single use, so that in this field the demands for mass production are significantly increased. Moreover, industrial pumping systems are often of a mechanically complex nature so that it is difficult to reduce them to the size of handheld medical equipment, in particular.
In the treatment of lung diseases, in the meantime, the use of portable handheld equipment has become indispensable. Using such equipment therapies can be given daily, even at a distance from the practice of the doctor providing the treatment, and in this way a patient can always have access to an essential emergency medication for inhalation.
When a liquid medicament formulation is nebulised a precisely metered amount of active substance is intended to be converted into an aerosol for inhalation. The aerosol should have a small average particle size with a small droplet size distribution. In order to achieve this using nozzle pump arrangements without the use of propellants, pressures of 100-1200 bar are required in the associated pump chambers, with high demands on the leak-tight construction of the system.
By the term “medicament formulation” is meant, in the present invention, apart from medicaments, therapeutic agents or the like, particularly every kind of agent for inhalation or other forms of administration.
However, the invention is not restricted to medical nebulisation but may be used across different sectors for dispensing all kinds of liquids under pressure, for example when dispensing measured amounts of liquid in injectors, spray systems and other dispensing systems and in systems in which jets of liquid under high pressure are used (e.g. in cutting systems), even though the description that follows is directed primarily to medical applications and the preferred nebulisation of a medicament formulation for inhalation. Moreover, high pressure chambers of this kind and the manufacturing techniques associated with them may be used in totally different industrial fields such as the motor industry, for example, although this invention relates primarily to pumping situations in which particularly clean handling of the liquid in question is essential, as for example in medical technology in the pharmaceutical industry or food technology.
WO 91/14468 A1 and WO 97/12687 A1 describe nebulisers or miniaturised high pressure nebulisers. These comprise as the reservoir for a medicament preparation that is to be nebulised an insertable rigid container with an inner bag and a manually operated pressure generator with a drive spring for conveying and nebulising the medicament preparation. A container of this kind, as disclosed in WO 96/06011 A1 and WO 00/49988 A2, holds a volume of about 2-10 ml. An alternative nebuliser to those mentioned above has become known from the prior art in the meantime and is shown by way of example in
The components used for the pump chamber are subject to particular requirements regarding the strength of the material. Often, they cannot be made of the comparatively cheap plastics that are otherwise conventional for mass produced components in medical technology. The retaining elements described are typically metal components manufactured on lathes.
US 2002/0176788 shows, inter alia, a high pressure pump body the wall of which consists of thin walled tubing and in which the strength-determining components are not screwed together but joined to connecting elements by means of a crimped sealing bead. An outlet valve with sealing elements is inserted in the thin walled tubing. The tubing is pressed into a suitable recess in the valve unit so as to engage in a positively locking manner. When the high pressure envisaged is reached in the high pressure pumping body the corresponding valve opens and allows the liquid to flow continuously to the pump outlet.
The problem on which the present invention is based is to provide a high pressure chamber with an integrated outlet nozzle, particularly for medical nebuliser or injector systems, which is suitable for industrial manufacture. Systems of this kind deliver a metered amount of liquid in short pulses. The liquid is sucked in without the use of pressure and within a short time is brought to a peak pressure in the high pressure chamber at which the liquid is dispensed (preferably directly) through a nozzle. The sealing requirements for a pulsed system of this kind have not only static but also dynamic aspects compared with continuous pumping, which means that the connecting technology, particularly between the high pressure chamber and the outlet nozzle, is subject to particular demands.
By the term high pressure chamber is meant here a chamber that is substantially circular cylindrical on the inside, in which a fluid is put under pressure and expelled by the advancing of a piston or plunger.
This problem is solved according to the invention by a high pressure chamber in the form of a piston pump chamber made up of a plurality of components. The high pressure chamber has an inlet valve and an outlet nozzle. In the high pressure chamber a liquid is placed under high pressure and expelled through the outlet nozzle by means of an axially movable piston. At least one component consists of a metal component which is deformable and/or capable of being crimped and/or flanged and/or squeezed. The at least one component is connected to at least one other component of the chamber by positive locking, frictional locking and so as to be non-releasable. Advantageous further features are described hereinafter and in detail by reference to the figures.
