Patent Application
20160015898
The present invention relates to the technical field of lubricated and siliconized surfaces, for example interior surfaces of pharmaceutical packages or other vessels for storing or other contact with fluids. (A “deposit of lubricant” as defined in this specification also includes deposits of “lubricants” for non-lubricating uses, for example siliconization of a vessel wall to prevent adherence of a fluid stored in the vessel.)
The present invention also relates to a pharmaceutical package or other vessel and to a method for making a pharmaceutical package with a lubricated surface. The present invention also relates more generally to medical articles, including articles other than packages or vessels, for example catheters.
In glass syringes and other pharmaceutical packages, silicone oil is typically used as a lubricant to allow the plunger tip to slide in the barrel, and/or to promote draining of the intended deliverable fluid from the syringe surfaces.
Glass pharmaceutical packages or other vessels are prone to breakage or degradation during manufacture, filling operations, shipping and use, which means that glass particulates may enter the drug. The presence of glass particles has led to many FDA Warning Letters and to product recalls.
Glass-forming processes do not yield the tight dimensional tolerances required for some of the newer auto-injectors and delivery systems. Glass is also more difficult and expensive to fabricate into syringes than injection molded plastics.
An important consideration regarding medical syringes is to ensure that the plunger can move at a constant speed and with a constant force when it is pressed into the barrel during use, with a low initiation or breakout force, Fi, and a low maintenance force, Fm. A similar consideration making lubrication desirable applies to vessels such as pharmaceutical vials which have to be closed by a closure, for example a plunger tip, septum or stopper, and to the septum or stopper itself, and more generally to any surface which desirably provides smooth operation of moving parts and/or is protectively coated.
One factor affecting the magnitude and aging of the breakout force is the surface composition and topology of the syringe. Specifically, the breakout force is lower for glass syringes than for plastic syringes due to the surface energy differences between glass and plastic (glass is a hydrophilic surface and plastic is a hydrophobic surface). PDMS is hydrophobic. It would be useful to provide a similar breakout force profile on plastic and glass syringes, and for the effect of aging on the breakout force to be minimal.
A non-limiting aspect of the invention is a syringe comprising a wall, a primer coating, and a deposit of fluid lubricant.
The wall has a generally cylindrical interior surface defining a lumen and adapted to receive a plunger
The primer coating or layer is between 1 and 1000 nm thick. It comprises SiOxCyHz, in which x is from about 0.5 to about 2.4 as measured by X-ray photoelectron spectroscopy (XPS), y is from about 0.6 to about 3 as measured by XPS, and z is from about 2 to about 9, on at least a portion of the interior surface. The primer coating or layer has an outside surface facing the interior surface of the barrel and an inside surface facing the lumen.
The deposit of fluid lubricant is deposited on the inside surface of the primer coating or layer.
The primer coating or layer improves the lubrication between the relatively sliding parts. More evenly distributed lubricant might be a factor in lowering the sliding friction and making the sliding friction more uniform. As another potential result, in a medical vessel coated on the interior wall with the primer coating or layer and a deposit of lubricant, the more evenly distributed lubricant can improve draining of the vessel. As a third potential result, the more evenly distributed lubricant can be used in a smaller quantity to obtain the same technical effect or advantage, thus potentially reducing the amount of lubricant available to mix with the contents of the vessel. Some potential examples of the lubricant mixing with the contents of the vessel are mechanical or chemical emulsification of the lubricant and a drug or other contents of the vessel.
Optionally, the primer coating or layer itself, without a deposit of lubricant, can improve draining of the vessel.
Optionally, a similar breakout force profile can be obtained on plastic and glass syringes if the plastic syringes are treated as described in this specification.
Another non-limiting aspect of the invention is a method of making a syringe as described above.
A syringe is provided having a surface to be lubricated.
A primer coating or layer of SiOxCy or SiNxCy, in which x is from about 0.5 to about 2.4 and y is from about 0.6 to about 3, is applied to the surface. The primer coating or layer can be applied by chemical vapor deposition of a polysiloxane or polysilazane precursor, typically in the presence of oxygen. The primer coating or layer is applied either directly to the syringe surface or with one or more intervening coatings or layers between the primer coating or layer and the syringe surface. The primer coating or layer has a first primer surface facing away from the syringe surface and a second primer surface facing the syringe surface.
A deposit of lubricant is applied to the first primer surface.
Another non-limiting aspect of the invention is a prefilled syringe comprising a syringe as described above containing a fluid to be dispensed and closed with a plunger. The fluid to be dispensed can be any of the inhalation anesthetics, injectable drugs, liquid drugs (non-injectable), drug classes, diagnostic test materials, or other materials recited in the specification or claims.
Many other embodiments of the present invention are expressly contemplated, as recited in the claims.
The following reference characters are used in the drawing figures:
In the context of the present invention, the following definitions and abbreviations are used:
The term “at least” in the context of the present invention means “equal or more” than the integer following the term. The word “comprising” does not exclude other elements or steps, and the indefinite article “a” or “an” does not exclude a plurality unless indicated otherwise. Whenever a parameter range is indicated, it is intended to disclose the parameter values given as limits of the range and all values of the parameter falling within said range.
“First” and “second” or similar references to, for example, deposits of lubricant, processing stations or processing devices refer to the minimum number of deposits, processing stations or devices that are present, but do not necessarily represent the order or total number of deposits, processing stations and devices or require additional deposits, processing stations and devices beyond the stated number. These terms do not limit the number of processing stations or the particular processing carried out at the respective stations.
For purposes of the present invention, an “organosilicon precursor” is a compound having at least one of the linkages:
which is a tetravalent silicon atom connected to an oxygen or nitrogen atom and an organic carbon atom (an organic carbon atom being a carbon atom bonded to at least one hydrogen atom). A volatile organosilicon precursor, defined as such a precursor that can be supplied as a vapor in a PECVD apparatus, is an optional organosilicon precursor. Optionally, the organosilicon precursor is selected from the group consisting of a linear siloxane, a monocyclic siloxane, a polycyclic siloxane, a polysilsesquioxane, an alkyl trimethoxysilane, linear silazane, a monocyclic silazane, a polycyclic silazane, or a combination of any two or more of these precursors, and preferably comprises octamethylenecyclotetrasiloxane (OMCTS), tetramethyldisiloxane (TMDSO), hexamethyldisiloxane (HMDSO), or a combination of two or more of these precursors.
The feed amounts of PECVD precursors, gaseous reactant or process gases, and carrier gas are sometimes expressed in “standard volumes” in the specification and claims. The standard volume of a charge or other fixed amount of gas is the volume the fixed amount of the gas would occupy at a standard temperature and pressure (without regard to the actual temperature and pressure of delivery). Standard volumes can be measured using different units of volume, and still be within the scope of the present disclosure and claims. For example, the same fixed amount of gas could be expressed as the number of standard cubic centimeters, the number of standard cubic meters, or the number of standard cubic feet. Standard volumes can also be defined using different standard temperatures and pressures, and still be within the scope of the present disclosure and claims. For example, the standard temperature might be 0° C. and the standard pressure might be 760 Torr (as is conventional), or the standard temperature might be 20° C. and the standard pressure might be 1 Torr. But whatever standard is used in a given case, when comparing relative amounts of two or more different gases without specifying particular parameters, the same units of volume, standard temperature, and standard pressure are to be used relative to each gas, unless otherwise indicated.
The corresponding feed rates of PECVD precursors, gaseous reactant or process gases, and carrier gas are expressed in standard volumes per unit of time in the specification. For example, in the working examples the flow rates are expressed as standard cubic centimeters per minute, abbreviated as sccm. As with the other parameters, other units of time can be used, such as seconds or hours, but consistent parameters are to be used when comparing the flow rates of two or more gases, unless otherwise indicated.
The present syringes optionally can be used as pharmaceutical packages or other vessels in which the lumen has a void volume of from 0.5 to 50 mL, optionally from 1 to 10 mL, optionally from 0.5 to 5 mL, optionally from 1 to 3 mL. The substrate surface can be part or all of the inner or interior surface of a vessel having at least one opening and an inner or interior surface.
A “hydrophobic layer” in the context of the present invention means that the coating or layer lowers the wetting tension of a surface coated with the coating or layer, compared to the corresponding uncoated surface. Hydrophobicity is thus a function of both the uncoated substrate and the coating or layer. The same applies with appropriate alterations for other contexts wherein the term “hydrophobic” is used. The term “hydrophilic” means the opposite, i.e. that the wetting tension is increased compared to reference sample. The present hydrophobic layers are primarily defined by their hydrophobicity and the process conditions providing hydrophobicity
The values of w, x, y, and z as applicable to the empirical composition SiwOxCyHz throughout this specification should be understood as ratios or an empirical formula (for example for a coating or layer), rather than as a limit on the number or type of atoms in a molecule. For example, octamethylcyclotetrasiloxane, which has the molecular composition Si4O4C8H24, can be described by the following empirical formula, arrived at by dividing each of w, x, y, and z in the molecular formula by 4, the largest common factor: Si1O1C2H6. The values of w, x, y, and z are also not limited to integers. For example, (acyclic) octamethyltrisiloxane, molecular composition Si3O2C8H24, is reducible to Si1O0.67C2.67H8. Also, although SiOxCyHz is described as equivalent to SiOxCy, it is not necessary to show the presence of hydrogen in any proportion to show the presence of SiOxCy.
