Patent Application
20150141918
This invention relates to a medical device, and in particular to a syringe for delivering a dose of medicament.
Automatically actuatable syringes are known and include a power source, such as a spring or a compressed gas to deliver a dose of medicament to a patient. Typically, a syringe has a barrel defining a chamber for containing a dose of medicament and a moveable stopper connected to a plunger rod for compressing the medicament to force it out of an opening in the barrel. In more complex devices, additional features are provided that are actuated in a sequence determined by the axial position of the plunger rod or the drive spring, for example. In such devices, the axial position of the plunger rod or the like is indicative of the stage of medicament delivery. Examples of such features include movement of the needle out of or into the device, and movement of a needle shroud between a needle-protecting and a needle-exposing position.
A self-contained pressurized injection device used for administering very viscous dermal filler material is described in WO-A-2009/086250 (Aesthetic Sciences Corporation). The described device includes an actuator assembly having a pressurized fluid container, a regulator and a bias member. The pressurized fluid container is configured to move between a first closed position and a second open position to selectively activate the device. The bias member biases the pressurized fluid container towards the first closed position.
It is an object of the present invention to provide a syringe device that is propellable by propellant that boils at a predetermined temperature that provides improved reliability and control in comparison to the prior art.
It is another object of the present invention to provide a syringe device that is propellable by propellant that boils at a predetermined temperature that may be used in a sequenced autoinjector device.
In accordance with a first aspect of the present invention there is provided a syringe propellable by propellant that boils at a predetermined temperature, the syringe comprising:
wherein the stopper defines and separates a first chamber and a second chamber, the first chamber being axially forwards of the stopper and being configured for containing a medicament, and the second chamber being axially rearwards of the stopper and being configured to receive propellant for acting on the stopper to move the stopper axially forwardly in the barrel to expel medicament through the outlet upon actuation of the syringe;
the syringe further comprising a rupturing portion and a third chamber for containing propellant where the third chamber is rupturable;
wherein the rupturing portion is configured to rupture the third chamber upon actuation of the syringe to fluidly connect the third chamber to the second chamber so that propellant is released into the second chamber and the pressure in the second chamber increases at or above the predetermined temperature causing the stopper to move axially forwardly and begin to expel medicament from the first chamber through the outlet.
The third chamber may have a rupturable portion, and the rupturable portion may form a propellant channel between the third chamber and second chamber when the rupturable portion is ruptured. Optionally, the propellant channel is defined by a propellant conduit that determines the flow rate of propellant from the third chamber to the second chamber. The propellant conduit may extend into the third chamber so as to minimise the flow of liquid propellant from the third chamber to the second chamber, in some preferable embodiments by at least 0.3 mm.
Optionally, the syringe further comprises a fourth chamber in fluid communication with the second chamber, where the third chamber is fluidly connectable to the fourth chamber upon rupturing. The third chamber may be entirely within the fourth chamber. The fourth chamber may be fluidly connected to the second chamber by a propellant conduit that determines the flow rate of propellant from the fourth chamber to the second chamber. The propellant conduit may extend into the fourth chamber so as to substantially prevent the flow of liquid propellant from the fourth chamber to the second chamber. Preferably, the propellant conduit extends into the fourth chamber by at least 0.3 mm.
In some preferable embodiments, the third chamber comprises a flexible rupturable container for containing propellant. The flexible rupturable container may be sealed by one or more seals, wherein the one or more seals are preferably formed between two like materials. The one or more seals may be formed by heat sealing, sonic welding, or adhesives. The flexible container is preferably formed from a material that is substantially impermeable to the propellant. The material preferably has a gas permeability of less than 0.365 g/(m2.day) where the propellant used is HFA 134a. In some preferable embodiments, the material includes polyethylene. Additionally or alternatively, the material includes a polyamide, where preferably the material includes nylon. The material may consist substantially of nylon. The material may include a cyclic olefin copolymer (COC). The material may include a cyclic olefin polymer (COP). The material may comprise a laminate of polyethylene and a polyamide. The material may comprise a laminate of polyethylene and a metal. The metal may be a metallic foil.
Optionally, the syringe further comprises trigger means for triggering an action upon activation of the trigger means, wherein the trigger means are activated when the pressure in the second chamber satisfies a predetermined condition.
The predetermined temperature may be ambient temperature. Alternatively, the predetermined temperature may be any temperature between 15° C. and 30° C. Specifically, the temperature is between 20° C. and 25° C.
In some preferable embodiments, the predetermined temperature is greater than ambient temperature.
In accordance with a second aspect of the present invention, there is provided a syringe propellable by propellant that boils at a predetermined temperature, the syringe comprising:
The syringe may further comprise a needle shield moveable between a first position in which the needle is exposed and a second position in which the needle is substantially covered by the needle shield such that the needle shield is not exposed, wherein the action includes the movement of the needle shield between the first position and the second position.
The syringe may form part of an autoinjector device in which the syringe is moveable relative to a housing of the autoinjector device between a first position in which the needle is within the housing and is not exposed and a second position in which the needle extends out of the housing, and wherein the action includes movement of the syringe between the first position and the second position.
The syringe may have one or more indicators for signalling to the user that an injection sequence is at a particular stage, and wherein the action includes activating the one or more indicators to produce the signal. The one or more indicators may include a visual indicator, which may be an LED. The one or more indicators may include an audible indicator, which may be a speaker. The one or more indicators may signal the end of delivery of medicament. The one or more indicators may signal that a predetermined time period has elapsed since the end of delivery of medicament. The predetermined condition may be exceeding a predetermined pressure. The predetermined condition may be exceeding the predetermined pressure after a predetermined time period has elapsed or subsequent to a prior predetermined condition being satisfied. The predetermined condition may be falling below a predetermined pressure. The predetermined condition may be falling below the predetermined pressure after a predetermined time period has elapsed or subsequent to a prior predetermined condition being satisfied. The predetermined temperature may be ambient temperature. The predetermined temperature may be any temperature between 15° C. and 30° C. More specifically, the temperature may be between 20° C. and 25° C. The predetermined temperature may be greater than ambient temperature.
Optionally, the syringe further comprises a dispenser for providing propellant to the second chamber, wherein the dispenser is moveable from a closed position in which propellant cannot exit the dispenser to an open position in which a predetermined volume of propellant can exit the dispenser. The dispenser may have a capacity for containing propellant, and the predetermined volume is less than the capacity. The capacity may be defined by a first internal volume of the dispenser, and the predetermined volume is defined by a second internal volume of the dispenser, and wherein in the closed position, the first internal volume is fluidly connected to the second internal volume so as to allow propellant to fill the second internal volume, and in the open position, the first internal volume is not fluidly connected to the second internal volume and the second internal volume is fluidly connected to the second chamber so as to allow the predetermined volume of propellant to be provided to the second chamber.
