NZ730120B2

NZ730120B2 - Inhalation device for use in aerosol therapy of respiratory diseases

Info

Publication number: NZ730120B2
Application number: NZ730120A
Authority: NZ
Inventors: Koen Allosery; Erik Depla; Martin Huber; Tobias Kolb; Bernhard Mullinger; Juliane Schick
Original assignee: Ablynx Nv; Vectura Gmbh
Priority date: 2014-10-10
Filing date: 2015-10-09
Publication date: 2021-02-02

Abstract

The invention provides an inhalation device, an assembly or inhalation system comprising the inhalation device, a kit and a combination of the inhalation device and a pharmaceutical composition. Moreover, the invention provides uses of the device, the assembly, the kit, and the combination. The device is adapted in particular for administering therapeutic aerosols to paediatric patients, including neonates, infants or toddlers. It comprises a vibrating mesh aerosol generator which is insertable into a flow channel of the inhalation device through a lateral opening, and a valved face mask. The device is connectable to a gas source through which a gas such as oxygen may be received into the flow channel at a low flow rate, but has no further inlet opening for receiving a gas. The inhalation device is particularly effective for delivering a therapeutic aerosol to patients having a low tidal volume, such as paediatric patients. In particular, it allows the delivery of the therapeutic aerosol in a manner that is largely independent of the inspiratory capability of the patient. ce is adapted in particular for administering therapeutic aerosols to paediatric patients, including neonates, infants or toddlers. It comprises a vibrating mesh aerosol generator which is insertable into a flow channel of the inhalation device through a lateral opening, and a valved face mask. The device is connectable to a gas source through which a gas such as oxygen may be received into the flow channel at a low flow rate, but has no further inlet opening for receiving a gas. The inhalation device is particularly effective for delivering a therapeutic aerosol to patients having a low tidal volume, such as paediatric patients. In particular, it allows the delivery of the therapeutic aerosol in a manner that is largely independent of the inspiratory capability of the patient.

Description

INHALATION DEVICE FOR USE IN AEROSOL THERAPY OF RESPIRATORY DISEASES Description BACKGROUND Diseases of the respiratory system such as asthma, bronchitis, cystic fibrosis, ary infections with viruses or bacteria, and a number of other respiratory diseases may be treated with s therapeutic agents which are administered to the patient either systemically, i.e. by parenteral or oral administration, or by inhalation.

While the concept of inhalation treatment is intriguing in that it involves the direct delivery of the active agent to the affected target site of the body, it is also challenging to achieve ive drug delivery to the lungs as this not only requires a particular aerosol y to be generated and red to the patient, but often also the collaboration of the patient who may have to perform a particular breathing manoeuvre.

Various types of inhalation devices are available that are, in principle, capable of converting solid or liquid pharmaceutical formulations into inhalable l, including dry powder inhalers, d-dose rs and nebulisers. Nebulisers have in common that they convert a non-pressurised liquid formulation into respirable aerosolised ts. ing on the mechanism by which the l droplets are generated, various different types of sers may be distinguished, such as jet nebulisers, ultrasonic nebulisers, and vibrating-mesh nebulisers.

Some patient groups present a particular challenge for inhalation treatment. Such patients e those that have special anatomical or physiological characteristics that require particular aerosol parameters, for example small children; or patients that are not capable of performing specific manoeuvres, such as an inspiratory manoeuvre coordinated with manually triggering the release of a drug dose, as is required in the case of some metered-dose inhalers and powder inhalers. Patients with difficulties in this respect include those patients that are severely ill, that are under sedation, or suffer from a mental disability.

For some of these special patients, in particular children, it is therefore rather difficult to make an ive use of inhalation therapy, using the inhalation devices and the pharmaceutical drugs and formulations that are available today. Nevertheless, there is a pronounced need to allow such patients to benefit from inhalation therapy. For example, there are respiratory diseases which affect in particular young children such as neonates, infants and toddlers, while rarely occurring in adults or older children. An example is infection with respiratory syncytial virus (RSV), more specifically the human respiratory syncytial virus (hRSV). RSV is a recurrent cause of severe respiratory tract infections in infants and very young children. It causes annual epidemics, especially during the winter months. RSV infection may affect the upper respiratory system, which typically involves mild and transient symptoms, or constitute a severe lower respiratory tract infection (LRTIs) involving more serious ms such as bronchopneumonia and bronchiolitis.

With children, the challenges of ive therapeutic aerosol delivery increase with decreasing age of the child. Typically, neonates, infants and toddlers cannot yet generate the inspiratory flow required for using breath-triggered inhalation devices or powder-inhalers. At the same time, they are not able to use the mouthpiece of a nebuliser appropriately. In fact, infants up to the age of 18 months may not even be capable of any controlled oral inhalation vre.

Moreover, the airways of young en are several times r than those of adults, with narrow airways, high breath resistance and thus increased risk of ion of aerosols in the upper airways. Also the tidal volume of young en is far lower than for adults and more variable, which further ses the challenges of paediatric inhalation therapy. Hence, there is a substantial need for improved therapies for paediatric patients affected with a respiratory disease. Similarly, there is a need for improved therapies for other patients with special limitations that are affected by respiratory es or conditions.

With respect to RSV therapy, the only approved drug product currently available in the market is Synagis®, a humanized monoclonal antibody administered by parenteral administration. With no other adequate treatment options at hand, the rd of care for infected infants is mainly supportive (e.g., fluid/feed supplementation, observation, and respiratory t as needed). Thus, there is clearly a need for an improved therapy for patients suffering from this disease, in particular tric patients. discloses globulin single variable s directed against the fusion protein of the human respiratory syncytial virus as potential new therapies for RSV patients. For example, the document describes n polypeptides including SEQ ID NOs: 65-85 along with some of their characteristics in vitro and in vivo.

These polypeptides comprise 3 anti-hRSV immunoglobulin single variable domains that are recombinantly linked by a flexible linker. The effectiveness of the polypeptides was shown in rats. However, it is known that biological effects observed in rat studies cannot be easily extrapolated to humans, in particular not to specific human t populations.

Moreover, formulations of these polypeptides in the form of nebuliser solutions have been described in . r, there remains a need for devices and methods to deliver such formulations effectively to patients in need f.

There is a need to improve the delivery of a therapeutic aerosol to a patient who cannot easily perform breathing manoeuvres required for conventional inhalation therapy, such as a paediatric patient.

There is also a need to improve the therapy of respiratory diseases, in ular atory infections such as RSV infections.

There is also need to overcome any of the disadvantages of the inhalation therapies of the art.

SUMMARY OF THE INVENTION In a first aspect the present invention provides an inhalation device for delivering a nebulised aerosol to a t, sing: (a) an aerosol generator with a vibratable mesh; (b) a reservoir for a liquid to be nebulised, said reservoir being in fluid connection with the vibratable mesh; (c) a gas inlet opening shaped as a tube g; (d) a face mask, having - a , - an aerosol inlet opening, - a patient contacting surface, and - a one-way exhalation valve or a two-way inhalation/exhalation valve in the casing having an exhalation overpressure resistance selected in the range from 0.5 to 5 mbar; and (e) a flow channel extending from the gas inlet opening to the aerosol inlet opening of the face mask, the flow channel having - a lateral opening through which the aerosol generator is at least partially inserted into the flow channel, - a constant flow resistance between the gas inlet opening and the aerosol inlet opening of the face mask at a flow rate of 1 to 20 L/min, wherein the flow channel ts no r inlet opening for ing a gas.

In a second aspect the invention provides an assembly comprising the inhalation device of the first aspect of the invention and a gas source providing a gas at a constant flow rate in the range from 1 to 5 L/min, wherein the gas source is connected to the inhalation device such that the gas enters the flow channel through the gas inlet opening, and wherein the gas is selected from oxygen, air, oxygen-enriched air, a mixture of oxygen and nitrogen, and a mixture of helium and .

In a third aspect the present invention provides a combination or kit comprising (a) the tion device of the first aspect of the invention or the assembly of the second aspect of the invention, and (b) a ceutical composition for inhalation use.

In addition, an inhalation device is disclosed for delivering a nebulised aerosol to a patient, comprising (a) an aerosol generator with a vibratable mesh; (b) a oir for a liquid to be nebulised, said reservoir being in fluid connection with the vibratable mesh; (c) a gas inlet g; (d) a face mask, having a casing, an aerosol inlet opening, a patient contacting e, and a one-way exhalation valve or a two-way inhalation/exhalation valve in the casing having an exhalation resistance selected in the range from 0.5 to 5 mbar; (e) a flow channel extending from the gas inlet opening to the aerosol inlet opening of the face mask, the flow channel having a lateral opening through which the l generator is at least partially inserted into the flow channel, and a nt flow resistance between the gas inlet opening and the aerosol inlet opening of the face mask at a flow rate of 1 to 20 L/min.

Upstream of the lateral opening, the flow channel may be shaped such as to effect a laminar flow when a gas is conducted through the flow l at a flow rate of 1 to 20 L/min. Further, the flow channel may be sized and shaped to achieve, at a position immediately upstream of the lateral opening, a high velocity at a flow rate of 2 L/min.

In one embodiment, the flow channel exhibits no further inlet g for receiving a gas. The gas inlet opening may be shaped as a tube fitting.

The aerosol generator of the inhalation device may be oriented such as to emit nebulised aerosol into the flow channel at an angle of approx. 90° to the longitudinal axis of the flow channel. In one embodiment of the invention, the inhalation device of the invention may comprise a switch for starting and stopping the operation of the aerosol generator and the ion of the aerosol generator may comprise the continuous vibration of the vibratable mesh.

The vibratable mesh of the inhalation device may comprise from 1,000 to 4,000 openings whose smallest diameter is inantly in the range from 1.5 to 3.0 µm.

In one embodiment, the inhalation device may be connected to a gas source that provides a gas at a constant flow rate in the range from 1 to 5 L/min; said gas source being connected to the inhalation device such that the gas enters the flow channel through the gas inlet opening. Accordingly, an assembly sing the inhalation device of the present invention and such a gas source is also considered to be falling under the scope of the invention. The gas provided by said gas source may be ed from oxygen, air, oxygen-enriched air, a e of oxygen and nitrogen, and a mixture of helium and oxygen. For the purpose of ting the tion device to the gas source, the gas inlet opening may be shaped as a tube fitting as mentioned above.

In an optional embodiment - or as an alternative to a gas source providing gas at a constant flow rate in the range from 1 to 5 L/min - the inhalation device may comprise a flow restrictor capable of restricting the flow of gas through the flow channel to a constant flow rate in the range from 1 to 5 L/min when connecting the gas inlet opening with a pressurised gas source.

In a specific embodiment, the inhalation device may comprise: a) a base unit comprising an electronic controller for controlling the aerosol generator, and an upstream portion of the flow l ing the gas inlet g; and b) a mixing channel unit, comprising a downstream portion of the flow channel including the lateral opening, wherein the downstream portion comprises a segment where the flow channel widens in the downstream direction, said segment being positioned downstream of the lateral opening.

In a further aspect of the invention, an ly - or inhalation system - is ed comprising the inhalation device and a gas source providing a gas at a constant flow rate in the range from 1 to 5 L/min. The gas source is connected to the inhalation device such that the gas enters the flow channel through the gas inlet opening. The gas is preferably selected from , air, oxygen-enriched air, a mixture of oxygen and nitrogen, and a mixture of helium and oxygen. Optionally, the constant gas flow is in the range from about 1 to 3 L/min, such as about 2 L/min.

A further aspect of the invention is directed to a combination or kit comprising (a) the inhalation device or the assembly, and (b) a ceutical composition for inhalation use. The ceutical composition may se an active agent ed from antibiotics, antiviral agents, bronchodilators, anticholinergics, corticosteroids, hypertonic saline, antibodies, antibody fragments, and immunoglobulin single le domains.

In a particular embodiment, pharmaceutical ition may comprise an anti- RSV agent, such as a polypeptide comprising or essentially consisting of one or more anti-RSV immunoglobulin single variable domains. The anti-RSV immunoglobulin single variable domain may comprise a CDR1 having the amino acid sequence of SEQ ID NO: 46, a CDR2 having the amino acid sequence of one of SEQ ID NOs: 49-50, and a CDR3 having the amino acid ce of SEQ ID NO: 61. In particular, the anti-RSV immunoglobulin single variable domain may be selected from one of the amino acid sequences of SEQ ID NOs: 1-34. Suitable polypeptides which act as anti-RSV agents are the polypeptide selected from one of the amino acid sequences of SEQ ID NOs: 65-85.

