US20150141918A1 - Syringe - Google Patents

Syringe Download PDF

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Publication number
US20150141918A1
US20150141918A1 US14/406,171 US201314406171A US2015141918A1 US 20150141918 A1 US20150141918 A1 US 20150141918A1 US 201314406171 A US201314406171 A US 201314406171A US 2015141918 A1 US2015141918 A1 US 2015141918A1
Authority
US
United States
Prior art keywords
chamber
propellant
syringe
pressure
stopper
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US14/406,171
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English (en)
Inventor
Ian Anderson
Matt Ekman
Rachel Suzanne Koppelman
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Consort Medical Ltd
Original Assignee
Consort Medical Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Consort Medical Ltd filed Critical Consort Medical Ltd
Publication of US20150141918A1 publication Critical patent/US20150141918A1/en
Assigned to CONSORT MEDICAL PLC reassignment CONSORT MEDICAL PLC ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: EKMAN, Matt, ANDERSON, IAN, KOPPELMAN, Rachel Suzanne
Abandoned legal-status Critical Current

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    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B65—CONVEYING; PACKING; STORING; HANDLING THIN OR FILAMENTARY MATERIAL
    • B65B—MACHINES, APPARATUS OR DEVICES FOR, OR METHODS OF, PACKAGING ARTICLES OR MATERIALS; UNPACKING
    • B65B31/00—Packaging articles or materials under special atmospheric or gaseous conditions; Adding propellants to aerosol containers
    • B65B31/04—Evacuating, pressurising or gasifying filled containers or wrappers by means of nozzles through which air or other gas, e.g. an inert gas, is withdrawn or supplied
    • B65B31/044—Evacuating, pressurising or gasifying filled containers or wrappers by means of nozzles through which air or other gas, e.g. an inert gas, is withdrawn or supplied the nozzles being combined with a filling device
    • B65B31/045—Evacuating, pressurising or gasifying filled containers or wrappers by means of nozzles through which air or other gas, e.g. an inert gas, is withdrawn or supplied the nozzles being combined with a filling device of Vertical Form-Fill-Seal [VFFS] machines
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B65—CONVEYING; PACKING; STORING; HANDLING THIN OR FILAMENTARY MATERIAL
    • B65D—CONTAINERS FOR STORAGE OR TRANSPORT OF ARTICLES OR MATERIALS, e.g. BAGS, BARRELS, BOTTLES, BOXES, CANS, CARTONS, CRATES, DRUMS, JARS, TANKS, HOPPERS, FORWARDING CONTAINERS; ACCESSORIES, CLOSURES, OR FITTINGS THEREFOR; PACKAGING ELEMENTS; PACKAGES
    • B65D83/00—Containers or packages with special means for dispensing contents
    • B65D83/14—Containers for dispensing liquid or semi-liquid contents by internal gaseous pressure, i.e. aerosol containers comprising propellant
    • B65D83/16—Actuating means
    • B65D83/24—Arrangements for keeping the actuating means in the active position, e.g. for continuous dispensing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/178—Syringes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M39/00—Tubes, tube connectors, tube couplings, valves, access sites or the like, specially adapted for medical use
    • A61M39/22—Valves or arrangement of valves
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
    • A61M5/1452—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons
    • A61M5/14526—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons the piston being actuated by fluid pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
    • A61M5/155—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by gas introduced into the reservoir
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16804—Flow controllers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16877—Adjusting flow; Devices for setting a flow rate
    • A61M5/16881—Regulating valves
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/178—Syringes
    • A61M5/20—Automatic syringes, e.g. with automatically actuated piston rod, with automatic needle injection, filling automatically
    • A61M5/2053—Media being expelled from injector by pressurised fluid or vacuum
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/178—Syringes
    • A61M5/31—Details
    • A61M5/32—Needles; Details of needles pertaining to their connection with syringe or hub; Accessories for bringing the needle into, or holding the needle on, the body; Devices for protection of needles
    • A61M5/3205—Apparatus for removing or disposing of used needles or syringes, e.g. containers; Means for protection against accidental injuries from used needles
    • A61M5/321—Means for protection against accidental injuries by used needles
    • A61M5/3243—Means for protection against accidental injuries by used needles being axially-extensible, e.g. protective sleeves coaxially slidable on the syringe barrel
    • A61M5/326—Fully automatic sleeve extension, i.e. in which triggering of the sleeve does not require a deliberate action by the user
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/44—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests having means for cooling or heating the devices or media
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B65—CONVEYING; PACKING; STORING; HANDLING THIN OR FILAMENTARY MATERIAL
    • B65B—MACHINES, APPARATUS OR DEVICES FOR, OR METHODS OF, PACKAGING ARTICLES OR MATERIALS; UNPACKING
    • B65B51/00—Devices for, or methods of, sealing or securing package folds or closures; Devices for gathering or twisting wrappers, or necks of bags
    • B65B51/10—Applying or generating heat or pressure or combinations thereof
    • B65B51/26—Devices specially adapted for producing transverse or longitudinal seams in webs or tubes
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B65—CONVEYING; PACKING; STORING; HANDLING THIN OR FILAMENTARY MATERIAL
    • B65B—MACHINES, APPARATUS OR DEVICES FOR, OR METHODS OF, PACKAGING ARTICLES OR MATERIALS; UNPACKING
    • B65B51/00—Devices for, or methods of, sealing or securing package folds or closures; Devices for gathering or twisting wrappers, or necks of bags