Optionally, when propellant is released into the second chamber the pressure in the second chamber increases over a first time period to a first pressure causing the stopper to move axially forwardly to begin expulsion of medicament from the first chamber through the outlet;
wherein the syringe is configured such that while the medicament is expelled from the first chamber the pressure in the second chamber changes over a second time period from the first pressure to a second pressure, and
when substantially all the medicament has been expelled from the first chamber the pressure in the second chamber increases over a third time period towards a third pressure, and
wherein the magnitude of the second pressure and the rate of increase of the pressure in the second chamber during the third time period are controlled by the thermal conductivity of the components of the syringe and defining the second chamber, the rate of delivery of propellant to the second chamber, and the phase of the propellant during delivery into the second chamber.
The first time period may be less than 1.0 second. The second time period may be less than 15 seconds. The first pressure may be more than 0.1 bar. The first pressure may be more than 2 bar. The first pressure may be less than 15 bar.
Optionally, one or both of the first pressure and the third pressure is substantially equal to the vapor pressure of the propellant at ambient temperature at the instantaneous volume of the vaporised propellant.
The second pressure may be less than 99% of the first pressure. The second pressure may be greater than 50% of the first pressure. The difference between the first pressure and the second pressure may be more than 0.1 bar.
Optionally, the syringe further comprises cooling means or heating means configured to supply or remove heat to propellant in the second chamber, respectively. The cooling means may comprise a refrigerant channel for receiving refrigerant, the channel being disposed proximate the barrel to permit the removal of heat from the barrel by refrigerant. The refrigerant channel may be configured to permit travel of refrigerant along the barrel from a rear end of the barrel towards the front end of the barrel. The refrigerant channel may be configured to permit application of refrigerant to an injection site after travelling from the rear end of the barrel towards the front end of the barrel along the channel.
Optionally, the third chamber is arranged to supply propellant to the refrigerant channel, where the supplied propellant is the refrigerant.
The cooling or heating means may include a thermal transfer component arranged in the second chamber and having a specific heat capacity such that the thermal transfer component removes heat or supplies heat to propellant in the second chamber, following actuation of the syringe. The thermal transfer component may comprise a metal.
The cooling means may include an insulation component arranged to insulate the barrel from the environment, thereby reducing heat transfer from the environment to the barrel.
Optionally, the syringe further comprises a fluid propellant in the third chamber. The fluid propellant may be configured to enter the second chamber primarily as a liquid. The fluid propellant may be configured to enter the second chamber primarily as a gas. The fluid propellant may include a hydrofluoroalkane (HFA), wherein the HFA may be HFA 134a, HFA 422d, HFA 123, HFA 245fa, or HFA 507c.
The propellant source of the third aspect of the present invention may be any suitable propellant source, including any described in the present application, and particularly including any described in relation to the first aspect of the present invention (i.e. the third chamber and optional fourth chamber arrangements).
In accordance with a third aspect of the present invention, there is provided a container comprising a chamber containing a propellant that boils at a predetermined temperature, and one or more seals sealing the chamber, wherein the container is formed of a flexible rupturable material substantially impermeable to the propellant and the one or more seals are formed between two like materials.
The one or more seals may be formed by heat sealing, sonic welding, or adhesives. The material may have a gas permeability of 0.365 g/(m2.day). The material may include polyethylene. The material may include a polyamide, and may include or consist substantially of nylon. The material may comprise a laminate of polyethylene and a polyamide. The material may comprise a laminate of polyethylene and a metal, wherein the metal may be a metallic foil.
The container may be formed from two sheets of the material, wherein the chamber is defined by an area where the two sheets are not bonded to one another and the one or more seals are defined by one or more areas where the two sheets are bonded to one another.
The container may be formed from a substantially cylindrical piece of the material initially having two open ends, wherein the two open ends are pinched closed to form two sealed ends.
The propellant may include a hydrofluoroalkane (HFA), wherein the HFA may be HFA 134a, HFA 422d, HFA 123, HFA 245fa, or HFA 507c.
Preferably, the container is a power source for actuating the syringe.
In accordance with a fourth aspect of the present invention, there is provided a method of manufacturing a container containing propellant comprising the steps of:
The method may further comprise the step of cutting the tube through the second upper seal to form the container. The method may further comprise the step of cutting the tube through the lower seal to form the container. Step iv) may be performed prior to performing step iii)
The step of depositing propellant in the internal volume through the opening may comprise bringing a propellant dispenser into fluid communication with the opening and where the propellant dispenser forms a sealing arrangement around the opening.
The tube of rupturable material may be an extruded tube, where optionally, at least steps i) to vi) are performed when the extruded tube has not been cut from the extrusion line.
The first upper seal may become the lower seal of a tube extending above thereof such that the method may be repeated for the tube extending above thereof.
Any or each of the lower seal, the first upper seal and the second upper seal may be a heat seal, a sonic weld, or an adhesive seal.
The step of forming an opening in the tube preferably produces substantially no loose material.
In accordance with a fifth aspect of the present invention, there is provided a method of manufacturing a container containing propellant comprising the steps of:
Optionally, the first and second sheets move relative to the propellant dispensing apparatus so that the upper seal of the container becomes a lower seal of a subsequent container, where steps i) to iv) are repeated to form the subsequent container.
Rollers may be provided to move the first and second sheets relative to the propellant dispensing apparatus, the rollers bringing the first sheet and the second sheet together along their respective edges for formation of the two side seals. The rollers may be configured to also form the two side seals. Two pairs of separate rollers may be provided.
The lower seal and the upper seal may be severed to form a discrete container. Any or each of the lower seal, the upper seal and the two side seals is a heat seal, a sonic weld, or an adhesive seal.
In accordance with a sixth aspect of the present invention, there is provided a method of designing a syringe, the syringe comprising:
The step of selecting the thermal properties of the syringe to exhibit the desired pressure profile of fluid acting on the stopper following actuation of the syringe may be performed by a computer implemented calculation.
The method may further comprise the step of manufacturing a syringe having the determined thermal properties required to exhibit the desired pressure profile of fluid acting on the stopper following actuation of the syringe.
The step of selecting the thermal properties of the syringe to exhibit the desired pressure profile of fluid acting on the stopper following actuation of the syringe may comprise the steps of:
The step of modifying the design of the syringe to alter the heat transfer to fluid propellant in the barrel following actuation of the syringe may comprise providing cooling means in the syringe design, the cooling means being configured to reduce heat transfer to the fluid propellant in the barrel following actuation of the modified syringe.
The step of modifying the design of the syringe to alter the heat transfer to fluid propellant in the barrel following actuation of the syringe may comprise providing heating means in the syringe design, the heating means being configured to increase heat transfer to the fluid propellant in the barrel following actuation of the modified syringe.
