Patent Application
20170152396
The present invention relates to methods of making components for medicinal delivery devices, to components for medicinal delivery devices and to medicinal delivery devices. In particular, the present invention relates to methods of making components for medicinal inhalation devices, such components and such devices.
Medicinal delivery devices, including medicinal inhalation devices such as pressurized inhalers, e.g. metered dose pressurized inhalers (MDIs), and dry powder inhalers (DPIs), are widely used for delivering medicaments.
Medicinal delivery devices typically comprise a plurality of hardware components, (which in the case of a MDI can include gasket seals; metered dose valves (including their individual components, such as ferrules, valve bodies, valve stems, tanks, springs, retaining cups and seals); containers; and actuators) as well as a number of internal surfaces which may be in contact with the medicinal formulation during storage or come in contact with the medicinal formulation during delivery. In medicinal delivery devices, variability in dosing (i.e. from dose to dose) variability in dosing between units (i.e. device to device) is undesirable. Attention is paid to the design of medicinal delivery devices to reduce variability in particular by ensuring that dose volume, concentration and (if necessary) pressure are consistent dose to dose and unit to unit.
Often a desirable material for a particular component is found to be unsuitable in regard to its surface properties, e.g. surface energy, and/or its interaction with the medicinal formulation. Potentially undesirable interactions between a component and the medicinal formulation may include enhanced medicament degradation or permeation of a formulation constituent or extraction of chemicals from materials. For DPIs often permeation and adsorption of ambient water pose issues. Also the use of materials having relatively high surface energy for certain components (e.g. metered dose valves and/or individual components thereof), may have undesirable effects for the operation of movable components of a medicinal delivery device.
Various improvements have been proposed in for example, WO-A-2005/026236, WO-A-2005/061572, WO-A-2002/30848, U.S. Pat. No. -B-3,810,874, WO-A-2009/061891, WO-A-2009/061902, WO-A-2009/061907, WO-A-2010/129783 and WO-A-2010/129758.
Although a number of different improvements have been proposed, there is an ongoing need for medicinal delivery devices and components having desirable surface properties (e.g. low surface energy) as well as methods of providing such medicinal delivery devices and components.
The present invention accordingly provides, in a first aspect, a method of making a component for a medicinal delivery device, the method comprising
a) providing a component of a medicinal delivery device,
b) providing a primer composition comprising a silane having two or more reactive silane groups separated by an organic linker group,
c) providing a coating composition comprising an at least partially fluorinated compound,
d) applying the primer composition to at least a portion of the surface of the component,
e) applying the coating composition to the portion of the surface of the component after application of the primer composition.
Previously, it was thought that aspects relating to the design or structure of medicinal delivery devices and not surface properties of medicinal delivery devices were the most important contributors to dose to dose and unit to unit variability, for example in e.g. MDI, differences in dose to dose delivery volume or concentration and unit to unit tolerances in formulation, pressure, or volume.
However, surprisingly, the inventors have discovered that methods according to the present invention provide components which, when assembled and in use, significantly reduce dose to dose variability of medicinal delivery devices. Additionally, such methods provide components which, when assembled and in use, provide reduced unit to unit variability.
The at least partially fluorinated compound will usually comprise one or more reactive functional groups, with the or each one reactive functional group usually being a reactive silane group, for example a hydrolysable silane group or a hydroxysilane group. Such reactive silane groups allow reaction of the partially fluorinated compound with one or more of the reactive silane groups of the primer. Often such reaction will be a condensation reaction.
The reactive silane group may be of formula —Si(R0)nX3-n, wherein R0 is a substantially non-hydrolysable group, X is a hydrolysable or hydroxy group and n is 0, 1 or 2.
Thus, in many embodiments the silane having two or more reactive silane groups is of formula
X3-m(R1)mSi-Q-Si(R2)kX3-k
wherein R1 and R2 are independently selected univalent groups such as C1-C4 alkyl, X is a hydrolysable or hydroxy group, m and k are independently 0, 1, or 2 and Q is a divalent organic linking group.
Usually, Q will comprise a 1 to 12 atom chain, more usually a substituted or unsubstituted C2 to C12 hydrocarbyl chain. Preferably, Q comprises a substituted or unsubstituted C2 to C12 alkyl chain.
Useful examples of silanes having two or more reactive silane groups include one or a mixture of two or more of 1,2-bis(trialkoxysilyl) ethane, 1,6-bis(trialkoxysilyl) hexane, 1,8-bis(trialkoxysilyl) octane, 1,4-bis(trialkoxysilylethyl)benzene, bis(trialkoxysilyl)itaconate, and 4,4′-bis(trialkoxysilyl)-1,1′-diphenyl, wherein any trialkoxy group may be independently trimethoxy or triethoxy.
Q may comprise a chain substituted by one or more atoms of N, O, and/or S. Thus, further examples of the silane having two or more reactive silane groups include one or a mixture of two or more of bis(trialkoxysilylpropyl)amine; bis (3-trialkoxysilylpropyl) ethylenediamine; bis (3-trialkoxysilylpropyl) n-methylamine; bis[3-(trialkoxysilyl)propyl]fumarate and N, N-bis (3-trialkoxysilylmethyl) allylamine, wherein any trialkoxy group may be independently trimethoxy or triethoxy.
In preferred embodiments, the silane is such that Q may be of formula —(CH2)i-A-(CH2)j—wherein A is NRn, O, or S; i and j are independently 0, 1, 2, 3 or 4 and wherein Rn is H or C1 to C4 alkyl. Even more preferably, Q may be of formula —(CH2)i—NH—(CH2)j— and i and j are each independently 1, 2, 3 or 4. Most preferably i and j are each 3.
The coating solvent usually comprises an alcohol or a hydrofluoroether.
If the coating solvent is an alcohol, preferred alcohols are C1 to C4 alcohols, in particular, an alcohol selected from ethanol, n-propanol, or iso-propanol or a mixture of two or more of these alcohols.
If the coating solvent is an hydrofluoroether, it is preferred if the coating solvent comprises a C4 to C10 hydrofluoroether. Generally, the hydrofluoroether will be of formula
CgF2g+1OChH2h+1
wherein g is 2, 3, 4, 5, or 6 and h is 1, 2, 3 or 4. Examples of suitable hydrofluoroethers include those selected from the group consisting of methyl heptafluoropropylether, ethyl heptafluoropropylether, methyl nonafluorobutylether, ethyl nonafluorobutylether and mixtures thereof.