“Wetting tension” is a specific measure for the hydrophobicity or hydrophilicity of a surface. An optional wetting tension measurement method in the context of the present invention is ASTM D 2578 or a modification of the method described in ASTM D 2578. This method uses standard wetting tension solutions (called dyne solutions) to determine the solution that comes nearest to wetting a plastic film surface for exactly two seconds. This is the film's wetting tension. The procedure utilized is varied herein from ASTM D 2578 in that the substrates are not flat plastic films, but are tubes made according to the Protocol for Forming PET Tube and (except for controls) coated according to the Protocol for coating Tube Interior with Hydrophobic Coating or Layer (see Example 9 of EP2251671 A2).
A “primer coating or layer” according to the present invention is a coating or layer which is more receptive than the uncoated surface to a deposit of lubricant, The deposit of lubricant reduces the frictional resistance of the coated surface in comparison to a reference surface that is uncoated. The primer coating or layer optionally can have a composition according to the empirical composition SiOx, or according to the empirical composition SiwOxCyHz, (or its equivalent SiOxCy) as defined herein, which omits hydrogen because it is not measured by the XPS (X-ray photoelectron spectroscopy) method used in this specification to define the composition of a plasma treated surface or a CVD or chemical vapor deposition coating or layer. The primer coating or layer generally has an atomic ratio SiwOxCy (or its equivalent SiOxCy) wherein w is 1, x is from about 0.5 to about 2.4, y is from about 0.6 to about 3, as measured by XPS.
Where it is desired to determine the proportion of hydrogen, and thus the value of z in SiwOxCyHz, this can be done using well-known techniques such as Rutherford backscattering (RBS) or hydrogen forward scattering (HFS).
Typically, expressed as the formula SiwOxCy, the atomic ratios of Si, O, and C in the “primer coating or layer” are, as several options:
Si 100: O 50-150: C 90-200 (i.e. w=1, x=0.5 to 1.5, y=0.9 to 2);
Si 100: O 70-130: C 90-200 (i.e. w=1, x=0.7 to 1.3, y=0.9 to 2)
Si 100: O 80-120: C 90-150 (i.e. w=1, x=0.8 to 1.2, y=0.9 to 1.5)
Si 100: O 90-120: C 90-140 (i.e. w=1, x=0.9 to 1.2, y=0.9 to 1.4), or
Si 100: O 92-107: C 116-133 (i.e. w=1, x=0.92 to 1.07, y=1.16 to 1.33)
The atomic ratio can be determined by XPS. Taking into account the H atoms, which are not measured by XPS, the coating or layer may thus in one aspect have the formula SiwOxCyHz (or its equivalent SiOxCy), for example where w is 1. X is from about 0.5 to about 2.4, optionally between 0.5 and 1.5, preferably between 0.7 and 1.3, more preferably between 0.8 and 1.2, still more preferably between 0.9 and 1.2. Y is from about 0.6 to about 3, optionally between 0.9 and 2, preferably between 0.9 and 1.5, more preferably between 0.9 and 1.4. Z is from about 2 to about 9. Typically, such coating or layer would hence contain 36% to 41% carbon normalized to 100% carbon plus oxygen plus silicon.
“Frictional resistance” can be static frictional resistance and/or kinetic frictional resistance.
One of the optional embodiments of the present invention is a syringe part, for example a syringe or plunger tip, coated with a deposit of lubricant on a primer coating or layer. In this contemplated embodiment, the relevant static frictional resistance in the context of the present invention is the breakout force as defined herein, and the relevant kinetic frictional resistance in the context of the present invention is the plunger sliding force as defined herein. For example, the plunger sliding force as defined and determined herein is suitable to determine the presence or absence and the lubricity and/or protective characteristics of a deposit of lubricant on a primer coating or layer in the context of the present invention whenever the coating or layer is applied to any syringe or syringe part, for example to the inner wall of a syringe. The breakout force is of particular relevance for evaluation of the coating or layer effect on a prefilled syringe, i.e. a syringe which is filled after coating and can be stored for some time, for example several months or even years, before the plunger tip is moved again (has to be “broken out”).
The “plunger sliding force” (synonym to “glide force,” “maintenance force”, or Fm, also used in this description) in the context of the present invention is the force required to maintain movement of a plunger tip in a syringe, for example during aspiration or dispense. It can advantageously be determined using the ISO 7886-1:1993 test described herein and known in the art. A synonym for “plunger sliding force” often used in the art is “plunger force” or “pushing force”.
The “plunger breakout force” (synonym to “breakout force”, “break loose force”, “initiation force”, Fi, also used in this description) in the context of the present invention is the initial force required to move the plunger tip in a syringe, for example in a prefilled syringe.
Both “plunger sliding force” and “plunger breakout force” and methods for their measurement are described in more detail in subsequent parts of this description. These two forces can be expressed in N, lbs or kg. These units correlate as follows: 1N=0.102 kg=0.2248 lbs (pounds).
Sliding force and breakout force are sometimes used herein to describe the forces required to advance a stopper or other closure into a pharmaceutical package or other vessel, such as a medical sample tube or a vial, to seat the stopper in a vessel to close the vessel. Its use is analogous to use in the context of a syringe and its plunger tip, and the measurement of these forces for a vessel and its closure are contemplated to be analogous to the measurement of these forces for a syringe, except that at least in most cases no liquid is ejected from a vessel when advancing the closure to a seated position.
“Slidably” means that the plunger tip, closure, or other removable part is permitted to slide in a syringe or other vessel.
The present invention will now be described more fully, with reference to the accompanying drawings, in which several embodiments are shown. This invention can, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth here. Rather, these embodiments are examples of the invention, which has the full scope indicated by the language of the claims. Like numbers refer to like or corresponding elements throughout. The following disclosure relates to all embodiments unless specifically limited to a certain embodiment.
Referring to
The syringe as illustrated includes a plunger 258 having an outer sliding surface 259 configured to slide within the lumen 300 along the inner sliding surface 254. Optionally, the outer sliding surface 259 can be a PECVD treated surface as well.
The term “syringe,” as used here, is broadly defined to include cartridges, injection “pens,” and other types of barrels or reservoirs adapted to be assembled with one or more other components to provide a functional syringe. “Syringe” is also broadly defined to include related articles such as auto-injectors, which provide a mechanism for dispensing the contents.
Optionally, the syringe, in particular a surface of a syringe such as the interior surface 254 to be lubricated, comprises a first deposit of lubricant 287 applied to the primer surface.
Optionally for any of the embodiments, at least a portion of the wall 214 of the vessel 250 comprises or consists essentially of a polymer, for example a polyolefin (for example a cyclic olefin polymer, a cyclic olefin copolymer, or polypropylene), a polyester, for example polyethylene terephthalate, polyethylene naphthalate, a polycarbonate, or any combination or copolymer of any of these. Specific contemplated wall materials include COC (cyclic olefin copolymer), COP (cyclic olefin polymer), PET (polyethylene terephthalate), polypropylene (PP), or a combination of two or more of these. Optionally, at least a portion of the wall 214 of the vessel 250 comprises or consists essentially of glass, for example borosilicate glass.
The plunger can be made of a variety of materials. For example, at least a portion of the plunger can be made of chlorobutyl rubber, bromobutyl rubber, silicone rubber, or a combination of any two or none or these.
Optionally, the outer diameter of the plunger when unconstrained by the syringe barrel is from about 0.05 mm to about 0.3 mm greater, preferably from 0.1 to about 0.3 mm, greater, more preferably from 0.15 mm to 0.25 mm greater, still more preferably about 0.2 mm greater than the average inner diameter of the interior surface.
Optionally, the PECVD treated surface comprises a primer coating or layer 286 of SiOxCy, in which x is from about 0.5 to about 2.4 and y is from about 0.6 to about 3. Optionally, x is between 0.5 and 1.5 and y is between 0.9 and 2. Optionally, x is between 0.7 and 1.3 and y is between 0.9 and 2. Optionally, x is between 0.8 and 1.2 and y is between 0.9 and 1.5. Optionally, x is between 0.9 and 1.2 and y is between 0.9 and 1.4. Optionally, x is between 0.92 and 1.07 and y is between 1.16 and 1.33.
As another option, the PECVD treated surface comprises a primer coating or layer 286 of SiOx, in which x is from 1.5 to 2.9.
Optionally, the primer coating or layer 286 is between 10 and 1000 nm thick. Optionally, the primer coating or layer is between 10 and 1000 nm thick. Optionally, the primer coating or layer is between 50 and 800 nm thick. Optionally, the primer coating or layer is between 100 and 700 nm thick. Optionally, the primer coating or layer is between 300 and 600 nm thick.
Optionally, the primer coating or layer 286 contacting the fluid is between 10 and 1000 nm thick two years after the article is assembled. Optionally, the primer coating or layer contacting the fluid is between 20 and 700 nm thick two years after the article is assembled. Optionally, the primer coating or layer contacting the fluid is between 50 and 500 nm thick two years after the article is assembled. Optionally, the primer coating or layer contacting the fluid is between 100 and 400 nm thick two years after the article is assembled. Optionally, the primer coating or layer contacting the fluid is between 150 and 300 nm thick two years after the article is assembled.