The step of modifying the design of the syringe to alter the heat transfer to fluid propellant in the barrel following actuation of the syringe may comprise providing thermal insulation means in the syringe design, the thermal insulation means being configured to reduce heat transfer to the fluid propellant in the barrel following actuation of the modified syringe.
The step of modifying the design of the syringe to alter the heat transfer to fluid propellant in the barrel following actuation of the syringe may comprise providing thermal conductive means in the syringe design, the thermal conductive means being configured to increase heat transfer to the fluid propellant in the barrel following actuation of the modified syringe.
The steps of determining a first pressure profile and a second pressure profile may each comprise a measurement of pressure. The step of determining a first pressure profile may comprise a calculation. The step of determining a second pressure profile may comprise a calculation. The or each calculation may be a computer implemented calculation. The step of modifying the design of the syringe may be a computer implemented step.
The method may further comprise the step of manufacturing a syringe according to the design of the modified syringe that had a second pressure profile approximately equal to the desired pressure profile as determined by the method of any preceding claim.
The step of determining the rate of delivery of propellant into the second chamber may comprise forming a restriction that restrict the flow of propellant into the second chamber by a desired amount.
The step of determining the phase of propellant entering the second chamber may comprise providing a formation that limits or prevents liquid propellant from entering the second chamber, but permits gaseous propellant to enter the second chamber.
All non-mutually exclusive combinations of features disclosed in the present application are within the scope of the present invention.
Embodiments of the invention are further described hereinafter with reference to the accompanying drawings, in which:
A syringe 10 according to an embodiment of the present invention is shown in
The syringe 10 additionally has a rupturing portion (not shown) configured to rupture the rupturable wall 24 to irreversibly fluidly connect the third chamber 22 and the second chamber 20 so that propellant enters the second chamber 20. That is, the rupturable wall 24 is frangible or breakable such that once it has been broken or opened, it cannot be reclosed or resealed without additional means for doing such. The rupturable wall 24 is preferably flexible at least in part so that the shape of the container 21 is changeable.
Within the scope of the present invention, once a fluid connection is established between the third chamber 22 and the second chamber 20, the fluid connection is maintained and not closed or sealed. This is necessary for the desired thermodynamic properties of the syringe 10 in accordance with the present invention, as is described in more detail below. Depending on the nature of the third chamber 22, the rupturing portion may be a needle or other suitable element configured to slice, rupture, break, pierce or otherwise create an opening in the rupturable wall 24 (or, in other embodiments, a similar rupturable element defining at least a part of the third chamber 22) and establish a fluid connection between the third chamber 22 and the second chamber 20. In the case where the rupturing portion is a needle or similar piercing element, it is preferable that it is either hooked, or hollow in configuration or otherwise shaped so that upon rupturing, breaking, or piercing the rupturable wall 24, the rupturing portion itself does not entirely block the newly formed fluid passageway between the third chamber 22 and the second chamber 20. In the case where the rupturing portion has a hollow configuration, the propellant may flow through the hollow portion from the third chamber 22 to the second chamber 20. In other embodiments, the rupturing portion may comprise apparatus for rupturing the rupturable wall 24 by a bursting mechanism. That is, the rupturing portion acts to exert a force on the container 21 so that that the pressure in the third chamber 22 increases so that the rupturable wall 24 is caused to rupture, thereby establishing a fluid connection between the third chamber 22 and the second chamber 20. In some embodiments, the rupturing portion may be moved towards the third chamber 22 to rupture the third chamber 22. In other embodiments, the third chamber 22 may be moved towards the rupturing portion to cause rupturing of the third chamber 22.
The rupturing portion 510 may be shaped (e.g. the shape of the base 514) so that multiple rupturing portions can be arranged in close proximity to act on the same rupturable wall. As an example,
Other non-conical but tapered elements may be used to form the rupturing portion of the present invention. In such cases, it is still preferable for the tapered element to include a cut-out portion to improve fluid flow and minimize the risk of the rupturing element sealing newly created hole in the rupturable wall. Additionally or alternatively, it is preferable for the rupturing portion to include a through-bore for channeling fluid from the third chamber 22 to the second chamber 20.
The propellant is one that boils at a predetermined temperature which in all cases must be below the local operating temperature of the system during use. A particularly preferable propellant is or includes a hydrofluoroalkane (HFA) as this provides a suitable pressure for use with aqueous solution in a fine bore needle syringe. HFA 134a boils at −26.4° C. which is able to provide sufficient pressure even when the medicament that is to be delivered is chilled. In other embodiments a propellant may have a lower boiling point which provides an increased pressure is use, which is especially useful for the delivery of highly viscous drugs. For example HFA 422d has a boiling point between −46.2° C. and −41.5° C. Similarly, HFA 507c has a boiling point of −46.9° C. In alternative embodiments, the propellant may boil at a higher temperature such that it cannot generate sufficient pressure to drive the medicament without additional energy from an external source such as the patient or another heat source. For example HFA 123 boils at +27.9° C. Similarly, HFA 245fa has a boiling point of +15.3° C.
When the third chamber 22 is in fluid communication with the second chamber 20, propellant is released into the second chamber 20. At the predetermined temperature, the propellant released into the second chamber 20 is initially in its liquid phase. Additionally or alternatively, some of the propellant may be initially in its liquid phase due to the confines of the volume in which it resides, even if the propellant is at a temperature above the predetermined temperature.
Some of this liquid propellant will evaporate due to the heat that the propellant is exposed to (e.g. ambient heat), thereby providing gas phase propellant to the second chamber 20. Since the vaporization of propellant requires the absorption of latent heat from the liquid propellant, the process of evaporation cools the remaining liquid propellant. This cooling results in the vapor pressure immediately above the liquid propellant being lower than it is at its initial starting (i.e. ambient) temperature. Nevertheless, the pressure in the second chamber 20 begins to increase enough so that the stopper 16 moves axially forwardly in the barrel 12, thereby reducing the volume of the first chamber 18 and pressurizing the medicament held therein. The pressurized medicament exits the barrel 12 through the outlet 14, which may be fluidly connected to a needle or other applicator, for entry into an injection site such as subcutaneous tissue.
In the case where a propellant is used that boils at a temperature higher than ambient temperature, the ambient temperature will not be sufficient to boil the propellant and thus the stopper 16 will not move as a consequence. In these embodiments, an additional heat source must be provided to boil the propellant and begin movement of the stopper 16. For example, the heat source could be the user's hand which will be at “body temperature” (approximately 37° C.). This arrangement may reduce the risk of accidental delivery of medicament if the propellant is inadvertently in fluid communication with the second chamber 20.