The subject matter of the present invention relates to high pressure chambers for technical medical applications, such as for example in the nebulisation of liquid medicament formulations for administration into a patient's lungs or for injection into a patient's body.
As well as pure liquids and solutions the term “liquid” additionally encompasses dispersions, suspensions, suslutions (mixtures of solutions and suspensions) or the like. In particular, it relates to the aggregate state of the contents of the high pressure chamber during use.
One feature of the present invention is to configure the geometry of strength-determining components, for example, using special manufacturing processes described hereinafter, such that some components contain elements with which these components are joined to other components. These connecting elements may preferably be embodied as arms, strips, zig-zag rings (as in crown corks) or in other forms. The connecting elements are deformed or bent, preferably crimped, when two components are positively locked to one another. Preferably, a crimpable material is chosen for the component which is ductile and sufficiently deformable in the deformation range in the various geometries. A preferred material is one that solidifies in the deformed range after mechanical deformation. Joining components together by crimping enables the components to be assembled faster in comparison with screw connections, for example. Moreover, crimped joints are less prone to failure than screw connections in terms of their positional tolerances. Crimped joints are very robust and can be subjected to internal pressures of up to 5000 bar.
The strength-determining components of the high pressure chamber are preferably joined together at the end of the assembly process by crimping. This produces a component unit in which all the functional components of the system, such as for example, sealing elements, filter elements and nozzles, are enclosed.
The high pressure chamber described here is highly suitable for incorporation in handheld medical equipment by virtue of its very compact construction.
Another feature of the present invention is that metal components produced by metal injection moulding methods (MIM technology) are used as strength-determining components in high pressure chambers. The abbreviation MIM stands for metal injection moulding. The MIM process is a metal injection moulding process in which a metal powder (any of the known powdered metals and alloys may be used) is moulded with a binder, e.g. polyolefin, in the injection moulding process to produce the desired component and is then treated at different temperatures in a number of process steps. First the binder is removed from the component and then the component is hardened by sintering. As a rule, in the MIM process, metal powders with particle sizes of less than 30 microns and a median particle size distribution of 6-7 microns are used. This method can be used to produce components in mass production quantities on an economic scale. These components can be used without any further machining, e.g. on lathes. The geometry of the sintered metal components can be varied in numerous ways compared with conventionally manufactured metal components; thus the geometry of the sintered metal components is not restricted to rotationally symmetrical shapes, for example. In addition, by a suitable choice of starting powder, it is possible particularly to use corrosion resistant materials for the components, thus increasing the robustness of the system.
In a further feature of the present invention, plastic elements or plastic coatings are applied directly to strength-determining components of the high pressure chamber (preferably before reshaping or joining together). This can be achieved by a combination of manufacturing processes, for example using a component made of sintered metal as an insert in a plastics injection moulding process or a coating process (in the course of the plastics injection moulding process a further process insert is referred to as an “injection coated part”, irrespective of the degree of surface coverage with plastics, but, in order to include other coating processes in the terminology, the term “base member” is used here). Similarly, metal components from other manufacturing or structuring processes may be used. In this way, different requirements of performance and function may advantageously be met with a single component.
The injection-coated metal components or base members have the rigidity needed for high pressure applications. By coating with plastics or attachment of plastics elements, depending on the position and contact with liquid and the choice of material, elastic sealing elements as well as pharmaceutical compatibility and corrosion proofing of the components can be achieved. Preferably all the surfaces of the components that are in direct contact with the liquid, i.e. particularly the surfaces inside the high pressure chamber, are coated, e.g. with polypropylene. This achieves compatibility between the component and active substance, in the case of sensitive active substances. Instead of polypropylene, depending on the desired effect, it is possible to coat elements or injection-coat the metal component with a plurality of standard commercial plastics selected from among the thermoplasts, duroplasts or elastomers.
Lining the interior of a sintered metal component with plastics, when it is used as a component of a pulse-operated high pressure chamber, has the further advantage that, depending on the choice of the metal powder for the injection moulding process, any open pores remaining in the sintered components are sealed and the surface is smoothed. In this way, even with coarse powders, it is possible to avoid increasing the inner volume of the high pressure chamber and hence the dead volume by pores in the surface of the sintered metal. The smaller the dead volume in a pumping system, the shorter the start-up phase of the system (in the description of a nebuliser this start-up phase is referred to hereinafter as priming) and the more accurate the metering of the liquid in pulsed systems.