Optionally, the fluid removes the primer coating or layer at a rate of 1 nm or less of primer coating or layer thickness per 44 hours of contact with the fluid. Optionally, the fluid removes the primer coating or layer at a rate of 1 nm or less of primer coating or layer thickness per 88 hours of contact with the fluid. Optionally, the fluid removes the primer coating or layer at a rate of 1 nm or less of primer coating or layer thickness per 175 hours of contact with the fluid. Optionally, the fluid removes the primer coating or layer at a rate of 1 nm or less of primer coating or layer thickness per 250 hours of contact with the fluid. Optionally, the fluid removes the primer coating or layer at a rate of 1 nm or less of primer coating or layer thickness per 350 hours of contact with the fluid.
Optionally, the primer has a contact angle (with distilled water) of from 70° to 130°. Optionally, the interior surface of the primer has a contact angle (with distilled water) of from 90° to 110°. Optionally, the interior surface of the primer has a contact angle (with distilled water) of from 80° to 120°.
Optionally, the fluid lubricant 287 comprises polydimethylsiloxane. For several examples, it can comprise non-reactive silicone fluid, nonreactive silicone emulsion, curable silicone fluid, or a combination of two or more of these.
A deposit of fluid lubricant 287 can be formed on the CVD treated surface 254 in any convenient manner, such as by spraying a liquid lubricant or by applying it using an applicator. Optionally, the lubricant has a molecular weight of from about 1900 to about 37,000. Optionally, the lubricant has a viscosity of from about 20 CSt. to about 13,000 CSt., alternatively from 500 to 30,000 cSt, preferably from 1000 to 25,000 cSt, more preferably from 5,000 to 20,000 cSt, still more preferably from 10,000 to 15,000 cSt, optionally about 12,500 cSt.
Optionally, the breakout force, Fi, of the plunger is between 0.5 and 15 N, alternatively between 1 and 10 N, alternatively between 5 and 15 N, after a park time of 3 days, alternatively 10 days, alternatively 30 days, alternatively 3 months, alternatively 6 months, alternatively 9 months, alternatively 12 months, alternatively 15 months, alternatively 18 months, alternatively two years.
Optionally, the maintenance force, Fm, of the plunger is between 0.5 and 15 N, alternatively between 1 and 10 N, alternatively between 5 and 15 N, after a park time of 3 days, alternatively 10 days, alternatively 30 days, alternatively 3 months, alternatively 6 months, alternatively 9 months, alternatively 12 months, alternatively 15 months, alternatively 18 months, alternatively two years.
Optionally, the lubricant has a contact angle (with distilled water) of from 90° to 150°.203. Optionally, the lubricant has a contact angle (with distilled water) of from 90° to 110°. Optionally, the lubricant has a contact angle (with distilled water) of from 90° to 120°. Optionally, the lubricant has a contact angle (with distilled water) of from 0° to 35° greater than the contact angle (with distilled water) of the primer coating or layer.
Optionally, the deposit of lubricant on the primer coating or layer is effective to provide a lower frictional resistance than the uncoated syringe surface between the syringe surface and a relatively sliding part at least one year after the syringe is assembled with a plunger. the frictional resistance is reduced by at least 25% in comparison to the uncoated article surface. Optionally, the frictional resistance is reduced by at least 45% in comparison to the uncoated article surface. Optionally, the frictional resistance is reduced by at least 60% in comparison to the uncoated article surface. Optionally, the deposit of lubricant is effective to reduce the frictional resistance between a portion of the article surface contacted by the fluid and a relatively sliding part after the article is assembled. Optionally, the deposit of lubricant is effective to reduce the frictional resistance between the article surface and a relatively sliding part at least one year after the article is assembled. Optionally, the deposit of lubricant is effective to reduce the frictional resistance between the article surface and a relatively sliding part at least eighteen months after the article is assembled. Optionally, the deposit of lubricant is effective to reduce the frictional resistance between the article surface and a relatively sliding part at least two years after the article is assembled.
Further PECVD coatings or layers are contemplated, in addition to the primer coating or layer 286.
Optionally, a barrier coating or layer 288 can be provided between the primer coating or layer 286 and the syringe surface 254. The barrier coating or layer 288 can be made at least in part of SiOx, wherein x is from 1.5 to 2.9, from 2 to 1000 nm thick. The barrier coating or layer of SiOx has an interior surface facing the lumen and an outer surface facing the wall inner or article surface 254. The barrier coating or layer 288 is effective to reduce the ingress of atmospheric gas into the lumen 212, compared to an uncoated container otherwise the same as the pharmaceutical package or other vessel 210.
As another option, an adhesion layer 266 can be provided between the barrier coating or layer 288 and the syringe surface 254.
A method of making a syringe as previously described is also contemplated. To carry out the method, a syringe is provided having a surface to be lubricated. A primer coating or layer of SiOxCy or SiNxCy is applied to the surface; in these formulas x can be from about 0.5 to about 2.4 and y can be from about 0.6 to about 3. The primer coating or layer can be applied by chemical vapor deposition of a polysiloxane or polysilazane precursor, in the presence of oxygen. The primer coating or layer can be applied either directly to the syringe surface or with one or more intervening coatings or layers between the primer coating or layer and the syringe surface.
The primer coating or layer can have a first primer surface facing away from the syringe surface and a second primer surface facing the syringe surface. A first deposit of lubricant can be adhered to the first primer surface.
Optionally, a fluid can be placed in the lumen via the opening, optionally for extended storage, and the opening can be closed with a closure such as the plunger 258. The fluid can be an aqueous liquid, for example a drug. The drug can be a parenteral drug, as one example. Other examples of suitable fluids are a food, a nutritional supplement, an inhalation anesthetic, or a diagnostic test material.
The fluid can be a member selected from the group consisting of:
Isopropenyl vinyl ether
methoxyflurane,
Apidra (Insulin Glulisine [rDNA origin] Inj)
Aranesp (darbepoetin alfa)
Cytovene (ganciclovir)
Depo-Provera 104 mg/ml
Depo-Provera 150 mg/ml
EC-Naprosyn (naproxen)
Enbrel (etanercept)
Fabrazyme (Adalsidase beta)
Forteo (Teriparatide (rDNA origin) Injection)
Fuzeon (enfuvirtide)
hG-CSF
Increlex (Mecasermin [rDNA origin] Injection)
Insulin Aspart [rDNA origin] Inj (NovoLog)
Insulin Glargine [rDNA origin] Injection (Lantus)
Insulin Glulisine [rDNA origin] Inj (Apidra)
Interferon alfa-2b, Recombinant for Injection (Intron A)
Intron A (Interferon alfa-2b, Recombinant for Injection)
Invirase (saquinavir mesylate)
Iplex (Mecasermin Rinfabate [rDNA origin] Injection)
Klonopin (clonazepam)
lacosamide Tablet and Injection (Vimpat)
Liraglutide [rDNA] Injection (Victoza)
Mecasermin [rDNA origin] Injection (Increlex)
Mecasermin Rinfabate [rDNA origin] Injection (Iplex)
Myozyme (Alglucosidase alfa)
Naprosyn (naproxen)
Neulasta (pegfilgrastim)
NovoLog (Insulin Aspart [rDNA origin] Inj)
Nplate (romiplostim)
Nutropin (Somatropin (rDNA origin) for Inj)
Nutropin Depot (Somatropin (rDNA origin) for Inj)
Omnitrope (Somatropin [rDNA origin] Injection)
Physostigmine Salicylate (Physostigmine Salicylate (injection))
Physostigmine Salicylate (injection) (Physostigmine Salicylate)
rhApo2L/TRAIL
Rocephin (ceftriaxone)
Roferon-A (interferon alfa-2a)
Romazicon (flumazenil)
Sensipar (cinacalcet)
Serostim LQ (Somatropin (rDNA origin) Injection)
Somatropin (rDNA origin) for Inj (Nutropin)
Teriparatide (rDNA origin) Injection (Forteo)
Tev-Tropin (Somatropin, rDNA Origin, for Injection)
tgAAC94
Valium (diazepam)
Victoza (Liraglutide [rDNA] Injection)
Vimpat (lacosamide Tablet and Injection)
Xenical (orlistat)
Zenapax (daclizumab)
Crystalline Amino Acid Solution with Electrolytes (Aminosyn Electrolytes)
Epogen (Epoetin alfa)
Methylin Oral Solution (Methylphenidate HCl Oral Solution 5 mg/5 mL and 10 mg/5 mL)
Methylphenidate HCl Oral Solution 5 mg/5 mL and 10 mg/5 mL (Methylin Oral Solution)
Methylprednisolone sodium succinate (Solu Medrol)
Nystatin (oral) (Nystatin Oral Suspension)
Nystatin Oral Suspension (Nystatin (oral))
Solu Medrol (Methylprednisolone sodium succinate)
5-alpha-reductase inhibitors
5-aminosalicylates
5HT3 receptor antagonists
adamantane antivirals
adrenal cortical steroids
adrenal corticosteroid inhibitors
adrenergic bronchodilators
agents for hypertensive emergencies
agents for pulmonary hypertension
aldosterone receptor antagonists
alkylating agents
alpha-adrenoreceptor antagonists
alpha-glucosidase inhibitors
alternative medicines
amebicides
aminoglycosides
aminopenicillins