    • B65B51/10—Applying or generating heat or pressure or combinations thereof
    • B65B51/26—Devices specially adapted for producing transverse or longitudinal seams in webs or tubes
    • B65B51/30—Devices, e.g. jaws, for applying pressure and heat, e.g. for subdividing filled tubes
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B65—CONVEYING; PACKING; STORING; HANDLING THIN OR FILAMENTARY MATERIAL
    • B65D—CONTAINERS FOR STORAGE OR TRANSPORT OF ARTICLES OR MATERIALS, e.g. BAGS, BARRELS, BOTTLES, BOXES, CANS, CARTONS, CRATES, DRUMS, JARS, TANKS, HOPPERS, FORWARDING CONTAINERS; ACCESSORIES, CLOSURES, OR FITTINGS THEREFOR; PACKAGING ELEMENTS; PACKAGES
    • B65D83/00—Containers or packages with special means for dispensing contents
    • B65D83/14—Containers for dispensing liquid or semi-liquid contents by internal gaseous pressure, i.e. aerosol containers comprising propellant
    • B65D83/44—Valves specially adapted for the discharge of contents; Regulating devices
    • B65D83/48—Lift valves, e.g. operated by push action
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B65—CONVEYING; PACKING; STORING; HANDLING THIN OR FILAMENTARY MATERIAL
    • B65D—CONTAINERS FOR STORAGE OR TRANSPORT OF ARTICLES OR MATERIALS, e.g. BAGS, BARRELS, BOTTLES, BOXES, CANS, CARTONS, CRATES, DRUMS, JARS, TANKS, HOPPERS, FORWARDING CONTAINERS; ACCESSORIES, CLOSURES, OR FITTINGS THEREFOR; PACKAGING ELEMENTS; PACKAGES
    • B65D83/00—Containers or packages with special means for dispensing contents
    • B65D83/14—Containers for dispensing liquid or semi-liquid contents by internal gaseous pressure, i.e. aerosol containers comprising propellant
    • B65D83/60—Containers for dispensing liquid or semi-liquid contents by internal gaseous pressure, i.e. aerosol containers comprising propellant with contents and propellant separated
    • B65D83/64—Containers for dispensing liquid or semi-liquid contents by internal gaseous pressure, i.e. aerosol containers comprising propellant with contents and propellant separated by pistons
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F17—STORING OR DISTRIBUTING GASES OR LIQUIDS
    • F17C—VESSELS FOR CONTAINING OR STORING COMPRESSED, LIQUEFIED OR SOLIDIFIED GASES; FIXED-CAPACITY GAS-HOLDERS; FILLING VESSELS WITH, OR DISCHARGING FROM VESSELS, COMPRESSED, LIQUEFIED, OR SOLIDIFIED GASES
    • F17C13/00—Details of vessels or of the filling or discharging of vessels
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
    • A61M2005/14513—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons with secondary fluid driving or regulating the infusion
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M39/00—Tubes, tube connectors, tube couplings, valves, access sites or the like, specially adapted for medical use
    • A61M39/22—Valves or arrangement of valves
    • A61M39/24—Check- or non-return valves
    • A61M2039/2473—Valve comprising a non-deformable, movable element, e.g. ball-valve, valve with movable stopper or reciprocating element
    • A61M2039/2486—Guided stem, e.g. reciprocating stopper
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2207/00—Methods of manufacture, assembly or production
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2207/00—Methods of manufacture, assembly or production
    • A61M2207/10—Device therefor
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04C—ROTARY-PISTON, OR OSCILLATING-PISTON, POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; ROTARY-PISTON, OR OSCILLATING-PISTON, POSITIVE-DISPLACEMENT PUMPS
    • F04C2270/00—Control; Monitoring or safety arrangements
    • F04C2270/04—Force
    • F04C2270/042—Force radial
    • F04C2270/0421—Controlled or regulated
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T29/00—Metal working
    • Y10T29/49—Method of mechanical manufacture
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T29/00—Metal working
    • Y10T29/49—Method of mechanical manufacture
    • Y10T29/49808—Shaping container end to encapsulate material

Definitions

  • This invention relates to a medical device, and in particular to a syringe for delivering a dose of medicament.
  • syringes include a power source, such as a spring or a compressed gas to deliver a dose of medicament to a patient.
  • 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.
  • 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.
  • a syringe propellable by propellant that boils at a predetermined temperature comprising:
  • 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;
  • 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.
  • 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.
  • 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.
  • the propellant conduit extends into the fourth chamber by at least 0.3 mm.
  • 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.
  • 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.
  • 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.
  • the predetermined temperature may be any temperature between 15° C. and 30° C. Specifically, the temperature is between 20° C. and 25° C.
  • the predetermined temperature is greater than ambient temperature.
  • a syringe propellable by propellant that boils at a predetermined temperature 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.
  • 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.
  • 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;
  • 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
  • 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • HFA hydrofluoroalkane
  • 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).
  • 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.
  • HFA hydrofluoroalkane
  • the container is a power source for actuating the syringe.
  • 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.
  • a method of manufacturing a container containing propellant comprising the steps of:
  • 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.
  • 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.