The at least partially fluorinated compound may contain a polyfluoroether moiety, in particular a polyfluoropolyether moiety. More particularly, the polyfluoroether moiety may be a perfluorinated polyfluoroether moiety, even more particularly the polyfluoroether moiety may be a perfluorinated polyfluoropolyether moiety.
The polyfluoropolyether silane may be of formula
RfQ1v[Q2w—[C(R4)2—Si(X)3-x(R5)x]y]z
wherein:
Rf is a polyfluoropolyether moiety;
Q1 is a trivalent linking group;
each Q2 is an independently selected organic divalent or trivalent linking group;
each R4 is independently hydrogen or a C1-4 alkyl group;
each X is independently a hydrolysable or hydroxyl group;
R5 is a C1-8 alkyl or phenyl group;
v and w are independently 0 or 1, x is 0 or 1 or 2; y is 1 or 2; and z is 2, 3, or 4.
The polyfluoropolyether moiety Rf may comprise perfluorinated repeating units selected from the group consisting of —(CnF2nO)—,—(CF(Z)O)—, —(CF(Z)CnF2nO)—, —(CnF2nCF(Z)O)—, —(CF2CF(Z)O)—, and combinations thereof; wherein n is an integer from 1 to 6 and Z is a perfluoroalkyl group, an oxygen-containing perfluoroalkyl group, a perfluoroalkoxy group, or an oxygen-substituted perfluoroalkoxy group, each of which can be linear, branched, or cyclic, and have 1 to 5 carbon atoms and up to 4 oxygen atoms when oxygen-containing or oxygen-substituted and wherein for repeating units including Z the number of carbon atoms in sequence is at most 6. In particular, n may be an integer from 1 to 4, more particularly from 1 to 3. For repeating units including Z the number of carbon atoms in sequence may be at most four, more particularly at most 3. Usually, n is 1 or 2 and Z is an —CF3 group, more wherein z is 2, and Rf is selected from the group consisting of —CF2O(CF2O)m(C2F4O)pCF2—, —CF(CF3)O(CF(CF3(CF2O)pCF(CF3)—, —CF2O(C2F4O)p CF2—, —(CF2)3O(C4F8O)p(CF2)3—, —CF(CF3)—(OCF2CF(CF3))pO—CtF2t—O(CF(CF3)CF2 O)pCF(CF3)—, wherein t is 2, 3 or 4 and wherein m is 1 to 50, and p is 3 to 40.
The composition may further comprise a cross-linking agent. The cross-linking agent may comprise a compound selected from group consisting of tetramethoxysilane; tetraethoxysilane; tetrapropoxysilane; tetrabutoxysilane; methyl triethoxysilane; dimethyldiethoxysilane; octadecyltriethoxysilane; 3-glycidoxy-propyltrimethoxysilane; 3-glycidoxy-propyltriethoxysilane; 3-aminopropyl-trimethoxysilane; 3-aminopropyl-triethoxysilane; bis (3-trimethoxysilylpropyl) amine; 3-aminopropyl tri(methoxyethoxyethoxy) silane; N (2-aminoethyl)3-aminopropyltrimethoxysilane; bis (3-trimethoxysilylpropyl) ethylenediamine; 3-mercaptopropyltrimethoxysilane; 3-mercaptopropyltriethoxysilane; 3-trimethoxysilyl-propylmethacrylate; 3-triethoxysilypropylmethacrylate; bis (trimethoxysilyl) itaconate; allyltriethoxysilane; allyltrimethoxysilane; 3-(N-allylamino)propyltrimethoxysilane; vinyltrimethoxysilane; vinyltriethoxysilane; and mixtures thereof.
Usually, the method may include a pre-treatment step prior to the step of applying the primer composition, said pre-treatment step in particular may comprise cleaning the surface with a solvent comprising a hydrofluoroether, e.g. HFE72DE an azeotropic mixture of about 70%w/w trans-dichloroethylene; 30% w/w of a mixture of methyl and ethyl nonafluorobutyl and nonafluoroisobutyl ethers.
Thus, in a second aspect, the present invention provides, a method of making a component for a medicinal delivery device, the method comprising
a) providing a component of a medicinal delivery device,
b) providing a coating composition comprising an at least partially fluorinated compound,
d) cleaning at least a portion of the surface of the component using a solvent comprising hydrofluoroether of formula
CgF2g+1OChH2h+1
e) applying the coating composition to the portion of the surface of the component after cleaning with the solvent.
The hydrofluoroether for the cleaning step in the first or second aspect may be selected from the group consisting of methyl heptafluoropropylether; ethyl heptafluoropropylether; methyl nonafluorobutylether; ethyl nonafluorobutylether and mixtures thereof.
In the method, the primer composition and/or the coating composition may be, independently of the application step used for the other, applied by spraying, dipping, rolling, brushing, spreading or flow coating, in particular by spraying or dipping.
In the method, after the step of applying either the primer composition or after the step of applying the coating composition, the method may further comprise a step of curing. The curing step may be carried out at an elevated temperature in the range from about 40° C. to about 300° C.
The primer may be cured by evaporating the solvent in a moist environment, as water is responsible for the curing, and may be aided by heat or elevated humidity. If heat is applied to the primer coating, it is preferable to allow the prime-coated component to cool to room temperature before applying the top coating.
Typically, a lower curing temperature is used than for coating polymers than for coating metals, to avoid deformation of the polymer. However, it has been found that it is not essential to ensure that the primer is cured before applying the top coating, as a final curing can be effectively done to both layers simultaneously, thereby simplifying the manufacturing process. Hence, the primer coat may be allowed to set on the surface such that it is not washed off by the subsequent top coating, by allowing (e.g. by leaving to stand) or causing (e.g. by blowing in a current of air) most of the primer solution solvent to be dispersed.
Coatings applied to valve components, such as plastic stems, metal stems or elastomeric seals, in which the at least partially fluorinated compound is a perfluoropolyether silane according to formula Ia in which Rf comprises from 20 to 40 linked repeating units confer additional lubricity compared to those with fewer repeating units, and when these are assembled with other component to make up valves, the valves have lower actuation forces.