The individual features of the present invention may be used largely independently of one another and/or combined with one another substantially as desired.
Further features and properties of the present invention will be explained in more detail in the description that follows and by reference to the drawings. In the drawings:
a shows the base member of a component (nozzle holder) of the high pressure chamber from
b shows the same base member from
The strength-determining components of this pressure chamber are a central part (23) which is substantially cylindrical in its interior, for example made of a solid plastic such as, preferably, PEEK, a support ring (25) screwed to this central part (23) in the upstream direction by a first check nut (26) and a nozzle holder (32) screwed to the central part (23) on the downstream side by second check nuts (33). These strength-determining components in the assembled state include a number of functional components, various seals, filters and nozzles, which will be explained hereinafter.
When the liquid (2) is nebulised, an aerosol (14) is formed (
After the nebuliser (1) has been opened, the container (3) holding the liquid (2) can be inserted in the nebuliser (1) from below or put in as a replacement. The container (3) forms a reservoir for the liquid (2) that is to be nebulised. Preferably, the container (3) contains sufficient liquid (2) for several doses of the liquid (2), for example up to 200 dosage units (doses) for up to 200 nebulisations or applications.
The nebuliser (1) further comprises a conveying device, particularly a pressure generator (5), for conveying and nebulising the liquid (2), in each case in a predetermined, optionally adjustable dosage quantity.
The nebuliser (1) comprises in particular a holder (6) for the container (3), an associated drive spring (7), only partly shown, preferably having a locking element (8) which can be manually actuated to release it, a hollow piston (9) embodied as a capillary, with a valve, particularly a non-return valve (10), a pressure chamber (11) and discharge nozzle (12) in the region of a mouthpiece (13). The non-return valve (10) preferably comprises a valve body which is movable in an axially restricted manner in a corresponding end recess in the hollow piston (9). In particular, the valve body is provided with a recess, groove or the like to the side and/or at the end (of the pressure chamber (11)) so that when the non-return valve (10) is opened the liquid (2) can flow around it, even if the valve body towards the pressure chamber abuts on an axial abutment of the hollow piston (9) with the non-return valve (10) open.
The container (3) is fixed in the nebuliser (1) by means of the holder 6, particularly by a locking or latching action, such that the lower end of the hollow piston (9) dips into the container (3). The holder (6) may be constructed so that the container (3) can be exchanged.
When the drive spring (7) is axially tensioned, the holder (6) with the container (3) and the hollow piston (9) is moved downwards and a dose of the liquid (2) is sucked out of the container (3) into the pressure chamber (11) of the pressure generator (5) past the non-return valve (10).
During the subsequent relaxation after the actuation of the locking element (8) the dose of liquid in the pressure chamber (11) is put under pressure by the hollow piston (9) being moved back up, with the non-return valve (10) now closed, by the release of the drive spring (7), causing it to act as a pressure piston. This pressure expels the liquid in the pressure chamber (11) out through the discharge nozzle (12), during which time it is nebulised into the preferably lung-bound aerosol (14) as shown in
The user (not shown) can inhale the aerosol (14), while preferably supply air is sucked into the mouthpiece (13) through at least one supply air opening (15).
During the nebulisation process the container (3) is moved back into its original position by the drive spring (7). It thus performs a lifting movement during the tensioning process and during the nebulisation process.