  • FIG. 1A is a schematic cross sectional view of a syringe according to an embodiment of the present invention comprising a self-contained rupturable container of propellant;
  • FIG. 1B is a schematic cross sectional view of a syringe according to an alternative embodiment of the present invention comprising a rupturable propellant chamber;
  • FIG. 1C is a schematic cross sectional view of a syringe according to an alternative embodiment of the present invention comprising a propellant chamber with a partially rupturable separating wall;
  • FIG. 1D is a schematic cross sectional view of a syringe according to an alternative embodiment of the present invention comprising a propellant chamber containing a self-contained rupturable container of propellant;
  • FIG. 1E is a schematic cross sectional view of the syringe of FIG. 1D additionally comprising a fluid conduit extending into the propellant chamber;
  • FIG. 1F is a schematic cross sectional view of a syringe according to an alternative embodiment of the present invention comprising a propellant chamber with a partially rupturable separating wall and a fluid conduit extending into the propellant chamber;
  • FIG. 2 shows an embodiment of a container for containing propellant in accordance with the present invention
  • FIG. 3 shows an alternative embodiment of a container for containing propellant in accordance with the present invention
  • FIG. 4 shows a rupturing portion in accordance with an embodiment of the present invention
  • FIG. 5 shows an alternative rupturing portion in accordance with an embodiment of the present invention
  • FIG. 6A shows a time-dependent gas volume profile of a compressed gas powered syringe in accordance with the prior art where the compressed gas reservoir is large relative to the internal volume of the system, and FIG. 6B shows the corresponding time-dependent pressure profile;
  • FIG. 7A shows a time-dependent gas volume profile of a compressed gas powered syringe in accordance with the prior art where the compressed gas reservoir is small relative to the internal volume of the system, and FIG. 7B shows the corresponding time-dependent pressure profile;
  • FIG. 8A shows a time-dependent gas volume profile of a propellant powered syringe in accordance with an embodiment of the present invention
  • FIG. 8B shows the corresponding time-dependent pressure profile
  • FIG. 9 shows a pressure profile of vapor pressure vs. time for propellant in the second chamber of a syringe in accordance with the present invention where liquid propellant is introduced into the second chamber;
  • FIG. 10 shows a pressure profile of vapor pressure vs. time for propellant in the second chamber of a syringe in accordance with the present invention where gaseous and liquid propellant is introduced into the second chamber;
  • FIG. 11 shows a pressure profile of vapor pressure vs. time for propellant in the second chamber of a syringe in accordance with the present invention where only gaseous propellant is introduced into the second chamber;
  • FIG. 12 shows a pressure profile of vapor pressure vs. time for propellant in the second chamber of a syringe in accordance with the present invention where the propellant in the second chamber has been actively cooled during delivery;
  • FIGS. 13A to 13D are schematic cross sectional views representing a method of filling a propellant container in accordance with an embodiment of the present invention
  • FIGS. 14A and 14B are schematic cross sectional views representing a method of filling a propellant container in accordance with an alternative embodiment of the present invention
  • FIG. 14C is a schematic perspective view of a further step of the method represented by FIGS. 14A and 14B ;
  • FIGS. 15A and 15B show cross-sectional views of a dispenser for providing a predetermined volume of propellant to the second chamber of the syringe in accordance with certain embodiments of the present invention, where FIG. 15A shows the dispenser in a closed position and FIG. 15B shows the dispenser in an open position.
  • FIG. 1A A syringe 10 according to an embodiment of the present invention is shown in FIG. 1A .
  • the syringe 10 has a barrel 12 having an outlet 14 at a forward end and a stopper 16 disposed in the barrel 12 .
  • the stopper 16 is axially moveable within the barrel 12 when subjected to a sufficient axial force.
  • the barrel 12 has a finger flange 12 a at a rear end, however some syringes within the scope of the present invention may not comprises finger flanges.
  • the stopper 16 defines and separates a first chamber 18 and a second chamber 20 where the first chamber 18 is axially forwards of the stopper 16 and is configured for containing a substance such as a medicament, and in particular, a liquid medicament.
  • the second chamber 20 is axially rearwards of the stopper 16 and is configured to receive propellant from a propellant source.
  • the propellant source is a container 21 which comprises a rupturable wall 24 defining a third chamber 22 containing propellant.
  • 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.
  • 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 .
  • 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 .
  • the propellant may flow through the hollow portion from the third chamber 22 to the second chamber 20 .
  • the rupturing portion may comprise apparatus for rupturing the rupturable wall 24 by a bursting mechanism.
  • 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 .
  • the rupturing portion may be moved towards the third chamber 22 to rupture the third chamber 22 .
  • the third chamber 22 may be moved towards the rupturing portion to cause rupturing of the third chamber 22 .
  • FIG. 4 shows an example of a rupturing portion 510 in accordance with an embodiment of the present invention for establishing a permanent fluid connection between the third chamber 22 and the second chamber 20 .
  • the rupturing portion 510 includes a conical element 512 that has a cut-out portion 512 a and a bore 512 b running therethrough.
  • the conical element 512 projects from a base 514 through which the bore 512 b passes.
  • the conical element 512 pierces a hole in a rupturable wall of the third chamber 22 requiring only a relatively low force to establish a fluid connection between the third chamber 22 and the second chamber 20 via the bore 512 b .
  • the tapered profile of the conical element 512 means that as the rupturing portion 510 is advanced further towards the rupturable wall, the conical element 512 will enlarge the hole created and ensure that the fluid path between the third chamber 22 and second chamber 20 is not obstructed.
  • the cut-out portion 512 a ensures that the hole is created effectively and minimizes the risk of the rupturing portion 510 itself sealing the hole it creates. Fluid egress from the third chamber 22 is therefore maximized.
  • the presence of the bore 512 b facilitates direct and efficient passage of both liquid and gaseous propellant between the third chamber 22 and second chamber 20 .
  • 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.
  • FIG. 5 shows two identical rupturing portions 510 in suitably close arrangement for acting on a single rupturable wall.
  • the use of multiple rupturing portions (in general) will facilitate greater transfer of fluid from the third chamber 22 to the second chamber 20 .
  • the one or more rupturing portions may rupture the third chamber 22 from any direction and in any orientation. Depending on the specific syringe, it may be preferable to rupture the third chamber 22 at a particular point or in a particular direction to maximize or otherwise control the release of propellant from the third chamber 22 .
  • non-conical but tapered elements may be used to form the rupturing portion of the present invention.
  • the tapered element 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.
  • the rupturing portion 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.
  • 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.
  • HFA 422d has a boiling point between ⁇ 46.2° C. and ⁇ 41.5° C.
  • HFA 507c has a boiling point of ⁇ 46.9° C.
  • 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.
  • HFA 123 boils at +27.9° C.
  • HFA 245fa has a boiling point of +15.3° C.
  • propellant is released into the second chamber 20 .
  • 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.
  • 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.
  • the ambient temperature will not be sufficient to boil the propellant and thus the stopper 16 will not move as a consequence.
  • an additional heat source must be provided to boil the propellant and begin movement of the stopper 16 .
  • 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 .
  • the second chamber 20 is made larger.
  • 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 .
  • 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 .
  • 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 .
  • the stopper 16 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 .
  • 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 .
  • 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 .
  • 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 .
  • FIG. 6A shows a time-dependent volume profile of a compressed gas syringe in accordance with the prior art.
  • 5 cc of compressed gas is initially contained in a reservoir which is in selective fluid communication with a volume of the syringe rearward of a stopper.
  • the compressed gas expands rapidly at 500 as the compressed gas fills the dead volume behind the stopper.
  • FIG. 6B shows a time-dependent pressure profile corresponding to the volume profile of FIG. 6A .