Formula Ia is:
Rf[Q1-[C(R)2—Si(Y)3-x(R1a)x]y]z Ia
wherein:
Rf is a monovalent or multivalent polyfluoropolyether moiety;
Q1 is an organic divalent or trivalent linking group;
each R is independently hydrogen or a C1-4 alkyl group;
each Y is independently a hydrolysable group;
R1a is a C1-8 alkyl or phenyl group;
x is 0 or 1 or 2;
y is 1 or 2; and
z is 1, 2, 3, or 4.
In either the first or the second aspect, the surface may be a metal surface, in particular a surface of an aluminium alloy, an iron alloy, or a steel alloy.
In the first aspect, the surface may be a polymer surface. The polymer may be a thermoplastic or thermoset material.
The types of plastics that can thus be coated includes polyalkylenes, polyesters, polyoxymethylene, poly(acrylonitrile-butadiene-styrene) (ABS) or other copolymers comprising monomers of acrylonitrile, butadiene and styrene, such as methylmethacrylate-acrylonitrile-butadiene-styrene (MABS), polycarbonate and nylon, e.g. nylon 6,6 or nylon 6,12. Examples of polyalkylenes are polypropylene and polyethylenes such as low density polyethylene (LDPE), ultra-high molecular weight polyethylene (UHMPE). Polyesters include polyethylene terephthalate (PET) and polybutylene terephthalate (PBT) and copolyester.
Thermosets that may be usefully coated include nitrile elastomer, neoprene elastomer, EPDM and co-vulcanisates of elastomeric polymers with thermoplastic polymers.
Medicinal delivery devices may include inhalers, or other dispensers in which accurate dosing depends on not leaving medicament behind on the device. Examples include a pressurized metered dose inhaler (pMDI), a nebulizer and a dry powder inhaler (DPI). When the device is a pMDI, examples of components include an actuator, an aerosol container, a ferrule, a valve body, a valve stem and a compression spring. For DPIs, examples of components include a powder container, a component used to open sealed powder container, a component that defines at least in part a deagglomeration chamber, a component of a deagglomeration system, a component that defines at least in part a flow channel, a dose-transporting component, a component that defines at least in part a mixing chamber, a component that defines at least in part an actuation chamber, a mouthpiece and a nosepiece.
Components to be coated may be made from one of the above materials, or from assemblies or co mouldings of more than one material including at least one of the above material types. Alternatively, plastics coatings on components may provide a surface amenable to further coating.
It has been found that the deposition of drug on plastics or thermoset components can be reduced when the component is coated by applying a primer coat of a silane having two or more reactive silane groups separated by an organic linker, followed by a top coating of an at least partially fluorinated compound.
The primer preferably comprises a linking group with a chain of one to twelve atoms. This may have at least one carbon atom either side of a heteroatom, such as nitrogen, oxygen or sulphur. Particularly useful primers include at least one amine group in the linking group.
It has surprisingly been found that deposition of drug on medicinal delivery device component surfaces is eliminated when the organic linker comprises one or more amine groups and the at least partially fluorinated compound is a perfluoropolyether silane according to formula Ia in which y=z=1.
In either the first or the second aspect, the surface of the device or the surface of the component of the device, as applicable, is preferably a surface that is or is intended to come in contact with a medicament or a medicinal formulation during storage or delivery from the medicinal delivery device.
The medicament may comprise or the medicinal formulation may comprise a medicament that may be a drug, vaccine, DNA fragment, hormone or other treatment. Suitable drugs include those for the treatment of respiratory disorders, e.g., bronchodilators, anti-inflammatories (e.g., corticosteroids), anti-allergics, anti-asthmatics, anti-histamines, and anti-cholinergic agents. Therapeutic proteins and peptides may also be employed for delivery by inhalation. Thus the medicament may be selected from the an exemplary group consisting of albuterol, terbutaline, ipratropium, oxitropium, tiotropium, TD-4208, beclomethasone, flunisolide, budesonide, mometasone, ciclesonide, cromolyn sodium, nedocromil sodium, ketotifen, azelastine, ergotamine, cyclosporine, aclidinium, umeclidinium, glycopyrrolate, salmeterol, fluticasone, formoterol, procaterol, indacaterol, TA2005, milveterol, olodaterol, vilanterol, abediterol, omalizumab, zileuton, insulin, pentamidine, calcitonin, leuprolide, alpha-1-antitrypsin, interferon, triamcinolone, salbutamol, pharmaceutically acceptable salts and esters of any of the listed medicaments and mixtures of any of the listed medicaments, their pharmaceutically acceptable salts and esters. For fluticasone, the preferred esters are propionate or furoate; for mometasone, the preferred ester is furoate.
In either the first or the second aspect, the medicinal delivery device is preferably a metered dose inhaler or a dry powder inhaler. Thus, preferably, the component (preferably comprising metal) is a component of a metered dose inhaler and the component is selected from the group consisting of an actuator, an aerosol container, a ferrule, a valve body (that defines a metering chamber), a bottle emptier, a valve stem and a compression spring.
An aerosol formulation used in a metered dose inhaler typically comprises a medicament or a combination of medicaments (as discussed above) and liquefied propellant selected from the group consisting of HFA 134a, HFA 227 and mixtures thereof.
Aerosol formulations may, as desired or needed, comprise other excipients, such as surfactant, a co-solvent (e.g., ethanol), CO2, or a particulate bulking agent. Medicament may be provided in particulate form (e.g. particles generally having a median diameter in the range of 1 to 10 microns) suspended (i.e. dispersed) in the liquefied propellant. Alternatively medicament may be in solution (i.e. dissolved) in the formulation. In the event a combination of two or more medicaments is used, all the medicaments may be suspended or in solution or alternatively one or more medicaments may be suspended, while one or more medicaments may be in solution.
The amount of medicament may be determined by the required dose per puff and available valve sizes, which for MDIs are typically 25, 50 or 63 microlitres, or 100 microlitres.
Pressurized metered dose inhalers including e.g., aerosol containers (in particular metal aerosol containers) whose interior surfaces are coated in accordance the invention are particularly advantageous for containing and delivering medicinal aerosol formulations comprising a medicament that is dispersed in said formulation.