aminosalicylates
amylin analogs
androgens and anabolic steroids
angiotensin converting enzyme inhibitors
angiotensin II inhibitors
anorectal preparations
anorexiants
antacids
anthelmintics
anti-angiogenic ophthalmic agents
anti-CTLA-4 monoclonal antibodies
anti-infectives
antiadrenergic agents, centrally acting
antiadrenergic agents, peripherally acting
antiandrogens
antianginal agents
antiarrhythmic agents
antiasthmatic combinations
antibiotics/antineoplastics
anticholinergic antiemetics
anticholinergic antiparkinson agents
anticholinergic bronchodilators
anticholinergic chronotropic agents
anticholinergics/antispasmodics
anticoagulants
anticonvulsants
antidepressants
antidiabetic agents
antidiabetic combinations
antidiarrheals
antidiuretic hormones
antidotes
antiemetic/antivertigo agents
antifungals
antigonadotropic agents
antigout agents
antihistamines
antihyperlipidemic agents
antihyperlipidemic combinations
antihypertensive combinations
antihyperuricemic agents
antimalarial agents
antimalarial combinations
antimalarial quinolines
antimetabolites
antimigraine agents
antineoplastic detoxifying agents
antineoplastic interferons
antineoplastic monoclonal antibodies
antineoplastics
antiparkinson agents
antiplatelet agents
antipseudomonal penicillins
antipsoriatics
antipsychotics
antirheumatics
antiseptic and germicides
antithyroid agents
antitoxins and antivenins
antituberculosis agents
antituberculosis combinations
antitussives
antiviral agents
antiviral combinations
antiviral interferons
anxiolytics, sedatives, and hypnotics
aromatase inhibitors
atypical antipsychotics
azole antifungals
bacterial vaccines
barbiturate anticonvulsants
barbiturates
BCR-ABL tyrosine kinase inhibitors
benzodiazepine anticonvulsants
benzodiazepines
beta-adrenergic blocking agents
beta-lactamase inhibitors
bile acid sequestrants
biologicals
bisphosphonates
bone resorption inhibitors
bronchodilator combinations
bronchodilators
calcitonin
calcium channel blocking agents
carbamate anticonvulsants
carbapenems
carbonic anhydrase inhibitor anticonvulsants
carbonic anhydrase inhibitors
cardiac stressing agents
cardioselective beta blockers
cardiovascular agents
catecholamines
CD20 monoclonal antibodies
CD33 monoclonal antibodies
CD52 monoclonal antibodies
central nervous system agents
cephalosporins
cerumenolytics
chelating agents
chemokine receptor antagonist
chloride channel activators
cholesterol absorption inhibitors
cholinergic agonists
cholinergic muscle stimulants
cholinesterase inhibitors
CNS stimulants
coagulation modifiers
colony stimulating factors
contraceptives
corticotropin
coumarins and indandiones
cox-2 inhibitors
decongestants
dermatological agents
diagnostic radiopharmaceuticals
dibenzazepine anticonvulsants
digestive enzymes
dipeptidyl peptidase 4 inhibitors
diuretics
dopaminergic antiparkinsonism agents
drugs used in alcohol dependence
echinocandins
EGFR inhibitors
estrogen receptor antagonists
estrogens
expectorants
factor Xa inhibitors
fatty acid derivative anticonvulsants
fibric acid derivatives
first generation cephalosporins
fourth generation cephalosporins
functional bowel disorder agents
gallstone solubilizing agents
gamma-aminobutyric acid analogs
gamma-aminobutyric acid reuptake inhibitors
gamma-aminobutyric acid transaminase inhibitors
gastrointestinal agents
general anesthetics
genitourinary tract agents
GI stimulants
glucocorticoids
glucose elevating agents
glycopeptide antibiotics
glycoprotein platelet inhibitors
glycylcyclines
gonadotropin releasing hormones
gonadotropin-releasing hormone antagonists
gonadotropins
group I antiarrhythmics
group II antiarrhythmics
group III antiarrhythmics
group IV antiarrhythmics
group V antiarrhythmics
growth hormone receptor blockers
growth hormones
H. pylori eradication agents
H2 antagonists
hematopoietic stem cell mobilizer
heparin antagonists
heparins
HER2 inhibitors
herbal products
histone deacetylase inhibitors
hormone replacement therapy
hormones
hormones/antineoplastics
hydantoin anticonvulsants
illicit (street) drugs
immune globulins
immunologic agents
immunosuppressive agents
impotence agents
in vivo diagnostic biologicals
incretin mimetics
inhaled anti-infectives
inhaled corticosteroids
inotropic agents
insulin
insulin-like growth factor
integrase strand transfer inhibitor
interferons
intravenous nutritional products
iodinated contrast media
ionic iodinated contrast media
iron products
ketolides
laxatives
leprostatics
leukotriene modifiers
lincomycin derivatives
lipoglycopeptides
local injectable anesthetics
loop diuretics
lung surfactants
lymphatic staining agents
lysosomal enzymes
macrolide derivatives
macrolides
magnetic resonance imaging contrast media
mast cell stabilizers
medical gas
meglitinides
metabolic agents
methylxanthines
mineralocorticoids
minerals and electrolytes
miscellaneous agents
miscellaneous analgesics
miscellaneous antibiotics
miscellaneous anticonvulsants
miscellaneous antidepressants
miscellaneous antidiabetic agents
miscellaneous antiemetics
miscellaneous antifungals
miscellaneous antihyperlipidemic agents
miscellaneous antimalarials
miscellaneous antineoplastics
miscellaneous antiparkinson agents
miscellaneous antipsychotic agents
miscellaneous antituberculosis agents
miscellaneous antivirals
miscellaneous anxiolytics, sedatives and hypnotics
miscellaneous biologicals
miscellaneous bone resorption inhibitors
miscellaneous cardiovascular agents
miscellaneous central nervous system agents
miscellaneous coagulation modifiers
miscellaneous diuretics
miscellaneous genitourinary tract agents
miscellaneous GI agents
miscellaneous hormones
miscellaneous metabolic agents
miscellaneous ophthalmic agents
miscellaneous otic agents
miscellaneous respiratory agents
miscellaneous sex hormones
miscellaneous topical agents
miscellaneous uncategorized agents
miscellaneous vaginal agents
mitotic inhibitors
monoamine oxidase inhibitors
monoclonal antibodies
mouth and throat products
mTOR inhibitors
mTOR kinase inhibitors
mucolytics
multikinase inhibitors
muscle relaxants
mydriatics
narcotic analgesic combinations
narcotic analgesics
nasal anti-infectives
nasal antihistamines and decongestants
nasal lubricants and irrigations
nasal preparations
nasal steroids
natural penicillins
neuraminidase inhibitors
neuromuscular blocking agents
next generation cephalosporins
nicotinic acid derivatives
nitrates
non-cardioselective beta blockers
non-iodinated contrast media
non-ionic iodinated contrast media
non-sulfonylureas
nonsteroidal anti-inflammatory agents
norepinephrine reuptake inhibitors
norepinephrine-dopamine reuptake inhibitors
nucleoside reverse transcriptase inhibitors (NRTIs)
nutraceutical products
nutritional products
ophthalmic anesthetics
ophthalmic anti-infectives
ophthalmic anti-inflammatory agents
ophthalmic antihistamines and decongestants
ophthalmic diagnostic agents
ophthalmic glaucoma agents
ophthalmic lubricants and irrigations
ophthalmic preparations
ophthalmic steroids
ophthalmic steroids with anti-infectives
ophthalmic surgical agents
oral nutritional supplements
otic anesthetics
otic anti-infectives
otic preparations
otic steroids
otic steroids with anti-infectives
oxazolidinedione anticonvulsants
parathyroid hormone and analogs
penicillinase resistant penicillins
penicillins
peripheral opioid receptor antagonists
peripheral vasodilators
peripherally acting antiobesity agents
phenothiazine antiemetics
phenothiazine antipsychotics
phenylpiperazine antidepressants
plasma expanders
platelet aggregation inhibitors
platelet-stimulating agents
polyenes
potassium-sparing diuretics
probiotics
progesterone receptor modulators
progestins
prolactin inhibitors
prostaglandin D2 antagonists
protease inhibitors
proton pump inhibitors
psoralens
psychotherapeutic agents
psychotherapeutic combinations
purine nucleosides
pyrrolidine anticonvulsants
quinolones
radiocontrast agents
radiologic adjuncts
radiologic agents
radiologic conjugating agents
radiopharmaceuticals
RANK ligand inhibitors
recombinant human erythropoietins
renin inhibitors
respiratory agents
respiratory inhalant products
rifamycin derivatives
salicylates
sclerosing agents
second generation cephalosporins
selective estrogen receptor modulators
selective serotonin reuptake inhibitors
serotonin-norepinephrine reuptake inhibitors
serotoninergic neuroenteric modulators
sex hormone combinations
sex hormones
skeletal muscle relaxant combinations
skeletal muscle relaxants
smoking cessation agents
somatostatin and somatostatin analogs
spermicides
statins
sterile irrigating solutions
streptomyces derivatives
succinimide anticonvulsants
sulfonamides
sulfonylureas
synthetic ovulation stimulants
tetracyclic antidepressants
tetracyclines
therapeutic radiopharmaceuticals
thiazide diuretics
thiazolidinediones
thioxanthenes
third generation cephalosporins
thrombin inhibitors
thrombolytics
thyroid drugs
tocolytic agents
topical acne agents
topical agents
topical anesthetics
topical anti-infectives
topical antibiotics
topical antifungals
topical antihistamines
topical antipsoriatics
topical antivirals
topical astringents
topical debriding agents
topical depigmenting agents
topical emollients
topical keratolytics
topical steroids
topical steroids with anti-infectives
toxoids
triazine anticonvulsants
tricyclic antidepressants
trifunctional monoclonal antibodies
tumor necrosis factor (TNF) inhibitors