  • This drop in pressure occurs both as the compressed gas enters the dead volume (i.e. when the compressed gas reservoir is initially opened) and during the time that the stopper is moving forwards and expelling medicament.
  • the result is an initially steep drop in pressure, followed by a more gradual drop in pressure.
  • the final pressure of the compressed gas is determined by the volume in which it resides at the end of the delivery, when the stopper is at its forwardmost position in the barrel.
  • FIGS. 6A and 6B relate to a syringe where the reservoir of compressed gas is large relative to the internal volume of the system. As a consequence of this, the final pressure of compressed gas is maintained at a relatively high level ( ⁇ 5 bar from an initial 10 bar).
  • FIGS. 7A and 7B relate to a syringe where the reservoir of compressed gas is small (0.3 cc) relative to the internal volume of the system.
  • FIG. 7A shows the time-dependent volume profile of the compressed gas
  • FIG. 7B shows the corresponding time-dependent pressure profile of the compressed gas.
  • FIG. 7A shows a rapid increase in volume at 500 when the compressed gas reservoir is initially opened and the compressed gas fills the dead volume. This is followed by a more gradual increase in volume at 502 as the stopper begins to move and the volume behind the stopper increases. Finally, when the stopper is in its forwardmost position in the barrel, the volume of the compressed gas ceases to increase as shown at 504 of FIG. 7A .
  • the corresponding pressure profile shown in FIG. 7B shows that there is a large and initially rapid reduction in pressure as the gas expands, and then a more gradual decrease in pressure as the stopper begins to move.
  • FIG. 8A shows a time-dependent volume profile of a syringe powered by 0.3 cc of a liquefied propellant in accordance with an embodiment of the present invention.
  • the propellant will be a liquid in equilibrium with a saturated vapour.
  • the volume behind the stopper increases and permits the volume of the gas to increase further as shown at 502 .
  • the volume of gas plateaus, as shown at 504 .
  • the propellant since the mass of gas increases as the liquid boils, the propellant generates more gas at the vapor pressure and therefore maintains a more constant pressure as shown in FIG. 8B . Whilst there is an initial variation in gas pressure as the reservoir is first put into fluid communication with the volume behind the stopper, there is no significant overall drop in gas pressure as there is with compressed gases, as evidenced by FIGS. 6B and 7B . Consequently, the present invention offers a much more consistent pressure profile with a very small initial volume of propellant.
  • FIG. 9 shows an example of a pressure profile (i.e. vapor pressure vs. time within the second chamber 20 ) exhibited by a syringe such as the one described above in relation to FIG. 1A during use.
  • Point A indicates the start of propellant release into the second chamber 20 and the subsequent boiling of the propellant which results in a very fast increase in vapor pressure over a first time period (typically of the order of 10-100 ms) up to point B.
  • the vapor pressure in the second chamber 20 is great enough to cause the stopper 16 to move axially forwardly and begin expulsion of medicament from the first chamber 18 .
  • the stopper 16 may start to move just before point B is reached as the pressure in the second chamber 20 is sufficient to overcome the frictional resistance of the stopper 16 in the syringe 10 .
  • the thermodynamics of the syringe 10 dictate that the vapor pressure drops during delivery. This is shown in the pressure profile of FIG. 9 as the negative gradient between points B and C over a second time period, where point C is indicative of the instant where axial movement of the stopper 16 ceases to continue (i.e. the end of delivery). Consequently, the vapor pressure at C is lower than the vapor pressure at B.
  • a third time period between point C and point D represents the vapor increase in the second chamber 20 as the propellant therein absorbs heat from the environment.
  • point D represents substantially this vapor pressure.
  • the vapor pressure at D is greater than both the vapor pressures at B and C (and of course A). This may be because the stopper 16 began moving axially forwardly before the propellant could reach its vapor pressure at the temperature of its immediate environment.
  • the pressure profile of FIG. 9 reveals that there is not necessarily a simple constant pressure acting on the stopper 16 (i.e. the vapor pressure in the second chamber 20 ) during delivery.
  • this pressure profile may be manipulated so as to provide a more reliable and/or useful device, and/or be more suitable for a particular medicament or application.
  • the form of the pressure profile is dependent 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.
  • syringes 10 in accordance with the present invention are described below with reference to FIGS. 2 to 6 . Given the differences in configuration, the various embodiments of syringes 10 will each exhibit a different pressure profile of vapor pressure in the second chamber 20 during use.
  • FIG. 1B a syringe 10 is shown that is largely the same as that shown in FIG. 1A , except that the third chamber 22 is no longer defined by a rupturable wall 24 forming a self-contained container 21 .
  • the rupturable wall 24 extends across the barrel 12 in a direction substantially perpendicular to the longitudinal direction of the syringe 10 (which is parallel the axial directions referred to above). Therefore, for the syringe 10 of FIG. 1B , the third chamber 22 is defined by the rupturable wall 24 and the walls of the barrel 12 .
  • the third chamber may be defined by the rupturable wall 24 and possibly the walls of an additional component (which may not be enveloped by or contained within the barrel 12 ), but where the rupturable wall provides a boundary between the third chamber 22 and the second chamber 20 .
  • the rupturable wall may, for example, be a septum separating the third chamber 22 and second chamber 20 .
  • the rupturable wall 24 need not necessarily be perpendicular to the longitudinal axis of the syringe 10 , nor need it be disposed in a single plane. As with the syringe 10 of FIG. 1A , the syringe 10 of FIG.
  • a rupturing portion (not shown) causes the rupturable wall 24 to rupture so as to form a fluid connection between the third chamber 22 and the second chamber 20 thereby permitting the flow of propellant from the third chamber 22 into the second chamber 20 .
  • the stopper 16 of the syringe 10 of FIG. 1B will then move axially forwardly under the force of the vapor pressure in the second chamber 20 to expel medicament from the first chamber 28 through the outlet 14 .
  • FIG. 1C A further embodiment of a syringe in accordance with the present invention is shown in FIG. 1C .