The nebuliser (1) comprises an upper housing part (16) and an inner housing part (17) which is rotatable relative thereto (
The lower housing part (18) can be rotated relative to the upper housing part (16), whereby the inner part (17) is also rotated. In this way, the drive spring (7) is tensioned in the axial direction by means of a gear (not shown) acting on the holder (6). During tensioning the container (3) is moved axially downwards and with its end portion further into the lower housing part (18) as far as the end face thereof, until the container (3) assumes the end position shown in
When tensioning first takes place, the container (3) is pierced in its base and thereby vented. An axially acting spring (20) arranged in the lower housing part (18) comes to abut on the container base (21), while the piercing element (22) mounted on the spring (20) pierces the container (3) or a seal provided in the base when contact is first made. This opens only the outer shell of the container (3), while the inner bag (4) containing the liquid (2) is not pierced. The inner volume of the bag (4) is opened by means of the hollow piston 9 which penetrates a seal at the top of the container (3) when the container (4) is inserted in the inner housing part (17), and is then inserted through a septum at the top of the container into the interior of the bag. In this way, the bag (4) in the container (3) is fluidically connected to the pressure chamber (11) via the hollow piston (9). Before the first use, after the fluidic attachment of the bag (4), the nebuliser (1) is tensioned and released several times. This process, referred to as “priming”, causes the air present in the hollow piston (9) and in the pressure generator (5) up to the discharge nozzle (12) to be displaced by the liquid and the nebuliser (1) is ready for use in the intended manner. When liquid is subsequently taken out of the bag (4) through the hollow piston (9), the flexible bag (4) collapses. In order to equalise the pressure in the container (3), ambient air can flow through the vent opening into the container (3), so that the same pressure conditions are always present when the liquid (2) is being conveyed.
The pressure generator (5) has a tubular central part (23) provided with a longitudinal bore that forms the pressure chamber (11). The hollow piston (9) projects into the pressure chamber (11). It is sealed with the first seal (24) which is held by a support ring (25) and a first check nut (26) in a corresponding recess at the container end of the central part (23). In the assembled state the hollow piston (9) extends through the first seal (24) and is externally or radially sealed off thereby.
The discharge nozzle (12) is mounted at the outlet end of the central part (23). Between the discharge nozzle (12) and the pressure chamber (11) a preliminary filter (27) is preferably provided, which is preferably made of a plastic such as polyethylene or polypropylene that is chemically compatible with the liquid (2).
The preliminary filter (27) holds back particles which could block up or distort the discharge nozzle (12) or a fine filter located downstream. The filter threshold is preferably in the region of about 10 microns. Larger particles are held back from the liquid (2) flowing through by the preliminary filter (27).
In
Preferably, a very fine filter and the discharge nozzle (12) are located directly after the preliminary filter (27) or the filter holder (28). A two-stage filtering of the liquid through the preliminary filter (27) and very fine filter before nebulisation is particularly preferred. In particular, the very fine filter and discharge nozzle (12) form a single component. Using the very fine filter, particles are filtered out which could block or displace the very fine outlet channels of the discharge nozzle (12). The filter threshold is in particular at 2-5 microns.
The discharge nozzle (12) is preferably received and radially held by a nozzle seal (30). A nozzle holder (32) is attached on the outlet side. For attachment to the central part (23), the second check nut (33) is provided. The nozzle holder (32) holds the discharge nozzle (12) and the nozzle seal (30).
The discharge nozzle (12) is made up of two parts fixedly attached to one another, the first plate (12a) and second plate (12b), which are made of glass and/or silicon. One plate is microstructured and contains, on a flat side, a flow region which connects the nozzle inlet to the nozzle outlet. The two plates (12a) and (12b) are preferably joined firmly together by bonding. The flow region with the nozzle inlet located upstream and the nozzle outlet located downstream is enclosed between the two plates. The microstructures located between the plates first of all form a very fine filter structure in the flow region in the direction of flow and then form the nozzle channel with nozzle outlet. This very fine filter structure is formed for example by narrow channels through walls and/or elevations with a specified surface density. The volume of the fluidic connection to the discharge nozzle (12) adjoining the pressure chamber (11) and the volume of the discharge nozzle (12) itself are as small as possible in order to achieve a small dead volume. The flow resistance through the discharge nozzle (12) is substantially higher than the flow resistance of the liquid (2) flowing through the hollow piston into the pressure chamber (11) during the tensioning stroke, so that the nebuliser operates without any valve on the outlet side in the nozzle region.
The nebuliser operates with a spring pressure of 50-600 bar, preferably 100-500 bar. On each actuation of the nebuliser, a liquid volume of 10-50 microliters is delivered. The liquid is converted into an aerosol, the droplets of which have an aerodynamic diameter of up to 20 microns, preferably 3-10 microns. The associated nozzles produce a nozzle spray spread of from 20° to 160°, preferably from 80° to 100°. These magnitudes apply to the nebuliser according to the teaching of the present invention as particularly preferred values.