In addition embodiments in accordance with the present invention are particularly useful in regard to metered dose inhalers including a medicinal aerosol formulation that includes low amounts of surfactant (0.005 wt % with respect to the formulation); or is substantially free (less than 0.0001 wt % with respect to drug) or free of a surfactant. Alternatively or additionally, embodiments, are particularly useful in metered dose inhalers including a medicinal aerosol formulation that contains low amounts of ethanol (less than 5 wt % with respect to the formulation), or is substantially free (less than 0.1 wt % with respect to the formulation) or free of ethanol.
In a third aspect, the present invention provides a coated component for a medicinal delivery device comprising a component and a fluorine-containing coating, wherein the fluorine-containing coating comprises two layers, a first polyfluoropolyether-containing layer comprising polyfluoropolyether silane entities of the following Formula Ib:
Rf[Q1-[C(R)2—Si(O—)3-x(R1a)x]y]z Ib
which shares at least one covalent bond with a second non-fluorinated layer comprising entities of the following Formula IIb:
(—O)3-m-n(X)n(R1)mSi-Q-Si(R2)k(X)1(O—)3-k-l IIb
which in turn shares at least one covalent bond with the component; and wherein:
Rf is a monovalent or multivalent polyfluoropolyether segment;
Q1 is an organic divalent or trivalent linking group;
each R is independently hydrogen or a C1-4 alkyl group;
R1a is a C1-8 alkyl or phenyl group;
k, 1, m and n are independently 0, 1 or 2, but with the priviso that m+n and k+1 are at most 2;
x is 0 or 1 or 2; y is 1 or 2; and z is 1, 2, 3, or 4; wherein R1 and R2 are independently selected univalent groups, X is a hydrolysable or hydroxy group, m and k are independently 0, 1, or 2 and Q is a divalent organic linking group, comprising a substituted C2 to C12 hydrocarbyl chain and one or more amine groups. Coated components with more specific surface structural features may be determined by the skilled person in respect of more specific process steps described earlier by taking into account the covalent bonding chemistry of this third aspect of the invention.
The invention, in its various combinations, either in method or apparatus form, may also be characterized by the following listing of items:
a) providing a component of a medicinal delivery device,
b) providing a primer composition comprising a silane having two or more reactive silane groups separated by an organic linker group,
c) providing a coating composition comprising an at least partially fluorinated compound,
d) applying the primer composition to at least a portion of the surface of the component,
e) applying the coating composition to the portion of the surface of the component after application of the primer composition.
X3-m(R1)mSi-Q-Si(R2)kX3-k
wherein R1 and R2 are independently selected univalent groups, X is a hydrolysable or hydroxy group, m and k are independently 0, 1, or 2 and Q is a divalent organic linking group.
CgF2g+1OChH2h+1
wherein g is 2, 3, 4, 5, or 6 and h is 1, 2, 3 or 4.
RfQ1v[Q2w-[C(R4)2—Si(X)3-x(R5)x]y]x
wherein:
Rf is a polyfluoropolyether moiety;
Q1 is a trivalent linking group;
each Q2 is an independently selected organic divalent or trivalent linking group;
each R4 is independently hydrogen or a C1-4 alkyl group;
each X is independently a hydrolysable or hydroxyl group;
5 R is a C1-8 alkyl or phenyl group;
v and w are independently 0 or 1, x is 0 or 1 or 2; y is 1 or 2; and z is 2, 3, or 4.
a) providing a component of a medicinal delivery device,
b) providing a coating composition comprising an at least partially fluorinated compound,
d) cleaning at least a portion of the surface of the component using a solvent comprising a hydrofluoroether of formula
CgF2g+1OChH2h+1
e) applying the coating composition to the portion of the surface of the component after cleaning with the solvent.
X3m(R1)mSi-Q-Si(R2)kX3-k
wherein R1 and R2 are independently selected univalent groups, X is a hydrolysable or hydroxy group, m and k are independently 0, 1, or 2 and Q is a divalent organic linking group, comprising a substituted C2 to C12 hydrocarbyl chain and one or more amine groups.
Rf[Q1-[C(R)2—Si(Y)3-x(R1a)x]y]x Ia
wherein:
Rf is a monovalent or multivalent polyfluoropolyether moiety;
Q1 is an organic divalent or trivalent linking group;
each R is independently hydrogen or a C1-4 alkyl group;
each Y is independently a hydrolysable group;
R1a is a C1-8 alkyl or phenyl group;
x is 0 or 1 or 2;
y is 1 or 2; and
z is 1, 2, 3, or 4.
Rf[Q1-[C(R)2—Si(O—)3-x(R1a)x]y]z Ib
which shares at least one covalent bond with a second non-fluorinated layer comprising entities of the following Formula IIb:
(—O)3-m-nXn(R1)mSi-Q-Si(R2)k(X)t(O—)3-k-l IIb
which in turn shares at least one covalent bond with the component; and wherein:
Rf is a monovalent or multivalent polyfluoropolyether segment;
Q1 is an organic divalent or trivalent linking group;
each R is independently hydrogen or a C1-4 alkyl group;
R1a is a C1-8 alkyl or phenyl group;
k, 1, m and n are independently 0, 1 or 2, but with the priviso that m+n and k+l are at most 2;
x is 0 or 1 or 2;
y is 1 or 2; and
z is 1, 2, 3, or 4;
R1 and R2 are independently selected univalent groups, X is a hydrolysable or hydroxy group, m and k are independently 0, 1, or 2 and Q is a divalent organic linking group, comprising a substituted C2 to C12 hydrocarbyl chain and one or more amine groups.
Throughout this specification, the word “inhaler” means a device for delivery of a medicament in fluid (or powder) and does not imply that the device requires inhalation on the part of the patient during delivery. It is known that a medicament may be delivered successfully to the nasal passages by an inhaler without the need for the patient to inhale.
So that the present specification may be more completely understood, reference is made to the accompanying drawings in which:
As shown in
The valve shown in
Referring to
Depending on the particular metered dose valve and/or filling system, aerosol formulation may be filled into the container either by cold-filling (in which chilled formulation (chilled to temperatures of about −50 to -55° C. for propellant HFA 134a-based formulations) is filled into the container and subsequently the metered dose valve is crimped onto the container) or by pressure filling (in which the metered dose valve is crimped onto the container and then formulation is pressure filled through the valve into the container).