  • the syringe 10 of FIG. 1C differs from the syringe of FIG. 1B in that the third chamber 22 is not only defined by a rupturable wall 24 , but also by a non-rupturable wall (or walls) 26 extending between the walls of the barrel 12 along an internal circumference of the barrel 12 .
  • the non-rupturable wall 26 extends from the barrel 12 and has a central aperture across which the rupturable wall 24 extends.
  • any configuration of rupturable walls 24 , or rupturable walls 24 and non-rupturable walls 26 may form a third chamber 22 that does not bisect the longitudinal axis of the syringe 10 .
  • the extent of the rupturable wall 24 (which is largely determined by the size of the aperture in the non-rupturable wall 26 ) will largely determine the flow rate of propellant from the third chamber 22 to the second chamber 20 upon rupturing of the rupturable wall 24 .
  • FIG. 1D A further embodiment of a syringe in accordance with the present invention is shown in FIG. 1D .
  • the syringe 10 of FIG. 1D comprises a non-rupturable wall 26 extending across the barrel 12 along an inner circumference of the barrel 12 .
  • the non-rupturable wall 26 does not form a continuous disc and has an axial aperture 26 a therethrough.
  • the non-rupturable wall 26 defines a fourth chamber 28 which is fluidly connected to the second chamber 20 via aperture 26 a which defines a propellant channel.
  • the fourth chamber 28 contains a container 21 as described above in relation to FIG. 1A .
  • the rupturable wall 24 of the container ruptures to fluidly connect the third chamber 22 to the fourth chamber 28 , and therefore also to the second chamber 20 via the aperture 26 a .
  • the extent of the aperture 26 a largely determines the flow rate of propellant from the fourth chamber 28 to the second chamber 20 upon rupturing of the rupturable wall 24 .
  • the aperture 26 a may be a simple hole, or may be any other fluid passageway that connects the fourth chamber 28 to the second chamber 20 .
  • the aperture 26 a may be a labyrinth arrangement or a valve arrangement that opens when the fluid pressure acting on it exceeds a predetermined threshold.
  • a baffle arrangement may prevent or minimize the flow of droplets (e.g. a mist) of propellant passing from the fourth chamber 28 to the second chamber 20 .
  • FIG. 1E Yet another embodiment of a syringe 10 in accordance with the present invention is shown in FIG. 1E .
  • the syringe 10 of FIG. 1E is largely the same as the syringe of FIG. 1D but the propellant channel fluidly connecting the third chamber 22 and the fourth chamber 28 is defined by a propellant conduit 30 .
  • the propellant conduit 30 has a bore therethrough fluidly connecting the third chamber 22 and the fourth chamber 28 , and the bore largely determines the flow rate of propellant from the third chamber 22 to the fourth chamber 28 .
  • the propellant conduit 30 extends axially rearwardly into the fourth chamber by distance L.
  • the axially rearwardly extending propellant conduit 30 acts to limit the quantity of liquid propellant passing from the fourth chamber 28 to the second chamber 20 during use of the syringe 10 .
  • the syringe 10 will be orientated so that the outlet 14 is proximate to an injection site.
  • the syringe 10 will be orientated so that the longitudinal axis of the syringe is held vertically above the injection site (or at least be inclined with respect to the horizontal). In this orientation, liquid propellant exiting the third chamber 22 (i.e. after rupture of rupturable wall 24 ) will move under the influence of gravity towards the non-rupturable wall 26 .
  • the propellant conduit 30 will then extend above some, if not all, of the liquid propellant, depending on the magnitude of L and the quantity of propellant present.
  • the propellant conduit 30 acts to limit or prevent entirely the flow of liquid propellant from the fourth chamber 28 to the second chamber 20 .
  • the syringe 10 may be used at orientations other than vertical (e.g. horizontal, or indeed any orientation between vertical and horizontal) and so it is preferable for L to be sufficient so that the flow of liquid propellant from the fourth chamber 28 to the second chamber 20 is limited, or further preferably, substantially prevented.
  • ⁇ r 2 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, ( ⁇ r 2 H/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 ⁇ l 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 ⁇ l 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.
  • FIG. 1F A similar syringe 10 to that described above in relation to FIG. 1E is shown in FIG. 1F .
  • the third chamber 22 is not defined by a self-contained container 21 , but by a combination of a rupturable wall 24 , non-rupturable wall 26 and the barrel 12 (similar to the embodiment shown in FIG. 1C ).
  • the syringe 10 of FIG. 1F comprises a propellant conduit 30 that extends axially rearwardly into the third chamber 22 by a distance L and has a bore fluidly connecting the third chamber 22 to the second chamber 20 (albeit for the presence of the rupturable wall 24 ).
  • the rupturable wall 24 may be located at any position along the bore of the propellant conduit 30 to temporarily fluidly isolate the third chamber 22 from the second chamber 20 .
  • the propellant conduit 30 acts to limit or prevent entirely the flow of liquid propellant into the second chamber 20 , this time from the third chamber 22 .
  • a labyrinth or valved arrangement may be present to prevent droplets of liquid propellant (e.g. a mist) passing through into the second chamber 20 .
  • 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 26 a does not constitute “regulated delivery”.
  • the propellant passes through the propellant conduit 30 or aperture 26 a at a constant pressure that is lower than the pressure that would be observed if the restriction (propellant conduit 30 or aperture 26 a ) were not present. Indeed, passage through the propellant conduit 30 or aperture 26 a constitutes bolus delivery of the propellant into the second chamber 20 .
  • FIG. 10 shows an example pressure profile of vapor pressure in the second chamber 20 of a syringe 10 where mostly gas propellant is supplied to the second chamber 20 .
  • the pressure profile of FIG. 10 shows that propellant enters the second chamber 20 at point A and immediately results in an increase of vapor pressure in the second chamber 20 to an initial maximum vapor pressure and point B.
  • the rate of increase of vapor pressure decreases slightly immediately prior to reaching point B.
  • the change from point A to point B occurs over a first time period.
  • the vapor pressure then decreases slightly over a second time period as the stopper 16 begins to move axially forwardly to deliver medicament until point C is reached.
  • point C represents the end of delivery when the stopper 16 has reached the front of the barrel 12 and is no longer moving axially forwardly.