The strength-determining components of the high pressure chamber (100) are a central part (123), which is substantially cylindrical on the inside, and the components that close off this central part at both ends, namely the nozzle holder (133) and the support ring (126). In the assembled state, these components may enclose further components such as seals, filters and nozzles in the system.
The central part (123) shown as a special embodiment in
The central part (123) may also comprise a central part second material region (123b) which is fixedly connected to the central part base member (123a), while this region may consist of a different material, preferably a plastic. This central part second material region (123b) may cover all the surfaces that are in contact with the liquid during operation throughout the entire system. Preferably, a plastic material is used which is chemically compatible with the liquid used, to ensure that there is no material corrosion and no change in the liquid such as, for example, a break down of active substance. Suitable plastics include for example polyethylene or polypropylene. Such plastics may also be used for example for the second material regions at the liquid end described hereinafter which are provided on other components such as the support ring (126) and nozzle holder (133).
The second material region—for example the central part second material region (123b)—may be a coating, the surface of which extends substantially parallel to the surface of the underlying base member, for example the central part base member (123a). In addition, the second material region may be attached to the base member, for example the central part base member (123a), by injection-moulding, gluing, bonding, snap-fitting or similar methods of attachment. In particular, using bonding methods as mentioned above, the second material region may have a shape which is different from the shape of the base member.
The central part second material region (123b) serves as a support surface for other components which may be included when the components that determine the strength of the high pressure chamber (100) are assembled, namely the central part (123), support ring (126) and nozzle holder (133). The structure of the central part second material region (123b) determines the position of installation of separate filters such as a preliminary filter (27) and another fine filter (31). These filters may be pushed in, by press-fitting in a partly conical shape, from the upstream end of the central part (123) against an annular collar or abutment in the inner structure of the second material region (123b). With this type of construction there is no need for any further components to act as a filter holder or as a seal in the region of the filters. The filter threshold of the fine filter (31) is chosen such that it is between that of the preliminary filter (27) and that of the very fine filter integrated in the discharge nozzle (12).
Other designs regarding the filter installation, the types of filters, number of filters and the sequence of filters are possible. The structures of the central part second material region (123b) prevent any contact between the liquid and the central part base member (123a). The seals with other components may abut on the central part second material region (123b) such that there is no direct contact between the central part base member (123a) and the seal. The first seal (24), for example an O-ring, seals off the central part (123) and the support ring (126) from the hollow piston (9). The first seal (24) is located in a recess provided in the central part second material region (123b). The central part second material region (123b) projects with a central part connecting ring (123c) downstream from the central part (123) and forms the support surface for the nozzle seal (12).
The support ring (126) shown in
Comparable in terms of operating principle but not shown in the drawings, protruding connecting elements are provided on the central part (123), which are shaped so as to engage positively in corresponding recesses on at least one of the other strength-determining components ((126) or (133)).
Analogously to the central part second material region (123b) of the central part (123), the support ring second material region (126b) of the support ring (126) may be a coating, on the one hand, the surface of which extends substantially parallel to that of the underlying central part base member (123a). On the other hand, the support ring second material region (126b) may be attached to the support ring base member (126a) by spraying on, gluing, bonding, snap-fitting or similar methods of attachment and have a suitable shape which is outwardly different from the support ring base member (126a).
The support ring second material region (126b) is also a contact surface for the first seal (24) of the high pressure chamber (100). The first seal (24) is enclosed in the system during the assembly of the components that are the central part (123) and support ring (126). The support ring second material region (126b) projects into the central part (123) which forms a receiving socket for the first seal (24). Thus, the first seal (24) does not make any direct contact with the support ring base member (126a). Any liquid passing through the sealing member within the high pressure chamber (100) does not make any contact with the material of the support ring base member (126a).
If necessary, in addition to filters ((27) and (31)) or first seal (24), other components may be enclosed by the assembly of the central part (123) and support ring (126), e.g. a spacer (36) in the form of a flat washer with a central bore. With the thickness of the spacer (36) the depth of penetration of the support ring second material region (126b) into the central part (123) can be varied. Thus, the degree of compression and the pretensioning of the first seal (24) can be adjusted.