As the stopper 16 moves axially forwards towards the outlet 14 to reduce the volume of the first chamber 18, the second chamber 20 is made larger. Thus, additional volume is continuously created in the second chamber 20 into which the propellant can evaporate into. This further vaporization causes further cooling of the remaining liquid propellant and thus further reduces the observed vapor pressure in the second chamber 20.
However, the system is not completely adiabatic (nor is it isothermal) so thermal energy is absorbed by the liquid propellant from its immediate environment (e.g. the barrel 12) to counter the reduction in temperature of the liquid propellant and the reduction in vapor pressure in the second chamber 20. Indeed, in the absence of this heat absorption, the propellant would freeze as the temperature of the liquid propellant continues to drop, and the syringe 10 would cease to operate correctly. This drop in vapor pressure in the second chamber 20 is exhibited throughout delivery of the medicament from the first chamber 18. In particular, since the stopper 16 is moving, the propellant in the second chamber 20 is continuously exposed to “new” sections of the inside of the barrel 12. Since the “new” sections of the inside of the barrel have not previously been in contact with the propellant, its thermal energy will initially be substantially at or near to ambient temperature or a higher temperature if additional heating means are present (unlike the sections of the barrel 12 axially rearward thereof which have already given up thermal energy to the liquid propellant). The “new” sections of barrel that the propellant is exposed to during delivery therefore act as a fresh heat source which is able to provide thermal energy to the propellant in the second chamber 20.
The stopper 16 continues to move axially forwardly in the barrel 12 until it reaches the forwardmost end of the barrel 12 where further forward axial movement is not possible. At this point, the full dose of medicament in the first chamber 18 has been delivered and the first chamber 18 has been reduced to its smallest volume (i.e. at or near substantially zero, depending on the formation of the front end of the barrel 12). With no further movement of the stopper 16, the temperature of the gas phase propellant, and any remaining liquid propellant, begins to increase as thermal energy is absorbed from the environment. Since, with the stopper 16 stationary in the barrel 12, the second chamber 20 has a constant volume, the increase in temperature of the propellant results in an increase in vapor pressure in the second chamber 20. This increase in vapor pressure tends towards the vapor pressure of the propellant at the temperature of its immediate environment (e.g. ambient temperature or a higher temperature if additional heating means are still present at this point). Indeed, the vapor pressure in the second chamber 20 will reach the vapor pressure of the propellant at the temperature of its immediate environment given long enough as equilibrium is reached.
The magnitude of the drop in vapor pressure in the second chamber 20 during delivery from the initial vapor pressure maximum when the propellant is released into the second chamber 20 to when the stopper 16 has reached the front end of the barrel 12 depends on any one or more of i) the thermal properties of the syringe 10, ii) the rate of delivery of propellant into the second chamber 20, and iii) the phase of the propellant entering the second chamber 20 (as will be described in more detail below). With regards to the effects of the thermal properties of the syringe 10, such properties determine the rate of heat transfer into the propellant in the second chamber 20. Similarly, the rate and phase of propellant entering the second chamber 20 affects the thermodynamic processes occurring during delivery with regards to the propellant in the second chamber 20.
As an example, a 0.5 bar drop in vapor pressure may be exhibited when delivering 1 ml of aqueous solution through a 27 gauge needle attached to the outlet 14 measured from the initial vapor pressure maximum when the propellant is released into the second chamber 20 to when the stopper 16 has reached the front end of the barrel 12.
The advantages of the present invention are best understood by comparison with a syringe powered by a compressed gas. In known prior art compressed gas syringes, compressed gas is released from a reservoir into a volume behind a stopper in a syringe barrel where the expanding volume of gas can act on the stopper and cause it to move and expel medicament from the barrel.
There is a constant mass of gas which follows the ideal gas law under adiabatic conditions and behaves as PV=nRT, where P is the pressure of the gas, V is the volume of the gas, n is the number of moles of gas, T is the temperature of the gas and R is the universal gas constant. Once the dead volume is filled with compressed gas, the expanding gas begins to gas the stopper to move, as indicated at 502 on
Since the quantity nRT is constant for adiabatic expansion, the pressure of the gas drops as the volume increases. This is shown in
In contrast, if the gas is initially a liquefied gas in accordance with the present invention, the mass of the gas increases as the gas expands as the liquid boils. It is this increasing mass aligned with the increasing volume that provides a more consistent pressure profile.
The pressure profile of
Further embodiments of syringes 10 in accordance with the present invention are described below with reference to
In
A further embodiment of a syringe in accordance with the present invention is shown in
In the embodiment of
A further embodiment of a syringe in accordance with the present invention is shown in
Yet another embodiment of a syringe 10 in accordance with the present invention is shown in
Modeling the second chamber 20 as a cylinder having radius r and height H, πr2 L should be greater than the maximum volume of liquid propellant in the second chamber 20 for the rear (open) end of the propellant conduit 30 to rise above the propellant liquid level when the syringe 10 is in a vertical orientation. Additionally, (πr2H/2) should be greater than the maximum volume of liquid propellant in the second chamber 20 for the propellant conduit to remain above the propellant liquid level when the syringe 10 is in a horizontal orientation. In one example, for a 100 μl volume of propellant in a second chamber 30 of diameter 6.35 mm, the magnitude of L should be 3.158 mm or greater to be above the propellant liquid level. In another example, for a 10 μl volume of propellant in a second chamber 30 of diameter 6.35 mm, the magnitude of L should be 0.316 mm or greater to be above the propellant liquid level.
A similar syringe 10 to that described above in relation to
The pressure profile of vapor pressure of propellant in the second chamber 20 during use will be influenced by the phase of propellant entering the second chamber. For example, if a constant or near constant flow of gas-phase (or predominantly gas-phase) propellant is being supplied to the second chamber 20 through the propellant conduit 30, then the stopper 16 will experience a more constant vapor pressure and move axially forwardly at a more constant rate within the barrel 12 and expel medicament from the first chamber 18 at a constant rate. This may be particularly suitable for applications where it is important to deliver medicament at a constant or near constant rate.
The passage of propellant through the propellant conduit 30 or aperture 26a does not constitute “regulated delivery”. The propellant passes through the propellant conduit 30 or aperture 26a at a constant pressure that is lower than the pressure that would be observed if the restriction (propellant conduit 30 or aperture 26a) were not present. Indeed, passage through the propellant conduit 30 or aperture 26a constitutes bolus delivery of the propellant into the second chamber 20.
Unless otherwise stated, all described features of the syringe of
Comparing the pressure profiles of
Indeed, it is anticipated that for some syringes in accordance with the present invention, where only gaseous propellant is introduced into the second chamber 20 that there will be no initial maximum prior to the end of delivery. That is, the initial increase in vapor pressure subsequent to point A will result in the movement of the stopper 16 and the expulsion of medicament, but at the end of delivery the vapor pressure will be at a level not previously exceeded in the delivery process. To put that another way, point C will represent the highest vapor pressure of the first and second time periods. In this scenario, following point C, the vapor pressure will increase as the propellant absorbs heat energy from its environment and tends towards the vapor pressure of the propellant at the temperature of its immediate environment (e.g. ambient temperature).