Optionally, the combination or kit comprising a pharmaceutical composition for inhalation use incorporating an anti-RSV agent further comprise a bronchodilator, either within the same composition which also contains the anti-RSV agent or in a separate, additional pharmaceutical composition. The bronchodilator may belong to the class of beta2-mimetics; including long-acting mimetics, such as a bronchodilator selected from formoterol or a solvate thereof, salmeterol or a salt thereof, and mixtures thereof; or short-acting mimetics, such as a odilator selected from salbutamol, terbutaline, pirbuterol, fenoterol, tulobuterol, levosabutamol and mixtures thereof. In a specific embodiment, the bronchodilator is salbutamol and may be administered at a dose of 200 micrograms. Alternatively, the bronchodilator may belong to the class of anticholinergics, such as a bronchodilator selected from tiotropium, oxitropium, ipratropium bromide and mixtures thereof.

In a yet further aspect of the ion, a method of delivering a sed aerosol to a patient is provided, comprising the steps of (a) providing the tion device, or the combination or kit, according to this invention; (b) providing a gas source; and (c) ting the gas source to the inhalation device such that the gas enters the flow channel through the gas inlet opening at a nt flow rate in the range from 1 to 5 L/min.

The invention further provides the use of the inhalation , or of the assembly, or of the kit or combination, for inhalation treatment of a patient in need thereof. The t may be a paediatric patient such as a neonate, an infant, a toddler, or a school child. Alternatively, the patient is an adult patient for whom controlled oral tion is not possible or considerably impeded, such as a patient with dementia, other mental impairment, COPD, severe asthma, cystic fibrosis, amyotrophic lateral sclerosis, emphysema, or heart failure, or a patient under sedation or anaesthesia.

Optionally, the t is suffering from a disease affecting the respiratory system. For example, the patient may suffer from a respiratory infection. In a particular embodiment, the patient is infected with RSV, such as with RSV lower atory tract infection, and the use involves the delivery of an anti-RSV agent to the t via the inhalation route.

Further advantageous ments, features, beneficial effects and uses of the device are described below in more detail.

DEFINITIONS The following expressions as used herein should normally be interpreted as outlined in this section, unless the description provides a different meaning in a specific context.

An “aerosol” is a dispersion of small, typically inhalable solid particles or liquid droplets in a continuous gas phase such as air. Herein, the term “aerosol” may refer either to the nascent aerosol as it is emitted from an aerosol generator within an inhalation device; or to aerosol resulting from the dispersion of such t aerosol in an inhalable gas, as it is emitted from the inhalation device and made available for inhalation. The exact meaning is derivable from the context.

An "aerosol generator" is a device or device component capable of ting an aerosol from a liquid formulation; e.g. a ceutical composition for inhalation use.

Synonymously, the terms "nebuliser" or "nebulising means" may be employed.

Unless specified otherwise, a “gas” refers to any gas or mixture of gases suitable for inhalation.

Unless specified otherwise, “young children” refers to children of 6 years age or r. “Neonates” means children up to 1 month of age, “infants” means an age from 1 to 12 months, and “toddlers” means an age from 1 to 3 years. For practical reasons, though, the attribution to these groups should be based on the physiological and cognitive development stage of the child rather than solely its age.

“Lateral”, or ally”, means away from the middle, centre, or centre axis of a device or device component.

All terms designating a position, ation or ion, such as left, right, front, rear, back, top, bottom, up, down and the like, should be understood with nce to the orientation of the inhalation device or its components under normal operational conditions, and typically from the perspective of the user. For the avoidance of any misunderstandings, it is clear that a user may also hold the device in such a way that there is some deviation from a normal operational orientation. For example, while the device is designed to be held in an approximately horizontal orientation with respect to the axis along which the air flow within the device occurs, the user may also hold the device at an angle of up to 45° deviating from the ntal orientation, without negative impact on the device function. rly, a user may, to some degree, rotate the device around said axis, again without any substantial oration of device performance.

"Comprise" or "comprising" with reference to any feature means that the respective feature must be present, but without excluding the presence of other features.

"A" or "an" does not exclude a plurality.

"Essentially", "about", "approximately” and the like in connection with an attribute or value include the exact attribute or the precise value, as well as any attribute or value typically considered to fall within a normal range or variability accepted in the technical field concerned.

A polypeptide (such as an immunoglobulin, an antibody, an immunoglobulin single variable domain, or lly an antigen binding molecule or a fragment thereof) that can “bind to” or “specifically bind to”, that “has affinity for” and/or that “has specificity for” a certain e, n or protein (or for at least one part, fragment or epitope thereof) is understood to be "against" or ted against” said epitope, antigen or protein or is a “binding” molecule with respect to such epitope, antigen or protein, or is said to be “anti”-epitope, “anti”-antigen or “anti”-protein (e.g., “anti”-hRSV).

Any reference signs in the claims should not be construed as a limitation to the embodiments ented in any of the drawings.

A single unit may fulfil the functions of several features recited in the claims.

BRIEF DESCRIPTION OF THE DRAWINGS Fig. 1 shows a cross-sectional side view of a specific embodiment of the tion device according to the invention Fig. 2 shows a perspective view of a specific ment of the inhalation device according to the invention.

Fig. 3 shows a top view of a specific embodiment of the tion device according to the ion.

Fig. 4 shows a side view of a specific embodiment of the inhalation device according to the invention.

Fig. 5 shows a bottom view of a specific embodiment of the inhalation device according to the invention.

Fig. 6 shows a front view of a specific embodiment of the inhalation device according to the invention.

Fig. 7 shows a rear view of a specific embodiment of the inhalation device according to the invention.

Fig. 8 shows an experimental set-up with a specific embodiment of the inhalation device according to the invention connected to a SAINT model LIST OF NUMERICAL REFERENCES USED IN THE S 100 Inhalation device 101 Aerosol generator 102 Vibratable Mesh 103 oir 104 Gas inlet opening 105 Face mask 106 Casing 107 Aerosol inlet opening 108 Patient contacting e 109 Valve (one-way exhalation or two-way inhalation/exhalation valve) 110 Flow channel 111 Lateral opening 112 Switch 113 Tube fitting 114 Lid 115 Key lock 116 USB-Port 117 Holes 118 Base unit 119 Mixing channel unit 200 SAINT model 201 Face/throat portion of the SAINT model 202 Nasal portion of the SAINT model 300 Glass fibre filter assembly DETAILED DESCRIPTION OF THE INVENTION In a first aspect of the invention, an inhalation device is ed for delivering a nebulised aerosol to a patient, comprising (a) an aerosol tor with a vibratable mesh; (b) a reservoir for a liquid to be nebulised, said reservoir being in fluid connection with the vibratable mesh; (c) a gas inlet opening ; (d) a face mask , having a casing, an aerosol inlet opening, a patient contacting surface, and a one-way exhalation valve or a two-way inhalation/exhalation valve in the casing having an exhalation resistance selected in the range from 0.5 to 5 mbar; and (e) a flow l extending from the gas inlet opening to the l inlet opening of the face mask, the flow channel having a lateral opening through which the aerosol generator is at least partially inserted into the flow channel, and a constant flow resistance between the gas inlet opening and the aerosol inlet opening of the face mask at a flow rate of 1 to 20 L/min.

A cross-sectional side view of one exemplary embodiment of such an inhalation device can be seen in figure 1. Figure 1 depicts an tion device (100); an aerosol generator (101) with a vibratable mesh (102); a reservoir (103) in fluid connection with the able mesh (102); a gas inlet opening (104); a face mask (105) with a casing (106), an aerosol inlet opening (107), a patient contacting surface (108), and a one-way tion valve or a two-way inhalation/exhalation valve (109); and a flow channel (110) leading from the gas inlet opening (104) to the aerosol inlet opening (107) of the face mask (105). The flow channel (110) has a lateral opening (111) through which the aerosol generator (101) is partially inserted with its downstream end. In the depicted embodiment, the oir is covered by a screw-on lid (114) and the gas inlet opening (104) is shaped as, or equipped with, a tube fitting (113).

The ary inhalation device of figure 1 is further depicted in a perspective side view in figure 2 and in top, side and bottom views in figures 3 to 5, tively. The front and rear views of this ary inhalation device are provided in figures 6 and 7, respectively. The referenced features will be dealt with in depth below. If a reference sign is used in the context of the general description of a feature below, this should be tood as an illustrative reference to an exemplary embodiment of the feature, and not as a limitation of the invention to that ment.

The inventors have unexpectedly found that the inventive inhalation device with a face mask and a flow channel having a constant flow resistance in combination with a vibrating mesh aerosol generator as defined in claim 1 is particularly effective for delivering a therapeutic aerosol to certain types of patients, such as patients having a low tidal volume, paediatric patients, elderly patients, patients that profit from inhaling oxygen in addition to air, and/or patients affected with certain respiratory diseases, such a ions of the respiratory tract, e.g. RSV infection. In ular, it allows the delivery of the therapeutic aerosol in a manner that is largely independent of the inspiratory capability of the patient. Moreover, it enables the effective use of a gas (such as , or oxygen-enriched air) supplied from an external source at a very low flow rate (such as 1 to 5 L/min) which may be used as sole carrier gas to receive and disperse the nascent aerosol in the inhalation device and provide it to the patient for inhalation.

As used herein, the inhalation device is a device capable of generating and delivering a therapeutic aerosol which is inhalable by a patient. An ble aerosol is different from e.g. a nasal or oral spray in that the le or droplet size of the inhalable l is substantially r, i.e. predominantly smaller than about 10 µm, and suitable for entering the lungs.

The device according to the invention comprises an aerosol generator (101) with a vibrating mesh (102). It has been found that vibrating mesh nebulisers are particularly advantageous in the context of the invention. They have a high output rate which helps to keep the time required to administer a dose short. This is particularly l if the patient is a paediatric patient, as paediatric patients are even less nt to long inhalation times. er, vibrating mesh nebulisers are capable of generating a dense aerosol without requiring a high gas flow rate for l generation, as e.g. jet sers do. In addition, vibrating mesh inhalers are more silent than other types of aerosol generators and thus found less disturbing by paediatric patients. They may even be used while the child sleeps, which could ensure a deep and calm breathing pattern.

Optionally, the vibratable mesh (102) of the inhalation device comprises from 1,000 to 4,000 openings whose smallest diameter is predominantly in the range from 1.5 to 3.0 µm. This provides a particularly fine aerosol mist. Preferably, the vibratable mesh is selected such as to generate an aerosol with a volume median droplet size as ed by laser diffraction ranging from 2 to 5 µm, or from 2 to 4 µm, or from 2 to 3 µm,. Such fine aerosols are particularly advantageous for neonates, infants and toddlers.

The inhalation device further comprises a reservoir (103) for a liquid to be nebulised; the reservoir is in fluid connection with the vibratable mesh (102). The reservoir may have a volume of 0.1 to 10 mL, or from 0.5 to 5 mL, to accommodate the liquid, which is typically a pharmaceutical composition comprising an active ingredient.

Preferably, the reservoir (103) is located at a superior position ve to the body of the aerosol tor (101). It may be closable by a screw-on or snap-on lid; see e.g. the screw-on lid (114) depicted in figure 1. This is particularly useful if the aerosol generator has a y vertical orientation during use, with the vibratable mesh being positioned at its lower end and having a roughly horizontal orientation. Such arrangement would be useful as it s the spilling risk and ensures that the vibratable mesh s covered with liquid during aerosol tion, which enables a more m aerosol output rate.

Optionally, the aerosol generator (101) and/or the reservoir (103) may be provided in a detachable manner with regard to the flow channel of the inhalation device. For instance, there may be a housing ent for both the aerosol generator (101) and the reservoir (103) which may be detachable from the flow channel component of the inhalation device. This offers the advantage that the components can be cleaned more easily and/or that different aerosol generators may be coupled to, and operated with the same flow channel.

The device further comprises a gas inlet opening (104). The gas inlet opening is preferably connectable to an external gas source, either directly or ctly via a tube or other conduct. The gas inlet g (104) may be shaped as, or equipped with, a tube fitting (113) in order to facilitate the attachment of a gas source, as can be seen e.g. in figures 1 and 2. The fitting may be a standard fitting with respect to its shape and dimensions, and preferably made from an inert material such as ess steel. It is also advantageous to use a tube fitting whose inner wall is smooth and shaped as a regular cylinder, such as to allow a laminar flow of gas. The gas inlet opening (104) may be accommodated in a rear position of the inhalation device (100), as shown in figures 1 to and figure 7 for the exemplary embodiment.