  • the propellant in the second chamber 20 absorbs heat from the environment which increases the vapor pressure within the second chamber 20 . This increase tends towards the vapor pressure of the propellant at the temperature of its immediate environment (e.g. ambient temperature) which is indicated at point D, where the time period between points C and D is a third time period.
  • FIG. 11 shows an example of a pressure profile of a syringe 10 in accordance with the present invention where substantially only gas propellant is introduced into the second chamber 20 .
  • the pressure profile of FIG. 11 is largely similar to that of FIG. 10 , however, in the pressure profile of FIG. 11 , there is substantially no change in the vapor pressure between points B and C. That is, during delivery, there is a substantially constant vapor pressure in the second chamber 20 .
  • the vapor pressure increases as the propellant in the second chamber absorbs heat from the environment.
  • 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.
  • FIG. 12 demonstrates the effects of parameter i) on the form of the pressure profile.
  • FIG. 12 represents the pressure profile of a syringe 10 in accordance with the present invention, similar to the syringe that produced the pressure profile of FIG. 9 .
  • the syringe 10 associated with the pressure profile of FIG. 12 additionally includes apparatus to further cool the propellant in the second chamber 20 during use.
  • further cool is meant reducing the temperature of the propellant in the second chamber 20 by an amount that is more than if the apparatus to further cool were not present, i.e. where the only reduction in temperature in liquid propellant is due to loss of latent heat of vaporization.
  • the propellant in the second chamber 20 can be further cooled by several methods within the scope of the present invention.
  • a coolant or refrigerant (which may be an additional supply of the propellant) may be applied to the outside of the barrel 12 proximate the second chamber 20 so that the portion of the barrel 12 proximate the second chamber 12 is cooled thereby removing some of its thermal energy such that it has less thermal energy to supply to the propellant in the second chamber 20 .
  • the liquid propellant has less thermal energy available to it from the barrel 12 proximate the second chamber 20 as it otherwise would. Therefore, there is less thermal energy available to the liquid propellant in its immediate environment that may be absorbed by the liquid propellant to offset the reduction in temperature due to boiling. For this reason, during operation of the syringe 10 , the drop in vapor pressure in the second chamber 20 is greater than it would otherwise be if no means to cool the propellant therein were in place.
  • any means or method that reduces the thermal energy available to the liquid propellant in the second chamber 20 as it is boiling and causing the stopper 16 to move axially forwardly in the barrel 12 will result in a greater drop in vapor pressure in the second chamber 20 than would otherwise occur if no such means or method were in place.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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.
  • 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 .
  • 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.
  • the materials must also provide other desired physical properties (e.g. strength and durability) to a sufficient degree.
  • 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.
  • 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).
  • 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.
  • 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.
  • 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).
  • 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.
  • first pressure an initial maximum vapor pressure
  • 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 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.
  • 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.
  • 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.
  • 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
  • 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.
  • 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.
  • 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.
  • 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.
  • the action triggered may be the movement of the syringe in the device between the first and second positions.
  • 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.
  • the indicators may include an audible indicator, such as a loud speaker.
  • 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.
  • 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).
  • 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.
  • the injection site e.g. the patient's skin
  • 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.
  • 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).
  • 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.
  • FIGS. 15A and 15B show one specific embodiment of an embodiment of a propellant dispenser 321 for supplying propellant to the second chamber, where the propellant dispenser 321 does not include a rupturable wall.
  • the dispenser 321 comprises a reservoir 324 that defines a central volume 322 containing propellant.
  • Inside the central volume 322 is an internal frame 400 that has a series of channels 400 a , 400 b for allowing propellant to pass therethrough.
  • Within the internal frame 400 are a carriage 402 and a nozzle 406 that are connected to one another.
  • the carriage 402 and nozzle 406 are connected to one another and are axially moveable within the dispenser 321 between a closed position in which propellant cannot exit the dispenser 321 (as shown in FIG.
  • the carriage 402 and hence nozzle 406 , are biased axially forwardly from the frame 400 to the closed position by a biasing member 404 in the form of a spring in the embodiment shown.
  • the carriage 402 and nozzle 406 are moveable through a rear seal 408 a and a forward seal 408 b .
  • the rear seal 408 a and the forward seal 408 b 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 408 b and an opening 321 a of the dispenser 321 in at least the open position.
  • the carriage 402 has a pair of passageways 402 a , 402 b that, together with a hollow region 402 b of the carriage 402 , form a fluidic bypass pathway (indicated as F1 in FIG. 15A ) around the rear seal 408 a when the carriage 402 is in the closed position. Therefore, in the closed position, propellant is able to flow from the central volume 322 to the annulus 410 via the passageways 402 a , 402 b.
  • a fluidic bypass pathway indicated as F1 in FIG. 15A
  • 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 .
  • the closed position there is no fluid pathway from the annulus 410 to outside of the dispenser.
  • nozzle 406 and carriage 402 are moved axially rearwardly (as indicated by arrows M in FIG. 15B ), they act against the spring 404 and move towards their open position.
  • the pair of passageways 402 a , 402 b both move axially rearwardly of the rear seal 408 a so that they no longer form a bypass pathway around the rear seal 408 .
  • the central volume 322 is no longer fluidly connected to the annulus 410 .
  • the annulus 410 is fluidly connected to the outside of the dispenser 321 via one or more radial passageways 406 a in the nozzle 406 that fluidly connect the annulus 410 to a hollow channel 406 b of the nozzle 406 that is open to the external environment of the dispenser 321 , bypassing the forward seal 408 b (indicated by F2 in FIG. 15B ).
  • the open position the entire volume of propellant present in the annulus 410 is dispensed from the dispenser 321 .
  • the one or more radial passageways 406 a do not fluidly connect the annulus 410 to the hollow channel 406 b thus preventing fluid communication between the annulus 410 and the external environment.
  • the dispenser 321 described above with reference to FIGS. 15A and 15B only dispenses a predetermined volume of fluid (propellant) when in the open position, where the predetermined volume is defined by the volume of the annulus 410 .