The present invention is further illustrated by the following Examples. In this specification, ENFBE refers to solvent ethyl nonafluorobutyl ether, MNFBE refers to methyl nonafluorobutyl ether. The polyfluoropolyethersilane that is referred to as fluorosilane A is a fluorosilane of formula:
(MeO)3Si(CH2)3NHC(O)OCH2CH[O(O)CHN(CH2)3Si(OMe)3]CH2NHCORf2
where Rf2 is a moiety of formula CF(CF3)(OCF2CF(CF3))kO(CF2)2CF3, k is approximately 5 to 6, but may be in the range 3 to 50, usually 3 to 20, more usually 4 to 10. Fluorosilane B is a fluorosilane of formula:
(MeO)3Si(CH2)3NHC(O)Rf2
Fluorosilane C is a fluorosilane of formula:
(MeO)3Si(CH2)3OCH2 Rf2, in which k is approximately 34.
In the Examples the salbutamol sulphate deposition screening test employed a salbutamol dispersion micronised non-amorphous salbutamol sulphate ultrasonically dispersed in decafluoropentane (1 g in 400 g). The test was run by employing an Eppendorf pipette to place a 0.3 ml aliquot of the salbutamol dispersion into each can. The cans were then immediately placed on a horizontal rolling mixer (Stuart Scientific model SRT2 operating to rotate cans at 35 rpm) for 3 minutes to allow the dispersion to dry to the surface. The cans were then placed in an air drying oven for 5 minutes at 65° C. to fully dry. The cans were then rinsed with 2 aliquots of decafluoropentane (5 ml) using a 5 inversion shaking regime with one shake cycle per second.
Controls were uncoated cans to which salbutamol sulphate dispersion had been added and dried but which had not undergone a subsequent rinse step and hence these cans had a deposit level that represented the maximum level possible in the test. Other cans had undergone a subsequent rinse step and hence cans which showed a low level of salbutamol deposition in this test were showing that the deposited salbutamol could be easily washed away and were therefore deemed to have good release/non-stick performance.
The residual deposited salbutamol was quantitatively transferred and assayed by u.v. spectrophotometry. For each sample, the amount assayed was divided by the corresponding amount for the controls and expressed as a percentage. Unless otherwise stated, 3 samples were taken for each determination.
Cans were immersed in HFE72DE at its boiling temperature (43° C.) for 7 minutes. They were allowed to drain for 2 minutes, and then re-immersed for 3 minutes with ultrasonic agitation. These were allowed to drain for a further 4 minutes then dried at ambient conditions for 7 minutes.
Washed aluminium cans were fill and drain coated with primer solution (BTMSPA 0.2 g in isopropanol (109.5 g)) by transfer filling brimful into a first can in a first row of 10 cans, allowing 60 s solution contact time, then transferring and topping up from primer solution similarly to the subsequent cans in the row. Meanwhile primer solution was transfer filled into a first can of a second row of 10 cans, and the process repeated as for the first row of cans. Altogether 6 rows of cans were treated, giving a total of 60 cans. The cans were placed inverted to drain on a laboratory wipe, each was shaken and blown dry with compressed air and then placed in an oven for 30 minutes at 60° C.
A similar quantity of washed cans was not primed.
Coating of Cans with Fluorosilane A Solution for Spray Coating
A reservoir bottle of 1% w/w fluorosilane A (13.5 g) in ENFBE (1355 g) was prepared.
An automated spray coater was employed to spray a sequence of cans. The primed and unprimed cans were presented to the sprayer alternately to eliminate any possible systematic trend in the coating efficiency.
In the automated spray coater, spraying liquid was pumped from a reservoir bottle through a spray nozzle mounted to spray vertically upwards for a programmed duration at a spraying station. Each can to be sprayed was delivered inverted to the spraying station, then allowed to drain. By suitable adjustment of the spraying pressure and duration, the optimum coating was achieved when the cans were delivered with a maximum load that did not drip excess coating solution upon draining. 8 cans for each experimental condition were coated. Results are reported to include samples from either side of the optimum. Furthermore, runs were included with 2 passes of the sprayer, allowing 60 s draining between passes, and a run with 3 short duration sprays adding up to the optimum duration for a single spray.
After completion of all coating runs, with draining complete, the cans were placed inverted into a single stainless steel coating tray and placed into the centre of the coating oven at 120° C. for 30 minutes. The cans were then removed, left to cool down and then placed into a large polythene bag for storage.
Each can was subjected to the deposition test for cans.
Certain of the deposition cans were tested using the deposition test for cans. Results are reported in Table 1.
With reference to Table 1, the data show that all fluorosilane The spray coated cans both with and without the primer show very low deposition values. The primed cans show marginally better deposition performance than the unprimed cans in this study. The uniformly low deposition data across the study indicate that the spray coating process is robust within the coating variable ranges tested.
Example 2 involved coating and performance testing of stainless steel valve components.
Metering tanks, springs, bottle emptiers, inner and outer seals, valve stems and ferrules were assembled for making valves as shown in
1000 metering tanks were placed in a stainless steel vessel with lid and ENFBE (1 litre) was added. The components were agitated and then left with the lid on for 30 minutes. After 30 minutes the components were strained using a stainless steel strainer and placed back in the vessel to which a further 1 litre of fresh ENFBE was added. Once more the components were agitated and then left to stand for 30 minutes. The components were then strained and then left in the vessel for the final residues of the ENFBE to evaporate. The components were then placed in a polythene bag for storage.
The same procedure as above was applied to 1000 springs with 500 ml ENFBE used in place of the 1 litre quantity. The washed springs were then placed in a polythene bag for storage.
100 washed springs and 100 washed tanks were placed into a glass 250 ml beaker.
Priming with BTMSPA
BTMSPA (0.3 g) was weighed into a 500 ml beaker and isopropanol (164 g) was added and the solution mixed. The latter solution was then added to the beaker of components and the components mixed with a spatula then left to stand for 30 seconds. The fluid and components were then poured back into the 500 ml beaker via a stainless steel sieve thereby collecting the coated components in the sieve. The components were then poured out on to a laboratory wipe and were dried off using a hot air blower. The components were returned to the glass beaker and were then placed in an air drying oven at 60° C. for 15 minutes.
The primed components were left to cool down and equilibrate with ambient air for 1 hour.