tyrosine kinase inhibitors
ultrasound contrast media
upper respiratory combinations
urea anticonvulsants
urinary anti-infectives
urinary antispasmodics
urinary pH modifiers
uterotonic agents
vaccine
vaccine combinations
vaginal anti-infectives
vaginal preparations
vasodilators
vasopressin antagonists
vasopressors
VEGF/VEGFR inhibitors
viral vaccines
viscosupplementation agents
vitamin and mineral combinations
vitamins
ACE (Angiotensin I converting enzyme)
Acid phosphatase
Activated clotting time
Activated protein C resistance
Adrenocorticotropic hormone (ACTH)
Alanine aminotransferase (ALT)
Alkaline phosphatase
Alkaline phosphatase (ALP)
Alpha1-antitrypsin
Ammonia levels
ANA (antinuclear antbodies)
ANA (antinuclear antibodies)
Angiotensin-converting enzyme (ACE)
Anticardiolipin antibody
Anticardiolipin antivbodies (ACA)
Anti-centromere antibody
Antidiuretic hormone
Anti-Gliadin antibody
Anti-glomerular basement membrane antibody
Anti-HBc (Hepatitis B core antibodies
Anti-HBs (Hepatitis B surface antibody
Antiphospholipid antibody
Anti-RNA polymerase
Anti-Smith (Sm) antibodies
Anti-Smooth Muscle antibody
Anti-Xa activity
Anti-Xa assay
Aspartate aminotransferase (AST)
Bilirubin, direct
Bilirubin, indirect
Bilirubin, total
Bleeding time
Blood gases (arterial)
Blood urea nitrogen (BUN)
BUN (blood urea nitrogen)
Calcium (ionized)
Carbon monoxide (CO)
Carcinoembryonic antigen (CEA)
CEA (carcinoembryonic antigen)
Clot lysis time
Clot retraction time
Cold agglutinins
Corticotrophin releasing hormone (CRH) stimulation test
Cortrosyn stimulation test
C-reactive protein
Creatinine kinase (CK)
DAT (Direct antiglobulin test)
Dexamethasone suppression test
Dilute Russell viper venom
Erythrocyte sedimentation rate (ESR)
Ethylene glycol
Euglobulin lysis
Factor VIII inhibitor
Factor VIII level
Fibrin split products
Folate (serum
Fractional excretion of sodium (FENA)
FSH (follicle stimulating factor)
Gamma glutamyl transferase (GGT)
GGTP (Gamma glutamyl transferase)
Growth hormone
HBeAg (Hepatitis Be antigen)
HBs-Ag (Hepatitis B surface antigen)
Helicobacter pylori
Hemoglobin electrophoresis
Hepatitis A antibodies
Hepatitis C antibodies
IAT (Indirect antiglobulin test)
Lactate dehydrogenase (LDH)
Lactic acid (lactate)
LH (Leutinizing hormone
Lupus anticoagulant
MCH (mean corpuscular hemoglobin
MCHC (mean corpuscular hemoglobin concentration)
MCV (mean corpuscular volume)
MPV (mean platelet volume)
Parathyroid hormone (PTH)
Platelets (plt)
Prostate specific antigen (PSA)
PSA (prostate specific antigen)
PT (Prothrombin time)
PTT (Partial thromboplastin time)
RDW (red cell distribution width)
Reticulocyte count
reticulocytes
Rheumatoid factor (RF)
Serum glutamic-pyruvic transaminase (SGPT
Serum protein electrophoresis (SPEP)
T3-resin uptake (T3RU)
Thrombin time
Thyroid stimulating hormone (TSH)
Total iron binding capacity (TIBC)
Total protein
Transferrin saturation
Uric acid
White blood cells (WBC)
Widal test
The apparatus and protocol generally as found in U.S. Pat. No. 7,985,188 were used for coating syringe barrel interiors with an SiOx barrier coating or layer, in some cases with minor variations. A similar apparatus and protocol were used for coating vials with an SiOx barrier coating or layer, in some cases with minor variations.
Protocol for Coating Syringe Barrel Interior with Primer Coating or Layer
Syringe barrels already interior coated with a barrier coating or layer of SiOx, as previously identified, are further interior coated with a primer coating or layer of SiOxCy as previously identified, generally following the protocols of U.S. Pat. No. 7,985,188 for applying the lubricity coating or layer, except with modified conditions in certain instances.
Convenient methods for measuring the breakout or initiation force required to initiate travel of a previously parked plunger in a syringe are described in Examples 11, 12, or 21 of U.S. Pat. No. 7,985,188, which are incorporated here by reference.
This protocol is used to determine the total amount of silicon coatings present on the entire vessel wall. A supply of 0.1 N potassium hydroxide (KOH) aqueous solution is prepared, taking care to avoid contact between the solution or ingredients and glass. The water used is purified water, 18 mΩ quality. A Perkin Elmer Optima Model 7300DV ICP-OES instrument is used for the measurement except as otherwise indicated.
Each device (vial, syringe, tube, or the like) to be tested and its cap and crimp (in the case of a vial) or other closure are weighed empty to 0.001 g, then filled completely with the KOH solution (with no headspace), capped, crimped, and reweighed to 0.001 g. In a digestion step, each vial is placed in an autoclave oven (liquid cycle) at 121° C. for 1 hour. The digestion step is carried out to quantitatively remove the silicon coatings from the vessel wall into the KOH solution. After this digestion step, the vials are removed from the autoclave oven and allowed to cool to room temperature. The contents of the vials are transferred into ICP tubes. The total Si concentration is run on each solution by ICP/OES following the operating procedure for the ICP/OES.
The total Si concentration is reported as parts per billion of Si in the KOH solution. This concentration represents the total amount of silicon coatings that were on the vessel wall before the digestion step was used to remove it.
The total Si concentration can also be determined for fewer than all the silicon layers on the vessel, as when an SiOx barrier layer is applied, an SiOxCy second layer (for example, a lubricity layer or a primer coating or layer) is then applied, and it is desired to know the total silicon concentration of just the SiOxCy layer. This determination is made by preparing two sets of vessels, one set to which only the SiOx layer is applied and the other set to which the same SiOx layer is applied, followed by the SiOxCy layer or other layers of interest. The total Si concentration for each set of vessels is determined in the same manner as described above. The difference between the two Si concentrations is the total Si concentration of the SiOxCy second layer.
In some of the working examples, the amount of silicon dissolved from the wall of the vessel by a test solution is determined, in parts per billion (ppb), for example to evaluate the dissolution rate of the test solution. This determination of dissolved silicon is made by storing the test solution in a vessel provided with an SiOx and/or SiOxCy coating or layer under test conditions, then removing a sample of the solution from the vessel and testing the Si concentration of the sample. The test is done in the same manner as the Protocol for Total Silicon Measurement, except that the digestion step of that protocol is replaced by storage of the test solution in the vessel as described in this protocol. The total Si concentration is reported as parts per billion of Si in the test solution
The average dissolution rates reported in the working examples are determined as follows. A series of test vessels having a known total total silicon measurement are filled with the desired test solution analogous to the manner of filling the vials with the KOH solution in the Protocol for Total Silicon Measurement. (The test solution can be a physiologically inactive test solution as employed in the present working examples or a physiologically active pharmaceutical preparation intended to be stored in the vessels to form a pharmaceutical package). The test solution is stored in respective vessels for several different amounts of time, then analyzed for the Si concentration in parts per billion in the test solution for each storage time. The respective storage times and Si concentrations are then plotted. The plots are studied to find a series of substantially linear points having the steepest slope.
The plot of dissolution amount (ppb Si) versus days decreases in slope with time, even though it does not appear that the Si layer has been fully digested by the test solution.
For the PC194 test data in Table 3, linear plots of dissolution versus time data are prepared by using a least squares linear regression program to find a linear plot corresponding to the first five data points of each of the experimental plots. The slope of each linear plot is then determined and reported as representing the average dissolution rate applicable to the test, measured in parts per billion of Si dissolved in the test solution per unit of time.
The calculated shelf life values reported in the working examples below are determined by extrapolation of the total silicon measurements and average dissolution rates, respectively determined as described in the Protocol for Total Silicon Measurement and the Protocol for Determining Average Dissolution Rate. The assumption is made that under the indicated storage conditions the SiOxCy primer coating or layer will be removed at the average dissolution rate until the coating is entirely removed. Thus, the total silicon measurement for the vessel, divided by the dissolution rate, gives the period of time required for the test solution to totally dissolve the SiOxCy coating. This period of time is reported as the calculated shelf life. Unlike commercial shelf life calculations, no safety factor is calculated. Instead, the calculated shelf life is the calculated time to failure.