As described above, the form of the pressure profile produced by a propellant powered syringe 10 is determined by one of three parameters, namely i) the thermal properties of the syringe 10, ii) the rate of delivery of propellant into the second chamber 20, and iii) the phase of the propellant entering the second chamber 20. The embodiments described above demonstrate the effects of parameters ii) and iii) on the form of the pressure profile.
In the case where a coolant or refrigerant is applied to the outside of the barrel 12 proximate the second chamber 20, the coolant or refrigerant may be channeled or otherwise caused to travel towards the injection site after cooling the barrel 12 (and the liquid propellant in the second chamber 20) to additionally provide cooling to the injection site. The cooling provided to the injection site may provide the effect of reducing the level of pain caused by the injection as perceived by the patient.
In other embodiments, thermally insulating material may be present on or around the barrel 12 proximate the second chamber 12 so that the thermal transfer of heat from the environment to the barrel 12 is reduced. In this embodiment, heat lost from the barrel 12 and absorbed by the liquid propellant in the second chamber 20 may not be replaced (or such replacement will at least be restricted) by absorption of heat by the barrel 12 from the external environment. Again, such measures will limit the heat transfer to the second chamber 20 which contains the propellant so that a greater vapor pressure drop will be exhibited.
Conversely, if more thermal energy is supplied to the second chamber 20 such that the liquid propellant contained therein is able to absorb more thermal energy during delivery than it otherwise would be able to, the drop in vapor pressure exhibited in the second chamber 20 during delivery may be reduced and even reduced to substantially zero. Thermal energy may be supplied to the second chamber 20 by active heating means, which for example may be achieved by providing a heat source that has a temperature above the ambient temperature so that thermal energy may be transferred from the heat source to the second chamber 20, and in particular to the propellant contained therein. Alternatively, the thermal properties of the syringe 10, e.g. the barrel 12, may be configured so as to increase the rate of heat transfer from the environment to the second chamber 20. For example, the materials of the syringe 10 may be chosen such that they have a high thermal conductivity to maximize heat transfer into the second chamber 20 so that the liquid propellant is able to absorb sufficient heat to offset (i.e. reduce or eliminate) the reduction in temperature due to vaporization. Of course, if using materials having high thermal conductivity to construct the syringe 10, the materials must also provide other desired physical properties (e.g. strength and durability) to a sufficient degree.
Thus, in accordance with the present invention a syringe 10 may be provided that has suitable properties such that upon actuation of the syringe 10, a desired pressure profile of vapor pressure in the second chamber is exhibited. The desired pressure profile may be dictated by the desire to produce a delivery having a particular pressure profile, to suit a particular medicament or injection type, for example. Alternatively, the desired pressure profile may be dictated by the requirement to have a pressure feature of a particular type (e.g. magnitude, duration, gradient or rate etc.). The pressure feature may be used to trigger a subsequent action so that more complex modes of operation of the syringe can be utilized (as is described in more detail below).
As described above, the “first time period” is the time period between the initial release of propellant into the second chamber 20 and the initial maximum vapor pressure. Typically (although not always, as described above) the initial movement of the stopper 16 will be coincident with an initial maximum vapor pressure from which the vapor pressure decreases from over the second time period. The “second time period” is the time period between the initial forwardly axial movement of the stopper 16 and the point where forward axial movement of the stopper 16 is arrested (i.e. the end of the delivery phase when the stopper 16 reaches the front end of the barrel 12). The “third time period” is defined as the time period between the end of the second time period and the point where vapor pressure in the second chamber 20 reaches a predetermined level. In a preferable embodiment, the predetermined level determining the third time period is the vapor pressure of the propellant at the temperature of its immediate environment (e.g. ambient temperature).
In preferable embodiments, the syringe 10 in accordance with the present invention exhibits a pressure profile of vapor pressure in the second chamber 20 wherein the first time period is less than 1.0 seconds. In further preferable embodiments, it is preferable for the first time period to be shorter, such as less than 0.5 seconds, less than 0.2 seconds, or less than 0.1 seconds. In preferable embodiments, it is preferable for the second time period to be less than 15 seconds. However a second time period of around 15 seconds represents a relatively long delivery period, so in practice it may be more preferable if the second time period is less than 10 seconds and further preferably less than 5 seconds. In particularly preferable embodiments, the second time period is less than 3 seconds, less than 2 seconds, or less than 1 second. Where an initial maximum vapor pressure (a “first pressure”) is reached that is substantially coincident with the initial movement of the stopper 16 (i.e. coincident with the end of the first time period and the beginning of the second time period) it is preferable that this be less than 15 bar, or further preferably less than 10 bar, less than 8 bar or less than 6 bar. In a preferable embodiment, the first pressure is substantially equal to the vapor pressure of the propellant at the temperature of its immediate environment (e.g. ambient temperature). Defining the vapor pressure in the second chamber 20 at the end of the second time period (i.e. the start of the third time period) as a “second pressure”, in preferable embodiments the second pressure is preferably less than 99% of the first pressure, or further preferably less than 95% or less than 90% of the first pressure. Similarly, in preferable embodiments the second pressure is preferably greater than 50% of the first pressure, or further preferably greater than 75% or greater than 85% of the first pressure. In preferable embodiments, the difference between the first pressure and the second pressure is more than 0.1 bar, and further preferably more than 0.5 bar or more than 1.0 bar.
In accordance with a further or alternative aspect of the present invention, there is provided a syringe propellable by a propellant that boils at a predetermined temperature where the syringe comprises a barrel having an outlet at a front end, and a stopper axially moveable in the barrel, wherein the stopper defines and separates a first chamber and a second chamber. The first chamber is axially forwards of the stopper and is configured for containing a substance such as a medicament, and the second chamber is axially rearwards of the stopper and is configured to receive propellant for acting on the stopper to move the stopper axially forwardly in the barrel to expel medicament through the outlet upon actuation of the syringe. Indeed, this syringe is much like the syringes described above in accordance with other embodiments of the invention, and, indeed, the syringe of this further aspect may be identical to one of those earlier described syringes. However, the syringe of this further aspect is not necessarily limited to receiving propellant from a third chamber that includes a rupturable container. Indeed, propellant may be supplied via a valved container or otherwise to the syringe of this further aspect of the invention.