In a preferred embodiment, the gas inlet opening (104) is the only inlet opening for ng a gas to flow into the flow channel (110), with the exception of the aerosol generator, or the reservoir ted with the aerosol generator, through which very small amounts of gas (typically air) may enter the device to replace the nebulised liquid.

In this ment, the gas phase of the therapeutic aerosol delivered to the patient by the device is predominantly the gas which is supplied to the gas inlet opening, and which may be selected according to the needs of the patient.

It is noted that the small openings (117) seen in figures 2, 5 and 7 are not in fluid connection with the flow channel. They may ally be provided in the casing of the device in order to allow for air-cooling of any electronic components.

An important feature of the device is the face mask (105). It has a casing (106), an aerosol inlet opening (107), a patient contacting surface (108), and a one-way exhalation valve or a two-way inhalation/exhalation valve (109) in the casing. The valve has an exhalation resistance selected in the range from 0.5 to 5 mbar.

Such face mask receives the aerosol ted in the device via a flow channel and allows the aerosol to be stored until it is inhaled by the patient. It also serves as a means to enable nasal inhalation. Thus the patient may inhale the aerosol either through the mouth or the nose. This is advantageous in that patients that are not capable of performing oral inhalation manoeuvers, such as small en or sleeping patients, may still receive inhalation therapy. It is particularly advantageous for paediatric patients who have a highly variable breathing frequency and a small and variable tidal volume.

Optionally, the face mask may also be provided separately from the inhalation device, or in a kit which comprises the tion device as described herein and a matching face mask, the inhalation device being connectable to the face mask and, vice versa, the face mask having an aerosol inlet opening which is adapted to engage with the inhalation .

The face mask is configured to allow the exhalation by the patient through the mask. This is achieved by the valve which exhibits a rather small tion resistance.

The valve, or the exhalation resistance of the valve, may be selected within the range specified above and in view of the patient. For a small child, a rather low tion resistance of less than about 3 mbar, or in the range from about 0.5 mbar to about 2 mbar, is tly preferred. Such resistance is low enough to enable easy exhalation without much erence with normal breathing; on the other hand, the ance is sufficient to achieve a slight overpressure in the face mask as it continuously receives the aerosol generated in the device when the aerosol generator operates. Such slight overpressure has been found to assist the patient to inhale the therapeutic aerosol more effectively, and may contribute to a more effective drug deposition in the deeper airways of the respiratory system.

As mentioned, the face mask is particularly suitable for patients that have difficulty using a iece to inhale an aerosol. This is often the case with paediatric ts, such as neonates, infants, rs, or young school children. However, the face mask is also advantageous for adult patients suffering e.g. from dementia, mental impairment, COPD, heart failure, severe asthma attacks, cystic is, amyotrophic lateral sclerosis, emphysema or patients under sedation or anaesthesia. The face mask may be held in place, or positioned, by a caregiver.

The face mask may be connectable to, or form an integral part of, the flow l, forming its down-stream end. A connectable face mask potentially offers the advantage of easy cleaning and/or replacement. The invention is also directed to a combination of an tion device and a face mask which together t the features of claim 1, as well as to an inhalation device adapted for being ted with a separate face mask where the inhalation device and the face mask together exhibit the same features. On the other hand, if the face mask forms an integral part of the flow channel, the number of components is reduced and mis-matches of flow channels and face masks of different patients, e.g. after cleaning, are d, which may be advantageous in hospital settings.

The face mask may further be provided in a movable , e.g. comprising a pivoting joint near the aerosol inlet opening. Such joint may enable a deflection of the downstream portion of the flow channel as part of the mask to allow the caregiver to hold the main body of the inhalation device at a different angle from that of the face mask.

Without the pivoting joint, the face mask is also suitable, in particular if the device dimensions are rather small. It has been found that caregivers tend to hold the inhalation device at or near the face mask, which is closer to the patient's face, rather than holding the main body of the device.

Preferably, the mask is made from a arent, break-resistant material, such as polypropylene or the like, to enable the parent or caregiver to see the aerosol mist and the patient's face and breathing activity.

The patient contacting surface may be made from a soft, mouldable, antiallergenic and well-tolerated material which is preferably free of additives or contaminants like ates, nol A or latex. The patient contacting surface may include a soft silicone lip or an inflatable cushion to increase patient comfort.

Preferably, the nominal al volume of the face mask is not more than about 120 mL. As used herein, the nominal internal volume is understood as the internal volume enclosed by the casing from the aerosol inlet opening to the patient contacting surface when the patient contacting surface is placed on a flat surface. This volume is slightly larger than the effective internal volume, or so-called dead space, which is the volume enclosed by the mask when placed against the face of a patient, and which therefore depends on the size and shape of the t's face. If the patient is a school child, the nominal internal volume is preferably not more than about 90 mL, or even not more than about 80 mL, or not more than about 70 mL, or not more than about 60 mL, or not more than about 50 mL, or not more than about 40 mL, respectively, depending on the size of the face of the patient. It is currently preferred to select a mask with a nominal internal volume of not more than about 40 or 50 mL if the patient is a neonate.

It is further red to select the nominal al volume of the face mask with respect to the patient's average tidal volume. Advantageously, the nominal internal mask volume is smaller than the tidal volume. For example, if the t is a paediatric t having an average tidal volume during normal ing of about 80 mL, the nominal internal face mask volume should be smaller than this. In particular, the respective volume may be in the range from about 10 % to about 80 % of the average tidal volume. In further embodiments, the nominal internal face mask volume is not more than about 60 %, or even not more than about 50 %, of the patient's e tidal volume.

In one embodiment, the face mask has a two-way inhalation- and exhalation valve having a resistance of not more than 3 mbar in either direction, and n the nominal internal volume of the face mask is not more than about 50 mL. This embodiment is particularly suitable for small paediatric patients such as neonates, infants, and toddlers. In another embodiment, the face mask has one or more inhalation valves and one or more exhalation valves, wherein the exhalation valve has a resistance of not more than 3 mbar, and wherein the l internal volume of the mask is not more than about 70 mL. This embodiment is particularly suitable for toddlers and children.

The inventors have found that such sed face mask s contribute to an increased uptake of the nebulised aerosol by the patients, and to a better deposition of the aerosolised active compound in the respiratory system of the patients.

As mentioned above, the face mask comprises in its casing at least one valve which may be a one-way exhalation valve or a two-way inhalation- and exhalation valve, and wherein the exhalation resistance of the valve is in the range from about 0.5 to 5 mbar. The effect of this feature is that it allows the generation of a mild overpressure in the face mask, in particular when the gas inlet opening of the device is connected to a gas source from which gas is received into the device at a flow rate of 1 to 5 L/min. The slight overpressure facilitates the patient's inhalation of the nebulised aerosol ted in the device, t interfering substantially with the normal breathing n, thus enabling effective drug delivery. ally, the face mask may comprise further inhalation and/or exhalation valves. If so, the effective exhalation pressure of the combined valves should still be in the specified range, i.e. between about 0.5 and 5 mbar. Optionally, the exhalation pressure may also be selected from about 0.5 mbar to about 3 mbar, such as about 1 mbar or about 2 mbar, respectively. The valve(s) provided in the face mask may have any structure suitable for providing this exhalation resistance; e.g. slit valves, duck bill valves or membrane valves, to mention only a few. For example, the valve may be a oneway valve with a cross-slit and an ing membrane, such as a silicone membrane. In one ion, from the cross-slit to the membrane, the valve opens, whereas in the te direction the ne will be pressed tightly onto the cross and thus blocks the valve. Depending on which way round the valve is inserted into the face mask, it can serve both as an inhalation or an exhalation valve.

An important e of the inhalation device of the invention is the flow channel (110), which extends from the gas inlet opening (104) to the aerosol inlet opening (107) of the face mask (105). The flow channel has a lateral opening (111), as exemplified by the device depicted in figure 1, through which the aerosol generator is at least partially inserted into the flow channel. Moreover, the flow channel exhibits a constant flow resistance n the gas inlet opening and the aerosol inlet g of the face mask at a flow rate of 1 to 20 L/min.

The flow channel is configured to receive a gas from an external gas source through the gas inlet opening which forms the upstream end of the flow channel. The upstream portion of the flow channel, i.e. the t from (and including) the gas inlet opening (104) to the lateral opening (111) through which the aerosol generator (101) is at least partially inserted, is preferably sized and shaped such as to achieve a r flow of a gas which in conducted through the flow channel at a constant flow rate selected in the range from 1 to 20 L/min, and in particular at a constant flow rate in the range from about 1 L/min to about 5 L/min.

It is generally known which type of shapes should be used (or avoided) in order to enable a laminar flow of gas in a flow channel. For example, abrupt diameter changes should be avoided, and a smooth inner wall is red to an inner wall made from a material having a rough surface. An example of a suitable upstream segment is a regular cylindrical pipe made of polished stainless steel or of an inert polymeric material having a smooth surface.

Also, the gas inlet opening, which may be shaped as a tube fitting in order to facilitate the attachment of a gas source as mentioned above, may preferably be made from an inert, smooth material such as stainless steel, such as to allow a substantially laminar flow of gas. It is r ageous to use a tube fitting whose inner wall is smooth and shaped as a regular cylinder, such as to further promote substantially laminar flow of gas. A substantially laminar flow means a Reynold's number of not more than about 2300. Preferably, the upstream segment of the flow l is sized and shaped to achieve a Reynold's number of not more than 2000 at the flow rates specified above.

According to the ion, the flow channel also has a constant flow resistance between the gas inlet opening and the aerosol inlet opening of the face mask. In this respect, it differs substantially from the inhalation device of e.g. EP2724741 which comprises a variable flow ctor to restrict the inspiratory flow rate of a patient - in particular an adult patient - to a desired low flow rate such as about 15 L/min, regardless of the underpressure created by the patient at the mouthpiece.

The lateral g (111) which receives the aerosol generator (101) is preferably located at an upper position of the flow channel (110) with respect to the normal orientation of the device in use, as is depicted e.g. in figures 1 and 2. The opening is preferably sized to match the dimensions of the aerosol generator so that the opening is completely and tightly closed when the aerosol generator is received. Preferably, the aerosol generator is in a partially inserted position during use, and the downstream end of the aerosol generator protrudes towards (or even to) the longitudinal centre axis of the flow l.

In the optional case where the aerosol generator is provided in a component detachable from the flow channel ent of the inhalation device (100), fixing means may be provided, such as a key lock (115), in order to secure, or fix, the at least partially ed aerosol generator in its intended position in the flow channel; as can be seen in s 2 or 4, for instance.

In one embodiment, the aerosol generator is oriented such as to emit nebulised l into the flow channel at an angle of approximately 90° to the longitudinal axis of the flow channel. In this case, the aerosol generator is arranged in an approximately vertical orientation and the vibrating mesh is approximately horizontal.

While such arrangement offers several advantages such as facilitating the manual g of the reservoir and a continuous supply of liquid to the vibratable mesh, it requires that the plume of nascent aerosol is deflected by about 90° without any significant degree of coalescence or l deposition. This is a particular challenge if the aerosol tor is efficient and exhibits a high rate of aerosol generation, which is desirable with an eye on the inhalation time required for the administration of a drug dose.

Optionally, the aerosol generator is selected and operated such as to have an aerosol generation rate (or nebulisation rate) of at least about 0.1 , or of at least 0.2 mL/min. In some embodiments, the aerosol generator has a nebulisation rate of at least 0.3 mL/min, 0.4 mL/min, 0.5 mL/min, 0.6 mL/min, or even at least 0.7 mL/min.

Unexpectedly, the inventors have found that the inhalation device with a vibratable mesh l generator and a flow l as defined herein is indeed capable of sing the nascent aerosol, even at a low gas flow rate of 1 to 5 L/min, such as at a constant flow rate of about 2 L/min, and of conducting the aerosol into the face mask without any significant deposition in the flow channel. It is believed that such effect is shown for the first time for a therapeutic inhalation device.

The effect is particularly pronounced if the flow channel is sized and shaped to achieve, at a position immediately upstream of the lateral opening, a vely high gas velocity at a given gas flow rate. In particular, it is preferred that the average gas velocity at a flow rate of 2 L/min is at least about 4 m/s. ally, it is at least about 5.5 m/s, or at least about 8 m/s, respectively. As used herein, the average gas velocity in the flow channel at a specific on is d as the mean velocity value obtained by Computational Fluid Dynamics analysis (CFD) for this position, such as immediately upstream of the lateral opening.