  • the dispenser will continue to dispense fluid until moved to a closed position.
  • the presently described dispenser 321 is therefore advantageous for use with the present invention in that a predetermined volume of propellant can be provided to the second chamber, where the predetermined volume can be tailored for a particular application, such as for delivering a specified dose of medicament contained in the first chamber.
  • 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.
  • propellant is not delivered continuously such that only the position of the dispenser determines when delivery of propellant will cease.
  • 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.
  • the container is configured to contain a predetermined volume of propellant sufficient for the delivery of a dose of medicament.
  • 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.
  • 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.
  • 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.
  • the inter-engaging member of the valve stem comprises a flange.
  • 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.
  • 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.
  • the valve may further comprise a biasing member (a compression spring, for example) for biasing the valve stem into the non-dispensing position.
  • a biasing member a compression spring, for example
  • 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.
  • 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.
  • 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.
  • 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 ( FIGS. 1E and 1F , for example) or by any suitable alternative means, such as using a propellant source that only supplies gaseous propellant, or supplies a desired ratio of liquid and gaseous propellant to the second chamber.
  • 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.
  • 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:
  • 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 may be executed by measurement of pressure or a calculation that may be a computer implemented calculation.
  • a syringe design is reached that exhibits the desired pressure profile, a syringe may be manufactured according to that design.
  • FIGS. 2 and 3 may be used.
  • a container 121 is shown to be made of an upper sheet 124 a and a lower sheet 124 b which together form a rupturable wall 124 of the container 121 .
  • the sheets 124 a , 124 b are generally square or rectangular in shape in the embodiment shown in FIG. 2 and are sealed to one another about their periphery forming seals 125 .
  • the seals 125 circumvent a central volume 122 formed between the sheets 124 a , 124 b .
  • This volume 122 is equivalent to the third chamber described above in relation to container 22 and contains a volume of propellant which is predominantly in its liquid phase at the operating temperature of the syringe (e.g. ambient temperature) due to being in the sealed volume 122 .
  • the propellant will exert an outward pressure from within the volume 122 . Therefore, the seals 125 must be sufficient to prevent substantial loss of propellant from the volume 125 .
  • an ideal seal 125 will entirely prevent propellant escaping therethrough from the volume 122 , however in practice, the seals 125 may be such that a finite, albeit acceptable and not substantial, amount of propellant may escape from the volume 122 .
  • the magnitude of “acceptable” amount will depend upon the perceived shelf life of the container (i.e. the length of time that the container 125 may remain in storage following manufacture prior to use), and the volume of propellant required to perform the desired action.
  • the material that forms the sheets 124 a , 124 b 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.
  • 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 ⁇ l of propellant in the container 121 . Therefore, over a two year storage period, a container 121 initially containing 100 ⁇ l of HFA propellant may lose up to 80 ⁇ l as gas through the rupturable wall 124 for there to be at least 20 IA remaining to deliver the 1 ml dose of medicament.
  • the maximum gas permeability of the container 121 would be 0.365 g/(m 2 .day).
  • a container 121 having a gas permeability that ensures that there is 5 ⁇ l 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).
  • the rupturable wall may be composed substantially of nylon.
  • one or each sheet 124 a , 124 b 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.
  • the seals 125 are formed between two like materials. So, in the case where one or both of the sheets 124 a , 124 b comprise laminates of two or more materials, the sheets 124 a , 124 b 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 FIG. 2 . Indeed, any suitable shape that is able to contain the propellant in the volume 122 sealed by the seals 125 may be used in accordance with the present invention. However, the shape of the container should be such that the outward pressure exerted by the propellant is resisted to ensure that such pressure does not inadvertently rupture the container 121 .
  • FIG. 3 shows a container 221 in accordance with an alternative embodiment of the present invention.
  • the container 221 has a generally cylindrical rupturable wall 224 that is pinched at either end to form seals 225 that are sealed by one of the above described sealing methods.
  • the rupturable wall 224 defines a central volume 222 for containing fluid propellant that, again, is equivalent to the third chamber 22 of embodiments described above.
  • the rupturable wall may be formed from the materials described above in connection with rupturable wall 124 of the embodiment of FIG. 2 .
  • the container 221 has the advantage that fewer seals 125 are required since a single cylindrical piece of material is used to form the rupturable wall 224 . Therefore, there are fewer potential leak paths that the propellant may escape the volume 222 through.
  • Either of the containers 121 and 221 may be used in any of the syringes described above in accordance with the present invention.
  • the containers 121 , 221 may be used in other applications, including other medical devices.
  • 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.
  • 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.
  • the propellant is or contains HFA and further preferable is or contains HFA 134a.
  • mixtures of several propellant substances or propellant substances and additives may provide a propellant for use in accordance with the present invention.
  • 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 .
  • FIGS. 13A to 13D A schematic representation of a method of manufacturing a container, such as the container 221 shown in FIG. 3 , is shown in FIGS. 13A to 13D .
  • FIG. 13A shows an extruded tube 224 formed of a rupturable material that has been sealed at a lower end by a lower seal 225 a .
  • the tube 224 defines a central volume 222 therein.
  • a piercing element 302 is provided that is adapted to form an opening 304 through the material of the tube 224 so as to provide a fluidic channel between the central volume 222 and the outside of the tube 224 .
  • 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.
  • the piercing element 302 is a hypodermic needle.
  • the first sealing elements 304 may then be used to form a first upper seal 225 b above (i.e. upstream) of the opening 304 as shown in FIG. 13B .
  • a propellant dispensing head 310 (which is connected to a source of propellant—not shown) is inserted into the opening 304 and seals the opening 304 .
  • the propellant dispensing head 310 may comprise seal rings to aid the sealing of the opening 304 .
  • the propellant dispensing head 310 may additionally have the feature of being the piercing element 302 and may form the opening 304 at this stage (i.e. subsequent to the formation of the first upper seal 225 b.
  • a predetermined dose of propellant 300 is then introduced into the central volume 222 to fill the tube 224 to the desired level.
  • a second upper seal 225 c is then formed by second sealing element 308 below (i.e. downstream) each of the first upper seal 225 b and the opening 304 .