It should be understood that because the plot of ppb Si versus hours decreases in slope with time, an extrapolation from relatively short measurement times to relatively long calculated shelf lives is believed to be a “worst case” test that tends to underestimate the calculated shelf life actually obtainable.
Syringe samples 1-3, employing three different primer coatings or layers, were produced under the following PECVD conditions:
Syringe 1 had a three-component primer coating or layer employing OMCTS, oxygen, and carrier gas. Syringe 2 had a two component primer coating or layer employing OMCTS and oxygen, but no carrier gas. Syringe 3 had a one-component primer coating or layer (OMCTS only). The primer coatings or layers produced according to these working examples are contemplated to function as protective coatings or layers to increase the shelf life of the vessels, compared to similar vessels provided with a barrier coating or layer but no primer coating or layer.
[03] HMDSO was used as the precursor in Examples 4-6. The results are shown in Table 1. The coatings produced according to these working examples are contemplated to function as primer coatings or layers, and also as protective coatings or layers to increase the shelf life of the vessels, compared to similar vessels provided with a barrier coating or layer but no primer coating or layer.
Silicon extractables from syringes were measured using ICP-MS analysis as described in the Protocol for Measuring Dissolved Silicon in a Vessel. The syringes were evaluated in both static and dynamic situations. The Protocol for Measuring Dissolved Silicon in a Vessel, modified as follows, describes the test procedure:
The extractable Silicon Levels from a silicone oil coated glass syringe and a protective coated and SiOx coated COC syringe are shown in Table 2. Precision of the ICP-MS total silicon measurement is +/−3%.
The Protocol for Measuring Dissolved Silicon in a Vessel is followed, except as modified here. Test solutions—50 mM buffer solutions at pH 3, 6, 7, 8, 9, and 12 are prepared. Buffers are selected having appropriate pKa values to provide the pH values being studied. A potassium phosphate buffer is selected for pH 3, 7, 8 and 12, a sodium citrate buffer is utilized for pH 6 and tris buffer is selected for pH 9. 3 ml of each test solution is placed in borosilicate glass 5 ml pharmaceutical vials and SiOxcoated 5 ml thermoplastic pharmaceutical vials. The vials are all closed with standard coated stoppers and crimped. The vials are placed in storage at 20-25° C. and pulled at various time points for inductively coupled plasma spectrometer (ICP) analysis of Si content in the solutions contained in the vials, in parts per billion (ppb) by weight, for different storage times.
The Protocol for Determining Average Dissolution Rate Si content is used to monitor the rate of glass dissolution, except as modified here. The data is plotted to determine an average rate of dissolution of borosilicate glass or SiOx coating at each pH condition.
The rate of Si dissolution in ppb is converted to a predicted thickness (nm) rate of Si dissolution by determining the total weight of Si removed, then using a surface area calculation of the amount of vial surface (11.65 cm2) exposed to the solution and a density of SiOx of 2.2 g/cm3. The predicted initial thickness of the SiOx coating required, based on the conditions and assumptions of this example (assuming a residual SiOx coating of at least 30 nm at the end of the desired shelf life of two years, and assuming storage at 20 to 25° C.) is about 36 nm at pH 5, about 80 nm at pH 6, about 230 nm at pH 7, about 400 nm at pH 7.5, about 750 nm at pH 8, and about 2600 nm at pH 9.
The coating thicknesses represent atypically harsh case scenarios for pharma and biotech products. Most biotech products and many pharma products are stored at refrigerated conditions and none are typically recommended for storage above room temperature. As a general rule of thumb, storage at a lower temperature reduces the thickness required, all other conditions being equivalent.
The following conclusions are reached, based on this test. First, the amount of dissolved Si in the SiOx coating or glass increases exponentially with increasing pH. Second, the SiOx coating dissolves more slowly than borosilicate glass at a pH lower than 8. The SiOx coating shows a linear, monophasic dissolution over time, whereas borosilicate glass tends to show a more rapid dissolution in the early hours of exposure to solutions, followed by a slower linear dissolution. This may be due to surface accumulation of some salts and elements on borosilicate during the forming process relative to the uniform composition of the SiOx coating. This result incidentally suggests the utility of an SiOx coating on the wall of a borosilicate glass vial to reduce dissolution of the glass at a pH lower than 8. Third, PECVD applied barrier coatings for vials in which pharmaceutical preparations are stored will need to be adapted to the specific pharmaceutical preparation and proposed storage conditions (or vice versa), at least in some instances in which the pharmaceutical preparation interacts with the barrier coating significantly.
An experiment is conducted with vessels coated with SiOx coating+OMCTS primer coating or layer, to test the primer coating or layer for its functionality as a protective coating or layer. The vessels are 5 mL vials (the vials are normally filled with product to 5 mL; their capacity without headspace, when capped, is about 7.5 mL) composed of cyclic olefin co-polymer (COC, Topas® 6013M-07).
Sixty vessels are coated on their interior surfaces with an SiOx coating produced in a plasma enhanced chemical vapor deposition (PECVD) process using a HMDSO precursor gas according to the Protocol for Coating Tube Interior with SiOx set forth above, except that equipment suitable for coating a vial is used. The following conditions are used.
Next the SiOx coated vials are coated over the SiOx with an SiOxCy coating produced in a PECVD process using an OMCTS precursor gas according to the Protocol for Coating COC Syringe Barrel Interior with OMCTS Lubricity Coating set forth above, except that the same coating equipment is used as for the SiOx coating. Thus, the special adaptations in the protocol for coating a syringe are not used. The following conditions are used.
Eight vials are selected and the total deposited quantity of PECVD coating (SiOx+SiOxCy) is determined with a Perkin Elmer Optima Model 7300DV ICP-OES instrument, using the Protocol for Total Silicon Measurement set forth above. This measurement determines the total amount of silicon in both coatings, and does not distinguish between the respective SiOx and SiOxCy coatings. The results are shown below.
In the following work, except as indicated otherwise in this example, the Protocol for Determining Average Dissolution Rate is followed. Two buffered pH test solutions are used in the remainder of the experiment, respectively at pH 4 and pH 8 to test the effect of pH on dissolution rate. Both test solutions are 50 mM buffers using potassium phosphate as the buffer, diluted in water for injection (WFI) (0.1 um sterilized, filtered). The pH is adjusted to pH 4 or 8, respectively, with concentrated nitric acid.
25 vials are filled with 7.5 ml per vial of pH 4 buffered test solution and 25 other vials are filled with 7.5 ml per vial of pH 4 buffered test solution (note the fill level is to the top of the vial—no head space). The vials are closed using prewashed butyl stoppers and aluminum crimps. The vials at each pH are split into two groups. One group at each pH containing 12 vials is stored at 4° C. and the second group of 13 vials is stored at 23° C.
The vials are sampled at Days 1, 3, 6, and 8. The Protocol for Measuring Dissolved Silicon in a Vessel is used, except as otherwise indicated in this example. The analytical result is reported on the basis of parts per billion of silicon in the buffered test solutions of each vial. A dissolution rate is calculated in terms of parts per billion per day as described above in the Protocol for Determining Average Dissolution Rate. The results at the respective storage temperatures follow:
The observations of Si dissolution versus time for the OMCTS-based coating at pH8 and pH 4 indicate the pH 4 rates are higher at ambient conditions. Thus, the pH 4 rates are used to determine how much material would need to be initially applied to leave a coating of adequate thickness at the end of the shelf life, taking account of the amount of the initial coating that would be dissolved. The results of this calculation are:
Based on this calculation, the OMCTS protective layer needs to be about 2.5 times thicker—resulting in dissolution of 33945 ppb versus the 14,371 ppb representing the entire mass of coating tested—to achieve a 3-year calculated shelf life.
The results of Comparative Example 8 and Example 9 above can be compared as follows, where the “primer coating or layer” is the coating of SiOxCy referred to in Example 9.
This data shows that the silicon dissolution rate of SiOx alone is reduced by more than 2 orders of magnitude at pH 8 in vials also coated with SiOxCy coatings.
Another comparison is shown by the data in Table 5 from several different experiments carried out under similar accelerated dissolution conditions.
Ta le 5, Row A (SiOx with OMCTS coating) versus C (SiOx without OMCTS coating) show that the OMCTS primer coating or layer is also an effective protective coating or layer to the SiOx coating at pH 8. The OMCTS coating reduced the one-day dissolution rate from 2504 ug/L (“u” or p or the Greek letter “mu” as used herein are identical, and are abbreviations for “micro”) to 165 ug/L. This data also shows that an HMDSO-based SiwOxCy (or its equivalent SiOxCy) overcoat (Row D) provided a far higher dissolution rate than an OMCTS-based SiwOxCy (or its equivalent SiOxCy) overcoat (Row A).