ENFBE (300 g) was added to fluorosilane A (3.0 g) in a 500 ml beaker and the solution was mixed. The solution was the poured into the beaker of primed components and the components were stirred with a spatula. The components were then left to sit for 30 seconds in the solution after which time they were drained via a stainless steel sieve back into the 500 ml beaker hence collecting the components in the sieve. The components were then transferred to a glass beaker and placed into an oven at 120° C. for 30 minutes to cure the fluorosilane. The coated components were assembled into inhaler valves as shown in
Similarly, the uncoated components (Comparative Example 2A) were also assembled into inhaler valves as a control.
The coated test valves and control valves were incorporated into metered dose inhaler and used to deliver a formulation of micronised salbutamol sulphate suspended in HFA134a. The target dose of the product was 100ug per actuation and the cold filling technique was employed for the filling process.
Both the coated (Example 2) and the uncoated (Comparative Example 2A) valve product lots were actuated through life to shot number 120, after which point the test inhalers were chilled down, the valves removed and the valve components disassembled and assayed for salbutamol sulphate residue. The assay was done by uv spectrophotometry of quantitative washings from each component made up to a suitable volume with washing solvent. The assay results are shown in table 2, below.
The data in Table 2 show that the valves incorporating stainless steel springs and stainless steel tanks coated with BTMSPA followed by fluorosilane A in Example 2 show a very large reduction in component salbutamol sulphate deposition levels compared to the uncoated controls in Comparative Example 2A. Although only the springs and the tanks were coated, coating appears to have had a further beneficial effect in terms of lowered deposition also on the stem and seal and the bottle emptier components of the coated valves. This effect is likely due to reduced deposition at the interface points between uncoated and coated components compared to that seen at the interface points between components that are all uncoated.
400 washed springs were placed into a 500 ml beaker and 400 washed 63 μl metering tanks were placed into a second 500 ml beaker. The washing procedure was as for example 2.
BTMSPA (0.4 g) was weighed into a 500 ml beaker and isopropanol (219 g) was added and the solution mixed. The latter solution was then added to the beaker of springs and mixed well with a stainless steel spatula and left to stand for 30 seconds. The fluid and components were then poured out into the beaker containing the metering tanks and the latter were then mixed well and left to stand for 30 seconds. The metering tanks and fluid contents were then poured through a sieve into a third beaker. The still wet metering tanks and springs were separated out onto two separate laboratory wipes and left in the fume cupboard with fast air flow for 10 minutes until all the isopropanol had evaporated. The components were then transferred into dry 500 ml glass beakers and placed into the air drying oven for 15 minutes at a temperature of 60° C.
The primed metering tanks and springs were removed from the air drying oven and poured out onto laboratory wipe in the fume cupboard to allow to cool and to equilibrate with atmospheric moisture for 30 minutes.
ENFBE (400 g) was added to fluorosilane A (4.0 g) in a 500 ml beaker and the solution was mixed. The latter solution was then poured into the beaker of primed springs components and the components were stirred with a spatula. The components were then left to sit for 30 seconds in the solution after which time they were drained via a stainless steel sieve back into the 500 ml beaker containing the metering tanks. After 30 seconds the metering tanks were sieved to isolate them and each beaker of components was air dried on a laboratory wipe with the aid of a hot air blower, then placed into the oven at 120° C. for 30 minutes to cure the fluorosilane.
Valves as shown in
A suspension formulation of fluticasone propionate was made up in propellant (1%w/w ethanol+99%w/w HFA134a). Aluminium cans were filled to deliver 120 shots via 63 μl valve, by cold transferring aliquots of the suspension, and valves prepared as above were crimped on to provide aerosol units.
Each aerosol unit to be tested was placed into a plastic actuator (the discharge actuator). The aerosol unit was shaken with a gentle rocking action through 180° inversion for at least 10 s and a shot was fired to waste. The valve was immediately released, and these steps repeated, once using the discharge actuator and again twice using a fresh plastic actuator (the test actuator).
An USCA (Unit Spray Sample Collection) apparatus as described in US Pharmacopoeia vol. 29 (2006) section <601> was set up. An aerosol unit which had been through firing shots to waste as described above was immediately attached and a pair of shots fired into an USCA Medication Delivery collection tube with a filter (USCA tube), according to the procedure for the apparatus. Each pair of shots from the unit was fired into a separate USCA tube. The drug was quantitatively transferred from each USCA tube for analysis by hplc.
The test regimen, following on from the firing to waste described above and carried out on 5 units for each of the 2 valve types, was as follows:
3 pairs of shots representing the start of unit life through the test actuator (referred to by their sample number as start 1, start 2 and start 3 in
48 shots fired to waste through the discharge actuator
2 shots fired to waste through the test actuator
4 pairs of shots representing the middle of unit life through the test actuator (referred to as middle 1, middle 2, middle 3 and middle 4 in
48 shots fired to waste through the discharge actuator
2 shots fired to waste through the test actuator
3 pairs of shots representing the end of unit life through the test actuator (referred to as end 1, end 2 and end 3 in
A graph of μg fluticasone released per shot is shown in
19 ml aluminium cans were washed with HFE72DE as in Example 1.
4A—BMSTPA (0.05 g) was dissolved in isopropanol (27.4 g). The solution was transferred sequentially brimful into 6 aluminium cans, allowing a solution contact time of 60 s per can. The cans were then drained and placed in an oven at 60° C. for 2 hours, to complete priming. fluorosilane A (0.5 g) was weighed into a plastic beaker and made up to 50 g with MNFBE. The solution was transferred sequentially brimful into 3 primed aluminium cans, allowing a solution contact time of 30 s per can. These cans were drained and placed in an oven at 120° C. for 15 minutes, to effect curing.
4B—BMSTPA (0.05 g) and fluorosilane A (0.5 g) were dissolved in ethanol (27.4 g) in a plastic beaker. The solution was transferred sequentially brimful into 3 cleaned aluminium cans, allowing a solution contact time of 60 s per can. These cans were drained and placed in an oven at 120° C. for 15 minutes, to effect curing.
4C—BMSTPA (0.05 g) was dissolved in ethanol (27.4 g). The solution was transferred sequentially brimful into 3 aluminium cans, allowing a solution contact time of 5 s per can. The cans were then drained and placed in an oven at 120° C. for 15 minutes, to complete priming. fluorosilane A (0.5 g) was dissolved in ethanol (27.4 g). The solution was transferred sequentially brimful into 3 primed aluminium cans, allowing a solution contact time of 60 s per can. These cans were drained and placed in an oven at 120° C. for 15 minutes, to effect curing and complete the coating.