It was also unexpected to find that it does not require a large mixing chamber to disperse the nascent aerosol in the g gas without significant droplet deposition in the . In particular if the preferred laminar flow and the preferred ties as described above are used, the actual dimensions of the flow channel can be rather small.

In fact, the relatively small dimensions enable rather high gas velocities, and the inventors have found that these are at least as useful to avoid aerosol loss through deposition in the device as large mixing chambers as used in some other devices.

Preferably, the flow channel's dimensions are such that the total interior volume of the channel between the l g and the aerosol inlet opening of the face mask is not more than about 30 mL. Optionally, it is not more than about 25 mL, or not more than about 20 mL, respectively. In some cases, the interior volume of the flow channel may be less than about 18 mL, or even less than about 15 mL.

In a specific embodiment, the flow channel has an al diameter at a position immediately upstream of the lateral opening of about 10 mm to about 13 mm; optionally in combination with a vibratable mesh that has a total diameter of about 6 mm to about 8 mm. It is noted that the diameter of the region of the mesh having the openings, or apertures, may be smaller than the total diameter, e.g. by about 1 to 3 mm.

In a specific embodiment, the ratio of the internal diameter of the flow channel immediately upstream of the lateral opening to the diameter of the able mesh is from about 1 to about 2.5, or from about 1.2 to about 2, respectively. Furthermore, the ratio of the internal er of the flow channel immediately upstream of the lateral opening to the diameter of the aperture region of the vibratable mesh is from about 1.2 to about 4, such as from about 1.6 to about 3.

In all these embodiments, the flow l effectively serves as a mixing channel, thereby advantageously obviating the need for a spacious mixing chamber.

The mixing effectiveness may be increased even more by r reducing the internal diameter of the flow channel at a position immediately downstream of the lateral opening; e.g. providing a ‘step’ which s the internal diameter of the flow channel to about 50 %, as is described in more detail in A1.

In a further embodiment, the inhalation device (100) of the invention comprises a switch (112) for starting and stopping the ion of the l generator (101), as shown e.g. in figure 2. In this context, the operation of the aerosol generator comprises the continuous vibration of the able mesh. In other words, aerosol is continuously generated while the inhalation device is switched on. This is in contrast to many inhalation devices which use breath triggering for switching the l generator on. It has been found that the manual control of the aerosol tor allows the effective inhalation treatment of relatively weak patients, such as tric patients, some of which may not easily achieve the atory flow rates or pressures required to trigger a typical inhalation device.

While continuous aerosol tion is commonly believed to be disadvantageous for an effective aerosol delivery as most of the aerosol generated during the exhalation phase of the patient is typically lost, this is not the case in the device according to the invention, due to the face mask and the features associated with it, as described in more detail below. ally, the inhalation device may have more than one switch for operating the aerosol generator, such as two switches located at opposite sides of the inhalation device in order to ensure easy and convenient control by the patient or the caregiver administering the inhalation therapy to the patient. An exemplary embodiment of such an inhalation device using more than one switch (112) can be seen e.g. in figure 2 or in figure 7.

In a specific embodiment, the inhalation device (100) comprises a) a base unit (118) comprising an electronic controller for controlling the aerosol generator (101), and an upstream portion of the flow channel including the gas inlet opening (104); and b) a mixing channel unit (119), comprising a downstream portion of the flow channel including the lateral opening (111), wherein the ream portion comprises a segment where the flow channel widens in the downstream ion, said segment being oned downstream of the lateral opening.

Such an embodiment may for ce be seen in figure 1. As can be seen there, the mixing channel unit (119) is formed by double walls; the internal, or inner, walls which face the flow of air and/or aerosol and guide the flow towards the face mask (105); and the external, or outer, walls facing the user. The external, or outer, walls have an almost constant diameter from the base unit (118) to the face mask (105), which is suited to fit safely and comfortably into a user’s hand. In contrast, the internal, or inner, walls of the mixing channel unit (119) widen in the downstream direction; i.e. towards the face mask (105). This widening of the downstream portion of the flow channel advantageously slows down the flow velocity of the aerosol-gas-mixture towards the l inlet opening of the face mask. This will reduce the risk of droplets impacting in the mouth and/or the pharyngeal region, as described in A1.

Optionally, the base unit with the electronic controller may further se, or house, a battery (e.g. a rechargeable battery), data storage means and/or a USB-port (116) for charging and data val, such as ed in figure 7.

Further ally, small holes (117) may optionally be provided, e.g. at the rear of the inhalation device (100) as shown in figures 2 and 7, and/or at the bottom side of the inhalation device (100) as shown in figure 5; in order to allow for oling of e.g. the electronic controller and any other parts of the base unit (118) which may generate warmth. However, these small holes (117) are not in fluid connection with the flow channel (110).

Optionally, the aerosol generator (101) with the vibrating mesh (102) and the reservoir (103) for the liquid to be nebulised may be provided in a combination component, which is not separable or not easily separable. This reduces the number of losable components of the device and may facilitate cleaning of the rather small aerosol generator. This combination component may r be provided with fixing means such as a key lock (115), which allow for very easy attachment of the combination component to the inhalation device and at the same time ensure, that the aerosol generator - and particularly the end equipped with the vibrating mesh – is inserted properly and at least partially through the lateral opening (111) of the flow channel (110). This is shown e.g. in figures 2 and 4. Moreover, an exemplary arrangement of some components of an inhalation device suitable for the present invention is described in EP 2 724 741 A1.

In one of the embodiments not depicted herein, the device may comprise a flow ctor in the flow channel upstream of the lateral opening which is adapted to restrict the flow of a gas in the flow channel to a constant flow rate ed in the range from 1 to 5 L/min.

As mentioned, the inhalation device of the invention is particularly useful for delivering a therapeutic aerosol to a patient. Preferably, the use also involves a gas which is supplied at a low flow rate to the gas inlet opening of the device. Such use of the device is an aspect of the invention.

Moreover, the invention provides a method of delivering a nebulised aerosol to a patient, comprising the steps of: (a) providing the inhalation device, or the ation or kit, according to this invention; (b) providing a gas source; and (c) connecting the gas source to the inhalation device such that the gas enters the flow channel through the gas inlet opening at a constant flow rate in the range from 1 to 5 L/min. The preferred and/or al features of the method include all the preferred and/or optional features bed above in the context of the design and operation of the inhalation device itself, or the combination or kit of said device with a pharmaceutical composition for inhalative use as will be described further below.

In a further aspect, the ion provides an assembly, which may also be referred to as an tion system, comprising the inhalation device of the ion and a gas source providing a gas at a constant flow rate in the range from 1 to 5 L/min, wherein the gas source is connected to the inhalation device such that the gas enters the flow channel through the gas inlet opening.

The gas provided by the gas source may be selected from oxygen, air, oxygenenriched air, a mixture of oxygen and nitrogen, and a mixture of helium and oxygen. For the e of connecting the inhalation device to the gas , the gas inlet opening may be shaped as a tube fitting as mentioned above; e.g. a ess steel fitting so that a gas tube may be used to connect the gas source and the inhalation device.

Again, the preferred and/or optional es as described in the context of the disclosure of the inhalation device itself apply also to the assembly, or inhalation system, comprising the device. And in the same way as the inhalation device itself, the assembly, may be provided in a combination or kit with a pharmaceutical ition for inhalative use.

Using a gas consisting of, or enriched with, oxygen for dispersing the nascent aerosol in the inhalation device is particularly useful for the treatment of certain patients, such as paediatric patients, patients affected with a severe disease of the respiratory system, sedated patients, sleeping patients, or adult patients for whom controlled oral inhalation is not possible or is considerably impeded, such as patients with dementia, COPD, severe asthma attacks, cystic fibrosis, amyotrophic lateral sis, emphysema, or heart failure, or patients under sedation or anaesthesia.

Paediatric patients include neonates, infants, toddlers, children, and school children.

In particular, tric patients ing from a lower respiratory tract infection with RSV (LRTI, including bronchiolitis and broncho-pneumonia) may benefit from an onal air and/or oxygen flow during the inhalation treatment. In addition, the inventors observed that an additional gas flow (e.g. 2 L/min) advantageously decreased aerosol deposition within the inhalation device, as described in Example 1 further below.

A further aspect of the invention relates to a combination or kit comprising the inhalation device ing to the invention or an assembly according to the invention and a pharmaceutical composition for inhalation use.

In the ation or kit both components, i.e. the tion device and the ceutical composition may be combined as separate units sold together as a kit.

The same applies s mutandis to a combination or kit of the above mentioned ly and the pharmaceutical composition.

However, as used , a combination does not e the two specified components to be physically combined and sold together, as would typically be the case for a kit, but also includes those combinations that are made by providing one of the components of the combination with instructions that specifically refer to the other component. Moreover, a combination according to the invention also includes the specified tion device or assembly comprising, or being filled with, the respective pharmaceutical composition. For the avoidance of doubt, a reference to an inhalation device or ly filled with a pharmaceutical compositions means that the reservoir of the inhalation device is at least partially filled with the composition.

A pharmaceutical composition, as used herein, is a composition comprising at least one active compound and at least one ceutically acceptable excipient, diluent or carrier. The active compound may also be referred to as active agent, active ingredient, bioactive compound, drug substance, and the like. In the context of the invention, the pharmaceutical composition is for inhalation use, which means that it is formulated and manufactured such that is meets the generally accepted requirements for inhalation use, as for example specified in pharmacopoeias and guidance documents issued by regulatory agencies. For example, a pharmaceutical composition for inhalation contains only excipients which are acceptable for this use, is relatively isotonic, exhibits a vely neutral pH (in particular a pH in the range from about 4 to about 8), and is sterile.

The ceutical composition may be provided in form of a ser on, presented in a vial, ampoule, or bottle, or for instance in the form of prefilled single-use cartridges which are emptied into the reservoir of the inhalation device prior to an inhalation ent.

The pharmaceutical composition may comprise an active agent selected from antibiotics, antiviral agents, bronchodilators, anticholinergics, corticosteroids, hypertonic saline, antibodies, antibody fragments, and immunoglobulin single variable domains. ally, the pharmaceutical composition may se more than one active agent selected from this group.

In a specific embodiment, the pharmaceutical composition may comprise a polypeptide comprising or consisting of one or more immunoglobulin single variable domains.

The term “immunoglobulin single variable domain”, interchangeably used with “single variable domain”, defines molecules wherein the antigen binding site is present on, and formed by, a single globulin . This sets immunoglobulin single variable domains apart from “conventional” immunoglobulins or their fragments, wherein two immunoglobulin domains, in ular two variable domains, interact to form an n g site. Typically, in conventional immunoglobulins, a heavy chain variable domain (VH) and a light chain variable domain (VL) interact to form an antigen binding site. In this case, the complementarity ining regions (CDRs) of both VH and VL will contribute to the antigen binding site, i.e. a total of 6 CDRs will be involved in antigen binding site formation.

In contrast, the binding site of an immunoglobulin single variable domain is formed by a single VH or VL domain. Hence, the antigen binding site of an immunoglobulin single variable domain is formed by no more than three CDRs.

The term “immunoglobulin single variable domain” and “single variable domain” hence does not comprise tional globulins or their fragments which require interaction of at least two variable domains for the formation of an antigen binding site. r, these terms do comprise fragments of conventional immunoglobulins n the antigen binding site is formed by a single variable domain.

The amino acid sequence and structure of an immunoglobulin single variable domain can be considered - without however being limited thereto - to be comprised of four ork regions or “FR’s”, which are referred to in the art and herein as “Framework region 1” or “FR1”; as work region 2” or “FR2”; as “Framework region 3” or “FR3”; and as work region 4” or “FR4”, tively; which framework regions are interrupted by three complementary determining s or “CDR’s”, which are referred to in the art as “Complementarity Determining Region 1” or “CDR1”; as “Complementarity Determining Region 2” or “CDR2”; and as “Complementarity Determining Region 3” or “CDR3”, respectively. Such single variable domains are most preferably such that they comprise an immunoglobulin fold or are capable of forming, under suitable conditions, an globulin fold. As such, the single le domain may for example comprise a light chain le domain sequence (e.g. a VL-sequence); or a heavy chain variable domain sequence (e.g. a VH- sequence or VHH sequence); as long as it is capable of forming a single antigen binding unit (i.e. a functional antigen binding unit that essentially consists of the single variable domain, such that the single antigen binding domain does not need to interact with another variable domain to form a functional antigen binding unit, as is for example the case for the variable domains that are present in for example conventional antibodies [Link] javascript:AL_get(this,%20'jour',%20'Nature.'); and scFv fragments that need to ct with another variable domain – e.g. h a VH/VL interaction – to form a functional antigen g ).