  • the central volume 222 containing the propellant 300 is sealed at an upper end by second upper seal 225 c and at a lower end by the lower seal 225 a thus forming a propellant container 221 .
  • the container 221 may be cut along lower seal 225 a and second upper seal 225 c to separate the container 221 .
  • 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 .
  • the second upper seal 225 c 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 225 b of the tube 224 becomes the lower seal 225 a ′ 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 225 a and second upper seal 225 c 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.
  • FIG. 14A shows two sheets 124 a , 124 b of like material being brought together by a set of rollers 412 rotating in direction R.
  • the cross-sectional views shown in FIGS. 14A and 14B show only two rollers 412
  • the set actually comprises four rollers 412 as shown in the perspective view of FIG. 14C .
  • the rollers 412 are arranged in pairs such that the two sheets 124 a , 124 b of material come together between the pairs, where the two rollers of each pair are spaced and arranged along edges of the sheets 124 a , 124 b .
  • the rotation of the rollers 412 along direction R causes the sheets 124 a , 124 b to come together with one another along their edges (which are coincident with the position of the rollers 412 ) and move downwards along direction D.
  • the edges of the sheets 124 a , 124 b seal to one another to form side seals 125 b , 125 c .
  • the rollers 412 may comprise means to form the side seals 125 b , 125 c or additional sealing apparatus may be employed to form the side seals 125 b , 125 c.
  • Sealing elements 408 seal the sheets 124 a , 124 b together across their entire width to form a lower seal 125 a .
  • a propellant dispensing head 410 is arranged between the sheets 124 a , 124 b and between the four rollers 412 and is arranged relative to the sheets 124 a , 124 b and the rollers 412 so that the sheets 124 a , 124 b 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 125 a , 125 b , 125 c and the seals between the sheets 124 a , 124 b and the propellant dispensing head 410 .
  • the propellant dispensing head 410 is able to deposit a desired dose of propellant 300 into the central volume 122 .
  • 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 124 a , 124 b above the deposited propellant 300 to form an upper seal 125 d .
  • Any or all of the seals 125 a , 125 b , 125 c , 125 d may be heat seals, sonic welds or other seals, such as adhesive seals.
  • the upper seal 125 d may then form the lower seal 125 a ′ of a subsequent container 121 ′ (see FIG. 14C ) so that the process may be repeated to produce a series of connected containers 121 , 121 ′, . . . , etc.
  • Lower and upper seals 125 a , 125 d may be cut or otherwise severed to separate each container 121 . This separation may be done when a series of containers has been produced or after the formation of each container 121 .
  • the pitch of the containers (e.g. the distance between lower seal 125 a and upper seal 125 c ) may be altered to change the magnitude of the central volume 122 in accordance with the desired dose of propellant 300 .
  • 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).
  • 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.
  • 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.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • General Health & Medical Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Vascular Medicine (AREA)
  • Mechanical Engineering (AREA)
  • Chemical & Material Sciences (AREA)
  • Dispersion Chemistry (AREA)
  • Fluid Mechanics (AREA)
  • Physics & Mathematics (AREA)
  • Pulmonology (AREA)
  • Environmental & Geological Engineering (AREA)
  • General Engineering & Computer Science (AREA)
  • Infusion, Injection, And Reservoir Apparatuses (AREA)
  • Containers And Packaging Bodies Having A Special Means To Remove Contents (AREA)
  • Containers And Plastic Fillers For Packaging (AREA)
  • Mechanically-Actuated Valves (AREA)
  • Nozzles (AREA)
  • Vacuum Packaging (AREA)
  • Closures For Containers (AREA)
  • Making Paper Articles (AREA)
  • Closing Of Containers (AREA)
US14/406,171 2012-06-07 2013-06-07 Syringe Abandoned US20150141918A1 (en)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
GB1210082.2 2012-06-07
GBGB1210082.2A GB201210082D0 (en) 2012-06-07 2012-06-07 Improved syringe
PCT/GB2013/051508 WO2013182857A1 (en) 2012-06-07 2013-06-07 Improved syringe

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US20150141918A1 true US20150141918A1 (en) 2015-05-21

Family

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Application Number Title Priority Date Filing Date
US14/406,171 Abandoned US20150141918A1 (en) 2012-06-07 2013-06-07 Syringe
US14/406,172 Active 2034-01-30 US10414579B2 (en) 2012-06-07 2013-06-07 Venting syringe
US14/406,178 Abandoned US20150151045A1 (en) 2012-06-07 2013-06-07 Method of manufacturing a propellant container
US14/406,167 Active US11053066B2 (en) 2012-06-07 2013-06-07 Propellant powered syringe with trigger
US14/406,083 Active US9527657B2 (en) 2012-06-07 2013-06-07 Dispensing valves

Family Applications After (4)

Application Number Title Priority Date Filing Date
US14/406,172 Active 2034-01-30 US10414579B2 (en) 2012-06-07 2013-06-07 Venting syringe
US14/406,178 Abandoned US20150151045A1 (en) 2012-06-07 2013-06-07 Method of manufacturing a propellant container
US14/406,167 Active US11053066B2 (en) 2012-06-07 2013-06-07 Propellant powered syringe with trigger
US14/406,083 Active US9527657B2 (en) 2012-06-07 2013-06-07 Dispensing valves

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US (5) US20150141918A1 (enrdf_load_stackoverflow)
EP (5) EP2858905B8 (enrdf_load_stackoverflow)
JP (5) JP2015523879A (enrdf_load_stackoverflow)
CN (5) CN104520197B (enrdf_load_stackoverflow)
AU (5) AU2013273354B2 (enrdf_load_stackoverflow)
BR (5) BR112014030397B1 (enrdf_load_stackoverflow)
CA (5) CA2874166C (enrdf_load_stackoverflow)
ES (4) ES2847899T3 (enrdf_load_stackoverflow)
GB (5) GB201210082D0 (enrdf_load_stackoverflow)
IN (5) IN2014DN11116A (enrdf_load_stackoverflow)
WO (5) WO2013182861A1 (enrdf_load_stackoverflow)

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