The syringe is configured such that, in use, upon actuation of the syringe, propellant is released into the second chamber (by any suitable means) and the pressure in the second chamber increases causing the stopper to move axially forwardly in the barrel and begin to expel the substance contained in first chamber therefrom through the outlet. The syringe additionally comprises a trigger that is activated (or “triggered”) in response to the pressure in the second chamber satisfying a predetermined condition. Upon activation of the trigger, an “action” is triggered. The action may be the movement of a protecting needle shield between a retracted exposing position and a forward protecting position. Alternatively, the syringe may be part of a larger autoinjector device where the syringe is axially moveable between a first position where the needle is wholly within a housing of the device and a second position where the needle protrudes from the housing so as to be able to penetrate an injection site. In this embodiment, the action triggered may be the movement of the syringe in the device between the first and second positions. Additionally or alternatively, the action triggered may be the activation of one or more indicators to produce one or more signals. The indicators may include a visual indicator, such as an LED. Alternatively, the indicators may include an audible indicator, such as a loud speaker. In any case, the one or more indicators may signal the end of delivery of medicament or signal that a predetermined time period has elapsed since the end of delivery.
The predetermined condition that causes the activation of the trigger may be a predetermined pressure being exceeded in the second chamber. The trigger may be activated when the predetermined pressure is exceeded in the second chamber after a predetermined time period has elapsed or subsequent to a prior predetermined condition being satisfied. The predetermined condition may be the pressure falling below a predetermined pressure, and may be the pressure falling below a predetermined pressure after a predetermined time period has elapsed or subsequent to a prior predetermined condition being satisfied. In further or alternative embodiments, the predetermined pressure may be in respect of the absolute pressure in the second chamber, a ratio of pressures in the second chamber (with respect to time), or a difference in pressures in the second chamber (with respect to time). Alternatively, the predetermined condition could be a ratio or difference between the pressure in the second chamber and the pressure in a reference chamber, such as the third chamber.
The trigger may include a pressure sensor that is connected to an actuator for causing the further action. Additionally or alternatively, the trigger may include a mechanism whereby the pressure in the second chamber directly causes the further action. For example, the vapor pressure in the second chamber may be used (once a predetermined condition is satisfied) to directly bias a needle shield to its forward protecting position, or cause some other physical mechanism to move. In the case of a moving needle shield, the needle shield could be released so that under the influence of a biasing member, the needle shield is biased against the injection site (e.g. the patient's skin) so that when the syringe is removed from the injection site there is no resistance to the bias provided by the biasing member and the needle shield moves fully to its protecting position.
If the syringe is configured to exhibit a pressure profile in accordance with the present invention, the pressure profile can be tailored (as part of the specification of the syringe) to have pressure features that can be used as or for the predetermined condition that activates the trigger.
As noted above, in certain embodiments, propellant may be provided to the second chamber by means that do not have rupturable walls (in accordance with certain aspects of the present invention). For example, the syringe may comprise a dispenser for providing propellant to the second chamber, wherein the dispenser is moveable from a closed position in which propellant cannot exit the dispenser to an open position in which a predetermined volume of propellant can exit the dispenser. The dispenser may have a capacity for containing propellant, where the predetermined volume is less than the capacity. the capacity may be defined by a first internal volume of the dispenser, and the predetermined volume is defined by a second internal volume of the dispenser, and wherein in the closed position, the first internal volume is fluidly connected to the second internal volume so as to allow propellant to fill the second internal volume, and in the open position, the first internal volume is not fluidly connected to the second internal volume and the second internal volume is fluidly connected to the second chamber so as to allow the predetermined volume of propellant to be provided to the second chamber.
The carriage 402 and nozzle 406 are moveable through a rear seal 408a and a forward seal 408b. The rear seal 408a and the forward seal 408b together with the frame 400 define an annulus 410 around the carriage 402 and the nozzle 406. The nozzle 406 is moveable so as to protrude through the forward seal 408b and an opening 321a of the dispenser 321 in at least the open position.
The carriage 402 has a pair of passageways 402a,402b that, together with a hollow region 402b of the carriage 402, form a fluidic bypass pathway (indicated as F1 in
Given that the carriage 402 and the nozzle 406 are biased by the spring 404 towards the closed position, the central volume 322 will be fluidly connected to the annulus 410 in the natural state of the dispenser 321 in the absence of external forces acting on the carriage 402 and nozzle 406. In the closed position, there is no fluid pathway from the annulus 410 to outside of the dispenser.
If the nozzle 406 and carriage 402 are moved axially rearwardly (as indicated by arrows M in
Therefore, unlike some prior art valve dispensers, the dispenser 321 described above with reference to
Whilst the above described embodiment represents a preferable arrangement of such as dispenser 321, alternative embodiments may comprise any arrangement that is capable of providing a predetermined volume of propellant to the second chamber when moved to an open position, such that it is reusable to then provide a further predetermined volume of propellant at a later time. Crucially for these embodiments, once the dispenser is in an open position, propellant is not delivered continuously such that only the position of the dispenser determines when delivery of propellant will cease.
In another example of a propellant dispenser, a container of propellant has a valved outlet that is moveable between a closed position where propellant cannot exit the container and an open position where propellant can exit the container. The dispenser additionally has a latching mechanism or other similar arrangement that prevents the valved outlet moving back to the closed position once moved to the open position. Therefore, once the valve has been moved to the open position, the entire volume of propellant in the container is discharged through the valved outlet. Preferably, the container is configured to contain a predetermined volume of propellant sufficient for the delivery of a dose of medicament. In this example, the rupturing portion comprises the valved outlet and the third chamber 22 is ruptured when the valved outlet is in the open position and prevented from moving back to the closed position. That is, the third chamber 22 is ruptured in the sense that it is irreversibly opened and the entire contents of the third chamber 22 discharge therefrom. In a specific example, the valved outlet is a valve having a valve body, valve stem, and a locking member, where the valve stem is slidably moveable relative to the valve body between a non-dispensing (“closed”) position in which an outlet port of the valve stem is out of fluid communication with the third chamber 22, and a dispensing (“open”) position in which the outlet port is in fluid communication with the third chamber 22 so as to permit transfer of propellant from the third chamber 22 through the valve stem.
The locking member is configured to prevent return of the valve stem into the non-dispensing position once the valve stem slides beyond a locking position.
In one embodiment, the locking member and the valve stem comprise inter-engaging members, where the inter-engaging members contact one another during movement of the valve stem towards the dispensing position and permit movement of the valve stem into the dispensing position, and contact one another during attempted movement of the valve stem from beyond the locking position back towards the dispensing position and prevent movement of the valve stem back into the non-dispensing position.
The inter-engaging members, may contact one another during movement of the valve stem towards the dispensing position and permit movement of the valve stem into the dispensing position by flexing or other distortion of at least one of the inter-engaging members.
In a preferable embodiment, the inter-engaging member of the valve stem comprises a flange. Wherein, further preferably, a distal edge of the flange is angled to promote flexing of the locking member during movement of the valve stem into the dispensing position.