In one embodiment of the invention, the immunoglobulin single variable s are light chain variable domain sequences (e.g. a VL-sequence), or heavy chain variable domain sequences (e.g. a VH-sequence); more specifically, the globulin single variable domains can be heavy chain variable domain sequences that are derived from a conventional four-chain antibody or heavy chain variable domain ces that are derived from a heavy chain antibody.

For example, the single variable domain or immunoglobulin single variable domain may be a (single) domain antibody, a “dAb”or dAb or a Nanobody (including but not limited to a VHH); other single variable domains, or any suitable fragment of any one thereof.

For a general description of (single) domain antibodies, reference is also made to the prior art cited herein, as well as to EP 0368684 A1. For the term “dAb’s”, reference is for example made to Ward et al. 1989 (Nature 341: 544-546), to Holt et al.2003 (Trends Biotechnol. 21: 484-490); as well as to for example A2, A1, A2, A2, A2, A2. It should also be noted that, although less preferred in the context of the present invention because they are not of ian origin, single le domains can be derived from certain species of shark (for example, the so-called “IgNAR domains”, see for example A1).

In particular, the globulin single variable domain may be a Nanobody® (as defined herein) or a suitable fragment thereof. (Note: Nanobody®, Nanobodies® and Nanoclone® are registered trademarks of Ablynx N.V.). For a further description of VHH’s and Nanobodies, nce is made to the review article by Muyldermans 2001 (Reviews in Molecular Biotechnology 74: 277-302), WO 01985 A2 and A2. As described in these references, Nanobodies (in particular VHH sequences and partially humanized VHH sequences) can in particular be characterized by the presence of one or more “Hallmark residues” in one or more of the framework sequences. A further description of the dies, including humanization and/or camelization of Nanobodies, as well as other modifications, parts or fragments, derivatives or “Nanobody fusions”, multivalent constructs (including some non-limiting examples of linker sequences) and different modifications to increase the half-life of the Nanobodies and their preparations can be found e.g. in A2 and Thus, in the meaning of the present invention, the term “immunoglobulin single variable domain” or “single variable domain” comprises polypeptides which are derived from a non-human source, ably a camelid, preferably a camelid heavy chain antibody. They may be humanized, as previously described. Moreover, the term comprises polypeptides derived from melid sources, e.g. mouse or human, which have been “camelized”, as e.g. described in Davies and Riechmann 1994 (FEBS 339: 285- 290), 1995 chnol. 13: 475-479), 1996 (Prot. Eng. 9: 531-537) and Riechmann and Muyldermans 1999 (J. l. Methods 231: 25-38).

Again, such Nanobodies may be derived in any suitable manner and from any suitable source, and may for example be naturally occurring VHH sequences (i.e. from a suitable s of Camelid) or tic or semi-synthetic amino acid sequences, including but not limited to partially or fully “humanized” VHH, “camelized” immunoglobulin sequences (and in particular camelized VH), as well as Nanobodies and/or VHH that have been obtained by techniques such as ty maturation (for example, starting from tic, random or naturally occurring immunoglobulin sequences, such as VHH sequences), CDR ng, veneering, combining fragments derived from different immunoglobulin sequences, PCR assembly using overlapping primers, and similar techniques for engineering immunoglobulin ces well known to the d person; or any suitable combination of any of the foregoing.

In a specific embodiment, the strength of the pharmaceutical composition is adapted for a paediatric t.

In a particular embodiment, the pharmaceutical composition comprises an anti- RSV agent. As used herein, an anti-RSV agent is an active agent capable of treating or managing an infection with human respiratory syncytial virus (RSV). The anti-RSV agent may be a small lar ral compound or a biological such as an antibody or an antibody fragment. An example of an antibody that may be used according to the invention is palivizumab, which is a monoclonal antibody directed against the RSV surface fusion protein.

In a r ic embodiment, the anti-RSV agent may e.g. be a polypeptide comprising or essentially consisting of one or more anti-RSV immunoglobulin single variable domains. It has been found by the inventors that a pharmaceutical ition comprising such agent may be effectively delivered to paediatric patients including neonates, infants and even toddlers. It is believed that these polypeptides have never before been effectively delivered to such patients, using a known inhalation .

The anti-RSV agent used according to the invention may in particular be a polypeptide comprising or essentially consisting of one or more anti-RSV globulin single variable domains, wherein the anti-RSV immunoglobulin single variable domain comprises a CDR1 having the amino acid ce of SEQ ID NO: 46, a CDR2 having the amino acid sequence of one of SEQ ID NOs: 49-50, and a CDR3 having the amino acid sequence of SEQ ID NO: 61 (see also Table A-1).

In a red embodiment, the anti-RSV immunoglobulin single variable domain is selected from one of the amino acid sequences of SEQ ID NOs: 1-34 (Table A-2).

In a preferred embodiment, the polypeptides encompass constructs comprising three or more antigen binding units in the form of single variable domains, as outlined above. For example, three or more immunoglobulin single variable domains that bind hRSV (also referred to herein as hRSV immunoglobulin single variable domain(s)”) can be linked to form a trivalent or multivalent construct. Preferably the polypeptide of the ion consists of three anti-hRSV immunoglobulin single variable domains.

In the polypeptides described above, the anti-hRSV immunoglobulin single variable domains may be linked directly to each other and/or via one or more suitable linkers or spacers. Suitable spacers or linkers for use in multivalent polypeptides will be clear to the skilled , and may lly be any linker or spacer used in the art to link amino acid ces. Preferably, said linker or spacer is suitable for use in constructing proteins or polypeptides that are intended for pharmaceutical use.

Some particularly preferred spacers include the spacers and linkers that are used in the art to link antibody fragments or antibody domains. These include the linkers mentioned in the general background art cited above, as well as for example linkers that are used in the art to construct diabodies or ScFv fragments (in this respect, however, it should be noted that, whereas in diabodies and in ScFv fragments, the linker sequence used should have a length, a degree of flexibility and other properties that allow the pertinent VH and VL domains to come together to form the complete antigen-binding site, there is no particular limitation on the length or the flexibility of the linker used in the polypeptide of the invention, since each globulin single variable domain by itself forms a complete antigen-binding site).

For example, a linker may be a suitable amino acid sequence, and in particular amino acid sequences of n 1 and 50, preferably between 1 and 30, such as between 1 and 20 or between 1 and 10 amino acid es. Widely used peptide linkers comprise Gly-Ser repeats, e.g. -Ser in one, two, three, four, five, six or more repeats, or for example of the type (glyxsery)z, such as (for example (gly4ser)3 or (gly3ser2)3, as described in WO 99/42077 A2, or hinge-like regions such as the hinge regions of naturally occurring heavy chain antibodies or similar sequences (such as described in WO 94/04678 A1). Some other particularly preferred linkers are polyalanine (such as AAA), as well as the linkers mentioned in Table A-4.

In a further red embodiment, the anti-RSV agent is a ptide selected from one of the amino acid sequences of SEQ ID NOs: 65-85; such as e.g. the amino acid sequence of SEQ ID NO: 71 (Table A-3).

In one of the preferred embodiments, the pharmaceutical composition comprises the anti-RSV polypeptide at a concentration of about 10 to 100 mg/mL, such as 50 mg/mL or more, and/or a dose of the agent in a volume from about 0.15 mL to about 0.40 mL.

Preferably, the combination or kit comprises instructions to administer such active agent based on one or more of these SV immunoglobulin single variable domains, such as e.g. one of SEQ ID NOs: 65-85, using daily doses of about 1 to 2 mg/kg body weight, in particular if the patient is a paediatric patient, preferably of not more than 2 years of age, or not more than 3 years.

Earlier modelling studies of the inventors for pediatric populations with these compounds revealed that the dose determination was mainly guided by pulmonary ry, distribution and drug absorption ences between the developing child’s lung and the adult’s lung. The primary g parameter for systemic as well as local pharmacokinetics in the RSV infected children appeared to be the amount of drug in alveolar absorption space.

The above described polypeptides, and in particular the polypeptides selected from one of the amino acid sequences of SEQ ID NOs: 65-85, bind the F-protein of hRSV with a KD of 5x10-10 M or less (as measured by immunoassay), and neutralize hRSV with an IC90 of 90 ng/mL or less (as ed in a micro-neutralization assay). A clinically meaningful reduction of RSV activity is obtained at a target concentration of 9 µg/mL.

This concentration of 9 µg/mL may be reached in the alveolar space using a deposited dose of 0.020 to 0.040 mg/kg daily, preferably 0.020 to 0.035 mg/kg daily, such as e.g. 0.024 mg/kg daily. For this purpose the polypeptide may be administered to a child by inhalation at a nominal dose of 1.00 to 2.00 mg/kg daily, preferably 1.00 to 1.75 mg/kg daily, such as e.g. 1.20 mg/kg daily.

This estimation is based on aerosol deposition studies performed with the Sophia Anatomical Infant Nose Throat ) model in which the polypeptide, e.g. SEQ ID NO: 71, was administered with an inhalation device according to the invention, more specifically a vibrating mesh ser with a constant flow rate of 2 L/min additional air or oxygen (see Example 1). The results showed that, from the total dose filled into the reservoir of the nebuliser, approximately 20 % is expected to be inhaled.

Optionally, the combination or kit of the inhalation device or assembly with the ceutical composition for inhalation use comprising an anti-RSV agent further comprises a bronchodilator. The bronchodilator may be incorporated within the pharmaceutical ition which also contains the anti-RSV agent. Alternatively, it may be provided in a separate pharmaceutical composition which may be filled into the reservoir of the inhalation device tely from, or along with, the composition comprising the anti-RSV agent.

There are two main classes of bronchodilators, namely the sympathomimetics, including short-acting and cting beta2-mimetics; and the anticholinergics.

In one ment, the odilator belongs to the class of beta2-mimetics.

Optionally, the beta2-mimetic is a long-acting beta2-mimetic and in particular a bronchodilator selected from formoterol, salmeterol, or salt and/or mixtures thereof.

Alternatively, the bronchodilator may be a short-acting beta2-mimetic substance, such as a bronchodilator selected from salbutamol, terbutaline, pirbuterol, rol, tulobuterol, levosabutamol, and the salts and mixtures thereof. In a specific [Link] http://en.wikipedia.org/wiki/Albuterol [Link] http://en.wikipedia.org/wiki/Bitolterol [Link] http://en.wikipedia.org/wiki/Ephedrine [Link] http://en.wikipedia.org/wiki/Epinephrine [Link] http://en.wikipedia.org/wiki/Isoetharine [Link] http://en.wikipedia.org/wiki/Isoproterenol [Link] http://en.wikipedia.org/wiki/Metaproterenol [Link] http://en.wikipedia.org/wiki/Pirbuterol [Link] http://en.wikipedia.org/wiki/Racepinephrine [Link] http://en.wikipedia.org/wiki/Ritodrine [Link] http://en.wikipedia.org/wiki/Terbutaline embodiment, the bronchodilator is salbutamol and is administered at a dose of 200 micrograms.

In a further alternative embodiment, the bronchodilator belongs to the class of olinergics, e.g. an anticholinergic agent selected from tiotropium, oxitropium, ipratropium bromide and mixtures thereof.

Without being limiting, additional bronchodilators for use in the products and methods of the invention include albuterol, bitolterol, ephedrine, epinephrine, isoetharine, isoproterenol, metaproterenol, pirbuterol, racepinephrine, ritodrine, terbutaline, levosabutamol, levabuterol, clenbuterol, amphetamine, methamphetamine, cocaine, theophylline, caffeine, theobromine, tetrahydrocannabinol (THC), and methylendioxypyrovaleron (MDPV).

As mentioned, the inhalation device according to the invention or the assembly of this inhalation device with a gas source as described above, or the respective kits or ations with a pharmaceutical composition for inhalative use, may be employed for use in the ent of a patient suffering from a e affecting the respiratory system.

The disease may be atory infection (an ion of the respiratory tract), such as a Respiratory ial Virus (RSV) ion, and more ically a RSV lower respiratory tract infection.

The patient suffering from the respiratory disease may be a paediatric patient, such as a neonate, an infant, a toddler, or a school child. In one embodiment, the patient may be a child younger than 24 ; in one embodiment, the t may be a child younger than 36 months, more specifically a child aged 1 month to less than 24 months, 1 month to less than 36 months, 5 months to less than 24 months, or 5 months to less than 36 months. In a particular embodiment, the child is hospitalised for RSV lower respiratory tract infection.