In another embodiment of the high pressure chamber which is not shown in the figures, the sealing function of a sealing element—such as one of the first seal (24) or second (29) or the nozzle seal (30)—can be taken over by a second material region on one of the strength determining components comprising the central part (123), the support ring (126) or the nozzle holder (133). The second material region may consist of a standard commercial elastomer such as silicon and may be connected to the respective central part base member (123a) or support ring base member (126a) analogously to the material composites described above with reference to the central part (123) and support ring (126).
In another embodiment of the high pressure chamber, which is not shown in the figures, the number of strength-determining components can be reduced from three to two. For this, the central part (123) may be combined with either the support ring (126) or the nozzle holder (133) to form a single component. This can be done by attaching seals by injection moulding. If the function of the first seal (24) is taken over by the central part second material region (123b)—e.g. consisting of an elastomer—of the central part, the counter-holder of this seal formed by the support ring (126) in
The nozzle holder (133) shown in
The nozzle holder second material region (133b) of the nozzle holder (133) may be designed analogously to the central part second material region (123b) of the central part (123) and to the support ring second material region (126b) of the support ring (126), on the one hand, in the form of a coating in which the surface of the nozzle holder second material region (133b) extends substantially parallel to that of the underlying nozzle holder base member (133a). On the other hand, the second material region may be attached to the nozzle holder base member (133a) by injection moulding, gluing, bonding, snap-fitting or other methods.
The use of a metal injection moulding process is preferred for the manufacture of the base members of the strength-determining components of the high pressure chamber (100), namely the nozzle holder (133), central part (123) and support ring (126).
For injection-moulding the second material region of plastics, flow channels (133d) are provided in the nozzle holder base member (133a). The nozzle holder base member (133a) is placed as an insert in the mould of an injection moulding machine. The liquefied injection moulding composition is distributed uniformly through the flow channels over the areas of the base member that are to be coated. Flow channels (133d) running parallel to the axis of the through-bore (34) allow material to be injected simultaneously on opposite surfaces of the nozzle holder base member (133a). After assembly, the through-bore (34) exposes the outlet opening of the discharge nozzle (12). The nozzle holder second material region (133b) is configured so that there cannot be any contact between the liquid (2) and the nozzle holder base member (133a). This may relate not only to the liquid (2) contained in the high pressure chamber (100) but also to the aerosol (4) emerging from the nozzle, the mist of which might wet the nozzle holder (133) in the upper area.
Using the possibilities of metal and plastics injection moulding technology which are known to the skilled man, other embodiments are possible, not shown here, in which the surface of the nozzle holder (133) at the aerosol end can be continued to the through-bore (34) by other channels which open upwardly and to the side of the holder. When sidestream air is sucked into the interior of the mouthpiece (13) though the supply air openings (15) as the patient breathes in, this sidestream air can be brought to the point of origin of the aerosol (14) through the new channels, where it acts as an enveloping flow. In this way, the alignment of the aerosol mist can be further assisted and the depositing of aerosol particles on the nozzle holder (133) or inside the mouthpiece (13) can be reduced.
If desired, an oriented assembly of the nozzle holder (133) may be provided during attachment to the central part (123) by means of a positioning aid on the nozzle holder (133e). This positioning aid on the nozzle holder (133e) may be made in any desired shape, using contours provided at the point of attachment, provided that it is a negative to the corresponding contour of the component that is to be attached. If orientation-free attachment is desired, the contour at the point of attachment may for example be in the form of an azimuthal groove in which the corresponding crimping engages.
Additionally, the outer surface of the nozzle holder base member (133a) and hence of the nozzle holder (133) may comprise gripping surfaces and insertion slopes for the following process steps. A gripping surface of this kind is shown in
The preferred manufacturing process for the components that determine the strength of the high pressure chamber (100), namely the central part (123) and support ring (126) and nozzle holder (133), and the attachment of these components will once again be summarised schematically:
For the choice of material for components from an MIM process (particularly for components with connecting elements that are to be shaped, such as support ring base member (126a) or nozzle holder (133a) from
Crimped joints are permanent joints, i.e. they cannot be undone without damaging the components. A crimp joint can certainly be opened by carefully bending back the crimp arms, but because of the solidification of the material during the first crimping the crimp arms cannot be returned to their original state, even if they can be bent back without breaking. When a crimp joint is opened, at least material wear or changes to the material must be expected.