An experiment similar to Example 9 was carried out, modified as indicated in this example and in Table 3 (where the results are tabulated). 100 5 mL COP vials were made and coated with an SiOx barrier layer and an OMCTS-based primer coating or layer as described previously, except that for Sample PC194 only the primer coating or layer was applied. The coating quantity was again measured in parts per billion extracted from the surfaces of the vials to remove the entire primer coating or layer, as reported in Table 3.
In this example, several different coating dissolution conditions were employed. The test solutions used for dissolution contained either 0.02 or 0.2 wt. % polysorbate-80 surfactant, as well as a buffer to maintain a pH of 8. Dissolution tests were carried out at either 23° C. or 40° C.
Multiple syringes were filled with each test solution, stored at the indicated temperature, and analyzed at several intervals to determine the extraction profile and the amount of silicon extracted. An average dissolution rate for protracted storage times was then calculated by extrapolating the data obtained according to the Protocol for Determining Average Dissolution Rate. The results were calculated as described previously and are shown in Table 3. Of particular note, as shown on Table 3, were the very long calculated shelf lives of the filled packages provided with a PC 194 primer coating or layer:
Referring to Table 3, the longest calculated shelf lives corresponded with the use of an RF power level of 150 Watts and a corresponding high W/FM value. It is believed that the use of a higher power level causes higher cross-link density of the primer coating or layer.
A preliminary study was conducted to compare the relative amounts of free (i.e. readily removable) Dow Corning 360 Medical Fluid (PMDS non-reactive silicone fluid) on:
The SiOx barrier coatings were applied according to the Protocol for Coating Syringe Barrel Interior with SiOx. The OMCTS primer coating or layer was applied according to the Protocol for Coating Syringe Barrel Interior with OMCTS Primer Coating or Layer.
This study was carried out by applying a deposit of Dow Corning 360 Medical Fluid (having a viscosity of 350 CST) to the test vials
To carry out the preliminary study, the vials were filled with a 50 mM potassium phosphate solution of pH 8 with 0.2% Tween®-80. The filled vials were closed with a prewashed stopper and aluminum crimp and stored for up to 600 hours at a temperature of 40° C., then the solutions from the vials were tested for PMDS non-reactive silicone fluid content according to the Protocol for Determining Average Dissolution Rate.
This preliminary study showed that the OMCTS primer coating or layer prevented significant amounts of PMDS non-reactive silicone fluid from dissolving into a Tween solution, while significant amounts of PMDS non-reactive silicone fluid dissolved in solution from the borosilicate glass vials and SiOx barrier-coated COP vials. The OMCTS primer coating or layer appeared to have a great affinity for PMDS non-reactive silicone fluid, compared to the other substrates tested.
A more rigorous study similar to Example 12 is conducted, using as the substrates:
One set of each type of vial is provided with a deposit of PMDS non-reactive silicone fluid, except that, as indicated above, some of the test vials receiving the deposit of lubricant have not previously been coated with a primer coating or layer. A second set of each type of vial does not receive a deposit of lubricant and serves as controls.
The vials are filled with one of the following test solutions:
All vials with solution are incubated at 40° C. and samples pulled at the intervals shown in the table below for testing. The following tests are performed:
The study is expected to demonstrate that the application of a primer coating or layer as described in this specification improves the retention of the PMDS non-reactive silicone fluid on the vials.
The test purpose was to determine the contact angle or surface energy on the inside surface of two kinds of plastic vials and one kind of glass vial
The specimens that underwent testing and analysis reported here are three kinds of vials. The specimens are (A) an uncoated COP vial, (B) an SiOx+primer layer coated COP vial prepared according to the above Protocol for Coating Syringe Barrel Interior with SiOx, followed by the Protocol for Coating Syringe Barrel Interior with OMCTS Primer Coating or Layer, and (C) a glass vial. Small pieces were obtained by cutting the plastic vials or crushing the glass vial in order to test the inside surface.
The analysis instrument for the contact angle tests is the Contact Angle Meter model DM-701, made by Kyowa Interface Science Co., Ltd. (Tokyo, Japan). To obtain the contact angle, five water droplets were deposited on the inside surface of small pieces obtained from each specimen. The testing conditions and parameters are summarized below. Both plastic vials were cut and trimmed, while the glass vial needed to be crushed. The best representative pieces for each specimen were selected for testing. A dropsize of 1 μL (one microliter) was used for all samples. Due to the curvature of the specimens, a curvature correction routine was used to accurately measure the contact angle. The second table below contains the values for the radius of curvature used for each specimen.
The contact angle results for each specimen are provided in an accompanying table.
The COP plus primer coated specimen had the highest average contact angle of all tested specimens. The average contact angle for the COP plus primer coating or layer specimen was 99.1°. The average contact angle for the uncoated COP specimen was 90.5°. The glass specimen had a significantly lower average contact angle at 10.6°. This data shows the utility of the primer coating to raise the contact angle of the uncoated COP vessel. It is expected that an SiOx coated vessel without the primer coating or layer would exhibit a result similar to glass, which shows a hydrophilic coating relative to the primer coating or layer.
The purpose of this example was to evaluate the recoverability or drainage of a slightly viscous aqueous solution from glass, COP and coated vials,
This study evaluated the recovery of a 30 cps (centipoise) carbohydrate solution in water-for-injection from (A) an uncoated COP vial, (B) an SiOx+primer layer coated COP vial prepared according to the above Protocol for Coating Syringe Barrel Interior with SiOx, followed by the Protocol for Coating Syringe Barrel Interior with OMCTS Primer Coating or Layer, and (C) a glass vial.
2.0 ml of the carbohydrate solution was pipetted into 30 vials each of glass, COP and primer coated vials. The solution was aspirated from the vials with a 10 ml syringe, through a 23 gauge, 1.5″ needle. The vials were tipped to one side as the solution was aspirated to maximize the amount recovered. The same technique and similar withdrawal time was used for all vials. The vials were weighed empty, after placing 2.0 ml of the solution to the vial and at the conclusion of aspirating the solution from the vial. The amount delivered to the vial (A) was determined by subtracting the weight of the empty vial from the weight of the vial with the 2.0 ml of solution. The weight of solution not recovered (B) was determined by subtracting the weight of the empty vial from the weight of the vials after aspirating the solution from the vial. The percent unrecovered was determined by dividing B by A and multiplying by 100.
It was observed during the aspiration of drug product that the glass vials remained wetted with the solution. The COP vial repelled the liquid and as the solution was aspirated from the vials. This helped with recovery but droplets were observed to bead on the sidewalls of the vials during the aspiration. The primer coated vials also repelled the liquid during aspiration but no beading of solution on the sidewalls was observed.
The conclusion was that primer coated vials do not wet with aqueous solutions as do glass vials, leading to superior recovery of drug product relative to glass. Primer coated vials were not observed to cause beading of solution on sidewall during aspiration of aqueous products therefore coated vials performed better than uncoated COP vials in product recovery experiments.
Multiple syringe samples of each type defined below are plasma processed (except the comparative examples), lubricated with polydimethylsiloxane (PDMS), assembled and filled, and then tested for breakout force. The plasma treating processes and PECVD primer coating formulations used on the syringes tested in this example are among those defined by the parameters set out in Table 4 (employing HMDSO to deposit a PECVD coating, or no HMDSO to effect a plasma treatment without coating, or no HMDSO to effect a plasma treatment of the SiOxCy or SiNxCy coated surface), and the data obtained is presented in
The treatment conditions and data identified as “421-48 COP” relate to plastic syringe samples composed of cyclic olefin polymer (COP) that has not been plasma treated (Comparative example).
The treatment conditions and data identified as “EO-4 bilayer” relate to plastic syringe samples composed of cyclic olefin polymer. A bi-layer coating (an SiOx barrier coating or layer, followed by an SiOxCy pH protective coating or layer) is applied to the interior surface of the syringe using a PECVD process. The top (pH protective) layer is hydrophobic. After PDMS is applied onto the top layer the syringe is treated with ethylene oxide (sterilization).
The treatment conditions and data identified as “EO-1 SiOx” relate to plastic syringe samples composed of cyclic olefin polymer. A SiOx coating is applied to the interior surface of the syringe using a PECVD process. The SiOx layer is hydrophilic. PDMS is applied on to the SiOx layer. The syringe has been treated with ethylene oxide (sterilization).
The treatment conditions and data identified as “BD” relate to a glass syringe commercially available from Becton, Dickinson and Company or a related company, which is coated by the supplier with 1000 cst PDMS (Comparative example).
The treatment conditions and data identified as “Schott” relate to a glass syringe commercially available from Schott AG or a related company, which is coated by the supplier with 1000 cst PDMS (Comparative example).
The barrel interior of each of the above-listed samples except the glass syringes is coated with approximately 1 mg of PDMS (Dow 360 Medical Fluid, 1,000 cst) using an IVEK Multispense 2000 coater under the following conditions:
The syringe barrels are then assembled with Grey Stelmi plunger tips, which are parked in the syringe for the amount of time indicated in
The results of this testing are shown in
The following guide is provided to assist interpretation of the test results represented in
As
The bilayer syringe samples represented by the data points 652 of
The SiOx barrier coated syringe samples represented by the data points 654 of
Example 17 is carried out comparably to Example 16, except that in addition to the above types of samples, all represented by data points having the same reference numbers in
The working examples thus show several different types of plasma treatments, with and without deposition of a PECVD coating, improving the breakout force and the rate of increase of breakout force with park time in a molded plastic syringe.