Alternatively, the patient may be an adult for whom controlled oral inhalation is not possible or is considerably impeded, such as patients with dementia, mental impairments, COPD, severe asthma attacks, cystic fibrosis, ophic lateral sclerosis, emphysema or heart failure, or patients under sedation or anaesthesia.

In a further aspect, the invention relates to a method of delivering a nebulised l to a young child, such as a e, infant or toddler, who is suffering from an fection, comprising the steps of (a) providing the inhalation device according to this invention; (b) providing a gas source; (c) connecting the gas source to the inhalation device such that the gas enters the flow l h the gas inlet opening at a constant flow rate in the range from 1 to 5 L/min, in particular at 2 L/min; and (d) providing a nebuliser solution sing at least an anti-RSV agent selected from one of the amino acid sequences of SEQ ID NOs: 65-85.

Example 1 – Deposition study for an anti-RSV Nanobody agent using the inhalation system according to the invention SEQ ID NO: 71 (Table A-3) was used in an experiment evaluating the effect of simulated inhalation and aerosol administration, with and without air supply, on the d drug amount.

The determination of the inhaled dose was performed with the Sophia Anatomical Infant Nose Throat (SAINT) model; an anatomically correct representation of the upper airways of a 9 month old child, which is built using stereolithographic techniques and used for studying aerosol deposition in young children (see e.g. Janssens et al.; J Aerosol Med. 2001 Winter;14(4):433-41.).

The experimental set-up is represented in figure 8; showing the inhalation device (100) with the reservoir (103), the gas inlet opening (104), the flow channel, or mixing l, (110) and the face mask (105) with the one-way exhalation valve or two-way inhalation/exhalation valve (109). Figure 8 further shows the patient contacting surface (108) in tight contact with the hroat portion (201) of the SAINT model (200), the nasal portion (202) of the SAINT model, and a glass fibre filter assembly (300) representing the lower atory tract. The glass fibre filter ly (300) is connected to a breath simulator, which in turn is connected to, and controlled by a computer; both not depicted in figure 8.

The nebuliser was connected to the SAINT model via the attached face mask covering nose and mouth of the model. Behind the SAINT model (in the direction of the air, or aerosol flow), a glass fibre filter representing the lower respiratory tract, was connected. Aerosol was collected during product nebulisation and simulated administration, using a breath simulator (ASL 5000, IngMar Medical, USA) to mimick typical breathing parameters such as atory rate, tidal volume and inhalation/exhalation ratio.

Different breathing parameter protocols were employed; e.g. an tion/exhalation ratio 1:3 as common for infants, and a tidal volume of 45 mL and a respiratory rate of 40 breaths per minute, which represents the distressed ing pattern of a 5 months old infant (see e.g. Totapally et al.; Critical Care 2002, 6:160-165).

The reservoir of the inhalation device was filled with 400 µL of the SEQ ID NO: 71 formulation using a 1-mL syringe (i.e. the filling dose). The inhalation device was weighed before and after filling, in order to determine the filling dose. Then continuous nebulisation was started in three different additional air supply gs: 1) no additional air supply; gas inlet g is open, 2) no additional air supply; gas inlet opening is blocked, and 3) additional air supply at 2 L/min via the gas inlet opening. sation times until auto shut-off of the device were recorded. After nebulisation, the device components (i.e., reservoir, mixing l, face mask) and the SAINT model compartments (i.e., nasopharyngeal airway and face/oral cavity) and the lower atory tract glass fibre filter were swilled with a defined volume of appropriate solvent (here distilled water) to collect samples and measure any deposited SEQ ID NO: 71. The samples were analysed for concentration via conductivity meter using calibration curves (because of the diluted SEQ ID NO: 71 concentrations in the collected samples, it was more sensitive to measure the conductivity of sodium chloride and phosphate salts present in the SEQ ID NO: 71 formulation).

The recorded deposition data (see Table 1 below) were used to determine, or calculate, e.g. the emitted dose, delivered dose, inhaled dose, lung dose, residual dose (all in rams and/or percentages of the filling dose).

The filling dose is the amount of drug that in theory could be nebulised and ed for inhalation; disregarding e.g. any losses into the ambient air, amounts nebulised during the exhalation phase, or losses within the device.

The exhaled dose is the drug amount ated in, or lost to, the environment; calculated as the difference of the total dose minus the cumulative drug amounts deposited within the device without the face mask (i.e. mainly in the aerosol generator and the flow channel, or mixing channel), in the face mask, in the SAINT model components (both nasal and face/throat) and in the glass fibre .

The emitted dose is the drug amount emitted by the device at the downstream end of the mixing channel; calculated as the sum of the d dose plus the delivered dose. The emitted dose may also be understood as the total dose minus the drug amount deposited within the nebuliser and its mixing channel (but not the face mask).

The delivered dose is the drug amount available for inhalation; calculated from the tive amounts of drug deposited in the face mask, the SAINT model components (both nasal and face/throat) and the glass fibre filter (the latter is also referred to as the “lung dose”).

The inhaled dose is the drug amount actually inhaled; i.e. the cumulative amounts of drug ted in the nasal SAINT model component and the glass fibre filter.

The lung dose is the drug amount deposited in the glass fibre filter which represents the lower respiratory tract.

Table 1 shows the distribution of the drug, as measured in the described experiment, as well as some calculated doses in percentage of the g dose: Percentage of filling dose [%] Measured depositions ated Neb.

Additional air Time supply setting glass [sec] device SAINT fibre Deli- Exhaled face SAINT Inhaled w/o (face, filter vered dose / mask (nasal) dose mask throat) (=lung dose losses dose) 100 54.6 8.1 0.9 3.6 5.2 8.8 17.8 27.6 (no air) 133 86.2 5.3 0.8 0.5 2.3 2.9 8.9 4.9 (blocked) 130 20.7 4.6 1.8 4.6 8.6 13.1 19.5 59.8 (2 L/min) These data show that the dose inhaled and the dose deposited in the glass fibre filter / the lower respiratory tract (“lung” dose) is higher when the air supply is present.

Also, the dose deposited within the device components is d significantly by the additional air supply.