In a further or alternative preferable embodiment, the inter-engaging member of the locking member comprises at least one flexible latch, wherein the at least one flexible latch preferably exhibits elastic behaviour.
The locking position of the valve stem may be defined as a point where the inter-engaging member of the valve stem slides beyond, and disengages from, the inter-engaging member of the locking member.
In some embodiments, the valve may further comprise a biasing member (a compression spring, for example) for biasing the valve stem into the non-dispensing position.
In a further or alternative aspect of the present invention, there is provided a method of designing a syringe where the syringe comprises a barrel for containing a substance such as medicament, where the barrel has an outlet. A stopper defines and separates a first chamber and a second chamber where the first chamber is axially forwards of the stopper and is configured for containing a substance such as a medicament, and the second chamber is axially rearwards of the stopper and is configured to receive propellant for acting on the stopper to move the stopper axially forwardly in the barrel to expel medicament through the outlet upon actuation of the syringe. The method in accordance with the present invention comprises one or more of the steps of i) selecting the thermal properties of the syringe, ii) determining the rate of delivery of propellant into the second chamber, or iii) determining the phase of propellant entering the second chamber, in order to exhibit a desired pressure profile of propellant acting on the stopper in the second chamber following actuation of the syringe.
Selecting the thermal properties of the syringe means configuring the syringe so that either additional heat or cooling is provided to the propellant during use, or that a thermal pathway of a desired thermal conductivity is present in the syringe. The thermal pathway may be configured by selection of the materials of the syringe, each material having a desired thermal conductivity. Additionally or alternatively, additional components such as thermally insulating or conducting elements such as jackets around the barrel, may be included to alter the thermal pathway from the external environment and the propellant in the second chamber. Alternatively, an additional component such as a heat sink or heat source may be provided in the second chamber. The heating or cooling provided to the propellant may be by one of the methods described above. As has been described above, the ability of the propellant in the second chamber to absorb heat from its surrounding (or not, as the case may be) impacts on the pressure profile of the propellant acting on the stopper in the second chamber.
The rate of delivery of propellant entering the second chamber is determined, amongst other factors, by the configuration of the source of propellant, the volume of propellant and the configuration of any restriction that the propellant must pass through in order to enter the second chamber. For example, a pressurized jet of propellant from a propellant source will result in a higher rate of delivery of propellant entering the second chamber compared with propellant entering the second chamber solely due to vaporization of the propellant by the temperature of its immediate environment (e.g. ambient temperature). Additionally, a narrow restriction will reduce the rate of propellant delivery entering the second chamber compared with a wider restriction. The rate of delivery of propellant into the second chamber affects the vapor pressure (and therefore force) exerted on the stopper 16 and therefore affects the rate of delivery of medicament and the profile (i.e. force or vapor pressure profile) of the delivery.
As is described above, the phase of propellant that enters the second chamber affects the pressure profile of the propellant acting on the stopper in the second chamber. The phase of the propellant entering the second chamber may be controlled by one of the mechanisms described above (
The method of design may be an iterative physical redesign sequence or may be assisted with computer implemented calculations, for example in selecting the thermal properties of the syringe to exhibit the desired pressure profile. In one embodiment, the step of selecting the thermal properties of the syringe to exhibit the desired pressure profile of fluid acting on the stopper following actuation of the syringe comprises the steps of:
Similar methods may be employed for obtaining a syringe design through iterative modification of properties that affect the rate of delivery of propellant into the second chamber and/or the phase of propellant entering the second chamber. Indeed, an iterative method in accordance with the present invention may include the iterative step of modifying any one or combination of properties that affect the thermal properties of the syringe, the rate of delivery of propellant into the second chamber, and the phase of propellant entering the second chamber.
The step of determining the pressure profile (at any point during the iterative method) may be executed by measurement of pressure or a calculation that may be a computer implemented calculation.
Once a syringe design is reached that exhibits the desired pressure profile, a syringe may be manufactured according to that design.
In any of the described embodiments of syringes in accordance with the present invention, the propellant containers shown in
The material that forms the sheets 124a,124b is flexible and rupturable such that once ruptured (i.e. broken, torn or otherwise penetrated) a fluid pathway is provided therethrough into the volume 122 that is not resealable. The rupturable wall 124 is preferably substantially impermeable to the propellant contained in the volume 122. The actual gas permeability of the rupturable wall 124 may depend upon the chosen propellant contained in the volume 122. For example, for HFA 134a, it is preferable for the rupturable wall to have a gas permeability such that the volume of propellant remaining in the container 121 is sufficient to reliably deliver a dose of medicament. Therefore, the limitations on the gas permeability of the rupturable wall 124 are determined by the intended volume of medicament to be delivered and the initial volume of propellant contained in the container 121. To deliver a 1 ml dose of medicament, it is particularly preferable to ensure that there is at least 20 μl of propellant in the container 121. Therefore, over a two year storage period, a container 121 initially containing 100 μl of HFA propellant may lose up to 80 μl as gas through the rupturable wall 124 for there to be at least 20 IA remaining to deliver the 1 ml dose of medicament. In this example, the maximum gas permeability of the container 121 would be 0.365 g/(m2.day). Whilst it would be preferable to have at least 20 μl of HFA propellant remaining after two years for delivering a 1 ml dose of medicament, a container 121 having a gas permeability that ensures that there is 5 μl or more of HFA propellant may be sufficient to ensure that enough propellant will remain after two years to deliver a 1 ml dose of medicament.
The rupturable wall 124 may include polyethylene and/or may include a polyamide and/or may include nylon and/or may include a cyclic olefin copolymer (COC) and/or may include a cyclic olefin polymer (COP). In some preferable embodiments, the rupturable wall may be composed substantially of nylon. In alternative embodiments, one or each sheet 124a,124b may be formed of a laminate of two or more different materials selected from polyethylene, polyamide, and metals (e.g. a metallic foil). The selection of the two or more materials may be based upon one of the layers providing a substantially impermeable gas barrier to prevent the propellant from escaping from the volume 122, and another of the layers providing mechanical strength to resist the outward pressure exerted by gaseous propellant in the volume 122. The rupturable wall 124 may be formed by co-extruding two or more materials.
Regardless of the type of material selected to form the rupturable wall 124, the seals 125 are formed between two like materials. So, in the case where one or both of the sheets 124a,124b comprise laminates of two or more materials, the sheets 124a,124b are arranged such that the interface between them comprises two adjacent like materials which may form the seals 125. The seals 125 may be formed by any of heat sealing, sonic welding or by use of an adhesive.
The shape of the container 121 may differ from that shown in
Either of the containers 121 and 221 may be used in any of the syringes described above in accordance with the present invention. Alternatively, the containers 121,221 may be used in other applications, including other medical devices. In particular, the containers 121,221 may be used as a power source in inhaler-type devices (e.g. nasal inhalers).