Depending on the demands made of the components and the complexity of the components and systems, this manufacturing process may be modified almost at will in accordance with methods which are fundamentally known to the skilled man. Thus, additional requirements of a component or the system may be met by means of a third material region on selected components if another set of process steps for coating or injection-coating components is included.
The strength-determining components of the high pressure pump may originate from different processes. For example, the central part (23) may consist directly of a high grade plastics such as the comparatively expensive PEEK (polyether-ether-ketone) depending entirely on the demands and material costs.
The strength-determining components may consist of a material other than metal or sintered metal. Instead of manufacturing the base member in the MIM process, the central part (123) may consist of a drawn tube which provides strength. The tube may be placed as an insert in an injection moulding machine. The structures located on the inside and outside may be moulded to the tube in a plastics injection moulding process.
The present invention has the following advantages:
If the high pressure chamber according to the invention is used in the medical field the liquid (2) is preferably a medicament preparation.
Some preferred compounds or pharmaceutical active substances, ingredients and/or formulations of medicinal liquids are listed below. Any desired mixtures with a range of other liquids may be used. Powdered substances may be dissolved either in water or in any desired solvent or may be present in the form of a suspension.
The pharmaceutical compounds listed below may be used in the device according to the invention on their own or in combination. In the compounds mentioned below, W is a pharmacologically active substance and is selected (for example) from among the betamimetics, anticholinergics, corticosteroids, PDE4-inhibitors, LTD4-antagonists, EGFR-inhibitors, dopamine agonists, H1-antihistamines, PAF-antagonists and PI3-kinase inhibitors. Moreover, double or triple combinations of W may be combined and used in the device according to the invention. Combinations of W might be, for example:
The compounds used as betamimetics are preferably compounds selected from among albuterol, arformoterol, bambuterol, bitolterol, broxaterol, carbuterol, clenbuterol, fenoterol, formoterol, hexoprenaline, ibuterol, isoetharine, isoprenaline, levosalbutamol, mabuterol, meluadrine, metaproterenol, orciprenaline, pirbuterol, procaterol, reproterol, rimiterol, ritodrine, salmefamol, salmeterol, soterenol, sulphonterol, terbutaline, tiaramide, tolubuterol, zinterol, CHF-1035, HOKU-81, KUL-1248 and
The anticholinergics used are preferably compounds selected from among the tiotropium salts, preferably the bromide salt, oxitropium salts, preferably the bromide salt, flutropium salts, preferably the bromide salt, ipratropium salts, preferably the bromide salt, glycopyrronium salts, preferably the bromide salt, trospium salts, preferably the chloride salt, tolterodine. In the above-mentioned salts the cations are the pharmacologically active constituents. As anions the above-mentioned salts may preferably contain the chloride, bromide, iodide, sulphate, phosphate, methanesulphonate, nitrate, maleate, acetate, citrate, fumarate, tartrate, oxalate, succinate, benzoate or p-toluenesulphonate, while chloride, bromide, iodide, sulphate, methanesulphonate or p-toluenesulphonate are preferred as counter-ions. Of all the salts the chlorides, bromides, iodides and methanesulphonates are particularly preferred.
Other preferred anticholinergics are selected from among the salts of formula AC-1
wherein X− denotes an anion with a single negative charge, preferably an anion selected from among the fluoride, chloride, bromide, iodide, sulphate, phosphate, methanesulphonate, nitrate, maleate, acetate, citrate, fumarate, tartrate, oxalate, succinate, benzoate and p-toluenesulphonate, preferably an anion with a single negative charge, particularly preferably an anion selected from among the fluoride, chloride, bromide, methanesulphonate and p-toluenesulphonate, particularly preferably bromide, optionally in the form of the racemates, enantiomers or hydrates thereof. Of particular importance are those pharmaceutical combinations which contain the enantiomers of formula AC-1-en
wherein X− may have the above-mentioned meanings. Other preferred anticholinergics are selected from the salts of formula AC-2
wherein R denotes either methyl or ethyl and wherein X− may have the above-mentioned meanings. In an alternative embodiment the compound of formula AC-2 may also be present in the form of the free base AC-2-base.