Tables Table A-1: Amino acid sequences of anti-hRSV globulin single variable domains (with FR and CDR sequences indicated) Nanobody SEQ FR1 SEQ CDR 1 SEQ FR2 SEQ CDR 2 SEQ FR3 SEQ CDR 3 SEQ FR4 SEQ ID ID ID ID ID ID ID ID NC41 1 EVQLVESGGGLVQAGG 35 NYVLG 46 WFRQAPG 47 AINWRGDITI 49 RFTISRDNAKNTGYLQ 51 GTPLNPGAYI 61 WGRGTQVTVSS 62 SLSISCAASGGSLS A GPPNVEG MNSLAPDDTAVYYCGA YDWSYDY NC41 2 SGGGLVQAGG 36 NYVLG 46 WFRQAPG 47 AINWRGDITI 49 RFTISRDNAKNTGYLQ 51 GTPLNPGAYI 61 WGRGTQVTVSS 62 E1D SLSISCAASGGSLS KEREFVA GPPNVEG MNSLAPDDTAVYYCGA YDWSYDY NC41v01 3 EVQLLESGGGLVQPGG 37 NYVLG 46 WFRQAPG 48 DITI 49 RFTISRDNAKNTLYLQ 52 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLRLSCAASGGSLS KGREFVA GPPNVEG MNSLAPEDTAVYYCGA YDWSYDY NC41v02 4 EVQLLESGGGLVQPGG 38 NYVLG 46 G 48 AINWRGDITI 49 RFTISRDNSKNTLYLQ 53 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLRISCAASGGSLS KGREFVA GPPNVEG MNSLAPEDTAVYYCGA YDWSYDY NC41v03 5 EVQLLESGGGLVQPGG 38 NYVLG 46 G 48 AINWRGDITI 49 RFTISRDNSKNTLYLQ 54 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLRISCAASGGSLS KGREFVA G MNSLRPEDTAVYYCGA YDWSYDY NC41v03 6 DVQLLESGGGLVQPGG 39 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 DNSKNTLYLQ 54 GTPLNPGAYI 61 WGQGTLVTVSS 63 E1D SLRISCAASGGSLS KGREFVA GPPNVEG MNSLRPEDTAVYYCGA YDWSYDY NC41v04 7 EVQLLESGGGLVQPGG 40 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 RFTISRDNSKNTLYLQ 55 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLSISCAASGGSLS KGREFVA GPPNVEG MNSLRPDDTAVYYCGA YDWSYDY 8 EVQLLESGGGLVQPGG 40 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 RFTISRDNSKNTLYLQ 53 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLSISCAASGGSLS KGREFVA GPPNVEG EDTAVYYCGA YDWSYDY NC41v06 9 EVQLLESGGGLVQPGG 37 NYVLG 46 WFRQAPG 48 AINWRDDITI 50 RFTISRDNAKNTLYLQ 56 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLRLSCAASGGSLS KGREFVA GPPNVEG MNSLRPEDTAVYYCGA YDWSYDY NC41v06 10 DVQLLESGGGLVQPGG 41 NYVLG 46 WFRQAPG 48 AINWRDDITI 50 RFTISRDNAKNTLYLQ 56 GTPLNPGAYI 61 WGQGTLVTVSS 63 E1D SLRLSCAASGGSLS A GPPNVEG EDTAVYYCGA YDWSYDY 7 11 EVQLLESGGGLVQPGG 40 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 RFTISRDNAKNTLYLQ 57 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLSISCAASGGSLS KGREFVA GPPNVEG MNSLAPDDTAVYYCGA YDWSYDY NC41v08 12 EVQLLESGGGLVQPGG 40 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 RFTISRDNAKNTLYLQ 56 GTPLNPGAYI 61 VTVSS 63 AASGGSLS KGREFVA GPPNVEG MNSLRPEDTAVYYCGA YDWSYDY NC41v09 13 SGGGLVQPGG 40 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 RFTISRDNSKNTLYLQ 55 GAYI 61 WGQGTLVTVSS 63 SLSISCAASGGSLS KGREFVA GPPNVEG MNSLRPDDTAVYYCGA YDWSYDY NC41v10 14 SGGGLVQPGG 40 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 RFTISRDNAKNTGYLQ 51 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLSISCAASGGSLS KGREFVA GPPNVEG MNSLAPDDTAVYYCGA Y NC41v11 15 EVQLLESGGGLVQAGG 42 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 RFTISRDNAKNTGYLQ 51 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLSISCAASGGSLS KGREFVA GPPNVEG MNSLAPDDTAVYYCGA YDWSYDY NC41v12 16 EVQLLESGGGLVQPGG 40 NYVLG 46 WFRQAPG 47 AINWRGDITI 49 RFTISRDNAKNTGYLQ 51 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLSISCAASGGSLS KEREFVA GPPNVEG MNSLAPDDTAVYYCGA YDWSYDY NC41v13 17 EVQLLESGGGLVQPGG 37 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 RFTISRDNAKNTGYLQ 58 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLRLSCAASGGSLS KGREFVA GPPNVEG MNSLAPEDTAVYYCGA YDWSYDY Table A-1: ued Nanobody® SEQ FR1 SEQ CDR 1 SEQ FR2 SEQ CDR 2 SEQ FR3 SEQ CDR 3 SEQ FR4 SEQ ID ID ID ID ID ID ID ID NC41v14 18 EVQLLESGGGLVQPGG 37 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 RFTISRDNSKNTLYLQ 53 GAYI 61 WGQGTLVTVSS 63 SLRLSCAASGGSLS KGREFVA GPPNVEG MNSLAPEDTAVYYCGA YDWSYDY NC41v15 19 EVQLLESGGGLVQAGG 43 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 RFTISRDNAKNTLYLQ 52 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLRLSCAASGGSLS KGREFVA GPPNVEG MNSLAPEDTAVYYCGA YDWSYDY NC41v17 20 EVQLLESGGGLVQPGG 37 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 RFTISRDNSKNTLYLQ 54 GAYI 61 WGQGTLVTVSS 63 SLRLSCAASGGSLS KGREFVA GPPNVEG MNSLRPEDTAVYYCGA YDWSYDY NC41v17 21 DVQLLESGGGLVQPGG 41 NYVLG 46 WFRQAPG 48 AINWRGDITI 49 RFTISRDNSKNTLYLQ 54 GTPLNPGAYI 61 WGQGTLVTVSS 63 E1D SLRLSCAASGGSLS KGREFVA GPPNVEG EDTAVYYCGA YDWSYDY NC41v18 22 EVQLLESGGGLVQPGG 37 NYVLG 46 WFRQAPG 48 AINWRDDITI 50 RFTISRDNSKNTLYLQ 54 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLRLSCAASGGSLS KGREFVA GPPNVEG MNSLRPEDTAVYYCGA YDWSYDY NC41v18 23 DVQLLESGGGLVQPGG 41 NYVLG 46 WFRQAPG 48 AINWRDDITI 50 RFTISRDNSKNTLYLQ 54 GTPLNPGAYI 61 WGQGTLVTVSS 63 E1D SLRLSCAASGGSLS KGREFVA GPPNVEG MNSLRPEDTAVYYCGA Y NC41v19 24 EVQLVESGGGLVQPGG 44 NYVLG 46 WFRQAPG 47 AINWRGDITI 49 RFTISRDNAKNTGYLQ 51 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLRLSCAASGGSLS KEREFVA GPPNVEG MNSLAPDDTAVYYCGA YDWSYDY NC41v20 25 EVQLVESGGGLVQPGG 44 NYVLG 46 WFRQAPG 47 DITI 49 RFTISRDNAKNTGYLQ 59 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLRLSCAASGGSLS KEREFVA GPPNVEG MNSLRPDDTAVYYCGA YDWSYDY NC41v21 26 EVQLVESGGGLVQPGG 44 NYVLG 46 WFRQAPG 47 AINWRGDITI 49 RFTISRDNAKNTGYLQ 58 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLRLSCAASGGSLS KEREFVA GPPNVEG MNSLAPEDTAVYYCGA YDWSYDY NC41v21 27 DVQLVESGGGLVQPGG 45 NYVLG 46 WFRQAPG 47 AINWRGDITI 49 RFTISRDNAKNTGYLQ 58 GTPLNPGAYI 61 WGQGTLVTVSS 63 E1D AASGGSLS KEREFVA GPPNVEG MNSLAPEDTAVYYCGA Y NC41v22 28 SGGGLVQPGG 44 NYVLG 46 WFRQAPG 47 AINWRGDITI 49 RFTISRDNAKNTGYLQ 60 GTPLNPGAYI 61 WGQGTLVTVSS 63 SLRLSCAASGGSLS KEREFVA GPPNVEG MNSLRPEDTAVYYCGA YDWSYDY NC41v22 29 DVQLVESGGGLVQPGG 45 NYVLG 46 WFRQAPG 47 AINWRGDITI 49 RFTISRDNAKNTGYLQ 60 GTPLNPGAYI 61 WGQGTLVTVSS 63 E1D SLRLSCAASGGSLS KEREFVA GPPNVEG MNSLRPEDTAVYYCGA YDWSYDY NC41v23 30 EVQLVESGGGLVQPGG 44 NYVLG 46 WFRQAPG 47 AINWRGDITI 49 DNAKNTGYLQ 51 GTPLNPGAYI 61 WGRGTLVTVSS 64 SLRLSCAASGGSLS KEREFVA GPPNVEG MNSLAPDDTAVYYCGA YDWSYDY NC41v24 31 EVQLVESGGGLVQPGG 44 NYVLG 46 G 47 AINWRGDITI 49 RFTISRDNAKNTGYLQ 59 GTPLNPGAYI 61 VTVSS 64 SLRLSCAASGGSLS A G MNSLRPDDTAVYYCGA YDWSYDY NC41v25 32 EVQLVESGGGLVQPGG 44 NYVLG 46 WFRQAPG 47 AINWRGDITI 49 RFTISRDNAKNTGYLQ 58 GTPLNPGAYI 61 WGRGTLVTVSS 64 SLRLSCAASGGSLS A GPPNVEG MNSLAPEDTAVYYCGA Y NC41v26 33 SGGGLVQPGG 44 NYVLG 46 WFRQAPG 47 AINWRGDITI 49 RFTISRDNAKNTGYLQ 60 GTPLNPGAYI 61 WGRGTLVTVSS 64 SLRLSCAASGGSLS KEREFVA GPPNVEG EDTAVYYCGA YDWSYDY NC41v26 34 DVQLVESGGGLVQPGG 45 NYVLG 46 WFRQAPG 47 AINWRGDITI 49 RFTISRDNAKNTGYLQ 60 GTPLNPGAYI 61 WGRGTLVTVSS 64 E1D SLRLSCAASGGSLS A GPPNVEG MNSLRPEDTAVYYCGA YDWSYDY Table A-2: Amino acid sequences of anti-hRSV immunoglobulin single variable domains Nanobody® SEQ ID Sequence NC41 1 SGGGLVQAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGA GTPLNPGAYIYDWSYDYWGRGTQVTVSS NC41 E1D 2 DVQLVESGGGLVQAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGA GTPLNPGAYIYDWSYDYWGRGTQVTVSS NC41v01 3 EVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTLYLQMNSLAPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS 2 4 EVQLLESGGGLVQPGGSLRISCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNSKNTLYLQMNSLAPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v03 5 EVQLLESGGGLVQPGGSLRISCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v03 E1D 6 DVQLLESGGGLVQPGGSLRISCAASGGSLSNYVLGWFRQAPGKGREFVAA INWRGDITIGPPNVEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGAGT PLNPGAYIYDWSYDYWGQGTLVTVSS NC41v04 7 EVQLLESGGGLVQPGGSLSISCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNSKNTLYLQMNSLRPDDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS 8 EVQLLESGGGLVQPGGSLSISCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNSKNTLYLQMNSLAPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v06 9 EVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRDDITIGPPNVEGRFTISRDNAKNTLYLQMNSLRPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v06 E1D 10 DVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAI NWRDDITIGPPNVEGRFTISRDNAKNTLYLQMNSLRPEDTAVYYCGAGTP LNPGAYIYDWSYDYWGQGTLVTVSS NC41v07 11 EVQLLESGGGLVQPGGSLSISCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTLYLQMNSLAPDDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v08 12 EVQLLESGGGLVQPGGSLSISCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTLYLQMNSLRPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS 9 13 EVQLLESGGGLVQPGGSLSISCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNSKNTLYLQMNSLRPDDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v10 14 EVQLLESGGGLVQPGGSLSISCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v11 15 EVQLLESGGGLVQAGGSLSISCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS 2 16 EVQLLESGGGLVQPGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVA DITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGA GAYIYDWSYDYWGQGTLVTVSS NC41v13 17 EVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS Table A-2: Continued Nanobody® SEQ ID Sequence NC41v14 18 EVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNSKNTLYLQMNSLAPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v15 19 SGGGLVQAGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTLYLQMNSLAPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v17 20 EVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGA GAYIYDWSYDYWGQGTLVTVSS NC41v17 E1D 21 DVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRGDITIGPPNVEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v18 22 EVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVA AINWRDDITIGPPNVEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS 8 E1D 23 DVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAA INWRDDITIGPPNVEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGAGT PLNPGAYIYDWSYDYWGQGTLVTVSS NC41v19 24 EVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v20 25 EVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLRPDDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v21 26 EVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v21 E1D 27 DVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPEDTAVYYCGA GAYIYDWSYDYWGQGTLVTVSS NC41v22 28 EVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLRPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v22 E1D 29 DVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLRPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGQGTLVTVSS NC41v23 30 EVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGA GTPLNPGAYIYDWSYDYWGRGTLVTVSS NC41v24 31 EVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLRPDDTAVYYCGA GTPLNPGAYIYDWSYDYWGRGTLVTVSS NC41v25 32 EVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPEDTAVYYCGA GAYIYDWSYDYWGRGTLVTVSS NC41v26 33 SGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLRPEDTAVYYCGA GAYIYDWSYDYWGRGTLVTVSS NC41v26 E1D 34 DVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVA AINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLRPEDTAVYYCGA GTPLNPGAYIYDWSYDYWGRGTLVTVSS Table A-3: Amino acid sequences of preferred polypeptides of the invention Nanobody® SEQ ID NO: ce RSV407 65 EVQLVESGGGLVQAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVAAI NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPL NPGAYIYDWSYDYWGRGTQVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLV QAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPN VEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPLNPGAYIYDWSYD YWGRGTQVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLVQAGGSLSISCAA SGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPNVEGRFTISRDNA KNTGYLQMNSLAPDDTAVYYCGAGTPLNPGAYIYDWSYDYWGRGTQVTVSS RSV408 66 EVQLVESGGGLVQAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVAAI NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPL NPGAYIYDWSYDYWGRGTQVTVSSAAAEVQLVESGGGLVQAGGSLSISCAA SGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPNVEGRFTISRDNA KNTGYLQMNSLAPDDTAVYYCGAGTPLNPGAYIYDWSYDYWGRGTQVTVSS AAAEVQLVESGGGLVQAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFV AAINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAG TPLNPGAYIYDWSYDYWGRGTQVTVSS RSV409 67 EVQLVESGGGLVQAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVAAI NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPL NPGAYIYDWSYDYWGRGTQVTVSSGGGGSGGGSEVQLVESGGGLVQAGGSL SISCAASGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPNVEGRFT ISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPLNPGAYIYDWSYDYWGRGT GGGGSGGGSEVQLVESGGGLVQAGGSLSISCAASGGSLSNYVLGW FRQAPGKEREFVAAINWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLA PDDTAVYYCGAGTPLNPGAYIYDWSYDYWGRGTQVTVSS RSV410 68 SGGGLVQAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVAAI NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPL NPGAYIYDWSYDYWGRGTQVTVSSGGGGSGGGGSGGGGSGGGGSEVQLVES GGGLVQAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVAAINWRGDIT EGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPLNPGAYIY DWSYDYWGRGTQVTVSSGGGGSGGGGSGGGGSGGGGSEVQLVESGGGLVQA GGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPNVE GRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPLNPGAYIYDWSYDYW GRGTQVTVSS RSV411 69 EVQLVESGGGLVQAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVAAI NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPL NPGAYIYDWSYDYWGRGTQVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLV QAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPN VEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPLNPGAYIYDWSYD YWGRGTQVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLVQPGGSLRLSCAA SGLTLDYYALGWFRQAPGKEREGVSCISSSDHSTTYTDSVKGRFTISWDNA KNTLYLQMNSLKPGDTAVYYCAADPALGCYSGSYYPRYDYWGQGTQVTVSS RSV413 70 EVQLVESGGGLVQAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVAAI NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPL NPGAYIYDWSYDYWGRGTQVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLV QPGGSLRLSCAASGLTLDYYALGWFRQAPGKEREGVSCISSSDHSTTYTDS ISWDNAKNTLYLQMNSLKPGDTAVYYCAADPALGCYSGSYYPRYD YWGQGTQVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLVQAGGSLSISCAA SGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPNVEGRFTISRDNA KNTGYLQMNSLAPDDTAVYYCGAGTPLNPGAYIYDWSYDYWGRGTQVTVSS Table A-3: Continued RSV434 71 DVQLVESGGGLVQAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVAAI NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPL NPGAYIYDWSYDYWGRGTQVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLV QAGGSLSISCAASGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPN VEGRFTISRDNAKNTGYLQMNSLAPDDTAVYYCGAGTPLNPGAYIYDWSYD YWGRGTQVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLVQAGGSLSISCAA NYVLGWFRQAPGKEREFVAAINWRGDITIGPPNVEGRFTISRDNA KNTGYLQMNSLAPDDTAVYYCGAGTPLNPGAYIYDWSYDYWGRGTQVTVSS RSV414 72 EVQLLESGGGLVQPGGSLRISCAASGGSLSNYVLGWFRQAPGKGREFVAAI V03 TIGPPNVEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGAGTPL NPGAYIYDWSYDYWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLV QPGGSLRISCAASGGSLSNYVLGWFRQAPGKGREFVAAINWRGDITIGPPN VEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYD YWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLVQPGGSLRISCAA SGGSLSNYVLGWFRQAPGKGREFVAAINWRGDITIGPPNVEGRFTISRDNS KNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYDYWGQGTLVTVSS RSV443 73 DVQLLESGGGLVQPGGSLRISCAASGGSLSNYVLGWFRQAPGKGREFVAAI V3D TIGPPNVEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGAGTPL NPGAYIYDWSYDYWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLV QPGGSLRISCAASGGSLSNYVLGWFRQAPGKGREFVAAINWRGDITIGPPN VEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYD YWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLVQPGGSLRISCAA SGGSLSNYVLGWFRQAPGKGREFVAAINWRGDITIGPPNVEGRFTISRDNS KNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYDYWGQGTLVTVSS RSV426 74 EVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAI V06 NWRDDITIGPPNVEGRFTISRDNAKNTLYLQMNSLRPEDTAVYYCGAGTPL NPGAYIYDWSYDYWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLV QPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAINWRDDITIGPPN VEGRFTISRDNAKNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYD YWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLVQPGGSLRLSCAA SGGSLSNYVLGWFRQAPGKGREFVAAINWRDDITIGPPNVEGRFTISRDNA KNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYDYWGQGTLVTVSS RSV444 75 SGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAI V6D NWRDDITIGPPNVEGRFTISRDNAKNTLYLQMNSLRPEDTAVYYCGAGTPL NPGAYIYDWSYDYWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLV QPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAINWRDDITIGPPN VEGRFTISRDNAKNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYD YWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLVQPGGSLRLSCAA SGGSLSNYVLGWFRQAPGKGREFVAAINWRDDITIGPPNVEGRFTISRDNA KNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYDYWGQGTLVTVSS RSV442 76 EVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAI V17 NWRGDITIGPPNVEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGAGTPL NPGAYIYDWSYDYWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLV QPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAINWRGDITIGPPN VEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYD YWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLVQPGGSLRLSCAA SGGSLSNYVLGWFRQAPGKGREFVAAINWRGDITIGPPNVEGRFTISRDNS KNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYDYWGQGTLVTVSS Table A-3: Continued RSV435 77 DVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAI V17D NWRGDITIGPPNVEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGAGTPL NPGAYIYDWSYDYWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLV QPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAINWRGDITIGPPN VEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYD YWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLVQPGGSLRLSCAA SGGSLSNYVLGWFRQAPGKGREFVAAINWRGDITIGPPNVEGRFTISRDNS KNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYDYWGQGTLVTVSS RSV427 78 EVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAI V18 NWRDDITIGPPNVEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGAGTPL NPGAYIYDWSYDYWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLV QPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAINWRDDITIGPPN ISRDNSKNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYD YWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLVQPGGSLRLSCAA SGGSLSNYVLGWFRQAPGKGREFVAAINWRDDITIGPPNVEGRFTISRDNS KNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYDYWGQGTLVTVSS RSV445 79 DVQLLESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAI V18D NWRDDITIGPPNVEGRFTISRDNSKNTLYLQMNSLRPEDTAVYYCGAGTPL NPGAYIYDWSYDYWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLV QPGGSLRLSCAASGGSLSNYVLGWFRQAPGKGREFVAAINWRDDITIGPPN ISRDNSKNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYD YWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLLESGGGLVQPGGSLRLSCAA SGGSLSNYVLGWFRQAPGKGREFVAAINWRDDITIGPPNVEGRFTISRDNS KNTLYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYDYWGQGTLVTVSS RSV436 80 EVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVAAI V20 NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLRPDDTAVYYCGAGTPL NPGAYIYDWSYDYWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLV QPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPN VEGRFTISRDNAKNTGYLQMNSLRPDDTAVYYCGAGTPLNPGAYIYDWSYD YWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLVQPGGSLRLSCAA SGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPNVEGRFTISRDNA RSV437 81 QMNSLRPDDTAVYYCGAGTPLNPGAYIYDWSYDYWGQGTLVTVSS DVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVAAI V20D NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLRPDDTAVYYCGAGTPL NPGAYIYDWSYDYWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLV QPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPN VEGRFTISRDNAKNTGYLQMNSLRPDDTAVYYCGAGTPLNPGAYIYDWSYD YWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLVQPGGSLRLSCAA SGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPNVEGRFTISRDNA RSV438 82 KNTGYLQMNSLRPDDTAVYYCGAGTPLNPGAYIYDWSYDYWGQGTLVTVSS SGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVAAI V22 NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLRPEDTAVYYCGAGTPL NPGAYIYDWSYDYWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLV QPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPN VEGRFTISRDNAKNTGYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYD YWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLVQPGGSLRLSCAA SGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPNVEGRFTISRDNA KNTGYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYDYWGQGTLVTVSS Table A-3: ued RSV439 83 SGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVAAI V26 NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLRPEDTAVYYCGAGTPL NPGAYIYDWSYDYWGRGTLVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLV QPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPN VEGRFTISRDNAKNTGYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYD YWGRGTLVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLVQPGGSLRLSCAA SGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPNVEGRFTISRDNA KNTGYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYDYWGRGTLVTVSS RSV440 84 DVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVAAI V26D NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLRPEDTAVYYCGAGTPL NPGAYIYDWSYDYWGRGTLVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLV QPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPN VEGRFTISRDNAKNTGYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYD YWGRGTLVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLVQPGGSLRLSCAA SGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPNVEGRFTISRDNA KNTGYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYDYWGRGTLVTVSS RSV441 85 DVQLVESGGGLVQPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVAAI V22D NWRGDITIGPPNVEGRFTISRDNAKNTGYLQMNSLRPEDTAVYYCGAGTPL NPGAYIYDWSYDYWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLV QPGGSLRLSCAASGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPN VEGRFTISRDNAKNTGYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYD YWGQGTLVTVSSGGGGSGGGGSGGGGSEVQLVESGGGLVQPGGSLRLSCAA SGGSLSNYVLGWFRQAPGKEREFVAAINWRGDITIGPPNVEGRFTISRDNA KNTGYLQMNSLRPEDTAVYYCGAGTPLNPGAYIYDWSYDYWGQGTLVTVSS Table A-4: Amino acid sequences of linkers Linker SEQ ID NO: Sequences 5GS 86 GGGGS 7GS 87 SGGSGGS GS8 88 GGGGSGGGS 9GS 89 GGGGSGGGS 10GS 90 GGGS 15GS 91 GGGGSGGGGSGGGGS 18GS 92 GGGGSGGGGSGGGGGGGS 20GS 93 GGGGSGGGGSGGGGSGGGGS 25GS 94 GGGGSGGGGSGGGGSGGGGSGGGGS 30GS 95 GGGGSGGGGSGGGGSGGGGSGGGGSGGGGS 35GS 96 GGGGSGGGGSGGGGSGGGGSGGGGSGGGGSGGGGS G1 hinge 97 EPKSCDKTHTCPPCP 9GS-G1 hinge 98 GGGGSGGGSEPKSCDKTHTCPPCP Llama upper long 99 EPKTPKPQPAAA hinge region G3 hinge 100 ELKTPLGDTTHTCPRCPEPKSCDTPPPCPRCPEPKSCDTPPPC PRCPEPKSCDTPPPCPRCP Ala 101 AAA