The containers 121,221 provide a small, convenient, portable, cost effective power source that may be used in a plethora of devices. For a re-usable syringe, for example, the containers 121,221 offer a simple and effective means to power the syringe over multiple uses, where the user removes a ruptured container 121,221 following an injection and replaces it with a new unruptured container 121,221 prior to the next use.
The propellant used in the containers 121,221 and indeed in any of the syringes described above may be any propellant that boils at a predetermined temperature. In preferable embodiments, the propellant is or contains HFA and further preferable is or contains HFA 134a. Indeed, mixtures of several propellant substances or propellant substances and additives may provide a propellant for use in accordance with the present invention. As described above, the propellant may be chosen to be one that boils at ambient temperature or one that boils at a temperature higher than ambient temperature, in which case a further heat source is required to cause the propellant to boil and move the stopper 16.
A schematic representation of a method of manufacturing a container, such as the container 221 shown in
The method includes the steps of using the piercing element 302 to form the opening 304. The tube 224 may be pressurized (i.e. a gaseous pressure may be applied in the central volume 222) to increase its rigidity so as to permit effective use of the piercing element 302. The opening 304 may be formed so that a complete hole is not created. This is not essential, but forming an opening 304 that does not result in the formation of loose material (a so-called “chad”) minimizes the risk of loose material entering the central volume 222 and/or interfering with the manufacturing process. A horse-shoe shaped (i.e. U-shaped) opening 304 is one suitable opening that does result in chad formation. In one example, the piercing element 302 is a hypodermic needle.
The first sealing elements 304 may then be used to form a first upper seal 225b above (i.e. upstream) of the opening 304 as shown in
As shown in
The tube 224 is oriented with its longitudinal axis substantially parallel to the (gravitational) vertical so that the propellant 300 condenses at a lower end of the tube 224. With this arrangement, the second upper seal 225c can be formed above the level of liquid propellant and therefore reduces the risk of liquid propellant leaking from the tube 224 during formation of the container 221.
The extruded tube may be moved relative to the first sealing elements 306, second sealing elements 308, piercing element 302 and/or propellant dispensing head 310 so that the first upper seal 225b of the tube 224 becomes the lower seal 225a′ of a subsequent tube 224′ and the process can begin again to fill the subsequent tube 224′. The container 221 (and subsequent containers) can be cut/removed from the production line following their filling and sealing and prior to the filling and sealing of a subsequent container. Alternatively, several containers may be filled and sealed before being separated by cutting or otherwise separating along the seals. Thus, a continuous string of containers can be formed that are each easily handled and cut as required. The pitch of the containers (e.g. the distance between lower seal 225a and second upper seal 225c for container 221) may be altered to change the magnitude of the central volume 222 in accordance with the desired dose of propellant 300.
The first and second sealing elements 306, 308 may be any suitable sealing apparatus that are capable of forming heat seals, sonic welds or other seals, such as adhesive seals. The first and second sealing elements 306,308 need not necessarily be capable of forming the same type of seal as one another.
A schematic representation of an alternative method of manufacturing a container, such as the container 121 shown in
Sealing elements 408 seal the sheets 124a,124b together across their entire width to form a lower seal 125a. A propellant dispensing head 410 is arranged between the sheets 124a,124b and between the four rollers 412 and is arranged relative to the sheets 124a,124b and the rollers 412 so that the sheets 124a,124b form a seal with one another or the propellant dispensing head 410. The result is that a sealed central volume 122 is formed that is initially defined by the seals 125a,125b,125c and the seals between the sheets 124a,124b and the propellant dispensing head 410.
In this position, the propellant dispensing head 410 is able to deposit a desired dose of propellant 300 into the central volume 122. Once the desired dose of propellant 300 has been deposited, the propellant dispensing head 410 may be switched off preventing further deposition of propellant 300 and the sealing elements 408 may then seal the sheets 124a,124b above the deposited propellant 300 to form an upper seal 125d. This forms a container 121 that has a central volume 122 containing propellant 300 where the central volume 122 is defined by seals 125a,125b,125c,125d. Any or all of the seals 125a,125b,125c,125d may be heat seals, sonic welds or other seals, such as adhesive seals.
The upper seal 125d may then form the lower seal 125a′ of a subsequent container 121′ (see
The pitch of the containers (e.g. the distance between lower seal 125a and upper seal 125c) may be altered to change the magnitude of the central volume 122 in accordance with the desired dose of propellant 300.
Throughout the description, claims and figures of this specification, 0 bar is considered to be defined as atmospheric pressure, so that all values of pressure given in bar are relative to atmospheric pressure (0 bar).
Throughout the present specification, the term “syringe” relates to and includes any medicament delivery device having a medicament container with an outlet and a moveable stopper for expelling medicament therefrom. As examples, the syringe may include a needle, a nozzle or a conduit attached to the outlet. In other embodiments, the syringe may not include any further components downstream of the outlet. The syringe of the present invention may be or form part of a subcutaneous delivery device, a nasal delivery device, an otic delivery device, an oral delivery device, an ocular delivery device, an infusion device or any other suitable medicament delivery device.
Throughout the description and claims of this specification, the words “comprise” and “contain” and variations of them mean “including but not limited to”, and they are not intended to (and do not) exclude other moieties, additives, components, integers or steps. Throughout the description and claims of this specification, the singular encompasses the plural unless the context otherwise requires. In particular, where the indefinite article is used, the specification is to be understood as contemplating plurality as well as singularity, unless the context requires otherwise.
Features, integers, characteristics, compounds, chemical moieties or groups described in conjunction with a particular aspect, embodiment or example of the invention are to be understood to be applicable to any other aspect, embodiment or example described herein unless incompatible therewith. All of the features disclosed in this specification (including any accompanying claims, abstract and drawings), and/or all of the steps of any method or process so disclosed, may be combined in any combination, except combinations where at least some of such features and/or steps are mutually exclusive. The invention is not restricted to the details of any foregoing embodiments. The invention extends to any novel one, or any novel combination, of the features disclosed in this specification (including any accompanying claims, abstract and drawings), or to any novel one, or any novel combination, of the steps of any method or process so disclosed.
The reader's attention is directed to all papers and documents which are filed concurrently with or previous to this specification in connection with this application and which are open to public inspection with this specification, and the contents of all such papers and documents are incorporated herein by reference.
| Number | Date | Country | Kind |
|---|---|---|---|
| 1210082.2 | Jun 2012 | GB | national |
This application is a US national phase under 35 USC §371 of International Application No. PCT/GB2013/051508, filed Jun. 7, 2013, which claims priority to United Kingdom patent application GB 1210082.2, filed Jun. 7, 2012. Priority application GB 1210082.2 is hereby incorporated by reference.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/GB2013/051508 | 6/7/2013 | WO | 00 |