4D—fluorosilane A (0.5 g) was dissolved in ethanol (27.4 g). The solution was transferred sequentially brimful into 3 cleaned aluminium cans, allowing a solution contact time of 60 s per can. These cans were drained and placed in an oven at 120° C. for 15 minutes, to effect curing and complete the coating.
The deposition test for cans described earlier was carried out.
10 ml Stainless steel cans were washed with ENFBE as follows. 65 cans were periodically agitated in ENFBE (2 liters) with a contact time of 1 hour, then drained and allowed to dry at ambient conditions.
Priming, where used, was carried out by taking 20 washed cans and contacting with a solution of BTMSPA (0.1 g) in isopropanol (54.8 g) for 30 s, allowing to drain, then placing in an oven at 60° C. for 1 hour.
Fluorosilane coating, where used, was carried out by taking 6 cans a filling with fluorosilane A (0.5 g) in MNFBE (50 g) for 30 s, allowing to drain, then placing in an oven at 120° C. for 15 minutes.
6 cans of each test condition were subjected to the Deposition test for cans as follows:
5A—washed only
5B—washed and primed
5C—washed, primed and coated
5D—washed and coated
The results indicate that the effect of coating was improved by a previous priming, while priming alone was ineffective.
It is to be understood that the specification is not limited to the embodiments described above and that various modifications can be made without departing from the principles or concepts of the specification.
Actuators and inhalers as claimed in the specification may include any feature described herein separately or in combination with any other feature(s), if necessary with appropriate modification of other features, as would be readily apparent to the skilled person.
Coatings were applied to the internal surfaces of PET vials and their effectiveness assessed by the deposition test referred to earlier.
BTMSPA, APTMS and APTES were each prepared individually as solutions of 0.1 g in ethanol (50 g). Each primer solution was then used to prime 3 PET vials using the fill and drain technique with 30 seconds contact time and then draining the vials upside down for 2 minutes then placing upright for 30 minutes to equilibrate then curing at 55° C. for 30 minutes in an oven with a wet lab wipe to boost the moisture level. Each of the 3 samples above was then left to equilibrate with room temperature and humidity for 4 hours prior to ECC7000 coating.
Each vial was then fill and drain coated with a solution of Fluorocarbon B (10% solution) (1.0 g) in MNFBE (99 g). The vials were left to equilibrate with ambient air for 30 minutes and then cured at 55° C. for 30 minutes in an oven with a wet lab wipe to boost the moisture level.
The details of any primer and the top coat are given in Table 6 along with the results of the deposition test.
Further examples of coatings applied to the internal surfaces of PET vials were assessed by the deposition test.
A top coating solution of Fluorosilane B (10%w/w) was prepared from Fluorosilane B (2 g) in MNFBE (18 g).
A top coating solution of Fluorosilane C (8%w/w) was prepared from a Fluorosilane C 20%w/w solution (13.5g) in MNFBE (20.2g).
PET vials (27) were fill and drain coated in a solution of BTMSPA (0.2 g) in dehydrated ethanol (99.8 g). The vials were then placed open end down onto lab wipe for 5 minutes, to drain excess coating solution, before being placed upright to equilibrate with ambient air (22° C. 34% RH) for 30 minutes. The vials were then cured in an oven at 60° C. for 30 minutes.
The 27 BTMSPA primed PET vials were separated into 9 sets of 3 vials and were coated as shown in the table below employing the fill and drain approach with a 30 seconds contact time. All vials were placed open end down for 5 minutes to drain the coating solution, before being stored open end up for 30 minutes to equilibrate at ambient temperature and humidity (22° C. 34% RH). The vials were then oven cured at 55° C. for 30 minutes.
A comparative experiment was performed at the same time in which a primer solution and top coat solution were mixed together and applied as a single coating. Another comparative experiment compared top coating without primer coating.
The details of top coat for examples are given in Table 7a along with results of the deposition test, and a comparison where no coating was applied. Table 7b gives some further comparative tests with alternative coatings and deposition test results. The vials with BTMSPA prime and Fluorosilane A top coat showed acceptably low deposition. Those with BTMSPA prime and Fluorosilane B or C top coat showed virtually no deposition at all.
Further examples of coatings applied to the internal surfaces of PET vials were assessed by the deposition test.
Each primer (A to E and also BTMSPA) (0.1 g) was separately dissolved in isopropanol (50 g).
PET vials (n=3, for each sample designation) were then fill and drain coated with each primer solution using a 30 seconds contact time. The vials were then oven cured at 60° C. for 30 minutes. The primed vials were then left overnight.
Fluorosilane B (1.0 g) was dissolved in MNFBE (9 g) to make a 10%w/w solution. 10%w/w solution (1.0 g) was then dissolved in MNFBE (99 g). All vials were fill and drain coated for 30 seconds and then oven cured for 30 minutes at 60° C.
Details of the coatings applied and results of the salbutamol sulphate deposition test are tabulated in Table 8.
Very low depositions similar to those seen in the previous example were repeated here when other primers were used, except where the primer had an unsubstituted alkyl linking group (Primer B).
A modified coating process for applying coatings to the internal surfaces of PET vials was assessed by the deposition test.
Priming solution was prepared from BTMSPA (0.2 g) dissolved in ethanol and made up to 99.8 g.
Fluorosilane B 10%w/w solution (1.0 g) was added to MNFBE (99 g) to prepare a top coating solution.
The following samples were prepared:
9A—PET vials (3) were fill and drain coated in priming solution. The vials were then placed open end down onto lab wipe for 5 minutes, to drain excess coating solution, before being placed upright to equilibrate with ambient air (22° C. 34% RH) for 30 minutes. The vials were then cured in an oven at 60° C. for 30 minutes. Top coating solution was applied by filling and draining with a 30 seconds contact time. All vials were placed open end down for 5 minutes to drain the coating solution, before being stored open end up for 30 minutes to equilibrate at ambient temperature and humidity (22° C. 34% RH). The vials were then oven cured at 60° C. for 30 minutes.