Claims

The claims defining the invention are as follows:

1. An inhalation device for delivering a nebulised aerosol to a patient, comprising: (a) an aerosol generator with a vibratable mesh; (b) a reservoir for a liquid to be nebulised, said oir being in fluid 5 connection with the vibratable mesh; (c) a gas inlet opening shaped as a tube fitting; (d) a face mask, having - a casing, - an aerosol inlet opening, 10 - a patient contacting e, and - a one-way exhalation valve or a two-way inhalation/exhalation valve in the casing having an exhalation overpressure resistance selected in the range from 0.5 to 5 mbar; and (e) a flow channel extending from the gas inlet opening to the aerosol inlet 15 opening of the face mask, the flow l having - a lateral opening through which the aerosol generator is at least partially inserted into the flow channel, - a constant flow resistance between the gas inlet opening and the aerosol inlet opening of the face mask at a flow rate of 1 to 20 L/min, 20 wherein the flow channel exhibits no further inlet g for receiving a gas.

2. The inhalation device of claim 1, wherein the flow channel upstream of the lateral opening is shaped such as to effect a r flow when a gas is conducted through the flow channel at a flow rate of 1 to 20 L/min.

3. The inhalation device of claim 1 or 2, wherein the flow channel is sized and shaped 25 to achieve, at a position immediately upstream of the l g, an average gas velocity of at least 4 m/s at a flow rate of 2 L/min.

4. The inhalation device of any one of claims 1 to 3, wherein the aerosol generator is oriented such as to emit nebulised aerosol into the flow channel at an angle of approx. 90° to the longitudinal axis of the flow channel, wherein the operation of the 30 aerosol generator ses the continuous vibration of the vibratable mesh.

5. The inhalation device of claim 4, wherein the inhalation device comprises a switch for starting and stopping the operation of the aerosol generator.

6. The inhalation device of any one of claims 1 to 5, wherein the face mask has a nominal internal volume of not more than 90 mL, or of not more than 70 mL, or of 5 not more than about 50 mL; or wherein the nominal internal volume is smaller than the e tidal volume of the patient.

7. The inhalation device of any one of claims 1 to 6, wherein the face mask has a twoway inhalation- and tion valve having a resistance of not more than 3 mbar in either direction, and wherein the nominal internal volume of the face mask is not 10 more than about 50 mL.

8. The inhalation device of any one of claims 1 to 7, n the interior volume of the flow channel between the lateral opening and the aerosol inlet opening of the face mask is not more than 30 mL.

9. The inhalation device of any one of claims 1 to 8, wherein the vibratable mesh 15 comprises from 1,000 to 4,000 openings whose smallest diameter is predominantly in the range from 1.5 to 3.0 µm.

10. The inhalation device of any one of claims 1 to 9, further comprising a flow restrictor capable of restricting the flow of gas through the flow channel to a constant flow rate in the range from 1 to 5 L/min when ting the gas inlet 20 opening with a pressurised gas source.

11. The tion device of any one of claims 1 to 10, comprising - a base unit, comprising - an electronic controller for controlling the l generator, and - an upstream portion of the flow channel including the gas inlet opening; 25 and - a mixing channel unit, comprising - a downstream n of the flow channel including the lateral opening, wherein the downstream portion comprises a segment where the flow l widens in the downstream direction, said segment being positioned downstream of 30 the lateral opening.

12. An assembly comprising the inhalation device of any one of claims 1 to 11 and a gas source providing a gas at a constant flow rate in the range from 1 to 5 L/min, wherein the gas source is connected to the inhalation device such that the gas enters the flow channel through the gas inlet opening, and wherein the gas is 5 selected from oxygen, air, oxygen-enriched air, a mixture of oxygen and nitrogen, and a mixture of helium and oxygen.

13. A combination or kit comprising (a) the inhalation device of any one of claims 1 to 11 or the ly of claim 12, and (b) a ceutical composition for inhalation use. 10

14. The combination or kit of claim 13, wherein the pharmaceutical composition comprises an active agent ed from antibiotics, antiviral agents, odilators, anticholinergics, corticosteroids, hypertonic saline, antibodies, antibody fragments, and immunoglobulin single variable domains.

15. The combination or kit of claim 14, wherein the active agent is an anti-RSV agent. 15

16. The combination or kit of claim 15,wherein the SV agent is a polypeptide sing or essentially consisting of one or more anti-RSV immunoglobulin single variable domains.

17. The combination or kit of claim 16, wherein (a) the anti-RSV immunoglobulin single variable domain comprises a CDR1 20 having the amino acid sequence of SEQ ID NO: 46, a CDR2 having the amino acid sequence of one of SEQ ID NOs: 49-50, and a CDR3 having the amino acid sequence of SEQ ID NO: 61; (b) the anti-RSV immunoglobulin single le domain is selected from one of the amino acid ces of SEQ ID NOs: 1-34; and/or 25 (c) the polypeptide is selected from one of the amino acid sequences of SEQ ID NOs: 65-85.

18. The combination or kit of any one of claims 13 to 17, wherein the patient is a paediatric patient.

19. The combination or kit of claim 18, wherein the patient is not more than 2 years of 30 age.

20. The combination or kit of any one of claims 13 to 19, wherein the combination or kit comprises instructions to administer the anti-RSV agent at daily doses of about 1 to 2 mg/kg body weight.

21. The ation or kit of any one of claims 13 to 20, further comprising a 5 odilator.

22. The combination or kit of claim 21, n the bronchodilator belongs to the class of beta2-mimetics.

23. The combination or kit of claim 22, wherein the odilator belongs to the class of long-acting beta2-mimetics. 10

24. The combination or kit of claim 23, wherein the bronchodilator is selected from formoterol or a solvate f, salmeterol or a salt thereof, and mixtures thereof.

25. The combination or kit of claim 22, wherein the bronchodilator belongs to the class of short-acting beta2-mimetics.

26. The combination or kit of claim 25, wherein the bronchodilator is selected from 15 salbutamol, terbutaline, pirbuterol, fenoterol, tulobuterol, levosabutamol and mixtures thereof.

27. The combination or kit of claim 21, wherein the bronchodilator belongs to the class of olinergics.

28. The combination or kit of claim 27, wherein the bronchodilator is selected from 20 tiotropium, oxitropium, ipratropium bromide and mixtures thereof.