These working examples compare the effects of aging lubricated 1 mL syringe barrels on their lubricity properties: breakout or initial force, Fi, and maintenance force, Fm, with dry storage at room temperature (RT) and wet storage at 40° C. Wet storage is defined as filling the syringe with 0.8 mL of water balanced to pH 8 and containing 0.2% Tween® 80 surfactant. Dry storage is of the unfilled syringe barrel.
Referring to
Still referring to
The bilayer and trilayer syringe barrels were evaluated with barrel inner diameters (ID) of 6.35 and 6.50 mm. The barrel inner diameters were measured at the midpoint between the front walls of the syringe barrels bearing the needle and the rear flange and opening of the syringe barrel, as is conventional.
For low-viscosity trials, the bilayer syringe barrels and trilayer syringe barrels were coated with 1 mg per syringe barrel of 1,000 centistoke (cSt) polydimethylsiloxane (PDMS). For high-viscosity trials, the bilayer and trilayer syringe barrels were coated with 1 mg of 12,500 cSt PDMS. The PDMS coatings are shown as 287 in
To apply the polydimethylsiloxane (PDMS) or silicone oil to the syringe barrels, the PDMS was sent through an IVEK 40 Point Linear Actuator that can dispense the PDMS at a specific rate and volume. For this experiment, the actuator was set to dispense a volume of 1.75 μL at a rate of 1.00 μL/min. Pressurized air is then mixed with the PDMS to aerosolize and spray it into the inside of the syringe. The syringe barrels were set aside for 8 days to allow the PDMS time to evenly disperse throughout the syringe and cure. The 1,000 cSt and 12,500 cSt PDMS materials used for this experiment were each 360 Dow Corning Medical Fluid. Due to the high viscosity of 12,500 cSt PDMS, the pressurized air was heated to 205° F., and the PDMS was heated to 250° F. before they were combined.
Commercial PDMS-coated BD Hypak® glass syringe barrels with 6.35 mm ID served as a benchmark under both storage conditions. These BD syringe barrels were coated with about 0.4 mg of 1000 cSt PDMS.
Except as otherwise indicated, 6.7 mm nominal diameter Stelmi plunger tips were inserted in the syringe barrels. The plunger depth was set to 15 mm from the bottom of the flange to the tip of the plunger, using a molded puck for consistent manual loading with a plunger rod. Each group contained 30 syringe barrels for five time data points after plunger insertion (3 hours, 1 day, 3 days, 7 days, 21 days), with 6 syringe barrels per time point. Syringe barrels were tested at each time point, except as noted.
Many of the sets of data points were extrapolated to a storage time of two years (740 days). Various combinations of data sets were plotted, and are presented as
For convenient reference, Table 6 shows all the types of syringe barrels tested and identifies the test conditions and corresponding data points in
Plunger Initiation Force, Fi, and Plunger Maintenance Force, Fm, were analyzed by the linear regression of log (Fl) vs. log (time), and a two year estimate was generated by extrapolation of this regression. The upper and lower prediction limits (UPL and LPL) of this two year estimate were calculated by a 100(1−α) % Prediction Interval using the t-distribution, with a 95% confidence interval. All error bars in
Next, SiOx bilayer syringe barrels with 1 mg PDMS (1,000 cSt) and a larger (6.50 mm) barrel ID were tested, as shown in
A larger barrel ID decreases compression on the plunger tip, which reduces the friction forces between the plunger and the barrel wall.
Based on this data, the use of 1000 cSt PDMS on 6.50 mm ID COP trilayer syringe barrels with a thin SiO2 layer deposited on the standard tri-layer coating is contemplated to be useful to deliver lubrication performance equal to the benchmark BD glass syringe. The SiOx bilayer 6.50 mm syringe barrels show Fi performance equivalent to the BD 6.35 mm syringe in both wet and dry conditions. The SiOx bilayer 6.50 mm syringe shows Fm,max approaching that of the BD 6.35 mm syringe in dry and wet conditions.
The Fi at the time of plunger insertion observed for 12,500 cSt PDMS coated on the SiOx bilayer 6.35 mm syringe barrels is greater than that observed with 1,000 PDMS coated on equivalent syringe barrels, for both dry and wet storage. However, the increase in Fi over time, under both storage conditions, with 12,500 cSt PDMS is slower than that of 1,000 cSt PDMS. The extrapolations suggest the 12,500 cSt PDMS lubricant will have lower Fi at long storage times.
In
12,500 cSt PDMS also has other advantages as a lubricant for syringes. It is less mobile when applied to the syringe barrel, and is believed to provide fewer sub-visible PDMS emulsion particles than 1,000 Cstk PDMS.
Referring to
This data shows that increasing the syringe ID to reduce initiation and sliding forces when dispensing from the syringe increases the failure rate resulting from loss of container closure integrity. This data shows that a plunger 0.2 mm larger than the Barrel ID provided a 3% failure rate in container closure integrity of the COP trilayer syringe barrel, while a plunger 0.1 mm larger than the Barrel ID provided a 100% failure rate with the same barrel.
Finally, the solution of increasing the barrel ID, used in this data to improve the initiation and maintenance forces of COP syringe barrels, is not as practical for improving a glass syringe barrel because the barrel ID tolerance of a glass syringe barrel is much greater than the barrel ID tolerance of an injection molded COP barrel, due to the different manufacturing methods used for glass vs. injection molded resin. For example, each member of a lot of 25 COP syringe barrels, nominally 0.2544 inch (6.462 mm) ID, was found to have a standard deviation of 0.0002 inch (0.005 mm), while a lot of BD Hypak® glass syringe barrels, nominally 0.2506 inch (6.365 mm) ID, had a standard deviation of 0.0012 inch (0.03 mm)—six times as great as for the COP syringe barrels. This larger statistical deviation of the glass syringe barrels means that glass outliers having the greatest ID are much more likely to cross the threshold of breakdown of CCI than COP outliers in a lot having the same nominal diameter.
To summarize this experimentation:
COP trilayer syringes with PDMS performed better during chemical aging than a BD glass syringe with PDMS (see
COP trilayer syringes with PDMS aged in a wet environment showed a slower increase in Fi over time than a BD syringe PDMS on glass.
Increasing the COP syringe barrel ID from 6.35 mm to 6.50 reduced the Fi/Fm with PDMS, for both bilayer and trilayer syringe barrels. A plastic, injection molded syringe has better dimensional tolerances than a glass syringe. Better dimensional tolerances mean that the nominal syringe ID can be increased from 6.35 mm (used in glass syringes) to 6.50 mm (for COP syringes) without degrading the seal integrity between the plunger and the syringe barrel.
COP bilayer 6.50 mm ID syringe barrels with PDMS had similar Fi/Fm characteristics to BD Hypak® glass syringe barrels using PDMS on glass.
Employing 12,500 Cstk PDMS, having a higher viscosity and molecular weight compared with 1,000 Cstk. PDMS, has several advantages. The comparative studies with 12,500 and 1,000 Cstk PDMS with COP and SiO2 coated COP syringes show that the rate of increase in force over time (aging) is slower with 12,500 Cstk PDMS. Thus, the magnitude of forces Fi/Fm is higher with 12,500 than 1,000 Cstk PDMS at early times, but the relative magnitude reverses at long storage times after plunger insertion
This application claims the priority of U.S. Provisional Appl. 61/771,644, filed Mar. 1, 2013, all of which is incorporated by reference here to provide continuity of disclosure. U.S. Provisional Ser. No. 61/177,984 filed May 13, 2009; 61/222,727, filed Jul. 2, 2009; 61/213,904, filed Jul. 24, 2009; 61/234,505, filed Aug. 17, 2009; 61/261,321, filed Nov. 14, 2009; 61/263,289, filed Nov. 20, 2009; 61/285,813, filed Dec. 11, 2009; 61/298,159, filed Jan. 25, 2010; 61/299,888, filed Jan. 29, 2010; 61/318,197, filed Mar. 26, 2010; 61/333,625, filed May 11, 2010; 61/413,334, filed Nov. 12, 2010; 61/636,377, filed Apr. 20, 2012; 61/654,612, filed Jun. 1, 2012; Ser. No. 12/779,007, filed May 12, 2010, now U.S. Pat. No. 7,985,188; International Application PCT/US11/36097, filed May 11, 2011; and U.S. Ser. No. 61/558,885, filed Nov. 11, 2011; are all incorporated here by reference in their entirety. Also incorporated by reference in their entirety are the following European patent applications: EP10162755.2 filed May 12, 2010; EP10162760.2 filed May 12, 2010; EP10162756.0 filed May 12, 2010; EP10162758.6 filed May 12, 2010; EP10162761.0 filed May 12, 2010; and EP10162757.8 filed May 12, 2010. These European patent applications describe apparatus, vessels, precursors, coatings or layers and methods (in particular coating methods and test methods for examining the coatings or layers) which can generally be used in performing the present invention, unless stated otherwise herein. They also describe SiOx barrier coatings or layers to which reference is made herein.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US2014/019684 | 2/28/2014 | WO | 00 |
| Number | Date | Country | |
|---|---|---|---|
| 61771644 | Mar 2013 | US |