Other specified compounds are:
The above-mentioned compounds may also be used as salts within the scope of the present invention, wherein instead of the methobromide the metho-X salts are used, wherein X may have the meanings given hereinbefore for X−.
As corticosteroids it is preferable to use compounds selected from among beclomethasone, betamethasone, budesonide, butixocort, ciclesonide, deflazacort, dexamethasone, etiprednol, flunisolide, fluticasone, loteprednol, mometasone, prednisolone, prednisone, rofleponide, triamcinolone, RPR-106541, NS-126, ST-26 and
PDE4-inhibitors which may be used are preferably compounds selected from among enprofyllin, theophyllin, roflumilast, ariflo (cilomilast), tofimilast, pumafentrin, lirimilast, arofyllin, atizoram, D-4418, Bay-198004, BY343, CP-325.366, D-4396 (Sch-351591), AWD-12-281 (GW-842470), NCS-613, CDP-840, D-4418, PD-168787, T-440, T-2585, V-11294A, CI-1018, CDC-801, CDC-3052, D-22888, YM-58997, Z-15370 and
The LTD4-antagonists used are preferably compounds selected from among montelukast, pranlukast, zafirlukast, MCC-847 (ZD-3523), MN-001, MEN-91507 (LM-1507), VUF-5078, VUF-K-8707, L-733321 and
EGFR-inhibitors which may be used are preferably compounds selected from among cetuximab, trastuzumab, ABX-EGF, Mab ICR-62 and
The dopamine agonists used are preferably compounds selected from among bromocriptin, cabergoline, alpha-dihydroergocryptine, lisuride, pergolide, pramipexol, roxindol, ropinirol, talipexol, tergurid and viozan, optionally in the form of the racemates, enantiomers, diastereomers thereof and optionally in the form of the pharmacologically acceptable acid addition salts, solvates or hydrates thereof. According to the invention these acid addition salts are preferably selected from among the hydrochloride, hydrobromide, hydriodide, hydrosulphate, hydrophosphate, hydromethanesulphonate, hydronitrate, hydromaleate, hydroacetate, hydrocitrate, hydrofumarate, hydrotartrate, hydrooxalate, hydrosuccinate, hydrobenzoate and hydro-p-toluenesulphonate.
H1-Antihistamines which may be used are preferably compounds selected from among epinastine, cetirizine, azelastine, fexofenadine, levocabastine, loratadine, mizolastine, ketotifen, emedastine, dimetindene, clemastine, bamipine, cexchlorpheniramine, pheniramine, doxylamine, chlorophenoxamine, dimenhydrinate, diphenhydramine, promethazine, ebastine, desloratidine and meclozine, optionally in the form of the racemates, enantiomers, diastereomers thereof and optionally in the form of the pharmacologically acceptable acid addition salts, solvates or hydrates thereof. According to the invention these acid addition salts are preferably selected from among the hydrochloride, hydrobromide, hydriodide, hydrosulphate, hydrophosphate, hydromethanesulphonate, hydronitrate, hydromaleate, hydroacetate, hydrocitrate, hydrofumarate, hydrotartrate, hydroxalate, hydrosuccinate, hydrobenzoate and hydro-p-toluenesulphonate.
As pharmaceutically active substances, substance formulations or substance mixtures, any inhalable compounds may be used, also including inhalable macromolecules as disclosed in EP 1 003 478. Preferably, substances, substance formulations or substance mixtures are used to treat respiratory complaints, which are used by inhalation.
In addition, the compound may be selected from among the ergot alkaloid derivatives, the triptans, the CGRP-inhibitors, the phosphodiesterase-V inhibitors, optionally in the form of the racemates, enantiomers or diastereomers thereof, optionally in the form of the pharmacologically acceptable acid addition salts, the solvates and/or hydrates thereof.
Examples of ergot alkaloid derivatives are dihydroergotamine and ergotamine.
| Number | Date | Country | Kind |
|---|---|---|---|
| 09165311 | Jul 2009 | EP | regional |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/EP2010/057937 | 6/7/2010 | WO | 00 | 2/6/2012 |
| Publishing Document | Publishing Date | Country | Kind |
|---|---|---|---|
| WO2011/006711 | 1/20/2011 | WO | A |
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