9B—PET vials (3) were fill and drain coated in priming solution. The vials were then quickly air-dried. Top coating solution was applied by filling and draining with a 30 seconds contact time. All vials were placed open end down for 5 minutes to drain the coating solution, before being stored open end up for 30 minutes to equilibrate at ambient temperature and humidity (22° C. 34% RH). The vials were then oven cured at 60° C. for 30 minutes.
9C—No primer was used. Top coating solution was applied by filling and draining with a 30 seconds contact time. All vials were placed open end down for 5 minutes to drain the coating solution, before being stored open end up for 30 minutes to equilibrate at ambient temperature and humidity (22° C. 34% RH). The vials were then oven cured at 60° C. for 30 minutes.
Details of the primer and top coat used and any method variations are provided in table 9, along with the results of the deposition test. The prime and top coating may be cured in a single curing step.
Metering valves as shown in
A priming solution of BTMSPA (0.2 g) dissolved in HFE72DE (168 g) was prepared. 120 springs and 120 tanks, which had previously been washed as in Example 2, were dip coated in the coating solution and then oven cured at 120° C. for 30 minutes.
80 PBT plastic stems were washed in ENFBE as in Example 2.
A priming solution of BTMSPA (0.1 g) dissolved in dehydrated ethanol (50 g) was prepared. 80 washed PBT plastic stems were dip coated in the coating solution and then oven cured at 55° C. for 30 minutes.
Top Coating of Primed Springs and Tanks with Fluorosilane A
A top coating solution of Fluorosilane A (2.0 g) dissolved in HFE72DE (168 g) was prepared. 80 primed tanks and 80 primed springs were dip coated for 30 seconds in the solution. The components were then oven cured at 120° C. for 30 minutes.
Top Coating of Primed Springs and Tanks with Fluorosilane B
A top coating solution of Fluorosilane B (10%) (1.0 g) dissolved in MNFBE (84 g) was prepared. 40 primed tanks and 40 primed springs were dip coated for 30 seconds in the solution. The components were then oven cured at 120° C. for 30 minutes.
A top coating solution of Fluorosilane A (1.0 g) dissolved in MNFBE (99 g) was prepared.
A top coating solution of Fluorosilane B (10%) (1.0 g) dissolved in MNFBE (99 g) was prepared.
40 of the BTMSPA-primed plastic stems were dip coated in each solution above as specified in Table 10a. The coated stems were then dried on lab wipe and then oven cured at 55° C. for 30 minutes.
Valves were constructed as in Table 10a below. For each valve lot 10A-10F, five valves were constructed and tested in inhaler canisters (n=5). The springs and tanks of the test samples and the controls were coated, while the bottle emptiers were left uncoated. Use of talc or Magnesium Stearate on the seals (inner tank seal and diaphragm seal) and/or silicone oil lubrication of the stem and seals sub-assembly during valve assembly was done to ensure that the valves functioned reliably when sealed onto inhaler canisters. Nevertheless, controls with and without the seal lubrication and silicone oil lubrication were performed. The assembled valves were then placed on inhaler canisters containing medicament suspended in an HFA propellant formulation.
The inhalers were actuated repeatedly to exhaust the contents through the valves, then the valves were removed and carefully dismantled. The medicament deposits on the separate components were assayed by washing them off in a suitable solvent and sampling to an hplc.
Magnesium Stearate dusting was carried out as disclosed in WO2012/173971 (Experiment 2 dry coating): about 2½ mg Magnesium stearate per gram of seals was used for the inner tank seals; about 1 mg Magnesium stearate per gram of seals was used for the diaphragm seals.
The levels of deposited medicament on each of the components following exhaustion of the contents of the inhalers is shown in Table 10b. The average cumulative deposition for 3 components (spring, tank and plastic stem) is presented alongside the individual values for the components.
The 3 component average medicament deposition was improved by coating the plastic stem relative to both controls (10A and 10B), as was the medicament deposition on the plastic stem itself
Even though the stems and springs were coated using primer and fluorosilane in both test and control runs, medicament deposition on the spring and tank was still generally improved by coating the plastic stem.
Valves as shown in
Metering tanks, springs, valve bodies, inner and outer seals, valve stems and ferrules were gathered for making valves as shown in
Priming of Metering Tanks, Stems, Springs and Valve Bodies with BTMSPA
20 metering tanks, stems, springs, valve bodies were immersed with agitation for 30 seconds in a primer solution comprising BTMSPA (0.2 g) in dehydrated ethanol (100 g). The components were strained out then air dried and then placed in an air drying oven for 30 minutes at 60° C. to cure the priming coating.
The primed components were left to cool down and equilibrate with ambient air overnight.
10 sets of metering tanks, stems, springs, valve bodies were each coated with one of each of 2 fluorosilanes as follows:
A top coating solution of Fluorosilane B (10%) (1.0 g) dissolved in MNFBE (99 g) was prepared for use in Example 11B.
A top coating solution of Fluorosilane C (0.2%) in MNFBE was prepared for use in Example 11C.
The above components sets were placed into individual 250 ml glass reagent bottles and contacted for 3 minutes with occasional agitation with the appropriate fluorosilane solution. The components were then strained out air dried and then cured at 60° C. for 16 hours.
The coated components were assembled into inhaler valves as shown in
Similarly, the uncoated components were also assembled into inhaler valves as controls.
The coated test valves and control valves were incorporated into metered dose inhaler and used to deliver a formulation of micronised salbutamol sulphate suspended in HFA134a. The target dose of the product was 100 μg per actuation and the cold filling technique was employed for the filling process.
Both the coated (Examples 11B and 11C) and the uncoated (Comparative Example 11A) valve product lots were actuated through life to shot number 120, after which point the test inhalers were chilled down, the valves removed and the valve components disassembled and assayed for salbutamol sulphate residue (n=5 for each valve lot).
The assay was done by uv spectrophotometry of quantitative washings from each component made up to a suitable volume with washing solvent. The assay results are shown in table 11.
| Number | Date | Country | Kind |
|---|---|---|---|
| 1409095.5 | May 2014 | GB | national |
| 1504277.3 | Mar 2015 | GB | national |
This application is a national stage filing under 35 U.S.C. 371 of PCT/US2015/031766, filed May 20, 2015, which claims the benefit of United Kingdom Application No.1409095.5, filed May 22, 2014, the disclosure of which is incorporated by reference in its/their entirety herein.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US2015/031766 | 5/20/2015 | WO | 00 |
